US20040204705A1 - Cryotreatment devices and methods of forming conduction blocks - Google Patents
Cryotreatment devices and methods of forming conduction blocks Download PDFInfo
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- US20040204705A1 US20040204705A1 US10/411,601 US41160103A US2004204705A1 US 20040204705 A1 US20040204705 A1 US 20040204705A1 US 41160103 A US41160103 A US 41160103A US 2004204705 A1 US2004204705 A1 US 2004204705A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
- A61B18/0218—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques with open-end cryogenic probe, e.g. for spraying fluid directly on tissue or via a tissue-contacting porous tip
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
- A61B2018/0212—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques using an instrument inserted into a body lumen, e.g. catheter
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
- A61B2018/0231—Characteristics of handpieces or probes
- A61B2018/0262—Characteristics of handpieces or probes using a circulating cryogenic fluid
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
- A61B2018/0293—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques using an instrument interstitially inserted into the body, e.g. needle
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Abstract
Description
- The present invention relates generally to medical devices for ablating tissue at one or more target sites. More specifically, the present invention relates to cryotreatment devices and methods for inducing controlled necrosis of cardiac tissue within the heart.
- Cardiac arrhythmias such as atrial fibrillation, bradycardia, ventricular tachycardia, ventricle fibrillation, and Wolff-Parkinson-White syndrome are common heart abnormalities that cause stroke, myocardial infarction, and other thromboembolic events within the body. In patients with normal sinus rhythm, the heart is electrically excited to beat in a synchronous and patterned manner, typically at a rate of 60 to 100 beats per minute (bpm). In contrast, in patients with cardiac arrhythmia, abnormal regions of the cardiac tissue may aberrantly conduct to adjacent tissue, causing the heart to beat irregularly. In ventricular tachycardia, for example, electrical signals may be errantly received in the lower heart chamber (i.e. the ventricle) instead of the right, upper chamber (i.e. the atria), causing the heart to beat rapidly. In atrial fibrillation, the most common type of cardiac arrhythmia, the upper chambers of the heart beat at an uncontrolled rate of 350 to 600 bpm, which results in a reduction of the pumping force of the heart. As a result of this reduced pumping force, blood in the heart chambers may become stagnant and pool, forming blood clots that can dislodge within the body and cause stroke or other life threatening events.
- To treat cardiac arrhythmia, a number of therapeutic procedures have been developed, including RF catheter ablation, chemical cardioversion, percutaneous myocardial revascularization (PMR), and suppression. Antiarrhythmic medications such as beta-blockers, calcium channel blockers, anticoagulants, and DIGOXIN have also been used successfully to treat some forms of cardiac arrhythmia. More recent trends have focused on the use of cryotreatment catheters to treat arrhythmias such as atrial fibrillation and ventricular tachycardia. Such devices provide a relatively non-invasive method of treatment in comparison to other surgical techniques.
- In one such method, for example, a catheter loaded with a cryogenic cooling fluid may used to cryogenically cool cardiac tissue at strategic locations of the heart, such as the right and left atria, or the pulmonary veins. The catheter can be used to induce necrosis at one or more pre-mapped target sites within the heart to create conduction blocks within the aberrant electrical conduction pathways. In atrial fibrillation, for example, necrosis of one or more target sites within the atrial cardiac muscle tissue can be used to block the electrical signals believed to cause and/or sustain the fibrillation.
- In some techniques, the use of a cryotreatment device to form the required conduction block may be ineffective since there is no adequate means to control the transmural depth of the lesion, or the distance between each lesion. To compensate for these shortcomings, many cryotreatment devices utilize relatively large catheter tips, which destroy more tissue than is necessary to form the conduction block and further reduce the already weakened pumping force of the heart. It is therefore desirable to have a cryotreatment device capable of transmurally controlling the depth of each lesion and in a contiguous manner.
- The present invention relates generally to cryotreatment devices and methods for reducing or eliminating arrhythmia by inducing controlled necrosis at one or more pre-mapped target sites within the heart. A cryotreatment device in accordance with an exemplary embodiment of the present invention may comprise an elongated member having a proximal portion, a distal portion, and one or more lumens therein in fluid communication with a cooling fluid adapted to cool the distal portion of the elongated member. The elongated member may include one or more needle-like ablation tips configured to pierce and necrotize cardiac tissue within the heart, preventing the conduction of aberrant electrical signals through the tissue to one or more relay sites of arrthymogenic foci. The cryotreatment device may include one or more features configured to form an array of ablations within the cardiac tissue, forming a contiguous line of conduction block.
