Connect public, paid and private patent data with Google Patents Public Datasets

Vacuum mandrel for use in fabricating an implantable electrode

Download PDF

Info

Publication number
US20070092591A1
US20070092591A1 US11257339 US25733905A US2007092591A1 US 20070092591 A1 US20070092591 A1 US 20070092591A1 US 11257339 US11257339 US 11257339 US 25733905 A US25733905 A US 25733905A US 2007092591 A1 US2007092591 A1 US 2007092591A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
electrode
groove
vacuum
mandrel
surface
Prior art date
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.)
Abandoned
Application number
US11257339
Inventor
Shawn Kollatschny
Joseph Sciacca
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Cyberonics Inc
Original Assignee
Cyberonics Inc
Priority date (The priority date 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 date listed.)
Filing date
Publication date

Links

Images

Classifications

    • BPERFORMING OPERATIONS; TRANSPORTING
    • B29WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE, IN GENERAL
    • B29CSHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
    • B29C70/00Shaping composites, i.e. plastics material comprising reinforcements, fillers or preformed parts, e.g. inserts
    • B29C70/68Shaping composites, i.e. plastics material comprising reinforcements, fillers or preformed parts, e.g. inserts by incorporating or moulding on preformed parts, e.g. inserts, layers, e.g. foam blocks
    • B29C70/72Encapsulating inserts having non-encapsulated projections, e.g. extremities, terminal portions of electrical components

Abstract

A vacuum mandrel for use in fabricating an implantable electrode comprises a hollow body member and a first groove provided radially on an outer surface of the hollow body member. The first groove is adapted to receive an implantable electrode and retain the electrode in place with a vacuum pressure during an elastomeric encapsulation of the electrode. The vacuum mandrel further comprises a vacuum port provided in the first groove.

