WO1994007565A1 - An implantable lead - Google Patents
An implantable lead Download PDFInfo
- Publication number
- WO1994007565A1 WO1994007565A1 PCT/US1992/010675 US9210675W WO9407565A1 WO 1994007565 A1 WO1994007565 A1 WO 1994007565A1 US 9210675 W US9210675 W US 9210675W WO 9407565 A1 WO9407565 A1 WO 9407565A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- porous ptfe
- length
- implantable lead
- fibrils
- tubular
- Prior art date
Links
- 229920001343 polytetrafluoroethylene Polymers 0.000 claims abstract description 46
- 239000004810 polytetrafluoroethylene Substances 0.000 claims abstract description 46
- 239000004020 conductor Substances 0.000 claims abstract description 31
- 229920001296 polysiloxane Polymers 0.000 claims abstract description 7
- 229920002635 polyurethane Polymers 0.000 claims abstract description 7
- 239000004814 polyurethane Substances 0.000 claims abstract description 7
- -1 polytetrafluoroethylene Polymers 0.000 claims description 8
- 239000013464 silicone adhesive Substances 0.000 claims description 2
- 229920000642 polymer Polymers 0.000 claims 8
- 229920001169 thermoplastic Polymers 0.000 claims 2
- 229920001187 thermosetting polymer Polymers 0.000 claims 2
- 239000004416 thermosoftening plastic Substances 0.000 claims 2
- 230000006835 compression Effects 0.000 abstract description 9
- 238000007906 compression Methods 0.000 abstract description 9
- 230000000747 cardiac effect Effects 0.000 abstract description 4
- 239000013536 elastomeric material Substances 0.000 abstract description 2
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 abstract description 2
- 230000007774 longterm Effects 0.000 abstract 1
- 230000000638 stimulation Effects 0.000 abstract 1
- 238000009413 insulation Methods 0.000 description 11
- 238000010276 construction Methods 0.000 description 8
- 239000000463 material Substances 0.000 description 6
- 210000001124 body fluid Anatomy 0.000 description 5
- 239000010839 body fluid Substances 0.000 description 5
- 239000011148 porous material Substances 0.000 description 3
- 230000002411 adverse Effects 0.000 description 2
- 238000006243 chemical reaction Methods 0.000 description 2
- 238000002513 implantation Methods 0.000 description 2
- 229910000990 Ni alloy Inorganic materials 0.000 description 1
- 238000005299 abrasion Methods 0.000 description 1
- 239000000853 adhesive Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- 238000010009 beating Methods 0.000 description 1
- 238000005452 bending Methods 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 230000001413 cellular effect Effects 0.000 description 1
- 230000005489 elastic deformation Effects 0.000 description 1
- 238000010292 electrical insulation Methods 0.000 description 1
- 239000012772 electrical insulation material Substances 0.000 description 1
- 239000012777 electrically insulating material Substances 0.000 description 1
- 239000012774 insulation material Substances 0.000 description 1
- 230000002452 interceptive effect Effects 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 239000010935 stainless steel Substances 0.000 description 1
- 229910001220 stainless steel Inorganic materials 0.000 description 1
- 230000008467 tissue growth Effects 0.000 description 1
- 238000009736 wetting Methods 0.000 description 1
- 238000004804 winding Methods 0.000 description 1
Classifications
-
- 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
Definitions
- This invention relates to the field of implantable electrical leads for use with various implantable electrical devices such as cardiac pacers and defibrillators.
- Implantable leads for use with implantable electrical devices such as cardiac pacemakers and defibrillators are typically constructed of a helically wound conductor having an outer insulation layer of tubular form surrounding the wire helix.
- the tubular insulation is most commonly of an elastomeric material such as silicone or polyurethane.
- implantable leads must have excellent mechanical integrity, electrical insulating properties and biocompatibility, and must be flexible with a long flex life to accommodate attachment to a beating heart.
- Patent 4,573,480 describes an implantable electrode lead in the form of a helically wound conductor having a tubular insulating layer surrounding the helically wound wire wherein the tubular insulating layer is porous polytetrafluoroethylene (hereinafter PTFE) having a pore size limited to a maximum size described as "being essentially impervious to body fluids to prevent tissue growth thereon.”
- PTFE porous polytetrafluoroethylene
- This pore size is described as being not larger than 4 microns. While pore sizes of this range and smaller are known to preclude cellular ingrowth, the material remains pervious to body fluids which will wet out such an insulating layer shortly after implantation. The result is that the effectiveness of the electrical insulation is destroyed.
