US20080097476A1 - Precision control systems for tissue visualization and manipulation assemblies - Google Patents
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Abstract
Precision control systems for tissue visualization and manipulation assemblies are described herein where such devices may utilise a variety of apparatus and methods for facilitating advancement, articulation, control, navigation, etc. of systems which may be used to visual and/or treat tissue regions. Additionally, methods and devices for enhancing navigation of the device through a patient body are also described.
Description
- This application claims the benefit of priority to U.S. Prov. Pat. App. 60/824,421 filed Sep. 1, 2006 and to U.S. Prov. Pat. App. 60/916,640 filed. May 8, 2007, each of which is incorporated herein by reference in its entirety.
- The present invention relates generally to medical devices used for accessing, visualizing, and/or treating regions of tissue within a body. More particularly, the present invention relates to systems for controlling and navigating devices used to directly visualize and/or manipulate tissue regions within a body lumen which are generally difficult to access and/or image.
- Conventional devices for visualizing interior regions of a body lumen are known. For example, ultrasound devices have been used to produce images from within a body in vivo. Ultrasound has been used both with, and without contrast agents, which typically enhance ultrasound-derived images.
- Other conventional methods have utilized catheters or probes having position sensors deployed within the body lumen, such as the interior of a cardiac chamber. These types of positional sensors are typically used to determine the movement of a cardiac tissue surface or the electrical activity within the cardiac tissue. When a sufficient number of points have been sampled by the sensors, a “map” of the cardiac tissue may be generated.
- Another conventional device utilizes an inflatable balloon which is typically introduced intravascularly in a deflated state and then inflated against the tissue region to be examined. Imaging is typically accomplished by an optical fiber or other apparatus such as electronic chips for viewing the tissue through the membrane(s) of the inflated balloon. Moreover, the balloon must generally be inflated for imaging. Other conventional balloons utilize a cavity, or depression formed at a distal end of the inflated balloon. This cavity or depression is pressed against the tissue to be examined and is flushed with a clear fluid to provide a clear pathway through the blood.
- However, such imaging balloons have many inherent disadvantages. For instance, such balloons generally require that the balloon be inflated to a relatively large size which may undesirably displace surrounding tissue and interfere with fine positioning of the imaging system against the tissue. Moreover, the working area created by such inflatable balloons are generally cramped and limited in size. Furthermore, inflated balloons may be susceptible to pressure changes in the surrounding fluid. For example, if the environment surrounding the inflated balloon undergoes pressure changes, e.g., during systolic and diastolic pressure cycles; in a beating heart, the constant pressure change may affect, the inflated balloon volume and its positioning to produce unsteady or undesirable conditions for optimal tissue imaging.
- Accordingly, these types of imaging modalities are generally unable to provide desirable images useful for sufficient diagnosis and therapy of the endoluminal structure, due in part to factors such as dynamic forces generated by the natural movement of the heart. Moreover, anatomic structures within, the body can occlude or obstruct the image acquisition process. Also, the presence and movement of opaque bodily fluids such as blood generally make in vivo imaging of tissue regions within the heart difficult.
- Other external imaging modalities are also conventionally utilized. For example, computed tomography (CT) and magnetic resonance imaging (MRI) are typical modalities which are widely used to obtain images of body lumens such as the interior chambers of the heart. However, such imaging modalities fail to provide real-time imaging for infra-operative therapeutic procedures. Fluoroscopic imaging, for instance, is widely used to identify anatomic landmarks within the heart and other regions of fire body. However, fluoroscopy fails to provide an accurate image of the tissue quality or surface and also fails to provide for instrumentation for performing tissue manipulation or other therapeutic procedures upon the visualized tissue regions. In addition, fluoroscopy provides a shadow of tire intervening tissue onto a plate or sensor when it may be desirable to view the intraluminal surface of the tissue to diagnose pathologies or to perform some form of therapy on it.
- Thus, a tissue imaging system which is able to provide real-time in vivo images of tissue regions within body lumens such as the heart through opaque media such as blood and which also provide instruments for therapeutic procedures upon the visualized tissue are desirable.
- A tissue imaging and manipulation apparatus that may be utilized for procedures within a body lumen, such as the heart, in which visualization of the surrounding tissue is made difficult, if not impossible, by medium contained within the lumen such as blood, is described below. Generally, such a tissue imaging and manipulation apparatus comprises ah optional delivery catheter or sheath through which a deployment catheter and imaging hood may be advanced for placement against or adjacent to the tissue to be imaged.
- The deployment catheter may define a fluid delivery lumen therethrough as well as an imaging lumen within which an optical imaging fiber or assembly may be disposed for imaging tissue. When deployed, the imaging hood may be expanded into any number of shapes, e.g., cylindrical, conical as shown, semi-spherical, etc., provided that an open area or field is defined by the imaging hood. The open area is the area within which the tissue region of interest may be imaged. The imaging hood may also define an atraumatic contact lip or edge for placement or abutment against the tissue region of interest. Moreover, the distal end of the deployment catheter or separate manipulatable catheters may be articulated through various controlling mechanisms such as push-pull wires manually or via computer control
- The deployment catheter may also be stabilized relative to the tissue surface through various methods. For instance, inflatable stabilizing balloons positioned along a length of the catheter may be utilized, or tissue engagement anchors may be passed through or along the deployment catheter for temporary engagement of the underlying tissue.
- In operation, after the imaging hood has been deployed, fluid may be pumped at a positive pressure through the fluid delivery lumen until the fluid fills the open area completely and displaces any blood from within the open area. The fluid may comprise any biocompatible fluid, e.g., saline, water, plasma, Fluorinert™, etc., which is sufficiently transparent to allow for relatively undistorted visualization through the fluid. The fluid may be pumped continuously or intermittently to allow for image capture by an optional processor which may be in communication with the assembly.
- In an exemplary variation for imaging tissue surfaces within a heart chamber containing blood, the tissue imaging and treatment system may generally comprise a catheter body having a lumen defined therethrough, a visualization element disposed adjacent the catheter body, the visualization element having a field of view, a transparent fluid source in fluid communication with the lumen, and a barrier or membrane extendable from the catheter body to localize, between the visualization element and the field of view, displacement of blood by transparent fluid that flows from the lumen, and a piercing instrument translatable through the displaced blood for piercing into the tissue surface within the field of view.
- The imaging hood may be formed into any number of configurations and the imaging assembly may also be utilized with any number of therapeutic tools which may be deployed through the deployment catheter.
- Moreover, the imaging hood may be utilized with various catheter control assemblies to provide for precise catheter motion. For instance, robotically-controlled catheter systems may be utilized with, the imaging hood and various instruments delivered through the hood. Alternatively, magnetic navigational systems may also be utilized to control and/or locate a hood within the patient body.
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FIG. 1A shows a side view of one variation of a tissue imaging apparatus during deployment from a sheath or delivery catheter. -
FIG. 1B shows the deployed tissue imaging apparatus ofFIG. 1A having an optionally expandable hood or sheath attached to an imaging and/or diagnostic catheter. -
FIG. 1C shows an end view of a deployed imaging apparatus. -
FIGS. 1D to 1F show the apparatus ofFIGS. 1A to 1C with an additional lumen, e.g. for passage of a guidewire therethrough. -
FIGS. 2A and 2B show one example of a deployed tissue imager positioned against or adjacent to the tissue to be imaged and a flow of fluid, such as saline, displacing blood from within the expandable hood. -
FIG. 3A shows an articulatable imaging assembly which may be manipulated, via push-pull wires or by computer control. -
FIGS. 3B and 3C show steerable instruments, respectively, where an articulatable delivery catheter may be steered within the imaging hood or a distal portion of the deployment catheter itself may be steered. -
FIGS. 4A to 4C show side and cross-sectional end views, respectively, of another variation having an off-axis imaging capability. -
FIG. 5 shows an illustrative view of an example of a tissue imager advanced intravascularly within a heart for imaging tissue regions within an atrial chamber. -
FIGS. 6A to 6C illustrate deployment catheters having one or more optional inflatable balloons or anchors for stabilizing the device during a procedure. -
FIGS. 7A and 7B illustrate a variation of an anchoring mechanism such as a helical tissue piercing device for temporarily stabilizing the imaging hood relative to a tissue surface. -
FIG. 7C shows another variation for anchoring the imaging hood having one or more tubular support members integrated with the imaging hood; each support members may define a lumen therethrough for advancing a helical tissue anchor within. -
FIG. 8A shows an illustrative example of one variation of how a tissue imager may be utilized with an imaging device. -
FIG. 8B shows a further illustration of a hand-held variation of the fluid delivery and tissue manipulation system. -
FIGS. 9A to 9C illustrate an example of capturing several images of the tissue at multiple regions. -
FIGS. 10A and 10B show charts illustrating how fluid pressure within the imaging hood may be coordinated with the surrounding blood pressure; the fluid pressure in the imaging hood may be coordinated with the blood pressure or it may be regulated based, upon pressure feedback from the blood. -
FIG. 11A shows a side view of another variation of a tissue imager having an imaging balloon within an expandable hood. -
FIG. 11B shows another variation of a tissue imager utilizing a translucent or transparent imaging balloon. -
FIG. 12A shows another variation in which a flexible expandable or distensible membrane may be incorporated within the imaging hood to alter the volume of fluid dispensed. -
FIGS. 12B and 12C show another variation in which, the imaging hood may be partially or selectively deployed from the catheter to alter the area of the tissue being visualized as well as the volume of the dispensed fluid. -
FIGS. 13A and 13B show exemplary side and cross-sectional views, respectively, of another variation, in which the injected fluid may be drawn back into the device for minimizing fluid input into a body being treated. -
FIGS. 14A to 14D show various configurations and methods for configuring an imaging hood into a low-profile for delivery and/or deployment. -
FIGS. 15A and 15B show an imaging hood having an helically expanding frame or support. -
FIGS. 16A and 16B show another imaging hood having one or more hood support members, which, are pivotably attached at their proximal ends to deployment catheter, integrated with a hood membrane. -
FIGS. 17A and 17B show yet another variation of the imaging hood having at least two or more longitudinally positioned support members supporting the imaging hood membrane where the support members are movable relative to one another via a torquing or pulling or pushing force. -
FIGS. 18A and 18B show another variation where a distal portion of the deployment catheter may have several pivoting members which form a tubular shape in its low profile configuration. -
FIGS. 19A and 19B show another variation where the distal portion, of deployment catheter may be fabricated from a flexible metallic or polymeric material to form a radially expanding hood. -
FIGS. 20A and 20B show another variation where the imaging hood may be formed from a plurality of overlapping hood members which overlie one another in an overlapping pattern. -
FIGS. 21A and 21B show another example of an expandable hood which is highly conformable against tissue anatomy with varying geography. -
FIG. 22A shows yet another example of an expandable hood having a number of optional electrodes placed about the contact edge or lip of the hood for sensing tissue contact or detecting arrhythmias. -
FIG. 22B shows another variation for conforming the imaging hood against the underlying tissue where an inflatable contact edge may be disposed around the circumference of the imaging hood. -
FIG. 23 shows a variation of the system which may be instrumented with a transducer for detecting the presence of blood seeping back into the imaging hood. -
FIGS. 24A and 24B show variations of the imaging hood instrumented with sensors for detecting, various physical parameters; the sensors may be instrumented around the outer surface of the imaging hood and also within the imaging hood. -
FIGS. 25A and 25B show a variation where the imaging hood may have one or more LEDs over the hood itself for providing illumination of the tissue to be visualized. -
FIGS. 26A and 26B show another variation in which a separate illumination tool having one or more LEDs mounted thereon may be utilized within the imaging hood. -
FIG. 27 shows one example of how a therapeutic tool may be advanced through the tissue imager for treating a tissue region of interest. -
FIG. 28 shows another example of a helical therapeutic tool for treating the tissue region of interest. -
FIG. 29 shows a variation, of how a therapeutic tool may be utilized with an expandable imaging balloon. -
FIGS. 30A and 30B show alternative configurations for therapeutic instruments which may be utilized; one variation is shown having an angled instrument arm and another variation is shown with an off-axis instrument arm. -
FIGS. 31A to 31C show side and end views, respectively, of an imaging system which may be utilized with an ablation probe. -
FIGS. 32A and 32B show side and end views, respectively, of another variation of the imaging hood with an ablation probe, where the imaging hood may be enclosed, for regulating a temperature of the underlying tissue. -
FIGS. 33A and 33B show an example in which the imaging fluid itself may be altered in temperature to facilitate various procedures upon the underlying tissue. -
FIGS. 34A and 34B show an example of a laser ring generator which may be utilized with the imaging system and an example for applying the laser ring generator within the left, atrium of a heart for treating atrial fibrillation. -
FIGS. 35A to 35C show an example of an extendible cannula generally comprising an elongate tubular member which may be positioned within the deployment catheter during delivery and then projected distally through the imaging hood and optionally beyond. -
FIGS. 36A and 36B show side and end views, respectively, of an imaging hood having one or more tubular support members integrated with the hood for passing instruments or tools therethrough for treatment upon the underlying tissue. -
FIGS. 37A and 37B illustrate how an imaging device may be guided within a heart chamber to a region, of interest utilizing a lighted probe positioned temporarily within, e.g., a lumen of the coronary sinus. -
FIGS. 38A and 38B show an imaging hood having a removable disk-shaped member for implantation upon the tissue surface. -
FIGS. 39A to 39C show one method for implanting the removable disk ofFIGS. 38A and 38B . -
FIGS. 40A and 40B illustrate an imaging hood having a deployable anchor assembly attached to the tissue contact edge and an assembly view of the anchors and the suture or wire connected to the anchors, respectively -
FIGS. 41A to 41D show one method for deploying the anchor assembly ofFIGS. 40A and 40B for closing an opening or wound. -
FIG. 42 shows another variation in which the imaging system may be fluidly coupled to a dialysis unit for filtering a patient's blood. -
FIGS. 43A and 43B show a variation of the deployment catheter having a first deployable hood and a second deployable hood positioned distal to the first hood: the deployment catheter may also have a side-viewing imaging element positioned between the first and second hoods for imaging tissue between the expanded hoods. -
FIGS. 44A and 44B show side and end views, respectively, of a deployment catheter having a side-imaging balloon in an un-inflated low-profile configuration. -
FIGS. 45A to 45C show side, top, and end views, respectively, of the inflated balloon, ofFIGS. 44A and 44B defining a visualization field in the inflated balloon. -
FIGS. 46A and 46B show side and cross-sectional end views, respectively, for one method of use in visualizing a lesion upon a vessel wall within the visualisation field of the inflated balloon fromFIGS. 45A to 45C. -
FIGS. 47A and 47B show assembly views of examples of a robotically-controlled guide instrument for precisely controlling a position of a hood. -
FIG. 47C illustrates an example of how a robotic guide instrument may be utilized with a visualization system. -
FIGS. 48A and 48B show perspective views of a variation of a robotic control assembly showing base having four proximal drive assemblies and the imaging hood positioned at a distal end of the catheter. -
FIG. 48C illustrates a perspective view of another variation of a robotic control assembly having an inflatable imaging balloon assembly. -
FIG. 49 shows a partially disassembled perspective view of the precision control driver. -
FIG. 50 shows a perspective assembly view of the guide instrument mounted upon an instrument driver. -
FIG. 51 shows the partially disassembled perspective view of the catheter instrument driver. -
FIGS. 52A and 52B show perspective views of another variation of the tissue visualization catheter with precision control steering. -
FIG. 53 illustrates an example of a simplified assembly view of the mechanisms within, the control drive unit for controlling the articulation of hood. -
FIGS. 54A and 54B show an assembled view and exploded assembly view, respectively, of a tissue visualization hood having a pivotably articulating steering assembly. -
FIGS. 55A to 55C show an assembled view, detailed spine, and exploded assembly view, respectively, of a tissue visualization hood utilizing steerable spine segments. -
FIGS. 56A to 56C show another variation in an assembled view, detailed spine, and exploded assembly view, respectively, of a tissue visualization hood also utilizing steerable spine segments. -
FIG. 57A shows a perspective view of a hood having a ferromagnetic ring attached circumferentially around the lip of the hood. -
FIG. 57B shows a perspective view of an example of a magnetic navigation system, which, may be used to steer the imaging hood through the patient body. -
FIG. 58 shows a perspective view of another variation, of the tissue visualization catheter which is configured to detect the position and/or orientation of the hood via ultrasound transducers and having a magnetic ring circumferentially positioned about the lip of the hood. -
FIG. 59 shows a perspective view of another variation of the tissue visualization catheter which is configured to detect the position and/or orientation of the hood via ultrasound, transducers and having electromagnetic coils wound about one or more struts. -
FIG. 60 shows a perspective view of another variation of the tissue visualization catheter having a ferromagnetic disc positioned within the hood. -
FIG. 61 shows a perspective view of a position sensor assembly which may be utilized to detect, an orientation and/or location of the hood within the body as well as to draw the hood against an internal tissue region. -
FIG. 62 illustrates an example of triangulation of the transducers to determine the orientation and position of the hood within a patient body. -
FIGS. 63A to 63C illustrate an example for orienting and drawing a hood within a left atrial chamber against the tissue surface to “walk” the hood along the tissue wall to visually survey the underlying surface. -
FIG. 64 illustrates another example where a catheter having several transducers may be positioned within, the coronary sinus to communicate with the hood. - A tissue-imaging and manipulation apparatus described below is able to provide real-time images in vivo of tissue regions within a body lumen such as a heart, which is filled with blood flowing dynamically therethrough and is also able to provide intravascular tools and instruments for performing various procedures upon the imaged tissue regions. Such an apparatus may be utilized for many procedures, e.g., facilitating transseptal access to the left, atrium, cannulating the coronary sinus, diagnosis of valve regurgitation/stenosis, valvuloplasty, atrial appendage closure, arrhythmogenic focus ablation, among other procedures.
- One variation of a tissue access and imaging apparatus is shown in the detail perspective views of
FIGS. 1A to 1C. As shown inFIG. 1A , tissue imagine andmanipulation assembly 10 may be delivered intravascularly through the patient's body in a low-profile configuration via a delivery catheter orsheath 14. In the case of treating tissue, such as the mitral valve located at the outflow tract of the left atrium of the heart, it is generally desirable to enter or access the left atrium while minimizing trauma to the patient. To non-operatively effect such access, one conventional approach involves puncturing the intra-atrial septum from the right atrial chamber to the left atrial, chamber in a procedure commonly called a transseptal procedure or septostomy. For procedures such as percutaneous valve repair and replacement, transseptal access to the left, atrial chamber of the heart may allow for larger devices to be introduced into the venous system than can generally be introduced percutaneously into the arterial system. - When the imaging and
manipulation assembly 10 is ready to be utilized for imaging tissue.Imaging hood 12 may be advanced relative tocatheter 14 and deployed from a distal, opening ofcatheter 14, as shown by the arrow. Upon deployment,imaging hood 12 may be unconstrained to expand, or open into a deployed imaging configuration, as shown inFIG. 1B .Imaging hood 12 may be fabricated from a variety of pliable or conformable biocompatible material including but not limited to, e.g., polymeric, plastic, or woven materials. One example of a woven material is Kevlar® (E. I. du Font de Nemours, Wilmington, Del.), which is an aramid and which can be made into thin, e.g., less than 0.001 in., materials which maintain enough integrity for such applications described herein. Moreover, theimaging hood 12 may be fabricated from a translucent or opaque material and in a variety of different colors to optimize or attenuate any reflected lighting from surrounding fluids or structures, i.e., anatomical or mechanical structures or instruments. In either case, imaginghood 12 may be fabricated into a uniform structure or a scaffold-supported structure, in which case a scaffold made of a shape memory alloy, such as Nitinol or a spring steel, or plastic, etc., may be fabricated and covered with the polymeric, plastic, or woven, material. Hence,imaging hood 12 may comprise any of a wide variety of barriers or membrane structures, as may generally be used to localize displacement of blood or the like from a selected volume of a body lumen or heart chamber. In exemplary embodiments, a volume within aninner surface 13 ofimaging hood 12 will be significantly less than a volume of thehood 12 betweeninner surface 13 andouter surface 11. -
Imaging hood 12 may be attached atinterface 24 to adeployment catheter 16 which may be translated independently of deployment catheter orsheath 14. Attachment ofinterface 24 may be accomplished through any number of conventional methods.Deployment catheter 16 may define afluid delivery lumen 18 as well as animaging lumen 20 within which, an optical imaging fiber or assembly may be disposed for imaging tissue. When deployed,imaging hood 12 may expand into any number of shapes, e.g., cylindrical, corneal as shown, semi-spherical, etc., provided that an open area orfield 26 is defined by imaginghood 12. Theopen area 26 is the area within which the tissue region of interest may be imaged.Imaging hood 12 may also define an atraumatic contact lip or edge 22 for placement or abutment against the tissue region of interest. Moreover, the diameter ofimaging hood 12 at its maximum fully deployed diameter, e.g., at contact lip oredge 22, is typically greater relative to a diameter of the deployment catheter 16 (although a diameter of contact lip or edge 22 may be made to have a smaller or equal diameter of deployment catheter 16). For instance, the contact edge diameter may range anywhere from 1 to 5 times (or even greater, as practicable) a diameter ofdeployment catheter 16.FIG. 1C shows an end view of theimaging hood 12 in its deployed configuration. Also shown are the contact lip or edge 22 andfluid delivery lumen 18 andimaging lumen 20. - The imaging and
manipulation assembly 10 may additionally define a guidewire lumen therethrough, e.g., a concentric or eccentric lumen, as shown in the side and end views, respectively, ofFIGS. 1D to 1F. Thedeployment catheter 16 may defineguidewire lumen 19 for facilitating the passage of the system over or along aguidewire 17, which may be advanced intravascularly within a body lumen. Thedeployment catheter 16 may then be advanced over theguidewire 17, as generally known in the art. - In operation, after imaging
hood 12 has been deployed, as inFIG. 1B , and desirably positioned against the tissue region to be imaged alongcontact edge 22, the displacing fluid may be pumped at positive pressure throughfluid delivery lumen 18 until the fluid fillsopen area 26 completely and displaces any fluid 28 from withinopen area 26. The displacing fluid flow may be laminarized to improve its clearing effect and to help prevent blood from re-entering theimaging hood 12. Alternatively, fluid flow may be started before the deployment takes place. The displacing fluid, also described herein as imaging fluid, may comprise any biocompatible fluid, e.g., saline, water, plasma, etc., which is sufficiently transparent to allow for relatively undistorted visualization through the fluid. Alternatively or additionally, any number of therapeutic drugs may be suspended within the fluid or may comprise the fluid itself which is pumped intoopen area 26 and which is subsequently passed into and through the heart and the patient body. - As seen in the example of
FIGS. 2A and 2B ,deployment catheter 16 may be manipulated to position deployedimaging hood 12 against or near the underlying tissue region of interest to be imaged, in this example a portion of annulus A of mitral valve MV within the left atrial chamber. As the surroundingblood 30 flows aroundimaging hood 12 and withinopen area 26 defined withinimaging hood 12, as seen inFIG. 2A , the underlying annulus A is obstructed by theopaque blood 30 and is difficult to view through theimaging lumen 20. Thetranslucent fluid 28, such as saline, may then be pumped throughfluid delivery lumen 18, intermittently or continuously, until theblood 30 is at least partially, and preferably completely, displaced from withinopen area 26 byfluid 28, as shown inFIG. 2B . - Although
contact edge 22 need not directly contact the underlying tissue, it is at least preferably brought into close proximity to the tissue such that the flow ofclear fluid 28 fromopen area 26 may be maintained to inhibit significant backflow ofblood 30 back intoopen area 26. Contact,edge 22 may also be made of a soft elastomeric material such as certain soft grades of silicone or polyurethane, as typically known, to help contact, edge 22 conform to an uneven or rough underlying anatomical tissue surface. Once theblood 30 has been displaced from imaginghood 12, an image may then be viewed of the underlying tissue through theclear fluid 30. This image may then be recorded or available for real-time viewing for performing a therapeutic procedure. The positive (low offluid 28 may be maintained continuously to provide for clear viewing of the underlying tissue. Alternatively, the fluid 28 may be pumped temporarily or sporadically only until a clear view of the tissue is available to be imaged and recorded, at which point thefluid flow 28 may cease andblood 30 may be allowed to seep or flow back intoimaging hood 12. This process may be repeated a number of times at the same tissue region or at multiple tissue regions. - In desirably positioning the assembly at various regions within the patient body, a number of articulation and manipulation controls may be utilized. For example, as shown in the
articulatable imaging assembly 40 inFIG. 3A , one or more push-pull wires 42 may be routed throughdeployment catheter 16 for steering the distal end portion of the device in various directions 46 to desirably position theimaging hood 12 adjacent to a region of tissue to be visualized. Depending upon the positioning and the number of push-pull wires 42 utilized,deployment catheter 16 andimaging hood 12 may be articulated into any number ofconfigurations 44. The push-pull wire orwires 42 may be articulated via their proximal ends from outside the patient body manually utilizing one or more controls. Alternatively,deployment catheter 16 may be articulated by computer control, as further described below. - Additionally or alternatively, an
