US20040106894A1 - Needleless drug injection device - Google Patents
Needleless drug injection device Download PDFInfo
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- US20040106894A1 US20040106894A1 US10/657,734 US65773403A US2004106894A1 US 20040106894 A1 US20040106894 A1 US 20040106894A1 US 65773403 A US65773403 A US 65773403A US 2004106894 A1 US2004106894 A1 US 2004106894A1
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- drug
- nozzle
- vial
- injector
- piston
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Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0048—Detecting, measuring or recording by applying mechanical forces or stimuli
- A61B5/0051—Detecting, measuring or recording by applying mechanical forces or stimuli by applying vibrations
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/44—Detecting, measuring or recording for evaluating the integumentary system, e.g. skin, hair or nails
- A61B5/441—Skin evaluation, e.g. for skin disorder diagnosis
- A61B5/442—Evaluating skin mechanical properties, e.g. elasticity, hardness, texture, wrinkle assessment
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/178—Syringes
- A61M5/30—Syringes for injection by jet action, without needle, e.g. for use with replaceable ampoules or carpules
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/11—General characteristics of the apparatus with means for preventing cross-contamination when used for multiple patients
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/178—Syringes
- A61M5/20—Automatic syringes, e.g. with automatically actuated piston rod, with automatic needle injection, filling automatically
- A61M5/204—Automatic syringes, e.g. with automatically actuated piston rod, with automatic needle injection, filling automatically connected to external reservoirs for multiple refilling
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- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- Veterinary Medicine (AREA)
- Public Health (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- General Health & Medical Sciences (AREA)
- Surgery (AREA)
- Physics & Mathematics (AREA)
- Molecular Biology (AREA)
- Medical Informatics (AREA)
- Pathology (AREA)
- Biophysics (AREA)
- Vascular Medicine (AREA)
- Dermatology (AREA)
- Anesthesiology (AREA)
- Hematology (AREA)
- Infusion, Injection, And Reservoir Apparatuses (AREA)
- Measuring And Recording Apparatus For Diagnosis (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
- Media Introduction/Drainage Providing Device (AREA)
Abstract
A drug injector includes a chamber for holding a drug to be injected into a biological body, and an nozzle through which the drug is injected. A piston is positioned in the chamber, and an actuator is coupled to the piston. The actuator includes a member that contracts when heated. In some embodiments, heating of the member is induced by applying a potential to the member. The actuator moves the piston towards the nozzle when the member is heated to expel the drug out of the chamber through the nozzle. The drug injector can include a sensor for measuring properties, such as stiffness, of the outer layer of the body. Further, the drug injector can adjust the piston movement based on the sensed properties. Alternatively, the sensor can be used with other medical devices, such as microneedle transport devices.
Description
- This application is a Continuation of Attorney Docket No. 0050.2048-002 entitled “Needleless Drug Injection Device” filed on Sep. 5, 2003 which claims the benefit of U.S. Provisional Application Nos. 60/409,090, filed Sep. 6, 2002 and 60/424,114, filed Nov. 5, 2002. The entire teachings of the above applications are incorporated herein by reference.
- Injection of a liquid such as a drug into a human patient or an agriculture animal is performed in a number of ways. One of the easiest methods for drug delivery is through the skin which is the outermost protective layer of the body. It is composed of the epidermis, including the stratum corneum, the stratum granulosum, the stratum spinosum, and the stratum basale, and the dermis, containing, among other things, the capillary layer. The stratum corneum is a tough, scaly layer made of dead cell tissue. It extends around 10-20 microns from the skin surface and has no blood supply. Because of the density of this layer of cells, moving compounds across the skin, either into or out of the body, can be difficult.
- The current technology for delivering local pharmaceuticals through the skin includes methods that use needles or other skin piercing devices. Invasive procedures, such as use of needles or lances, effectively overcome the barrier function of the stratum corneum. However, these methods suffer from several major disadvantages: local skin damage, bleeding, and risk of infection at the injection site, and creation of contaminated needles or lances that must be disposed. Further, when these devices are used to inject drugs in agriculture animals, the needles break off from time to time and remain embedded in the animal.
- Needleless injection devices have been proposed to overcome the problems associated with needles, but the proposed devices present different problems. For example, some needleless injection devices rely on spring actuators that offer limited control. Others use solenoids, compressed air or hydraulic actuators also offer limited control.
- Needleless drug injection apparatus and methods described herein use specially-configured shaped memory materials in combination with one or more nozzles to effectively inject a drug through an animal's skin to a selected depth without first piercing the skin with a lance or needle.
- A drug injector includes a housing having a chamber for holding a drug to be injected into a biological body, and a nozzle through which the drug is injected. A piston is positioned in the housing, and an actuator is coupled to the piston. The actuator includes a member that contracts when a potential is applied to the member. The actuator moves the piston towards the nozzle when the potential is applied to the member to expel the drug out of the chamber through the nozzle.
- A resilient member, such as a coiled spring, may be used to force the piston away from the nozzle after the potential diminishes. The member may be one or more wires of shape memory alloy, for example, Ni—Ti.
- In certain embodiments, the chamber is coupled to a reservoir holding a sufficient amount of drug for multiple injections. A sterile interface can be positioned between the orifice and the body to prevent cross contamination between bodies when the injector is used as a multiuse device. The sterile interface can be a flexible ribbon supplied from a roller, with a new sterile portion of the ribbon being positioned over the nozzle after an injection. In some embodiments, the chamber is within a vial positioned in the housing. A plurality of vials can be sequentially supplied to the injector so that a new vial is positioned in the injector after an injection.
- In particular embodiments, the injector includes a skin sensor that measures skin properties of the body, and a servo-controller coupled to the actuator and the skin sensor. The servo-controller adjusts the injection pressure of the drug injector based on the skin properties. A tailored stochastic sequence can be used to determine the skin properties. The skin properties can be determined with system identification techniques. In certain embodiments, the skin is modeled as a second order mechanical system.
- The foregoing and other objects, features and advantages of the invention will be apparent from the following more particular description of preferred embodiments of the invention, as illustrated in the accompanying drawings in which like reference characters refer to the same parts throughout the different views. The drawings are not necessarily to scale, emphasis instead being placed upon illustrating the principles of the invention.
- FIG. 1A is a perspective view of a drug delivery device in accordance with the invention.
- FIG. 1B is a side view of the drug delivery device of FIG. 1A.
- FIG. 1C is an end view of the drug delivery device taken along the
line 1C-1C of FIG. 1B. - FIG. 2 is a perspective view of the drug delivery device of FIG. 1A with a controller and energy source.
- FIG. 3A is a graph of the time response of a shape memory alloy fiber of the drug delivery device of FIG. 1A for a high strain.
- FIG. 3B is a graph of the time response of the shape memory alloy fiber of the drug delivery device of FIG. 1A when the fiber is subjected to a potential as a quick pulse.
- FIGS.4A-4C are respectively side, front, and top views of a hand-held drug delivery device.
- FIG. 4D is a perspective view of the drug delivery device shown in FIGS.4A-4C.
- FIG. 5A is a cross-sectional view of the drug delivery device taken along the line5A-5A of FIG. 1C prior to delivery of a drug.
- FIG. 5B is a cross-sectional view of the drug delivery device of FIG. 1A during drug delivery.
- FIG. 6A is a perspective view of an alternative embodiment of the drug delivery device in accordance with the invention.
- FIG. 6B is a side view of the drug delivery device of FIG. 6A.
- FIG. 6C is top view of the drug delivery device taken along the
line 6C-6C of FIG. 6B. - FIG. 6D is front view of the drug delivery device taken along the line5D-5D of FIG. 6B.
- FIG. 7A is a perspective view of a drug vile for the drug delivery device of FIG. 6A.
- FIG. 7B is a cross-sectional view of the drug vile of FIG. 7A.
- FIG. 8 is a perspective view of the drug delivery device of FIG. 6A with a controller and energy source.
- FIG. 9A is a cross-sectional view of the drug delivery device taken along the
line 9A-9A of FIG. 6D prior to delivery of a drug. - FIG. 9B is a cross-sectional view of the drug delivery device during drug delivery.
- FIG. 10 is cross-sectional view of another alternative embodiment of the drug delivery device in accordance with the invention.
- FIG. 11 illustrates the drug delivery device of FIG. 10 with a protective sterile ribbon in accordance with the invention.
- FIGS. 12A and 12B illustrate yet another alternative embodiment of the drug delivery device in accordance with the invention.
- FIG. 13 illustrates the drug delivery device with a sensor used to detect properties of the skin in accordance with the invention.
- FIG. 14 is a block diagram of an alternative embodiment of the sensor used to detect properties of the skin in accordance with the invention.
- A description of preferred embodiments of the invention follows.
