US20100069835A1 - Knitted catheter - Google Patents
Knitted catheter Download PDFInfo
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- US20100069835A1 US20100069835A1 US12/549,801 US54980109A US2010069835A1 US 20100069835 A1 US20100069835 A1 US 20100069835A1 US 54980109 A US54980109 A US 54980109A US 2010069835 A1 US2010069835 A1 US 2010069835A1
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- United States
- Prior art keywords
- conductive filament
- catheter
- knitted
- medical device
- conductive
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- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
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Classifications
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- 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
- A61M25/00—Catheters; Hollow probes
- A61M25/0009—Making of catheters or other medical or surgical tubes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/0404—Electrodes for external use
- A61N1/0472—Structure-related aspects
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/0404—Electrodes for external use
- A61N1/0472—Structure-related aspects
- A61N1/0484—Garment electrodes worn by the patient
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/0526—Head electrodes
- A61N1/0529—Electrodes for brain stimulation
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- D—TEXTILES; PAPER
- D04—BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
- D04B—KNITTING
- D04B1/00—Weft knitting processes for the production of fabrics or articles not dependent on the use of particular machines; Fabrics or articles defined by such processes
- D04B1/10—Patterned fabrics or articles
- D04B1/12—Patterned fabrics or articles characterised by thread material
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2401/00—Physical properties
- D10B2401/16—Physical properties antistatic; conductive
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2403/00—Details of fabric structure established in the fabric forming process
- D10B2403/02—Cross-sectional features
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2403/00—Details of fabric structure established in the fabric forming process
- D10B2403/02—Cross-sectional features
- D10B2403/024—Fabric incorporating additional compounds
- D10B2403/0243—Fabric incorporating additional compounds enhancing functional properties
- D10B2403/02431—Fabric incorporating additional compounds enhancing functional properties with electronic components, e.g. sensors or switches
Definitions
- the present invention relates generally to catheters, and more particularly, to a knitted catheter.
- Implantable medical devices Medical devices having one or more implantable components, generally referred to as implantable medical devices, have provided a wide range of therapeutic benefits to patients over recent decades.
- One type of implantable medical device includes an implantable, hermetically sealed electronics module, and a device that interfaces with a patient's tissue, sometimes referred to as a tissue interface.
- the tissue interface may include, for example, one or more instruments, apparatus, sensors or other functional components that are permanently or temporarily implanted in a patient.
- the tissue interface is used to, for example, diagnose, monitor, and/or treat a disease or injury, or to modify a patient's anatomy or physiological process.
- Such devices are referred to herein as active implantable medical devices (AIMDs).
- AIMDs active implantable medical devices
- Implantable medical devices include an implantable tubular member, referred to herein as a catheter, having a lumen extending there through.
- Medical catheters are used by physicians to diagnose and treat a range conditions in a patient's body. Specifically, catheters are used to introduce or withdraw fluids, introduce an instrument, apparatus, or other functional component, delivering electrical stimulation signals to a patient's tissue, etc.
- a medical device comprises: an elongate tubular knitted catheter comprising at least one biocompatible, electrically non-conductive filament arranged in longitudinally adjacent substantially parallel rows each stitched to an adjacent row, wherein the tubular catheter has an inner diameter that is sufficient to receive at least one instrument.
- a method for manufacturing a knitted tubular catheter comprises: providing at least one biocompatible, electrically non-conductive filament; and knitting the at least one non-conductive filament into an elongate tube of longitudinally adjacent substantially parallel rows, each row stitched to an adjacent row, wherein the tube has an inner diameter that is sufficient to receive at least one instrument.
- FIG. 1 is a perspective view of an exemplary implantable medical device comprising a knitted catheter in accordance with embodiments of the present invention
- FIG. 2 is a perspective view of a section of a knitted member
- FIG. 3 is a side view of a section of a knitted catheter in accordance with embodiments of the present invention.
- FIG. 4 is a side view of a section of a knitted catheter in accordance with embodiments of the present invention.
- FIG. 5A is a perspective view of a composite conductive filament in accordance with embodiments of the present invention.
- FIG. 5B is a side view of a section of a knitted catheter comprising a composite conductive filament of FIG. 5A , in accordance with embodiments of the present invention
- FIG. 6A is a partial cross-sectional side view of a section of a knitted catheter having an active component positioned therein, in accordance with embodiments of the present invention.
- FIG. 6B is a side view of a section of a knitted catheter having an active component positioned thereon, in accordance with embodiments of the present invention.
- FIG. 7 is a partial cross-sectional side view of a section of a knitted catheter having a steering element positioned therein, in accordance with embodiments of the present invention.
- FIG. 8A is a side view of a steering element in accordance with embodiments of the present invention.
- FIG. 8B is a side view of a steering element in accordance with embodiments of the present invention.
- FIG. 8C is a partial cross-sectional side view of a section of a knitted catheter having steering elements in accordance with embodiments of FIG. 8B positioned therein;
- FIG. 9A is a side view of a section of a knitted catheter having a support structure positioned therein, in accordance with embodiments of the present invention.
- FIG. 9B is a side view of a section of a knitted catheter having a stylet at least partially positioned therein, in accordance with embodiments of the present invention.
- FIG. 9C is a side view of a section of a knitted catheter having an agent delivery mechanism therein, in accordance with embodiments of the present invention.
- FIG. 10 is a side view of a section of a knitted catheter having a knitted tubular member positioned therein, in accordance with embodiments of the present invention.
- FIG. 11 is a side view of a section of a knitted catheter having a gel therein, in accordance with embodiments of the present invention.
- FIG. 12A is a side view of a section of a knitted catheter having an anchoring element therein, in accordance with embodiments of the present invention.
- FIG. 12B is a side view of a section of a knitted catheter having an anchoring element therein, in accordance with embodiments of the present invention.
- FIG. 13 is a side view of a section of a conductive cuff positioned on a non-conductive support member, in accordance with embodiments of the present invention.
- FIG. 14A is a high level flowchart illustrating a method for manufacturing a knitted catheter in accordance with embodiments of the present invention.
- FIG. 14B is a high level flowchart illustrating a method for manufacturing a knitted catheter in accordance with embodiments of the present invention.
- aspects of the present invention are generally directed to an implantable medical device comprising an implantable elongate tubular catheter formed using textile or fabric manufacturing methods.
- Exemplary textile manufacturing methods include, but are not limited to, weaving, knitting, braiding, crocheting, etc.
- embodiments of the present invention will be primarily described herein with reference to forming a knitted catheter. It would be appreciated that other textile manufacturing methods are also within the scope of the present invention.
- a knitted catheter in accordance with embodiments of the present invention comprises at least one biocompatible, electrically non-conductive filament arranged in longitudinally adjacent substantially parallel rows each stitched to an adjacent row.
- the knitted catheter has an inner diameter that is sufficient to receive at least one instrument.
- Embodiments of the present invention are described herein primarily in connection with one type of implantable medical device, namely a steerable catheter system. It should be appreciated that embodiments of the present invention may be implemented in any implantable medical device comprising an elongate tubular member. For instance, embodiments of the present invention may be implemented in medical devices that are implanted for a relatively short period of time to address acute conditions, as well in devices that are implanted for a relatively long period of time to address chronic conditions.
- FIG. 1 is a perspective view of an implantable medical device, namely a steerable catheter system 100 , in accordance with embodiments of the present invention.
- Steerable catheter system 100 comprises an implantable knitted catheter 104 , and a handle 130 coupled to the knitted catheter by support member 108 .
- knitted catheter 104 comprises a biocompatible, electrically non-conductive filament arranged in substantially parallel rows each stitched to an adjacent row.
- Knitted catheter 104 is configured to be implanted in a patient using, for example, a sleeve or guide tube, while handle 130 is positionable external to the patient.
- Handle 130 provides a physician, surgeon, or other medical practitioner, (generally and collectively referred to as “surgeons” herein), with the ability to control the operation of knitted catheter 104 .
- handle 130 includes user controls 116 which permit a surgeon to control the orientation of distal region 126 of knitted catheter 104 .
- user controls 116 comprise three control knobs 124 .
- control knobs 124 are mechanically or electrically connected to distal region 126 , or one or more components positioned therein, to steer knitted catheter 104 .
- Control knobs 124 may also control the operation of one or more components positioned in or on knitted catheter 104 .
- Handle 130 further comprises a lumen 122 extending through the center thereof.
- the proximal end of lumen 122 comprises an opening, referred to as access port 118 , for introduction of one or more instruments or other devices into lumen 122 .
- handle 130 is mechanically coupled to knitted catheter 104 by support member 108 .
- Support member 108 comprises a bio-compatible tube extending from handle 130 .
- Support member 108 also has a lumen (not shown) extending through the center thereof.
- the proximal end (not shown) of knitted catheter 104 is configured to be mechanically connected to support member 108 such that a continuous pathway is created from access port 118 through distal region 126 of knitted catheter 104 . As such, the distal end of an elongate instrument introduced through access port 118 may emerge from distal region 126 .
- catheters of various lengths may be formed in accordance with embodiments of the present invention.
- catheters of various lengths may be formed in accordance with embodiments of the present invention.
- only a section of knitted catheter 104 is shown.
- a knitted catheter in accordance with embodiments of the present invention comprises at least one biocompatible, electrically non-conductive filament arranged in substantially parallel rows each stitched to an adjacent row.
- Knitting is a technique for producing a two or three-dimensional structure from a linear or one-dimensional yarn, thread or other filament (collectively and generally referred to as “filaments” herein).
- filaments There are two primary varieties of knitting, known as weft knitting and warp knitting.
- FIG. 2 is a perspective view of a section of a knitted structure 220 formed by weft knitting a single filament 218 .
- the generally meandering path of the filament referred to as the filament course 242
- the filament course 242 is substantially perpendicular to the sequences of interlocking stitches 246 .
- a sequence of stitches 246 is referred to as a wale 244 .
- the entire knitted structure may be manufactured from a single filament by adding stitches 246 to each wale 244 in turn.
- the wales run roughly parallel to the filament course 242 .
- embodiments of the present invention may be implemented using weft or warp knitting.
- embodiments of the present invention may use circular knitting or flat knitting. Circular knitting creates a seamless tube, while flat knitting creates a substantially planar sheet. In certain embodiments in which flat knitting is used, the knitted structure would be disposed around a cylindrical support member as described with reference to FIG. 9A below to provide the desired tubular shape.