Description

    BACKGROUND
  • [0001]
    Many types of implantable medical devices, such as pacemakers, defibrillators, and vagus nerve stimulators, have leads connected to an electronics unit. The distal end of the lead typically comprises or is coupled to one or more conductive electrodes. Such electrodes are typically fragile and thus should be handled carefully by the implanting surgeon when attaching the electrode to the relevant tissue to be stimulated. Fabrication of such electrodes is often a painstaking, time-consuming process.
  • BRIEF SUMMARY
  • [0002]
    A vacuum mandrel is disclosed that is used during the fabrication of an implantable conductive electrode. In accordance with at least one embodiment, the mandrel comprises a hollow body member having an axis, a first groove provided radially on an outer surface of the hollow body member, and a vacuum port provided in the groove. The first groove is adapted to receive the implantable electrode. In a particular embodiment, the first groove is a spiral groove around the outer periphery of the hollow body. By application of vacuum pressure through the hollow body member and the vacuum port, an electrode can be retained in place in the first groove while an elastomer, or another type of insulating material, is applied to the electrode. One or more second grooves, which are preferably longitudinal relative to the axis of the hollow body member, may be provided on opposing ends of the spiral groove to receive the elastomer and thereby form gripping members that an implantation surgeon can use when coupling the resulting electrode to a neural tissue such as a vagus nerve.
  • [0003]
    In accordance with another embodiment, a method comprises locating a conductive electrode formed on end of a lead adjacent a first, preferably spiral, groove in a vacuum mandrel, retaining the conductive electrode in the first groove through vacuum pressure applied through the at least one port, and applying an insulator over the conductive electrode while the electrode is retained in place in the first groove. The first groove contains at least one port through which the vacuum is applied to retain the conductive electrode in place.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • [0004]
    For a detailed description of exemplary embodiments of the invention, reference will now be made to the accompanying drawings in which:
  • [0005]
    FIGS. 1 a-1 c show a vacuum mandrel in accordance with a preferred embodiment of the invention;
  • [0006]
    FIG. 2 shows an enlarged portion of the vacuum mandrel;
  • [0007]
    FIG. 3 shows a side of the vacuum mandrel opposite from that shown in FIGS. 1 and 2;
  • [0008]
    FIG. 4 shows a ribbon electrode provided on a lead;
  • [0009]
    FIG. 5 shows a view of the vacuum mandrel with an electrode wrapped around a groove formed in the mandrel in accordance with a preferred embodiment of the invention;
  • [0010]
    FIG. 6 illustrates the connection between the vacuum mandrel and a vacuum source;
  • [0011]
    FIG. 7 shows a lead with coil electrode formed thereon and elastomer formed on a portion of the electrode in accordance with a preferred embodiment of the invention;
  • [0012]
    FIG. 8 shows a completed electrode assembly in accordance with embodiments of the invention; and
  • [0013]
    FIG. 9 shows an enlarged portion of FIG. 7.
  • DETAILED DESCRIPTION
  • [0014]
    The following discussion is directed to various embodiments of the invention. Although one or more of these embodiments may be preferred, the embodiments disclosed should not be interpreted, or otherwise used, as limiting the scope of the disclosure, including the claims. In addition, one skilled in the art will understand that the following description has broad application, and the discussion of any embodiment is meant only to be exemplary of that embodiment, and not intended to intimate that the scope of the disclosure, including the claims, is limited to that embodiment. Any numerical dimensions provided herein are merely exemplary and do not limit the scope of this disclosure or the claims that follow.
  • [0015]
    FIG. 1 a shows a plan view of a vacuum mandrel 10 in accordance with a preferred embodiment of the invention. The mandrel 10 comprises an elongate hollow body member formed from stainless steel or tool steel and has an exterior finish of nickel plating with Teflon®. As illustrated FIG. 1 b, the mandrel 10 is generally circular in cross section, although other cross sectional shapes are possible as well. As shown, the vacuum mandrel 10 comprises a plurality of segments 12, 14, and 16. Segment 12 has a diameter D3 that, as is evident from FIG. 1 a, is greater than the diameter D1 of segment 16. In accordance with at least one embodiment, D1 is approximately 0.171 inches and D3 is approximately 0.50 inches. The length L1 of segment 12 preferably approximately is 2.094 inches and the length L3 of segment 16 preferably is approximately 0.875 inches. Segment 12 includes a tip portion 11 provided at one end as shown in FIG. 1 a. Tip portion 11 has a diameter D2 of approximately 0.312 inches and a length L4 of approximately 0.625 inches. Segment 14 has a generally frustoconical shape that transitions between segments 12 and 16. The slope of segment 14 preferably is at an angle A1 of approximately 60 degrees as shown in FIG. 1 a, and the length L2 of segment 14 is approximately 0.281 inches. Mandrel 10 may be formed as a unitary hollow body or in multiple pieces that are joined together in a suitable manner (e.g., by welding).
  • [0016]
    Segment 16 includes a first, preferably spiral (e.g., helical) groove 20 formed radially about the outer surface of segment 16 as shown in FIG. 1 a. FIG. 2 shows an enlarged view of segment 16 of the vacuum mandrel. In the embodiments of FIGS. 1 and 2, the first groove 20 comprises a spiral groove having about 2.5 revolutions around the outer surface of the mandrel. It will be appreciated by persons of skill in the art that non-spiral grooves can be used, and that where a spiral groove is employed the number of revolutions of the groove can be varied. The first groove 20 can have any dimensions that are suitable for the application described herein. In one embodiment, the groove 20 has a generally flat bottom surface 21 and flat side walls 23 formed generally perpendicular to the bottom surface 21. In this embodiment, the groove has a rectangular cross-sectional shape, with a width W1 of approximately 0.053 to 0.058 inches and a height H1 of approximately 0.024 to 0.028 inches.
  • [0017]
    As best shown in FIG. 2, a raised surface 25 is provided within groove 20. The raised surface 25 preferably is formed integrally with the segment 12 although, in other embodiments, the raised surface can be a separately formed component that is then adhered in a suitable manner (e.g., welded, glued, etc.) to surface 21. The raised surface 25 preferably has a height relative to the bottom surface 21 of approximately 0.002 to 0.003 inches and a width W2 that is less than the width W1 of the groove 20. In one embodiment, the width W2 of the raised surface 25 may range from approximately 0.028 to 0.032 inches. In such embodiments, therefore, the width W2 of the raised surface is approximately 45% to 60% of the width W1 of the first groove 20. At least one vacuum port 22 is provided within the first groove 20. In accordance with one embodiment, eight vacuum ports 22 are provided, although any number of ports sufficient to retain an electrode in place in the first groove may be employed. Preferably, the vacuum ports 22 comprise bore holes that extend through the raised surface 25 and into the hollow interior portion of segment 16. In at least one embodiment, the eight radially extending vacuum ports 22 are spaced apart in increments of 30 degrees.
  • [0018]
    Referring to FIG. 1 a, segment 12 of mandrel 10 comprises a lead groove 36 provided longitudinally along at least some or all of the length of segment 12. Referring to FIGS. 1 a and 1 c, the lead groove 36 that is provided longitudinally along segment 12 relative to a plane that contains central axis 19 preferably is formed in the outer surface of the segment 12 at a location disposed on an angular measure A2 from the plane. In one embodiment, the lead groove 36 preferably has a depth D8 of approximately 0.089 inches and a width W3 of approximately 0.063 inches. As will be explained above, an implantable lead resides in the lead groove 36 during fabrication of an electrode. Thus, the lead groove 36 has an engaging surface that engages the electrode during manufacturing.
  • [0019]
    The interior of the hollow body member is shown in FIG. 1 b. In the embodiment depicted, the dimensions of the hollow interior of the body vary, although persons of skill in the art will appreciate that various hollow chamber designs may be employed. The hollow interior of segment 12 is shown with a diameter D4 of approximately 0.19 inches. The hollow interior of segments 14 and 16 has a diameter D5 of approximately 0.06 inches. The hollow interior of segment 16 extends to the end of, or just beyond the end of, the first groove 20. The hollow interior may also extend throughout the hollow body and be sealed off via a plug fastened by various techniques such as welding, screw threads, or adhesive.