- tubular porous PTFE insulating layer may be provided with an outer covering of smooth and impervious material. While this alternative construction prevents the wetting out of the porous PTFE layer by body fluids, it loses the biocompatible advantage provided by the tissue contacting outer surface of porous expanded PTFE.
- the present invention is an implantable lead having improved tensile strength, excellent flexibility, excellent insulating characteristics, improved biocompatibility and controlled amounts of elongation during the application of tension to the lead.
- the amount of elongation may be varied over different portions of the length of the lead.
- the implantable lead comprises a helically wound electrical conductor having a layer of elastomeric insulating tubing coaxially surrounding the helix formed by the helically wound conductor.
- the layer of elastomeric insulating tubing is in turn coaxially surrounded by a layer of porous PTFE tubing having a microstructure of nodes interconnected by fibrils.
- At least a portion of the length of the porous PTFE may be under longitudinal compression whereby the fibrils of the microstructure within that portion of the length have a substantially bent and wavy appearance. Consequently this portion of the length may be stretched or extended until the fibrils of the microstructure are straightened as a result of tension applied to that portion of the lead.
- the entire length of a lead may be provided with an exterior covering of longitudinally compressed porous PTFE tubing if desired.
- coaxial is herein used in relationship to the longitudinal axis of the helix formed by the at least one helically wound conductor.
- porous PTFE outer covering provides the lead wire with excellent flexibility, biocompatibility and tensile strength while simultaneously providing the lead with a controlled amount of extensibility.
- the fibril length of the porous PTFE must be adequate to provide the necessary amount of flexibility and extensibility for the intended application and preferably should be of adequate size to present an acceptable biocompatible surface to the blood chemistry to which the outer surface of the lead will be exposed.
- the preferred fibril lengths are greater than about 4 microns and most preferably greater than about 10 microns. Fibril length is measured as taught by U. S. Patent 4,972,846.
- the layer of tubular elastomeric insulation surrounding the helically wound conductor provides excellent insulation because these materials are substantially impervious to body fluids. They are disadvantageous as the exterior surface of a lead because they are not ideally biocompatible and are known in some patients to provoke adverse tissue reactions.
- the additional exterior covering of porous PTFE tubing of the lead of the present invention provides a superior biocompatible surface. While this porous exterior covering is likely to be wet out by body fluids and is consequently inadequate by itself as an effective electrical insulation material for purposes of implantation in living bodies, the combination of a porous PTFE exterior covering surrounding a layer of impervious elastomeric insulating tubing offers a superior biocompatible lead insulation.
- the at least one helically wound conductor wire used with the present invention may be a single conductor or alternatively may be multiple-filar if more than one conductor is required for a desired application.
- porous PTFE having a microstructure of nodes interconnected by fibrils used for the exterior tubular covering of the inventive lead is made according to the teachings of 4,187,390 and 3,953,566.
- the tubular covering of porous PTFE may be provided with bent or wavy fibrils resulting in stretch characteristics in a similar manner to that taught by U.S. Patents 4,877,661 and 5,026,513.
- Figure 1 describes a cross section of the implantable lead of the present invention wherein a helically wound electrical conductor is coaxially covered by a layer of tubular elastomeric insulation which is in turn coaxially covered by an exterior tubular layer of porous PTFE having a microstructure of nodes interconnected by fibrils.
- Figure 2 describes a cross section of the implantable lead of one embodiment of the present invention wherein the exterior tubular layer of porous PTFE is shown under longitudinal compression wherein the fibrils of the microstructure have a bent and wavy appearance.
- Figure 3 describes a cross section of the implantable lead of one embodiment of the present invention wherein the exterior tubular layer of porous PTFE is shown under tension wherein the fibrils of the microstructure are substantially straight.
- Figure 1 describes a cross section of the implantable lead 10 of the present invention wherein a helically wound electrical conductor J_2 is coaxially covered by a tubular layer of an elastomeric electrically insulating material .14 such as silicone or polyurethane.
- the lead is further provided with an exterior coaxial tubular covering of porous PTFE 16 having a microstructure of nodes interconnected by fibrils.
- Elastomeric materials are herein defined as polymeric materials which at room temperature can be stretched under low stress to at least twice their original length and, immediately upon release of the stress, will recover with force to their approximate original length.