- The ablation tips may be retractable within the elongated member to control the penetration depth of the tips transmurally into the cardiac tissue. A pull cord operatively coupled to the ablation tip can be used to retract the ablation tip from the cardiac tissue. An ultrasonic probe or other measuring device may also be provided to measure and control the insertion depth of the cryotreatment device within the cardiac tissue.
- A cryosurgical method in accordance with the present invention may comprise the steps of providing a cryotreatment device to a target site within the heart, and necrotizing one or more locations within the cardiac tissue to form a contiguous line of conduction block. A cooling fluid such as liquid nitrous oxide can be injected through an inner lumen extending to the distal portion of the cryotreatment device to cool the surrounding tissue adjacent the ablation tips.
- FIG. 1 is an illustration of a cryotreatment device in accordance with an exemplary embodiment of the present invention, wherein the device is shown inserted through the septal wall of the heart and advanced to a target site at or near one or more relay points;
- FIG. 2 is a partial cross-sectional view of the cryotreatment device of FIG. 1;
- FIG. 3 is a detailed view of the cryotreatment device of FIGS. 1-2, wherein the device includes an ultrasonic probe adapted measure and control the transmural depth of the device into the cardiac tissue;
- FIG. 4 is another detailed view illustrating multiple cryotreatment devices coupled together using a coupling member;
- FIG. 5 is a view of a cryotreatment device in accordance with an exemplary embodiment of the present invention, wherein the cryotreatment device includes a linear array of ablation tips;
- FIG. 6 is a partial cross-sectional view of a cryotreatment device in accordance with an exemplary embodiment of the present invention, wherein the cryotreatment device includes several retractable cryogenic tips configured to form a circumferential line of conduction block within the heart; and
- FIG. 7 is a partial cross-sectional view of a cryotreatment device in accordance with another exemplary embodiment of the present invention, wherein the cryotreatment devices includes an enlarged distal portion with retractable ablation tips.
- The following description should be read with reference to the drawings, in which like elements in different drawings are numbered in like fashion. The drawings, which are not necessarily to scale, depict selected embodiments and are not intended to limit the scope of the invention. Although examples of construction, dimensions, and materials are illustrated for the various elements, those skilled in the art will recognize that many of the examples provided have suitable alternatives that may be utilized.
- FIG. 1 is an illustrative view of a
cryotreatment device 10 in accordance with an exemplary embodiment of the present invention for inducing controlled necrosis at one or more pre-mapped target sites within the heart. Aguide wire 12 inserted percutaneously into the femoral or jugular veins is shown advanced through theseptal wall 14 and into theupper chambers heart 20. Using known manipulation techniques in the art,guidewire 12 can be advanced to a location distal atarget site 22 determined to cause electrical interference with one or more downstreamarrythmogenic foci 24. Aguide catheter 26 sufficiently sized to receivecryotreatment device 10 can be used to advance thecryotreatment device 10 to a location at or near thetarget site 22. - Arrhythmias such as atrial flutter, atrial fibrillation and ventricular tachycardia are typically caused when abnormal regions of the heart transmit aberrant electrical signals vis-à-vis arrythmogenic foci. To treat such arrhythmias, a cryotreatment device in accordance with the present invention can be inserted into cardiac tissue at a pre-mapped target site and cooled to a temperature of about −40 to −100° C. to induce necrosis at one or
more locations pulmonary vein 36. The cryotreatment device can be inserted at thevarious locations foci points 24. In necrotizing the cardiac tissue at several locations, thereby forming a line of conduction block in thepulmonary vein 36, the transmission of aberrant signals believed to cause the arrhythmia can be reduced or in some cases altogether eliminated. - FIG. 2 is a partial cross-sectional view of the
cryotreatment device 10 of FIG. 1, showing thedistal portion 38 of thedevice 10 in greater detail. In the exemplary embodiment of FIGS. 1-2,cryotreatment device 10 comprises a multiplelumen catheter body 40 having anouter shaft 42 configured to pierce and cool the cardiac tissue, and aninner shaft 44 defining aninner lumen 46 in fluid communication with a cooling fluid. Theouter shaft 42 ofcatheter body 40 may have a transverse cross-sectional area that is substantially circular in shape, extending from a proximal end (not shown) located outside of the patient's body to atransition region 48 on thecatheter body 40. Attransition region 48,catheter body 40 tapers distally to a needle-like ablation tip 50 configured to pierce and contact cardiac tissue. - To cool the