  • [0020]
    FIGS. 1 a and 2 also show one or more second grooves 30, 32 formed at, or near, opposing ends of first groove 20. Second grooves 30 and 32 may advantageously have a different cross-sectional shape than groove 20. Each second groove 30, 32 preferably is curved and extends circumferentially preferably for less than one complete revolution around segment 16 and, in some embodiments, extends for three-fourths of one revolution. As better shown in FIG. 3, each second groove 30 and 32 ends in a longitudinal groove portion 31 and 33, respectively. Each second groove 30, 32 may have a pitch of approximately from 0.65 to 0.70, a radius of curvature of approximately 0.020 inches and a depth D9 (shown in FIG. 2) of approximately 0.018 inches. Each of the longitudinal groove portions 31 and 33 may have a length D7 (FIG. 3) of approximately 0.074 inches. Further, each second groove 30, 32 begins at or near an end of the first groove 20. For example, second groove 32 begins at end 37 (FIG. 2) of first groove 20. The beginning of each second groove 30, 32 preferably is centered within first groove 20 thereby forming a continuous groove within the body segment 16. In one embodiment, each second groove 30 and 32 preferably comprises a spiral curved groove that extends for three-fourths of a revolution and the central flat-bottom groove 20 (having bottom surface 21) extends for 2.5 revolutions. Thus, the combination of the two spiral curved second grooves 30 and 32 and the central flat first groove 20 form a groove that extends for, in a particular embodiment, four total revolutions around the body segment 16.
  • [0021]
    The vacuum mandrel 10 may be used during a manufacturing process for an electrode. The electrode preferably comprises an electrode such as may be used in conjunction with an implantable medical device such as a vagus nerve stimulator. FIG. 4 shows an electrode 52 provided on an end of lead 50. The electrode 52 preferably is an electrically conductive ribbon electrode that, when further processed as described below, can be attached to a nerve or nerve bundle such as a cranial nerve (e.g., a vagus nerve). The electrode 52 preferably comprises a conductive ribbon electrode formed from platinum, platinum-iridium, or other suitable material. In a particular embodiment, the electrode 52 is approximately 0.040 inches wide by approximately 0.500 inches long by approximately 0.0005 inches thick. The electrode 52 is coupled (e.g., welded) to the lead 50 at approximately the mid-point of the electrode. The lead 50 comprises an electrical conductor that is covered by an insulator and that electrically couples the implanted device (not shown) to electrode 52 provided on the end of the lead. When implanted, the electrode 52 is placed in contact with the tissue to be stimulated. Through the lead 50 and electrode 52, the implanted device is able to deliver electrical current to the tissue to be stimulated.
  • [0022]
    FIG. 5 shows the body segment 16 of the vacuum mandrel 10 with the lead 50 and electrode 52 disposed thereon. The electrode 52 is placed on the mandrel and wrapped around and located within at least a portion of the first groove 20. By residing in the first groove 20, the ribbon electrode covers at least one or more, and preferably all, of the vacuum ports 22. FIG. 5 also shows the lead 50 extending down the length of the segment 16. The remaining length of the lead rests in the longitudinal lead groove 36 formed in segment 12 (FIG. 1 a).
  • [0023]
    FIG. 6 illustrates the vacuum mandrel 10 coupled to a vacuum tube 62 that, in turn, connects to a vacuum source 60. The vacuum tube 62 preferably comprises a flexible hose of rubber or other suitable material. The tip 11 of the vacuum mandrel is inserted into the vacuum tube 62. Once the vacuum source 60 is turned on, the vacuum pressure thereby created through the mandrel 10 and vacuum ports 22 will cause the ribbon electrode to be retained in place during the next part of the manufacturing process. The raised surface 25 provides an engaging surface for the electrode in groove 20 and enables the electrode edges to be encapsulated by the elastomer/insulator. In one embodiment, the vacuum pressure is approximately 28 inches Hg, although the pressure can be varied as desired.
  • [0024]
    With the electrode held in place in first groove 20 by vacuum pressure, the next step in the manufacturing process is to apply an insulator such as an elastomer to all, or substantially all, of the lengths of first groove 20, and second grooves 30 and 32, thereby covering the ribbon electrode with the insulator. The ribbon electrode 52 preferably does not extend throughout the combined lengths of first groove 20 and second grooves 30 and 32, and as such a portion of the insulator fills the grooves beyond the reach of the ribbon electrode. The insulator is applied by spraying or pouring by methods well known in the art. In a particular embodiment, the insulator comprises a silicone elastomer. However, persons of skill in the art will appreciate that other elastomers, and other insulators may be used.
  • [0025]
    The insulator is then permitted to cure. Once cured, vacuum source is turned off and the lead 50 and insulator-covered electrode 52 assembly can be removed from the vacuum mandrel. Examples of the completed electrodes 52 are shown in FIGS. 7 and 8. FIG. 7 shows an electrode with a cut away portion to better illustrate the elastomer 70 covering the ribbon electrode 52. Because the elastomer cured while the electrode 52 was still wrapped in the spiral first groove 20 of the vacuum mandrel, the resulting electrode generally retains the shape of the first groove 20. Other shapes are, of course, possible depending upon the needs of the particular application in which the electrode will be used. Further, because the elastomer covered the exposed electrode 52 and was not able to penetrate between the electrode 52 and the raised surface 25 of the first groove 20, one side of the electrode is not covered with elastomer, i.e., the interior surface 71 of the spirally formed electrode. This interior surface is the surface that will be in contact with the body tissue (e.g., a vagus nerve) being stimulated. The elastomer generally is an electrical insulator and thus the surface of the electrode opposite the body tissue is electrically insulated from other body tissues while the surface of the electrode touching the nerve is in electrical contact with the nerve.
  • [0026]
    The raised surface 25 on which the ribbon electrode rests while the elastomer is applied causes elastomer to fill the sides of the first groove 20 adjacent the electrode. As a result, some of the elastomer, such as that shown at reference numeral 90, covers the side edges of the ribbon electrode and thereby covers any sharp edges that might otherwise cut into the nerve to which the electrode is attached. The relationship between the elastomer and the edges of the electrode are better shown in the enlarged view of FIG. 9.
  • [0027]
    Reference numeral 80 in FIG. 7 shows the elastomer that was applied to the spiral second grooves 30 and 32. The width of second grooves 30 and 32 preferably is less than the width of first groove 20 as measured in the direction parallel to axis 19. As such, as shown in FIG. 7, the two elastomer end portions 80 of the electrode assembly are narrower than the central portion that contains the ribbon electrode.
  • [0028]
    The longitudinal groove portions 31 and 33 (FIG. 3) are also filled with elastomer. After the elastomer cures and the electrode is removed from the mandrel, the elastomer that filled the longitudinal groove portions 31 and 33 form gripping portions 74 and 76, respectively. The gripping portions 74 and 76 are used during implantation to attach the electrode to the nerve. More specifically, the gripping portions 74 and 76 are pulled in opposite directions using, for example, forceps. Pulling the gripping surfaces 74 and 76 apart in this manner stretches the spiral electrode so that it can be wrapped around the nerve. Once wrapped around the nerve, the gripping portions 74 and 76 are released and the spring-like nature of the spiral electrode 52 causes the electrode naturally to attach itself to the nerve.
  • [0029]
    Another prior type of spiral electrode included a thread suture embedded in the elastomer. The ends of the suture protruded from the electrode and functioned as gripping mechanisms for the implantation surgeon. Unfortunately, embedding a thread suture in a spiral electrode adds complexity and time to the manufacturing process of such an electrode. Gripping portions 74 and 76 obviate the need for such a thread suture, although one could be included if desired. Without such a thread suture, the manufacturing of the disclosed electrode is made easier and less time consuming.
  • [0030]
    The above discussion is meant to be illustrative of the principles and various embodiments of the present invention. Numerous variations and modifications will become apparent to those skilled in the art once the above disclosure is fully appreciated. It is intended that the following claims be interpreted to embrace all such variations and modifications.