- Catheters in accordance with embodiments of the present invention may be knitted using automated knitting methods known in the art, or alternatively using a hand knitting process. It should be appreciated that the knitting method, filament diameter, number of needles and/or the knitting needle size may all affect the size of the stitches and the size of the resulting catheter. As such, the size and shape of the catheter is highly customizable.
- a knitted catheter comprises one or more electrodes positioned on the surface of the distal region of the catheter.
- the electrodes are used to deliver electrical stimulation signals to a patient, or record/monitor the physiological response of a patient's tissue to, for example, a therapy.
- Electrical stimulations signals may be delivered to stimulate tissue, or, in alternative embodiments, for tissue ablation.
- FIG. 3 illustrates a catheter 304 having electrodes 306 thereon.
- a non-conductive filament 318 is knitted into longitudinally adjacent, substantially parallel rows 332 each stitched to an adjacent row.
- two conductive filaments 312 are concurrently knitted with sections of non-conductive filament 318 such that the conductive filament and the non-conductive filament 318 follow the same course.
- the concurrently knit sections of conductive filaments 312 are referred to as being intertwined with non-conductive filament 318 .
- the intertwined portions of conductive filaments 312 A, 312 B each form an electrode 306 A, 306 B, respectively, that may be used to deliver electrical stimulation signals to, and/or receive signals from, a patient's tissue.
- conductive filaments 312 A, 312 B are configured to be electrically connected to a stimulator unit (not shown) or electronics module (also not shown) positioned external to the patient. As such, a section of the each filament 312 extends proximally from the intertwined portions of the filament through the interior of catheter 304 for connection to the stimulator unit or electronics module.
- filament is used to refer to both the conductive and non-conductive threads, fibers or wires that are used to form knitted catheter 304 . It should be appreciated that, as shown in FIG. 3 , filaments of varying diameters and properties may be used to form catheter 304 . As such, the use of filament to refer to both conductive and non-conductive elements should not be construed to imply that the conductive and non-conductive elements have the same diameter or properties.
- the conductive filament is a fiber manufactured from carbon nanotubes.
- the conductive filament is a platinum or other biocompatible conductive wire.
- Such wires may be given suitable surface treatments to increase their surface area (e.g. forming a layer of iridium oxide on the surface of platinum, utilizing platinum “blacking,” or coating the wire with carbon nanotubes).
- the conductive filament comprises several grouped strands of a conductive material.
- the filament may be a composite filament formed from two or more materials to provide a desired structure. In certain such embodiments, the properties of the composite filament may change along the length thereof.
- portions of the composite filament may be conductive, while portions are non-conductive. It would also be appreciated that other types of conductive filaments may also be used. Furthermore, although embodiments of the present invention are described using tubular or round fibers, it would be appreciated that other shapes are within the scope of the present invention.
- conductive filaments in accordance embodiments of the present invention are intertwined with a non-conductive filament to form the catheter. While a majority of the intertwined portion is an exposed conductive element, the remainder of the conductive filament may be insulated. In one such embodiment, a length of suitably insulated conductive filament (e.g. parylene coated platinum wire) is provided and the insulation is removed from the section that is to be intertwined, leaving the remainder of the filament with the insulated coating.
- suitably insulated conductive filament e.g. parylene coated platinum wire
- non-conductive filaments may be used to knit a catheter in accordance with embodiments of the present invention.
- the non-conductive filament is a biocompatible non-elastomeric polymer material.
- the non-conductive filament is a biocompatible elastomeric material.
- the elastomeric material may comprise, for example, silicone, silicone/polyurethane, silicone polymers, or other suitable materials including AORTech® and PBAX.
- Other elastomeric polymers that provide for material elongation while providing structural strength and abrasion resistance so as to facilitate knitting may also be used. It should be appreciated that other types of non-conductive filaments may also be used.
- the filament may be knitted under tension to reduce the final size of the catheter, or portions thereof.
- the knitting of filaments under tension to form a catheter is described in commonly owned and co-pending U.S. Utility Patent Application entitled Knitted Catheter and Integrated Connector for an Active Implantable Medical Device,” filed Aug. 28, 2009, the content of which is hereby incorporated by reference herein.
- a non-conductive filament comprises a drug-eluting polymer.
- drugs appropriate to the application may be incorporated into the structure so as to be automatically dispensed once the catheter is implanted.
- fibers may be coated with any of a number of materials that provide a therapeutic benefit.
- the fibers may receive an anti-fibrogenic coating that prevents attachment to tissue.
- the fibers may be coated with a therapeutic material which promotes healing.
- the non-conductive filament comprises a thermo-softening plastic material, such as polypropylene. As described below, the thermo-softening plastic material allows the knitted structure to be formed into a variety of shapes using, for example, molding, sintering, etc.
- FIG. 4 illustrates embodiments of the present invention in which a distal region 426 of a catheter 404 is formed by alternately knitting with conductive and non-conductive filaments.
- a plurality of rows 432 A are knitted from a first non-conductive filament 418 A and form a first section of catheter 404 .
- a first conductive filament 412 A forms a row 432 B that is knitted to rows 432 A of non-conductive filament 418 A.
- Row 432 B of first conductive filament 412 A forms an electrode 406 A that may be used to deliver electrical stimulation signals to, and/or receive signals from, a patient's tissue.
- a second non-conductive filament 418 B is knitted to row 432 B of conductive filament 412 A to form an additional non-conductive section of catheter 404 .
- a second conductive filament 412 B forms a row 432 D that is knitted to rows 432 C of non-conductive filament 418 B.
- row 432 D of second conductive filament 412 B forms an electrode 406 B that may be used to deliver electrical stimulation signals to, and/or receive signals from, a patient's tissue.
- conductive filaments 412 A and 412 B are referred to as being intertwined with non-conductive filament 418 B.
- Conductive filaments 412 A, 412 B are configured to be electrically connected to a stimulator unit (not shown) or an electronics module (also not shown) positioned external to the patient. As such, a section of the each filament 412 extends proximally from the intertwined portions of the filament through the interior of catheter 404 for connection to the stimulator unit or electronics module.
- FIGS. 5A and 5B illustrate embodiments of the present invention in which a composite conductive filament is used to form a distal region of a catheter.
- a composite conductive filament 516 is formed by winding a section of a conductive filament 512 around a section of a non-conductive filament 518 .
- Conductive filament 512 may be loosely or tightly wound onto non-conductive filament 518 , and is referred to herein as being intertwined with non-conductive filament 518 .
- non-conductive filament 518 comprises a thermo-softening plastic material.
- a thermo-softening filament allows conductive filament 512 to be wound around non-conductive filament 518 while the non-conductive filament is in a softened state. This ensures that conductive filament 512 is well integrated into non-conductive filament 518 so as to reduce any difference in the size of the stitches in the electrode area when compare to those in the non-conductive areas of a formed catheter.
- conductive filament 512 may be loosely or tightly wound onto non-conductive filament 518 .
- a loose winding provides integration of the two filaments and provides a compliant structure to manage fatigue.
- a tight winding provides substantially the same benefits, but also increases the amount of conductive filament in a single stitch.
- FIG. 5B is a side view of a distal region 526 of a knitted catheter 504 formed from composite conductive filament 516 .
- composite conductive filament 516 is knitted into longitudinally adjacent and substantially parallel rows 532 .
- the conductive portions of composite conductive filament 516 i.e. the portions of conductive filament 512 wound around non-conductive filament 518
- electrode 506 may be used to deliver electrical stimulation signals to, and/or receive signals from, a patient's tissue.
- Further details of forming an elongate member from a composite conductive filament are provided in commonly owned and co-pending U.S. Utility Patent Application entitled “Knitted Electrode Assembly For An Active Implantable Medical Device,” filed Aug. 28, 2009, the content of which is hereby incorporated by reference herein.
- a catheter in accordance with certain embodiments of the present invention comprises one or more electrodes to deliver electrical stimulation signals to, and/or receive signals from, a patient's tissue.
- a catheter may also, or alternatively, include one or more passive or active components configured to perform a variety of functions.
- an active component refers to any component that utilizes, or operates with, electrical signals.
- a passive components refers to a functional component that does not utilize, or operate with, electrical signals.
- Passive components include, but are not limited to, forceps, mechanical biopsy devices, etc.
- embodiments of the present invention will be primarily discussed with reference to active components positioned in or on a knitted catheter. It should be appreciated that the incorporation of passive components into a knitted are within the scope of the present invention.
- FIG. 6A illustrates a knitted catheter 604 in accordance with such embodiments of the present invention knitted from a non-conductive filament 618 .
- a section of the exterior surface of knitted catheter 604 is cut away to expose an exemplary location for an active component 644 within distal region 626 .
- active component 644 is schematically illustrated by a box.
- active component 644 may comprise one or more instruments, apparatus, sensors, processors, controllers or other functional components that are used to, for example, diagnosis, monitor, and/or treat a disease or injury, or to modify the patient's anatomy or physiological process.
- FIG. 6B illustrates an alternative embodiment of catheter 604 in which an active component 644 is mounted on the surface of distal region 626 .
- active component 644 comprises an agent delivery system for administering drugs, active substances or therapeutic agents (collectively and generally referred to as “therapeutic agents” herein) to a patient.
- active component 644 may comprise a pump, reservoir and an agent delivery mechanism.
- active component 644 comprises an agent delivery mechanism that is fluidically coupled to a pump and/or reservoir positioned outside catheter 604 .
- a fluid is passed down the length of the catheter for delivery to tissue.
- active component 644 includes one or more sensors for monitoring, for example, pressure, temperature, etc., within the patient.
- the catheter is knitted using a non-conductive filament that is an insulated conducting element which is suitable for strain gauge applications.
- the catheter may be constructed in one or more sections, each section being able to measure the strain experienced across that section.
- Other sensing devices may be incorporated into the structure using a similar method.
- active component 644 comprises one or more actuators incorporated into the knitted structure.
- Suitable actuators may include a low power linear motor.
- Such an actuator is anchored at a suitable location in catheter 604 and may allow the catheter to, for example, provide a method of applying pressure to an organ or body tissue for therapeutic benefit.
- active component 644 comprises an enclosed electronics package.
- one of more electronics packages may be encapsulated in the knitted tube either during its manufacture or afterwards providing a compact and robust final assembly for the whole implantable device.
- FIG. 7 is a side view of one such steerable catheter.
- Knitted catheter 704 of FIG. 7 comprises a non-conductive filament 718 formed into longitudinally adjacent rows each stitched to an adjacent row.