distal portion 38 ofcryotreatment device 10 to a sufficiently low temperature to induce necrosis when inserted into cardiac tissue,cryotreatment device 10 can be placed in fluid communication with a cooling fluid such as liquid nitrogen, nitrous oxide (N2O), carbon dioxide (C2O), chlorodifluoromethane, polydimethysiloxane, ethyl alcohol, chlorofluorocarbons (Freon), or other suitable fluid. The cooling fluid can be delivered in either a liquid or gas state throughinner lumen 46, and injected into theannular space 52 between the outer andinner shafts several apertures 54 disposed in theinner shaft 44. In one embodiment, for example, pressurized liquid nitrous oxide can be fluidly coupled to theinner lumen 46 ofcatheter body 40, and ejected throughseveral apertures 54 disposed in theinner lumen 44. Using the Joule-Thompson cooling effect, theapertures 54 are adapted to act as a throttling element (e.g. a throttling nozzle) for the cryogen, producing isenthalpic cooling as the fluid is expended from a relatively high pressure within theinner lumen 46 to a lower pressure as it enters theannular space 52. As the cryogenic fluid expands as it passes through theapertures 54, it transitions to a gas and impinges upon theinterior wall 56 of theouter shaft 42 cooling thedistal portion 38 of thecatheter body 40. This temperature drop is then thermally transferred through thecatheter body 40 and into the surroundingcardiac tissue 58, inducing necrosis at thetarget site 22. The cryogenic fluid is subsequently returned throughannular lumen 52 to the proximal end of thedevice 10. - The number of
apertures 54 can be varied to provide a desired temperature decrease to thedistal portion 38 of thecatheter body 40. The type of cryogen used and the pressure and/or volume at which the cryogen is delivered through theinner lumen 46 can also be selected to impart a particular cooling characteristic to thedevice 10, as desired. In the exemplary embodiment of FIGS. 1-2,cryotreatment device 10 includes several equidistantly spacedapertures 54 configured to provide uniform cooling through thedistal portion 38 of thecatheter body 40. It should be recognized, however, that theapertures 54 could be placed at any number of strategic locations, at either equidistant or non-equidistant intervals, to direct the cryogenic fluid to a particular location within thedevice 10. - The outer and
inner shafts cryotreatment device 10 may be fabricated from materials having certain desirable flexibility and thermodynamic properties. For example, the outer andinner shafts cryotreatment device 10 to be inserted through relatively tortuous locations of the body without kinking. Other suitable biocompatible materials such stainless steel or a polymer/metal composition may also be utilized, depending on the particular application. - Referring now to FIG. 3, methods of using
cryotreatment device 10 will now be described in the context of a cryosurgical procedure to necrotizecardiac tissue 58 within a body lumen such as apulmonary vein 36.Cryotreatment device 10 can be inserted through a previously positionedguide catheter 26 and advanced to apre-mapped target site 22 within the heart believed to transmit aberrant electrical signals to one or more relay points. As shown in FIG. 3, needle-like ablation tip 50 ofdevice 10 can be configured to pierce and contact thecardiac tissue 58 ofpulmonary vein 36, allowing thedistal portion 38 ofcatheter body 40 to be inserted into thecardiac tissue 58. Acurved portion 60 on thecatheter body 40 may be adapted to orient the needle-like ablation tip 50 in a direction substantially perpendicular to thetissue wall 58. - In one aspect of the present invention,
cryotreatment device 10 can be configured to measure and control the transmural depth at which the device is inserted into thecardiac tissue 58. Controlled insertion of the needle-tip ablation tip 50 into thecardiac tissue 58 prevents distension of thevein 36 from occurring, and prevents the ablation of cardiac tissue not necessary to form the conduction block. Controlled insertion of the needle-like ablation tip 50 into thecardiac tissue 58 also ensures that thecryotreatment device 10 is inserted at a sufficient depth to form the desired conduction block. - An