Claims (23)

1. A vacuum mandrel for use in fabricating an implantable electrode, comprising:
a hollow body member having an outer surface;
a first groove on said outer surface, adapted to receive an electrode member; and
a vacuum port provided in said first groove.
2. The vacuum mandrel of claim 1 wherein said first groove is a spiral groove.
3. The vacuum mandrel of claim 2 further comprising a plurality of vacuum ports provided in said spiral groove.
4. The vacuum mandrel of claim 1 further comprising a longitudinal groove portion provided at an end of said first groove.
5. The vacuum mandrel of claim 1 further comprising a pair of second grooves provided at or near opposing ends of said first groove, each of said second grooves ending in a longitudinal groove portion.
6. The vacuum mandrel of claim 5 wherein each of said second grooves is provided on said hollow body member for less than one revolution.
7. The vacuum mandrel of claim 1 further comprising a raised surface in said first groove through which said vacuum port is provided.
8. The vacuum mandrel of claim 7 wherein the first groove comprises a first width and the raised surface comprises a second width that is less than the first width.
9. The vacuum mandrel of claim 7 wherein the raised surface has a height of approximately 0.002 to 0.003 inches.
10. The vacuum mandrel of claim 1 wherein said hollow body member comprises a distal segment and a proximal segment, and wherein said first groove is located in said distal segment.
11. An electrode fabrication system, comprising:
the vacuum mandrel of claim 10;
a lead;
an electrode coupled to an end of said lead, said electrode being positioned in said first groove of said vacuum mandrel;
a longitudinal groove provided along at least a portion of the distal segment of said hollow body member, in which at least a portion of the lead is positioned.
12. An electrode fabrication system comprising:
the vacuum mandrel of claim 1;
a vacuum source in communication with said vacuum port via said hollow body member;
an electrode positioned over said vacuum port in said first groove and retained in position through the application of vacuum pressure by said vacuum source, to thereby permit an elastomer to-be applied to said first groove to cover said electrode.
13. The vacuum mandrel of claim 1 wherein said first groove has a width of approximately 0.053 to 0.058 inches.
14. The vacuum mandrel of claim 1 wherein said vacuum port has a diameter of approximately 0.018 inches.
15. A method of making an electrode, comprising:
providing a mandrel comprising a first groove in an outer surface thereof, and a vacuum port in said first groove,
providing an electrode coupled to an end of a lead;
positioning said electrode in said first groove over said vacuum port; and
retaining said electrode in said first groove through vacuum pressure applied through said vacuum port; and
applying an elastomer over said conductive electrode while said electrode is retained in said first groove.
16. The method of claim 16 wherein said vacuum mandrel further comprises at least one longitudinal groove formed at one end of said spiral groove, and wherein applying said elastomer comprises applying said elastomer to said and least one longitudinal groove.
17. An electrode manufactured according to a method comprising:
locating a conductive ribbon electrode in a first groove of a hollow body member, said groove containing at least one vacuum port; and
retaining said conductive electrode in said spiral groove through vacuum pressure applied through said at least one vacuum port; and
applying an elastomer over said conductive electrode while said electrode is retained in place.
18. The electrode of claim 17 further manufactured by applying the elastomer in at least one longitudinal groove portion formed on the hollow body, the elastomer applied to said a least one longitudinal groove portion comprising a gripping surface to be used during implantation.
19. An apparatus for holding an implantable electrode in place during a manufacturing process, comprising:
an elongate body having an outer surface and a hollow interior portion;
a vacuum source in fluid communication with said hollow interior portion;
a channel formed in said outer surface and extending helically about said elongate body, said channel comprising an engaging surface for engaging the implantable electrode; and
at least one bore extending between said hollow interior portion and said engaging surface of said channel such that said bore and said hollow interior portion are in fluid communication.
20. The apparatus of claim 19 wherein the channel has a rectangular cross-sectional shape.
21. The apparatus of claim 19 wherein the engaging surface is raised from a bottom surface of said channel.
22. The apparatus of claim 19 wherein said channel extends for approximately 2.5 turns about said outer surface.
23. The apparatus of claim 19 wherein said elongate body has a longitudinal axis and said channel has opposing ends that extend in a direction generally parallel to the axis.
US11257339 2005-10-24 2005-10-24 Vacuum mandrel for use in fabricating an implantable electrode Abandoned US20070092591A1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US11257339 US20070092591A1 (en) 2005-10-24 2005-10-24 Vacuum mandrel for use in fabricating an implantable electrode

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US11257339 US20070092591A1 (en) 2005-10-24 2005-10-24 Vacuum mandrel for use in fabricating an implantable electrode
US12652185 US7901613B2 (en) 2005-10-24 2010-01-05 Vacuum mandrel for use in fabricating an implantable electrode

Publications (1)

Publication Number Publication Date
US20070092591A1 true true US20070092591A1 (en) 2007-04-26

Family

ID=37985667

Family Applications (2)

Application Number Title Priority Date Filing Date
US11257339 Abandoned US20070092591A1 (en) 2005-10-24 2005-10-24 Vacuum mandrel for use in fabricating an implantable electrode
US12652185 Expired - Fee Related US7901613B2 (en) 2005-10-24 2010-01-05 Vacuum mandrel for use in fabricating an implantable electrode

Family Applications After (1)

Application Number Title Priority Date Filing Date
US12652185 Expired - Fee Related US7901613B2 (en) 2005-10-24 2010-01-05 Vacuum mandrel for use in fabricating an implantable electrode

Country Status (1)

Country Link
US (2) US20070092591A1 (en)

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2951390B1 (en) * 2009-10-20 2012-01-06 Areva Nc Device for changing electrode has improved safety
US9679330B2 (en) * 2012-06-10 2017-06-13 Apple Inc. Interface for enhanced continuity of browsing experience