- Disposed in distal region 726 of catheter 704 is a steering element 752 .
- steering element 752 comprises a spring 754 wound between plates 756 .
- Guide wires extend froms plate 756 to control knobs 124 ( FIG. 1 ) positioned external to the patient. A surgeon may manipulate control knobs 124 to bend spring 754 in different directions, thereby altering the orientation of distal region 726 . In this manner, catheter 704 may steered within the patient's body.
- FIGS. 8A-8C illustrates alternative embodiments of catheter 704 in which spring 754 has been omitted.
- catheter 704 is formed from an elastomeric non-conductive filament 718
- two plates 854 are mounted in distal region 726 .
- FIG. 8B illustrates a side view of a plate 854 .
- plate 854 has points 860 with mate with stitches of non-conductive filament 718 .
- guide wires 855 which extend to control knobs 124 positioned external to the patient. By manipulating control knobs 124 , a surgeon exerts forces on plates 854 which, due to the use of elastomeric filament 718 , causes distal region to 726 to bend.
- FIG. 8C plates 854 having an aperture 858 in the center thereof that permit one or more instruments to extend there though.
- FIG. 8A illustrates an alternative plate 852 that does not include an aperture.
- guide wires may be replaced with hydraulic mechanisms for manipulating distal region 726 .
- a knitted catheter 904 may be formed around a hollow biocompatible support structure 952 .
- catheter 904 A is knitted from a composite conductive filament 916 that is substantially similar to composite conductive filament 516 described above with reference to FIGS. 5A-5C .
- the conductive portion of composite conductive filament 916 forms electrode 906 .
- support structure 952 comprises a cylindrical member formed from a biocompatible, electrically non-conductive material that is sized to substantially fill the inner diameter of catheter 904 A. Because support structure 952 substantially fills the inner diameter of catheter 904 , the knitted structure is disposed on the surface of the support structure, and support structure 952 provides additional mechanical strength to catheter 904 A. Support structure 952 has a lumen 956 extending through the center thereof to permit the introduction of one or more instruments into catheter 904 A.
- support structure 952 comprises a shape memory element.
- heating elements are integrated into catheter 904 A adjacent shape memory element 952 to alter the shape thereof.
- the change in the shape of memory element 952 alters the orientation of distal region 926 .
- a series of temperature activated shape memory alloy components are mounted within catheter 904 A.
- the alloy components are electrically connected to a controller in handle 130 ( FIG. 1 ) that selectively delivers electrical current to the alloy components to cause distal region 926 to bend in different directions as the shape-memory alloy components change shape.
- FIG. 9B illustrates a catheter 904 B in accordance with still other embodiments of the present invention.
- distal region 926 of catheter 904 B is pre-formed to a first curved configuration.
- Catheter 904 B further comprises a central tube 954 that is configured to receive a stylet 962 . While stylet 962 is positioned in central tube 954 , stylet 962 retains catheter 904 B in a straight configuration. When stylet 962 is withdrawn, distal region 926 returns to the first curved configuration. Stylet 962 may be withdrawn during or following implantation of catheter 904 B into the patient.
- a catheter in accordance with embodiments of the present invention has an inner diameter that is sufficient to receive one or more instruments.
- instruments may be introduced through a catheter of the present invention.
- an endoscopic camera or cameras, lighting instruments, tissue ablation instruments, drug delivery devices, scissors, forceps, biopsy devices, clamps, etc. may all be used in accordance with embodiments of the present invention.
- any of these devices may integrated in, or disposed on, a knitted catheter as described above with reference to FIGS. 6A and 6B .
- FIG. 9C illustrates specific embodiments of the present invention in which an irrigation device 978 is inserted into a knitted catheter 904 C.
- irrigation device 978 comprises an elongate tube that is fluidically coupled to a pump and/or reservoir positioned outside catheter 904 C.
- a cooling fluid is passed down the length of device 978 for delivery to a patient's tissue via delivery ports 964 .
- the fluid is delivered to cool tissue adjacent electrode 906 .
- FIG. 10 illustrates further embodiments of the present invention in which a knitted catheter 1004 comprises a first tube 1038 knitted from a non-conductive filament 1018 . Disposed in the center of first knitted tube 1038 is a second knitted tube 1048 knitted from a non-conductive filament 1028 .
- the different tubes 1038 , 1048 may be made of different materials to achieve different performance characteristics. For example, softer materials may be used in inner tubes while the outer tube may be constructed from a harder material (i.e. a material having a higher durometer level) for abrasion resistance or strength. In certain embodiments, silicone filaments having different durometer levels may be used.
- a knitted catheter in accordance with embodiments of the present may be used in devices implanted for a short period of time to address acute conditions, as well in devices that are implanted for a relatively long period of time to address chronic conditions. Over a period of time, fibrous tissue may begin to integrate with the stitches of a knitted catheter. Although such integration may be beneficial, integration is not desirable in all circumstances.
- FIG. 11 illustrates embodiments of the present invention designed to limit tissue integration.
- catheter 1104 is knitted from non-conductive filament 1118 .
- a biocompatible gel 1170 is disposed at least inside a number of stitches 1172 . By filling stitches 1172 , gel 1170 provides a barrier to tissue ingrowth. In certain embodiments, gel 1170 may substantially fill the interior of catheter 1104 . It should be appreciated that a variety of suitable gels, such as silicone, may be used in embodiments of the present invention.
- FIGS. 12A and 12B illustrate alternative embodiments in which an element is positioned in a catheter to anchor the catheter.
- a catheter 1204 is formed using a non-conductive filament 1218 .
- anchor plates 1254 Disposed in catheter 1204 are anchor plates 1254 .
- anchor plates 1254 include a plurality of anchor points 1260 that, when positioned in catheter 1204 , extend through the catheter stitches. Anchor points 1260 engage a patient's tissue to retain the catheter in a desired location.
- anchor plates 1254 have an aperture 1258 therein that allows wires or other instruments to extend there through. In alternative embodiments the anchor plates do not include an aperture.
- FIG. 13 illustrates an alternative embodiment of the present invention in which a conductive filament 1312 is knitted into an elongate tube 1330 , referred to as conductive tube 1330 .
- Conductive tube 1330 comprises longitudinally adjacent rows each stitched to an adjacent row.
- Conductive tube 1330 is disposed on a biocompatible non-conductive solid or hollow carrier member 1352 .
- Conductive tube 1330 may function, for example, as a stimulating or ablation electrode. It should be appreciated that a plurality of conductive tubes 1330 may be disposed on carrier member 1352
- FIG. 14A is a flowchart illustrating a method 1400 for manufacturing a knitted implantable catheter in accordance with embodiments of the present invention.
- method 1400 begins at block 1402 where at least one biocompatible, electrical non-conductive filament is provided. As noted above, numerous different types of non-conductive and conductive filaments may be provided. After the filaments have been provided, the method proceeds to block 1404 where the at least one non-conductive filament is knitted into an elongate tube of longitudinally adjacent rows.
- FIG. 14B is a flowchart illustrating a variation of method 1400 of FIG. 14A , referred to as method 1410 .
- method 1410 begins at block 1406 where at least one biocompatible, electrical non-conductive filament and at least one biocompatible, electrically conductive filament are provided. After the filaments have been provided, the method proceeds to block 1408 where the at least one non-conductive filament is knitted into an elongate tube of longitudinally adjacent rows. The at least one conductive filament intertwined with the at least one non-conductive filament.
- catheters in accordance with certain embodiments of the present invention include electrodes that are electrically connected to one or more components positioned external to a patient.
- catheters are subject to bending and stretching during implantation, as well as during normal operation, that may damage or break the electrical connection between the electrodes and the external components.
- embodiments of the present invention provide strain relief to protect the electrical connection.
- a strain relief refers to a non-linear section of a wire or filament between the electrode and external components. Upon bending or stretching of the catheter, the non-linear section of wire will expand to a longer length, thus preventing tension on the filament that results in a damaged electrical connection.
- strain relief in a knitted structure is provided in commonly owned and co-pending U.S. Utility Patent Application entitled “Knitted Electrode Assembly For An Active Implantable Medical Device,” filed Aug. 28, 2009, the content of which is hereby incorporated by reference herein. All embodiments of strain relief described in “Knitted Electrode Assembly For An Active Implantable Medical Device” may be implemented in embodiments of the present invention.
- a catheter may be further processed following the knitting process.
- the catheter may be molded or sintered following the knitting process.
- the knitted structure may be laser sintered, and fiber crossing points within the structure may be formed into bending anisotropies.
- catheter may be processed (via molding, sintering, etc.) to create inflexible portions, such as a stiffened tip, or to create, for example, anchoring barbs that may be used to secure the catheter to the patient.
- the catheter is dipped into, or molded over by, a second material to form a desired shape or configuration.
- a second material for example, one or more portions of the catheter may sealed with an added material to prevent the entry of body fluid into the structure. It would be appreciated that a number of different post-processing methods may be implemented to form the final structure.
- a catheter may be fully or partially covered by an outer structure, such as a tube.
- the knitted structure would be stretched to reduce the width thereof, and the outer covering is placed over the desired portion.
- the knitted structure is then allowed to return to its previous non-stretched shape.
- the outer covering may be conductive, non-conductive or have both conductive and non-conductive sections, depending on the desired configuration.
- an outer covering may be placed on the knitted structure such that conductive sections of the covering are disposed over the electrodes, while non-conductive sections extend over the other portions of the assembly.
- An outer structure may be beneficial to inhibit tissue growth into the knitted structure, to improve implantation by providing a smooth outer surface, to increase the surface area of conductive regions used to deliver electrical stimulation, increase stiffness of the catheter, etc.
- a catheter in accordance with embodiments of the present invention may include electrodes for delivery of electrical stimulation signals to a patient.
- a catheter is knitted from a non-conductive filament and has two or more conductive filaments extending there through. Disposed on the surface of the knitted catheter are two electrodes formed by creating a ball or other shaped structure on the distal end of the conductive filaments.
- the conductive filaments comprise platinum wire that is inserted into the knitted structure such that distal structure mates with the non-conductive filament, and is held in the appropriate position.
- the distal structure may be formed by, for example, melting the distal end of the conductive filament with a localized heat source, by bunching the conductive filament into the desired shape, attaching a bulk material piece (e.g. platinum foil) having the desired shape to the conductive filament by weld, crimping or other method, etc.