articulatable delivery catheter 48, which may be articulated via one or more push-pull wires and having an imaging lumen, and one or more working lumens, may be delivered through thedeployment catheter 16 and intoimaging hood 12. With a distal portion ofarticulatable delivery catheter 48 withinimaging hood 12, the clear displacing fluid may be pumped throughdelivery catheter 48 ordeployment catheter 16 to clear the field withinimaging hood 12. As shown inFIG. 3B , thearticulatable delivery catheter 48 may be articulated within the imaging hood to obtain a better image of tissue adjacent to theimaging hood 12. Moreover,articulatable delivery catheter 48 may be articulated to direct an instrument or tool, passed through thecatheter 48, as described in detail below, to specific areas of tissue imaged throughimaging hood 12 without having to repositiondeployment catheter 16 and re-clear the imaging field withinhood 12. - Alternatively, rather than passing an
articulatable delivery catheter 48 through thedeployment catheter 16, a distal portion of thedeployment catheter 16 itself may comprise a distal, end 49 which is articulatable withinimaging hood 12, as shown inFIG. 3C . Directed imaging, instrument delivery, etc., may be accomplished directly through one of more lumens withindeployment catheter 16 to specific regions of the underlying tissue imaged withinimaging hood 12. - Visualization within the
imaging hood 12 may be accomplished through animaging lumen 20 defined throughdeployment catheter 16, as described above. In such a configuration, visualization is available in a straight-line manner, i.e., images are generated from the field distally along a longitudinal axis defined by thedeployment catheter 16. Alternatively or additionally, an articulatable imaging assembly having apivotable support member 50 may be connected to, mounted to, or otherwise passed throughdeployment catheter 16 to provide for visualization off-axis relative to the longitudinal axis defined bydeployment catheter 16, as shown inFIG. 4A .Support member 50 may have animaging element 52, e.g., a CCD or CMOS imager or optical fiber, attached at its distal end with its proximal end connected todeployment catheter 16 via apivoting connection 54. - If one or more optical fibers are utilized for imaging, the
optical fibers 58 may be passed throughdeployment catheter 16, as shown in the cross-section ofFIG. 4B , and routed through thesupport member 50. The use ofoptical fibers 58 may provide for increased diameter sizes of the one orseveral lumens 56 throughdeployment catheter 16 for the passage of diagnostic and/or therapeutic tools therethrough. Alternatively, electronic chips, such as a charge coupled device (CCD) or a CMOS imager, which are typically known, may be utilized in place of theoptical fibers 58, in which case the electronic imager may be positioned in the distal portion of thedeployment catheter 16 with, electric wires being routed proximally through thedeployment catheter 16. Alternatively, the electronic imagers may be wirelessly coupled to a receiver for the wireless transmission of images. Additional optical fibers or light emitting diodes (LEDs) can be used to provide lighting for the image or operative theater, as described below in further detail.Support member 50 may be pivoted viaconnection 54 such that themember 50 can be positioned in a low-profile configuration within channel or groove 60 defined in a distal portion ofcatheter 16, as shown in the cross-section ofFIG. 4C . During intravascular delivery ofdeployment catheter 16 through the patient body,support member 50 can be positioned within channel or groove 60 withimaging hood 12 also in its low-profile configuration. During visualization,imaging hood 12 may be expanded into its deployed configuration andsupport member 50 may be deployed into its off-axis configuration for imaging the tissue adjacent tohood 12, as inFIG. 4A . Other configurations forsupport member 50 for off-axis visualization may be utilized, as desired. -
FIG. 5 shows an illustrative cross-sectional view of a heart H having tissue regions of interest being viewed via animaging assembly 10. In this example,delivery catheter assembly 70 may be introduced percutaneously into the patient's vasculature and advanced through the superior vena cava SVC and into the right atrium RA. The delivery catheter orsheath 72 may be articulated through the atrial septum AS and into the left atrium LA for viewing or treating the tissue, e.g., the annulus A, surrounding the mitral valve MY. As shown,deployment catheter 16 andimaging hood 12 may be advanced out ofdelivery catheter 72 and brought into contact or in proximity to the tissue region of interest. In other examples,delivery catheter assembly 70 may be advanced through the inferior vena cava IVC, if so desired. Moreover, other regions of the heart H. e.g., the right ventricle RV or left ventricle LV, may also be accessed and imaged or treated by imagingassembly 10. - In accessing regions of the heart H or other parts of the body, the delivery catheter or
sheath 14 may comprise a conventional intra-vascular catheter or an endoluminal delivery device. Alternatively, robotically-controlled delivery catheters may also be optionally utilized with the imaging assembly described herein, in which case a computer-controller 74 may be used to control the articulation and positioning of thedelivery catheter 14. An example of a robotically-controlled delivery catheter which may be utilized is described in further detail in US Pat. Pub. 2002/0087169 A1 to Brock et al. entitled “Flexible Instrument”, which is incorporated herein by reference in its entirety. Other robotically-controlled delivery catheters manufactured by Hansen Medical, Inc. (Mountain View, Calif.) may also be utilized with thedelivery catheter 14, as described in further detail below. - To facilitate stabilization of the
deployment catheter 16 during a procedure, one or more inflatable balloons or anchors 76 may be positioned along the length ofcatheter 16, as shown inFIG. 6A . For example, when utilizing a transseptal approach across the atrial septum AS into the left atrium LA, theinflatable balloons 76 may be inflated from a low-profile into their expanded configuration to temporarily anchor or stabilize thecatheter 16 position relative to the heart H.FIG. 6B shows afirst balloon 78 inflated whileFIG. 6G also shows asecond balloon 80 inflated proximal to thefirst balloon 78. In such a configuration, the septal wall AS may be: wedged or sandwiched between theballoons catheter 16 andimaging hood 12. Asingle balloon 78 or bothballoons balloon assembly 76 may be deflated or re-configured into a low-profile for removal of thedeployment catheter 16. - To further stabilize a position of the
imaging hood 12 relative to a tissue surface to be imaged, various anchoring mechanisms may be optionally employed for temporarily holding theimaging hood 12 against the tissue. Such anchoring mechanisms may be particularly useful for imaging tissue which is subject to movement, e.g., when imaging tissue within the chambers of a beating heart. Atool delivery catheter 82 having at least one instrument lumen and an optional visualization lumen may be delivered throughdeployment catheter 16 and into an expandedimaging hood 12. As theimaging hood 12 is brought into contact against a tissue surface T to be examined, anchoring mechanisms such as a helicaltissue piercing device 84 may be passed through thetool delivery catheter 82, as shown inFIG. 7A , and intoimaging hood 12. - The helical
tissue engaging device 84 may be torqued from its proximal end outside the patient body to temporarily anchor itself into the underlying tissue surface T. Once embedded within the tissue T, the helicaltissue engaging device 84 may be pulled proximally relative todeployment catheter 16 while thedeployment catheter 16 andimaging hood 12 are pushed distally, as indicated by the arrows inFIG. 7B , to gently force the contact edge orlip 22 of imaging hood against the tissue T. The positioning of thetissue engaging device 84 may be locked temporarily relative to thedeployment catheter 16 to ensure secure positioning of theimaging hood 12 during a diagnostic or therapeutic procedure within theimaging hood 12. After a procedure,tissue engaging device 84 may be disengaged from the tissue by torquing its proximal end in the opposite direction to remove the anchor form the tissue T and thedeployment catheter 16 may be repositioned to another region of tissue where the anchoring process may be repeated or removed from the patient body. Thetissue engaging device 84 may also be constructed from other known tissue engaging devices such as vacuum-assisted engagement or grasper-assisted engagement tools, among others. - Although a
helical anchor 84 is shown, this is intended to be illustrative and other types of temporary anchors may be utilized, e.g., hooked or barbed anchors, graspers, etc. Moreover, thetool delivery catheter 82 may be omitted entirely and the anchoring device may be delivered directly through a lumen defined through thedeployment catheter 16. - In another variation where the
tool delivery catheter 82 may be omitted entirely to temporarily anchorimaging hood 12,FIG. 7C shows animaging hood 12 having one or moretubular support members 86, e.g., foursupport members 86 as shown, integrated with theimaging hood 12. Tiretubular support members 86 may define lumens therethrough each having helicaltissue engaging devices 88 positioned within. When an expandedimaging hood 12 is to be temporarily anchored to the tissue, the helicaltissue engaging devices 88 may be urged distally to extendfront imaging hood 12 and each may be torqued from its proximal end to engage the underlying tissue T. Each of the helicaltissue engaging devices 88 may be advanced through the length ofdeployment catheter 16 or they may be positioned withintubular support members 86 during tire delivery and deployment ofimaging hood 12. Once the procedure withinimaging hood 12 is finished, each of thetissue engaging devices 88 may be disengaged from the tissue and theimaging hood 12 may be repositioned to another region of tissue or removed from the patient body. - An illustrative example is shown in
FIG. 8A of a tissue imaging assembly connected to afluid delivery system 90 and to anoptional processor 98 and image recorder and/orviewer 100. The fluid,delivery system 90 may generally comprise apump 92 and anoptional valve 94 for controlling the flow rate of the fluid into the system. Afluid reservoir 96, fluidly connected to pump 92, may hold, the fluid to be pumped throughimaging hood 12. An optional central processing unit orprocessor 98 may be in electrical communication withfluid delivery system 90 for controlling flow parameters such as the flow rate and/or velocity of the pumped fluid. Theprocessor 98 may also be in electrical communication with an image recorder and/orviewer 100 for directly viewing the images of tissue received from withinimaging hood 12. Imager recorder and/orviewer 100 may also be used not only to record the image but also the location of the viewed tissue region, if so desired. - Optionally,
processor 98 may also be utilized to coordinate the fluid flow and the image capture. For instance,processor 98 may be programmed to provide for fluid flow fromreservoir 96 until the tissue area has been, displaced of blood to obtain a clear image. Once the image has been determined to be sufficiently clear, either visually by a practitioner or by computer, an image of the tissue may be captured automatically byrecorder 100 and pump 92 may be automatically stopped or slowed byprocessor 98 to cease the fluid flow into the patient. Other variations for fluid delivery and image capture are, of course, possible and the aforementioned configuration is intended only to be illustrative and not limiting. -
FIG. 8B shows a further illustration of a hand-held variation of the fluid delivery andtissue manipulation system 110. In this variation,system 110 may have a housing or handleassembly 112 which can be held or manipulated by the physician from outside the patient body. Thefluid reservoir 114, shown in this variation as a syringe, can be fluidly coupled to thehandle assembly 112 and actuated via apumping mechanism 116, e.g., lead screw.Fluid reservoir 114 may be a simple reservoir separated from thehandle assembly 112 and fluidly coupled to handleassembly 112 via one or more tubes. The fluid flow rate and other mechanisms may be metered by theelectronic controller 118. - Deployment of
imaging hood 12 may be actuated by ahood deployment switch 120 located on thehandle assembly 112 while dispensation of the fluid fromreservoir 114 may be actuated by afluid deployment switch 122, which can be electrically coupled to thecontroller 118.Controller 118 may also be electrically coupled to a wired orwireless antenna 124 optionally integrated with thehandle assembly 112, as shown in the figure. Thewireless antenna 124 can be used to wirelessly transmit images captured from, theimaging hood 12 to a receiver, e.g., via Bluetooth® wireless technology (Bluetooth SIG, Inc., Bellevue, Wash.), RF, etc., for viewing on amonitor 128 or for recording for later viewing. - Articulation control of the
deployment catheter 16, or a delivery catheter orsheath 14 through which thedeployment catheter 16 may be delivered, may be accomplished by computer control, as described above, in which case an additional controller may be utilized, withhandle assembly 112. In the case of manual articulation, handleassembly 112 may incorporate one or more articulation controls 126 for manual manipulation, of the position ofdeployment catheter 16.Handle assembly 112 may also define one or more instrument,ports 130 through which a number of intravascular tools may be passed for tissue manipulation and treatment withinimaging hood 12, as described further below. Furthermore, in certain procedures, fluid or debris may be sucked intoimaging hood 12 for evacuation from the patient body by optionally fluidly coupling asuction pump 132 to handleassembly 112 or directly todeployment catheter 16. - As described above, fluid may be pumped continuously into
imaging hood 12 to provide for clear viewing of the underlying tissue. Alternatively, fluid may be pumped temporarily or sporadically only until a clear view of the tissue is available to be imaged and recorded, at which point: the fluid flow may cease and the blood may be allowed to seep or flow back intoimage hood 12.FIGS. 9A to 9C illustrate an example of capturing several, images of the tissue at multiple regions.Deployment catheter 16 may be desirably positioned andimaging hood 12 deployed and brought into position against a region of tissue to be imaged, in this example the tissue surrounding a mitral valve MV within the left atrium of a patient's heart. Theimaging hood 12 may be optionally anchored to the tissue, as described above, and then cleared by pumping the imaging fluid into thehood 12. Once sufficiently clear, the tissue may be visualized and the image captured bycontrol electronics 118. The first capturedimage 140 may be stored and/or transmitted wirelessly 124 to amonitor 128 for viewing by the physician, as shown inFIG. 9A . - The
deployment catheter 16 may be then repositioned to an adjacent portion of mitral valve MV, as shown inFIG. 9B , where the process may be repeated to capture asecond image 142 for viewing and/or recording. Thedeployment catheter 16 may again be repositioned to another region of tissue, as shown inFIG. 9C , where athird image 144 may be captured for viewing and/or recording. This procedure may be repeated as many times as necessary for capturing a comprehensive image of the tissue surrounding mitral valve MV, or any other tissue region. When thedeployment catheter 16 andimaging hood 12 is repositioned from tissue region to tissue region, the pump may be stopped, during positioning and blood or surrounding fluid may be allowed to enter withinimaging hood 12 until the tissue is to be imaged, where theimaging hood 12 may be cleared, as above. - As mentioned, above, when the
imaging hood 12 is cleared by pumping the imaging fluid within for clearing the blood or other bodily fluid, the fluid may be pumped continuously to maintain the imaging fluid within thehood 12 at a positive pressure or it may be pumped under computer control for slowing or stopping the fluid flow into thehood 12 upon detection of various parameters or until a clear image of the underlying tissue is obtained. Thecontrol electronics 118 may also be programmed to coordinate the fluid flow into theimaging hood 12 with various physical parameters to maintain a clear image withinimaging hood 12. - One example is shown in
FIG. 10A which shows achart 150 illustrating how fluid pressure within theimaging hood 12 may be coordinated with the surrounding blood pressure. Chart 150 shows thecyclical blood pressure 156 alternating between,diastolic pressure 152 andsystolic pressure 154 over time T due to the beating motion of the patient heart. The fluid pressure of the imaging fluid, indicated byplot 160, withinimaging hood 12 may be automatically timed to correspond to the blood pressure changes 160 such that an increased pressure is maintained withinimaging hood 12 which is consistently above theblood pressure 156 by a slight increase ΔP, as illustrated by the pressure difference at the peaksystolic pressure 158. This pressure difference, ΔP, may be maintained withinimaging hood 12 over the pressure variance of the surrounding blood pressure to maintain a positive imaging fluid pressure withinimaging hood 12 to maintain a clear view of the underlying tissue. One benefit of maintaining a constant ΔP is a constant flow and maintenance of a clear field. -
FIG. 10B shows achart 162 illustrating another variation for maintaining a clear view of the underlying tissue where one or more sensors within theimaging hood 12, as described in further detail below, may be configured to sense, pressure changes within theimaging hood 12 and to correspondingly increase the imaging fluid pressure withinimaging hood 12. This may result in a time delay, ΔT, as illustrated by the shiftedfluid pressure 160 relative to thecycling blood pressure 156, although the time delays ΔT may be negligible in maintaining the clear image of the underlying tissue. Predictive software algorithms can also be used to substantially eliminate this time delay by predicting when the next pressure wave peak will arrive and by increasing the pressure ahead of the pressure wave's arrival by an amount of time equal to the aforementioned time delay to essentially cancel the time delay out. - The variations in fluid pressure within
imaging hood 12 may be accomplished in part due to the nature ofimaging hood 12. An inflatable balloon, which is conventionally utilized for imaging tissue, may be affected, by the surrounding blood pressure changes. On the other hand, animaging hood 12 retains a constant volume therewithin and is structurally unaffected by the surrounding blood pressure changes, thus allowing for pressure increases therewithin. The material thathood 12 is made from may also contribute to the manner in which the pressure is modulated within thishood 12. A stiffer hood material, such as high durometer polyurethane or Nylon, may facilitate the maintaining of an open hood when deployed. On the other hand, a relatively lower durometer or softer material, such as a low durometer PVC or polyurethane, may collapse from the surrounding fluid pressure and may not adequately maintain a deployed or expanded hood. - Turning now to the imaging hood, other variations of the tissue imaging assembly may be utilized, as shown in
FIG. 11A , which shows another variation comprising anadditional imaging balloon 172 within an imaging hood 174. In this variation, anexpandable balloon 172 having a translucent skin may be positioned within imaging hood 174.Balloon 172 may be made from any distensible biocompatible material having sufficient translucent properties which allow for visualization therethrough. Once the imaging hood 174 has been deployed against the tissue region of interest,balloon 172 may be filled with a fluid, such as saline, or less preferably a gas, untilballoon 172 has been expanded until the blood has been sufficiently displaced. Theballoon 172 may thus be expanded proximal to or into contact against the tissue region to be viewed. Theballoon 172 can also be tilled with contrast media to allow it to be viewed on fluoroscopy to aid in its positioning. The imager, e.g., fiber optic, positioned withindeployment catheter 170 may then be utilized to view the tissue region through theballoon 172 and any additional fluid which may be pumped into imaging hood 174 via one or moreoptional fluid ports 176, which may be positioned proximally ofballoon 172 along a portion ofdeployment catheter 170. Alternatively,balloon 172 may define one or more holes over its surface which allow for seepage or passage of the fluid contained therein to escape and displace the blood from within: imaging hood 174. -
FIG. 11B shows another alternative in whichballoon 180 may be utilized alone.Balloon 180, attached to deployment catheter 178, may be filled with fluid, such as saline or contrast media, and is preferably allowed to come into direct contact with the tissue region to be imaged. -
FIG. 12A shows another alternative in whichdeployment catheter 16 incorporatesimaging hood 12, as above, and includes an additionalflexible membrane 182 withinimaging hood 12.Flexible membrane 182 may be attached at a distal end ofcatheter 16 and optionally atcontact edge 22.Imaging hood 12 may be utilized, as above, andmembrane 182 may be deployed fromcatheter 16 in vivo or prior to placingcatheter 16 within a patient to reduce the volume withinimaging hood 12. The volume may be reduced or minimized to reduce the amount of fluid dispensed for visualization or simply reduced depending upon the area of tissue to be visualized. -
FIGS. 12B and 12C show yet another alternative in whichimaging hood 186 may be withdrawn proximally withindeployment catheter 184 or deployed distally fromcatheter 186, as shown, to vary the volume ofimaging hood 186 and thus the volume of dispensed fluid.Imaging hood 186 may be seen inFIG. 12B as being partially deployed from, e.g., a circumferentially defined lumen withincatheter 184, such asannular lumen 188. The underlying tissue may be visualized withimaging hood 186 only partially deployed. Alternatively,imaging hood 186′ may be fully deployed, as shown inFIG. 12C , by urginghood 186′ distally out fromannular lumen 188. In this expanded configuration, the area of tissue to be visualized may be increased ashood 186′ is expanded circumferentially. -
FIGS. 13A and 13B show perspective and cross-sectional side views, respectively, of yet another variation of imaging assembly which may utilize a fluid suction system for minimizing the amount of fluid injected into the patient's heart or other body lumen during tissue visualization.Deployment catheter 190 in this variation may define an innertubular member 196 which may be integrated withdeployment catheter 190 or independently translatable.Fluid delivery lumen 198 defined throughmember 196 may be fluidly connected toimaging hood 192, which may also define one or moreopen channels 194 over its contact lip region. Fluid pumped throughfluid delivery lumen 198 may thus fillopen area 202 to displace any blood or other fluids or objects therewithin. As the clear fluid is forced out ofopen area 202, it may be sucked or drawn immediately through one ormore channels 194 and back intodeployment catheter 190.Tubular member 196 may also define one or more additional workingchannels 200 for the passage of any fools or visualization devices. - In deploying the imaging hood in the examples described herein, the imaging hood may take on any number of configurations when positioned or configured for a low-profile delivery within the delivery catheter, as shown in the examples of
FIGS. 14A to 14D. These examples are intended to be illustrative and are not intended to be limiting in scope.FIG. 14A shows one example in whichimaging hood 212 may be compressed withincatheter 210 by foldinghood 212 along a plurality of pleats.Hood 212 may also comprise scaffolding orframe 214 made of a super-elastic or shape memory material or alloy, e.g. Nitinol, Elgiloy, shape memory polymers, electroactive polymers, or a spring stainless steel. The shape memory material may act to expand or deployimaging hood 212 into its expanded configuration when urged in the direction of the arrow from the constraints ofcatheter 210. -
FIG. 14B shows another example in whichimaging hood 216 may be expanded or deployed fromcatheter 210 from a folded and overlapping configuration. Frame orscaffolding 214 may also be utilized in this example.FIG. 14C shows yet another example in whichimaging hood 218 may be rolled. Inverted, or everted upon itself for deployment, in yet another example,FIG. 14D shows a configuration in whichimaging hood 220 may be fabricated from an extremely compliant material which allows forhood 220 to be simply compressed into a low-profile shape. From this low-profile compressed shape, simply releasinghood 220 may allow for it to expand into its deployed configuration, especially if a scaffold or frame of a shape memory or superelastic material, e.g., Nitinol, is utilized in its construction. - Another variation for expanding the imaging hood is shown in
FIGS. 15A and 15B which illustrates an helically expanding frame orsupport 230. In its constrained low-profile configuration, shown inFIG. 15A ,helical frame 230 may be integrated with, theimaging hood 12 membrane. When free to expand, as shown inFIG. 15B ,helical frame 230 may expand, into a conical or tapered shape.Helical frame 230 may alternatively be made out of heat-activated Nitinol to allow it to expand upon application of a current. -
FIGS. 16A and 16B show yet another variation in whichimaging hood 12 may comprise one or morehood support members 232 integrated with the hood membrane. These longitudinally attachedsupport members 232 may be pivotably attached at their proximal ends todeployment catheter 16. One or more pullwires 234 may be routed through the length ofdeployment catheter 16 and extend, through one ormore openings 238 defined in deployment,catheter 16 proximally toimaging hood 12 into attachment with acorresponding support member 232 at apullwire attachment point 236. The support,members 232 may be fabricated from a plastic or metal, such as stainless steel. Alternatively, thesupport members 232 may be made from a superelastic or shape memory alloy, such as Nitinol, which may self-expand into its deployed configuration without the use or need of pullwires. A heat-activated Nitinol may also be used which expands upon the application of thermal energy or electrical, energy. In another alternative,support members 232 may also be constructed as inflatable lumens utilizing, e.g., PET balloons. From its low-profile delivery configuration shown inFIG. 16A , the one or more pullwires 234 may be tensioned from their proximal ends outside the patient body to pull acorresponding support member 232 into a deployed configuration, as shown inFIG. 16B , to expandimaging hood 12. To reconfigureimaging hood 12 back into its low profile,deployment catheter 16 may be pulled proximally into a constraining catheter or thepullwires 234 may be simply pushed distally to collapseimaging hood 12. -
FIGS. 17A and 17B show yet another variation ofimaging hood 240 having at least two or more longitudinally positionedsupport members 242 supporting the imaging hood membrane. Thesupport members 242 each havecross-support members 244 which extend diagonally between and are pivotably attached to thesupport members 242. Each of thecross-support members 244 may be pivotably attached to one another where they intersect between thesupport members 242. A jack orscrew member 246 may be coupled to each cross-support,member 244 at this intersection point and a torquing member, such as a torque-able wire 248, may be coupled to each jack orscrew member 246 and extend proximally throughdeployment catheter 16 to outside the patient body. From outside the patient body, thetorqueable wires 248 may be torqued to turn the jack orscrew member 246 which in turn urges thecross-support members 244 to angle relative to one another and thereby urge thesupport members 242 away from one another. Thus, theimaging hood 240 may be transitioned from its low-profile, shown inFIG. 17A , to its expanded profile, shown inFIG. 17B , and back into its low-profile by torquingwires 248. -
FIGS. 18A and 18B show yet another variation on the imaging hood and its deployment. As shown, a distal portion ofdeployment catheter 16 may have several pivotingmembers 250, e.g., two to four sections, which form a tubular shape in its low profile configuration, as shown inFIG. 18A . When pivoted radially aboutdeployment catheter 16, pivotingmembers 250 may open into a deployed configuration having distensible or expandingmembranes 252 extending over the gaps in-between the pivotingmembers 250, as shown inFIG. 18B . Thedistensible membrane 252 may be attached to the pivotingmembers 250 through various methods, e.g., adhesives, such that when the pivotingmembers 250 are fully extended into a conical shape, the pivotingmembers 250 andmembrane 252 form a conical shape for use as an imaging hood. Thedistensible membrane 252 may be made out of a porous material such as a mesh or PTFE or out of a translucent or transparent polymer such as polyurethane, PVC, Nylon, etc. -
FIGS. 19A and 19B show yet another variation where the distal portion ofdeployment catheter 16 may be fabricated from a flexible metallic or polymeric material to form aradially expanding hood 254. A plurality ofslots 256 may be formed in a uniform pattern over the distal portion ofdeployment catheter 16, as shown inFIG. 19A . Theslots 356 may be formed in a pattern such that when the distal portion is urged radially open, utilizing any of the methods described above, a radially expanded and conically-shapedhood 254 may be formed by each of theslots 256 expanding into an opening, as shown inFIG. 19B . Adistensible membrane 258 may overlie the exterior surface or the interior surface of thehood 254 to form a fluid-impermeable hood 254 such that thehood 254 may be utilized as an imaging hood. Alternatively, thedistensible membrane 258 may alternatively be formed, in eachopening 258 to form the fluid-impermeable hood 254. Once tire imaging procedure has been completed,hood 254 may be retracted into its low-profile configuration. - Yet another configuration for the imaging hood, may be seen in