- Referring to FIGS.1A-1C, there are shown various views of a drug delivery device used to inject a liquid formulation of an active principle, for example, a drug, into biological body such as an agriculture animal or human being. The delivery device is generally identified as 10 in the illustrated embodiment as well as in other embodiments described later. The drug is initially contained in a chamber 12 (FIG. 5A) and is injected out through an orifice or
output port 14 into the body. - A nozzle is typically used to convey the drug to the skin at the required speed and diameter to penetrate the skin as required. The nozzle generally contains a flat surface, such as the
head 17 that can be placed against the skin and anorifice 14. It is the inner diameter of theorifice 14 that controls the diameter of the drug stream. Additionally, the length of an aperture, or tube, defining theorifice 14 also controls the injection pressure. In some embodiments, a standard hypodermic needle is cut to a predetermined length and coupled to the head. One end of the needle is flush, or slightly recessed, with respect to the surface of thehead 17 that contacts the skin to avoid puncturing the skin during use. The internal diameter of the needle (e.g., 100 μm) defines the diameter of the aperture, and the length of the needle (e.g., 5 mm) together with the aperture dimension controls the resulting injection pressure, for a given applicator pressure. In other embodiments, a hole can be drilled directly into thehead 17 to reduce assembly steps. In general, the length of the orifice is selectable, for example ranging from 500 μm to 5 mm, while its diameter can range from 80 μm to 200 μm. - The
device 10 includes aguide tube 16 in which apiston 18 is positioned. Aninterchangeable head 17 is attached at anenlarged end 19 of thetube 16 with a set ofscrews 21. One end of thepiston 18, along with the inside of theenlarged end 19 andhead 17 define thechamber 12, and apush block 22 is attached at the other end of thepiston 18. Although thepiston 18 forms a clearance seal with thetube 16, a seal ring can be placed about thepiston 18 to prevent drug from escaping from thechamber 12 between thepiston 18 and thetube 16. Attached on the outside of thepush block 22 is anelectrical contact plate 24. Anothercontact plate 26 is positioned between theinterchangeable head 17 and theenlarged end 19. - In some embodiments, the
guide tube 16 includes linear bearings to reduce the friction of thepiston 18. Preferably, thepiston 18 is rigid to avoid buckling under the force exerted by the actuator. Further, thepiston 18 is light weight to reduce its inertia ensuring a rapid acceleration upon activation. In one embodiment, thepiston 18 is formed from a hollow aluminum rod. Other parts can also be advantageously constructed of light weight materials. For example, thepush block 22 can be formed from a machinable poly acetal. - In addition to the
contact plates actuator 28 includes one to six ormore wires 30 positioned about thetube 16 and parallel to one another. Oneend 32 of eachwire 30 is attached to thecontact plate 24 through thepush block 22, and anotherend 34 of thewire 30 is attached to arespective capstan 36. Thecapstan 36, and thecontact plates wires 30 are electrically connected to each other through thecontact plates collar 38 positioned about theguide tube 20 helps guide thewires 30 through theholes 39 between theenlarged region 19 and thepush block 22. - To apply the appropriate tension to the
wires 30 and to define the volume of thechamber 12, acoiled spring 37 is positioned about thepiston 18 between the end of thetube 16 and thepush block 22, and thecapstans 36 are turned accordingly, much like adjusting the tension in guitar strings. Thewires 30 are wrapped around therespective capstans 36 one or more times. As such, the strain near the terminal ends 34 of thewires 30 attached to thecapstans 36 are significantly less than the strain along the remainder of the length of thewires 30. For example, the strain near theterminal end 34 may be about 1% while that of the remainder of the wire may be about 15%. - The
wires 30 can be secured to thecontact plate 24 with capstans, as well. Alternatively, thewires 30 can be attached to one or bothcontact plates - Alternatively, each
wire 30 can be twisted with a respective electrically conductive wire made of, for example, copper or iron. The twisted segment is then bent back, and partially twisted forming a loop, with the partially twisted segment formed of two strands of thewire 30 and two strands of the copper wire. The formed loop can be placed on a pin, for example, or it can be fully twisted and then bent back and partially twisted forming another loop, with the partially twisted segment formed of four strands of thewire 30 and four strands of the copper wire. Again, the formed loop can be placed on a pin to secure thewire 30 to thecontact plate 24 and/or 26. - More generally, the
wires 30 can be formed from a shape memory material that changes from a first stable state to a second stable state upon excitation. For example, the shape memory material can be a shape memory polymer. Alternatively, or in addition, the shape memory material can be an alloy. In some embodiments, a phase change of the shape memory material occurs when the material is heated. For example, a shape metal alloy can exist with one of two different lattice structures, such that a phase change from one lattice structure to another occurs responsive to the application and/or removal of thermal energy. - The
wires 30 are made of a suitable material that contracts when heated and can be used as an actuation method. Heating can be accomplished by passing a current through thewire 30, known as Joule heating. Thus, the current is conducted within thewires 30 after a potential is applied across them. A class of materials that contract when a potential is applied to them includes piezoelectric materials and shape memory alloys. While piezoelectric crystals contract about 1%, shape memory alloys are able to contract approximately 15% or more. The larger contraction of shape memory alloys makes them desirable for the illustrated embodiment. Accordingly, thewires 30 are made of shape memory alloy such as, for example, Ni—Ti (also known as Nitinol), available from Shaped Memory Applications Inc., of San Jose, Calif., and from Dynalloy Inc. of Costa Mesa, Calif., under the Trade Mark FLEXINOL. When a potential is applied across thewires 30 via thecontact plates wires 30 heat up. As thewires 30 heat up, a phase transformation of the wire material occurs, namely, the wire changes phase from martensite to austenite. This phase transformation causes thewires 30 to contract such that thepiston 18 is pushed towards theorifice 14, thereby forcing the drug from thechamber 12 out theorifice 14. Preferably, the shape memory alloy is fast acting to provide a sudden force suitable for injecting a drug into a patient's skin without using a needle. A more detailed description of shape memory alloys and their use is described in U.S. Pat. No. 5,092,901, the entire contents of which are incorporated herein by reference. - To use the
device 10, the device is connected to acontroller 50 with a pair ofleads 52, and the controller in turn in connected to acapacitor bank 54 with another pair ofleads 56, as illustrated in FIG. 2. Thecontroller 50 can be a simple microprocessor, or alternatively a personal computer with multifunction capabilities. The capacitors of thebank 54 are energized through a power source in thecontroller 50 or by an external power source. Once energized, the capacitors, under the direction of thecontroller 50, discharge to apply a potential across thewires 30 via theplates wires 30 are connected together in a parallel configuration, the supply potential being applied equally across the ends of each of themultiple wires 30. In another embodiment, thewires 30 are connected together in a series configuration. Still other arrangements can be used to apply the potential across thewires 30, for example, as describe in U.S. application Ser. No. 10/200,574 filed Jul. 19, 2002, by Angel and Hunter, the entire contents of which are incorporated herein by reference. - Although any capacitor can be used in the
bank 54, a super capacitor has the advantageous feature of providing a large energy density in a small physical size. Hence the capacitors of thebank 54 can besuper capacitors 53 that have a volume from 1.5 ml to 30 ml, preferably 3 ml, and an energy output of 10 J to 1 KJ, preferably 100 J. The current applied to thewires 30 is approximately 100 mAmps to 5 Amps, and the voltage applied to thewires 30 is between about 1 volt to 10 volts. In one embodiment, the applied current is 1 Amp, and the applied voltage is 5 volts. To heat thewires 30 quickly, larger currents of 25 to 100 Amps can be applied. As fast action is required, the power source must also be able to switch large currents with millisecond timing. - The amount of force per area generated by the
wires 30 is about 235 MN/m2. In the illustrated embodiment, the volume of drug initially contained in thechamber 12 is about 200 μL to 250 μL, and theorifice 14 has a diameter of between about 50 μm to 500 μm. In some embodiments, the drug volume is up to 500 μL. The drug injection velocity is about 150 m/s with a 150μm orifice 14. Generally, an injection velocity of 100 m/s or greater is required for successful skin penetration (e.g., penetrating skin to a depth of 2 mm) in a stream having a diameter of 100 μm. Advantageously, the stream diameter of the needleless injector can be substantially smaller than a typical 24 gauge needle having a diameter of 450 μm. - The
device 10 has a length, L1, of approximately 150 mm, and thewires 30 contract about 7 mm when a potential is applied across them. Thewires 30 can have circular cross section, in which case eachwire 30 has a diameter of approximately 0.025 mm to 2 mm, preferably 380 μm. Alternatively, each fiber can have a flat ribbon shape with a thickness approximately in the range 0.025 mm to 0.5 mm and a width of approximately 0.75 mm to 10 mm. Other suitable shape memory alloys include Ag—Cd, Au—Cd, Au—Cu—Zn, Cu—Al, Cu—Al—N, Cu—Zn, Cu—Zn—Al, Cu—Zn—Ga, Cu—Zn—Si, Cu—Zn—Sn, Fe—Pt, Fe—Ni, In—Cd, In—Ti, and Ti—Nb. - Referring now to FIGS. 3A and 3B, there are shown graphs of the time response of
wires 30 made from Ni—Ti. Shown in FIG. 3A is the response of a wire subjected to a strain of nearly 5%. As can be seen, the contraction time for this wire is about 10 ms. By way of contrast, FIG. 3B illustrates a wire subjected to faster pulse than that applied to the wire of FIG. 3A. With the faster pulse, the fiber experiences a strain of about 1%, with a contraction time of about 1 ms. - In use, the
device 10 is typically mounted within an applicator that is held by an operator. The applicator can be shaped as a pistol, cylinder or any other suitable geometry. An exemplary applicator is shown in FIGS. 4A through 4D. In one embodiment, referring to FIG. 4A, a pistol shapedapplicator 400 includes abarrel 405 configured to house thedevice 10. Thebarrel 405 can be a hollow tube or rectangle having a cavity sized to accept thedevice 10. Referring to FIG. 4B, thebarrel 405 includes anaperture 420 at one end sized to accept thehead 17 of thedevice 10. Thehead 17 protrudes through theaperture 420 to facilitate contact with an animal's skin. Further, theapplicator 400 includes ahandle 410 configured to be grasped by an operator. Thehandle 410 is coupled at one end to thebarrel 405. Additionally, theapplicator 400 can include a base 415 coupled to another end of thehandle 410. The base 415 can be configured to house other parts of the needleless injector, such as the power source and/or control unit. Thehandle 410 can be similarly configured (e.g., hollowed out) to also house parts of the needleless injector. Further, theapplicator 400 can include aswitch 420. Theswitch 420 can be controlled by an operator to operate thedevice 10 to initiate an injection and/or a filling of the device with a drug. - Referring to FIGS. 5A and 5B, as well as to FIG. 1A, the operator positions the applicator to place a