Citations (88)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1404042A (en) * 1922-01-17 Everard f
US3089600A (en) * 1961-05-26 1963-05-14 Rca Corp Transfer apparatus
US3421511A (en) * 1965-12-10 1969-01-14 Medtronic Inc Implantable electrode for nerve stimulation
US3468648A (en) * 1966-07-08 1969-09-23 Owens Illinois Inc Method and apparatus for forming hollow glass articles
US3539322A (en) * 1967-03-23 1970-11-10 Quickfit & Quartz Ltd Method and apparatus for producing an internal precision sealing surface in hollow glass bodies
US3743457A (en) * 1971-07-13 1973-07-03 Acme Hamilton Mfg Corp Stock flow control means for extruders and the like
US3760812A (en) * 1971-03-19 1973-09-25 Univ Minnesota Implantable spiral wound stimulation electrodes
US3922134A (en) * 1973-12-17 1975-11-25 Robintech Inc Pipe bending mandrel
US4106744A (en) * 1975-09-11 1978-08-15 Analog Technology Corporation Mandrel for formation of mass spectrometer filter
US4384926A (en) * 1982-03-25 1983-05-24 Amp Incorporated Plating interior surfaces of electrical terminals
US4413636A (en) * 1979-11-19 1983-11-08 Phillip R. Beutel Catheter
US4427498A (en) * 1982-03-25 1984-01-24 Amp Incorporated Selective plating interior surfaces of electrical terminals
US4459989A (en) * 1981-06-30 1984-07-17 Neuromed, Inc. Non-invasive multiprogrammable tissue stimulator and methods for use
US4484586A (en) * 1982-05-27 1984-11-27 Berkley & Company, Inc. Hollow conductive medical tubing
US4490104A (en) * 1982-11-22 1984-12-25 Borg-Warner Chemicals, Inc. Apparatus for separating a low viscosity material from a high _viscosity material
US4508053A (en) * 1983-01-05 1985-04-02 Xis, Incorporated Vacuum deposition apparatus for manufacturing selenium photoreceptors
US4573481A (en) * 1984-06-25 1986-03-04 Huntington Institute Of Applied Research Implantable electrode array
US4590946A (en) * 1984-06-14 1986-05-27 Biomed Concepts, Inc. Surgically implantable electrode for nerve bundles
US4602624A (en) * 1984-10-11 1986-07-29 Case Western Reserve University Implantable cuff, method of manufacture, and method of installation
US4608985A (en) * 1984-10-11 1986-09-02 Case Western Reserve University Antidromic pulse generating wave form for collision blocking
US4612934A (en) * 1981-06-30 1986-09-23 Borkan William N Non-invasive multiprogrammable tissue stimulator
US4628942A (en) * 1984-10-11 1986-12-16 Case Western Reserve University Asymmetric shielded two electrode cuff
US4643658A (en) * 1984-09-26 1987-02-17 Gordon John H Expanding mandrel
US4649936A (en) * 1984-10-11 1987-03-17 Case Western Reserve University Asymmetric single electrode cuff for generation of unidirectionally propagating action potentials for collision blocking
US4789327A (en) * 1988-02-25 1988-12-06 Harry Chan Adjustable pipe extrusion die with internal cooling
US4822272A (en) * 1986-10-17 1989-04-18 Agency Of Industrial Science And Technology Mandrel for use in a manufacture of an article made of composite material
US4832048A (en) * 1987-10-29 1989-05-23 Cordis Corporation Suction ablation catheter
US4850356A (en) * 1980-08-08 1989-07-25 Darox Corporation Defibrillator electrode system
US4860616A (en) * 1988-06-17 1989-08-29 Smith Winford L Method and apparatus for the manufacture of rotary sheet dies
US4920979A (en) * 1988-10-12 1990-05-01 Huntington Medical Research Institute Bidirectional helical electrode for nerve stimulation
US4940065A (en) * 1989-01-23 1990-07-10 Regents Of The University Of California Surgically implantable peripheral nerve electrode
US4944906A (en) * 1988-10-11 1990-07-31 Spirex Corporation Methods of injection molding and extruding wet hygroscopic ionomers
US4979511A (en) * 1989-11-03 1990-12-25 Cyberonics, Inc. Strain relief tether for implantable electrode
US5003975A (en) * 1988-04-19 1991-04-02 Siemens-Pacesetter, Inc. Automatic electrode configuration of an implantable pacemaker
US5063018A (en) * 1990-06-04 1991-11-05 Cordis Corporation Extrusion method
US5095905A (en) * 1990-06-07 1992-03-17 Medtronic, Inc. Implantable neural electrode
US5143067A (en) * 1990-06-07 1992-09-01 Medtronic, Inc. Tool for implantable neural electrode
US5176866A (en) * 1989-02-28 1993-01-05 Asahi Kasei Kogyo Kabushiki Kaisha Process for producing a resin product having a bent hollow portion and a core usable for the same process
US5215089A (en) * 1991-10-21 1993-06-01 Cyberonics, Inc. Electrode assembly for nerve stimulation
US5251634A (en) * 1991-05-03 1993-10-12 Cyberonics, Inc. Helical nerve electrode
US5460501A (en) * 1994-04-07 1995-10-24 Advanced Drainage Systems, Inc. Pipe production line for the manufacture of plastic pipe
US5515848A (en) * 1991-10-22 1996-05-14 Pi Medical Corporation Implantable microelectrode
US5531778A (en) * 1994-09-20 1996-07-02 Cyberonics, Inc. Circumneural electrode assembly
US5624693A (en) * 1996-01-16 1997-04-29 Outboard Marine Corporation Molding apparatus with combined venting and flushing valve
US5630968A (en) * 1995-06-07 1997-05-20 The Japan Steel Works, Ltd. Water-injection foaming devolatilizing method
US5874116A (en) * 1996-04-19 1999-02-23 Nanbu Plastic Co., Ltd. Injection molding apparatus having a divided degassing pin
US5938596A (en) * 1997-03-17 1999-08-17 Medtronic, Inc. Medical electrical lead
US5964702A (en) * 1994-04-20 1999-10-12 Case Western Reserve University Implantable helical spiral cuff electrode method of installation
US6093197A (en) * 1997-12-08 2000-07-25 Axon Engineering, Inc. Spiral nerve cuff electrode implantation tool
US6240320B1 (en) * 1998-06-05 2001-05-29 Intermedics Inc. Cardiac lead with zone insulated electrodes
US6292703B1 (en) * 1998-10-08 2001-09-18 Biotronik Mess-Und Therapiegerate Gmbh & Co. Neural electrode arrangement
US6304787B1 (en) * 1998-08-26 2001-10-16 Advanced Bionics Corporation Cochlear electrode array having current-focusing and tissue-treating features
US6304785B1 (en) * 1998-10-27 2001-10-16 Huntington Medical Research Institute Electrode insertion tool
US6350229B1 (en) * 1995-09-20 2002-02-26 Medtronic, Inc. Method and apparatus for temporarily immobilizing a local area of tissue
US6352422B1 (en) * 1997-08-06 2002-03-05 Micron Technology, Inc. Method and apparatus for epoxy loc die attachment
US6418348B1 (en) * 1999-06-25 2002-07-09 Biotronik Mess-Und Therapiegeraete Gmbh & Co. Ingenieurbuero Berlin Implantable lead with selectively operable electrodes
US20020100860A1 (en) * 1999-09-09 2002-08-01 Wieder Klaus A. Mold vent and method
US6461474B1 (en) * 1996-09-06 2002-10-08 Kimberly-Clark Worldwide, Inc. Process for producing high-bulk tissue webs using nonwoven substrates
US6473653B1 (en) * 1996-04-04 2002-10-29 Medtronic, Inc. Selective activation of electrodes within an inplantable lead
US6477417B1 (en) * 2001-04-12 2002-11-05 Pacesetter, Inc. System and method for automatically selecting electrode polarity during sensing and stimulation
US20020173785A1 (en) * 2000-03-31 2002-11-21 Medtronic, Inc. System and method for positioning implantable medical devices within coronary veins
US20020192320A1 (en) * 1997-01-28 2002-12-19 Brand J. Michael Method and apparatus for filling a gap between spaced layers of a semiconductor
US6526321B1 (en) * 1998-06-05 2003-02-25 Intermedics, Inc. Method for making cardiac leads with zone insulated electrodes
US20030065242A1 (en) * 2001-08-13 2003-04-03 Ludger Dinkelborg Radioactive implantable devices and methods and apparatuses for their production and use
US6600956B2 (en) * 2001-08-21 2003-07-29 Cyberonics, Inc. Circumneural electrode assembly
US6609956B2 (en) * 2000-11-28 2003-08-26 Bottero S.P.A. Method and machine for grinding coated sheets of glass
US20040039434A1 (en) * 1999-09-16 2004-02-26 Schrom Mark G. Neurostimulating lead
US20040111139A1 (en) * 2002-12-10 2004-06-10 Mccreery Douglas B. Apparatus and methods for differential stimulation of nerve fibers
US6782619B2 (en) * 2001-08-17 2004-08-31 Advanced Cochlear Systems, Inc. Method of making high contact density electrode array
US20040186368A1 (en) * 2003-03-21 2004-09-23 Scimed Life Systems, Inc. Systems and methods for internal tissue penetration
US20040231365A1 (en) * 2003-04-09 2004-11-25 Tatsuhiro Yabuki Manufacturing methods of double-spiral arc tubes
US20040247849A1 (en) * 2003-06-05 2004-12-09 Csaba Truckai Polymer composites for biomedical applications and methods of making
US20040260145A9 (en) * 1995-09-20 2004-12-23 Cornelius Borst Method and apparatus for temporarily immobilizing a local area of tissue
US6837848B2 (en) * 2003-01-15 2005-01-04 Medtronic, Inc. Methods and apparatus for accessing and stabilizing an area of the heart
US6884055B2 (en) * 2002-05-29 2005-04-26 The Boeing Company Potting compound injection apparatus and method of injecting potting compound into panel cells
US6907295B2 (en) * 2001-08-31 2005-06-14 Biocontrol Medical Ltd. Electrode assembly for nerve control
US20050203488A1 (en) * 2004-03-09 2005-09-15 Usgi Medical Inc. Apparatus and methods for mapping out endoluminal gastrointestinal surgery
US20050203489A1 (en) * 2004-03-09 2005-09-15 Usgi Medical Inc. Apparatus and methods for performing mucosectomy
US20050245944A1 (en) * 2002-02-01 2005-11-03 Rezai Ali R Apparatus for facilitating delivery of at least one device to a target site in a body
US20060030919A1 (en) * 2004-08-04 2006-02-09 Ndi Medical, Llc Devices, systems, and methods employing a molded nerve cuff electrode
US20060089697A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead
US20060089691A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead with axially oriented coiled wire conductors
US20060089696A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead with reinforced outer jacket
US7114944B2 (en) * 2004-01-21 2006-10-03 David Wolfe Design, Inc Tactical venting
US7201940B1 (en) * 2001-06-12 2007-04-10 Advanced Cardiovascular Systems, Inc. Method and apparatus for thermal spray processing of medical devices
US7212868B2 (en) * 2004-03-30 2007-05-01 Cardiac Pacemakers, Inc. Electrode and insulation assembly for a lead and method therefor
US7212867B2 (en) * 2000-12-07 2007-05-01 Medtronic, Inc. Directional brain stimulation and recording leads
US20070100406A1 (en) * 2005-10-28 2007-05-03 Cyberonics, Inc. Insert for implantable electrode