- Figures 2 and 3 describe cross sections of a preferred embodiment wherein Figure 2 shows the lead in a relaxed state and Figure 3 shows the lead under longitudinal tension.
- Figure 2 shows the lead in a relaxed state
- Figure 3 shows the lead under longitudinal tension.
- the fibrils 21 that interconnect the nodes £4 within the microstructure of the porous PTFE tubing 16 will assume a bent and wavy appearance due to the longitudinal compression applied to the porous PTFE tubing 16 when it is fitted over the elastomeric tubing 1_4 during construction of the lead.
- the spring characteristic of the helically wound conductor 12 and the elastic characteristic of the elastomeric tubing J_4 allow those components of the lead construction to extend longitudinally.
- the bent fibrils 21 of the porous PTFE tubing 16 as shown previously in Figure 2 are able to extend until they become straight and taut fibrils £6 as a result of the applied tension, as shown by Figure 3. It is apparent that the amount of extension of the porous PTFE tubing is a function of the amount of longitudinal compression applied to the porous PTFE tubing during construction of the lead and the resulting amount of bending that is applied to the fibrils.
- the exterior tubular covering of porous PTFE 1_6 is fitted over the exterior surface of the elastomeric tubing 14.
- the relationship between the inside diameter of the porous PTFE tubing and the outside diameter of the elastomeric tubing should be such that there is at most only a small amount of interference when these respective diameters are measured with the tubes in relaxed states with no tension applied. Preferably there is no interference between these respective diameters.
- the porous PTFE tubing 16 is most easily fitted over the elastomeric tubing 14 prior to inserting the helically wound conductor into the bore of the elastomeric tubing. This avoids any risk to the conductor.
- the elastomeric tubing 4 may be placed under tension adequate to cause a significant reduction in its outside diameter before fitting it into the exterior porous PTFE tubing. This tension is preferably applied with a pull- wire attached to the ends of the bore of the elastomeric tubing, thereby not interfering with access to the exterior surface of the elastomeric tubing.
- the exterior tubular covering of porous PTFE is then fitted over the reduced diameter of the tensioned elastomeric tube. After the exterior tubular covering of porous PTFE has been fitted over the tensioned elastomeric tubing, the tension on the elastomeric tubing is released. The diametrical interference between the porous PTFE tubing and the elastomeric tubing results in the securing of the two tubes together.
- a biocompatible adhesive such as a silicone adhesive may be used during the construction process.
- the porous PTFE tube is longitudinally compressed according to the amount of extensibility, if any, that is desired of the completed implantable lead.
- the longitudinal compression can be uniformly applied over the chosen length of porous PTFE tubing or alternatively the compression can be applied non-uniformly if it is desired to have different extensibility characteristics over different parts of the lead.
- the helically wound conductor is preferably fitted into the bore of the elastomeric tubing after completion of the insulation construction.
- the at least one helically wound conductor wire used with the present invention may be a single conductor or alternatively may be multiple-filar if more than one conductor is required for a desired application. Multiple conductors will require that the individual conductors be separately insulated from each other, preferably by a layer of insulation covering the surface of each individual conductor. In the case of a single helically wound conductor, the conductor may optionally be separately insulated within the two-layer coaxially oriented insulation of the present invention.
- Insulation covering the surface of helically wound conductors is preferably applied to each conductor surface prior to helical winding of the conductors.
- the conductor is preferably a MP35N nickel alloy stainless steel material.
Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP50898594A JP3445273B2 (en) | 1992-10-02 | 1992-12-14 | Lead wire for implant |
CA002143091A CA2143091C (en) | 1992-10-02 | 1992-12-14 | An implantable lead |
EP93901387A EP0662853B1 (en) | 1992-10-02 | 1992-12-14 | An implantable lead |
DE69223264T DE69223264T2 (en) | 1992-10-02 | 1992-12-14 | IMPLANTABLE LINE |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US955,611 | 1992-10-02 | ||
US07/955,611 US5466252A (en) | 1992-10-02 | 1992-10-02 | Implantable lead |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1994007565A1 true WO1994007565A1 (en) | 1994-04-14 |
Family
ID=25497076
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1992/010675 WO1994007565A1 (en) | 1992-10-02 | 1992-12-14 | An implantable lead |
Country Status (7)
Country | Link |
---|---|
US (1) | US5466252A (en) |
EP (1) | EP0662853B1 (en) |
JP (1) | JP3445273B2 (en) |
CA (1) | CA2143091C (en) |
DE (1) | DE69223264T2 (en) |
IT (1) | ITTO930721A1 (en) |
WO (1) | WO1994007565A1 (en) |
Cited By (2)
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WO1996008828A1 (en) * | 1994-09-13 | 1996-03-21 | W.L. Gore & Associates, Inc. | Jacket material for protection of electrical conductors |
WO2008119387A1 (en) * | 2007-04-02 | 2008-10-09 | Neurotech | Stretchable conductor and method for producing the same |
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US5569883A (en) * | 1994-08-31 | 1996-10-29 | Pacesetter, Inc. | Joint for providing a secure connection between a wound element and a mating part in a body implantable lead assembly and method for making such joint |
US5674272A (en) * | 1995-06-05 | 1997-10-07 | Ventritex, Inc. | Crush resistant implantable lead |
US5868704A (en) * | 1995-09-18 | 1999-02-09 | W. L. Gore & Associates, Inc. | Balloon catheter device |
US5752934A (en) * | 1995-09-18 | 1998-05-19 | W. L. Gore & Associates, Inc. | Balloon catheter device |
US5788626A (en) * | 1995-11-21 | 1998-08-04 | Schneider (Usa) Inc | Method of making a stent-graft covered with expanded polytetrafluoroethylene |
US5824026A (en) * | 1996-06-12 | 1998-10-20 | The Spectranetics Corporation | Catheter for delivery of electric energy and a process for manufacturing same |
US5755762A (en) * | 1996-06-14 | 1998-05-26 | Pacesetter, Inc. | Medical lead and method of making and using |
US5782898A (en) * | 1996-10-15 | 1998-07-21 | Angeion Corporation | System for anchoring mid-lead electrode on an endocardial catheter lead |
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US5931862A (en) * | 1997-12-22 | 1999-08-03 | Pacesetter, Inc. | Medical lead and method of making and using with sodium sulfosuccinic ester |
US7313444B2 (en) * | 1998-11-20 | 2007-12-25 | Pacesetter, Inc. | Self-anchoring coronary sinus lead |
US7049380B1 (en) * | 1999-01-19 | 2006-05-23 | Gore Enterprise Holdings, Inc. | Thermoplastic copolymer of tetrafluoroethylene and perfluoromethyl vinyl ether and medical devices employing the copolymer |
US7892201B1 (en) | 1999-08-27 | 2011-02-22 | Gore Enterprise Holdings, Inc. | Balloon catheter and method of mounting same |
US6704604B2 (en) | 2000-12-28 | 2004-03-09 | Medtronic, Inc. | System and method for promoting selective tissue in-growth for an implantable medical device |
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US7904178B2 (en) * | 2002-04-11 | 2011-03-08 | Medtronic, Inc. | Medical electrical lead body designs incorporating energy dissipating shunt |
US8396568B2 (en) * | 2002-04-11 | 2013-03-12 | Medtronic, Inc. | Medical electrical lead body designs incorporating energy dissipating shunt |
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US20040064175A1 (en) * | 2002-09-30 | 2004-04-01 | Lessar Joseph F. | Implantable medical device lead conductor having integral biostable in-situ grown oxide insulation and process for forming |
US7155293B2 (en) * | 2003-01-29 | 2006-12-26 | Cardiac Pacemakers, Inc. | Medical electrical lead employing load bearing sleeve |
US8903512B2 (en) * | 2003-05-15 | 2014-12-02 | Medtronic, Inc. | Medical system including a novel bipolar pacing pair |
US7191016B2 (en) * | 2003-05-15 | 2007-03-13 | Medtronic, Inc. | Medical system including a novel bipolar pacing and sensing pair |
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US6990378B1 (en) | 2003-09-30 | 2006-01-24 | Pacesetter, Inc. | Abrasion-resistant implantable medical lead and a method of fabricating such a lead |