surface 60 of thehead 17 against the skin, S, of the biological body. Prior to the placement of thehead 17 against the skin, or while thehead 17 is positioned against the skin, thecapacitor bank 54 is energized as described above. The operator then triggers thedevice 10 through thecontroller 50 to discharge thecapacitor bank 54, thereby applying a potential across thewires 30 which causes them to contract. As thewires 30 contract, they pull thepush block 22, which pushes thepiston 18 towards thehead 17 to force the drug, D, from thechamber 12 through theorifice 14 into the body. The injection pressure can be as low as 1 MPa or lower or as high as 300 MPa. For comparison, a minimum local pressure of approximately 1.91 MPa is required for piercing skin to a depth of 2 mm using a 100 μm diameter needle After the energy in the capacitor bank is depleted, the potential across thewires 30 is removed which causes thewires 30 to extend to their original length as thecoiled spring 37 pushes thepush block 22 away from thehead 17. Thechamber 12 can then be refilled if desired with additional drug to be injected into another body or the same body. - Turning now to FIGS.6A-6D, there are shown various views of an alternative embodiment of the
drug delivery device 10, where like features are identified by like numerals. Here, thedevice 10 includes twobase portions piston 18 extends through thebase portion 72 and through part of thebase portion 70, as shown, for example, in FIG. 9A. As before, thepiston 18 is attached at one end to thepush block 22, which slides back and forth over asurface 76 of thebase portion 72, such that the piston slides back and forth in the base portions. - Referring also to FIGS. 7A and 7B, a removable and/or
disposable vial 80 is mounted in thebase portion 70. For example, thevial 80 can be screw mounted to thebase portion 70. Thevial 80 is provided with a nozzle, as described above, at one end defining theorifice 14. Thevial 80 also includes aplunger 82 that moves back and forth in thechamber 12 defined within thevial 80. Theplunger 82 abuts theterminal end 84 of thepiston 18. As such, as thepiston 18 moves towards theorifice 14, drug, D, contained in thechamber 12 is expelled through theorifice 14. In some implementations, the orifice of the drug vial, or the chamber of the embodiment of FIG. 1A, is sealed with a suitable material prior to use. The seal may be manually removed, or it may be removed by the injection pressure of the drug as it ejects from the vial or chamber. - A
single length wire 30 is positioned on each side of thebase portions lead capstan 90 a, wrapped sequentially aroundintermediate capstans terminal capstan 90 e. To apply the appropriate tension to thewires 30, thecoiled spring 37 is positioned about thepiston 18 between thebase portion 72 and thepush block 22, and arachet mechanism 92 is employed to adjust the tension in thewires 30. Thecapstans conductive bars capstans conductive plates plates push block 22, but electrically insulated from thepiston 18 andbase portion 72. The twobars base portion 70. As such, when a potential is applied across theconductive bars wire 30. - In one implementation, the
device 10 of FIG. 6A is connected to thecontroller 50 with the pair ofleads 52, and the controller in turn in connected to thecapacitor bank 54 with another pair ofleads 56, as illustrated in FIG. 8. As mentioned above, the capacitors of thebank 54 are energized through a power source in thecontroller 50 or by an external power source. Once energized, the capacitors, under the direction of thecontroller 50, discharge to apply a potential across thewires 30 via theconductive bars wires 30 heat up and contract such that thepiston 18 is pushed towards theorifice 14, thereby forcing the drug D from thechamber 12 of thevial 80 out theorifice 14. - Although shown as blocks, the
base portions device 10 of FIG. 6A in a particular application. As mentioned before, the device can be mounted within an applicator that is held by an operator. - Referring to FIGS. 9A and 9B, as well as to FIG. 6A, to use the
device 10, the operator positions the applicator such that asurface 101 of thevial 80 is placed against the skin, S, of the body. Prior to the placement of thesurface 101 against the skin, or while thesurface 101 is positioned against the skin, thecapacitor bank 54 is energized, as described earlier. The operator then triggers thedevice 10 through thecontroller 50 to discharge thecapacitor bank 54, thereby applying a potential across thewires 30 which causes them to contract. As thewires 30 contract, they pull thepush block 22 which pushes thepiston 18, which in turn pushes theplunger 82 towards theorifice 14 to force the drug, D, from thechamber 12 through theorifice 14 into the body. After the energy in the capacitor bank is depleted, the potential across thewires 30 is removed which causes thewires 30 to extend to their original length as thecoiled spring 37 pushes thepush block 22 away from thevial 80. Thechamber 12 can then be refilled if desired with additional drug to be injected into another body. - The
device 10 of FIGS. 1A or 5A can be used as a single-use device or for multiple uses. When used as a multiuse device, the cycle time between uses can be 0.5 seconds or less. - For example, there is shown in FIG. 10 the
device 10 of FIG. 1A coupled to areservoir 100 that supplies thechamber 12 with a sufficient amount of drug, D, for each injection, and holds enough drug for approximately 20 to 200 or more injections. Alternatively, individual doses may be provided in a plurality of reservoirs sequentially coupled to thedelivery device 10. Avalve 102 is associated with atube 103 connecting thereservoir 100 with aninlet port 104 of thechamber 12. Thevalve 102 is opened and closed under the direction of thecontroller 50, or an additional controller, to allow the desired amount of drug into thechamber 12 for each injection. Thedevice 10 of FIG. 6A can also be coupled to a similar reservoir that is operated in the manner just described. - When the
device 10 of FIG. 10 is in use, thecontroller 50 instructs thevalve 102 to open to allow the drug to flow from thereservoir 100 through theinlet port 104 into thechamber 12, and, after a prescribed period of time, thecontroller 50 directs thevalve 102 to close so that a desired amount of the drug is held in thechamber 12 for a single injection. - Next, or while the
chamber 12 is being filled with drug, the operator positions the applicator to place thesurface 60 of thehead 17 against the skin, S, of the body. Meanwhile, thecapacitor bank 54 is energized as described above. The operator then triggers thedevice 10 through thecontroller 50 to discharge thecapacitor bank 54, thereby applying a potential across thewires 30 which causes them to contract. As thewires 30 contract, they pull thepush block 22 which pushes thepiston 18 towards thehead 17 to force the drug, D, from thechamber 12 through theorifice 14 into the body. After the energy in the capacitor bank is depleted, the potential across thewires 30 is removed which causes thewires 30 to extend to their original length as thecoiled spring 37 pushes thepush block 22 away from thehead 17. Thecontroller 50 then instructs thevalve 102 to open to refill thechamber 12 with additional drug from thereservoir 100 to be injected into another body. - When the
device 10 is intended for multiple uses, it may be desirable to provide some type of protective sterile barrier between thehead 17 and the skin of the body to eliminate or at least minimize exposing a subsequent body with contaminants from a previous body. - For example, there is shown in FIG. 11 the
device 10 provided with a supply of ribbon from asupply roller 110 mounted to thedevice 10 with asupport 112. A sheet ofribbon 111 passes between the face 60 (see, e.g., FIG. 1A) and the skin, S, of the body. After use, theribbon 111 is spooled onto a take-uproller 114 that is mounted to thedevice 10 with asupport 116. Theribbon 111 is wide enough to cover theface 60 such that none of theface 60 makes contact with the skin, S. Theribbon 111 is made of any suitable material that prevents cross-contamination between biological bodies, such as a non-porous flexible material. - The operation of the take-up
roller 114, and, optionally, thesupply roller 110, can be controlled by thecontroller 50, or an additional controller. Thus, when in use, thedevice 10 ejects drug from theorifice 14 through theribbon 111 into the body. After the drug has been injected into the body, additional drug can be supplied from thereservoir 100 according to the techniques described above, while thecontroller 50 instructs theroller 114 to take up a sufficient amount ofribbon 111 in the direction A, so that the next body is exposed only to a new sterile portion of theribbon 111 during the injection procedure. - In other implementations, a new
sterile head 17 is positioned on thedevice 10 after an injection, while theprevious head 17 is disposed in a suitable manner. - Referring now to FIGS. 12A and 12B, there is shown another embodiment of the
device 10 suitable for multiuse operations. Thedevice 10 is provided with a series ofvials 80 connected together, for example, with aflexible web 120.Enlarged regions 122 and 124 (see, e.g., FIG. 7A) of thevials 80 engage with aslot 126 of thebase portion 70. Thus, after each injection, adriver 200, separate from or integral with thedevice 10, pulls theweb 120, and hence thevials 80, in the direction B until a vial filled with drug and fed from the top of thebase 70 is suitably coupled with thepiston 18 for the next injection. The injection procedure proceeds as described earlier, for example, for the embodiment of FIG. 6A. As such, thedevice 10 can be used in a “machine-gun” like manner, with new vials being fed through the top of thebase 70, while depleted vials are pulled out from the bottom of thebase 70. Thedriver 200 can be under the control of thecontroller 50 or another controller. Thevials 80 could be fed and removed from the side of thebase portion 70. Moreover, such an automated arrangement could be implemented with thedevice 10 of FIGS. 1-4. - In some implementations, the
controller 50 is coupled with a sensor that detects skin properties. This information can be used to servo-control theactuator 28 to tailor the injection pressure, and, therefore, the depth of penetration of drug into the skin for a particular application. For instance, when thedevice 10 is used on a baby, the sensor detects the softness of the baby's skin, and thecontroller 50 uses the properties of the baby's skin and consequently reduces the injection pressure. The injection pressure can be adjusted, for example, by controlling the current amplitude applied to thewires 30 and/or the current pulse rise time and/or duration. When used on an adult or someone with sun damaged skin, the controller may increase the injection pressure. The injection pressure may be adjusted depending on location of the skin on the body, for example, the face versus the arm of the patient. The injection pressure can also be tailored to deliver the drug just underneath the skin or deep into muscle tissue. Moreover, the injection pressure may be varied over time. For instance, in some implementations, a large injection pressure is initially used to pierce the skin with the drug, and then a lower injection pressure is used to deliver the drug. A larger injection may also be used to break a seal that seals the chamber or vial. - Skin is a non-linear, viscoelastic material. Microscopic changes in cellular mechanical properties or adhesion between tissue can be observed as macroscopic changes in static or dynamic mechanical tissue properties. These factors combine to determine the behavior of skin in response to outside stimulants. For small force perturbations about an applied static force, the skin mechanical dynamics can be approximated as a linear mechanical system relating the applied force F(t) to skin deformation x(t) as:
-
- A Bode plot (gain vs. freq.) can be obtained for the above mechanical system, illustrating a decrease in compliance with increase skin stiffness. A tailored stochastic sequence can also be performed by tuning F(t) to pull out the relevant parameters. As such, skin properties can be determined with system identification techniques. Such techniques are described in the article “The Identification of Nonlinear Biological Systems: Volterra Kernel Approaches,” by Michael J. Korenberg and Ian W. Hunter, Annals of Biomedical Engineering, Vol. 24, pp. 250-269, 1996, the entire contents of which are incorporated herein by reference.