FIGS. 20A and 20B where the imaging hood may be formed from a plurality of overlapping hood,members 260 which overlie one another in an overlapping pattern. When expanded, each of thehood members 260 may extend radially outward relative todeployment catheter 16 to form a conically-shaped imaging hood, as shown inFIG. 20B .Adjacent hood members 260 may overlap one another along an overlappinginterface 262 to form a fluid-retaining surface within the imaging hood. Moreover, thehood members 260 may be made from any number of biocompatible materials, e.g., Nitinol, stainless steel, polymers, etc., which are sufficiently strong to optionally retract surrounding tissue from the tissue region of interest. - Although it is generally desirable to have an imaging hood contact against a tissue surface in a normal orientation, the imaging hood may be alternatively, configured to contact the tissue surface at air acute angle. An imaging hood configured for such contact against tissue may also be especially suitable for contact against, tissue surfaces having an unpredictable or uneven anatomical geography. For instance, as shown in the variation of
FIG. 21A ,deployment catheter 270 may have animaging hood 272 that is configured to be especially compliant. In this variation,imaging hood 272 may be comprised of one ormore sections 274 that are configured to fold or collapse, e.g., by utilizing a pleated surface. Thus, as shown inFIG. 21B , when imaginghood 272 is contacted against uneven tissue surface T,sections 274 are able to conform closely against the tissue. Thesesections 274 may be individually collapsible by utilizing an accordion style construction to allow conformation, e.g., to the trabeculae in the heart or the uneven anatomy that may be found inside the various body lumens. - In yet another alternative,
FIG. 22A shows another variation in which animaging hood 282 is attached todeployment catheter 280. The contact lip or edge 284 may comprise one or moreelectrical contacts 286 positioned circumferentially aroundcontact edge 284. Theelectrical contacts 286 may be configured to contact the tissue and indicate affirmatively whether tissue contact was achieved, e.g., by measuring the differential impedance between blood and tissue. Alternatively, a processor, e.g.,processor 98, in electrical communication withcontacts 286 may be configured to determine what type of tissue is in contact withelectrical contacts 286. In yet another alternative, theprocessor 98 may be configured to measure any electrical activity that may be occurring in the underlying tissue, e.g., accessory pathways, for the purposes of electrically mapping the cardiac tissue and subsequently treating, as described below, any arrhythmias which may be detected. - Another variation for ensuring contact between
imaging hood 282 and the underlying tissue may be seen inFIG. 22B . This variation may have an inflatable contact: edge 288 around the circumference ofimaging hood 282. Theinflatable contact edge 288 may be inflated with a fluid or gas throughinflation lumen 289 when theimaging hood 282 is to be placed against a tissue surface having an uneven or varied anatomy. The inflatedcircumferential surface 288 may provide for continuous contact over the hood edge by conforming against the tissue surface and facilitating imaging fluid retention withinhood 282. - Aside from the imaging hood, various instrumentation may be utilized with the imaging and manipulation system. For instance, after the field within
imaging hood 12 has been cleared of the opaque blood and the underlying tissue is visualized through the clear fluid, blood may seep back into theimaging hood 12 and obstruct the view. One method for automatically maintaining a clear imaging field may utilize a transducer, e.g., anultrasonic transducer 290, positioned at the distal end of deployment catheter within theimaging hood 12, as shown inFIG. 23 . Thetransducer 290 may send anenergy pulse 292 into theimaging hood 12 and wait to detect back-scatteredenergy 294 reflected from debris or blood within theimaging hood 12. If back-scattered energy is detected, the pump may be actuated automatically to dispense more fluid into the imaging hood until the debris or blood is no longer detected. - Alternatively, one or
more sensors 300 may be positioned on theimaging hood 12 itself, as shown inFIG. 24A , to detect a number of different parameters. For example,sensors 300 may be configured to detect for the presence of oxygen in the surrounding blood, blood and/or imaging fluid pressure, color of the fluid, within the imaging hood, etc. Fluid color may be particularly useful in detecting the presence of blood within theimaging hood 12 by utilizing a reflective type sensor to detect back reflection from blood. Any reflected light from blood which may be present withinimaging hood 12 may be optically or electrically transmitted throughdeployment catheter 16 and to a red colored filter withincontrol electronics 118. Any red color which may be detected may indicate the presence of blood and trigger a signal to the physician or automatically actuate the pump to dispense more fluid into theimaging hood 12 to cleat the blood. - Alternative methods for detecting the presence of blood within, the
hood 12 may include detecting transmitted light through the imaging fluid withinimaging hood 12. If a source of white light, e.g., utilizing LEDs or optical fibers, is illuminated insideimaging hood 12, the presence of blood may cause the color red to be filtered, through this fluid. The degree or intensity of the red color detected may correspond to the amount of blood present withinimaging hood 12. A red color sensor can simply comprise, in one variation, a phototransistor with a red transmitting filter over it which can establish how much red light is detected, which in turn can indicate the presence of blood, withinimaging hood 12. Once blood is detected, the system may pump more clearing fluid through and enable closed loop feedback control of the clearing fluid pressure and flow level. - Any number of sensors may be positioned along the
exterior 302 ofimaging hood 12 or within theinterior 304 ofimaging hood 12 to detect parameters not only exteriorly toimaging hood 12 but also withinimaging hood 12. Such a configuration, as shown inFIG. 24B , may be particularly useful for automatically maintaining a clear imaging field based upon physical, parameters such as blood pressure, as described above forFIGS. 10A and 10B . - Aside from sensors, one or more light emitting diodes (LEDs) may be utilized to provide lighting within the
imaging hood 12. Although illumination may be provided by optical fibers routed throughdeployment catheter 16, the use of LEDs over theimaging hood 12 may eliminate the need for additional optical fibers for providing illumination. The electrical wires connected to the one or more LEDs may be routed through or over thehood 12 and along an exterior surface or extruded withindeployment catheter 16. One or more LEDs may be positioned in acircumferential pattern 306 aroundimaging hood 12, as shown inFIG. 25A , or in a linearlongitudinal pattern 308 alongimaging hood 12, as shown inFIG. 25B . Other patterns, such as a helical or spiral pattern, may also be utilized. Alternatively, LEDs may be positioned along a support member forming part ofimaging hood 12. - In another alternative for illumination within
imaging hood 12, aseparate illumination tool 310 may be utilized, as shown inFIG. 26A . An example of such a tool may comprise a flexibleintravascular delivery member 312 having acarrier member 314 pivotably connected 316 to a distal end ofdelivery member 312. One ormore LEDs 318 may be mounted alongcarrier member 314. In use,delivery member 312 may be advanced throughdeployment catheter 16 untilcarrier member 314 is positioned withinimaging hood 12. Once withinimaging hood 12,carrier member 314 may be pivoted in any number of directions to facilitate or optimize the illumination within theimaging hood 12, as shown, inFIG. 26B . - In utilizing LEDs for illumination, whether positioned along
imaging hood 12 or along a separate instrument, the LEDs may comprise a single LED color, e.g., white light. Alternatively, LEDs of other colors, e.g., red, blue, yellow, etc., may be utilized exclusively or in combination with white LEDs to provide for varied illumination of the tissue or fluids, being imaged. Alternatively, sources of infrared or ultraviolet light may be employed to enable imaging beneath the tissue, surface or cause fluorescence of tissue for use in system guidance, diagnosis, or therapy. - Aside from providing a visualization platform, the imaging assembly may also be utilized to provide a therapeutic platform for treating tissue being visualized. As shown in
FIG. 27 ,deployment catheter 320 may haveimaging hood 322, as described above, andfluid delivery lumen 324 andimaging lumen 326. In this variation, a therapeutic tool such asneedle 328 may be delivered, throughfluid delivery lumen 324 or in another working lumen and advanced throughopen area 332 for treating the tissue which is visualized. In this instance,needle 328 may define one orseveral ports 330 for delivering drugs therethrough. Thus, once the appropriate region of tissue has been imaged and located,needle 328 may be advanced and pierced into the underlying tissue where a therapeutic agent may be delivered throughports 330. Alternatively,needle 328 may be in electrical communication with apower source 334, e.g., radio-frequency, microwave, etc., for ablating the underlying tissue area of interest. -
FIG. 28 shows another alternative in which deployment catheter 340 may haveimaging hood 342 attached thereto, as above, but with atherapeutic tool 344 in the configuration of a helicaltissue piercing device 344. Also shown and described above inFIGS. 7A and 7B for use in stabilizing the imaging hood relative to the underlying tissue, the helicaltissue piercing device 344 may also be utilized to manipulate the tissue for a variety of therapeutic procedures. Thehelical portion 346 may also define one or several ports for delivery of therapeutic agents therethrough. - In yet another alternative,
FIG. 29 shows adeployment catheter 350 having anexpandable imaging balloon 352 filled with, e.g.,saline 356. Atherapeutic tool 344, as above, may be translatable relative to balloon 352. To prevent the piercingportion 346 of the tool from tearingballoon 352, astop 354 may be formed onballoon 352 to prevent the proximal passage ofportion 346past stop 354. - Alternative configurations for tools which may be delivered through
deployment catheter 16 for use in tissue manipulation withinimaging hood 12 are shown inFIGS. 30A and 30B .FIG. 30A shows one variation of anangled instrument 360, such as a tissue grasper, which may be configured to have an elongate shaft for intravascular delivery throughdeployment catheter 16 with a distal end which may be angled relative to its elongate shaft upon deployment intoimaging hood 12. The elongate shaft may be configured to angle itself automatically, e.g., by the elongate shaft being made at least partially from a shape memory alloy, or upon actuation, e.g., by tensioning a pull wire.FIG. 30B shows another configuration for aninstrument 362 being configured to reconfigure its distal portion into an off-axis configuration withinimaging hood 12. In either case, theinstruments deployment catheter 16. - Other instruments or tools which may be utilized with the imaging system is shown in the side and end views of
FIGS. 31A to 31C.FIG. 31A shows aprobe 370 having adistal end effector 372, which may be reconfigured from, a low-profile shape to a curved profile. Theend effector 372 may be configured as an ablation probe utilizing radio-frequency energy, microwave energy, ultrasound energy, laser energy or even cryo-ablation. Alternatively, theend effector 372 may have several electrodes upon it for detecting or mapping electrical signals transmitted through the underlying tissue. - In the case of an
end effector 372 utilized for ablation of the underlying tissue, an additional temperature sensor such as a thermocouple orthermistor 374 positioned upon anelongate member 376 may be advanced into theimaging hood 12 adjacent to the distal,end effector 372 for contacting and monitoring a temperature of the ablated tissue.FIG. 31B shows an example in the end view of one configuration for thedistal end effector 372 which may be simply angled into a perpendicular configuration for contacting the tissue.FIG. 31C shows another example where the end effector may be reconfigured into acurved end effector 378 for increased tissue contact. -
FIGS. 32A and 32B show another variation of an ablation tool utilized with animaging hood 12 having an enclosed bottom portion. In this variation, an ablation probe, such as a cryo-ablation probe 380 having adistal end effector 382, may be positioned through theimaging hood 12 such that theend effector 382 is placed distally of a transparent membrane orenclosure 384, as shown in the end view ofFIG. 32B . The shaft ofprobe 380 may pass through anopening 386 defined through themembrane 384. In use, the clear fluid may be pumped intoimaging hood 12, as described above, and thedistal end effector 382 may be placed against a tissue region, to be ablated with theimaging hood 12 and themembrane 384 positioned atop or adjacent to the ablated tissue. In the case of cryo-ablation, the imaging fluid may be warmed prior to dispensing into theimaging hood 12 such that the tissue contacted by themembrane 384 may be warmed during the cryo-ablation: procedure. In the case of thermal ablation, e.g., utilizing radio-frequency energy, the fluid dispensed into theimaging hood 12 may be cooled such that the tissue contacted bytire membrane 384 and adjacent to the ablation probe during the ablation procedure is likewise cooled. - In either example described above, the imaging fluid may be varied in its temperature to facilitate various procedures to be performed upon the tissue, brother cases, the imaging fluid itself may be altered to facilitate various procedures. For instance as shown in
FIG. 33A , adeployment catheter 16 andimaging hood 12 may be advanced within a hollow body organ, such as a bladder filled withurine 394, towards a lesion ortumor 392 on the bladder wall. Theimaging hood 12 may be placed entirely over thelesion 392, or over a portion of the lesion. Once secured against thetissue wall 390, a cryo-fluid, i.e., a fluid which has been cooled to below freezing temperatures of, e.g., water or blood, may be pumped into theimaging hood 12 to cryo-ablate thelesion 390, as shown inFIG. 33B while avoiding the creation of ice on the instrument or surface of tissue. - As the cryo-fluid leaks out of the
imaging hood 12 and into the organ, the fluid may be warmed naturally by the patient body and ultimately removed. The cryo-fluid may be a colorless and translucent fluid which enables visualization therethrough of the underlying tissue. An example of such a fluid is Fluorinert™ (3M, St. Paul, Minn.), which is a colorless and odorless perfluorinated liquid. The use of a liquid such as Fluorinert™ enables the cryo-ablation procedure without the formation of ice within or outside of theimaging hood 12. Alternatively, rather than utilizing cryo-ablation, hyperthermic treatments may also be effected by heating the Fluorinert™ liquid to elevated temperatures for ablating thelesion 392 within theimaging hood 12. Moreover, Fluorinert™ may be utilized in various other parts of the body, such as within the heart. -
FIG. 34A shows another variation of an instrument which may be utilized with the imaging system. In this variation, alaser ring generator 400 may be passed through thedeployment catheter 16 and partially intoimaging hood 12. Alaser ring generator 400 is typically used to create a circular ring oflaser energy 402 for generating a conduction block around the pulmonary veins typically in the treatment of atrial fibrillation. The circular ring oflaser energy 402 may be generated such that a diameter of thering 402 is contained within a diameter of theimaging hood 12 to allow for tissue ablation directly upon tissue being imaged. Signals which cause atrial fibrillation typically come from the entry area of the pulmonary veins into the left atrium and treatments may sometimes include delivering ablation energy to the ostia of the pulmonary veins within the atrium. The ablated areas of the tissue may produce a circular scar which blocks the impulses for atrial fibrillation. - When using the laser energy to ablate the tissue of the heart, it may be generally desirable to maintain the integrity and health of the tissue overlying the surface while ablating the underlying tissue. This may be accomplished, for example, by cooling the imaging fluid to a temperature below the body temperature of the patient but which is above the freezing point of blood (e.g., 2° C. to 35° C.). The cooled imaging fluid may thus maintain the surface tissue at the cooled fluid temperature while the deeper underlying tissue remains at the patient body temperature. When the laser energy (or other types of energy such as radio frequency energy, microwave energy, ultrasound energy, etc.) irradiates the tissue, both the cooled tissue surface as well as the deeper underlying tissue will rise in temperature uniformly. The deeper underlying tissue, which was maintained at the body temperature, will increase to temperatures which are sufficiently high to destroy the underlying tissue. Meanwhile, the temperature of the cooled surface tissue will also rise but only to temperatures that are near body temperature or slightly above.
- Accordingly, as shown in
FIG. 34B , one example for treatment may include passingdeployment catheter 16 across the atrial septum AS and into the left atrium LA of the patient's heart H. Other methods of accessing the left atrium LA may also be utilized. Theimaging hood 12 andlaser ring generator 400 may be positioned adjacent to or over one or more of the ostium OT of the pulmonary veins PV and thelaser generator 400 may ablate the tissue around the ostium OT with the circular ring oflaser energy 402 to create a conduction block. Once one or more of the tissue, around the ostium OT have been ablated, theimaging hood 12 may be reconfigured into a low profile for removal from the patient heart H. - One of the difficulties in treating tissue in or around the ostium OT is the dynamic fluid flow of blood through the ostium OT. The dynamic forces make cannulation or entry of the ostium OT difficult. Thus, another variation on instruments or tools utilizable with the imaging system is an
extendible cannula 410 having acannula lumen 412 defined therethrough, as shown inFIG. 35A . Theextendible cannula 410 may generally comprise an elongate tubular member which may be positioned within thedeployment catheter 16 during delivery and then projected distally through theimaging hood 12 and optionally beyond, as shown inFIG. 35B . - In use, once the
imaging hood 12 has been desirably positioned relative to the tissue, e.g., as shown inFIG. 35C outside the ostium OT of a pulmonary vein PV, theextendible cannula 410 may be projected distally from, thedeployment catheter 16 while optionally imaging tire tissue through theimaging hood 12, as described above. Theextendible cannula 410 may be projected distally until its distal end is extended at least partially into the ostium OT. Once in the ostium OT, an instrument or energy ablation device may be extended through and out of thecannula lumen 412 for treatment within the ostium OT. Upon completion of the procedure, thecannula 410 may be withdrawn proximally and removed from the patient body. Theextendible cannula 410 may also include an inflatable occlusion balloon at or near its distal end to block the blood flow out of the PV to maintain a clear view of the tissue region. Alternatively, theextendible cannula 410 may define a lumen therethrough beyond the occlusion balloon to bypass at least a portion of the blood that normally exits the pulmonary vein PV by directing the blood through thecannula 410 to exit proximal of the imaging hood. - Yet another variation for tool, or instrument use may be seen in the side and end views of
FIGS. 36A and 36B . In this variation, imaginghood 12 may have one or moretubular support members 420 integrated with thehood 12. Each of thetubular support members 420 may define anaccess lumen 422 through which one or more instruments or tools may be delivered for treatment upon the underlying tissue. One particular example is shown and described above forFIG. 7C . - Various methods and instruments may be utilized for using or facilitating the use of the system. For instance, one method may include facilitating the initial delivery and placement of a device into the patient's heart, in initially guiding the imaging assembly within the heart chamber to, e.g., the mitral valve MV, a
separate guiding probe 430 may be utilized, as shown, inFIGS. 37A and 37B . Guidingprobe 430 may, for example, comprise an optical fiber through which, alight source 434 may be used to illuminate adistal tip portion 432. Thetip portion 432 may be advanced into the heart: through, e.g., the coronary sinus CS, until the tip is positioned adjacent to the mitral valve MV. Thetip 432 may be illuminated, as shown inFIG. 37A , andimaging assembly 10 may then be guided towards the illuminatedtip 432, which, is visible from within the atrial chamber, towards mitral valve MV. - Aside from the devices and methods described above, the imaging system may be utilized to facilitate various other procedures. Turning now to
FIGS. 38A and 38B , the imaging hood of the device in particular may be utilized. In this example, a collapsible membrane or disk-shapedmember 440 may be temporarily secured around the contact edge or lip ofimaging hood 12. During intravascular delivery, theimaging hood 12 and the attachedmember 440 may both be in a collapsed configuration to maintain a low profile for delivery. Upon deployment, both theimaging hood 12 and themember 440 may extend into their expanded configurations. - The disk-shaped
member 440 may be comprised of a variety of materials depending upon the application. For instance,member 440 may be fabricated from a porous polymeric material infused with adrug eluting medicament 442 for implantation against a tissue surface for slow infusion of the medicament into tire underlying tissue. Alternatively, themember 440 may be fabricated from a non-porous material, e.g., metal or polymer, for implantation and closure of a wound or over a cavity to prevent fluid leakage. In yet another alternative, themember 440 may be made from a distensible material which is secured toimaging hood 12 in an expanded condition. Once implanted or secured on a tissue surface or wound, the expandedmember 440 may be released from imaginghood 12. Upon release, the expandedmember 440 may shrink to a smaller size while approximating the attached underlying tissue, e.g., to close a wound or opening. - One method for securing the disk-shaped
member 440 to a tissue surface may include a plurality of tissue anchors 444, e.g., barbs, hooks, projections, etc., which are attached to a surface of themember 440. Other methods of attachments may include adhesives, suturing, etc. In use, as shown inFIGS. 39A to 39C, theimaging hood 12 may be deployed in its expanded configuration withmember 440 attached thereto with the plurality of tissue anchors 444 projecting distally. The tissue anchors 444 may be urged into a tissue region to be treated 446, as seen inFIG. 39A , until theanchors 444 are secured in the tissue andmember 440 is positioned directly against the tissue, as shown inFIG. 39B . A pullwire may be actuated to release themember 440 from theimaging hood 12 anddeployment catheter 16 may be withdrawn proximally to leavemember 440 secured against thetissue 446. - Another variation for tissue manipulation, and treatment may be seen in the variation of
FIG. 40A , which illustrates animaging hood 12 having adeployable anchor assembly 450 attached to thetissue contact edge 22.FIG. 40B illustrates theanchor assembly 450 detached from theimaging hood 12 for clarity. Theanchor assembly 450 may be seen as having a plurality of discrete tissue anchors 456, e.g., barbs, hooks, projections, etc., each having a suture retaining end, e.g., an eyelet or opening 458 in a proximal end of theanchors 456. A suture member orwire 452 may be slidingly connected to eachanchor 456 through theopenings 458 and through a cinchingelement 454, which may be configured to slide uni-directionally over the suture orwire 452 to approximate each of theanchors 456 towards one another. Each of theanchors 456 may be temporarily attached to theimaging hood 12 through a variety of methods. For instance, a pullwire or retaining wire may hold each of the anchors within a receiving ring around the circumference of theimaging hood 12. When theanchors 456 are released, the pullwire or retaining wire may be tensioned from its proximal end outside the patient body to thereby free theanchors 456 from theimaging hood 12. - One example for use of the
anchor assembly 450 is shown inFIGS. 41A to 41D for closure of an opening or wound 460, e.g., patent foramen ovale (PFO). Thedeployment catheter 16 andimaging hood 12 may be delivered intravascularly into, e.g., a patient heart. As theimaging hood 12 is deployed into its expanded configuration, theimaging hood 12 may be positioned adjacent to the opening or wound 460, as shown inFIG. 41A . With theanchor assembly 450 positioned upon the expandedimaging hood 12,deployment catheter 16 may be directed to urge the contact edge ofimaging hood 12 andanchor assembly 450 into the region surrounding thetissue opening 460, as shown inFIG. 41B . Once theanchor assembly 450 has been secured within the surrounding, tissue, the anchors may be released from imaginghood 12 leaving theanchor assembly 450 andsuture member 452 trailing from the anchors, as shown inFIG. 41C . The suture orwire member 452 may be tightened by pulling it proximally from outside the patient body to approximate the anchors ofanchor assembly 450 towards one another in a purse-string manner to close thetissue opening 462, as shown inFIG. 41D . The cinchingelement 454 may also be pushed distally over the suture orwire member 452 to prevent the approximated-anchor assembly 450 from loosening or widening. - Another example for an alternative use is shown in
FIG. 42 , where thedeployment catheter 16 and deployedimaging hood 12 may be positioned within a patient body for drawingblood 472 intodeployment catheter 16. The drawnblood 472 may be pumped through adialysis unit 470 located externally of the patient body for filtering the drawnblood 472 and the filtered blood may be reintroduced back into the patient. - Yet another variation is shown, in
FIGS. 43A and 43B , which show a variation of thedeployment catheter 480 having a firstdeployable hood 482 and a seconddeployable hood 484 positioned distal to thefirst hood 482. Thedeployment catheter 480 may also have a side-viewing imaging element 486 positioned between the first andsecond hoods deployment catheter 480. In use, such a device may be introduced through alumen 488 of a vessel VS, where one or bothhoods hoods hoods imaging space 490, as shown inFIG. 43B . With the clear fluid in-betweenhoods imaging element 486 may be used to view the surrounding tissue surface contained betweenhoods deployment catheter 480 and through one or more openings defined along thecatheter 480 for additionally performing therapeutic procedures upon the vessel wall. - Another variation of a
deployment catheter 500 which may be used for imaging tissue to the side of the instrument may be seen inFIGS. 44A to 45B.FIGS. 44A and 44B show side and end views ofdeployment catheter 500 having a side-imaging balloon 502 in an un-inflated low-profile configuration. A side-imaging element 504 may be positioned within a distal portion of thecatheter 500 where theballoon 502 is disposed. Whenballoon 502 is inflated, it may expand radially to contact the surrounding tissue, but where theimaging element 504 is located, avisualization field 506 may be created by theballoon 502, as shown in the side, top, and end views ofFIGS. 45A to 45B, respectively. Thevisualization field 506 may simply be a cavity or channel which is defined within theinflated balloon 502 such that thevisualization element 504 is provided an image of the area withinfield 506 which is clear and unobstructed byballoon 502. - In use,
deployment catheter 500 may be advanced intravascularly throughvessel lumen 488 towards a lesion ortumor 508 to be visualized and/or treated. Upon reaching thelesion 508,deployment catheter 500 may be positioned adjacently to thelesion 508 andballoon 502 may be inflated such that thelesion 508 is contained within thevisualization field 506. Onceballoon 502 is fully inflated and in contact against the vessel wall, clear fluid may be pumped intovisualization field 506 throughdeployment catheter 500 to displace any blood or opaque fluids from thefield 506, as shown in the side and end views ofFIGS. 46A and 46B , respectively. Thelesion 508 may then be visually inspected and treated by passing any number of instruments throughdeployment catheter 500 and intofield 506. - In controlling the advancement and articulation of any of the delivery catheters described herein, the catheter may be manually controlled or robotically-controlled, as mentioned above. Examples of robotically-controlled catheter systems which utilize precision motion control mechanisms are shown and described in U.S. Pat. App. 2006/0084945 A1 and U.S. Pat. No. 7,090,683, each of which is incorporated herein by reference in its entirety. Generally, a visualization hood may be attached or coupled to the distal end of a catheter articulated or controlled by precision motion control mechanisms. The articulatable neck portion of the shaft, located proximally of the visualization hood, may be comprised of an assembly of links fabricated, e.g., from stainless steel, plastics, etc., that allow the neck portion to be articulated in multiple planes. One or more, e.g., four, pullwires may be routed through the neck and/or shaft such that they terminate at the hood attachment, while the proximal end or ends of the pullwires may be routed through the links to a proximal end of the catheter. Combinations of retraction and/or extension motions of these pullwires may be utilized to steer the neck portion to articulate the hood in multiple directions as desired by the operator.
- The proximal ends of the pullwires are threaded through a pulley assembly and terminated in rotatable spools. Rotating these spools will either retract the pullwires or release more slack into the catheter to enable steering as appropriate. The pullwire spools are further driven by control elements such, as low speed motors, which, in turn, may be driven by a central processing unit. Precise and consistent, low speed rotation of the spools controlled by the central processing unit and the motors will enable the pullwires to be retracted or released with high precision. This will translate into precision articulation and motion control of the tissue visualization hood.