- a bulk material piece e.g. platinum foil
Abstract
Description
- The present application claims priority from Australian Provisional Patent Application No. 2008904838, filed Sep. 17, 2008, Australian Provisional Patent Application No. 2009901534, filed Apr. 8, 2009, and Australian Provisional Patent Application No. 2009901531, filed Apr. 8, 2009, which are hereby incorporated by reference herein.
- The present application is related to commonly owned and co-pending U.S. Utility Patent Applications entitled “Knitted Electrode Assembly For An Active Implantable Medical Device,” filed Aug. 28, 2009, “Knitted Electrode Assembly And Integrated Connector For An Active Implantable Medical Device,” filed Aug. 28, 2009, “Bonded Hermetic Feed Through For An Active Implantable Medical Device,” filed Aug. 28, 2009, “Stitched Components of An Active Implantable Medical Device,” filed Aug. 28, 2009, and “Electronics Package For An Active Implantable Medical Device,” filed Aug. 28, 2009, which are hereby incorporated by reference herein.
- 1. Field of the Invention
- The present invention relates generally to catheters, and more particularly, to a knitted catheter.
- 2. Related Art
- Medical devices having one or more implantable components, generally referred to as implantable medical devices, have provided a wide range of therapeutic benefits to patients over recent decades. One type of implantable medical device includes an implantable, hermetically sealed electronics module, and a device that interfaces with a patient's tissue, sometimes referred to as a tissue interface. The tissue interface may include, for example, one or more instruments, apparatus, sensors or other functional components that are permanently or temporarily implanted in a patient. The tissue interface is used to, for example, diagnose, monitor, and/or treat a disease or injury, or to modify a patient's anatomy or physiological process. Such devices are referred to herein as active implantable medical devices (AIMDs).
- Other types of implantable medical devices include an implantable tubular member, referred to herein as a catheter, having a lumen extending there through. Medical catheters are used by physicians to diagnose and treat a range conditions in a patient's body. Specifically, catheters are used to introduce or withdraw fluids, introduce an instrument, apparatus, or other functional component, delivering electrical stimulation signals to a patient's tissue, etc.
- In accordance with one aspect of the present invention, a medical device is provided. The medical device comprises: an elongate tubular knitted catheter comprising at least one biocompatible, electrically non-conductive filament arranged in longitudinally adjacent substantially parallel rows each stitched to an adjacent row, wherein the tubular catheter has an inner diameter that is sufficient to receive at least one instrument.
- In accordance with one aspect of the present invention, a method for manufacturing a knitted tubular catheter is provided. The method comprises: providing at least one biocompatible, electrically non-conductive filament; and knitting the at least one non-conductive filament into an elongate tube of longitudinally adjacent substantially parallel rows, each row stitched to an adjacent row, wherein the tube has an inner diameter that is sufficient to receive at least one instrument.
- Aspects and embodiments of the present invention are described herein with reference to the accompanying drawings, in which:
-
FIG. 1 is a perspective view of an exemplary implantable medical device comprising a knitted catheter in accordance with embodiments of the present invention; -
FIG. 2 is a perspective view of a section of a knitted member; -
FIG. 3 is a side view of a section of a knitted catheter in accordance with embodiments of the present invention; -
FIG. 4 is a side view of a section of a knitted catheter in accordance with embodiments of the present invention; -
FIG. 5A is a perspective view of a composite conductive filament in accordance with embodiments of the present invention; -
FIG. 5B is a side view of a section of a knitted catheter comprising a composite conductive filament ofFIG. 5A , in accordance with embodiments of the present invention; -
FIG. 6A is a partial cross-sectional side view of a section of a knitted catheter having an active component positioned therein, in accordance with embodiments of the present invention; -
FIG. 6B is a side view of a section of a knitted catheter having an active component positioned thereon, in accordance with embodiments of the present invention; -
FIG. 7 is a partial cross-sectional side view of a section of a knitted catheter having a steering element positioned therein, in accordance with embodiments of the present invention; -
FIG. 8A is a side view of a steering element in accordance with embodiments of the present invention; -
FIG. 8B is a side view of a steering element in accordance with embodiments of the present invention; -
FIG. 8C is a partial cross-sectional side view of a section of a knitted catheter having steering elements in accordance with embodiments ofFIG. 8B positioned therein; -
FIG. 9A is a side view of a section of a knitted catheter having a support structure positioned therein, in accordance with embodiments of the present invention; -
FIG. 9B is a side view of a section of a knitted catheter having a stylet at least partially positioned therein, in accordance with embodiments of the present invention; -
FIG. 9C is a side view of a section of a knitted catheter having an agent delivery mechanism therein, in accordance with embodiments of the present invention; -
FIG. 10 is a side view of a section of a knitted catheter having a knitted tubular member positioned therein, in accordance with embodiments of the present invention; -
FIG. 11 is a side view of a section of a knitted catheter having a gel therein, in accordance with embodiments of the present invention; -
FIG. 12A is a side view of a section of a knitted catheter having an anchoring element therein, in accordance with embodiments of the present invention; -
FIG. 12B is a side view of a section of a knitted catheter having an anchoring element therein, in accordance with embodiments of the present invention; -
FIG. 13 is a side view of a section of a conductive cuff positioned on a non-conductive support member, in accordance with embodiments of the present invention; -
FIG. 14A is a high level flowchart illustrating a method for manufacturing a knitted catheter in accordance with embodiments of the present invention; and -
FIG. 14B is a high level flowchart illustrating a method for manufacturing a knitted catheter in accordance with embodiments of the present invention. - Aspects of the present invention are generally directed to an implantable medical device comprising an implantable elongate tubular catheter formed using textile or fabric manufacturing methods. Exemplary textile manufacturing methods include, but are not limited to, weaving, knitting, braiding, crocheting, etc. For ease of illustration, embodiments of the present invention will be primarily described herein with reference to forming a knitted catheter. It would be appreciated that other textile manufacturing methods are also within the scope of the present invention.
- A knitted catheter in accordance with embodiments of the present invention comprises at least one biocompatible, electrically non-conductive filament arranged in longitudinally adjacent substantially parallel rows each stitched to an adjacent row. In certain embodiments, the knitted catheter has an inner diameter that is sufficient to receive at least one instrument.
- Embodiments of the present invention are described herein primarily in connection with one type of implantable medical device, namely a steerable catheter system. It should be appreciated that embodiments of the present invention may be implemented in any implantable medical device comprising an elongate tubular member. For instance, embodiments of the present invention may be implemented in medical devices that are implanted for a relatively short period of time to address acute conditions, as well in devices that are implanted for a relatively long period of time to address chronic conditions.
-
FIG. 1 is a perspective view of an implantable medical device, namely asteerable catheter system 100, in accordance with embodiments of the present invention.Steerable catheter system 100 comprises an implantableknitted catheter 104, and ahandle 130 coupled to the knitted catheter bysupport member 108. As described in greater detail below,knitted catheter 104 comprises a biocompatible, electrically non-conductive filament arranged in substantially parallel rows each stitched to an adjacent row. -
Knitted catheter 104 is configured to be implanted in a patient using, for example, a sleeve or guide tube, whilehandle 130 is positionable external to the patient. Handle 130 provides a physician, surgeon, or other medical practitioner, (generally and collectively referred to as “surgeons” herein), with the ability to control the operation ofknitted catheter 104. More specifically, handle 130 includes user controls 116 which permit a surgeon to control the orientation ofdistal region 126 ofknitted catheter 104. - In the embodiments of
FIG. 1 , user controls 116 comprise three control knobs 124. As described below, control knobs 124 are mechanically or electrically connected todistal region 126, or one or more components positioned therein, to steerknitted catheter 104. Control knobs 124 may also control the operation of one or more components positioned in or onknitted catheter 104. - Handle 130 further comprises a
lumen 122 extending through the center thereof. The proximal end oflumen 122 comprises an opening, referred to asaccess port 118, for introduction of one or more instruments or other devices intolumen 122. - In the embodiments of
FIG. 1 , handle 130 is mechanically coupled to knittedcatheter 104 bysupport member 108.Support member 108 comprises a bio-compatible tube extending fromhandle 130.Support member 108 also has a lumen (not shown) extending through the center thereof. The proximal end (not shown) of knittedcatheter 104 is configured to be mechanically connected to supportmember 108 such that a continuous pathway is created fromaccess port 118 throughdistal region 126 ofknitted catheter 104. As such, the distal end of an elongate instrument introduced throughaccess port 118 may emerge fromdistal region 126. - It should be appreciated that catheters of various lengths may be formed in accordance with embodiments of the present invention. For ease of illustration, only a section of
knitted catheter 104 is shown. - As noted above, a knitted catheter in accordance with embodiments of the present invention comprises at least one biocompatible, electrically non-conductive filament arranged in substantially parallel rows each stitched to an adjacent row. Knitting is a technique for producing a two or three-dimensional structure from a linear or one-dimensional yarn, thread or other filament (collectively and generally referred to as “filaments” herein). There are two primary varieties of knitting, known as weft knitting and warp knitting.
FIG. 2 is a perspective view of a section of aknitted structure 220 formed by weft knitting asingle filament 218. - As shown in
FIG. 2 , the generally meandering path of the filament, referred to as thefilament course 242, is substantially perpendicular to the sequences of interlocking stitches 246. A sequence ofstitches 246 is referred to as awale 244. In weft knitting, the entire knitted structure may be manufactured from a single filament by addingstitches 246 to eachwale 244 in turn. In contrast to the embodiments illustrated inFIG. 2 , in warp knitting, the wales run roughly parallel to thefilament course 242. - It should be appreciated that embodiments of the present invention may be implemented using weft or warp knitting. Furthermore, embodiments of the present invention may use circular knitting or flat knitting. Circular knitting creates a seamless tube, while flat knitting creates a substantially planar sheet. In certain embodiments in which flat knitting is used, the knitted structure would be disposed around a cylindrical support member as described with reference to
FIG. 9A below to provide the desired tubular shape. - Catheters in accordance with embodiments of the present invention may be knitted using automated knitting methods known in the art, or alternatively using a hand knitting process. It should be appreciated that the knitting method, filament diameter, number of needles and/or the knitting needle size may all affect the size of the stitches and the size of the resulting catheter. As such, the size and shape of the catheter is highly customizable.