- Referring now to FIG. 13, there is shown a
skin property sensor 200 associated with thedrug delivery device 10. Thesensor 200 includes an electromagnetically drivenvoice coil 202 coupled to aforce transducer 206 with aflexure 204. Theforce transducer 206 in turn is coupled to a linear variable differential transducer (LVDT) 208 with asensor tip 201. In the implementation shown, thevoice coil 202, theforce transducer 206, and theLVDT 208 are connected to a controller such as thecontroller 50, which drives thesensor 200 as well as receives signals from thesensor 200. Thesensor 200 can be integrated with thedevice 10, or it can be a separate unit. As shown, the sensor is positioned within thedevice 10, with thesensor tip 201 located near the orifice 14 (see also FIGS. 1A, 5A, and 6A). - Accordingly, when the
device 10 is used with thesensor 200, thedevice 10 is initially placed against the skin, S, of the body such that thesensor tip 201 also rests against the skin. Thecontroller 50 then drives thevoice coil 202, for example, up to 20 kHz, to perturb the skin, while theforce transducer 202 detects the force thetip 201 applies to the skin, and theLVDT 208 detects the displacement of the skin. This data is fed back to thecontroller 50 which then evaluates the skin properties with the system identification techniques described earlier. Based on the detected skin properties, thecontroller 50 directs theactuator 28 to eject the drug, D, contained in thechamber 12, through theorifice 14 with the desired injection pressure. Alternatively, abody portion 210 in which thechamber 12 is defined can function as thesensor tip 201. In such implementations, thebody portion 210 would be coupled to theLVDT 208 andforce sensor 206 so that thechamber 12,body portion 210, andsensor 200 would be positioned in line. - Other skin property sensor arrangements can also be used with the
device 10, such as thesensor configuration 300 shown as a block diagram in FIG. 14. Thesensor 300 includes a linear electromagnetic actuator 302 (e.g., model no. 4910, available from Bruel and Kjaer) vertically mounted to a rigid frame. A strain gauge type load cell 304 (e.g., model no. ELF-TC13-15, available from Entran, of Fairfield, N.J.) is mounted to the actuator platform for the purpose of measuring the DC offset of the system corresponding to the static loading, as measured with a multimeter 303 (e.g., model no.HP 972A, available from Hewlett Packard, or Palo Alto, Calif.) via asignal conditioning amplifier 305. Below theload cell 304 is an impedance head 306 (Bruel and Kjaer model no. 8001) consisting of apiezoelectric accelerometer 306 a and apiezoelectric force transducer 306 b. The two outputs from the accelerometer record the force applied to the skin and its resulting acceleration. Twocharge amplifiers 308′, 308″ (generally 308) (Bruel and Kjaer model no. 2635) transform the force to a proportional voltage and doubly integrate the acceleration to give the skin displacement. Theactuator 302 is driven by an algorithm, such as a Visual BASIC program, that simulates a Dynamic Signal Analyzer through apower amplifier 310. The algorithm outputs a swept sinusoidal signal within a range of pre-determined frequencies. This modulation is a small perturbation on top of an initial static load, which is determined from the output voltage of theload cell 304. The measured force and displacement of the actuator are then input to two separate channels of adata acquisition board 312 and used to calculate the compliance transfer function gain and phase with a computer or thecontroller 50. In one implementation, there is a 50 kHz per channel of the data acquisition board, which can be increased to 100 kHz per channel when multiplexed. The A/D is 18 bits with ±4.5 V, while the D/A is 18 bits with ±3.0 V. Like that shown in FIG. 13 for thesensor 200, thesensor 300 is preferably associated with thedevice 10 through thecontroller 50. Accordingly, properties of the skin are analyzed by thecontroller 50 based on the data from thesensor 300. Thecontroller 50 then directs thedevice 10 to eject drug into the body with the appropriate injection pressure. - Although the
sensors device 10, the sensors can be combined with other types of medical devices. For example, the sensor can be combined with other types of needleless injectors such as those using magnetic, chemical, hydraulic, and spring actuators, and those described in U.S. application Ser. No. 10/200,574 filed Jul. 19, 2002, and U.S. Provisional Application No. 60/409,090 filed Sep. 6, 2002, incorporated by reference in their entireties. Additionally, the sensor can be combined with injectors that use needles, such as microneedle injectors, and those described in U.S. application Ser. Nos. 10/238,844 filed Sep. 9, 2002 and 10/278,049 filed Oct. 21, 2002, also incorporated by reference in their entireties. Advantageously, the sensed properties can be used to control the depth and/or insertion force of the needles. - Furthermore, the
sensors - In some embodiments, the
sensors - While this invention has been particularly shown and described with references to preferred embodiments thereof, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the scope of the invention encompassed by the appended claims. For example, contractile polymers, or any other suitable contracting material, can be used instead of the shape memory alloy. The
device 10 may include multiple chambers or may accommodate multiple drug vials. Thus, thedevice 10 is able to deliver drug sequentially or simultaneously. For example, thedevice 10 is able to deliver two or more drugs at once to the body.
Claims (35)
1. A drug injector configured to inject a drug to a depth beneath an animal's skin comprising:
a chamber for holding a drug to be injected into a biological body;
a nozzle in fluid communication with the chamber, the drug being injected though the nozzle;
a piston positioned within the chamber; and
an actuator coupled to the piston, the actuator including a member that contracts when a potential is applied to the member, the actuator moving the piston towards the nozzle when the potential is applied to the member to expel the drug out of the chamber through the nozzle, thereby delivering the drug to a depth beneath an animal's skin.
2. The drug injector of claim 1 further comprising an inlet port for filling the chamber with the drug.
3. The drug injector of claim 1 further comprising a resilient member that applies a force to the piston away from the nozzle.
4. The drug injector of claim 3 wherein the resilient member is a coiled spring.
5. The drug injector of claim 1 wherein the member is one or more wires of shape memory material.
6. The drug injector of claim 5 wherein the shape memory material is a shape memory polymer.
7. The drug injector of claim 5 wherein the shape memory material is a shape memory alloy.
8. The drug injector of claim 7 wherein the shape memory alloy is selected from the group including: Ag—Cd, Au—Cd, Au—Cu—Zn, Cu—Al, Cu—Al—N, Cu—Zn, Cu—Zn—Al, Cu—Zn—Ga, Cu—Zn—Si, Cu—Zn—Sn, Fe—Pt, Fe—Ni, In—Cd, In—Ti, Ti—Nb, and combinations thereof.
9. The drug injector of claim 7 wherein the shape memory alloy is Ni—Ti.
10. The drug injector of claim 7 wherein the shape memory alloy structure changes phase from martensite to austenite when the potential is applied to the member.
11. The drug injector of claim 1 wherein the chamber is coupled to a reservoir, the reservoir containing enough drug for multiple injections.
12. The drug injector of claim 1 further comprising a sterile interface positioned between the nozzle and the body.
13. The drug injector of claim 12 wherein the sterile interface is a flexible ribbon supplied from a roller, a new sterile portion of the ribbon being positioned over the nozzle after an injection.
14. The drug injector of claim 1 wherein the chamber receives a vial, the chamber being located within the vial, and the nozzle being associated with the vial.
15. The drug injector of claim 14 wherein a plurality of vials are sequentially supplied to the injector, a new vial being positioned in the injector after an injection.
16. The drug injector of claim 1 further comprising:
a skin sensor that measures skin properties of the body; and
a servo-controller coupled to the drug injector and the skin sensor, the servo-controller adjusting the injection pressure of the drug injector to selectively deliver the drug to the body based on the skin properties.
17. A drug injector configured to inject a drug to a depth beneath an animal's skin comprising:
a housing;
a vial positioned within the housing, the vial holding a drug to be injected into a biological body;
a nozzle associated with the housing through which the drug is injected;
a piston positioned within the housing; and
an actuator coupled to the piston, the actuator including a member of shape memory alloy, the actuator moving the piston towards the nozzle of the vial when a potential is applied to the member to expel the drug out of the vial through the nozzle, thereby delivering the drug to a depth beneath an animal's skin.