- Referring now to
FIG. 47A , an example of arobotic guide instrument 600 is illustrated having two control element interface assemblies configured to drive, e.g., fourcontrol elements 606, e.g., pullwires. Rotation of the pulleys in a first direction may spool and proximally displace onecontrol element 606, while unspooling in a second opposite direction may distally displace acomplementary control element 606 to deflect the distal end of thedeployment catheter 14 in the opposite direction. Tension may be maintained in thecontrol elements 606 via pre-tensioning or pre-stressing the elements to prevent excess slack. Tension may also be maintained, on thecontrol elements 606 using a slottedguide instrument base 602 which forms one ormore slots 604 through which thecontrol elements 606 may remain taut. -
FIG. 47B illustrates therobotic guide instrument 600 havinghood 12 positioned upondeployment catheter 16 with an inflatable balloon ormembrane 608 optionally disposable within or uponhood 12 and an instrument advanced throughcatheter 16 and intohood 12. As schematically illustrated, therobotic guide instrument 600, and optionally the instruments advanced throughhood 12, may be controlled via a computer orprocessor 612 to control the articulation of thehood 12 as well as other functions. The treatment instrument may include any number of instruments, e.g., ablation tools, a piercingneedle 610, etc., which may be advanced through the hood for treating the underlying tissue. Examples of instruments as well as alternative configurations forhood 12 are shown and described in further detail in the following U.S. patent application Ser. Nos. 11/775,771 and 11/775,837 both filed Jul. 10, 2007, and Ser. No. 11/828,267 filed Jul. 25, 2007, each of which is incorporated herein by reference in its entirety. -
FIG. 47C illustrates an example of how a robotic guide instrument may be utilized with a visualization system. Generally, a user may interface withinput device 651, which may utilize any number of different interfaces, e.g., handle, joystick, etc., by which the user may transmit desired, commands toprocessor 631.Processor 631 may receive the commands and transmit the appropriate drive signals to the catheter and computer-controlledguidance assembly 639 which may then control the hood, imaging systems, fluid purging systems, etc. in accordance with the received commands from the user. When the catheter and/or hood interfaces with the surrounding tissue, the resulting force or tracking feedback, may be optionally sensed byguidance assembly 639 and transmitted back toprocessor 631, which in turn may signal or indicate to the user via force feedback throughinput device 651 or some other force or visual feedback. Moreover, the image data captured by the imaging element within or alonghood 12 may also be received byguidance assembly 639 and transmitted toprocessor 631, which may receive foe image data for processing, and display upon a tissuesurface image display 649 to the user. - Catheter and computer-controlled
guidance assembly 639 may comprise several sub-systems for controlling each of a number of different functions, for instance (amongst other sub-systems), anarticulation drive 641 for controlling a movement of thecatheter 16 and/orhood 12, amovement tracking system 643 for tracking a position and/or orientation of thecatheter 16 and/orhood 12 within the patient body, animaging element system 645 for controlling the visualization features, as well as ablood displacement system 647 for controlling and/or tracking an infusion of transparent, fluid into thehood 12. -
Processor 631 may also be configured to handle several different processing functions to process various data. For instance,processor 631 may be configured to input commands registered withtissue surface images 633 as received frominput device 651, as well as processcatheter position data 635 based, upon catheter tracking feedback, signals as received from themovement tracking system 643 fromguidance assembly 639. Moreover,processor 631 may be configured to process desiredcatheter articulations 637 in accordance with the commands received from theinput device 651 such that drive signals are generated byprocessor 631 and transmitted to thearticulation drive 641 inguidance assembly 639 to control the movements of the catheter and/or hood in a desired manner. -
FIG. 48A illustrates a perspective view of a variation of a robotic controlassembly showing base 602 having fourproximal drive assemblies 630 attached thereupon where eachassembly 630 may control a corresponding control element, e.g., pullwire, for controlling an articulation ofhood 12 positioned upondeployment catheter 16. Delivery catheter orsheath 14 may be attached or otherwise coupled tobase 602 or tosheath instrument 632 having aninstrument base 636, which may also have adrive assembly 630 rotatably positioned thereon. The control elements attached to theirrespective drive assembly 630 may each extend throughdelivery catheter 14 and couple to thehood 12, as described below, to bend, the distal end of thedeployment catheter 16 and/orhood 12 itself in any number of directions by displacing one of the control elements in the proximal direction to deflect the distal end of the catheter member in the predetermined direction. -
Catheter 14 may be coupled toinstrument base 636 such that, thedrive assembly 630 may be used to control a retraction or advancement of thecatheter 14 relative tohood 12 to control the expansion or collapse ofhood 12,FIG. 48B shows a detail perspective view of the distal end ofcatheter 16 extending fromdelivery catheter 14 and articulation of thehood 12 relative to thecatheter 16. In one variation,hood 12 may utilizeimaging element 620, e.g., CMOS, CCD imager, etc., positioned off axis relative to a longitudinal axis ofcatheter 16 and attached along one or more support struts 622 withinhood 12.Hood 12 may be connected tohood base 640 which is pivotable in a first plane via hinge orpivot 642.Flood base 640 may itself be pivotable in a second plane via hinge or pivot 644 and the distal end ofdeployment catheter 16 may further define anarticulatable section 638, which may allow its distal, end to articulate within a plane when urged by the one or more control elements. -
FIG. 48C illustrates a perspective view of another variation of a robotic control, assembly having aninflatable imaging balloon 653 assembly. As shown,imaging balloon 653 may be positioned uponarticulatable deployment catheter 16 and may further include aseparate anchoring balloon 655 positioned, uponsupport catheter 657 distally ofimaging balloon 653.Support catheter 657 may extend through both anchoringballoon 655 andimaging balloon 653 and define alumen 659 therethrough for accessing the tissue regions with, any number ofinstruments 667. In use,support catheter 657 and anchoring balloon 655 (in its deflated state) may be advanced into a vessel lumen, e.g., through the ostium of a pulmonary vein, where anchoringballoon 655 may be inflated into contact against the surrounding vessel walls. With anchoringballoon 655 inflated,support catheter 657 may be independently translatable with, respect to imaging balloon 653 (which may be inflated prior to, during, or after anchoring of the anchoring balloon 655) to allow for positional adjustment betweenimaging balloon 653 and the tissue surrounding the ostium. -
Imaging balloon 653 may be inflated with a transparent fluid or gas, as described above, and may be further supported structurally by one or more support struts 665 extending distally fromcatheter 16 within or along a proximal portion ofimaging balloon 653. During introduction and/or advancement through the patient body, support struts 665 may be collapsed along withimaging balloon 653 into a low-profile configuration and when deployed,balloon 653 may be inflated and support struts 665 may extend radially relative tocatheter 16 to supportimaging balloon 653. Additionally, support struts 665 may also support, one or morelight sources 661, e.g., light emitting diodes, optical fibers, etc. to provide illumination throughimaging balloon 653 for viewing the underlying contacted tissue.Imaging element 663, as above, may also be supported along or upon asupport strut 665 for viewing the tissue region throughballoon 653 as well. - A partially disassembled view of the
control element 606 spooled around arespective drive assembly 630 is illustrated in the perspective view ofFIG. 49 . As shown, eachassembly 630 may comprise anaxle 650 about whichassembly 630 may rotate in a first direction to spool, and thus proximally displace an attachedcontrol element 606 to deflect the distal end ofcatheter 16 is a first direction, or rotate in a second opposite direction to unspool, and thus distally displace the attachedcontrol element 606 to deflect the distal end ofcatheter 16 in a second opposite direction. - The
guide instrument 662 andsheath instrument 632 havingdeployment catheter 16 extending distally therefrom withhood 12 articulately disposed upon the distal end ofcatheter 16 is illustrated, in the perspective assembly view ofFIG. 50 . Bothguide instrument 662 andinstrument guide 632 are illustrated mounted uponinstrument driver 660, which functions as a platform.Instrument driver 660 may also provide additional degrees of precision control movements for the visualization catheter system.FIG. 51 shows a partial disassembled perspective view of theinstrument driver 660 assembly illustrating themain housing structure 670 underlying the assembly. As illustrated, cams and motors may be controlled by one ormore electronics boards 672 which may be coupled to themain housing structure 670. - In yet another variation of a mechanism which provides precision steering and articulation of the
hood 12 is shown in the perspective assembly view ofFIG. 52A . A precisioncontrol drive unit 680 may be attached todelivery catheter 14 and/ordeployment catheter 16 for providing articulation control.FIG. 52B illustrates a detailed perspective view of the distal end of one variation ofdeployment catheter 16 having thearticulatable section 638. Hinge orpivot imaging element 620 positioned withinhood 12, as described above.FIG. 53 illustrates an example of a simplified assembly view of the mechanisms withincontrol drive unit 680 for controlling the articulation ofhood 12. As shown, one or more pullwires 682 may be routed throughcatheter 14 tohood 12 with their proximal ends coupled to one ormore cams 684 or gears. Thesecams 684 may be rotatably coupled to one or more drive wheels 686, which are in turn in communication throughcontrol cables 688 to (optional) gearing 692 of motor driver 690. - The examples illustrating precision control assemblies for articulating the
hood 12 and/orcatheter 16 are further described in detail in U.S. Pat. App. 2006/0084945 A1 and U.S. Pat. No. 7,090,683, each of which has been incorporated above in their entirety. - In enabling the precision control assemblies to steer
hood 12 and/orcatheter 16 in multiple degrees of freedom, various couplings betweenhood 12 andcatheter 16 may be provided. One variation is illustrated in the detail perspective view ofFIGS. 54A and 54B , which show an assembled view and exploded assembly view, respectively. In this variation,hood 12, havingimaging element 620 positioned therewithin in an off-axis location, may be coupled or otherwise attached tohood base 640, which itself is pivotably coupled viahood mating portion 706 connected to receivingportion 708 viapin 710 to allowhood 12 to articulate within a first plane. Receivingportion 708 may also be pivotably coupled to receivingportion 702 viapin 704 to allowhood 12 to articulate within a second plane transverse to the first plane. The receivingportion 708 may also have one or more pullwire termination points 700 to which one or more pullwires 682 may be terminated. -
FIGS. 55A and 55C shows another variation where a pair ofpullwires 682 may steer a first planarly articulatablespine section 720 located near or at the distal end ofdeployment catheter 16. A second pair ofpullwires 682 may steerhood base 640 andhood 12 in a second plane transverse to the first plane. Thesteerable spine section 720 may comprise aspine segment 722 having multiple cut-outs or reducedsections 724 along either side of thespine segment 722 such that thespine section 720 may bend in a plane by flexing to either side of the reducedsections 724 while maintaining structural integrity by thespine segment 722, as illustrated in the detail view ofFIG. 55B .Spine section 720 may be comprised of various materials, e.g., stainless steel, PEEK or hard plastics, through machining, molding or metal injection molding. Moreover, stainless steel cables, Nitinol, elgiloy, or tungsten wires can be used for pullwires. Thesection 720 can be alternatively constructed as bump links, pinned links, ring links, laser cut tubes, fish bone spine links, silt tubes or double durometer tubes, etc., may also be steered using various mechanisms such as single bend steering, double bend steering with two or more pullwires, multi-way bend steering, and/or steering through multiple variations of catheter-sheath interactions. -
FIGS. 56A and 56C illustrate yet another variation of steering mechanisms in the perspective assembly and exploded assembly views. In this variation, a fullyarticulatable spine section 730 may be included near or at the distal end of deployment,catheter 16, as above, where thesection 730 includes acentral spine 734 having multiple cut-outs or reducedsections 732 circumferentially defined aboutcentral spine 734, as illustrated inFIG. 56B . Having the reducedsections 732 defined, entirely aroundspine 734 enables full articulation ofhood 12 aboutspine 734 rather than being limited for movement within a plane. - While utilizing a computer-controller for articulating the assembly, the computer may also track the movement of
hood 12 within a patient body, e.g., within the left atrial chamber of the heart, such that the location, and position relative to an anatomical landmark, e.g., the pulmonary veins, are known, at any given time. Other alternative mechanisms may also be utilized to track and/or record the position ofhood 12 within the body at any given time. - For instance,
FIG. 57A shows a perspective view of one such variation where aferromagnetic ring 740 may be attached circumferentially around the lip ofhood 12. Such a configuration may be utilized in conjunction with conventional magnetic navigation, systems, such as the NIOBE® system developed by Stereotaxis. Inc. (Saint Louis, Mo.), as illustrated in the perspective view ofFIG. 57B . An example of such a magnetic navigation system is shown and described in U.S. Pat. No. 7,019,610 (Creighton et al.) which is incorporated herein by reference in its entirety. Generally, an arrangement of twomagnets magnets ferromagnetic ring 740 positioned about the lip ofhood 12. By rotating and moving theexternal magnets -
FIG. 58 shows a perspective view of yet another variation of the tissue visualization catheter which is configured to detect the position and/or orientation of thehood 12 through the use of existing ultrasound technologies as described in, e.g., U.S. Pat. No. 5,515,853, which is incorporated herein by reference in its entirety. As shown, a first 750 and second 752 ultrasound signal transducer may be symmetrically attached, to thehood 12 around the circumference of the lip ofhood 12, while athird ultrasound transducer 754 may be placed between, the tip of thedeployment catheter 16 and the proximal end of thehood 12. - A ferromagnetic ring or an
electromagnetic coil 740 that is able to interact with a magnetic field to pull the hood towards a tissue surface may also be attached to the circumference of thehood 12. Alternatively, thestruts 758 supportinghood 12 may be made of a ferromagnetic material where one or more of thestruts 758 may haveelectromagnetic coils 756 wound around thestruts 758, as shown in the perspective view ofFIG. 59 . In yet another alternative, aferromagnetic disc 760 positioned upon asupport member 762 extending throughhood 12 may also be utilized, as shown in the perspective view ofFIG. 60 . In these or other variations ofhood 12, acircumferential balloon 742 which is inflatably positioned withinhood 12 and which defines a lumen orchannel 744 through theinflated balloon 742 may be optionally utilized. Such aballoon 742 is described in further detail in U.S. Pat. App. 11/775,771 filed Jul. 10, 2007, which is incorporated herein by reference in its entirety. - In either case, the ferromagnetic or electromagnetic feature and the
ultrasound signal transducers hood 12 may be used with aposition sensor assembly 770, as shown in the perspective view ofFIG. 61 .Position sensor assembly 770 may generally comprise aplate 772 made of radio-transparent material which may be positioned externally of a patient along a skin surface proximate or adjacent to where thehood 12 is to be controlled or tracked within the patient body.Plate 772 may have three ormore ultrasound transducers electromagnet 776 attached to handle 774 may be slidably positioned withinplate 772 for controlling a position ofhood 12 within the patient body, as described below. - Generally, each of the
ultrasound transducers hood 12 may communicate with theultrasound transducers plate 772 to determine their relative distances from one other by measuring the time between transmission and detection of the ultrasound signals, as illustrated inFIG. 62 . By triangulation methods, the position of each transducer alonghood 12 relative to each transducer alongplate 772, the three-dimensional orientation and position of thehood 12 within the patient body may be computationally determined by a processor and displayed graphically or otherwise to the user. The user may determine an orientation of thehood 12, for instance if thehood 12 is facing theexternal plate 772 within the patient body, when 750 and 752 are of equal distance to theplate 772. Similarly using the same triangulation method, the position of thehood 12 can be determined. Moreover, knowing whichquadrant hood 12 is relatively positioned may be utilized in differentiating between particular anatomical features, e.g., determining which of the four pulmonary veins the user may be viewing in a patient's heart utilizing the imaging element withinhood 12, as described above. - Detailed examples are further shown and described in U.S. Pat. No. 5,515,853, which is incorporated herein above. Additionally, although three transducers are illustrated in the example on
hood 12 as well asplate 772, additional transducers may be optionally utilized. - Moreover, in activating the
electromagnet 776, e.g., by a foot pedal, the ferromagnetic element located on thehood 12 may be drawn via magnetic attraction towards the externally locatedplate 772 such thathood 12 is consequently drawn against the internal tissue surface. By drawing thehood 12 against the internal tissue surface,hood 12 may be positioned or articulated against the tissue surface by the externally locatedhandle 774 andelectromagnet 776 to facilitate movement of thehood 12 along tissue walls. - An example is illustrated, in
FIGS. 63A to 63C which showshood 12 having circumferentialferromagnetic ring 740 positioned thereon located within the left atrium LA of heart H. In placingplate 772 ofassembly 770 against the external skin surface S of the patient body (e.g., behind the back of the patient, in a position directly below the heart H, or any other position on the patient body where a visualization catheter is to be advanced along, into, or through an underlying organ or body lumen), a layer of ultrasound coupling gel may be applied between tire skin S and theexternal plate 772, to ensure that ultrasound signals are conducted efficiently. After entry ofhood 12 within left atrium LA, the orientation and position of thehood 12 may be determined via triangulation relative toplate assembly 770, as shown inFIG. 63A . Upon orienting thehood 12 in a desired orientation and/or position, themovable electromagnet 776 in theexternal plate 772 can be magnetized, e.g., by stepping on a foot pedal, to draw theelectromagnetic ring 740mid hood 12 towards the tissue wall, as shown inFIG. 63B . With thehood 12 positioned upon the tissue wall, handle 774 andelectromagnet 776 may be moved in adirection 800 withinplate 772 to “walk” or movehood 12 along the tissue wall in acorresponding direction 800′. Whilehood 12 is drawn against the tissue wall, the open area may be purged of blood and the underlying tissue may be viewed throughimaging element 620, as described above. - Another variation is illustrated in the partial cross-sectional, view of
FIG. 64 , which illustrates an example where rather than utilizing ultrasound transducers along an externally located plate, acatheter 810 having at least threetransducers transducers hood 12, may reduce the loss of ultrasound signals to the environment as compared to having-transducers placed outside the body. Moreover, having the transducers communicating within the body also removes the need for ultrasound coupling gel to be applied, on the patient's skin. - The applications of the disclosed invention discussed above are not limited to certain treatments or regions of the body, but may include any number of other treatments and areas of the body. Modification of the above-described methods and devices for carrying out the invention, and variations of aspects of the invention that are obvious to those of skill in the arts are intended to be within the scope of this disclosure. Moreover, various combinations of aspects between examples are also contemplated and are considered to be within the scope of this disclosure as well.
Claims (30)
1. A computer-assisted heart treatment system for treating a tissue of a heart, wherein blood is disposed within a chamber of the heart, the heart, treatment system comprising:
an articulatable catheter;
an imaging assembly carried by the catheter, the imaging assembly configured to obtain, while blood is disposed in the chamber, an image of a tissue surface within the chamber;
a display coupleable to the imaging assembly so as to display tire tissue surface image;
a computer-controlled guidance assembly coupled to the catheter so as to move the imaging assembly; and
a processor coupled to the computer-controlled guidance assembly so that the articulation of the catheter effects repositioning of the imaging assemble registered to the displayed tissue surface.
2. The system, of claim 1 further comprising a tracking system transmitting position feedback signals to the processor, wherein the processor transmits drive signals for the computer-controlled guidance assembly using the position feedback signals.
3. The system, of claim 2 wherein the imaging assembly comprises an imaging element and a barrier or membrane, and wherein the imaging assembly is pivotably coupled to the articulatable catheter.
4. The system of claim 3 wherein the barrier or membrane is pivotably coupled to the articulatable catheter such that the membrane is movable within a first plane in response to signals from the computer-controlled guidance assembly, and wherein the barrier or membrane is further pivotably coupled to the articulatable catheter such that the barrier or membrane is movable within a second plane transverse to the first plane in response to signals from the computer-controlled guidance assembly.
5. The system of claim 3 wherein the articulatable catheter comprises a steerable segment proximal to the barrier or membrane and having a spine and a plurality of reduced sections along the segment to facilitate steering of the segment.
6. The system of claim 5 wherein the plurality of reduced sections are located circumferentially such that the segment is steerable in more than one plane.
7. The system of claim 1 wherein the computer-controlled guidance assembly comprises one or more drive assemblies coupled to the distal end of the catheter via a respective pullwire.
8. The system of claim 7 wherein the drive assemblies comprise a member rotatably positioned upon an axle such that rotation of the member in a first rotational direction urges the catheter to deflect in a first direction and rotation of the member in a second rotational direction opposite to the first rotational direction urges the catheter to deflect in a second direction opposite to the first direction.
9. The system of claim 1 further comprising an instrument guidance assembly configured to retract an outer sheath relative to the articulatable catheter.
10. The system of claim 1 further comprising an instrument driver upon which the catheter is mounted and extends from.
11. A computer-assisted heart treatment system for treating a tissue of a heart, wherein blood is disposed within a chamber of the heart, the heart treatment system comprising:
an articulatable catheter;
an imaging assembly carried by the catheter, the imaging assembly configured to obtain, while blood is disposed in the chamber, an image of a tissue surface within the chamber;
a computer-control led guidance assembly coupled to the catheter so as to move the imaging assembly in response to drive signals;
a tracking system transmitting position feedback signals in response to movement of the imaging assembly; and
a processor coupled to the computer-controlled guidance assembly and the tracking system, the processor configured to transmits the drive signals using the position feedback signals.
12. A tissue treatment system, comprising:
a barrier or membrane having a first low-profile configuration and a second expanded, configuration defining an open area therein;
an articulatable catheter upon which the membrane projects distally; and
at least one magnetic element positioned within or along the barrier or membrane.
13. The system of claim 12 wherein the barrier or membrane is configured in a conical shape.
14. The system of claim 12 further comprising an imaging element positioned within or along the barrier or membrane such that tissue adjacent to the open area is able to be visualized via the imaging element.
15. The system of claim 12 wherein the open area is in communication with a fluid lumen defined through the catheter, and further comprising a fluid, reservoir fluidly coupled to the barrier or membrane via the fluid lumen.
16. The system of claim 12 wherein the at least one magnetic element comprises a magnetic ring positioned circumferentially about a lip of the barrier or membrane.