- As noted above, medical catheters are used by surgeons to perform various functions, including the diagnosis and/or treatment of a range of conditions in a patient. In certain embodiments of the present invention, a knitted catheter comprises one or more electrodes positioned on the surface of the distal region of the catheter. In such embodiments, the electrodes are used to deliver electrical stimulation signals to a patient, or record/monitor the physiological response of a patient's tissue to, for example, a therapy. Electrical stimulations signals may be delivered to stimulate tissue, or, in alternative embodiments, for tissue ablation.
-
FIG. 3 illustrates acatheter 304 having electrodes 306 thereon. In the embodiments ofFIG. 3 , anon-conductive filament 318 is knitted into longitudinally adjacent, substantiallyparallel rows 332 each stitched to an adjacent row. As shown, two conductive filaments 312 are concurrently knitted with sections ofnon-conductive filament 318 such that the conductive filament and thenon-conductive filament 318 follow the same course. The concurrently knit sections of conductive filaments 312 are referred to as being intertwined withnon-conductive filament 318. The intertwined portions ofconductive filaments electrode - In the embodiments of
FIG. 3 ,conductive filaments catheter 304 for connection to the stimulator unit or electronics module. - As noted, the term filament is used to refer to both the conductive and non-conductive threads, fibers or wires that are used to form
knitted catheter 304. It should be appreciated that, as shown inFIG. 3 , filaments of varying diameters and properties may be used to formcatheter 304. As such, the use of filament to refer to both conductive and non-conductive elements should not be construed to imply that the conductive and non-conductive elements have the same diameter or properties. - A variety of different types and shapes of conductive filaments may be used to knit a catheter in accordance with embodiments of the present invention. In one embodiment, the conductive filament is a fiber manufactured from carbon nanotubes. Alternatively, the conductive filament is a platinum or other biocompatible conductive wire. Such wires may be given suitable surface treatments to increase their surface area (e.g. forming a layer of iridium oxide on the surface of platinum, utilizing platinum “blacking,” or coating the wire with carbon nanotubes). In other embodiments, the conductive filament comprises several grouped strands of a conductive material. In other embodiments, the filament may be a composite filament formed from two or more materials to provide a desired structure. In certain such embodiments, the properties of the composite filament may change along the length thereof. For example, certain portions of the composite filament may be conductive, while portions are non-conductive. It would also be appreciated that other types of conductive filaments may also be used. Furthermore, although embodiments of the present invention are described using tubular or round fibers, it would be appreciated that other shapes are within the scope of the present invention.
- As noted above, conductive filaments in accordance embodiments of the present invention are intertwined with a non-conductive filament to form the catheter. While a majority of the intertwined portion is an exposed conductive element, the remainder of the conductive filament may be insulated. In one such embodiment, a length of suitably insulated conductive filament (e.g. parylene coated platinum wire) is provided and the insulation is removed from the section that is to be intertwined, leaving the remainder of the filament with the insulated coating.
- A variety of non-conductive filaments may be used to knit a catheter in accordance with embodiments of the present invention. In one embodiment, the non-conductive filament is a biocompatible non-elastomeric polymer material. In another embodiment, the non-conductive filament is a biocompatible elastomeric material. For example, the elastomeric material may comprise, for example, silicone, silicone/polyurethane, silicone polymers, or other suitable materials including AORTech® and PBAX. Other elastomeric polymers that provide for material elongation while providing structural strength and abrasion resistance so as to facilitate knitting may also be used. It should be appreciated that other types of non-conductive filaments may also be used.
- In embodiments in which an elastomeric non-conductive filament is used, the filament may be knitted under tension to reduce the final size of the catheter, or portions thereof. The knitting of filaments under tension to form a catheter is described in commonly owned and co-pending U.S. Utility Patent Application entitled Knitted Catheter and Integrated Connector for an Active Implantable Medical Device,” filed Aug. 28, 2009, the content of which is hereby incorporated by reference herein.
- In a further embodiment, a non-conductive filament comprises a drug-eluting polymer. In such embodiments, drugs appropriate to the application may be incorporated into the structure so as to be automatically dispensed once the catheter is implanted. In alterative embodiments, fibers may be coated with any of a number of materials that provide a therapeutic benefit. For example, in one embodiment the fibers may receive an anti-fibrogenic coating that prevents attachment to tissue. In other embodiments the fibers may be coated with a therapeutic material which promotes healing. In still further embodiments, the non-conductive filament comprises a thermo-softening plastic material, such as polypropylene. As described below, the thermo-softening plastic material allows the knitted structure to be formed into a variety of shapes using, for example, molding, sintering, etc.
-
FIG. 4 illustrates embodiments of the present invention in which adistal region 426 of acatheter 404 is formed by alternately knitting with conductive and non-conductive filaments. In the embodiments ofFIG. 4 , a plurality ofrows 432A are knitted from a firstnon-conductive filament 418A and form a first section ofcatheter 404. A firstconductive filament 412A forms arow 432B that is knitted torows 432A ofnon-conductive filament 418A.Row 432B of firstconductive filament 412A forms anelectrode 406A that may be used to deliver electrical stimulation signals to, and/or receive signals from, a patient's tissue. - In the embodiments of
FIG. 4B , a secondnon-conductive filament 418B is knitted to row 432B ofconductive filament 412A to form an additional non-conductive section ofcatheter 404. A secondconductive filament 412B forms arow 432D that is knitted torows 432C ofnon-conductive filament 418B. Similar to row 432B ofconductive filament 412B,row 432D of secondconductive filament 412B forms anelectrode 406B that may be used to deliver electrical stimulation signals to, and/or receive signals from, a patient's tissue. As used herein,conductive filaments non-conductive filament 418B. Further details of knitting an elongate member using alternating conductive and non-conductive filaments are provided in commonly owned and co-pending U.S. Utility Patent Application entitled “Knitted Electrode Assembly For An Active Implantable Medical Device,” filed Aug. 28, 2009, the content of which is hereby incorporated by reference herein. -
Conductive filaments catheter 404 for connection to the stimulator unit or electronics module. -
FIGS. 5A and 5B illustrate embodiments of the present invention in which a composite conductive filament is used to form a distal region of a catheter. As shown inFIG. 5A , a compositeconductive filament 516 is formed by winding a section of aconductive filament 512 around a section of anon-conductive filament 518.Conductive filament 512 may be loosely or tightly wound ontonon-conductive filament 518, and is referred to herein as being intertwined withnon-conductive filament 518. - In certain embodiments of
FIG. 5A ,non-conductive filament 518 comprises a thermo-softening plastic material. The use of a thermo-softening filament allowsconductive filament 512 to be wound aroundnon-conductive filament 518 while the non-conductive filament is in a softened state. This ensures thatconductive filament 512 is well integrated intonon-conductive filament 518 so as to reduce any difference in the size of the stitches in the electrode area when compare to those in the non-conductive areas of a formed catheter. As noted,conductive filament 512 may be loosely or tightly wound ontonon-conductive filament 518. A loose winding provides integration of the two filaments and provides a compliant structure to manage fatigue. A tight winding provides substantially the same benefits, but also increases the amount of conductive filament in a single stitch. An alternative composite conductive filament is formed using a cording method as described in commonly owned and co-pending U.S. Utility Application entitled “Knitted Electrode Assembly For An Active Implantable Medical Device,” filed Aug. 28, 2009, the content of which are hereby incorporated by reference herein. -
FIG. 5B is a side view of adistal region 526 of aknitted catheter 504 formed from compositeconductive filament 516. In these embodiments, compositeconductive filament 516 is knitted into longitudinally adjacent and substantiallyparallel rows 532. Whencatheter 504 is formed, the conductive portions of composite conductive filament 516 (i.e. the portions ofconductive filament 512 wound around non-conductive filament 518) form electrode 506 that may be used to deliver electrical stimulation signals to, and/or receive signals from, a patient's tissue. Further details of forming an elongate member from a composite conductive filament are provided in commonly owned and co-pending U.S. Utility Patent Application entitled “Knitted Electrode Assembly For An Active Implantable Medical Device,” filed Aug. 28, 2009, the content of which is hereby incorporated by reference herein. - As noted above, a catheter in accordance with certain embodiments of the present invention comprises one or more electrodes to deliver electrical stimulation signals to, and/or receive signals from, a patient's tissue. In other embodiments of the present invention, a catheter may also, or alternatively, include one or more passive or active components configured to perform a variety of functions. As used herein, an active component refers to any component that utilizes, or operates with, electrical signals. A passive components refers to a functional component that does not utilize, or operate with, electrical signals. Passive components include, but are not limited to, forceps, mechanical biopsy devices, etc. For ease of illustration, embodiments of the present invention will be primarily discussed with reference to active components positioned in or on a knitted catheter. It should be appreciated that the incorporation of passive components into a knitted are within the scope of the present invention.
-
FIG. 6A illustrates aknitted catheter 604 in accordance with such embodiments of the present invention knitted from anon-conductive filament 618. InFIG. 6A , a section of the exterior surface ofknitted catheter 604 is cut away to expose an exemplary location for anactive component 644 withindistal region 626. For ease of illustration,active component 644 is schematically illustrated by a box. In accordance with embodiments of the present invention,active component 644 may comprise one or more instruments, apparatus, sensors, processors, controllers or other functional components that are used to, for example, diagnosis, monitor, and/or treat a disease or injury, or to modify the patient's anatomy or physiological process.FIG. 6B illustrates an alternative embodiment ofcatheter 604 in which anactive component 644 is mounted on the surface ofdistal region 626. - In certain specific embodiments of the present invention,
active component 644 comprises an agent delivery system for administering drugs, active substances or therapeutic agents (collectively and generally referred to as “therapeutic agents” herein) to a patient. In certain such embodiments,active component 644 may comprise a pump, reservoir and an agent delivery mechanism. In alternative embodiments,active component 644 comprises an agent delivery mechanism that is fluidically coupled to a pump and/or reservoir positioned outsidecatheter 604. In one such embodiment, a fluid is passed down the length of the catheter for delivery to tissue. In another specific example,active component 644 includes one or more sensors for monitoring, for example, pressure, temperature, etc., within the patient. - In a still further embodiment of the present invention, the catheter is knitted using a non-conductive filament that is an insulated conducting element which is suitable for strain gauge applications. In such embodiments, the catheter may be constructed in one or more sections, each section being able to measure the strain experienced across that section. Other sensing devices may be incorporated into the structure using a similar method.