Family Cites Families (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4284856A (en) * 1979-09-24 1981-08-18 Hochmair Ingeborg Multi-frequency system and method for enhancing auditory stimulation and the like
US4686765A (en) * 1984-05-03 1987-08-18 Regents Of The University Of California Method for making an intracochlear electrode array
US5037497A (en) * 1988-08-30 1991-08-06 Cochlear Corporation Method of fabricating an array of recessed radially oriented bipolar electrodes
DE19624929C2 (en) * 1996-06-21 2001-08-02 Siemens Ag Process automation system
US5961909A (en) * 1997-09-03 1999-10-05 Pmt Corporation Method of manufacture of tissue-conformable electrodes
US7444183B2 (en) 2003-02-03 2008-10-28 Enteromedics, Inc. Intraluminal electrode apparatus and method
EP1804902A4 (en) 2004-09-10 2008-04-16 Cleveland Clinic Foundation Intraluminal electrode assembly

Patent Citations (100)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1404042A (en) * 1922-01-17 Everard f
US3089600A (en) * 1961-05-26 1963-05-14 Rca Corp Transfer apparatus
US3421511A (en) * 1965-12-10 1969-01-14 Medtronic Inc Implantable electrode for nerve stimulation
US3468648A (en) * 1966-07-08 1969-09-23 Owens Illinois Inc Method and apparatus for forming hollow glass articles
US3539322A (en) * 1967-03-23 1970-11-10 Quickfit & Quartz Ltd Method and apparatus for producing an internal precision sealing surface in hollow glass bodies
US3760812A (en) * 1971-03-19 1973-09-25 Univ Minnesota Implantable spiral wound stimulation electrodes
US3743457A (en) * 1971-07-13 1973-07-03 Acme Hamilton Mfg Corp Stock flow control means for extruders and the like
US3922134A (en) * 1973-12-17 1975-11-25 Robintech Inc Pipe bending mandrel
US4106744A (en) * 1975-09-11 1978-08-15 Analog Technology Corporation Mandrel for formation of mass spectrometer filter
US4413636A (en) * 1979-11-19 1983-11-08 Phillip R. Beutel Catheter
US4850356A (en) * 1980-08-08 1989-07-25 Darox Corporation Defibrillator electrode system
US4612934A (en) * 1981-06-30 1986-09-23 Borkan William N Non-invasive multiprogrammable tissue stimulator
US4459989A (en) * 1981-06-30 1984-07-17 Neuromed, Inc. Non-invasive multiprogrammable tissue stimulator and methods for use
US4427498A (en) * 1982-03-25 1984-01-24 Amp Incorporated Selective plating interior surfaces of electrical terminals
US4384926A (en) * 1982-03-25 1983-05-24 Amp Incorporated Plating interior surfaces of electrical terminals
US4484586A (en) * 1982-05-27 1984-11-27 Berkley & Company, Inc. Hollow conductive medical tubing
US4490104A (en) * 1982-11-22 1984-12-25 Borg-Warner Chemicals, Inc. Apparatus for separating a low viscosity material from a high _viscosity material
US4508053A (en) * 1983-01-05 1985-04-02 Xis, Incorporated Vacuum deposition apparatus for manufacturing selenium photoreceptors
US4590946A (en) * 1984-06-14 1986-05-27 Biomed Concepts, Inc. Surgically implantable electrode for nerve bundles
US4573481A (en) * 1984-06-25 1986-03-04 Huntington Institute Of Applied Research Implantable electrode array
US4643658A (en) * 1984-09-26 1987-02-17 Gordon John H Expanding mandrel
US4602624A (en) * 1984-10-11 1986-07-29 Case Western Reserve University Implantable cuff, method of manufacture, and method of installation
US4608985A (en) * 1984-10-11 1986-09-02 Case Western Reserve University Antidromic pulse generating wave form for collision blocking
US4628942A (en) * 1984-10-11 1986-12-16 Case Western Reserve University Asymmetric shielded two electrode cuff
US4649936A (en) * 1984-10-11 1987-03-17 Case Western Reserve University Asymmetric single electrode cuff for generation of unidirectionally propagating action potentials for collision blocking
US4822272A (en) * 1986-10-17 1989-04-18 Agency Of Industrial Science And Technology Mandrel for use in a manufacture of an article made of composite material
US4832048A (en) * 1987-10-29 1989-05-23 Cordis Corporation Suction ablation catheter
US4789327B1 (en) * 1988-02-25 2000-07-18 Corma Inc Adjustable pipe extrusion die with internal cooling
US4789327A (en) * 1988-02-25 1988-12-06 Harry Chan Adjustable pipe extrusion die with internal cooling
US5003975A (en) * 1988-04-19 1991-04-02 Siemens-Pacesetter, Inc. Automatic electrode configuration of an implantable pacemaker
US4860616A (en) * 1988-06-17 1989-08-29 Smith Winford L Method and apparatus for the manufacture of rotary sheet dies
US4944906A (en) * 1988-10-11 1990-07-31 Spirex Corporation Methods of injection molding and extruding wet hygroscopic ionomers
US4920979A (en) * 1988-10-12 1990-05-01 Huntington Medical Research Institute Bidirectional helical electrode for nerve stimulation
US4940065A (en) * 1989-01-23 1990-07-10 Regents Of The University Of California Surgically implantable peripheral nerve electrode
US5176866A (en) * 1989-02-28 1993-01-05 Asahi Kasei Kogyo Kabushiki Kaisha Process for producing a resin product having a bent hollow portion and a core usable for the same process
US4979511A (en) * 1989-11-03 1990-12-25 Cyberonics, Inc. Strain relief tether for implantable electrode
US5063018A (en) * 1990-06-04 1991-11-05 Cordis Corporation Extrusion method
US5143067A (en) * 1990-06-07 1992-09-01 Medtronic, Inc. Tool for implantable neural electrode
US5095905A (en) * 1990-06-07 1992-03-17 Medtronic, Inc. Implantable neural electrode
US5282468A (en) * 1990-06-07 1994-02-01 Medtronic, Inc. Implantable neural electrode
US5351394A (en) * 1991-05-03 1994-10-04 Cyberonics, Inc. Method of making a nerve electrode array
US5251634A (en) * 1991-05-03 1993-10-12 Cyberonics, Inc. Helical nerve electrode
US5215089A (en) * 1991-10-21 1993-06-01 Cyberonics, Inc. Electrode assembly for nerve stimulation
US5515848A (en) * 1991-10-22 1996-05-14 Pi Medical Corporation Implantable microelectrode
US5524338A (en) * 1991-10-22 1996-06-11 Pi Medical Corporation Method of making implantable microelectrode
US5460501A (en) * 1994-04-07 1995-10-24 Advanced Drainage Systems, Inc. Pipe production line for the manufacture of plastic pipe
US5964702A (en) * 1994-04-20 1999-10-12 Case Western Reserve University Implantable helical spiral cuff electrode method of installation
US5531778A (en) * 1994-09-20 1996-07-02 Cyberonics, Inc. Circumneural electrode assembly