17. The system of claim 12 wherein the at least, one magnetic element comprises one or more coils positioned about one or more respective support struts extending along the barrier or membrane.
18. The system of claim 12 wherein the at least one magnetic element comprises a magnetic disc positioned upon, a support member extending through the barrier or membrane.
19. The system of claim 12 further comprising at least two external magnets positioned in proximity to a patient body and independently moveable, wherein movement by the at least two external magnets relative to the patient body results in a corresponding movement by the at least one magnetic element within the patient body.
20. The system of claim 12 further comprising at least two ultrasonic transducers positioned along the barrier or membrane and a third ultrasonic transducer positioned proximal to the barrier or membrane.
21. The system of claim 20 further comprising an external plate assembly having at least three ultrasonic transducers positioned over the plate assembly at known distances relative to one another.
22. The system of claim 21 further comprising an electromagnetic element moveable over the plate assembly, whereby movement by the electromagnetic element relative to the patient body results in a corresponding movement by the at least one magnetic element within the patient body.
23. A computer assisted method of treating a tissue surface region within a chamber of a heart, comprising:
positioning a distal portion of a catheter within the chamber, the catheter coupled to a computer-controlled guidance assembly;
locally displacing blood with a transparent fluid from an open area disposed within a portion of the chamber, the open area disposed adjacent the tissue region;
visualizing, on a display, the tissue region within the open area as imaged through the transparent fluid, and
articulating the catheter with the computer-controlled guidance assembly so that movement of the catheter within the chamber is registered, with the tissue surface region shown on the display.
24. The method of claim 23 wherein positioning comprises advancing the barrier or membrane into a left atrial chamber of a heart.
25. The method of claim 23 wherein positioning comprises deploying the barrier or membrane from a low-profile delivery configuration into an expanded deployed configuration.
26. The method of claim 23 wherein positioning comprises stabilizing a position of the barrier or membrane relative to the tissue region.
27. The method of claim 23 wherein displacing an opaque fluid comprises infusing the transparent fluid into the open area through a fluid delivery lumen defined through the catheter.
28. The method of claim 27 wherein infusing the transparent fluid comprises pumping saline, plasma, water, or perfluorinated liquid into the open area such that blood is displaced from therefrom.
29. The method of claim 23 wherein positioning comprises rotating one or more drive assemblies coupled to a distal end of the catheter via a respective pullwire.
30. The method of claim 29 wherein rotation of the drive assemblies in a first rotational direction urges the catheter to deflect in a first direction and rotation of the member in a second rotational direction opposite to the first rotational direction urges the catheter to deflect in a second direction opposite to the first direction.
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Cited By (64)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060184048A1 (en) * | 2005-02-02 | 2006-08-17 | Vahid Saadat | Tissue visualization and manipulation system |
US20070288078A1 (en) * | 2006-03-17 | 2007-12-13 | Steve Livneh | Apparatus and method for skin tightening and corrective forming |
US20080009747A1 (en) * | 2005-02-02 | 2008-01-10 | Voyage Medical, Inc. | Transmural subsurface interrogation and ablation |
US20080033290A1 (en) * | 2005-10-25 | 2008-02-07 | Voyage Medical, Inc. | Delivery of biological compounds to ischemic and/or infarcted tissue |
US20080058590A1 (en) * | 2006-09-01 | 2008-03-06 | Nidus Medical, Llc. | Tissue visualization device having multi-segmented frame |
US20080108876A1 (en) * | 2001-09-06 | 2008-05-08 | Houser Russell A | Superelastic/Shape Memory Tissue Stabilizers and Surgical Instruments |
US20080214889A1 (en) * | 2006-10-23 | 2008-09-04 | Voyage Medical, Inc. | Methods and apparatus for preventing tissue migration |
US20090227999A1 (en) * | 2007-05-11 | 2009-09-10 | Voyage Medical, Inc. | Visual electrode ablation systems |
US20100049099A1 (en) * | 2008-07-18 | 2010-02-25 | Vytronus, Inc. | Method and system for positioning an energy source |
US20100094081A1 (en) * | 2008-10-10 | 2010-04-15 | Voyage Medical, Inc. | Electrode placement and connection systems |
US20100204561A1 (en) * | 2009-02-11 | 2010-08-12 | Voyage Medical, Inc. | Imaging catheters having irrigation |
US20100211057A1 (en) * | 1995-01-23 | 2010-08-19 | Cardio Vascular Technologies, Inc. a California Corporation | Tissue heating device and rf heating method with tissue attachment feature |
US20100262140A1 (en) * | 2008-10-10 | 2010-10-14 | Voyage Medical, Inc. | Integral electrode placement and connection systems |
US20100292558A1 (en) * | 2006-06-14 | 2010-11-18 | Voyage Medical, Inc. | In-vivo visualization systems |
US20100305451A1 (en) * | 2009-05-29 | 2010-12-02 | Boston Scientific Scimed, Inc. | Systems and methods for making and using image-guided intravascular and endocardial therapy systems |
US7860556B2 (en) | 2005-02-02 | 2010-12-28 | Voyage Medical, Inc. | Tissue imaging and extraction systems |
US7918787B2 (en) | 2005-02-02 | 2011-04-05 | Voyage Medical, Inc. | Tissue visualization and manipulation systems |
US7930016B1 (en) | 2005-02-02 | 2011-04-19 | Voyage Medical, Inc. | Tissue closure system |
US20110160596A1 (en) * | 2009-12-24 | 2011-06-30 | Renzo Cecere | Instrument including a movement sensor and method of using same |
US8050746B2 (en) | 2005-02-02 | 2011-11-01 | Voyage Medical, Inc. | Tissue visualization device and method variations |
US8078266B2 (en) | 2005-10-25 | 2011-12-13 | Voyage Medical, Inc. | Flow reduction hood systems |
US8131350B2 (en) | 2006-12-21 | 2012-03-06 | Voyage Medical, Inc. | Stabilization of visualization catheters |
US8221310B2 (en) | 2005-10-25 | 2012-07-17 | Voyage Medical, Inc. | Tissue visualization device and method variations |
US8235985B2 (en) | 2007-08-31 | 2012-08-07 | Voyage Medical, Inc. | Visualization and ablation system variations |
US20130012929A1 (en) * | 2011-07-08 | 2013-01-10 | Tyco Healthcare Group Lp | Swinging Bars with Axial Wheels to Drive Articulating Cables |
US8657805B2 (en) | 2007-05-08 | 2014-02-25 | Intuitive Surgical Operations, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
US8694071B2 (en) | 2010-02-12 | 2014-04-08 | Intuitive Surgical Operations, Inc. | Image stabilization techniques and methods |
US8758229B2 (en) | 2006-12-21 | 2014-06-24 | Intuitive Surgical Operations, Inc. | Axial visualization systems |
US20140276725A1 (en) * | 2013-03-13 | 2014-09-18 | Arthrocare Corporation | Method and system of controlling conductive fluid flow during an electrosurgical procedure |
US8858609B2 (en) | 2008-02-07 | 2014-10-14 | Intuitive Surgical Operations, Inc. | Stent delivery under direct visualization |
US20140330133A1 (en) * | 2013-05-02 | 2014-11-06 | VS Medtech, Inc. | Systems and methods for measuring and characterizing interior surfaces of luminal structures |
US8934962B2 (en) | 2005-02-02 | 2015-01-13 | Intuitive Surgical Operations, Inc. | Electrophysiology mapping and visualization system |
US9014789B2 (en) | 2011-09-22 | 2015-04-21 | The George Washington University | Systems and methods for visualizing ablated tissue |
US9084611B2 (en) | 2011-09-22 | 2015-07-21 | The George Washington University | Systems and methods for visualizing ablated tissue |
US9101735B2 (en) | 2008-07-07 | 2015-08-11 | Intuitive Surgical Operations, Inc. | Catheter control systems |
US9155452B2 (en) | 2007-04-27 | 2015-10-13 | Intuitive Surgical Operations, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
US9468364B2 (en) | 2008-11-14 | 2016-10-18 | Intuitive Surgical Operations, Inc. | Intravascular catheter with hood and image processing systems |
US9510732B2 (en) | 2005-10-25 | 2016-12-06 | Intuitive Surgical Operations, Inc. | Methods and apparatus for efficient purging |
US9814522B2 (en) | 2010-04-06 | 2017-11-14 | Intuitive Surgical Operations, Inc. | Apparatus and methods for ablation efficacy |
US20180021089A1 (en) * | 2015-02-09 | 2018-01-25 | Vimecon Gmbh | Laser Applicator Having Electrodes |
US10004388B2 (en) | 2006-09-01 | 2018-06-26 | Intuitive Surgical Operations, Inc. | Coronary sinus cannulation |
US10058380B2 (en) | 2007-10-05 | 2018-08-28 | Maquet Cordiovascular Llc | Devices and methods for minimally-invasive surgical procedures |
US10064540B2 (en) | 2005-02-02 | 2018-09-04 | Intuitive Surgical Operations, Inc. | Visualization apparatus for transseptal access |
US10070772B2 (en) | 2006-09-01 | 2018-09-11 | Intuitive Surgical Operations, Inc. | Precision control systems for tissue visualization and manipulation assemblies |
US10143517B2 (en) | 2014-11-03 | 2018-12-04 | LuxCath, LLC | Systems and methods for assessment of contact quality |
CN109310283A (en) * | 2016-04-19 | 2019-02-05 | 波士顿科学国际有限公司 | Foley's tube visualization device including reinforcing element |
US10441136B2 (en) | 2006-12-18 | 2019-10-15 | Intuitive Surgical Operations, Inc. | Systems and methods for unobstructed visualization and ablation |
CN111278343A (en) * | 2017-10-25 | 2020-06-12 | 波士顿科学国际有限公司 | Direct visualization catheter and system |
US10722301B2 (en) | 2014-11-03 | 2020-07-28 | The George Washington University | Systems and methods for lesion assessment |
CN111655115A (en) * | 2017-09-14 | 2020-09-11 | 维卡瑞斯外科手术股份有限公司 | Virtual reality surgical camera system |
US10779904B2 (en) | 2015-07-19 | 2020-09-22 | 460Medical, Inc. | Systems and methods for lesion formation and assessment |
US20200311930A1 (en) * | 2019-03-28 | 2020-10-01 | Purdue Research Foundation | System and methods for clear optimally matched panoramic channel technique for deep brain photonic interface |
US10828081B2 (en) | 2013-03-07 | 2020-11-10 | Arthrocare Corporation | Methods and systems related to electrosurgical wands |
WO2021022205A1 (en) * | 2019-07-31 | 2021-02-04 | Orsus, Llc | Devices and methods for guide wire placement |
CN112584774A (en) * | 2018-06-28 | 2021-03-30 | 皇家飞利浦有限公司 | Internally ultrasound assisted local therapy delivery |
US11096584B2 (en) | 2013-11-14 | 2021-08-24 | The George Washington University | Systems and methods for determining lesion depth using fluorescence imaging |
US11344365B2 (en) | 2016-01-05 | 2022-05-31 | Cardiofocus, Inc. | Ablation system with automated sweeping ablation energy element |
US11389236B2 (en) | 2018-01-15 | 2022-07-19 | Cardiofocus, Inc. | Ablation system with automated ablation energy element |
US11406250B2 (en) | 2005-02-02 | 2022-08-09 | Intuitive Surgical Operations, Inc. | Methods and apparatus for treatment of atrial fibrillation |
CN115040063A (en) * | 2022-06-10 | 2022-09-13 | 兰州大学第二医院 | Biliary tract photography catheter system and use method |
US11439464B2 (en) * | 2016-06-28 | 2022-09-13 | Karl PIEPER | Appliance for conveying a catheter, light guide or cable in a controlled manner |
US11457817B2 (en) | 2013-11-20 | 2022-10-04 | The George Washington University | Systems and methods for hyperspectral analysis of cardiac tissue |
US20220322926A1 (en) * | 2017-11-09 | 2022-10-13 | Corinth MedTech, Inc. | Surgical devices and methods |
US11478152B2 (en) | 2005-02-02 | 2022-10-25 | Intuitive Surgical Operations, Inc. | Electrophysiology mapping and visualization system |
Families Citing this family (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20110015484A1 (en) * | 2009-07-16 | 2011-01-20 | Alvarez Jeffrey B | Endoscopic robotic catheter system |
US9254090B2 (en) * | 2010-10-22 | 2016-02-09 | Intuitive Surgical Operations, Inc. | Tissue contrast imaging systems |
US9629595B2 (en) * | 2013-03-15 | 2017-04-25 | Hansen Medical, Inc. | Systems and methods for localizing, tracking and/or controlling medical instruments |
WO2017144288A1 (en) * | 2016-02-23 | 2017-08-31 | Koninklijke Philips N.V. | Ultrasound ablation device |
EP3372356B1 (en) * | 2017-03-06 | 2020-05-06 | Siemens Healthcare GmbH | System and method for motion capture and controlling a robotic tool |
JP2021104072A (en) * | 2018-03-14 | 2021-07-26 | オリンパス株式会社 | Endoscope apparatus and fluid feeding method using endoscope apparatus |
AU2020366348A1 (en) | 2019-10-15 | 2022-05-12 | Imperative Care, Inc. | Systems and methods for multivariate stroke detection |
US11786106B2 (en) | 2020-05-26 | 2023-10-17 | Canon U.S.A., Inc. | Robotic endoscope probe having orientation reference markers |
US20230329689A1 (en) * | 2020-09-17 | 2023-10-19 | Shifamed Holdings, Llc | Tissue piercing assemblies and methods of use |
Citations (31)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3874388A (en) * | 1973-02-12 | 1975-04-01 | Ochsner Med Found Alton | Shunt defect closure system |
US4681093A (en) * | 1982-12-13 | 1987-07-21 | Sumitomo Electric Industries, Ltd. | Endoscope |
US5515853A (en) * | 1995-03-28 | 1996-05-14 | Sonometrics Corporation | Three-dimensional digital ultrasound tracking system |
US5575756A (en) * | 1993-08-16 | 1996-11-19 | Olympus Optical Co., Ltd. | Endoscope apparatus |
US5695448A (en) * | 1994-08-29 | 1997-12-09 | Olympus Optical Co., Ltd. | Endoscopic sheath |
US5895417A (en) * | 1996-03-06 | 1999-04-20 | Cardiac Pathways Corporation | Deflectable loop design for a linear lesion ablation apparatus |
US5941845A (en) * | 1997-08-05 | 1999-08-24 | Irvine Biomedical, Inc. | Catheter having multiple-needle electrode and methods thereof |
US5944690A (en) * | 1997-03-17 | 1999-08-31 | C.R. Bard, Inc. | Slidable control mechanism for steerable catheter |
US6129724A (en) * | 1993-10-14 | 2000-10-10 | Ep Technologies, Inc. | Systems and methods for forming elongated lesion patterns in body tissue using straight or curvilinear electrode elements |
US6258083B1 (en) * | 1996-03-29 | 2001-07-10 | Eclipse Surgical Technologies, Inc. | Viewing surgical scope for minimally invasive procedures |
US20020087166A1 (en) * | 1998-02-24 | 2002-07-04 | Brock David L. | Flexible instrument |
US20020087169A1 (en) * | 1998-02-24 | 2002-07-04 | Brock David L. | Flexible instrument |
US6428536B2 (en) * | 1996-01-19 | 2002-08-06 | Ep Technologies, Inc. | Expandable-collapsible electrode structures made of electrically conductive material |
US6475223B1 (en) * | 1997-08-29 | 2002-11-05 | Stereotaxis, Inc. | Method and apparatus for magnetically controlling motion direction of a mechanically pushed catheter |
US6482162B1 (en) * | 1998-12-08 | 2002-11-19 | Scimed Life Systems, Inc. | Loop imaging catheter |
US6587709B2 (en) * | 2001-03-28 | 2003-07-01 | Koninklijke Philips Electronics N.V. | Method of and imaging ultrasound system for determining the position of a catheter |
US20030171741A1 (en) * | 2001-11-14 | 2003-09-11 | Latis, Inc. | Catheters for clot removal |
US20040117032A1 (en) * | 1993-02-22 | 2004-06-17 | Roth Alex T. | Devices for less-invasive intracardiac interventions |
US20050182465A1 (en) * | 2004-02-12 | 2005-08-18 | Ness Gregory O. | Instruments and methods for accessing an anatomic space |
US20060030844A1 (en) * | 2004-08-04 | 2006-02-09 | Knight Bradley P | Transparent electrode for the radiofrequency ablation of tissue |
US7019610B2 (en) * | 2002-01-23 | 2006-03-28 | Stereotaxis, Inc. | Magnetic navigation system |
US20060084945A1 (en) * | 2004-03-05 | 2006-04-20 | Hansen Medical, Inc. | Instrument driver for robotic catheter system |
US20060184048A1 (en) * | 2005-02-02 | 2006-08-17 | Vahid Saadat | Tissue visualization and manipulation system |
US20060271032A1 (en) * | 2005-05-26 | 2006-11-30 | Chin Albert K | Ablation instruments and methods for performing abalation |
US20070270686A1 (en) * | 2006-05-03 | 2007-11-22 | Ritter Rogers C | Apparatus and methods for using inertial sensing to navigate a medical device |
US20070293724A1 (en) * | 2005-02-02 | 2007-12-20 | Voyage Medical, Inc. | Visualization apparatus for transseptal access |
US20080009747A1 (en) * | 2005-02-02 | 2008-01-10 | Voyage Medical, Inc. | Transmural subsurface interrogation and ablation |
US20080015569A1 (en) * | 2005-02-02 | 2008-01-17 | Voyage Medical, Inc. | Methods and apparatus for treatment of atrial fibrillation |
US20080015445A1 (en) * | 2005-02-02 | 2008-01-17 | Voyage Medical, Inc. | Tissue visualization device and method variations |
US20080033290A1 (en) * | 2005-10-25 | 2008-02-07 | Voyage Medical, Inc. | Delivery of biological compounds to ischemic and/or infarcted tissue |
US20080275300A1 (en) * | 2007-04-27 | 2008-11-06 | Voyage Medical, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
Family Cites Families (545)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US623002A (en) | 1899-04-11 | Gerald | ||
US623022A (en) | 1899-04-11 | johnson | ||
US2305462A (en) | 1940-06-20 | 1942-12-15 | Wolf Richard | Cystoscopic instrument |
US2453862A (en) | 1947-06-02 | 1948-11-16 | Salisbury Peter Frederic | Gastroscope |
US3559651A (en) * | 1968-10-14 | 1971-02-02 | David H Moss | Body-worn all disposable urinal |
US3831587A (en) | 1973-02-08 | 1974-08-27 | Mc Anally R | Multipurpose vaginal and cervical device |
US3903877A (en) | 1973-06-13 | 1975-09-09 | Olympus Optical Co | Endoscope |
US4175545A (en) | 1977-03-10 | 1979-11-27 | Zafmedico Corp. | Method and apparatus for fiber-optic cardiovascular endoscopy |
DE2853466C2 (en) | 1977-12-11 | 1983-03-24 | Kabushiki Kaisha Medos Kenkyusho, Tokyo | endoscope |
US4198981A (en) * | 1978-03-27 | 1980-04-22 | Manfred Sinnreich | Intrauterine surgical device |
US4326529A (en) | 1978-05-26 | 1982-04-27 | The United States Of America As Represented By The United States Department Of Energy | Corneal-shaping electrode |
US4403612A (en) | 1980-10-20 | 1983-09-13 | Fogarty Thomas J | Dilatation method |
JPS5869527A (en) | 1981-10-20 | 1983-04-25 | 富士写真フイルム株式会社 | High frequency knife and endoscope using same |
US4470407A (en) | 1982-03-11 | 1984-09-11 | Laserscope, Inc. | Endoscopic device |
US4445892A (en) | 1982-05-06 | 1984-05-01 | Laserscope, Inc. | Dual balloon catheter device |
US5435805A (en) | 1992-08-12 | 1995-07-25 | Vidamed, Inc. | Medical probe device with optical viewing capability |
JPS5993413A (en) | 1982-11-18 | 1984-05-29 | Olympus Optical Co Ltd | Endoscope |
CA1244889A (en) | 1983-01-24 | 1988-11-15 | Kureha Chemical Ind Co Ltd | Device for hyperthermia |
JPS59172621A (en) * | 1983-03-22 | 1984-09-29 | Sumitomo Electric Ind Ltd | Fiberscope |
US4619247A (en) | 1983-03-31 | 1986-10-28 | Sumitomo Electric Industries, Ltd. | Catheter |
JPS59181315A (en) | 1983-03-31 | 1984-10-15 | Kiyoshi Inoue | Fiber scope |
US4569335A (en) * | 1983-04-12 | 1986-02-11 | Sumitomo Electric Industries, Ltd. | Fiberscope |
JPS60125610U (en) | 1984-02-03 | 1985-08-24 | オリンパス光学工業株式会社 | Strabismus-type rigid endoscope |
US4960411A (en) | 1984-09-18 | 1990-10-02 | Medtronic Versaflex, Inc. | Low profile sterrable soft-tip catheter |
JPS626212A (en) * | 1985-07-02 | 1987-01-13 | Olympus Optical Co Ltd | Image signal processing circuit |
US4696668A (en) * | 1985-07-17 | 1987-09-29 | Wilcox Gilbert M | Double balloon nasobiliary occlusion catheter for treating gallstones and method of using the same |
DE3686621T2 (en) | 1985-07-31 | 1993-02-25 | Bard Inc C R | INFRARED LASER CATHETER DEVICE. |
US4917084A (en) | 1985-07-31 | 1990-04-17 | C. R. Bard, Inc. | Infrared laser catheter system |
US4710192A (en) | 1985-12-30 | 1987-12-01 | Liotta Domingo S | Diaphragm and method for occlusion of the descending thoracic aorta |
US4772260A (en) | 1986-05-02 | 1988-09-20 | Heyden Eugene L | Rectal catheter |
US4709698A (en) | 1986-05-14 | 1987-12-01 | Thomas J. Fogarty | Heatable dilation catheter |
US4838246A (en) | 1986-08-13 | 1989-06-13 | Messerschmitt-Bolkow-Blohm Gmbh | Application part for an endoscope |
US4961738A (en) | 1987-01-28 | 1990-10-09 | Mackin Robert A | Angioplasty catheter with illumination and visualization within angioplasty balloon |
US4784133A (en) | 1987-01-28 | 1988-11-15 | Mackin Robert A | Working well balloon angioscope and method |
US4976710A (en) | 1987-01-28 | 1990-12-11 | Mackin Robert A | Working well balloon method |
NL8700329A (en) | 1987-02-11 | 1988-09-01 | Hoed Daniel Stichting | DEVICE AND METHOD FOR EXAMINING AND / OR EXPOSING A CAVE IN A BODY. |
US5090959A (en) * | 1987-04-30 | 1992-02-25 | Advanced Cardiovascular Systems, Inc. | Imaging balloon dilatation catheter |
US4943290A (en) | 1987-06-23 | 1990-07-24 | Concept Inc. | Electrolyte purging electrode tip |
IT1235460B (en) | 1987-07-31 | 1992-07-30 | Confida Spa | FLEXIBLE ENDOSCOPE. |
US5372138A (en) | 1988-03-21 | 1994-12-13 | Boston Scientific Corporation | Acousting imaging catheters and the like |
US4998972A (en) * | 1988-04-28 | 1991-03-12 | Thomas J. Fogarty | Real time angioscopy imaging system |
EP0415997A4 (en) | 1988-05-18 | 1992-04-08 | Kasevich Associates, Inc. | Microwave balloon angioplasty |
US4880015A (en) * | 1988-06-03 | 1989-11-14 | Nierman David M | Biopsy forceps |
US6120437A (en) | 1988-07-22 | 2000-09-19 | Inbae Yoon | Methods for creating spaces at obstructed sites endoscopically and methods therefor |
US4957484A (en) | 1988-07-26 | 1990-09-18 | Automedix Sciences, Inc. | Lymph access catheters and methods of administration |
US5123428A (en) | 1988-10-11 | 1992-06-23 | Schwarz Gerald R | Laparoscopically implanting bladder control apparatus |
US4994069A (en) * | 1988-11-02 | 1991-02-19 | Target Therapeutics | Vaso-occlusion coil and method |
US4998916A (en) * | 1989-01-09 | 1991-03-12 | Hammerslag Julius G | Steerable medical device |
US4914521A (en) | 1989-02-03 | 1990-04-03 | Adair Edwin Lloyd | Sterilizable video camera cover |
USRE34002E (en) | 1989-02-03 | 1992-07-21 | Sterilizable video camera cover | |
US4911148A (en) * | 1989-03-14 | 1990-03-27 | Intramed Laboratories, Inc. | Deflectable-end endoscope with detachable flexible shaft assembly |
US4991578A (en) * | 1989-04-04 | 1991-02-12 | Siemens-Pacesetter, Inc. | Method and system for implanting self-anchoring epicardial defibrillation electrodes |
DE3915636C1 (en) | 1989-05-12 | 1990-04-26 | Sass, Wolfgang, Dr. | |
NL8901350A (en) * | 1989-05-29 | 1990-12-17 | Wouter Matthijs Muijs Van De M | CLOSURE ASSEMBLY. |
US4950285A (en) | 1989-11-27 | 1990-08-21 | Wilk Peter J | Suture device |
US5345927A (en) | 1990-03-02 | 1994-09-13 | Bonutti Peter M | Arthroscopic retractors |
US5514153A (en) | 1990-03-02 | 1996-05-07 | General Surgical Innovations, Inc. | Method of dissecting tissue layers |
US5025778A (en) | 1990-03-26 | 1991-06-25 | Opielab, Inc. | Endoscope with potential channels and method of using the same |
JP2893833B2 (en) | 1990-03-30 | 1999-05-24 | 東レ株式会社 | Endoscopic balloon catheter |
WO1991015155A1 (en) | 1990-04-02 | 1991-10-17 | Kanji Inoue | Device for closing shunt opening by nonoperative method |
US5236413B1 (en) | 1990-05-07 | 1996-06-18 | Andrew J Feiring | Method and apparatus for inducing the permeation of medication into internal tissue |
US5197457A (en) | 1990-09-12 | 1993-03-30 | Adair Edwin Lloyd | Deformable and removable sheath for optical catheter |
US5370647A (en) | 1991-01-23 | 1994-12-06 | Surgical Innovations, Inc. | Tissue and organ extractor |
JP2953079B2 (en) | 1991-02-14 | 1999-09-27 | 富士写真光機株式会社 | Electronic endoscope device |
US5156141A (en) | 1991-03-11 | 1992-10-20 | Helmut Krebs | Connector for coupling an endoscope to a video camera |
JP3065702B2 (en) | 1991-04-23 | 2000-07-17 | オリンパス光学工業株式会社 | Endoscope system |
US5330496A (en) | 1991-05-06 | 1994-07-19 | Alferness Clifton A | Vascular catheter assembly for tissue penetration and for cardiac stimulation and methods thereof |
ATE168545T1 (en) | 1991-05-29 | 1998-08-15 | Origin Medsystems Inc | RETRACTOR DEVICE FOR ENDOSCOPIC SURGERY |
US5865728A (en) | 1991-05-29 | 1999-02-02 | Origin Medsystems, Inc. | Method of using an endoscopic inflatable lifting apparatus to create an anatomic working space |
US5697281A (en) | 1991-10-09 | 1997-12-16 | Arthrocare Corporation | System and method for electrosurgical cutting and ablation |
JPH05103746A (en) | 1991-10-18 | 1993-04-27 | Olympus Optical Co Ltd | Metabolism information measuring device |
US5282827A (en) * | 1991-11-08 | 1994-02-01 | Kensey Nash Corporation | Hemostatic puncture closure system and method of use |
US5281238A (en) * | 1991-11-22 | 1994-01-25 | Chin Albert K | Endoscopic ligation instrument |
US6190381B1 (en) * | 1995-06-07 | 2001-02-20 | Arthrocare Corporation | Methods for tissue resection, ablation and aspiration |
US5697882A (en) | 1992-01-07 | 1997-12-16 | Arthrocare Corporation | System and method for electrosurgical cutting and ablation |
CA2089999A1 (en) | 1992-02-24 | 1993-08-25 | H. Jonathan Tovey | Resilient arm mesh deployer |
US5334159A (en) | 1992-03-30 | 1994-08-02 | Symbiosis Corporation | Thoracentesis needle assembly utilizing check valve |
FR2689388B1 (en) | 1992-04-07 | 1999-07-16 | Celsa Lg | PERFECTIONALLY RESORBABLE BLOOD FILTER. |
DE4214283A1 (en) | 1992-04-30 | 1993-11-04 | Schneider Co Optische Werke | Contactless length measuring camera - contains semiconducting transducer moved axially within camera body during focussing |
US5305121A (en) | 1992-06-08 | 1994-04-19 | Origin Medsystems, Inc. | Stereoscopic endoscope system |
US5336252A (en) | 1992-06-22 | 1994-08-09 | Cohen Donald M | System and method for implanting cardiac electrical leads |
US5672153A (en) | 1992-08-12 | 1997-09-30 | Vidamed, Inc. | Medical probe device and method |
US5527338A (en) | 1992-09-02 | 1996-06-18 | Board Of Regents, The University Of Texas System | Intravascular device |
US5313934A (en) | 1992-09-10 | 1994-05-24 | Deumed Group Inc. | Lens cleaning means for invasive viewing medical instruments |
US5339800A (en) | 1992-09-10 | 1994-08-23 | Devmed Group Inc. | Lens cleaning means for invasive viewing medical instruments with anti-contamination means |
AT397458B (en) | 1992-09-25 | 1994-04-25 | Avl Verbrennungskraft Messtech | SENSOR ARRANGEMENT |
US5313943A (en) | 1992-09-25 | 1994-05-24 | Ep Technologies, Inc. | Catheters and methods for performing cardiac diagnosis and treatment |
US5373840A (en) | 1992-10-02 | 1994-12-20 | Knighton; David R. | Endoscope and method for vein removal |