- In another embodiment,
active component 644 comprises one or more actuators incorporated into the knitted structure. Suitable actuators may include a low power linear motor. Such an actuator is anchored at a suitable location incatheter 604 and may allow the catheter to, for example, provide a method of applying pressure to an organ or body tissue for therapeutic benefit. - In a further embodiment,
active component 644 comprises an enclosed electronics package. In this embodiment one of more electronics packages may be encapsulated in the knitted tube either during its manufacture or afterwards providing a compact and robust final assembly for the whole implantable device. - As noted above, embodiments of the present invention are directed to steerable catheters.
FIG. 7 is a side view of one such steerable catheter.Knitted catheter 704 ofFIG. 7 comprises anon-conductive filament 718 formed into longitudinally adjacent rows each stitched to an adjacent row. Disposed indistal region 726 ofcatheter 704 is asteering element 752. As shown, steeringelement 752 comprises aspring 754 wound between plates 756. Guide wires (not shown) extend froms plate 756 to control knobs 124 (FIG. 1 ) positioned external to the patient. A surgeon may manipulate control knobs 124 to bendspring 754 in different directions, thereby altering the orientation ofdistal region 726. In this manner,catheter 704 may steered within the patient's body. -
FIGS. 8A-8C illustrates alternative embodiments ofcatheter 704 in which spring 754 has been omitted. In the embodiments ofFIG. 8C ,catheter 704 is formed from an elastomericnon-conductive filament 718, and twoplates 854 are mounted indistal region 726.FIG. 8B illustrates a side view of aplate 854. As shown,plate 854 haspoints 860 with mate with stitches ofnon-conductive filament 718. Connected toplates 854 are guide wires 855 which extend to control knobs 124 positioned external to the patient. By manipulating control knobs 124, a surgeon exerts forces onplates 854 which, due to the use ofelastomeric filament 718, causes distal region to 726 to bend. - In the embodiments of
FIG. 8C ,plates 854 having anaperture 858 in the center thereof that permit one or more instruments to extend there though.FIG. 8A illustrates analternative plate 852 that does not include an aperture. - It should be appreciated that numerous variations to the arrangements shown in
FIGS. 7-8C are within the scope of the present invention. For example, in certain embodiments, guide wires may be replaced with hydraulic mechanisms for manipulatingdistal region 726. - According to another aspect of the present invention illustrated in
FIG. 9A , a knitted catheter 904 may be formed around a hollow biocompatible support structure 952. In the embodiments ofFIG. 9A ,catheter 904A is knitted from a compositeconductive filament 916 that is substantially similar to compositeconductive filament 516 described above with reference toFIGS. 5A-5C . The conductive portion of compositeconductive filament 916forms electrode 906. - As shown, support structure 952 comprises a cylindrical member formed from a biocompatible, electrically non-conductive material that is sized to substantially fill the inner diameter of
catheter 904A. Because support structure 952 substantially fills the inner diameter of catheter 904, the knitted structure is disposed on the surface of the support structure, and support structure 952 provides additional mechanical strength tocatheter 904A. Support structure 952 has alumen 956 extending through the center thereof to permit the introduction of one or more instruments intocatheter 904A. - The inherent ability of the knitted catheter to change diameter as it is compressed or expanded allows support structures 952 of various shapes and diameters to be easily introduced. This process may be further facilitated if composite
conductive filament 916 has elastomeric properties. - It would be appreciated that variations of the embodiments of
FIG. 9A are within the scope of the present invention. For instance, in one such variation, support structure 952 comprises a shape memory element. In such embodiment, heating elements are integrated intocatheter 904A adjacent shape memory element 952 to alter the shape thereof. The change in the shape of memory element 952 alters the orientation ofdistal region 926. - In still other embodiments, a series of temperature activated shape memory alloy components are mounted within
catheter 904A. In such embodiments, the alloy components are electrically connected to a controller in handle 130 (FIG. 1 ) that selectively delivers electrical current to the alloy components to causedistal region 926 to bend in different directions as the shape-memory alloy components change shape. -
FIG. 9B illustrates acatheter 904B in accordance with still other embodiments of the present invention. In these embodiments,distal region 926 ofcatheter 904B is pre-formed to a first curved configuration.Catheter 904B further comprises acentral tube 954 that is configured to receive astylet 962. Whilestylet 962 is positioned incentral tube 954,stylet 962 retainscatheter 904B in a straight configuration. Whenstylet 962 is withdrawn,distal region 926 returns to the first curved configuration.Stylet 962 may be withdrawn during or following implantation ofcatheter 904B into the patient. - As noted above, a catheter in accordance with embodiments of the present invention has an inner diameter that is sufficient to receive one or more instruments. It would be appreciated that a variety of instruments may be introduced through a catheter of the present invention. For instance, an endoscopic camera or cameras, lighting instruments, tissue ablation instruments, drug delivery devices, scissors, forceps, biopsy devices, clamps, etc. may all be used in accordance with embodiments of the present invention. It should also be appreciated that any of these devices may integrated in, or disposed on, a knitted catheter as described above with reference to
FIGS. 6A and 6B . -
FIG. 9C illustrates specific embodiments of the present invention in which anirrigation device 978 is inserted into aknitted catheter 904C. In these embodiments,irrigation device 978 comprises an elongate tube that is fluidically coupled to a pump and/or reservoir positioned outsidecatheter 904C. A cooling fluid is passed down the length ofdevice 978 for delivery to a patient's tissue viadelivery ports 964. In certain embodiments, the fluid is delivered to cool tissueadjacent electrode 906. -
FIG. 10 illustrates further embodiments of the present invention in which aknitted catheter 1004 comprises afirst tube 1038 knitted from anon-conductive filament 1018. Disposed in the center of first knittedtube 1038 is a secondknitted tube 1048 knitted from anon-conductive filament 1028. In the embodiments ofFIG. 10 , thedifferent tubes - As noted, a knitted catheter in accordance with embodiments of the present may be used in devices implanted for a short period of time to address acute conditions, as well in devices that are implanted for a relatively long period of time to address chronic conditions. Over a period of time, fibrous tissue may begin to integrate with the stitches of a knitted catheter. Although such integration may be beneficial, integration is not desirable in all circumstances.
FIG. 11 illustrates embodiments of the present invention designed to limit tissue integration. - In the embodiments of
FIG. 11 ,catheter 1104 is knitted fromnon-conductive filament 1118. Abiocompatible gel 1170 is disposed at least inside a number ofstitches 1172. By fillingstitches 1172,gel 1170 provides a barrier to tissue ingrowth. In certain embodiments,gel 1170 may substantially fill the interior ofcatheter 1104. It should be appreciated that a variety of suitable gels, such as silicone, may be used in embodiments of the present invention. - In certain embodiments of the present invention, it is desirable to secure or anchor a knitted catheter to a patient. As noted above, in certain embodiments, a catheter may be anchored through the growth of fibrous tissue into the catheter stitches.
FIGS. 12A and 12B illustrate alternative embodiments in which an element is positioned in a catheter to anchor the catheter. - As shown in
FIG. 12B , acatheter 1204 is formed using anon-conductive filament 1218. Disposed incatheter 1204 areanchor plates 1254. As shown inFIG. 12A ,anchor plates 1254 include a plurality ofanchor points 1260 that, when positioned incatheter 1204, extend through the catheter stitches. Anchor points 1260 engage a patient's tissue to retain the catheter in a desired location. - In the embodiments of
FIGS. 12A and 12B ,anchor plates 1254 have anaperture 1258 therein that allows wires or other instruments to extend there through. In alternative embodiments the anchor plates do not include an aperture. -
FIG. 13 illustrates an alternative embodiment of the present invention in which aconductive filament 1312 is knitted into anelongate tube 1330, referred to asconductive tube 1330.Conductive tube 1330 comprises longitudinally adjacent rows each stitched to an adjacent row.Conductive tube 1330 is disposed on a biocompatible non-conductive solid orhollow carrier member 1352.Conductive tube 1330 may function, for example, as a stimulating or ablation electrode. It should be appreciated that a plurality ofconductive tubes 1330 may be disposed oncarrier member 1352 -
FIG. 14A is a flowchart illustrating amethod 1400 for manufacturing a knitted implantable catheter in accordance with embodiments of the present invention. As shown,method 1400 begins atblock 1402 where at least one biocompatible, electrical non-conductive filament is provided. As noted above, numerous different types of non-conductive and conductive filaments may be provided. After the filaments have been provided, the method proceeds to block 1404 where the at least one non-conductive filament is knitted into an elongate tube of longitudinally adjacent rows. -
FIG. 14B is a flowchart illustrating a variation ofmethod 1400 ofFIG. 14A , referred to asmethod 1410. As shown,method 1410 begins atblock 1406 where at least one biocompatible, electrical non-conductive filament and at least one biocompatible, electrically conductive filament are provided. After the filaments have been provided, the method proceeds to block 1408 where the at least one non-conductive filament is knitted into an elongate tube of longitudinally adjacent rows. The at least one conductive filament intertwined with the at least one non-conductive filament. - As noted above, catheters in accordance with certain embodiments of the present invention include electrodes that are electrically connected to one or more components positioned external to a patient. However, catheters are subject to bending and stretching during implantation, as well as during normal operation, that may damage or break the electrical connection between the electrodes and the external components. As such, embodiments of the present invention provide strain relief to protect the electrical connection. As used herein, a strain relief refers to a non-linear section of a wire or filament between the electrode and external components. Upon bending or stretching of the catheter, the non-linear section of wire will expand to a longer length, thus preventing tension on the filament that results in a damaged electrical connection. Further details of strain relief in a knitted structure are provided in commonly owned and co-pending U.S. Utility Patent Application entitled “Knitted Electrode Assembly For An Active Implantable Medical Device,” filed Aug. 28, 2009, the content of which is hereby incorporated by reference herein. All embodiments of strain relief described in “Knitted Electrode Assembly For An Active Implantable Medical Device” may be implemented in embodiments of the present invention.
- It would also be appreciated that a catheter may be further processed following the knitting process. In one such embodiment, the catheter may be molded or sintered following the knitting process. For example, the knitted structure may be laser sintered, and fiber crossing points within the structure may be formed into bending anisotropies. In other embodiments, catheter may be processed (via molding, sintering, etc.) to create inflexible portions, such as a stiffened tip, or to create, for example, anchoring barbs that may be used to secure the catheter to the patient.
- It would be appreciated that in alternative embodiments the catheter is dipped into, or molded over by, a second material to form a desired shape or configuration. For example, one or more portions of the catheter may sealed with an added material to prevent the entry of body fluid into the structure. It would be appreciated that a number of different post-processing methods may be implemented to form the final structure.