ultrasonic probe 62 or other measurement device may be utilized to measure the precise depth at whichcryotreatment device 10 is inserted into thecardiac tissue 58. Theultrasonic probe 62 can be coupled to catheter body 40 a predetermined distance from the needle-like ablation tip 50, and engaged to acoustically measure the depth at which thedistal portion 38 is inserted into thecardiac tissue 58. Theultrasonic probe 62 may be coupled to thecatheter body 40, or may be formed as a separate element that can be advanced along thecatheter body 40 and positioned proximal thecardiac tissue 58. In one exemplary embodiment, theultrasonic probe 62 may act as a guiding member for thedevice 10, eliminating the need for a separate guide catheter. Those of skill in the art will readily recognize that other suitable devices for measuring the insertion depth of thecryotreatment device 10 may be employed, including, for example, the use of an optical probe, acoustic reflective coatings, distal bipolar electrodes, or through the use radiographic techniques such as fluoroscopic marker bands. - In operation, a fluid controller or other similar device can be coupled to the proximal end of the
cryotreatment device 10 and used to inject a controlled flow of cryogenic fluid (e.g. liquid N2O) through theinner lumen 46. One or more temperature sensors (not shown) on thedistal portion 38 ofcatheter body 40 may also optionally be used to monitor the temperature of thedevice 10 and adjust the flow rate via the fluid controller, as necessary. Aninsulated sleeve 64 surrounding thecatheter body 40 may be utilized to thermally isolate thecatheter body 40 proximal thedistal portion 38 to prevent ablating other areas of the body. - In certain embodiments, the cryotreatment device may include a coupling member configured to couple multiple ablation tips together in an array. As shown in FIG. 4, for example, a
coupling member 66 can be used to connect multiplecryotreatment devices 10 together, forming a linear array of needle-like ablation tips 50 that, when thermally cooled via a cryogenic fluid, create a line of contiguous conduction block along thecardiac tissue 58 at thetarget site 22. Thecoupling member 66 can be configured to couple together any number of cryotreatment devices together in any desired array or pattern. Themultiple cooling members 10 applied in a sequential cooling method will allow the lesions to be made in a stitched like fashion to ensure contiguous connection of all the lesions. The method of stitching is accomplished by moving oneneedle 50 while theother needle 50′ is anchored and froze into the tissue. The sequence of operation would be as follows: - 1. Insert two needles at start point and apply maximum freeze;
- 2. Thaw the proximal needle and reduce temperature on distal needle;
- 3. Retract proximal needle and rotate around anchored distal needle;
- 4. Apply maximum cooling on both needles and repeat steps2-4.
- FIG. 5 is a view of a
cryotreatment device 68 in accordance with another exemplary embodiment of the present invention.Cryotreatment 68 comprises acatheter body 70 having several linearly disposedablation tips 72 along adistal portion 74 that, when placed into fluid communication with a cryogenic cooling fluid, are configured to form a line of conduction block within a target site of the heart. Eachablation tip 72 may be configured similar to tip 50 described above, having a needle-like shape configured to pierce and contact the cardiac tissue when inserted. The number ofneedles 72 andlumens 76 may be the same as shown, or may be as few as twoneedles 72 for any number oflumens 76 in the method previously described. Aninner lumen 76 in fluid communication with a source of pressurized cryogen at or near the proximal end of thedevice 70 is configured to cool eachablation tip 72 in a manner similar that described above with respect tocryotreatment device 10. Thecryotreatment device 70 may also optionally include an ultrasonic probe or other measurement means (not shown) for measuring the precise depth at which theablations tips 72 are transmurally inserted into the cardiac tissue. Aninsulation layer 78 surrounding thecatheter body 70 thermally insulates thebody 70 from ablating other areas of the body. - To form a line of conduction block within a target site of the heart,
ablation tips 72 can be aligned with a portion of the cardiac tissue believed to transfer the aberrant electrical signal(s) to one or more downstream relay points, and inserted into the tissue at a controlled depth. A pressurized cryogenic fluid can be delivered through thecatheter body 70, causing theablation tips 72 on thedistal portion 74 to undergo a temperature drop to a temperature of about −40 to −100° C., inducing necrosis in the surrounding cardiac tissue. - The destruction of more tissue than is necessary to form the conduction block may be mitigated through the use of a series of smaller ablation tips. Moreover, the number, shape and arrangement of the ablation tips may be varied in accordance with the particular application. In certain applications, for example, a cryotreatment device in accordance with the present invention may be configured to form a circumferential line of conduction blocks at a target site within the heart.