18. The apparatus of claim 17 wherein the drug is expelled through the nozzle with an injection velocity of at least about 100 meters per second.
19. A drug injector configured to inject a drug to a depth beneath an animal's skin comprising:
a housing;
a vial positioned within the housing, the vial holding a drug to be injected into a biological body;
a nozzle associated with the vial through which the drug is injected;
a piston positioned within the housing;
an actuator coupled to the piston, the actuator including a member of shape memory alloy, the actuator moving the piston towards the nozzle of the vial when a potential is applied to the member to expel the drug out of the vial through the nozzle;
a skin sensor that measures skin properties of the body; and
a servo-controller coupled to the actuator and the skin sensor, the servo-controller adjusting the injection pressure of the drug injector based on the skin properties.
20. A method of injecting a drug into a biological body comprising:
holding a drug in a chamber, the chamber being in fluid communication with an nozzle through which the drug is injected;
applying a potential to a member of an actuator, the member contracting upon the application of the potential, the actuator being coupled to a piston, the actuator moving the piston towards the nozzle when the potential is applied to the member; and
expelling the drug from the chamber through the nozzle as the piston moves towards the chamber.
21. The method of claim 20 wherein the drug is expelled through the nozzle at an injection velocity of at least about 100 meters per second.
22. The method of claim 20 further comprising moving the piston away from the nozzle with a spring when the potential is removed from the actuator.
23. The method of claim 20 further comprising supplying drug from a reservoir coupled to the chamber.
24. The method of claim 20 further comprising positioning a sterile interface positioned between the nozzle and the body.
25. The method of claim 24 further comprising supplying the sterile interface as a ribbon from a roller, a new sterile portion of the ribbon being positioned over the nozzle after an injection.
26. The method of claim 20 further comprising receiving a vial in the chamber, the chamber being contained within the vial, and the nozzle being associated with the vial.
27. The method of claim 26 further comprising supplying a plurality of vials to the injector in a sequential manner, a new vial being positioned in the injector after an injection.
28. The method of claim 20 wherein the member includes a shaped memory material.
29. The method of claim 28 wherein the shape memory material is a shape memory polymer.
30. The method of claim 28 wherein the shape memory material is a shape memory alloy.
31. The method of claim 30 wherein the shape memory alloy is selected from the group including: Ag—Cd, Au—Cd, Au—Cu—Zn, Cu—Al, Cu—Al—N, Cu—Zn, Cu—Zn—Al, Cu—Zn—Ga, Cu—Zn—Si, Cu—Zn—Sn, Fe—Pt, Fe—Ni, In—Cd, In—Ti, Ti—Nb, and combinations thereof.
32. The method of claim 20 wherein the member is one or more wires of shape memory alloy.
33. The method of claim 32 wherein the shape memory alloy is Ni—Ti.
34. A method of injecting a drug into a biological body comprising:
positioning a drug vial in a housing, the vial containing a drug to be injected into the body, and having an nozzle through which the drug is injected;
applying a potential to a member of shape memory alloy, the member forming part of an actuator coupled to a piston positioned in the housing, the actuator moving the piston towards the nozzle when the potential is applied to the member; and
expelling the drug from the vial through the nozzle as the piston moves towards the nozzle.
35. The method of claim 34 wherein the drug is expelled through the nozzle at an injection velocity of at least about 100 meters per second.
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Cited By (33)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2006086742A2 (en) * | 2005-02-09 | 2006-08-17 | Nanopharmatix, Inc. | Microstream injector |
US20060258986A1 (en) * | 2005-02-11 | 2006-11-16 | Hunter Ian W | Controlled needle-free transport |
US20070191758A1 (en) * | 2005-02-11 | 2007-08-16 | Hunter Ian W | Controlled needle-free transport |
US20100004558A1 (en) * | 2007-06-29 | 2010-01-07 | Piezo Resonance Innovations, Inc. | Medical tool for reduced penetration force with feedback means |
US20100004624A1 (en) * | 2002-09-06 | 2010-01-07 | Massachusetts Institute Of Technology | Measuring properties of an anatomical body |
US20100016827A1 (en) * | 2006-09-01 | 2010-01-21 | Massachusetts Institute Of Technology | Needle-free injector device with autoloading capability |
WO2010123495A1 (en) * | 2009-04-21 | 2010-10-28 | Dutcher Michael H | Injection safety mechanism |
US20110054354A1 (en) * | 2009-09-01 | 2011-03-03 | Massachusetts Institute Of Technology | Nonlinear System Identification Techniques and Devices for Discovering Dynamic and Static Tissue Properties |
US20110054355A1 (en) * | 2009-09-01 | 2011-03-03 | Hunter Ian W | Identification Techniques and Device for Testing the Efficacy of Beauty Care Products and Cosmetics |
US20110082388A1 (en) * | 2008-07-09 | 2011-04-07 | Massachusetts Institute Of Technology | Bi-directional motion of a lorentz-force actuated needle-free injector (nfi) |
US20110131964A1 (en) * | 2009-12-04 | 2011-06-09 | Cameron International Corporation | Shape memory alloy powered hydraulic accumulator |
US20120017583A1 (en) * | 2010-07-22 | 2012-01-26 | University Of Houston | Shape memory alloy powered hydraulic accumulator having actuation plates |
US20120095435A1 (en) * | 2010-10-07 | 2012-04-19 | Massachusetts Institute Of Technology | Delivery of a solid body and/or a fluid using a linear lorentz-force actuated needle-free jet injection system |
WO2012109621A1 (en) * | 2011-02-10 | 2012-08-16 | Actuated Medical, Inc. | Medical tool with electromechanical control and feedback |
US20130046233A1 (en) * | 2001-10-24 | 2013-02-21 | Zogenix, Inc. | Needleless injector |
US8668675B2 (en) | 2010-11-03 | 2014-03-11 | Flugen, Inc. | Wearable drug delivery device having spring drive and sliding actuation mechanism |
US8695334B2 (en) | 2010-07-22 | 2014-04-15 | University Of Houston | Shape memory alloy powered hydraulic accumulator having wire clamps |
US8701406B2 (en) | 2010-07-22 | 2014-04-22 | University Of Houston | Shape memory alloy powered hydraulic accumulator having wire guides |
US8740838B2 (en) | 2010-10-07 | 2014-06-03 | Massachusetts Institute Of Technology | Injection methods using a servo-controlled needle-free injector |
US9144434B1 (en) | 2010-09-29 | 2015-09-29 | Rodan & Fields, Llc | Methods and compositions for treating skin |
US9238102B2 (en) | 2009-09-10 | 2016-01-19 | Medipacs, Inc. | Low profile actuator and improved method of caregiver controlled administration of therapeutics |
US9333060B2 (en) | 2009-12-15 | 2016-05-10 | Massachusetts Institute Of Technology | Plaque removal and differentiation of tooth and gum |
US9500186B2 (en) | 2010-02-01 | 2016-11-22 | Medipacs, Inc. | High surface area polymer actuator with gas mitigating components |
GB2497437B (en) * | 2010-07-22 | 2017-11-08 | Univ Houston | Actuation of shape memory alloy materials using ultracapacitors |
US9987468B2 (en) | 2007-06-29 | 2018-06-05 | Actuated Medical, Inc. | Reduced force device for intravascular access and guidewire placement |
US9995295B2 (en) | 2007-12-03 | 2018-06-12 | Medipacs, Inc. | Fluid metering device |
US10000605B2 (en) | 2012-03-14 | 2018-06-19 | Medipacs, Inc. | Smart polymer materials with excess reactive molecules |
US10208158B2 (en) | 2006-07-10 | 2019-02-19 | Medipacs, Inc. | Super elastic epoxy hydrogel |
US10219832B2 (en) | 2007-06-29 | 2019-03-05 | Actuated Medical, Inc. | Device and method for less forceful tissue puncture |
US10940292B2 (en) | 2015-07-08 | 2021-03-09 | Actuated Medical, Inc. | Reduced force device for intravascular access and guidewire placement |
US11666741B1 (en) * | 2021-06-01 | 2023-06-06 | TruCelium Inc. | Method for delivering matter into the human body |
US11793543B2 (en) | 2015-09-18 | 2023-10-24 | Obvius Robotics, Inc. | Device and method for automated insertion of penetrating member |