- In still further embodiments, following the knitting process a catheter may be fully or partially covered by an outer structure, such as a tube. In such embodiments, the knitted structure would be stretched to reduce the width thereof, and the outer covering is placed over the desired portion. The knitted structure is then allowed to return to its previous non-stretched shape. The outer covering may be conductive, non-conductive or have both conductive and non-conductive sections, depending on the desired configuration. For example, an outer covering may be placed on the knitted structure such that conductive sections of the covering are disposed over the electrodes, while non-conductive sections extend over the other portions of the assembly. An outer structure may be beneficial to inhibit tissue growth into the knitted structure, to improve implantation by providing a smooth outer surface, to increase the surface area of conductive regions used to deliver electrical stimulation, increase stiffness of the catheter, etc.
- As noted above, a catheter in accordance with embodiments of the present invention may include electrodes for delivery of electrical stimulation signals to a patient. In certain embodiments, a catheter is knitted from a non-conductive filament and has two or more conductive filaments extending there through. Disposed on the surface of the knitted catheter are two electrodes formed by creating a ball or other shaped structure on the distal end of the conductive filaments. For example, in certain embodiments the conductive filaments comprise platinum wire that is inserted into the knitted structure such that distal structure mates with the non-conductive filament, and is held in the appropriate position. The distal structure may be formed by, for example, melting the distal end of the conductive filament with a localized heat source, by bunching the conductive filament into the desired shape, attaching a bulk material piece (e.g. platinum foil) having the desired shape to the conductive filament by weld, crimping or other method, etc. Such embodiments are illustrated in commonly owned and co-pending U.S. Utility Application entitled “Knitted Electrode Assembly For An Active Implantable Medical Device,” filed Aug. 28, 2009, the content of which are hereby incorporated by reference herein.
- The present application is related to commonly owned and co-pending U.S. Utility Patent Applications entitled “Knitted Electrode Assembly For An Active Implantable Medical Device,” filed Aug. 28, 2009, “Knitted Electrode Assembly And Integrated Connector For An Active Implantable Medical Device,” filed Aug. 28, 2009, “Bonded Hermetic Feed Through For An Active Implantable Medical Device,” filed Aug. 28, 2009, “Stitched Components of An Active Implantable Medical Device,” filed Aug. 28, 2009, and “Electronics Package For An Active Implantable Medical Device,” filed Aug. 28, 2009. The contents of these applications are hereby incorporated by reference herein.
- While various embodiments of the present invention have been described above, it should be understood that they have been presented by way of example only, and not limitation. It will be apparent to persons skilled in the relevant art that various changes in form and detail may be made therein without departing from the spirit and scope of the invention. Thus, the breadth and scope of the present invention should not be limited by any of the above-described exemplary embodiments, but should be defined only in accordance with the following claims and their equivalents. All patents and publications discussed herein are incorporated in their entirety by reference thereto.
Claims (49)
Applications Claiming Priority (6)
Application Number | Priority Date | Filing Date | Title |
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AU2008904838A AU2008904838A0 (en) | 2008-09-17 | A Knitted or Woven Medical Device | |
AU2008904838 | 2008-09-17 | ||
AU2009901534A AU2009901534A0 (en) | 2009-04-08 | An implantable connector | |
AU2009901531 | 2009-04-08 | ||
AU2009901531A AU2009901531A0 (en) | 2009-04-08 | Multi-Channel Catheter or Implantable Electrode and Lead | |
AU2009901534 | 2009-04-08 |
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Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20100070007A1 (en) * | 2008-09-17 | 2010-03-18 | National Ict Australia Limited | Knitted electrode assembly and integrated connector for an active implantable medical device |
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Families Citing this family (48)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP2370150A1 (en) * | 2008-11-20 | 2011-10-05 | Cardiac Pacemakers, Inc. | Cell-repelling electrode having a structured surface |
PL2640262T3 (en) | 2010-11-17 | 2015-12-31 | Smart Solutions Tech S L | Sensor for acquiring physiological signals |
US9808196B2 (en) | 2010-11-17 | 2017-11-07 | Smart Solutions Technologies, S.L. | Sensors |
US20120136273A1 (en) * | 2010-11-29 | 2012-05-31 | Epilepsy Solutions, Llc | Apparatus and method for monitoring and analyzing brainwaves |
CA2761036C (en) * | 2010-12-08 | 2019-02-12 | Groupe Ctt Inc. | Fully integrated three-dimensional textile electrodes |
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US8781599B2 (en) | 2011-08-12 | 2014-07-15 | Cochlear Limited | Flexible protected lead |
AU2012334926B2 (en) | 2011-11-11 | 2017-07-13 | The Regents Of The University Of California | Transcutaneous spinal cord stimulation: noninvasive tool for activation of locomotor circuitry |
US20150164420A1 (en) * | 2013-02-25 | 2015-06-18 | King's Metal Fiber Technologies Co., Ltd. | Structure of three-dimensional electrically conductive fabric |
US20140246296A1 (en) * | 2013-03-01 | 2014-09-04 | King's Metal Fiber Technologies Co., Ltd. | Fabric pressure switch |
US9132736B1 (en) | 2013-03-14 | 2015-09-15 | Oshkosh Defense, Llc | Methods, systems, and vehicles with electromechanical variable transmission |
EP2968940B1 (en) | 2013-03-15 | 2021-04-07 | The Regents Of The University Of California | Multi-site transcutaneous electrical stimulation of the spinal cord for facilitation of locomotion |
WO2014165997A1 (en) * | 2013-04-10 | 2014-10-16 | Omsignal Inc. | Textile blank with seamless knitted electrode system |
CA2925754C (en) | 2013-09-27 | 2023-02-21 | The Regents Of The University Of California | Engaging the cervical spinal cord circuitry to re-enable volitional control of hand function in tetraplegic subjects |
DE102014105215A1 (en) * | 2014-04-11 | 2015-10-15 | Thermofer GmbH & Co. KG | heating element |
EP3183028A4 (en) | 2014-08-21 | 2018-05-02 | The Regents of the University of California | Regulation of autonomic control of bladder voiding after a complete spinal cord injury |
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EP3193759B1 (en) | 2014-09-05 | 2023-08-02 | Apyx Medical Corporation | Electrosurgical snare device |
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US11701959B2 (en) | 2015-02-17 | 2023-07-18 | Oshkosh Corporation | Inline electromechanical variable transmission system |
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US9650032B2 (en) | 2015-02-17 | 2017-05-16 | Oshkosh Corporation | Multi-mode electromechanical variable transmission |
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US10421350B2 (en) | 2015-10-20 | 2019-09-24 | Oshkosh Corporation | Inline electromechanical variable transmission system |
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CN109475300B (en) * | 2016-05-11 | 2022-05-03 | 森索医疗实验室有限公司 | Bidirectional wire interlocking method for electrode lead |
EP3421081B1 (en) | 2017-06-30 | 2020-04-15 | GTX medical B.V. | A system for neuromodulation |
DE102018101561B3 (en) * | 2018-01-24 | 2019-04-18 | Moduu GmbH | An electrically conductive yarn for garment electrodes, garment and method of making an electrically conductive garment for garments for stimulation and data collection of body areas |
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WO2019246579A1 (en) | 2018-06-21 | 2019-12-26 | Medtronic, Inc. | Ecap based control of electrical stimulation therapy |
US11129991B2 (en) | 2018-06-21 | 2021-09-28 | Medtronic, Inc. | ECAP based control of electrical stimulation therapy |
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ES2911465T3 (en) | 2018-11-13 | 2022-05-19 | Onward Medical N V | Control system for the reconstruction and/or restoration of a patient's movement |
EP3695878B1 (en) | 2019-02-12 | 2023-04-19 | ONWARD Medical N.V. | A system for neuromodulation |
US11931582B2 (en) | 2019-10-25 | 2024-03-19 | Medtronic, Inc. | Managing transient overstimulation based on ECAPs |
US11547855B2 (en) | 2019-10-25 | 2023-01-10 | Medtronic, Inc. | ECAP sensing for high frequency neurostimulation |
DE19211698T1 (en) | 2019-11-27 | 2021-09-02 | Onward Medical B.V. | Neuromodulation system |
GB2595552B (en) * | 2020-04-20 | 2024-01-10 | Prevayl Innovations Ltd | Fabric article and method of making the same |
US11857793B2 (en) | 2020-06-10 | 2024-01-02 | Medtronic, Inc. | Managing storage of sensed information |
US11707626B2 (en) | 2020-09-02 | 2023-07-25 | Medtronic, Inc. | Analyzing ECAP signals |
US11896828B2 (en) | 2020-10-30 | 2024-02-13 | Medtronic, Inc. | Implantable lead location using ECAP |
WO2023154259A2 (en) * | 2022-02-08 | 2023-08-17 | Cz Biohub Sf, Llc | Woven fabric bioelectronic device |
Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4944727A (en) * | 1986-06-05 | 1990-07-31 | Catheter Research, Inc. | Variable shape guide apparatus |
US5065757A (en) * | 1987-09-28 | 1991-11-19 | Dragisic Branislav M | Shielding to protect material from laser light |