US5630968A (en) * 1995-06-07 1997-05-20 The Japan Steel Works, Ltd. Water-injection foaming devolatilizing method
US20060036128A1 (en) * 1995-09-20 2006-02-16 Medtronic, Inc. Method and apparatus for temporarily immobilizing a local area of tissue
US7189201B2 (en) * 1995-09-20 2007-03-13 Medtronic, Inc. Method and apparatus for temporarily immobilizing a local area of tissue
US20040260145A9 (en) * 1995-09-20 2004-12-23 Cornelius Borst Method and apparatus for temporarily immobilizing a local area of tissue
US6371906B1 (en) * 1995-09-20 2002-04-16 Medtronic, Inc. Method and apparatus for temporarily immobilizing a local area of tissue
US6350229B1 (en) * 1995-09-20 2002-02-26 Medtronic, Inc. Method and apparatus for temporarily immobilizing a local area of tissue
US7048683B2 (en) * 1995-09-20 2006-05-23 Medtronic, Inc. Method and apparatus for temporarily immobilizing a local area of tissue
US5624693A (en) * 1996-01-16 1997-04-29 Outboard Marine Corporation Molding apparatus with combined venting and flushing valve
US6473653B1 (en) * 1996-04-04 2002-10-29 Medtronic, Inc. Selective activation of electrodes within an inplantable lead
US5874116A (en) * 1996-04-19 1999-02-23 Nanbu Plastic Co., Ltd. Injection molding apparatus having a divided degassing pin
US6461474B1 (en) * 1996-09-06 2002-10-08 Kimberly-Clark Worldwide, Inc. Process for producing high-bulk tissue webs using nonwoven substrates
US20020192320A1 (en) * 1997-01-28 2002-12-19 Brand J. Michael Method and apparatus for filling a gap between spaced layers of a semiconductor
US5938596A (en) * 1997-03-17 1999-08-17 Medtronic, Inc. Medical electrical lead
US6352422B1 (en) * 1997-08-06 2002-03-05 Micron Technology, Inc. Method and apparatus for epoxy loc die attachment
US6093197A (en) * 1997-12-08 2000-07-25 Axon Engineering, Inc. Spiral nerve cuff electrode implantation tool
US6526321B1 (en) * 1998-06-05 2003-02-25 Intermedics, Inc. Method for making cardiac leads with zone insulated electrodes
US6240320B1 (en) * 1998-06-05 2001-05-29 Intermedics Inc. Cardiac lead with zone insulated electrodes
US6304787B1 (en) * 1998-08-26 2001-10-16 Advanced Bionics Corporation Cochlear electrode array having current-focusing and tissue-treating features
US6292703B1 (en) * 1998-10-08 2001-09-18 Biotronik Mess-Und Therapiegerate Gmbh & Co. Neural electrode arrangement
US6304785B1 (en) * 1998-10-27 2001-10-16 Huntington Medical Research Institute Electrode insertion tool
US6418348B1 (en) * 1999-06-25 2002-07-09 Biotronik Mess-Und Therapiegeraete Gmbh & Co. Ingenieurbuero Berlin Implantable lead with selectively operable electrodes
US20020100860A1 (en) * 1999-09-09 2002-08-01 Wieder Klaus A. Mold vent and method
US6827569B2 (en) * 1999-09-09 2004-12-07 Klaus A. Wieder Mold vent and method
US7047082B1 (en) * 1999-09-16 2006-05-16 Micronet Medical, Inc. Neurostimulating lead
US20040039434A1 (en) * 1999-09-16 2004-02-26 Schrom Mark G. Neurostimulating lead
US7051419B2 (en) * 1999-09-16 2006-05-30 Micronet Medical, Inc. Neurostimulating lead
US20020173785A1 (en) * 2000-03-31 2002-11-21 Medtronic, Inc. System and method for positioning implantable medical devices within coronary veins
US6609956B2 (en) * 2000-11-28 2003-08-26 Bottero S.P.A. Method and machine for grinding coated sheets of glass
US7212867B2 (en) * 2000-12-07 2007-05-01 Medtronic, Inc. Directional brain stimulation and recording leads
US6477417B1 (en) * 2001-04-12 2002-11-05 Pacesetter, Inc. System and method for automatically selecting electrode polarity during sensing and stimulation
US7201940B1 (en) * 2001-06-12 2007-04-10 Advanced Cardiovascular Systems, Inc. Method and apparatus for thermal spray processing of medical devices
US20030065242A1 (en) * 2001-08-13 2003-04-03 Ludger Dinkelborg Radioactive implantable devices and methods and apparatuses for their production and use
US6782619B2 (en) * 2001-08-17 2004-08-31 Advanced Cochlear Systems, Inc. Method of making high contact density electrode array
US6600956B2 (en) * 2001-08-21 2003-07-29 Cyberonics, Inc. Circumneural electrode assembly
US6907295B2 (en) * 2001-08-31 2005-06-14 Biocontrol Medical Ltd. Electrode assembly for nerve control
US20050245944A1 (en) * 2002-02-01 2005-11-03 Rezai Ali R Apparatus for facilitating delivery of at least one device to a target site in a body
US6884055B2 (en) * 2002-05-29 2005-04-26 The Boeing Company Potting compound injection apparatus and method of injecting potting compound into panel cells
US20040111139A1 (en) * 2002-12-10 2004-06-10 Mccreery Douglas B. Apparatus and methods for differential stimulation of nerve fibers
US6918908B2 (en) * 2003-01-15 2005-07-19 Medtronic, Inc. Methods and apparatus for accessing and stabilizing an area of the heart
US6837848B2 (en) * 2003-01-15 2005-01-04 Medtronic, Inc. Methods and apparatus for accessing and stabilizing an area of the heart
US20040186368A1 (en) * 2003-03-21 2004-09-23 Scimed Life Systems, Inc. Systems and methods for internal tissue penetration
US20040231365A1 (en) * 2003-04-09 2004-11-25 Tatsuhiro Yabuki Manufacturing methods of double-spiral arc tubes
US20040247849A1 (en) * 2003-06-05 2004-12-09 Csaba Truckai Polymer composites for biomedical applications and methods of making
US7114944B2 (en) * 2004-01-21 2006-10-03 David Wolfe Design, Inc Tactical venting
US20050203488A1 (en) * 2004-03-09 2005-09-15 Usgi Medical Inc. Apparatus and methods for mapping out endoluminal gastrointestinal surgery
US20050203489A1 (en) * 2004-03-09 2005-09-15 Usgi Medical Inc. Apparatus and methods for performing mucosectomy
US7212868B2 (en) * 2004-03-30 2007-05-01 Cardiac Pacemakers, Inc. Electrode and insulation assembly for a lead and method therefor
US20060030919A1 (en) * 2004-08-04 2006-02-09 Ndi Medical, Llc Devices, systems, and methods employing a molded nerve cuff electrode
US20060089691A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead with axially oriented coiled wire conductors
US20060089696A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead with reinforced outer jacket
US20060089697A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead
US20070100406A1 (en) * 2005-10-28 2007-05-03 Cyberonics, Inc. Insert for implantable electrode