US11806096B2 (en) | 2018-12-04 | 2023-11-07 | Mako Surgical Corp. | Mounting system with sterile barrier assembly for use in coupling surgical components |
Families Citing this family (42)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7591834B2 (en) * | 2004-03-26 | 2009-09-22 | Lawrence Livermore National Security, Llc | Shape memory system with integrated actuation using embedded particles |
ATE490037T1 (en) | 2004-08-16 | 2010-12-15 | Functional Microstructures Ltd | METHOD FOR PRODUCING A MICRONEEDLE OR A MICROIMPLANT |
NZ560516A (en) | 2005-02-01 | 2010-12-24 | Intelliject Inc | A delivery system where a medicant is automatically delivered on activation as well as a recorded instruction |
AU2012201481C1 (en) * | 2005-02-01 | 2016-01-07 | Kaleo, Inc. | Devices, systems, and methods for medicament delivery |
WO2006108185A1 (en) * | 2005-04-07 | 2006-10-12 | 3M Innovative Properties Company | System and method for tool feedback sensing |
AU2006279244B2 (en) * | 2005-08-05 | 2011-09-15 | Cobbett Technologies Pty. Ltd. | Non-surgical mulesing applicator |
JP5241714B2 (en) | 2006-07-07 | 2013-07-17 | プロテウス デジタル ヘルス, インコーポレイテッド | Smart parenteral delivery system |
WO2008052221A2 (en) * | 2006-10-27 | 2008-05-02 | Aretais, Inc. | Use of coherent raman techniques for medical diagnostic and therapeutic purposes, and calibration techniques for same |
JP4922056B2 (en) * | 2007-05-01 | 2012-04-25 | 伊藤超短波株式会社 | Muscle hardness tester |
WO2008154504A2 (en) | 2007-06-08 | 2008-12-18 | William Marsh Rice University | System and method for intra-body communication |
US9125979B2 (en) | 2007-10-25 | 2015-09-08 | Proteus Digital Health, Inc. | Fluid transfer port information system |
WO2009067463A1 (en) | 2007-11-19 | 2009-05-28 | Proteus Biomedical, Inc. | Body-associated fluid transport structure evaluation devices |
US8986253B2 (en) | 2008-01-25 | 2015-03-24 | Tandem Diabetes Care, Inc. | Two chamber pumps and related methods |
US8408421B2 (en) | 2008-09-16 | 2013-04-02 | Tandem Diabetes Care, Inc. | Flow regulating stopcocks and related methods |
US8650937B2 (en) | 2008-09-19 | 2014-02-18 | Tandem Diabetes Care, Inc. | Solute concentration measurement device and related methods |
AU2009322967B2 (en) * | 2008-12-05 | 2015-06-11 | Ams Research Corporation | Devices, systems and methods for delivering fluid to tissue |
EP2724739B1 (en) | 2009-07-30 | 2015-07-01 | Tandem Diabetes Care, Inc. | Portable infusion pump system |
JP5841951B2 (en) | 2010-02-01 | 2016-01-13 | プロテウス デジタル ヘルス, インコーポレイテッド | Data collection system |
CN102905612A (en) | 2010-02-01 | 2013-01-30 | 普罗秋斯数字健康公司 | Two-wrist data gathering system |
WO2011116388A1 (en) * | 2010-03-19 | 2011-09-22 | Nanostar Health Corporation | Body fluid sampling/fluid delivery device |
WO2011163264A2 (en) * | 2010-06-21 | 2011-12-29 | Candela Corporation | Driving microneedle arrays into skin and delivering rf energy |
WO2012112985A2 (en) * | 2011-02-18 | 2012-08-23 | The General Hospital Corporation | System and methods for evaluating vocal function using an impedance-based inverse filtering of neck surface acceleration |
WO2013034775A1 (en) * | 2011-09-09 | 2013-03-14 | The Provost, Fellows, Foundation Scholars, And The Other Members Of Board, Of The College Of The Holy And Undivided Trinity Of Queen Elizabeth, Near Dublin | System and method to determine tissue compression |
US20130304017A1 (en) * | 2012-05-09 | 2013-11-14 | Bioject, Inc. | Peformance of needle-free injection according to known relationships |
US9180242B2 (en) | 2012-05-17 | 2015-11-10 | Tandem Diabetes Care, Inc. | Methods and devices for multiple fluid transfer |
US9555186B2 (en) | 2012-06-05 | 2017-01-31 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
WO2014106056A2 (en) | 2012-12-27 | 2014-07-03 | Kaleo, Inc. | Devices, systems and methods for locating and interacting with medicament delivery systems |
US9173998B2 (en) | 2013-03-14 | 2015-11-03 | Tandem Diabetes Care, Inc. | System and method for detecting occlusions in an infusion pump |
EP3065586A4 (en) * | 2013-11-05 | 2017-06-21 | The Board Of Regents Of The Nevada System Of Higher Education On Behalf Of The University Of Nevada | Actuated foot orthotic with sensors |
US10737032B2 (en) * | 2015-11-25 | 2020-08-11 | Portal Instruments, Inc. | Needle-free transdermal injection device |
DE102015122069A1 (en) * | 2015-12-17 | 2017-06-22 | Henke-Sass, Wolf Gmbh | Injection device for administering an injection to an animal |
US9724473B2 (en) * | 2016-01-12 | 2017-08-08 | Nickolas Peter Demas | Multi-directional low-displacement force sensor |
US20170312456A1 (en) * | 2016-04-27 | 2017-11-02 | David Bruce PHILLIPS | Skin Desensitizing Device |
TWI602541B (en) * | 2016-08-19 | 2017-10-21 | 章學賢 | Soft tissue characteristic measurement system |
EP3338835A1 (en) * | 2016-12-23 | 2018-06-27 | Sanofi-Aventis Deutschland GmbH | Medicament delivery device |
US10332623B2 (en) | 2017-01-17 | 2019-06-25 | Kaleo, Inc. | Medicament delivery devices with wireless connectivity and event detection |
US11929160B2 (en) | 2018-07-16 | 2024-03-12 | Kaleo, Inc. | Medicament delivery devices with wireless connectivity and compliance detection |
JPWO2020149152A1 (en) * | 2019-01-16 | 2021-11-25 | 株式会社ダイセル | Needleless syringe |
US10985951B2 (en) | 2019-03-15 | 2021-04-20 | The Research Foundation for the State University | Integrating Volterra series model and deep neural networks to equalize nonlinear power amplifiers |
US10855159B1 (en) * | 2020-02-27 | 2020-12-01 | John Sabah Gewarges | Coil regeneration device and method of use |
CN113662701B (en) * | 2021-07-15 | 2024-01-26 | 北京思灵机器人科技有限责任公司 | Firing device and automatic injection equipment |
NL2030901B1 (en) * | 2022-02-11 | 2023-08-18 | Univ Twente | Material characterization method |
Citations (50)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2754818A (en) * | 1950-06-24 | 1956-07-17 | Scherer Corp R P | Hypo jet injector |
US2928390A (en) * | 1957-07-15 | 1960-03-15 | Scherer Corp R P | Multi-dose hypodermic injector |
US3057349A (en) * | 1959-12-14 | 1962-10-09 | Ismach Aaron | Multi-dose jet injection device |
US3574431A (en) * | 1968-12-23 | 1971-04-13 | Kimberly Clark Co | Continuous roll towel dispenser |
US3659600A (en) * | 1970-02-24 | 1972-05-02 | Estin Hans H | Magnetically operated capsule for administering drugs |
US3815594A (en) * | 1972-08-10 | 1974-06-11 | N Doherty | Needleless inoculator |
US3977402A (en) * | 1975-03-25 | 1976-08-31 | William Floyd Pike | Injection apparatus and method with automatic aspiration feature |
US4108177A (en) * | 1976-04-23 | 1978-08-22 | Michel Louis Paul Pistor | Automatic injector device |
US4206769A (en) * | 1978-03-14 | 1980-06-10 | Shabtay Dikstein | Measurement of surface properties |
US4435173A (en) * | 1982-03-05 | 1984-03-06 | Delta Medical Industries | Variable rate syringe pump for insulin delivery |
US4436173A (en) * | 1981-05-15 | 1984-03-13 | Honda Giken Kogyo Kabushiki Kaisha | Shaft drive apparatus for motorized two-wheeled vehicle |
US4447225A (en) * | 1982-03-22 | 1984-05-08 | Taff Barry E | Multidose jet injector |
US4744841A (en) * | 1986-04-21 | 1988-05-17 | Thomas Thomas L | Apparatus and method for repairing glass bodies |
US4777599A (en) * | 1985-02-26 | 1988-10-11 | Gillette Company | Viscoelastometry of skin using shear wave propagation |
US4886499A (en) * | 1986-12-18 | 1989-12-12 | Hoffmann-La Roche Inc. | Portable injection appliance |
US5092901A (en) * | 1990-06-06 | 1992-03-03 | The Royal Institution For The Advancement Of Learning (Mcgill University) | Shape memory alloy fibers having rapid twitch response |
US5116313A (en) * | 1989-08-31 | 1992-05-26 | Her Majesty The Queen In Right Of Canada, As Represented By The National Research Council | Variable intensity remote controlled needleless injectors |
US5318522A (en) * | 1987-06-08 | 1994-06-07 | Antonio Nicholas F D | Hypodermic fluid dispenser |
US5354273A (en) * | 1992-12-14 | 1994-10-11 | Mallinckrodt Medical, Inc. | Delivery apparatus with pressure controlled delivery |
US5405614A (en) * | 1992-04-08 | 1995-04-11 | International Medical Associates, Inc. | Electronic transdermal drug delivery system |
US5478328A (en) * | 1992-05-22 | 1995-12-26 | Silverman; David G. | Methods of minimizing disease transmission by used hypodermic needles, and hypodermic needles adapted for carrying out the method |