NL9201965A (en) | 1992-11-10 | 1994-06-01 | Draeger Med Electronics Bv | Invasive MRI transducer. |
US5676693A (en) | 1992-11-13 | 1997-10-14 | Scimed Life Systems, Inc. | Electrophysiology device |
US6068653A (en) | 1992-11-13 | 2000-05-30 | Scimed Life Systems, Inc. | Electrophysiology catheter device |
DE4338758C2 (en) | 1992-11-13 | 2001-08-09 | Scimed Life Systems Inc | Catheter assembly |
US5334193A (en) | 1992-11-13 | 1994-08-02 | American Cardiac Ablation Co., Inc. | Fluid cooled ablation catheter |
US6923805B1 (en) | 1992-11-13 | 2005-08-02 | Scimed Life Systems, Inc. | Electrophysiology energy treatment devices and methods of use |
US5348554A (en) | 1992-12-01 | 1994-09-20 | Cardiac Pathways Corporation | Catheter for RF ablation with cooled electrode |
US5417699A (en) * | 1992-12-10 | 1995-05-23 | Perclose Incorporated | Device and method for the percutaneous suturing of a vascular puncture site |
US5385146A (en) | 1993-01-08 | 1995-01-31 | Goldreyer; Bruce N. | Orthogonal sensing for use in clinical electrophysiology |
US5409483A (en) | 1993-01-22 | 1995-04-25 | Jeffrey H. Reese | Direct visualization surgical probe |
US5403326A (en) | 1993-02-01 | 1995-04-04 | The Regents Of The University Of California | Method for performing a gastric wrap of the esophagus for use in the treatment of esophageal reflux |
US6161543A (en) | 1993-02-22 | 2000-12-19 | Epicor, Inc. | Methods of epicardial ablation for creating a lesion around the pulmonary veins |
US5797960A (en) | 1993-02-22 | 1998-08-25 | Stevens; John H. | Method and apparatus for thoracoscopic intracardiac procedures |
US5306234A (en) | 1993-03-23 | 1994-04-26 | Johnson W Dudley | Method for closing an atrial appendage |
US5403311A (en) | 1993-03-29 | 1995-04-04 | Boston Scientific Corporation | Electro-coagulation and ablation and other electrotherapeutic treatments of body tissue |
US5985307A (en) | 1993-04-14 | 1999-11-16 | Emory University | Device and method for non-occlusive localized drug delivery |
US5549553A (en) | 1993-04-29 | 1996-08-27 | Scimed Life Systems, Inc. | Dilation ballon for a single operator exchange intravascular catheter or similar device |
US5860974A (en) * | 1993-07-01 | 1999-01-19 | Boston Scientific Corporation | Heart ablation catheter with expandable electrode and method of coupling energy to an electrode on a catheter shaft |
US5571088A (en) | 1993-07-01 | 1996-11-05 | Boston Scientific Corporation | Ablation catheters |
DE69432148T2 (en) | 1993-07-01 | 2003-10-16 | Boston Scient Ltd | CATHETER FOR IMAGE DISPLAY, DISPLAY OF ELECTRICAL SIGNALS AND ABLATION |
US6285898B1 (en) | 1993-07-20 | 2001-09-04 | Biosense, Inc. | Cardiac electromechanics |
US5391199A (en) * | 1993-07-20 | 1995-02-21 | Biosense, Inc. | Apparatus and method for treating cardiac arrhythmias |
US5385148A (en) * | 1993-07-30 | 1995-01-31 | The Regents Of The University Of California | Cardiac imaging and ablation catheter |
AU7404994A (en) | 1993-07-30 | 1995-02-28 | Regents Of The University Of California, The | Endocardial infusion catheter |
US5391182A (en) * | 1993-08-03 | 1995-02-21 | Origin Medsystems, Inc. | Apparatus and method for closing puncture wounds |
US5431649A (en) | 1993-08-27 | 1995-07-11 | Medtronic, Inc. | Method and apparatus for R-F ablation |
US5405376A (en) | 1993-08-27 | 1995-04-11 | Medtronic, Inc. | Method and apparatus for ablation |
US5797903A (en) | 1996-04-12 | 1998-08-25 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures with electrically conductive surfaces |
US5575810A (en) | 1993-10-15 | 1996-11-19 | Ep Technologies, Inc. | Composite structures and methods for ablating tissue to form complex lesion patterns in the treatment of cardiac conditions and the like |
US5462521A (en) | 1993-12-21 | 1995-10-31 | Angeion Corporation | Fluid cooled and perfused tip for a catheter |
US5458612A (en) | 1994-01-06 | 1995-10-17 | Origin Medsystems, Inc. | Prostatic ablation method and apparatus for perineal approach |
US5471515A (en) | 1994-01-28 | 1995-11-28 | California Institute Of Technology | Active pixel sensor with intra-pixel charge transfer |
GB9401913D0 (en) | 1994-02-01 | 1994-03-30 | Watkins David L | Bag sealing apparatus |
US5411016A (en) | 1994-02-22 | 1995-05-02 | Scimed Life Systems, Inc. | Intravascular balloon catheter for use in combination with an angioscope |
US5547455A (en) | 1994-03-30 | 1996-08-20 | Medical Media Systems | Electronically steerable endoscope |
US5653677A (en) | 1994-04-12 | 1997-08-05 | Fuji Photo Optical Co. Ltd | Electronic endoscope apparatus with imaging unit separable therefrom |
US5484412A (en) * | 1994-04-19 | 1996-01-16 | Pierpont; Brien E. | Angioplasty method and means for performing angioplasty |
US5746747A (en) | 1994-05-13 | 1998-05-05 | Mckeating; John A. | Polypectomy instrument |
US5842973A (en) | 1994-05-17 | 1998-12-01 | Bullard; James Roger | Nasal intubation apparatus |
US5575788A (en) | 1994-06-24 | 1996-11-19 | Stuart D. Edwards | Thin layer ablation apparatus |
US5681308A (en) | 1994-06-24 | 1997-10-28 | Stuart D. Edwards | Ablation apparatus for cardiac chambers |
US6056744A (en) | 1994-06-24 | 2000-05-02 | Conway Stuart Medical, Inc. | Sphincter treatment apparatus |
US5505730A (en) | 1994-06-24 | 1996-04-09 | Stuart D. Edwards | Thin layer ablation apparatus |
US5593405A (en) * | 1994-07-16 | 1997-01-14 | Osypka; Peter | Fiber optic endoscope |
US5593424A (en) * | 1994-08-10 | 1997-01-14 | Segmed, Inc. | Apparatus and method for reducing and stabilizing the circumference of a vascular structure |
US5643282A (en) | 1994-08-22 | 1997-07-01 | Kieturakis; Maciej J. | Surgical instrument and method for removing tissue from an endoscopic workspace |
US6558375B1 (en) | 2000-07-14 | 2003-05-06 | Cardiofocus, Inc. | Cardiac ablation instrument |
US8025661B2 (en) | 1994-09-09 | 2011-09-27 | Cardiofocus, Inc. | Coaxial catheter instruments for ablation with radiant energy |
US6579285B2 (en) | 1994-09-09 | 2003-06-17 | Cardiofocus, Inc. | Photoablation with infrared radiation |
US6168591B1 (en) * | 1994-09-09 | 2001-01-02 | Cardiofocus, Inc. | Guide for penetrating phototherapy |
US6270492B1 (en) | 1994-09-09 | 2001-08-07 | Cardiofocus, Inc. | Phototherapeutic apparatus with diffusive tip assembly |
US6572609B1 (en) | 1999-07-14 | 2003-06-03 | Cardiofocus, Inc. | Phototherapeutic waveguide apparatus |
US6676656B2 (en) * | 1994-09-09 | 2004-01-13 | Cardiofocus, Inc. | Surgical ablation with radiant energy |
US6102905A (en) | 1994-09-09 | 2000-08-15 | Cardiofocus, Inc. | Phototherapy device including housing for an optical element and method of making |
US6423055B1 (en) | 1999-07-14 | 2002-07-23 | Cardiofocus, Inc. | Phototherapeutic wave guide apparatus |
US5591119A (en) * | 1994-12-07 | 1997-01-07 | Adair; Edwin L. | Sterile surgical coupler and drape |
US5498230A (en) * | 1994-10-03 | 1996-03-12 | Adair; Edwin L. | Sterile connector and video camera cover for sterile endoscope |
US5792045A (en) | 1994-10-03 | 1998-08-11 | Adair; Edwin L. | Sterile surgical coupler and drape |
US5879366A (en) * | 1996-12-20 | 1999-03-09 | W.L. Gore & Associates, Inc. | Self-expanding defect closure device and method of making and using |
AU1426995A (en) | 1995-01-19 | 1996-08-07 | Ten Cate, F.J. | Local delivery and monitoring of drugs |
US5665062A (en) | 1995-01-23 | 1997-09-09 | Houser; Russell A. | Atherectomy catheter and RF cutting method |
US6690963B2 (en) | 1995-01-24 | 2004-02-10 | Biosense, Inc. | System for determining the location and orientation of an invasive medical instrument |
US6409722B1 (en) | 1998-07-07 | 2002-06-25 | Medtronic, Inc. | Apparatus and method for creating, maintaining, and controlling a virtual electrode used for the ablation of tissue |
US5897553A (en) | 1995-11-02 | 1999-04-27 | Medtronic, Inc. | Ball point fluid-assisted electrocautery device |
US6063081A (en) | 1995-02-22 | 2000-05-16 | Medtronic, Inc. | Fluid-assisted electrocautery device |
US6132438A (en) * | 1995-06-07 | 2000-10-17 | Ep Technologies, Inc. | Devices for installing stasis reducing means in body tissue |
US5709224A (en) * | 1995-06-07 | 1998-01-20 | Radiotherapeutics Corporation | Method and device for permanent vessel occlusion |
CA2224975A1 (en) * | 1995-06-23 | 1997-01-09 | Gyrus Medical Limited | An electrosurgical instrument |
US5713907A (en) * | 1995-07-20 | 1998-02-03 | Endotex Interventional Systems, Inc. | Apparatus and method for dilating a lumen and for inserting an intraluminal graft |
JP3134726B2 (en) | 1995-08-14 | 2001-02-13 | 富士写真光機株式会社 | Ultrasound diagnostic equipment |
JP3151153B2 (en) | 1995-09-20 | 2001-04-03 | 定夫 尾股 | Frequency deviation detection circuit and measuring instrument using the same |
US5716321A (en) * | 1995-10-10 | 1998-02-10 | Conceptus, Inc. | Method for maintaining separation between a falloposcope and a tubal wall |
US6726677B1 (en) | 1995-10-13 | 2004-04-27 | Transvascular, Inc. | Stabilized tissue penetrating catheters |
US5860953A (en) | 1995-11-21 | 1999-01-19 | Catheter Imaging Systems, Inc. | Steerable catheter having disposable module and sterilizable handle and method of connecting same |
AU690862B2 (en) | 1995-12-04 | 1998-04-30 | Target Therapeutics, Inc. | Fibered micro vaso-occlusive devices |
US5846239A (en) | 1996-04-12 | 1998-12-08 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using segmented porous electrode structures |
US5749889A (en) | 1996-02-13 | 1998-05-12 | Imagyn Medical, Inc. | Method and apparatus for performing biopsy |
US6266551B1 (en) | 1996-02-15 | 2001-07-24 | Biosense, Inc. | Catheter calibration and usage monitoring system |
US5725523A (en) * | 1996-03-29 | 1998-03-10 | Mueller; Richard L. | Lateral-and posterior-aspect method and apparatus for laser-assisted transmyocardial revascularization and other surgical applications |
US6063077A (en) | 1996-04-08 | 2000-05-16 | Cardima, Inc. | Linear ablation device and assembly |
US6549800B1 (en) | 1996-04-25 | 2003-04-15 | Johns Hopkins Unversity School Of Medicine | Methods for in vivo magnetic resonance imaging |
US5713867A (en) | 1996-04-29 | 1998-02-03 | Medtronic, Inc. | Introducer system having kink resistant splittable sheath |
US6270477B1 (en) | 1996-05-20 | 2001-08-07 | Percusurge, Inc. | Catheter for emboli containment |
US5754313A (en) | 1996-07-17 | 1998-05-19 | Welch Allyn, Inc. | Imager assembly |
US5662671A (en) | 1996-07-17 | 1997-09-02 | Embol-X, Inc. | Atherectomy device having trapping and excising means for removal of plaque from the aorta and other arteries |
US6905505B2 (en) | 1996-07-26 | 2005-06-14 | Kensey Nash Corporation | System and method of use for agent delivery and revascularizing of grafts and vessels |
US6830577B2 (en) | 1996-07-26 | 2004-12-14 | Kensey Nash Corporation | System and method of use for treating occluded vessels and diseased tissue |
US5826576A (en) | 1996-08-08 | 1998-10-27 | Medtronic, Inc. | Electrophysiology catheter with multifunction wire and method for making |
US6126682A (en) | 1996-08-13 | 2000-10-03 | Oratec Interventions, Inc. | Method for treating annular fissures in intervertebral discs |
US5827175A (en) | 1996-09-30 | 1998-10-27 | Fuji Photo Optical Co., Ltd. | Endoscopically inserting ultrasound probe |
WO1998015226A1 (en) | 1996-10-08 | 1998-04-16 | Hitachi Medical Corporation | Method and apparatus for forming and displaying image from a plurality of sectional images |
US6464697B1 (en) | 1998-02-19 | 2002-10-15 | Curon Medical, Inc. | Stomach and adjoining tissue regions in the esophagus |
US6805128B1 (en) | 1996-10-22 | 2004-10-19 | Epicor Medical, Inc. | Apparatus and method for ablating tissue |
US6237605B1 (en) | 1996-10-22 | 2001-05-29 | Epicor, Inc. | Methods of epicardial ablation |
US6719755B2 (en) | 1996-10-22 | 2004-04-13 | Epicor Medical, Inc. | Methods and devices for ablation |
US6840936B2 (en) | 1996-10-22 | 2005-01-11 | Epicor Medical, Inc. | Methods and devices for ablation |
US6311692B1 (en) | 1996-10-22 | 2001-11-06 | Epicor, Inc. | Apparatus and method for diagnosis and therapy of electrophysiological disease |
US7052493B2 (en) | 1996-10-22 | 2006-05-30 | Epicor Medical, Inc. | Methods and devices for ablation |
US5904651A (en) | 1996-10-28 | 1999-05-18 | Ep Technologies, Inc. | Systems and methods for visualizing tissue during diagnostic or therapeutic procedures |
US5752518A (en) | 1996-10-28 | 1998-05-19 | Ep Technologies, Inc. | Systems and methods for visualizing interior regions of the body |
US5848969A (en) | 1996-10-28 | 1998-12-15 | Ep Technologies, Inc. | Systems and methods for visualizing interior tissue regions using expandable imaging structures |
US5722403A (en) * | 1996-10-28 | 1998-03-03 | Ep Technologies, Inc. | Systems and methods using a porous electrode for ablating and visualizing interior tissue regions |
US5908445A (en) | 1996-10-28 | 1999-06-01 | Ep Technologies, Inc. | Systems for visualizing interior tissue regions including an actuator to move imaging element |
US5827268A (en) | 1996-10-30 | 1998-10-27 | Hearten Medical, Inc. | Device for the treatment of patent ductus arteriosus and method of using the device |
US6002955A (en) | 1996-11-08 | 1999-12-14 | Medtronic, Inc. | Stabilized electrophysiology catheter and method for use |
US5749890A (en) | 1996-12-03 | 1998-05-12 | Shaknovich; Alexander | Method and system for stent placement in ostial lesions |
US6071279A (en) | 1996-12-19 | 2000-06-06 | Ep Technologies, Inc. | Branched structures for supporting multiple electrode elements |
US6007521A (en) | 1997-01-07 | 1999-12-28 | Bidwell; Robert E. | Drainage catheter system |
US6013024A (en) | 1997-01-20 | 2000-01-11 | Suzuki Motor Corporation | Hybrid operation system |
JP3134287B2 (en) | 1997-01-30 | 2001-02-13 | 株式会社ニッショー | Catheter assembly for endocardial suture surgery |
US5968053A (en) | 1997-01-31 | 1999-10-19 | Cardiac Assist Technologies, Inc. | Method and apparatus for implanting a graft in a vessel of a patient |
US6295989B1 (en) | 1997-02-06 | 2001-10-02 | Arteria Medical Science, Inc. | ICA angioplasty with cerebral protection |
US20020026145A1 (en) * | 1997-03-06 | 2002-02-28 | Bagaoisan Celso J. | Method and apparatus for emboli containment |
US6086534A (en) | 1997-03-07 | 2000-07-11 | Cardiogenesis Corporation | Apparatus and method of myocardial revascularization using ultrasonic pulse-echo distance ranging |
WO1998040014A1 (en) | 1997-03-10 | 1998-09-17 | Robin Medical Inc. | Method and apparatus for the assessment and display of variability in mechanical activity of the heart, and enhancement of ultrasound contrast imaging by variability analysis |
US6086582A (en) | 1997-03-13 | 2000-07-11 | Altman; Peter A. | Cardiac drug delivery system |
US5897487A (en) | 1997-04-15 | 1999-04-27 | Asahi Kogaku Kogyo Kabushiki Kaisha | Front end hood for endoscope |
US6081740A (en) | 1997-04-23 | 2000-06-27 | Accumed International, Inc. | Method and apparatus for imaging and sampling diseased tissue |
US5971983A (en) | 1997-05-09 | 1999-10-26 | The Regents Of The University Of California | Tissue ablation device and method of use |
US6012457A (en) | 1997-07-08 | 2000-01-11 | The Regents Of The University Of California | Device and method for forming a circumferential conduction block in a pulmonary vein |
US6024740A (en) * | 1997-07-08 | 2000-02-15 | The Regents Of The University Of California | Circumferential ablation device assembly |
US6251109B1 (en) | 1997-06-27 | 2001-06-26 | Daig Corporation | Process and device for the treatment of atrial arrhythmia |
US6500174B1 (en) | 1997-07-08 | 2002-12-31 | Atrionix, Inc. | Circumferential ablation device assembly and methods of use and manufacture providing an ablative circumferential band along an expandable member |
US6514249B1 (en) * | 1997-07-08 | 2003-02-04 | Atrionix, Inc. | Positioning system and method for orienting an ablation element within a pulmonary vein ostium |
US6997925B2 (en) | 1997-07-08 | 2006-02-14 | Atrionx, Inc. | Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall |
US6164283A (en) | 1997-07-08 | 2000-12-26 | The Regents Of The University Of California | Device and method for forming a circumferential conduction block in a pulmonary vein |
EP0893137B1 (en) | 1997-07-22 | 2004-03-31 | Terumo Kabushiki Kaisha | Assembly for an indwelling catheter and method of making it |
DE69829974T8 (en) | 1997-07-24 | 2006-04-27 | Rex Medical, L.P. | DEVICE FOR BRUSH SURGERY |
US5902299A (en) * | 1997-07-29 | 1999-05-11 | Jayaraman; Swaminathan | Cryotherapy method for reducing tissue injury after balloon angioplasty or stent implantation |
US6459919B1 (en) | 1997-08-26 | 2002-10-01 | Color Kinetics, Incorporated | Precision illumination methods and systems |
US6043839A (en) | 1997-10-06 | 2000-03-28 | Adair; Edwin L. | Reduced area imaging devices |
US5929901A (en) | 1997-10-06 | 1999-07-27 | Adair; Edwin L. | Reduced area imaging devices incorporated within surgical instruments |
US6401719B1 (en) | 1997-09-11 | 2002-06-11 | Vnus Medical Technologies, Inc. | Method of ligating hollow anatomical structures |
US6179832B1 (en) * | 1997-09-11 | 2001-01-30 | Vnus Medical Technologies, Inc. | Expandable catheter having two sets of electrodes |
US6086528A (en) | 1997-09-11 | 2000-07-11 | Adair; Edwin L. | Surgical devices with removable imaging capability and methods of employing same |
US6211904B1 (en) | 1997-09-11 | 2001-04-03 | Edwin L. Adair | Surgical devices incorporating reduced area imaging devices |
US5916147A (en) | 1997-09-22 | 1999-06-29 | Boury; Harb N. | Selectively manipulable catheter |
US7030904B2 (en) * | 1997-10-06 | 2006-04-18 | Micro-Medical Devices, Inc. | Reduced area imaging device incorporated within wireless endoscopic devices |
US6310642B1 (en) | 1997-11-24 | 2001-10-30 | Micro-Medical Devices, Inc. | Reduced area imaging devices incorporated within surgical instruments |
US5986693A (en) | 1997-10-06 | 1999-11-16 | Adair; Edwin L. | Reduced area imaging devices incorporated within surgical instruments |
US6240312B1 (en) | 1997-10-23 | 2001-05-29 | Robert R. Alfano | Remote-controllable, micro-scale device for use in in vivo medical diagnosis and/or treatment |
US6749617B1 (en) | 1997-11-04 | 2004-06-15 | Scimed Life Systems, Inc. | Catheter and implants for the delivery of therapeutic agents to tissues |
US6234995B1 (en) | 1998-11-12 | 2001-05-22 | Advanced Interventional Technologies, Inc. | Apparatus and method for selectively isolating a proximal anastomosis site from blood in an aorta |
US6982740B2 (en) * | 1997-11-24 | 2006-01-03 | Micro-Medical Devices, Inc. | Reduced area imaging devices utilizing selected charge integration periods |
US5997571A (en) | 1997-12-17 | 1999-12-07 | Cardiofocus, Inc. | Non-occluding phototherapy probe stabilizers |
US6632171B2 (en) | 1997-12-22 | 2003-10-14 | Given Imaging Ltd. | Method for in vivo delivery of autonomous capsule |
US6071302A (en) | 1997-12-31 | 2000-06-06 | Cardiofocus, Inc. | Phototherapeutic apparatus for wide-angle diffusion |
US6423058B1 (en) | 1998-02-19 | 2002-07-23 | Curon Medical, Inc. | Assemblies to visualize and treat sphincters and adjoining tissue regions |
US6142993A (en) | 1998-02-27 | 2000-11-07 | Ep Technologies, Inc. | Collapsible spline structure using a balloon as an expanding actuator |
US5997509A (en) | 1998-03-06 | 1999-12-07 | Cornell Research Foundation, Inc. | Minimally invasive gene therapy delivery device and method |
US6115626A (en) | 1998-03-26 | 2000-09-05 | Scimed Life Systems, Inc. | Systems and methods using annotated images for controlling the use of diagnostic or therapeutic instruments in instruments in interior body regions |
US6383195B1 (en) | 1998-04-13 | 2002-05-07 | Endoline, Inc. | Laparoscopic specimen removal apparatus |
JPH11299725A (en) | 1998-04-21 | 1999-11-02 | Olympus Optical Co Ltd | Hood for endoscope |
US6522930B1 (en) | 1998-05-06 | 2003-02-18 | Atrionix, Inc. | Irrigated ablation device assembly |
US6908474B2 (en) * | 1998-05-13 | 2005-06-21 | Gore Enterprise Holdings, Inc. | Apparatus and methods for reducing embolization during treatment of carotid artery disease |
EP1079724A1 (en) | 1998-05-13 | 2001-03-07 | Inbae Yoon | Penetrating endoscope and endoscopic surgical instrument with cmos image sensor and display |
US7263397B2 (en) | 1998-06-30 | 2007-08-28 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Method and apparatus for catheter navigation and location and mapping in the heart |
US6494902B2 (en) | 1998-07-07 | 2002-12-17 | Medtronic, Inc. | Method for creating a virtual electrode for the ablation of tissue and for selected protection of tissue during an ablation |
US6706039B2 (en) | 1998-07-07 | 2004-03-16 | Medtronic, Inc. | Method and apparatus for creating a bi-polar virtual electrode used for the ablation of tissue |
US6315777B1 (en) | 1998-07-07 | 2001-11-13 | Medtronic, Inc. | Method and apparatus for creating a virtual electrode used for the ablation of tissue |
US6537272B2 (en) | 1998-07-07 | 2003-03-25 | Medtronic, Inc. | Apparatus and method for creating, maintaining, and controlling a virtual electrode used for the ablation of tissue |
US6238393B1 (en) | 1998-07-07 | 2001-05-29 | Medtronic, Inc. | Method and apparatus for creating a bi-polar virtual electrode used for the ablation of tissue |
US6562020B1 (en) | 1998-07-15 | 2003-05-13 | Corazon Technologies, Inc. | Kits for use in the treatment of vascular calcified lesions |
US6527979B2 (en) | 1999-08-27 | 2003-03-04 | Corazon Technologies, Inc. | Catheter systems and methods for their use in the treatment of calcified vascular occlusions |
US6290689B1 (en) | 1999-10-22 | 2001-09-18 | Corazón Technologies, Inc. | Catheter devices and methods for their use in the treatment of calcified vascular occlusions |
EP1100392B1 (en) | 1998-07-15 | 2009-02-25 | Corazon Technologies, Inc. | devices for reducing the mineral content of vascular calcified lesions |
US6394096B1 (en) | 1998-07-15 | 2002-05-28 | Corazon Technologies, Inc. | Method and apparatus for treatment of cardiovascular tissue mineralization |
US6352503B1 (en) | 1998-07-17 | 2002-03-05 | Olympus Optical Co., Ltd. | Endoscopic surgery apparatus |
US6112123A (en) | 1998-07-28 | 2000-08-29 | Endonetics, Inc. | Device and method for ablation of tissue |
JP2003524443A (en) | 1998-08-02 | 2003-08-19 | スーパー ディメンション リミテッド | Medical guidance device |
US6139508A (en) | 1998-08-04 | 2000-10-31 | Endonetics, Inc. | Articulated medical device |
US6461327B1 (en) | 1998-08-07 | 2002-10-08 | Embol-X, Inc. | Atrial isolator and method of use |
US6099498A (en) | 1998-09-02 | 2000-08-08 | Embol-X, Inc | Cardioplegia access view probe and methods of use |
US6123703A (en) | 1998-09-19 | 2000-09-26 | Tu; Lily Chen | Ablation catheter and methods for treating tissues |
US6178346B1 (en) | 1998-10-23 | 2001-01-23 | David C. Amundson | Infrared endoscopic imaging in a liquid with suspended particles: method and apparatus |
US6123718A (en) | 1998-11-02 | 2000-09-26 | Polymerex Medical Corp. | Balloon catheter |
US6152144A (en) | 1998-11-06 | 2000-11-28 | Appriva Medical, Inc. | Method and device for left atrial appendage occlusion |
US7128073B1 (en) | 1998-11-06 | 2006-10-31 | Ev3 Endovascular, Inc. | Method and device for left atrial appendage occlusion |
US6896690B1 (en) | 2000-01-27 | 2005-05-24 | Viacor, Inc. | Cardiac valve procedure methods and devices |
US6396873B1 (en) | 1999-02-25 | 2002-05-28 | Envision Advanced Medical Systems | Optical device |
JP3596340B2 (en) | 1999-03-18 | 2004-12-02 | 株式会社日立製作所 | Surgical insertion device |
US6325797B1 (en) | 1999-04-05 | 2001-12-04 | Medtronic, Inc. | Ablation catheter and method for isolating a pulmonary vein |
US20040044350A1 (en) | 1999-04-09 | 2004-03-04 | Evalve, Inc. | Steerable access sheath and methods of use |
US6167297A (en) | 1999-05-05 | 2000-12-26 | Benaron; David A. | Detecting, localizing, and targeting internal sites in vivo using optical contrast agents |
JP3490933B2 (en) | 1999-06-07 | 2004-01-26 | ペンタックス株式会社 | Swallowable endoscope device |
US6890329B2 (en) | 1999-06-15 | 2005-05-10 | Cryocath Technologies Inc. | Defined deflection structure |
US6306132B1 (en) | 1999-06-17 | 2001-10-23 | Vivant Medical | Modular biopsy and microwave ablation needle delivery apparatus adapted to in situ assembly and method of use |
AUPQ115499A0 (en) * | 1999-06-24 | 1999-07-15 | Colocare Holdings Pty Limited | Colostomy pump device |
US6626899B2 (en) | 1999-06-25 | 2003-09-30 | Nidus Medical, Llc | Apparatus and methods for treating tissue |
US7128708B2 (en) | 2002-06-13 | 2006-10-31 | Usgi Medical Inc. | Shape lockable apparatus and method for advancing an instrument through unsupported anatomy |
US7637905B2 (en) | 2003-01-15 | 2009-12-29 | Usgi Medical, Inc. | Endoluminal tool deployment system |
US20050222558A1 (en) | 1999-07-14 | 2005-10-06 | Cardiofocus, Inc. | Methods of cardiac ablation employing a deflectable sheath catheter |
US8540704B2 (en) | 1999-07-14 | 2013-09-24 | Cardiofocus, Inc. | Guided cardiac ablation catheters |
US20050234436A1 (en) | 1999-07-14 | 2005-10-20 | Cardiofocus, Inc. | Methods of cardiac ablation in the vicinity of the right inferior pulmonary vein |
US20050234437A1 (en) | 1999-07-14 | 2005-10-20 | Cardiofocus, Inc. | Deflectable sheath catheters with out-of-plane bent tip |
US7935108B2 (en) | 1999-07-14 | 2011-05-03 | Cardiofocus, Inc. | Deflectable sheath catheters |
WO2001005306A1 (en) | 1999-07-19 | 2001-01-25 | Epicor, Inc. | Apparatus and method for ablating tissue |
US6235044B1 (en) * | 1999-08-04 | 2001-05-22 | Scimed Life Systems, Inc. | Percutaneous catheter and guidewire for filtering during ablation of mycardial or vascular tissue |
US20040167503A1 (en) | 1999-08-25 | 2004-08-26 | Cardiofocus, Inc. | Malleable surgical ablation instruments |
US20040147911A1 (en) | 1999-08-25 | 2004-07-29 | Cardiofocus, Inc. | Surgical ablation instruments for forming an encircling lesion |
US6755811B1 (en) | 1999-08-25 | 2004-06-29 | Corazon Technologies, Inc. | Methods and devices for reducing the mineral content of a region of non-intimal vascular tissue |
US6702780B1 (en) | 1999-09-08 | 2004-03-09 | Super Dimension Ltd. | Steering configuration for catheter with rigid distal device |
US6315778B1 (en) | 1999-09-10 | 2001-11-13 | C. R. Bard, Inc. | Apparatus for creating a continuous annular lesion |
US6458151B1 (en) | 1999-09-10 | 2002-10-01 | Frank S. Saltiel | Ostial stent positioning device and method |
US6423051B1 (en) | 1999-09-16 | 2002-07-23 | Aaron V. Kaplan | Methods and apparatus for pericardial access |
US6231561B1 (en) | 1999-09-20 | 2001-05-15 | Appriva Medical, Inc. | Method and apparatus for closing a body lumen |