- In one exemplary embodiment shown in FIG. 6, a
cryotreatment device 80 in accordance with the present invention may include acatheter body 82 having several needle-like ablation tips 84 ondistal end 86 that, when thermally cooled via a supplied source of cryogenic fluid, form a circumferential line of conduction block at a target site within the heart (e.g. about a pulmonary vein).Cryotreatment device 80 may comprise anouter shaft 88, and aninner shaft 90 disposed within theouter shaft 88. Theinner shaft 90 can be configured to deliver a pressurized source of cryogenic fluid such as liquid nitrogen or N2O throughaperture 92 towards theinterior surface 94 ofdistal end 86, causing theinterior surface 94 of thedistal end 86 ofcatheter body 82 to cool and conduct heat. - Each of the needle-
like ablation tips 84 can be configured to retract throughseveral openings 96 disposed on thedistal end 86 of thecatheter body 82. Acontrol wire 98 extending proximally from eachablation tip 84 to a location outside of the patient's body may be used to retract eachtip 84 through itsrespective opening 96, allowing the operator to adjust the precise depth at which thetip 84 is inserted the cardiac tissue. Aflange 100 coupled to eachablation tip 84 prevents thetip 84 from being pulled proximally through opening 96 ascontrol wire 98 is retracted. As with any of the other embodiments described herein, an ultrasonic probe or other suitable device can be utilized to measure and, if necessary, control the penetration depth of theablation tips 84 within the tissue. - In use,
cryotreatment device 80 can be advanced to a target site within the heart, and, with theablation tips 84 initially in a fully deployed position, inserted into the cardiac tissue. Once thedevice 80 is inserted into the tissue, the operator can retract thecontrol wire 98 proximally a distance, causing theablation tips 84 to retract from within the tissue a slight distance (e.g. 0.5-3.0 cm). An ultrasonic probe or other suitable device may be used to measure the precise depth at which theablation tips 84 are inserted into the cardiac tissue. At the desired depth, a pressurized flow of cryogen is then delivered through the device, causing thedistal end 86 of the device, including theablation tips 84, to cool to a temperature of about −40 to −100° C., forming a circumferential line of conduction block within the body. - FIG. 7 is a partial cross-sectional view of a
cryotreatment device 102 in accordance with another exemplary embodiment of the present invention.Cryotreatment device 102 comprises anouter shaft 104 having a proximal portion (not shown), adistal portion 106, and aninner lumen 108 in fluid communication with a cooling fluid such as liquid N2O. Thedistal portion 106 ofcryotreatment device 102 may be enlarged slightly, orienting several retractable needle-like ablation tips 110 in a wider radial array, permitting the formation of a circumferential line of conduction block at larger target sites. Acontrol wire 112 operatively coupled to eachablation tip 110 can be utilized to adjust the transmural depth of thetip 110 into the cardiac tissue. Aflanged portion 114 on eachablation tip 110 prevents the operator from pulling theablation tip 110 proximally through thetip openings 116 on thedistal portion 106 of theouter shaft 104. - Having thus described the several embodiments of the present invention, those of skill in the art will readily appreciate that other embodiments may be made and used which fall within the scope of the claims attached hereto. Numerous advantages of the invention covered by this document have been set forth in the foregoing description. It will be understood that this disclosure is, in many respects, only illustrative. Changes may be made in details, particularly in matters of shape, size and arrangement of parts without exceeding the scope of the invention.