Also Published As

Publication number Publication date Type
US7901613B2 (en) 2011-03-08 grant
US20100101944A1 (en) 2010-04-29 application

Similar Documents

Publication Publication Date Title
US4744370A (en) Lead assembly with selectable electrode connection
US6477427B1 (en) Implantable stimulation lead and method of manufacture
US7082337B2 (en) Suture sleeve
US6256542B1 (en) Extractable implantable medical lead
US6920361B2 (en) Reverse wound electrodes
US7460913B2 (en) Implantable electrode, insertion tool for use therewith, and insertion method
US5324321A (en) Medical electrical lead having sigmoidal conductors and non-circular lumens
US7822482B2 (en) Electrical stimulation lead with rounded array of electrodes
US5042143A (en) Method for fabrication of implantable electrode
US5938596A (en) Medical electrical lead
US7437197B2 (en) Medical lead and manufacturing method therefor
US4590950A (en) Electrical connection
US3757789A (en) Electromedical stimulator lead connector
US6564107B1 (en) Coil-less lead system
US20040106964A1 (en) Implantable Medical Device with Multiple Electrode Lead and Connector with Central Fastener
US20120071949A1 (en) Systems and methods for making and using radially-aligned segmented electrodes for leads of electrical stimulation systems
US4832051A (en) Multiple-electrode intracochlear device
US20120316615A1 (en) Systems and methods for making and using improved leads for electrical stimulation systems
US5843141A (en) Medical lead connector system
US4744371A (en) Multi-conductor lead assembly for temporary use
US7174220B1 (en) Construction of a medical electrical lead
US20050027340A1 (en) System and method for providing a medical lead body having dual conductor layers
US6801809B2 (en) Extractable implantable medical lead
US4641664A (en) Endocardial electrode arrangement
US6687550B1 (en) Active fixation electrode lead having an electrical coupling mechanism

Legal Events

Date Code Title Description
AS Assignment

Owner name: CYBERONICS, INC., TEXAS

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:KOLLATSCHNY, SHAWN D.;SCIACCA, JOSEPH J.;REEL/FRAME:017146/0603

Effective date: 20051020