US6385476B1 (en) | 1999-09-21 | 2002-05-07 | Biosense, Inc. | Method and apparatus for intracardially surveying a condition of a chamber of a heart |
US6915154B1 (en) | 1999-09-24 | 2005-07-05 | National Research Council Of Canada | Method and apparatus for performing intra-operative angiography |
US6485489B2 (en) | 1999-10-02 | 2002-11-26 | Quantum Cor, Inc. | Catheter system for repairing a mitral valve annulus |
US6488671B1 (en) | 1999-10-22 | 2002-12-03 | Corazon Technologies, Inc. | Methods for enhancing fluid flow through an obstructed vascular site, and systems and kits for use in practicing the same |
US6533767B2 (en) | 2000-03-20 | 2003-03-18 | Corazon Technologies, Inc. | Methods for enhancing fluid flow through an obstructed vascular site, and systems and kits for use in practicing the same |
US6780151B2 (en) | 1999-10-26 | 2004-08-24 | Acmi Corporation | Flexible ureteropyeloscope |
US7758521B2 (en) | 1999-10-29 | 2010-07-20 | Medtronic, Inc. | Methods and systems for accessing the pericardial space |
US6613062B1 (en) | 1999-10-29 | 2003-09-02 | Medtronic, Inc. | Method and apparatus for providing intra-pericardial access |
US6529756B1 (en) | 1999-11-22 | 2003-03-04 | Scimed Life Systems, Inc. | Apparatus for mapping and coagulating soft tissue in or around body orifices |
US6711444B2 (en) * | 1999-11-22 | 2004-03-23 | Scimed Life Systems, Inc. | Methods of deploying helical diagnostic and therapeutic element supporting structures within the body |
US6626855B1 (en) | 1999-11-26 | 2003-09-30 | Therus Corpoation | Controlled high efficiency lesion formation using high intensity ultrasound |
US6156350A (en) | 1999-12-02 | 2000-12-05 | Corazon Technologies, Inc. | Methods and kits for use in preventing restenosis |
CA2395924C (en) | 2000-01-06 | 2008-11-18 | Raymond L. Bedell | Steerable fiberoptic epidural balloon catheter and scope |
WO2001053871A2 (en) | 2000-01-21 | 2001-07-26 | Molecular Diagnostics, Inc. | In-vivo tissue inspection and sampling |
US6892091B1 (en) | 2000-02-18 | 2005-05-10 | Biosense, Inc. | Catheter, method and apparatus for generating an electrical map of a chamber of the heart |
US6478769B1 (en) | 2000-02-22 | 2002-11-12 | The Board Of Trustees Of The University Of Arkansas | Anatomical fluid evacuation apparatus and method |
US6436118B1 (en) | 2000-02-25 | 2002-08-20 | General Surgical Innovations, Inc. | IMA dissection device |
US6544195B2 (en) | 2000-03-04 | 2003-04-08 | Joseph F. Wilson | Tissue of foreign body extractor |
US6565526B2 (en) | 2000-03-09 | 2003-05-20 | The Regents Of The University Of California | Bistable microvalve and microcatheter system |
JP2001258822A (en) | 2000-03-14 | 2001-09-25 | Olympus Optical Co Ltd | Endoscope |
US6770070B1 (en) | 2000-03-17 | 2004-08-03 | Rita Medical Systems, Inc. | Lung treatment apparatus and method |
US6440061B1 (en) | 2000-03-24 | 2002-08-27 | Donald E. Wenner | Laparoscopic instrument system for real-time biliary exploration and stone removal |
US6743227B2 (en) | 2000-03-31 | 2004-06-01 | Medtronic, Inc. | Intraluminal visualization system with deflectable mechanism |
US6858005B2 (en) * | 2000-04-03 | 2005-02-22 | Neo Guide Systems, Inc. | Tendon-driven endoscope and methods of insertion |
IL135571A0 (en) | 2000-04-10 | 2001-05-20 | Doron Adler | Minimal invasive surgery imaging system |
US6692430B2 (en) | 2000-04-10 | 2004-02-17 | C2Cure Inc. | Intra vascular imaging apparatus |
US7056294B2 (en) * | 2000-04-13 | 2006-06-06 | Ev3 Sunnyvale, Inc | Method and apparatus for accessing the left atrial appendage |
US6650923B1 (en) | 2000-04-13 | 2003-11-18 | Ev3 Sunnyvale, Inc. | Method for accessing the left atrium of the heart by locating the fossa ovalis |
US6558382B2 (en) | 2000-04-27 | 2003-05-06 | Medtronic, Inc. | Suction stabilized epicardial ablation devices |
US6375654B1 (en) | 2000-05-19 | 2002-04-23 | Cardiofocus, Inc. | Catheter system with working portion radially expandable upon rotation |
JP4674975B2 (en) | 2000-05-26 | 2011-04-20 | オリンパス株式会社 | Endoscope hood |
US6532380B1 (en) | 2000-06-30 | 2003-03-11 | Cedars Sinai Medical Center | Image guidance for coronary stent deployment |
US6811562B1 (en) | 2000-07-31 | 2004-11-02 | Epicor, Inc. | Procedures for photodynamic cardiac ablation therapy and devices for those procedures |
US7399271B2 (en) | 2004-01-09 | 2008-07-15 | Cardiokinetix, Inc. | Ventricular partitioning device |
US6538375B1 (en) | 2000-08-17 | 2003-03-25 | General Electric Company | Oled fiber light source |
JP2002058642A (en) | 2000-08-21 | 2002-02-26 | Asahi Optical Co Ltd | Imaging element for electronic endoscope |
US6605055B1 (en) | 2000-09-13 | 2003-08-12 | Cardiofocus, Inc. | Balloon catheter with irrigation sheath |
JP3533163B2 (en) | 2000-09-18 | 2004-05-31 | ペンタックス株式会社 | Endoscope tip |
JP2002177198A (en) | 2000-10-02 | 2002-06-25 | Olympus Optical Co Ltd | Endoscope |
US6926669B1 (en) | 2000-10-10 | 2005-08-09 | Medtronic, Inc. | Heart wall ablation/mapping catheter and method |
US6659981B2 (en) | 2000-12-08 | 2003-12-09 | Medtronic, Inc. | Medical device delivery catheter with distal locator |
US6623452B2 (en) | 2000-12-19 | 2003-09-23 | Scimed Life Systems, Inc. | Drug delivery catheter having a highly compliant balloon with infusion holes |
EP1345542B1 (en) * | 2000-12-20 | 2011-02-23 | Fox Hollow Technologies, Inc. | Debulking catheter |
US6540733B2 (en) | 2000-12-29 | 2003-04-01 | Corazon Technologies, Inc. | Proton generating catheters and methods for their use in enhancing fluid flow through a vascular site occupied by a calcified vascular occlusion |
US6958069B2 (en) | 2001-01-17 | 2005-10-25 | Mark LoGuidice | Instruments and methods for use in laparoscopic surgery |
US6837901B2 (en) | 2001-04-27 | 2005-01-04 | Intek Technology L.L.C. | Methods for delivering, repositioning and/or retrieving self-expanding stents |
US7422579B2 (en) | 2001-05-01 | 2008-09-09 | St. Jude Medical Cardiology Divison, Inc. | Emboli protection devices and related methods of use |
EP1385439A1 (en) | 2001-05-10 | 2004-02-04 | Rita Medical Systems, Inc. | Rf tissue ablation apparatus and method |
US6635070B2 (en) | 2001-05-21 | 2003-10-21 | Bacchus Vascular, Inc. | Apparatus and methods for capturing particulate material within blood vessels |
US6771996B2 (en) | 2001-05-24 | 2004-08-03 | Cardiac Pacemakers, Inc. | Ablation and high-resolution mapping catheter system for pulmonary vein foci elimination |
JP3722729B2 (en) * | 2001-06-04 | 2005-11-30 | オリンパス株式会社 | Endoscope treatment device |
US6693821B2 (en) | 2001-06-28 | 2004-02-17 | Sharp Laboratories Of America, Inc. | Low cross-talk electrically programmable resistance cross point memory |
US6773402B2 (en) | 2001-07-10 | 2004-08-10 | Biosense, Inc. | Location sensing with real-time ultrasound imaging |
US6796963B2 (en) | 2001-07-10 | 2004-09-28 | Myocardial Therapeutics, Inc. | Flexible tissue injection catheters with controlled depth penetration |
US6916286B2 (en) | 2001-08-09 | 2005-07-12 | Smith & Nephew, Inc. | Endoscope with imaging probe |
US7218344B2 (en) * | 2001-08-15 | 2007-05-15 | Sony Corporation | System and method for efficiently performing a white balance operation |
US20030036698A1 (en) * | 2001-08-16 | 2003-02-20 | Robert Kohler | Interventional diagnostic catheter and a method for using a catheter to access artificial cardiac shunts |
WO2003020179A1 (en) | 2001-08-31 | 2003-03-13 | Mitral Interventions | Apparatus for valve repair |
CA2460501A1 (en) | 2001-09-28 | 2003-04-10 | Institut De Cardiologie De Montreal | Method for identification and visualization of atrial tissue |
US6862468B2 (en) | 2001-09-28 | 2005-03-01 | Scimed Life Systems, Inc. | Systems and methods for magnetic resonance imaging elastography |
US8308710B2 (en) | 2001-10-12 | 2012-11-13 | Applied Medical Resources Corporation | High flow-low pressure irrigation system |
AU2002365095A1 (en) | 2001-11-09 | 2003-07-09 | Cardio-Optics, Inc. | Coronary sinus access catheter with forward-imaging |
IL162420A0 (en) | 2001-12-11 | 2005-11-20 | C2Cure Inc | Apparatus, method and system for intravascular ph otographic imaging |
ATE459388T1 (en) | 2001-12-26 | 2010-03-15 | Univ Yale | VASCULAR SHUNTING DEVICE |
US7717899B2 (en) | 2002-01-28 | 2010-05-18 | Cardiac Pacemakers, Inc. | Inner and outer telescoping catheter delivery system |
JP3826045B2 (en) | 2002-02-07 | 2006-09-27 | オリンパス株式会社 | Endoscope hood |
US6974464B2 (en) | 2002-02-28 | 2005-12-13 | 3F Therapeutics, Inc. | Supportless atrioventricular heart valve and minimally invasive delivery systems thereof |
EP1511426A2 (en) | 2002-02-28 | 2005-03-09 | Medtronic Inc. | Improved system and method of positioning implantable medical devices |
US20060146172A1 (en) | 2002-03-18 | 2006-07-06 | Jacobsen Stephen C | Miniaturized utility device having integrated optical capabilities |
US6712798B2 (en) | 2002-03-18 | 2004-03-30 | Corazon Technologies, Inc. | Multilumen catheters and methods for their use |
US7787939B2 (en) | 2002-03-18 | 2010-08-31 | Sterling Lc | Miniaturized imaging device including utility aperture and SSID |
US7591780B2 (en) * | 2002-03-18 | 2009-09-22 | Sterling Lc | Miniaturized imaging device with integrated circuit connector system |
US6866651B2 (en) | 2002-03-20 | 2005-03-15 | Corazon Technologies, Inc. | Methods and devices for the in situ dissolution of renal calculi |
US6932809B2 (en) | 2002-05-14 | 2005-08-23 | Cardiofocus, Inc. | Safety shut-off device for laser surgical instruments employing blackbody emitters |
US7118566B2 (en) | 2002-05-16 | 2006-10-10 | Medtronic, Inc. | Device and method for needle-less interstitial injection of fluid for ablation of cardiac tissue |
DE10392670B4 (en) | 2002-05-16 | 2012-10-11 | C2Cure Inc. | Miniature camera head |
US8956280B2 (en) | 2002-05-30 | 2015-02-17 | Intuitive Surgical Operations, Inc. | Apparatus and methods for placing leads using direct visualization |
US6979290B2 (en) | 2002-05-30 | 2005-12-27 | The Board Of Trustees Of The Leland Stanford Junior University | Apparatus and methods for coronary sinus access |
AU2003247526A1 (en) | 2002-06-12 | 2003-12-31 | Mitral Interventions, Inc. | Method and apparatus for tissue connection |
AU2003245507A1 (en) * | 2002-06-13 | 2003-12-31 | Guided Delivery Systems, Inc. | Devices and methods for heart valve repair |
US6679836B2 (en) * | 2002-06-21 | 2004-01-20 | Scimed Life Systems, Inc. | Universal programmable guide catheter |
US20030236493A1 (en) | 2002-06-25 | 2003-12-25 | Medamicus, Inc. | Articulating handle for a deflectable catheter and method therefor |
US7421295B2 (en) | 2002-07-19 | 2008-09-02 | Oscor Inc. | Implantable cardiac lead having removable fluid delivery port |
US6887237B2 (en) | 2002-07-22 | 2005-05-03 | Medtronic, Inc. | Method for treating tissue with a wet electrode and apparatus for using same |
US7314446B2 (en) | 2002-07-22 | 2008-01-01 | Ep Medsystems, Inc. | Method and apparatus for time gating of medical images |
US7001329B2 (en) | 2002-07-23 | 2006-02-21 | Pentax Corporation | Capsule endoscope guidance system, capsule endoscope holder, and capsule endoscope |
US6701581B2 (en) | 2002-08-10 | 2004-03-09 | Epicor Industries, Inc. | Clamp retention device |
US6863668B2 (en) | 2002-08-16 | 2005-03-08 | Edwards Lifesciences Corporation | Articulation mechanism for medical devices |
DE60336914D1 (en) | 2002-08-24 | 2011-06-09 | Atrial Fibrillation Division Inc | METHOD AND DEVICE FOR LOCATING THE FOSSA OVALIS AND PERFORMING A TRANSSEPTAL PUNCTURE |
US6755790B2 (en) | 2002-10-14 | 2004-06-29 | Medtronic, Inc. | Transseptal access tissue thickness sensing dilator devices and methods for fabricating and using same |
WO2004041183A2 (en) | 2002-11-01 | 2004-05-21 | The Regents Of The University Of California | Methods of treating pulmonary fibrotic disorders |
US6899672B2 (en) | 2002-11-08 | 2005-05-31 | Scimed Life Systems, Inc. | Endoscopic imaging system including removable deflection device |
US20050020914A1 (en) * | 2002-11-12 | 2005-01-27 | David Amundson | Coronary sinus access catheter with forward-imaging |
AU2002952663A0 (en) | 2002-11-14 | 2002-11-28 | Western Sydney Area Health Service | An intramural needle-tipped surgical device |
US7697972B2 (en) | 2002-11-19 | 2010-04-13 | Medtronic Navigation, Inc. | Navigation system for cardiac therapies |
US20040158289A1 (en) | 2002-11-30 | 2004-08-12 | Girouard Steven D. | Method and apparatus for cell and electrical therapy of living tissue |
JP4391765B2 (en) | 2002-12-02 | 2009-12-24 | オリンパス株式会社 | Endoscopic mucosal resection tool |
US20040138707A1 (en) | 2003-01-14 | 2004-07-15 | Greenhalgh E. Skott | Anchor removable from a substrate |
US20040249367A1 (en) | 2003-01-15 | 2004-12-09 | Usgi Medical Corp. | Endoluminal tool deployment system |
US6984232B2 (en) * | 2003-01-17 | 2006-01-10 | St. Jude Medical, Daig Division, Inc. | Ablation catheter assembly having a virtual electrode comprising portholes |
US7323001B2 (en) * | 2003-01-30 | 2008-01-29 | Ev3 Inc. | Embolic filters with controlled pore size |
US8021359B2 (en) * | 2003-02-13 | 2011-09-20 | Coaptus Medical Corporation | Transseptal closure of a patent foramen ovale and other cardiac defects |
JP4887138B2 (en) | 2003-02-21 | 2012-02-29 | エレクトロ−キャット リミテッド ライアビリティ カンパニー | System and method for measuring cross-sectional area and pressure gradient of an organ having a lumen |
US7004925B2 (en) | 2003-02-25 | 2006-02-28 | Cleveland Clinic Foundation | Apparatus and method for auto-retroperfusion of a coronary vein |
US7473237B2 (en) | 2003-02-25 | 2009-01-06 | The Cleveland Clinic Foundation | Apparatus for auto-retroperfusion of a coronary vein |
US7658747B2 (en) | 2003-03-12 | 2010-02-09 | Nmt Medical, Inc. | Medical device for manipulation of a medical implant |
US20050015048A1 (en) * | 2003-03-12 | 2005-01-20 | Chiu Jessica G. | Infusion treatment agents, catheters, filter devices, and occlusion devices, and use thereof |
US20070055142A1 (en) | 2003-03-14 | 2007-03-08 | Webler William E | Method and apparatus for image guided position tracking during percutaneous procedures |
AU2004221408A1 (en) | 2003-03-18 | 2004-09-30 | Catharos Medical Systems, Inc. | Methods and devices for retrieval of a medical agent from a physiological efferent fluid collection site |
US7300429B2 (en) | 2003-03-18 | 2007-11-27 | Catharos Medical Systems, Inc. | Methods and devices for retrieval of a medical agent from a physiological efferent fluid collection site |
US7293562B2 (en) * | 2003-03-27 | 2007-11-13 | Cierra, Inc. | Energy based devices and methods for treatment of anatomic tissue defects |
US6939348B2 (en) | 2003-03-27 | 2005-09-06 | Cierra, Inc. | Energy based devices and methods for treatment of patent foramen ovale |
US20040199052A1 (en) | 2003-04-01 | 2004-10-07 | Scimed Life Systems, Inc. | Endoscopic imaging system |
US7569952B1 (en) | 2003-04-18 | 2009-08-04 | Ferro Solutions, Inc. | High efficiency, inductive vibration energy harvester |
US7112195B2 (en) | 2003-04-21 | 2006-09-26 | Cynosure, Inc. | Esophageal lesion treatment method |
US20040215180A1 (en) | 2003-04-25 | 2004-10-28 | Medtronic, Inc. | Ablation of stomach lining to treat obesity |
US20040220471A1 (en) | 2003-04-29 | 2004-11-04 | Yitzhack Schwartz | Method and device for transseptal facilitation using location system |
US6994094B2 (en) * | 2003-04-29 | 2006-02-07 | Biosense, Inc. | Method and device for transseptal facilitation based on injury patterns |
US7604649B2 (en) | 2003-04-29 | 2009-10-20 | Rex Medical, L.P. | Distal protection device |
JP4414682B2 (en) | 2003-06-06 | 2010-02-10 | オリンパス株式会社 | Ultrasound endoscope device |
US20040260182A1 (en) | 2003-06-23 | 2004-12-23 | Zuluaga Andres F. | Intraluminal spectroscope with wall contacting probe |
JP4398184B2 (en) | 2003-06-24 | 2010-01-13 | オリンパス株式会社 | Endoscope |
CA2532449C (en) | 2003-07-17 | 2013-04-16 | Corazon Technologies, Inc. | Devices and methods for percutaneously treating aortic valve stenosis |
US20050027163A1 (en) * | 2003-07-29 | 2005-02-03 | Scimed Life Systems, Inc. | Vision catheter |
US7534204B2 (en) | 2003-09-03 | 2009-05-19 | Guided Delivery Systems, Inc. | Cardiac visualization devices and methods |
CA2538476A1 (en) | 2003-09-11 | 2005-04-21 | Nmt Medical, Inc. | Devices, systems, and methods for suturing tissue |
US7569052B2 (en) | 2003-09-12 | 2009-08-04 | Boston Scientific Scimed, Inc. | Ablation catheter with tissue protecting assembly |
US20050059862A1 (en) | 2003-09-12 | 2005-03-17 | Scimed Life Systems, Inc. | Cannula with integrated imaging and optical capability |
US7736362B2 (en) | 2003-09-15 | 2010-06-15 | Boston Scientific Scimed, Inc. | Catheter balloons |
US8172747B2 (en) | 2003-09-25 | 2012-05-08 | Hansen Medical, Inc. | Balloon visualization for traversing a tissue wall |
US7435248B2 (en) | 2003-09-26 | 2008-10-14 | Boston Scientific Scimed, Inc. | Medical probes for creating and diagnosing circumferential lesions within or around the ostium of a vessel |
US7207989B2 (en) | 2003-10-27 | 2007-04-24 | Biosense Webster, Inc. | Method for ablating with needle electrode |
US20050096502A1 (en) | 2003-10-29 | 2005-05-05 | Khalili Theodore M. | Robotic surgical device |
WO2005044124A1 (en) * | 2003-10-30 | 2005-05-19 | Medical Cv, Inc. | Apparatus and method for laser treatment |
WO2005046487A1 (en) | 2003-11-06 | 2005-05-26 | Nmt Medical, Inc. | Transseptal puncture apparatus |
WO2005048813A2 (en) | 2003-11-12 | 2005-06-02 | The Board Of Trustees Of The Leland Stanford Junior University | Devices and methods for three-dimensional body images |
WO2005053517A1 (en) | 2003-12-01 | 2005-06-16 | Olympus Corporation | Endoscope system |
US20050177182A1 (en) | 2003-12-04 | 2005-08-11 | Van Der Burg Erik J. | System and method for delivering a left atrial appendage containment device |
US8057420B2 (en) | 2003-12-09 | 2011-11-15 | Gi Dynamics, Inc. | Gastrointestinal implant with drawstring |
US20050165456A1 (en) | 2003-12-19 | 2005-07-28 | Brian Mann | Digital electrode for cardiac rhythm management |
JP3823321B2 (en) | 2003-12-25 | 2006-09-20 | 有限会社エスアールジェイ | Balloon control device |
US7179224B2 (en) | 2003-12-30 | 2007-02-20 | Cardiothoracic Systems, Inc. | Organ manipulator and positioner and methods of using the same |
US8652089B2 (en) | 2004-01-19 | 2014-02-18 | Arthrex, Inc. | System for distending body tissue cavities by continuous flow irrigation |
US20050228452A1 (en) | 2004-02-11 | 2005-10-13 | Mourlas Nicholas J | Steerable catheters and methods for using them |
US20050197623A1 (en) | 2004-02-17 | 2005-09-08 | Leeflang Stephen A. | Variable steerable catheters and methods for using them |
US8052636B2 (en) * | 2004-03-05 | 2011-11-08 | Hansen Medical, Inc. | Robotic catheter system and methods |
WO2005087128A1 (en) | 2004-03-05 | 2005-09-22 | Hansen Medical, Inc. | Robotic catheter system |
US7632265B2 (en) * | 2004-05-28 | 2009-12-15 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Radio frequency ablation servo catheter and method |
US7537580B2 (en) | 2004-06-23 | 2009-05-26 | Boston Scientific Scimed, Inc. | Intravascular dilatation infusion catheter |
US7678081B2 (en) * | 2004-07-12 | 2010-03-16 | Pacesetter, Inc. | Methods and devices for transseptal access |
US8005537B2 (en) * | 2004-07-19 | 2011-08-23 | Hansen Medical, Inc. | Robotically controlled intravascular tissue injection system |
WO2006014993A1 (en) | 2004-07-27 | 2006-02-09 | Medeikon Corporation | Device for tissue characterization |
US7300397B2 (en) * | 2004-07-29 | 2007-11-27 | C2C Cure, Inc. | Endoscope electronics assembly |
WO2006024015A1 (en) | 2004-08-24 | 2006-03-02 | The General Hospital Corporation | Method and apparatus for imaging of vessel segments |
WO2006026712A2 (en) | 2004-08-31 | 2006-03-09 | Fox Chase Cancer Center | Yeast/bacterial two-hybrid system and methods of use thereof |
US7753906B2 (en) * | 2004-09-14 | 2010-07-13 | Richard Esposito | Catheter having anchoring and stabilizing devices |
US20060069303A1 (en) | 2004-09-30 | 2006-03-30 | Couvillon Lucien A Jr | Endoscopic apparatus with integrated hemostasis device |
US20060069313A1 (en) | 2004-09-30 | 2006-03-30 | Couvillon Lucien A Jr | Medical devices with light emitting regions |
US8029470B2 (en) | 2004-09-30 | 2011-10-04 | Pacesetter, Inc. | Transmembrane access systems and methods |
US7875049B2 (en) | 2004-10-04 | 2011-01-25 | Medtronic, Inc. | Expandable guide sheath with steerable backbone and methods for making and using them |
US20060089637A1 (en) | 2004-10-14 | 2006-04-27 | Werneth Randell L | Ablation catheter |
US20060122587A1 (en) | 2004-11-17 | 2006-06-08 | Shiva Sharareh | Apparatus for real time evaluation of tissue ablation |
US20060149129A1 (en) | 2005-01-05 | 2006-07-06 | Watts H D | Catheter with multiple visual elements |
US7883503B2 (en) | 2005-01-26 | 2011-02-08 | Kalser Gary | Illuminating balloon catheter and method for using the catheter |
US7860556B2 (en) | 2005-02-02 | 2010-12-28 | Voyage Medical, Inc. | Tissue imaging and extraction systems |
US7918787B2 (en) * | 2005-02-02 | 2011-04-05 | Voyage Medical, Inc. | Tissue visualization and manipulation systems |
US8078266B2 (en) | 2005-10-25 | 2011-12-13 | Voyage Medical, Inc. | Flow reduction hood systems |
US9510732B2 (en) | 2005-10-25 | 2016-12-06 | Intuitive Surgical Operations, Inc. | Methods and apparatus for efficient purging |
US11478152B2 (en) | 2005-02-02 | 2022-10-25 | Intuitive Surgical Operations, Inc. | Electrophysiology mapping and visualization system |
US7930016B1 (en) | 2005-02-02 | 2011-04-19 | Voyage Medical, Inc. | Tissue closure system |
EP1866019B1 (en) | 2005-02-22 | 2017-10-25 | Cardiofocus, Inc. | Deflectable sheath catheters |
US7708748B2 (en) | 2005-03-30 | 2010-05-04 | Ethicon Endo-Surgery, Inc. | Anastomosis device |
US20060258909A1 (en) | 2005-04-08 | 2006-11-16 | Usgi Medical, Inc. | Methods and apparatus for maintaining sterility during transluminal procedures |
WO2006122061A1 (en) * | 2005-05-06 | 2006-11-16 | Acumen Medical, Inc. | Complexly shaped steerable catheters and methods for making and using them |
JP2007000463A (en) * | 2005-06-24 | 2007-01-11 | Terumo Corp | Catheter assembly |
WO2007011689A2 (en) | 2005-07-15 | 2007-01-25 | The Brigham And Women's Hospital, Inc. | Sterile access conduit |
WO2007014313A2 (en) | 2005-07-26 | 2007-02-01 | Precision Thoracic Corporation | Minimally invasive methods and apparatus |
US7765014B2 (en) | 2005-08-16 | 2010-07-27 | Medtronic, Inc. | Apparatus and methods for delivering transvenous leads |
US7575569B2 (en) | 2005-08-16 | 2009-08-18 | Medtronic, Inc. | Apparatus and methods for delivering stem cells and other agents into cardiac tissue |
US7416552B2 (en) | 2005-08-22 | 2008-08-26 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Multipolar, multi-lumen, virtual-electrode catheter with at least one surface electrode and method for ablation |
US8355801B2 (en) | 2005-09-26 | 2013-01-15 | Biosense Webster, Inc. | System and method for measuring esophagus proximity |
US20070083099A1 (en) | 2005-09-29 | 2007-04-12 | Henderson Stephen W | Path related three dimensional medical imaging |
US20070106214A1 (en) | 2005-10-17 | 2007-05-10 | Coaptus Medical Corporation | Systems and methods for securing cardiovascular tissue, including via asymmetric inflatable members |
US8221310B2 (en) | 2005-10-25 | 2012-07-17 | Voyage Medical, Inc. | Tissue visualization device and method variations |
US7918793B2 (en) | 2005-10-28 | 2011-04-05 | Biosense Webster, Inc. | Synchronization of ultrasound imaging data with electrical mapping |
US20070106113A1 (en) | 2005-11-07 | 2007-05-10 | Biagio Ravo | Combination endoscopic operative delivery system |
US20070135826A1 (en) | 2005-12-01 | 2007-06-14 | Steve Zaver | Method and apparatus for delivering an implant without bias to a left atrial appendage |
EP1955643B1 (en) | 2005-12-01 | 2019-01-09 | Olympus Corporation | Guiding long medical member and long medical device |
US8303505B2 (en) | 2005-12-02 | 2012-11-06 | Abbott Cardiovascular Systems Inc. | Methods and apparatuses for image guided medical procedures |
JP4855482B2 (en) | 2005-12-30 | 2012-01-18 | シー・アール・バード・インコーポレーテッド | Method and apparatus for exfoliating heart tissue |
EP1980194B1 (en) | 2006-01-06 | 2013-05-08 | Olympus Medical Systems Corp. | Trans-natural opening based or transcutaneous medical system |
WO2007106081A2 (en) | 2006-03-10 | 2007-09-20 | The Board Of Trustees Of The Leland Stanford Junior University | Percutaneous access and visualization of the spine |
WO2007133845A2 (en) | 2006-03-20 | 2007-11-22 | Medtronic, Inc. | Removable valves and methods for making them |
US20070239010A1 (en) | 2006-04-11 | 2007-10-11 | Medtronic Vascular, Inc. | Catheters with Laterally Deployable Elements and Linear Ultrasound Arrays |
WO2007134258A2 (en) | 2006-05-12 | 2007-11-22 | Vytronus, Inc. | Device for ablating body tissue |
US20070270639A1 (en) | 2006-05-17 | 2007-11-22 | Long Gary L | Medical instrument having a catheter and having a catheter accessory device and method for using |
US7615067B2 (en) | 2006-06-05 | 2009-11-10 | Cambridge Endoscopic Devices, Inc. | Surgical instrument |
US20070299456A1 (en) | 2006-06-06 | 2007-12-27 | Teague James A | Light responsive medical retrieval devices |
US9220402B2 (en) | 2006-06-07 | 2015-12-29 | Intuitive Surgical Operations, Inc. | Visualization and treatment via percutaneous methods and devices |
US9055906B2 (en) | 2006-06-14 | 2015-06-16 | Intuitive Surgical Operations, Inc. | In-vivo visualization systems |
US8048072B2 (en) * | 2006-07-12 | 2011-11-01 | Les Hospitaux Universitaires de Geneva | Medical device for tissue ablation |
WO2008014425A2 (en) * | 2006-07-26 | 2008-01-31 | Hansen Medical, Inc. | Systems for performing minimally invasive surgical operations |
US20080033241A1 (en) * | 2006-08-01 | 2008-02-07 | Ruey-Feng Peh | Left atrial appendage closure |
WO2008015625A2 (en) | 2006-08-02 | 2008-02-07 | Koninklijke Philips Electronics N.V. | 3d segmentation by voxel classification based on intensity histogram thresholding initialised by k-means clustering |
US8409172B2 (en) | 2006-08-03 | 2013-04-02 | Hansen Medical, Inc. | Systems and methods for performing minimally invasive procedures |
WO2008024261A2 (en) | 2006-08-23 | 2008-02-28 | Cardio-Optics, Inc | Image-guided therapy of the fossa ovalis and septal defects |
WO2008027371A2 (en) | 2006-08-29 | 2008-03-06 | Surmodics, Inc. | Low profile bioactive agent delivery device |
JP2010502313A (en) * | 2006-09-01 | 2010-01-28 | ボエッジ メディカル, インコーポレイテッド | Method and apparatus for the treatment of atrial fibrillation |
EP2056707A4 (en) | 2006-09-01 | 2010-05-26 | Nidus Medical Llc | Tissue visualization device having multi-segmented frame |