US5628782A (en) * | 1992-12-11 | 1997-05-13 | W. L. Gore & Associates, Inc. | Method of making a prosthetic vascular graft |
US6221099B1 (en) * | 1992-05-20 | 2001-04-24 | Boston Scientific Corporation | Tubular medical prosthesis |
US20060106459A1 (en) * | 2004-08-30 | 2006-05-18 | Csaba Truckai | Bone treatment systems and methods |
US20080147155A1 (en) * | 2006-12-19 | 2008-06-19 | Quan Emerteq Corp. | Braided Electrical Lead |
US7815626B1 (en) * | 1998-06-12 | 2010-10-19 | Target Therapeutics, Inc. | Catheter with knit section |
Family Cites Families (54)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1144277A (en) * | 1914-02-27 | 1915-06-22 | W A Adams | Wheel dresser and truer. |
US2396099A (en) * | 1944-02-24 | 1946-03-05 | Metal Textile Corp | Electrical resistance and method of producing same |
US3773034A (en) | 1971-11-24 | 1973-11-20 | Itt Research Institute | Steerable catheter |
US4239046A (en) * | 1978-09-21 | 1980-12-16 | Ong Lincoln T | Medical electrode |
US4437109A (en) | 1980-11-07 | 1984-03-13 | General Electric Company | Silicon-on-sapphire body with conductive paths therethrough |
US4411277A (en) | 1981-04-28 | 1983-10-25 | Medtronic, Inc. | Implantable connector |
US4411276A (en) | 1981-04-28 | 1983-10-25 | Medtronic, Inc. | Implantable multiple connector |
US4549556A (en) | 1982-12-08 | 1985-10-29 | Cordis Corporation | Implantable lead |
US4543090A (en) | 1983-10-31 | 1985-09-24 | Mccoy William C | Steerable and aimable catheter |
DE3510212A1 (en) | 1985-03-21 | 1986-09-25 | Reinhard 7760 Radolfzell Wiggenhauser | Bioelectrically active textile support |
US4708149A (en) * | 1985-06-14 | 1987-11-24 | Jens Axelgaard | Electrical stimulation electrode |
US5102727A (en) * | 1991-06-17 | 1992-04-07 | Milliken Research Corporation | Electrically conductive textile fabric having conductivity gradient |
JPH07505316A (en) * | 1992-03-31 | 1995-06-15 | ボストン サイエンティフィック コーポレーション | medical wire |
US5466252A (en) | 1992-10-02 | 1995-11-14 | W. L. Gore & Associates, Inc. | Implantable lead |
US5300110A (en) * | 1992-10-15 | 1994-04-05 | Angeion Corporation | Dirk-based epicardial defibrillation electrode |
US5314451A (en) | 1993-01-15 | 1994-05-24 | Medtronic, Inc. | Replaceable battery for implantable medical device |
US5604976A (en) | 1994-10-18 | 1997-02-25 | Pi Medical Corporation | Method of making percutaneous connector for multi-conductor electrical cables |
US5679026A (en) | 1995-12-21 | 1997-10-21 | Ventritex, Inc. | Header adapter for an implantable cardiac stimulation device |
WO1997028668A1 (en) | 1996-01-31 | 1997-08-07 | Cochlear Limited | Thin film fabrication technique for implantable electrodes |
JPH10118188A (en) * | 1996-10-24 | 1998-05-12 | Terumo Corp | Medical treatment appliance for insertion into celom and its production |
US6381482B1 (en) * | 1998-05-13 | 2002-04-30 | Georgia Tech Research Corp. | Fabric or garment with integrated flexible information infrastructure |
US6210771B1 (en) * | 1997-09-24 | 2001-04-03 | Massachusetts Institute Of Technology | Electrically active textiles and articles made therefrom |
US6231516B1 (en) * | 1997-10-14 | 2001-05-15 | Vacusense, Inc. | Endoluminal implant with therapeutic and diagnostic capability |
US6198969B1 (en) | 1998-02-12 | 2001-03-06 | Advanced Bionics Corporation | Implantable connector for multi-output neurostimulators |
US6321126B1 (en) | 1998-12-07 | 2001-11-20 | Advanced Bionics Corporation | Implantable connector |
NO311317B1 (en) * | 1999-04-30 | 2001-11-12 | Thin Film Electronics Asa | Apparatus comprising electronic and / or optoelectronic circuits and method of realizing and / or integrating circuits of this kind in the apparatus |
DE69940081D1 (en) | 1999-05-21 | 2009-01-22 | Cochlear Ltd | Electrode matrix for cochlear implant |
US6358238B1 (en) * | 1999-09-02 | 2002-03-19 | Scimed Life Systems, Inc. | Expandable micro-catheter |
US6649886B1 (en) * | 2002-05-11 | 2003-11-18 | David Kleshchik | Electric heating cloth and method |
EP1324692A1 (en) | 2000-10-10 | 2003-07-09 | MAGILL, Alan Remy | Health monitoring |
CA2443782A1 (en) | 2001-05-07 | 2002-11-14 | Dusan Milojevic | Process for manufacturing electrically conductive components |
US6662035B2 (en) | 2001-09-13 | 2003-12-09 | Neuropace, Inc. | Implantable lead connector assembly for implantable devices and methods of using it |
US6860122B2 (en) * | 2002-03-28 | 2005-03-01 | F&S, Llc | Fabric with pain-relieving characteristics and structures therefrom, and method |
US20030186608A1 (en) * | 2002-03-28 | 2003-10-02 | Arthur Goldberg | Fabric with pain-relieving characteristics and structures fabricated therefrom, and method |
GB0230361D0 (en) | 2002-12-27 | 2003-02-05 | Koninkl Philips Electronics Nv | Electrode arrangement |
US7135227B2 (en) | 2003-04-25 | 2006-11-14 | Textronics, Inc. | Electrically conductive elastic composite yarn, methods for making the same, and articles incorporating the same |
GB0311320D0 (en) * | 2003-05-19 | 2003-06-25 | Univ Manchester | Knitted transducer devices |
EP1491299A1 (en) | 2003-06-26 | 2004-12-29 | Abb Ab | Robot wrist comprising a plurality of parts arranged in series and driven by bevel gears |
US7534127B2 (en) | 2004-01-05 | 2009-05-19 | Cochlear Limited | Implantable connector |
CN1934302B (en) * | 2004-03-08 | 2011-04-06 | Kb世联株式会社 | Woven or knitted fabric, diaphragm for speaker, and speaker |
US7682381B2 (en) * | 2004-04-23 | 2010-03-23 | Boston Scientific Scimed, Inc. | Composite medical textile material and implantable devices made therefrom |
US7410497B2 (en) * | 2004-12-14 | 2008-08-12 | Boston Scientific Scimed, Inc. | Stimulation of cell growth at implant surfaces |
US20060218778A1 (en) * | 2005-04-04 | 2006-10-05 | Govindaraj Jawahar | Flexible conducting thread |
AU2006247018A1 (en) * | 2005-05-19 | 2006-11-23 | Kaho Abe | Discreet interface system |
US20060265049A1 (en) * | 2005-05-19 | 2006-11-23 | Gray Robert W | Stent and MR imaging process and device |
US7720904B2 (en) * | 2005-05-27 | 2010-05-18 | Microsoft Corporation | Entity projection |
US20060281382A1 (en) * | 2005-06-10 | 2006-12-14 | Eleni Karayianni | Surface functional electro-textile with functionality modulation capability, methods for making the same, and applications incorporating the same |
US20090099441A1 (en) * | 2005-09-08 | 2009-04-16 | Drexel University | Braided electrodes |
US20070089800A1 (en) * | 2005-10-24 | 2007-04-26 | Sensatex, Inc. | Fabrics and Garments with Information Infrastructure |
US7654843B2 (en) | 2006-02-28 | 2010-02-02 | Medtronic, Inc. | Connector assembly with internal seals and manufacturing method |
DE102006053729A1 (en) * | 2006-11-15 | 2008-05-21 | Biotronik Crm Patent Ag | Contact assembly, contact assembly, implantable device and electrode lead |
US9044592B2 (en) * | 2007-01-29 | 2015-06-02 | Spinal Modulation, Inc. | Sutureless lead retention features |
US8897888B2 (en) * | 2008-09-17 | 2014-11-25 | Saluda Medical Pty Limited | Knitted electrode assembly and integrated connector for an active implantable medical device |
WO2010117381A1 (en) * | 2009-04-08 | 2010-10-14 | National Ict Australia Limited (Nicta) | Stitched components of an active implantable medical device |
-
2009
- 2009-08-28 US US12/549,457 patent/US8897888B2/en active Active
- 2009-08-28 EP EP09792067.2A patent/EP2362799B1/en active Active
- 2009-08-28 WO PCT/US2009/055400 patent/WO2010033370A2/en active Application Filing
- 2009-08-28 EP EP09792070A patent/EP2361113A2/en not_active Withdrawn
- 2009-08-28 EP EP09792068.0A patent/EP2362800B1/en active Active
- 2009-08-28 WO PCT/US2009/055392 patent/WO2010033368A1/en active Application Filing
- 2009-08-28 WO PCT/US2009/055393 patent/WO2010033369A1/en active Application Filing
- 2009-08-28 AU AU2009293506A patent/AU2009293506B2/en not_active Ceased
- 2009-08-28 US US12/549,801 patent/US20100069835A1/en not_active Abandoned
- 2009-08-28 US US12/549,899 patent/US8923984B2/en active Active
- 2009-08-28 AU AU2009293507A patent/AU2009293507B2/en not_active Ceased
- 2009-08-28 AU AU2009293508A patent/AU2009293508A1/en not_active Abandoned
-
2014
- 2014-10-30 US US14/528,817 patent/US9283373B2/en active Active
Patent Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4944727A (en) * | 1986-06-05 | 1990-07-31 | Catheter Research, Inc. | Variable shape guide apparatus |
US5065757A (en) * | 1987-09-28 | 1991-11-19 | Dragisic Branislav M | Shielding to protect material from laser light |
US6221099B1 (en) * | 1992-05-20 | 2001-04-24 | Boston Scientific Corporation | Tubular medical prosthesis |
US5628782A (en) * | 1992-12-11 | 1997-05-13 | W. L. Gore & Associates, Inc. | Method of making a prosthetic vascular graft |
US7815626B1 (en) * | 1998-06-12 | 2010-10-19 | Target Therapeutics, Inc. | Catheter with knit section |
US20060106459A1 (en) * | 2004-08-30 | 2006-05-18 | Csaba Truckai | Bone treatment systems and methods |
US20080147155A1 (en) * | 2006-12-19 | 2008-06-19 | Quan Emerteq Corp. | Braided Electrical Lead |
Cited By (48)
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AU2009293506A1 (en) | 2010-03-25 |
EP2362800B1 (en) | 2014-04-09 |
AU2009293507A1 (en) | 2010-03-25 |
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US8923984B2 (en) | 2014-12-30 |
WO2010033369A1 (en) | 2010-03-25 |
EP2362799B1 (en) | 2017-10-11 |
US20100070008A1 (en) | 2010-03-18 |
EP2361113A2 (en) | 2011-08-31 |
US20100070007A1 (en) | 2010-03-18 |
US8897888B2 (en) | 2014-11-25 |
EP2362800A1 (en) | 2011-09-07 |
AU2009293508A1 (en) | 2010-03-25 |
WO2010033370A3 (en) | 2010-06-24 |
AU2009293506B2 (en) | 2015-10-22 |
WO2010033370A2 (en) | 2010-03-25 |
AU2009293507B2 (en) | 2015-03-12 |
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