US5480381A (en) * | 1991-08-23 | 1996-01-02 | Weston Medical Limited | Needle-less injector |
US5505697A (en) * | 1994-01-14 | 1996-04-09 | Mckinnon, Jr.; Charles N. | Electrically powered jet injector |
US5622482A (en) * | 1994-10-31 | 1997-04-22 | Daewood Electronics, Co., Ltd. | Pump using shape memory alloys |
US5694920A (en) * | 1996-01-25 | 1997-12-09 | Abrams; Andrew L. | Inhalation device |
US5722953A (en) * | 1996-02-29 | 1998-03-03 | Medi-Ject Corporation | Nozzle assembly for injection device |
US5783684A (en) * | 1995-09-11 | 1998-07-21 | Beckman Instruments, Inc. | Oxidizing reagent for use in oligonucleotide synthesis |
US5840062A (en) * | 1995-11-08 | 1998-11-24 | Gumaste; Anand V. | Solid state fluid delivery system |
US5919167A (en) * | 1998-04-08 | 1999-07-06 | Ferring Pharmaceuticals | Disposable micropump |
US6004287A (en) * | 1997-09-23 | 1999-12-21 | Loomis; Dale J | Biolistic apparatus for delivering substances into cells and tissues |
US6037682A (en) * | 1998-01-08 | 2000-03-14 | Etrema Products, Inc. | Integrated multi-mode transducer and method |
US6048337A (en) * | 1992-01-07 | 2000-04-11 | Principal Ab | Transdermal perfusion of fluids |
US6056716A (en) * | 1987-06-08 | 2000-05-02 | D'antonio Consultants International Inc. | Hypodermic fluid dispenser |
US6074360A (en) * | 1997-07-21 | 2000-06-13 | Boehringer Mannheim Gmbh | Electromagnetic transdermal injection device and methods related thereto |
US6203521B1 (en) * | 1998-12-21 | 2001-03-20 | Ferton Holding Sa | Ejection device for the high-pressure ejection of a liquid |
US6258062B1 (en) * | 1999-02-25 | 2001-07-10 | Joseph M. Thielen | Enclosed container power supply for a needleless injector |
US6272857B1 (en) * | 1999-08-06 | 2001-08-14 | Ut-Battelle, Llc | Shape memory alloy actuator |
US6375638B2 (en) * | 1999-02-12 | 2002-04-23 | Medtronic Minimed, Inc. | Incremental motion pump mechanisms powered by shape memory alloy wire or the like |
US6375624B1 (en) * | 1996-06-14 | 2002-04-23 | Medrad, Inc. | Extravasation detector using microwave radiometry |
US6408204B1 (en) * | 1999-07-28 | 2002-06-18 | Medrad, Inc. | Apparatuses and methods for extravasation detection |
US20020145364A1 (en) * | 1999-07-05 | 2002-10-10 | Albert Gaide | Towel loop formation in a hand towel dispenser |
US6565532B1 (en) * | 2000-07-12 | 2003-05-20 | The Procter & Gamble Company | Microneedle apparatus used for marking skin and for dispensing semi-permanent subcutaneous makeup |
US6611707B1 (en) * | 1999-06-04 | 2003-08-26 | Georgia Tech Research Corporation | Microneedle drug delivery device |
US6626871B1 (en) * | 1999-10-11 | 2003-09-30 | Felton International, Inc. | Method and apparatus for removing cap from medical device |
US6656159B2 (en) * | 2002-04-23 | 2003-12-02 | Insulet Corporation | Dispenser for patient infusion device |
US6678556B1 (en) * | 1998-07-13 | 2004-01-13 | Genetronics, Inc. | Electrical field therapy with reduced histopathological change in muscle |
US6723072B2 (en) * | 2002-06-06 | 2004-04-20 | Insulet Corporation | Plunger assembly for patient infusion device |
US6743211B1 (en) * | 1999-11-23 | 2004-06-01 | Georgia Tech Research Corporation | Devices and methods for enhanced microneedle penetration of biological barriers |
US6770054B1 (en) * | 1999-11-23 | 2004-08-03 | Felton International, Inc. | Injector assembly with driving means and locking means |
US20050022806A1 (en) * | 2001-06-11 | 2005-02-03 | Beaumont Gary Robert | Medicament dispenser |
Family Cites Families (41)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2194535A (en) * | 1937-04-15 | 1940-03-26 | Vedee Corp | Electric translating device |
GB686343A (en) | 1950-09-26 | 1953-01-21 | Becton Dickinson Co | Improvements relating to hypodermic injection devices |
JPS6446344A (en) | 1987-08-14 | 1989-02-20 | Nec Corp | Group broadcast communication system |
DE3832690C1 (en) * | 1988-09-26 | 1990-04-12 | Courage + Khazaka Electronic Gmbh, 5000 Koeln, De | |
GB2229497B (en) * | 1989-03-10 | 1992-06-03 | Graseby Medical Ltd | Infusion pump |
DK94990A (en) | 1990-04-17 | 1991-10-18 | Skintech Holdings Aps | PROCEDURE AND APPARATUS FOR INTRODUCTION-FREE MEASUREMENT OF AT LEAST ONE MECHANICAL PROPERTY OF BLOOD BIOLOGICAL TISSUE |
JPH0556934A (en) * | 1991-09-04 | 1993-03-09 | Nikon Corp | Probe for biodiagnosis using super-magnetostriction material |
US5347186A (en) * | 1992-05-26 | 1994-09-13 | Mcq Associates, Inc. | Linear motion electric power generator |
US5242408A (en) * | 1992-09-23 | 1993-09-07 | Becton, Dickinson And Company | Method and apparatus for determining pressure and detecting occlusions in a syringe pump |
JPH06327639A (en) | 1993-05-27 | 1994-11-29 | Copal Co Ltd | Apparatus and method for inspection of skin |
ATE254939T1 (en) | 1993-07-31 | 2003-12-15 | Aradigm Corp | NEEDLELESS INJECTOR |
US5641391A (en) | 1995-05-15 | 1997-06-24 | Hunter; Ian W. | Three dimensional microfabrication by localized electrodeposition and etching |
US5820373A (en) * | 1995-08-29 | 1998-10-13 | Koichi Okano | Cleaning device for periodontal pocket |
EE03374B1 (en) * | 1996-03-27 | 2001-04-16 | Tartu �likool | Method and device for recording soft biological tissue self-oscillation - myometer |
BR9711214A (en) | 1996-08-23 | 2000-01-11 | Osteobiologics Inc | Device and process for measuring a compression property of a material, and processes for determining cartilage health or disease and for making the device. |
JP3951257B2 (en) * | 1996-11-08 | 2007-08-01 | 株式会社井元製作所 | Muscle hardness meter |
JP3907267B2 (en) | 1997-05-14 | 2007-04-18 | 株式会社資生堂 | Vibrator with built-in sensor for measuring mechanical properties of biological surface |
US6030399A (en) * | 1997-06-04 | 2000-02-29 | Spectrx, Inc. | Fluid jet blood sampling device and methods |
CN1320050A (en) * | 1998-07-27 | 2001-10-31 | 梅迪-杰克特公司 | Loading mechanism for medical injector assembly |
ATE304872T1 (en) * | 1998-10-16 | 2005-10-15 | Kolbe Eckard | PRESSURE JET INJECTOR FOR PAINLESS INJECTION OF MEDICATIONS |
US6164966A (en) * | 1999-03-17 | 2000-12-26 | Medjet, Inc. | Removal of dental caries with high speed water jet |
JP3326791B2 (en) | 1999-08-10 | 2002-09-24 | 花王株式会社 | Skin property measurement probe |
AU1194701A (en) | 1999-10-11 | 2001-04-23 | Victor N. Katov | Method and apparatus for removing cap from medical device |
DE60029338T2 (en) | 1999-11-23 | 2007-07-12 | Felton International, Inc., Lenexa | INJECTOR ARRANGEMENT WITH DRIVE AND LOCKING MEANS |
JP2001212087A (en) | 2000-01-31 | 2001-08-07 | Axiom Co Ltd | Equipment for calculating age of skin and its method |
DE50010517D1 (en) * | 2000-06-21 | 2005-07-14 | Courage Brewing Ltd | Measuring device for measuring the elastic properties of a surface structure |
US7429258B2 (en) | 2001-10-26 | 2008-09-30 | Massachusetts Institute Of Technology | Microneedle transport device |
US6939323B2 (en) | 2001-10-26 | 2005-09-06 | Massachusetts Institute Of Technology | Needleless injector |
JP4154720B2 (en) | 2002-07-04 | 2008-09-24 | 株式会社ウェイブサイバー | Measuring device for mechanical properties of viscoelastic surface |
AU2003272279B2 (en) * | 2002-09-06 | 2007-04-26 | Massachusetts Institute Of Technology | Measuring properties of an anatomical body |
AU2003216706A1 (en) | 2002-12-27 | 2004-07-22 | Department Of Science And Technology | Device for measurement of tissue hardness |
JP2004239686A (en) | 2003-02-04 | 2004-08-26 | Shiseido Co Ltd | Apparatus for measuring hardness |
US20080009788A1 (en) | 2005-02-11 | 2008-01-10 | Hunter Ian W | Surface injection device |
US7833189B2 (en) * | 2005-02-11 | 2010-11-16 | Massachusetts Institute Of Technology | Controlled needle-free transport |
US20060258986A1 (en) * | 2005-02-11 | 2006-11-16 | Hunter Ian W | Controlled needle-free transport |
CA2600855C (en) * | 2005-03-09 | 2011-11-22 | The Procter & Gamble Company | Sensor responsive electric toothbrushes and methods of use |
WO2007124038A2 (en) * | 2006-04-20 | 2007-11-01 | Dentatek Corporation | Apparatus and methods for treating root canals of teeth |
JP5284962B2 (en) | 2006-09-01 | 2013-09-11 | マサチューセッツ インスティテュート オブ テクノロジー | Needleless syringe with automatic filling function |
WO2008156515A2 (en) * | 2007-04-03 | 2008-12-24 | The Regents Of The University Of California | Improved methods and instruments for materials testing |