US7844344B2 (en) * | 2004-03-30 | 2010-11-30 | Medtronic, Inc. | MRI-safe implantable lead |
US8989840B2 (en) | 2004-03-30 | 2015-03-24 | Medtronic, Inc. | Lead electrode for use in an MRI-safe implantable medical device |
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US9155877B2 (en) | 2004-03-30 | 2015-10-13 | Medtronic, Inc. | Lead electrode for use in an MRI-safe implantable medical device |
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US20060089696A1 (en) * | 2004-10-21 | 2006-04-27 | Medtronic, Inc. | Implantable medical lead with reinforced outer jacket |
US7519432B2 (en) * | 2004-10-21 | 2009-04-14 | Medtronic, Inc. | Implantable medical lead with helical reinforcement |
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US8535704B2 (en) * | 2005-12-29 | 2013-09-17 | Medtronic, Inc. | Self-assembling cross-linking molecular nano film |
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US10537730B2 (en) | 2007-02-14 | 2020-01-21 | Medtronic, Inc. | Continuous conductive materials for electromagnetic shielding |
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US8483842B2 (en) | 2007-04-25 | 2013-07-09 | Medtronic, Inc. | Lead or lead extension having a conductive body and conductive body contact |
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US9814560B2 (en) | 2013-12-05 | 2017-11-14 | W. L. Gore & Associates, Inc. | Tapered implantable device and methods for making such devices |
US9993638B2 (en) | 2013-12-14 | 2018-06-12 | Medtronic, Inc. | Devices, systems and methods to reduce coupling of a shield and a conductor within an implantable medical lead |
US20150257702A1 (en) * | 2014-03-11 | 2015-09-17 | Biotronik Se & Co. Kg | Insulation Tube for an Electric Line for Medical Use, and Method for Producing Such a Tube |
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US10155111B2 (en) | 2014-07-24 | 2018-12-18 | Medtronic, Inc. | Methods of shielding implantable medical leads and implantable medical lead extensions |
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JP7274412B2 (en) * | 2016-09-01 | 2023-05-16 | イーピーアイ-マインダー・ピーティーワイ・リミテッド | Electrode device for monitoring and/or stimulating activity in a subject |
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1992
- 1992-10-02 US US07/955,611 patent/US5466252A/en not_active Expired - Lifetime
- 1992-12-14 JP JP50898594A patent/JP3445273B2/en not_active Expired - Lifetime
- 1992-12-14 EP EP93901387A patent/EP0662853B1/en not_active Expired - Lifetime
- 1992-12-14 DE DE69223264T patent/DE69223264T2/en not_active Expired - Lifetime
- 1992-12-14 CA CA002143091A patent/CA2143091C/en not_active Expired - Lifetime
- 1992-12-14 WO PCT/US1992/010675 patent/WO1994007565A1/en active IP Right Grant
-
1993
- 1993-10-01 IT IT93TO000721A patent/ITTO930721A1/en not_active IP Right Cessation
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US4573480A (en) * | 1983-02-16 | 1986-03-04 | Siemens Aktiengesellschaft | Implantable electrode lead with microporous insulation |
EP0388480A1 (en) * | 1989-03-20 | 1990-09-26 | Siemens Aktiengesellschaft | Implantable stimulation electrode |
WO1992011061A1 (en) * | 1990-12-21 | 1992-07-09 | Etablissements Thiebaud Freres S.A. | Transdermal electrode for electrotherapy |
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
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WO1996008828A1 (en) * | 1994-09-13 | 1996-03-21 | W.L. Gore & Associates, Inc. | Jacket material for protection of electrical conductors |
US5519172A (en) * | 1994-09-13 | 1996-05-21 | W. L. Gore & Associates, Inc. | Jacket material for protection of electrical conductors |
US5846355A (en) * | 1994-09-13 | 1998-12-08 | W. L. Gore & Associates, Inc. | Jacket material for protection of electrical conductors |
WO2008119387A1 (en) * | 2007-04-02 | 2008-10-09 | Neurotech | Stretchable conductor and method for producing the same |
US8426735B2 (en) | 2007-04-02 | 2013-04-23 | Neurotech | Stretchable conductor and method for producing the same |
Also Published As
Publication number | Publication date |
---|---|
ITTO930721A0 (en) | 1993-10-01 |
EP0662853A1 (en) | 1995-07-19 |
DE69223264D1 (en) | 1998-01-02 |
JP3445273B2 (en) | 2003-09-08 |
EP0662853B1 (en) | 1997-11-19 |
DE69223264T2 (en) | 1998-06-18 |
ITTO930721A1 (en) | 1994-04-04 |
CA2143091A1 (en) | 1994-04-14 |
CA2143091C (en) | 2000-05-09 |
JPH08501963A (en) | 1996-03-05 |
US5466252A (en) | 1995-11-14 |
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