US10004388B2 (en) | 2006-09-01 | 2018-06-26 | Intuitive Surgical Operations, Inc. | Coronary sinus cannulation |
US20080097476A1 (en) | 2006-09-01 | 2008-04-24 | Voyage Medical, Inc. | Precision control systems for tissue visualization and manipulation assemblies |
US10335131B2 (en) | 2006-10-23 | 2019-07-02 | Intuitive Surgical Operations, Inc. | Methods for preventing tissue migration |
US8337518B2 (en) | 2006-12-20 | 2012-12-25 | Onset Medical Corporation | Expandable trans-septal sheath |
US8131350B2 (en) | 2006-12-21 | 2012-03-06 | Voyage Medical, Inc. | Stabilization of visualization catheters |
US8758229B2 (en) | 2006-12-21 | 2014-06-24 | Intuitive Surgical Operations, Inc. | Axial visualization systems |
US8657805B2 (en) | 2007-05-08 | 2014-02-25 | Intuitive Surgical Operations, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
EP3025636B1 (en) * | 2007-05-11 | 2017-11-01 | Intuitive Surgical Operations, Inc. | Visual electrode ablation systems |
US20080287805A1 (en) | 2007-05-16 | 2008-11-20 | General Electric Company | System and method to guide an instrument through an imaged subject |
US8527032B2 (en) | 2007-05-16 | 2013-09-03 | General Electric Company | Imaging system and method of delivery of an instrument to an imaged subject |
WO2008154000A1 (en) | 2007-06-08 | 2008-12-18 | Cynosure, Inc. | Thermal surgery safety suite |
US20090030276A1 (en) * | 2007-07-27 | 2009-01-29 | Voyage Medical, Inc. | Tissue visualization catheter with imaging systems integration |
US20090048480A1 (en) | 2007-08-13 | 2009-02-19 | Paracor Medical, Inc. | Cardiac harness delivery device |
US20090076476A1 (en) | 2007-08-15 | 2009-03-19 | Hansen Medical, Inc. | Systems and methods employing force sensing for mapping intra-body tissue |
AU2008293549A1 (en) | 2007-08-27 | 2009-03-05 | Spine View, Inc. | Balloon cannula system for accessing and visualizing spine and related methods |
US20090062790A1 (en) | 2007-08-31 | 2009-03-05 | Voyage Medical, Inc. | Direct visualization bipolar ablation systems |
US8235985B2 (en) | 2007-08-31 | 2012-08-07 | Voyage Medical, Inc. | Visualization and ablation system variations |
US20090125022A1 (en) | 2007-11-12 | 2009-05-14 | Voyage Medical, Inc. | Tissue visualization and ablation systems |
US20090143640A1 (en) | 2007-11-26 | 2009-06-04 | Voyage Medical, Inc. | Combination imaging and treatment assemblies |
WO2009092021A1 (en) | 2008-01-17 | 2009-07-23 | Nidus Medical, Llc | Epicardial access and treatment systems |
US8858609B2 (en) | 2008-02-07 | 2014-10-14 | Intuitive Surgical Operations, Inc. | Stent delivery under direct visualization |
WO2009112262A2 (en) | 2008-03-12 | 2009-09-17 | Afreeze Gmbh | Handle for an ablation device |
US7534294B1 (en) | 2008-04-14 | 2009-05-19 | Xerox Corporation | Quinacridone nanoscale pigment particles and methods of making same |
US8494608B2 (en) | 2008-04-18 | 2013-07-23 | Medtronic, Inc. | Method and apparatus for mapping a structure |
US8532734B2 (en) | 2008-04-18 | 2013-09-10 | Regents Of The University Of Minnesota | Method and apparatus for mapping a structure |
US9125562B2 (en) | 2009-07-01 | 2015-09-08 | Avinger, Inc. | Catheter-based off-axis optical coherence tomography imaging system |
US20090326572A1 (en) | 2008-06-27 | 2009-12-31 | Ruey-Feng Peh | Apparatus and methods for rapid tissue crossing |
US9101735B2 (en) * | 2008-07-07 | 2015-08-11 | Intuitive Surgical Operations, Inc. | Catheter control systems |
US8333012B2 (en) | 2008-10-10 | 2012-12-18 | Voyage Medical, Inc. | Method of forming electrode placement and connection systems |
US9468364B2 (en) | 2008-11-14 | 2016-10-18 | Intuitive Surgical Operations, Inc. | Intravascular catheter with hood and image processing systems |
US8468637B2 (en) | 2009-02-06 | 2013-06-25 | Endoclear Llc | Mechanically-actuated endotracheal tube cleaning device |
JP5219228B2 (en) | 2009-06-09 | 2013-06-26 | 独立行政法人産業技術総合研究所 | Vascular function testing device |
US8906007B2 (en) | 2009-09-28 | 2014-12-09 | Covidien Lp | Electrosurgical devices, directional reflector assemblies coupleable thereto, and electrosurgical systems including same |
US20110144576A1 (en) | 2009-12-14 | 2011-06-16 | Voyage Medical, Inc. | Catheter orientation control system mechanisms |
US9204858B2 (en) | 2010-02-05 | 2015-12-08 | Ultrasonix Medical Corporation | Ultrasound pulse-wave doppler measurement of blood flow velocity and/or turbulence |
US8694071B2 (en) * | 2010-02-12 | 2014-04-08 | Intuitive Surgical Operations, Inc. | Image stabilization techniques and methods |
US9814522B2 (en) | 2010-04-06 | 2017-11-14 | Intuitive Surgical Operations, Inc. | Apparatus and methods for ablation efficacy |
US9254090B2 (en) | 2010-10-22 | 2016-02-09 | Intuitive Surgical Operations, Inc. | Tissue contrast imaging systems |
KR101323330B1 (en) | 2011-12-28 | 2013-10-29 | 삼성메디슨 주식회사 | Ultrasound system and method for providing vector doppler image based on decision data |
US10537310B2 (en) | 2012-04-18 | 2020-01-21 | Hitachi, Ltd. | Ultrasound image capture device and ultrasound image capture method |
JP6152218B2 (en) | 2014-02-28 | 2017-06-21 | 株式会社日立製作所 | Ultrasonic imaging apparatus and method |
EP3125809B1 (en) | 2014-03-28 | 2020-09-09 | Intuitive Surgical Operations, Inc. | Surgical system with haptic feedback based upon quantitative three-dimensional imaging |
-
2007
- 2007-08-31 US US11/848,429 patent/US20080097476A1/en not_active Abandoned
-
2009
- 2009-05-12 US US12/464,800 patent/US10070772B2/en active Active
-
2018
- 2018-08-30 US US16/117,993 patent/US11779195B2/en active Active
-
2023
- 2023-09-06 US US18/462,175 patent/US20240032776A1/en active Pending
Patent Citations (32)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3874388A (en) * | 1973-02-12 | 1975-04-01 | Ochsner Med Found Alton | Shunt defect closure system |
US4681093A (en) * | 1982-12-13 | 1987-07-21 | Sumitomo Electric Industries, Ltd. | Endoscope |
US20040117032A1 (en) * | 1993-02-22 | 2004-06-17 | Roth Alex T. | Devices for less-invasive intracardiac interventions |
US5575756A (en) * | 1993-08-16 | 1996-11-19 | Olympus Optical Co., Ltd. | Endoscope apparatus |
US6129724A (en) * | 1993-10-14 | 2000-10-10 | Ep Technologies, Inc. | Systems and methods for forming elongated lesion patterns in body tissue using straight or curvilinear electrode elements |
US5695448A (en) * | 1994-08-29 | 1997-12-09 | Olympus Optical Co., Ltd. | Endoscopic sheath |
US5515853A (en) * | 1995-03-28 | 1996-05-14 | Sonometrics Corporation | Three-dimensional digital ultrasound tracking system |
US6428536B2 (en) * | 1996-01-19 | 2002-08-06 | Ep Technologies, Inc. | Expandable-collapsible electrode structures made of electrically conductive material |
US5895417A (en) * | 1996-03-06 | 1999-04-20 | Cardiac Pathways Corporation | Deflectable loop design for a linear lesion ablation apparatus |
US6258083B1 (en) * | 1996-03-29 | 2001-07-10 | Eclipse Surgical Technologies, Inc. | Viewing surgical scope for minimally invasive procedures |
US5944690A (en) * | 1997-03-17 | 1999-08-31 | C.R. Bard, Inc. | Slidable control mechanism for steerable catheter |
US5941845A (en) * | 1997-08-05 | 1999-08-24 | Irvine Biomedical, Inc. | Catheter having multiple-needle electrode and methods thereof |
US6475223B1 (en) * | 1997-08-29 | 2002-11-05 | Stereotaxis, Inc. | Method and apparatus for magnetically controlling motion direction of a mechanically pushed catheter |
US20020087166A1 (en) * | 1998-02-24 | 2002-07-04 | Brock David L. | Flexible instrument |
US20020087169A1 (en) * | 1998-02-24 | 2002-07-04 | Brock David L. | Flexible instrument |
US7090683B2 (en) * | 1998-02-24 | 2006-08-15 | Hansen Medical, Inc. | Flexible instrument |
US6482162B1 (en) * | 1998-12-08 | 2002-11-19 | Scimed Life Systems, Inc. | Loop imaging catheter |
US6587709B2 (en) * | 2001-03-28 | 2003-07-01 | Koninklijke Philips Electronics N.V. | Method of and imaging ultrasound system for determining the position of a catheter |
US20030171741A1 (en) * | 2001-11-14 | 2003-09-11 | Latis, Inc. | Catheters for clot removal |
US7019610B2 (en) * | 2002-01-23 | 2006-03-28 | Stereotaxis, Inc. | Magnetic navigation system |
US20050182465A1 (en) * | 2004-02-12 | 2005-08-18 | Ness Gregory O. | Instruments and methods for accessing an anatomic space |
US20060084945A1 (en) * | 2004-03-05 | 2006-04-20 | Hansen Medical, Inc. | Instrument driver for robotic catheter system |
US20060030844A1 (en) * | 2004-08-04 | 2006-02-09 | Knight Bradley P | Transparent electrode for the radiofrequency ablation of tissue |
US20080015569A1 (en) * | 2005-02-02 | 2008-01-17 | Voyage Medical, Inc. | Methods and apparatus for treatment of atrial fibrillation |
US20070293724A1 (en) * | 2005-02-02 | 2007-12-20 | Voyage Medical, Inc. | Visualization apparatus for transseptal access |
US20080009747A1 (en) * | 2005-02-02 | 2008-01-10 | Voyage Medical, Inc. | Transmural subsurface interrogation and ablation |
US20060184048A1 (en) * | 2005-02-02 | 2006-08-17 | Vahid Saadat | Tissue visualization and manipulation system |
US20080015445A1 (en) * | 2005-02-02 | 2008-01-17 | Voyage Medical, Inc. | Tissue visualization device and method variations |
US20060271032A1 (en) * | 2005-05-26 | 2006-11-30 | Chin Albert K | Ablation instruments and methods for performing abalation |
US20080033290A1 (en) * | 2005-10-25 | 2008-02-07 | Voyage Medical, Inc. | Delivery of biological compounds to ischemic and/or infarcted tissue |
US20070270686A1 (en) * | 2006-05-03 | 2007-11-22 | Ritter Rogers C | Apparatus and methods for using inertial sensing to navigate a medical device |
US20080275300A1 (en) * | 2007-04-27 | 2008-11-06 | Voyage Medical, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
Cited By (126)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20100211057A1 (en) * | 1995-01-23 | 2010-08-19 | Cardio Vascular Technologies, Inc. a California Corporation | Tissue heating device and rf heating method with tissue attachment feature |
US20080108876A1 (en) * | 2001-09-06 | 2008-05-08 | Houser Russell A | Superelastic/Shape Memory Tissue Stabilizers and Surgical Instruments |
US7930016B1 (en) | 2005-02-02 | 2011-04-19 | Voyage Medical, Inc. | Tissue closure system |
US10064540B2 (en) | 2005-02-02 | 2018-09-04 | Intuitive Surgical Operations, Inc. | Visualization apparatus for transseptal access |
US10368729B2 (en) | 2005-02-02 | 2019-08-06 | Intuitive Surgical Operations, Inc. | Methods and apparatus for efficient purging |
US20080009747A1 (en) * | 2005-02-02 | 2008-01-10 | Voyage Medical, Inc. | Transmural subsurface interrogation and ablation |
US8814845B2 (en) | 2005-02-02 | 2014-08-26 | Intuitive Surgical Operations, Inc. | Delivery of biological compounds to ischemic and/or infarcted tissue |
US10463237B2 (en) | 2005-02-02 | 2019-11-05 | Intuitive Surgical Operations, Inc. | Delivery of biological compounds to ischemic and/or infarcted tissue |
US8934962B2 (en) | 2005-02-02 | 2015-01-13 | Intuitive Surgical Operations, Inc. | Electrophysiology mapping and visualization system |
US11889982B2 (en) | 2005-02-02 | 2024-02-06 | Intuitive Surgical Operations, Inc. | Electrophysiology mapping and visualization system |
US10772492B2 (en) * | 2005-02-02 | 2020-09-15 | Intuitive Surgical Operations, Inc. | Methods and apparatus for efficient purging |
US8050746B2 (en) | 2005-02-02 | 2011-11-01 | Voyage Medical, Inc. | Tissue visualization device and method variations |
US9526401B2 (en) | 2005-02-02 | 2016-12-27 | Intuitive Surgical Operations, Inc. | Flow reduction hood systems |
US11478152B2 (en) | 2005-02-02 | 2022-10-25 | Intuitive Surgical Operations, Inc. | Electrophysiology mapping and visualization system |
US11819190B2 (en) | 2005-02-02 | 2023-11-21 | Intuitive Surgical Operations, Inc. | Methods and apparatus for efficient purging |
US7860556B2 (en) | 2005-02-02 | 2010-12-28 | Voyage Medical, Inc. | Tissue imaging and extraction systems |
US7860555B2 (en) | 2005-02-02 | 2010-12-28 | Voyage Medical, Inc. | Tissue visualization and manipulation system |
US7918787B2 (en) | 2005-02-02 | 2011-04-05 | Voyage Medical, Inc. | Tissue visualization and manipulation systems |
US10278588B2 (en) | 2005-02-02 | 2019-05-07 | Intuitive Surgical Operations, Inc. | Electrophysiology mapping and visualization system |
US11406250B2 (en) | 2005-02-02 | 2022-08-09 | Intuitive Surgical Operations, Inc. | Methods and apparatus for treatment of atrial fibrillation |
US20060184048A1 (en) * | 2005-02-02 | 2006-08-17 | Vahid Saadat | Tissue visualization and manipulation system |
US8419613B2 (en) | 2005-02-02 | 2013-04-16 | Voyage Medical, Inc. | Tissue visualization device |
US9332893B2 (en) | 2005-02-02 | 2016-05-10 | Intuitive Surgical Operations, Inc. | Delivery of biological compounds to ischemic and/or infarcted tissue |
US8417321B2 (en) | 2005-02-02 | 2013-04-09 | Voyage Medical, Inc | Flow reduction hood systems |
US8221310B2 (en) | 2005-10-25 | 2012-07-17 | Voyage Medical, Inc. | Tissue visualization device and method variations |
US9192287B2 (en) | 2005-10-25 | 2015-11-24 | Intuitive Surgical Operations, Inc. | Tissue visualization device and method variations |
US8137333B2 (en) | 2005-10-25 | 2012-03-20 | Voyage Medical, Inc. | Delivery of biological compounds to ischemic and/or infarcted tissue |
US8078266B2 (en) | 2005-10-25 | 2011-12-13 | Voyage Medical, Inc. | Flow reduction hood systems |
US20080033290A1 (en) * | 2005-10-25 | 2008-02-07 | Voyage Medical, Inc. | Delivery of biological compounds to ischemic and/or infarcted tissue |
US9510732B2 (en) | 2005-10-25 | 2016-12-06 | Intuitive Surgical Operations, Inc. | Methods and apparatus for efficient purging |
US20070288078A1 (en) * | 2006-03-17 | 2007-12-13 | Steve Livneh | Apparatus and method for skin tightening and corrective forming |
US20150250382A1 (en) * | 2006-06-14 | 2015-09-10 | Intuitive Surgical Operations, Inc. | In-Vivo Visualization Systems |
US11882996B2 (en) | 2006-06-14 | 2024-01-30 | Intuitive Surgical Operations, Inc. | In-vivo visualization systems |
US9055906B2 (en) * | 2006-06-14 | 2015-06-16 | Intuitive Surgical Operations, Inc. | In-vivo visualization systems |
US20100292558A1 (en) * | 2006-06-14 | 2010-11-18 | Voyage Medical, Inc. | In-vivo visualization systems |
US10470643B2 (en) * | 2006-06-14 | 2019-11-12 | Intuitive Surgical Operations, Inc. | In-vivo visualization systems |
US11779195B2 (en) | 2006-09-01 | 2023-10-10 | Intuitive Surgical Operations, Inc. | Precision control systems for tissue visualization and manipulation assemblies |
US10004388B2 (en) | 2006-09-01 | 2018-06-26 | Intuitive Surgical Operations, Inc. | Coronary sinus cannulation |
US10070772B2 (en) | 2006-09-01 | 2018-09-11 | Intuitive Surgical Operations, Inc. | Precision control systems for tissue visualization and manipulation assemblies |
US11337594B2 (en) | 2006-09-01 | 2022-05-24 | Intuitive Surgical Operations, Inc. | Coronary sinus cannulation |
US20080058590A1 (en) * | 2006-09-01 | 2008-03-06 | Nidus Medical, Llc. | Tissue visualization device having multi-segmented frame |
US10335131B2 (en) | 2006-10-23 | 2019-07-02 | Intuitive Surgical Operations, Inc. | Methods for preventing tissue migration |
US20080214889A1 (en) * | 2006-10-23 | 2008-09-04 | Voyage Medical, Inc. | Methods and apparatus for preventing tissue migration |
US11369356B2 (en) | 2006-10-23 | 2022-06-28 | Intuitive Surgical Operations, Inc. | Methods and apparatus for preventing tissue migration |
US10441136B2 (en) | 2006-12-18 | 2019-10-15 | Intuitive Surgical Operations, Inc. | Systems and methods for unobstructed visualization and ablation |
US10390685B2 (en) | 2006-12-21 | 2019-08-27 | Intuitive Surgical Operations, Inc. | Off-axis visualization systems |
US8758229B2 (en) | 2006-12-21 | 2014-06-24 | Intuitive Surgical Operations, Inc. | Axial visualization systems |
US8131350B2 (en) | 2006-12-21 | 2012-03-06 | Voyage Medical, Inc. | Stabilization of visualization catheters |
US11559188B2 (en) | 2006-12-21 | 2023-01-24 | Intuitive Surgical Operations, Inc. | Off-axis visualization systems |
US9226648B2 (en) | 2006-12-21 | 2016-01-05 | Intuitive Surgical Operations, Inc. | Off-axis visualization systems |
US9155452B2 (en) | 2007-04-27 | 2015-10-13 | Intuitive Surgical Operations, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
US8657805B2 (en) | 2007-05-08 | 2014-02-25 | Intuitive Surgical Operations, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
US10092172B2 (en) | 2007-05-08 | 2018-10-09 | Intuitive Surgical Operations, Inc. | Complex shape steerable tissue visualization and manipulation catheter |
US20090227999A1 (en) * | 2007-05-11 | 2009-09-10 | Voyage Medical, Inc. | Visual electrode ablation systems |
US9155587B2 (en) | 2007-05-11 | 2015-10-13 | Intuitive Surgical Operations, Inc. | Visual electrode ablation systems |
US10624695B2 (en) | 2007-05-11 | 2020-04-21 | Intuitive Surgical Operations, Inc. | Visual electrode ablation systems |
US8709008B2 (en) | 2007-05-11 | 2014-04-29 | Intuitive Surgical Operations, Inc. | Visual electrode ablation systems |
US8235985B2 (en) | 2007-08-31 | 2012-08-07 | Voyage Medical, Inc. | Visualization and ablation system variations |
US10058380B2 (en) | 2007-10-05 | 2018-08-28 | Maquet Cordiovascular Llc | Devices and methods for minimally-invasive surgical procedures |
US10993766B2 (en) | 2007-10-05 | 2021-05-04 | Maquet Cardiovascular Llc | Devices and methods for minimally-invasive surgical procedures |
US10278849B2 (en) | 2008-02-07 | 2019-05-07 | Intuitive Surgical Operations, Inc. | Stent delivery under direct visualization |
US11241325B2 (en) | 2008-02-07 | 2022-02-08 | Intuitive Surgical Operations, Inc. | Stent delivery under direct visualization |
US8858609B2 (en) | 2008-02-07 | 2014-10-14 | Intuitive Surgical Operations, Inc. | Stent delivery under direct visualization |
US9101735B2 (en) | 2008-07-07 | 2015-08-11 | Intuitive Surgical Operations, Inc. | Catheter control systems |
US11350815B2 (en) | 2008-07-07 | 2022-06-07 | Intuitive Surgical Operations, Inc. | Catheter control systems |
US20100049099A1 (en) * | 2008-07-18 | 2010-02-25 | Vytronus, Inc. | Method and system for positioning an energy source |
US8333012B2 (en) | 2008-10-10 | 2012-12-18 | Voyage Medical, Inc. | Method of forming electrode placement and connection systems |
US10111705B2 (en) | 2008-10-10 | 2018-10-30 | Intuitive Surgical Operations, Inc. | Integral electrode placement and connection systems |
US20100094081A1 (en) * | 2008-10-10 | 2010-04-15 | Voyage Medical, Inc. | Electrode placement and connection systems |
US20100262140A1 (en) * | 2008-10-10 | 2010-10-14 | Voyage Medical, Inc. | Integral electrode placement and connection systems |
US11950838B2 (en) | 2008-10-10 | 2024-04-09 | Intuitive Surgical Operations, Inc. | Integral electrode placement and connection systems |
US8894643B2 (en) | 2008-10-10 | 2014-11-25 | Intuitive Surgical Operations, Inc. | Integral electrode placement and connection systems |
US9468364B2 (en) | 2008-11-14 | 2016-10-18 | Intuitive Surgical Operations, Inc. | Intravascular catheter with hood and image processing systems |
US11622689B2 (en) | 2008-11-14 | 2023-04-11 | Intuitive Surgical Operations, Inc. | Mapping and real-time imaging a plurality of ablation lesions with registered ablation parameters received from treatment device |
US20100204561A1 (en) * | 2009-02-11 | 2010-08-12 | Voyage Medical, Inc. | Imaging catheters having irrigation |
US8545412B2 (en) * | 2009-05-29 | 2013-10-01 | Boston Scientific Scimed, Inc. | Systems and methods for making and using image-guided intravascular and endocardial therapy systems |
US20100305451A1 (en) * | 2009-05-29 | 2010-12-02 | Boston Scientific Scimed, Inc. | Systems and methods for making and using image-guided intravascular and endocardial therapy systems |
US8758257B2 (en) | 2009-12-24 | 2014-06-24 | Renzo Cecere | Instrument including a movement sensor for positioning an effective portion and method of using same |
US20110160596A1 (en) * | 2009-12-24 | 2011-06-30 | Renzo Cecere | Instrument including a movement sensor and method of using same |
US9474471B2 (en) | 2009-12-24 | 2016-10-25 | Renzo Cecere | Instrument including a movement sensor for determining the position of an anchoring mechanism |
US8694071B2 (en) | 2010-02-12 | 2014-04-08 | Intuitive Surgical Operations, Inc. | Image stabilization techniques and methods |
US9814522B2 (en) | 2010-04-06 | 2017-11-14 | Intuitive Surgical Operations, Inc. | Apparatus and methods for ablation efficacy |
US20130012929A1 (en) * | 2011-07-08 | 2013-01-10 | Tyco Healthcare Group Lp | Swinging Bars with Axial Wheels to Drive Articulating Cables |
US9351751B2 (en) * | 2011-07-08 | 2016-05-31 | Covidien Lp | Swinging bars with axial wheels to drive articulating cables |
US10716462B2 (en) | 2011-09-22 | 2020-07-21 | The George Washington University | Systems and methods for visualizing ablated tissue |
US10736512B2 (en) | 2011-09-22 | 2020-08-11 | The George Washington University | Systems and methods for visualizing ablated tissue |
US11559192B2 (en) | 2011-09-22 | 2023-01-24 | The George Washington University | Systems and methods for visualizing ablated tissue |
US9014789B2 (en) | 2011-09-22 | 2015-04-21 | The George Washington University | Systems and methods for visualizing ablated tissue |
US9084611B2 (en) | 2011-09-22 | 2015-07-21 | The George Washington University | Systems and methods for visualizing ablated tissue |
US10076238B2 (en) | 2011-09-22 | 2018-09-18 | The George Washington University | Systems and methods for visualizing ablated tissue |
US10828081B2 (en) | 2013-03-07 | 2020-11-10 | Arthrocare Corporation | Methods and systems related to electrosurgical wands |
US10695121B2 (en) * | 2013-03-13 | 2020-06-30 | Arthrocare Corporation | Method and system of controlling conductive fluid flow during an electrosurgical procedure |
US20140276725A1 (en) * | 2013-03-13 | 2014-09-18 | Arthrocare Corporation | Method and system of controlling conductive fluid flow during an electrosurgical procedure |
US20180014873A1 (en) * | 2013-03-13 | 2018-01-18 | Arthrocare Corporation | Method and system of controlling conductive fluid flow during an electrosurgical procedure |
US9801678B2 (en) * | 2013-03-13 | 2017-10-31 | Arthrocare Corporation | Method and system of controlling conductive fluid flow during an electrosurgical procedure |
US20140330133A1 (en) * | 2013-05-02 | 2014-11-06 | VS Medtech, Inc. | Systems and methods for measuring and characterizing interior surfaces of luminal structures |
US11701033B2 (en) * | 2013-05-02 | 2023-07-18 | VS Medtech, Inc. | Systems and methods for measuring and characterizing interior surfaces of luminal structures |
US10219724B2 (en) * | 2013-05-02 | 2019-03-05 | VS Medtech, Inc. | Systems and methods for measuring and characterizing interior surfaces of luminal structures |
US20220338758A1 (en) * | 2013-05-02 | 2022-10-27 | VS Medtech, Inc. | Systems and methods for measuring and characterizing interior surfaces of luminal structures |
US11363965B2 (en) | 2013-05-02 | 2022-06-21 | VS Medtech, Inc. | Systems and methods for measuring and characterizing interior surfaces of luminal structures |
US11096584B2 (en) | 2013-11-14 | 2021-08-24 | The George Washington University | Systems and methods for determining lesion depth using fluorescence imaging |
US11457817B2 (en) | 2013-11-20 | 2022-10-04 | The George Washington University | Systems and methods for hyperspectral analysis of cardiac tissue |
US11559352B2 (en) | 2014-11-03 | 2023-01-24 | The George Washington University | Systems and methods for lesion assessment |
US10143517B2 (en) | 2014-11-03 | 2018-12-04 | LuxCath, LLC | Systems and methods for assessment of contact quality |
US10682179B2 (en) | 2014-11-03 | 2020-06-16 | 460Medical, Inc. | Systems and methods for determining tissue type |
US10722301B2 (en) | 2014-11-03 | 2020-07-28 | The George Washington University | Systems and methods for lesion assessment |
US11596472B2 (en) | 2014-11-03 | 2023-03-07 | 460Medical, Inc. | Systems and methods for assessment of contact quality |
US20180021089A1 (en) * | 2015-02-09 | 2018-01-25 | Vimecon Gmbh | Laser Applicator Having Electrodes |
US10779904B2 (en) | 2015-07-19 | 2020-09-22 | 460Medical, Inc. | Systems and methods for lesion formation and assessment |
US11344365B2 (en) | 2016-01-05 | 2022-05-31 | Cardiofocus, Inc. | Ablation system with automated sweeping ablation energy element |
US11832878B2 (en) | 2016-01-05 | 2023-12-05 | Cardiofocus, Inc. | Ablation system with automated ablation energy element |
CN109310283A (en) * | 2016-04-19 | 2019-02-05 | 波士顿科学国际有限公司 | Foley's tube visualization device including reinforcing element |
US11439464B2 (en) * | 2016-06-28 | 2022-09-13 | Karl PIEPER | Appliance for conveying a catheter, light guide or cable in a controlled manner |
CN111655115A (en) * | 2017-09-14 | 2020-09-11 | 维卡瑞斯外科手术股份有限公司 | Virtual reality surgical camera system |
US11911116B2 (en) | 2017-09-14 | 2024-02-27 | Vicarious Surgical Inc. | Virtual reality surgical camera system |
CN111278343A (en) * | 2017-10-25 | 2020-06-12 | 波士顿科学国际有限公司 | Direct visualization catheter and system |
US11944276B2 (en) * | 2017-11-09 | 2024-04-02 | Aulea Medical, Inc. | Surgical devices and methods |
US20220322926A1 (en) * | 2017-11-09 | 2022-10-13 | Corinth MedTech, Inc. | Surgical devices and methods |
US11389236B2 (en) | 2018-01-15 | 2022-07-19 | Cardiofocus, Inc. | Ablation system with automated ablation energy element |
CN112584774A (en) * | 2018-06-28 | 2021-03-30 | 皇家飞利浦有限公司 | Internally ultrasound assisted local therapy delivery |
US20200311930A1 (en) * | 2019-03-28 | 2020-10-01 | Purdue Research Foundation | System and methods for clear optimally matched panoramic channel technique for deep brain photonic interface |
US11599994B2 (en) * | 2019-03-28 | 2023-03-07 | Purdue Research Foundation | System and methods for clear optimally matched panoramic channel technique for deep brain photonic interface |
US20220151711A1 (en) * | 2019-07-31 | 2022-05-19 | Orsus, Llc | Devices And Methods For Guide Wire Placement |
CN114375213A (en) * | 2019-07-31 | 2022-04-19 | 奥盛有限责任公司 | Device and method for guidewire placement |
WO2021022205A1 (en) * | 2019-07-31 | 2021-02-04 | Orsus, Llc | Devices and methods for guide wire placement |
CN115040063A (en) * | 2022-06-10 | 2022-09-13 | 兰州大学第二医院 | Biliary tract photography catheter system and use method |
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US20240032776A1 (en) | 2024-02-01 |
US11779195B2 (en) | 2023-10-10 |
US20090221871A1 (en) | 2009-09-03 |
US20190008360A1 (en) | 2019-01-10 |
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