US8758271B2 (en) * | 2009-09-01 | 2014-06-24 | Massachusetts Institute Of Technology | Nonlinear system identification techniques and devices for discovering dynamic and static tissue properties |
WO2011028716A1 (en) * | 2009-09-01 | 2011-03-10 | Massachusetts Institute Of Technology | Nonlinear system identification technique for testing the efficacy of skin care products |
-
2003
- 2003-09-08 AU AU2003272279A patent/AU2003272279B2/en not_active Ceased
- 2003-09-08 US US10/657,734 patent/US20040106894A1/en not_active Abandoned
- 2003-09-08 JP JP2004569992A patent/JP2005537907A/en active Pending
- 2003-09-08 AU AU2003270355A patent/AU2003270355A1/en not_active Abandoned
- 2003-09-08 EP EP03754455A patent/EP1534132B1/en not_active Expired - Lifetime
- 2003-09-08 EP EP03752043A patent/EP1534365A2/en not_active Withdrawn
- 2003-09-08 US US10/657,724 patent/US7530975B2/en active Active
- 2003-09-08 CA CA2497815A patent/CA2497815C/en not_active Expired - Fee Related
- 2003-09-08 WO PCT/US2003/027909 patent/WO2004022138A2/en not_active Application Discontinuation
- 2003-09-08 AT AT03754455T patent/ATE510494T1/en not_active IP Right Cessation
- 2003-09-08 WO PCT/US2003/027907 patent/WO2004021882A2/en active IP Right Grant
-
2009
- 2009-05-12 US US12/464,774 patent/US8105270B2/en not_active Expired - Fee Related
Patent Citations (50)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2754818A (en) * | 1950-06-24 | 1956-07-17 | Scherer Corp R P | Hypo jet injector |
US2928390A (en) * | 1957-07-15 | 1960-03-15 | Scherer Corp R P | Multi-dose hypodermic injector |
US3057349A (en) * | 1959-12-14 | 1962-10-09 | Ismach Aaron | Multi-dose jet injection device |
US3574431A (en) * | 1968-12-23 | 1971-04-13 | Kimberly Clark Co | Continuous roll towel dispenser |
US3659600A (en) * | 1970-02-24 | 1972-05-02 | Estin Hans H | Magnetically operated capsule for administering drugs |
US3815594A (en) * | 1972-08-10 | 1974-06-11 | N Doherty | Needleless inoculator |
US3977402A (en) * | 1975-03-25 | 1976-08-31 | William Floyd Pike | Injection apparatus and method with automatic aspiration feature |
US4108177A (en) * | 1976-04-23 | 1978-08-22 | Michel Louis Paul Pistor | Automatic injector device |
US4206769A (en) * | 1978-03-14 | 1980-06-10 | Shabtay Dikstein | Measurement of surface properties |
US4436173A (en) * | 1981-05-15 | 1984-03-13 | Honda Giken Kogyo Kabushiki Kaisha | Shaft drive apparatus for motorized two-wheeled vehicle |
US4435173A (en) * | 1982-03-05 | 1984-03-06 | Delta Medical Industries | Variable rate syringe pump for insulin delivery |
US4447225A (en) * | 1982-03-22 | 1984-05-08 | Taff Barry E | Multidose jet injector |
US4777599A (en) * | 1985-02-26 | 1988-10-11 | Gillette Company | Viscoelastometry of skin using shear wave propagation |
US4744841A (en) * | 1986-04-21 | 1988-05-17 | Thomas Thomas L | Apparatus and method for repairing glass bodies |
US4886499A (en) * | 1986-12-18 | 1989-12-12 | Hoffmann-La Roche Inc. | Portable injection appliance |
US5318522A (en) * | 1987-06-08 | 1994-06-07 | Antonio Nicholas F D | Hypodermic fluid dispenser |
US6056716A (en) * | 1987-06-08 | 2000-05-02 | D'antonio Consultants International Inc. | Hypodermic fluid dispenser |
US5116313A (en) * | 1989-08-31 | 1992-05-26 | Her Majesty The Queen In Right Of Canada, As Represented By The National Research Council | Variable intensity remote controlled needleless injectors |
US5092901A (en) * | 1990-06-06 | 1992-03-03 | The Royal Institution For The Advancement Of Learning (Mcgill University) | Shape memory alloy fibers having rapid twitch response |
US5480381A (en) * | 1991-08-23 | 1996-01-02 | Weston Medical Limited | Needle-less injector |
US6048337A (en) * | 1992-01-07 | 2000-04-11 | Principal Ab | Transdermal perfusion of fluids |
US5405614A (en) * | 1992-04-08 | 1995-04-11 | International Medical Associates, Inc. | Electronic transdermal drug delivery system |
US5478328A (en) * | 1992-05-22 | 1995-12-26 | Silverman; David G. | Methods of minimizing disease transmission by used hypodermic needles, and hypodermic needles adapted for carrying out the method |
US5354273A (en) * | 1992-12-14 | 1994-10-11 | Mallinckrodt Medical, Inc. | Delivery apparatus with pressure controlled delivery |
US5505697A (en) * | 1994-01-14 | 1996-04-09 | Mckinnon, Jr.; Charles N. | Electrically powered jet injector |
US5622482A (en) * | 1994-10-31 | 1997-04-22 | Daewood Electronics, Co., Ltd. | Pump using shape memory alloys |
US5783684A (en) * | 1995-09-11 | 1998-07-21 | Beckman Instruments, Inc. | Oxidizing reagent for use in oligonucleotide synthesis |
US5840062A (en) * | 1995-11-08 | 1998-11-24 | Gumaste; Anand V. | Solid state fluid delivery system |
US5694920A (en) * | 1996-01-25 | 1997-12-09 | Abrams; Andrew L. | Inhalation device |
US5722953A (en) * | 1996-02-29 | 1998-03-03 | Medi-Ject Corporation | Nozzle assembly for injection device |
US6375624B1 (en) * | 1996-06-14 | 2002-04-23 | Medrad, Inc. | Extravasation detector using microwave radiometry |
US6074360A (en) * | 1997-07-21 | 2000-06-13 | Boehringer Mannheim Gmbh | Electromagnetic transdermal injection device and methods related thereto |
US6004287A (en) * | 1997-09-23 | 1999-12-21 | Loomis; Dale J | Biolistic apparatus for delivering substances into cells and tissues |
US6037682A (en) * | 1998-01-08 | 2000-03-14 | Etrema Products, Inc. | Integrated multi-mode transducer and method |
US5919167A (en) * | 1998-04-08 | 1999-07-06 | Ferring Pharmaceuticals | Disposable micropump |
US6678556B1 (en) * | 1998-07-13 | 2004-01-13 | Genetronics, Inc. | Electrical field therapy with reduced histopathological change in muscle |
US6203521B1 (en) * | 1998-12-21 | 2001-03-20 | Ferton Holding Sa | Ejection device for the high-pressure ejection of a liquid |
US6375638B2 (en) * | 1999-02-12 | 2002-04-23 | Medtronic Minimed, Inc. | Incremental motion pump mechanisms powered by shape memory alloy wire or the like |
US6258062B1 (en) * | 1999-02-25 | 2001-07-10 | Joseph M. Thielen | Enclosed container power supply for a needleless injector |
US6611707B1 (en) * | 1999-06-04 | 2003-08-26 | Georgia Tech Research Corporation | Microneedle drug delivery device |
US20020145364A1 (en) * | 1999-07-05 | 2002-10-10 | Albert Gaide | Towel loop formation in a hand towel dispenser |
US6408204B1 (en) * | 1999-07-28 | 2002-06-18 | Medrad, Inc. | Apparatuses and methods for extravasation detection |
US6272857B1 (en) * | 1999-08-06 | 2001-08-14 | Ut-Battelle, Llc | Shape memory alloy actuator |
US6626871B1 (en) * | 1999-10-11 | 2003-09-30 | Felton International, Inc. | Method and apparatus for removing cap from medical device |
US6743211B1 (en) * | 1999-11-23 | 2004-06-01 | Georgia Tech Research Corporation | Devices and methods for enhanced microneedle penetration of biological barriers |
US6770054B1 (en) * | 1999-11-23 | 2004-08-03 | Felton International, Inc. | Injector assembly with driving means and locking means |
US6565532B1 (en) * | 2000-07-12 | 2003-05-20 | The Procter & Gamble Company | Microneedle apparatus used for marking skin and for dispensing semi-permanent subcutaneous makeup |
US20050022806A1 (en) * | 2001-06-11 | 2005-02-03 | Beaumont Gary Robert | Medicament dispenser |
US6656159B2 (en) * | 2002-04-23 | 2003-12-02 | Insulet Corporation | Dispenser for patient infusion device |
US6723072B2 (en) * | 2002-06-06 | 2004-04-20 | Insulet Corporation | Plunger assembly for patient infusion device |
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US8777944B2 (en) | 2007-06-29 | 2014-07-15 | Actuated Medical, Inc. | Medical tool for reduced penetration force with feedback means |
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Also Published As
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WO2004022138A2 (en) | 2004-03-18 |
AU2003270355A1 (en) | 2004-03-29 |
EP1534365A2 (en) | 2005-06-01 |
JP2005537907A (en) | 2005-12-15 |
CA2497815C (en) | 2013-06-11 |
ATE510494T1 (en) | 2011-06-15 |
AU2003272279A1 (en) | 2004-03-29 |
US20100004624A1 (en) | 2010-01-07 |
WO2004022138A3 (en) | 2004-08-05 |
WO2004021882A2 (en) | 2004-03-18 |
US8105270B2 (en) | 2012-01-31 |
EP1534132A2 (en) | 2005-06-01 |
CA2497815A1 (en) | 2004-03-18 |
US20040106893A1 (en) | 2004-06-03 |
EP1534132B1 (en) | 2011-05-25 |
AU2003272279B2 (en) | 2007-04-26 |
WO2004021882A3 (en) | 2004-07-15 |
US7530975B2 (en) | 2009-05-12 |
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