Claims (44)
Priority Applications (10)
Application Number | Priority Date | Filing Date | Title |
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US10/411,601 US20040204705A1 (en) | 2003-04-10 | 2003-04-10 | Cryotreatment devices and methods of forming conduction blocks |
CA002521714A CA2521714A1 (en) | 2003-04-10 | 2004-04-08 | Cryotreatment devices and methods of forming conduction blocks |
EP04759260.5A EP1610702B1 (en) | 2003-04-10 | 2004-04-08 | Cryotreatment devices for forming conduction blocks |
JP2006509805A JP4653734B2 (en) | 2003-04-10 | 2004-04-08 | Cryogenic treatment device and method for forming a conduction block |
PCT/US2004/010806 WO2004091416A1 (en) | 2003-04-10 | 2004-04-08 | Cryotreatment devices and methods of forming conduction blocks |
US12/485,697 US8048066B2 (en) | 2003-04-10 | 2009-06-16 | Cryotreatment device and method of forming conduction blocks |
US13/252,817 US8585689B2 (en) | 2003-04-10 | 2011-10-04 | Cryotreatment devices and methods of forming conduction blocks |
US14/084,257 US9033967B2 (en) | 2003-04-10 | 2013-11-19 | Cryotreatment devices and methods of forming conduction blocks |
US14/711,232 US9339322B2 (en) | 2003-04-10 | 2015-05-13 | Cryotreatment devices and methods of forming conduction blocks |
US15/132,934 US9750556B2 (en) | 2003-04-10 | 2016-04-19 | Cryotreatment devices and methods of forming conduction blocks |
Applications Claiming Priority (1)
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US10/411,601 US20040204705A1 (en) | 2003-04-10 | 2003-04-10 | Cryotreatment devices and methods of forming conduction blocks |
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US12/485,697 Division US8048066B2 (en) | 2003-04-10 | 2009-06-16 | Cryotreatment device and method of forming conduction blocks |
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US12/485,697 Expired - Fee Related US8048066B2 (en) | 2003-04-10 | 2009-06-16 | Cryotreatment device and method of forming conduction blocks |
US13/252,817 Expired - Fee Related US8585689B2 (en) | 2003-04-10 | 2011-10-04 | Cryotreatment devices and methods of forming conduction blocks |
US14/084,257 Expired - Lifetime US9033967B2 (en) | 2003-04-10 | 2013-11-19 | Cryotreatment devices and methods of forming conduction blocks |
US14/711,232 Expired - Lifetime US9339322B2 (en) | 2003-04-10 | 2015-05-13 | Cryotreatment devices and methods of forming conduction blocks |
US15/132,934 Expired - Lifetime US9750556B2 (en) | 2003-04-10 | 2016-04-19 | Cryotreatment devices and methods of forming conduction blocks |
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US13/252,817 Expired - Fee Related US8585689B2 (en) | 2003-04-10 | 2011-10-04 | Cryotreatment devices and methods of forming conduction blocks |
US14/084,257 Expired - Lifetime US9033967B2 (en) | 2003-04-10 | 2013-11-19 | Cryotreatment devices and methods of forming conduction blocks |
US14/711,232 Expired - Lifetime US9339322B2 (en) | 2003-04-10 | 2015-05-13 | Cryotreatment devices and methods of forming conduction blocks |
US15/132,934 Expired - Lifetime US9750556B2 (en) | 2003-04-10 | 2016-04-19 | Cryotreatment devices and methods of forming conduction blocks |
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EP (1) | EP1610702B1 (en) |
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US20090171334A1 (en) * | 2005-05-20 | 2009-07-02 | Myoscience, Inc. | Subdermal cryogenic remodeling of muscles, nerves, connective tissue, and/or adipose tissue (fat) |
US20090292279A1 (en) * | 2006-01-26 | 2009-11-26 | Galil Medical Ltd. | Device and Method for Coordinated Insertion of a Plurality of Cryoprobes |
US20090299420A1 (en) * | 2008-06-02 | 2009-12-03 | Shuros Allan C | Method and apparatus for cryotherapy and pacing preconditioning |
US7713266B2 (en) | 2005-05-20 | 2010-05-11 | Myoscience, Inc. | Subdermal cryogenic remodeling of muscles, nerves, connective tissue, and/or adipose tissue (fat) |
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JP4653734B2 (en) | 2011-03-16 |
EP1610702B1 (en) | 2016-01-13 |
US20160228174A1 (en) | 2016-08-11 |
US20120022513A1 (en) | 2012-01-26 |
US9750556B2 (en) | 2017-09-05 |
US20140066914A1 (en) | 2014-03-06 |
CA2521714A1 (en) | 2004-10-28 |
WO2004091416A1 (en) | 2004-10-28 |
US20150238244A1 (en) | 2015-08-27 |
US8585689B2 (en) | 2013-11-19 |
JP2006524105A (en) | 2006-10-26 |
EP1610702A1 (en) | 2006-01-04 |
US9033967B2 (en) | 2015-05-19 |
US9339322B2 (en) | 2016-05-17 |
US8048066B2 (en) | 2011-11-01 |
US20090299358A1 (en) | 2009-12-03 |
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