WO1998010826A1 - Electrode cable for electrical stimulation - Google Patents
Electrode cable for electrical stimulation Download PDFInfo
- Publication number
- WO1998010826A1 WO1998010826A1 PCT/SE1997/001470 SE9701470W WO9810826A1 WO 1998010826 A1 WO1998010826 A1 WO 1998010826A1 SE 9701470 W SE9701470 W SE 9701470W WO 9810826 A1 WO9810826 A1 WO 9810826A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- wires
- cable
- resistivity
- wire
- low
- Prior art date
Links
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
- A61N1/056—Transvascular endocardial electrode systems
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B7/00—Insulated conductors or cables characterised by their form
- H01B7/06—Extensible conductors or cables, e.g. self-coiling cords
- H01B7/065—Extensible conductors or cables, e.g. self-coiling cords having the shape of an helix
Definitions
- the present invention relates to an electrode cable made of a plurality of wires arranged helically along the length of the cable, said cable, which is encased in an outer, tubular sheath made of an electrically insulating material, being mainly intended to serve as an electrical connection between an electrical stimulation device, such as a heart stimulator, defibrillator etc . , which can be connected to the proximal end of the cable, on the one hand, and an electrode connected to the distal end of the cable, on the other hand.
- an electrical stimulation device such as a heart stimulator, defibrillator etc .
- a lead device comprising one or more helices, each consisting of at least one conductor, is previously known from EP Al 0 162 178.
- Each conductor consists of a plurality of wires arranged in a bundle by intertwining. All the wires in each conductor can be made of the same or of different materials. When different materials are used, the wires can differ in strength and electrical conductivity.
- This known lead device can be used as an electrical connection between e.g. a heart stimulator and contact electrodes for implantation in the human body. The objective of this known lead device is to achieve a device which, with the smallest possible external diameter for the helix, displays great fatigue resistance, relatively great electrical conductivity and small electrical resistance.
- Each helical conductor in this known lead device has a core made of a wire and a plurality of wires coiled or wound around that core's longitudinal axis.
- the wires helically coiled around the core are intertwined into a bundle, making the lead device rather stiff and, therefore, scarcely suitable for advancement through the vascular system tcgether with a stylet unit, inserted into a central channel in sa d lead device, to a desired location in the heart during an implantatio .
- One main objective of the present invention is to provide a new type of low- resistivity electrode cable which can be used as an efficient electrical connection between a device for electrical stimulation in the human body and an electrode connected to the device.
- the device can be e.g. a heart stimulator or defibrillator, and the electrode can be e.g. an lmplantable heart electrode.
- the electrode cable can also be used for nerve stimulation.
- the electrode cable must be designed so it has very good electrical conductivity while simultaneously displaying optimal strength, tensile strength, flexural strength and fatigue resistance in particular.
- the problem addressed by the invention is to provide an electrode cable with optimal properties in respect to its electrical conductivity, mechanical strength and ability to withstand dynamic stress capable of causing fatigue breakage of the cable, an event which could have fatal consequences for a patient with a heart stimulator.
- Another objective of the invention is to provide an electrode 'cable design making t possible to minimize the use of expensive materials in manufacturing the wires or conductors in the cable.
- an increase in the number of wires in the lead increases the lead's external diameter which is a disadvantage for a patient in whom such an electrode is to be implanted. The disadvantage is even greater if a plurality of leads must be itrplanted in the patient.
- an increase in the cross-sectional area of a conductor has an adverse impact on e.g. fatigue resistance.
- the pitch of each individual conductor wire also increases, thereby impairing the mechanical properties of the lead.
- the conductors employ wires made of either a low-resistivity material or a material which is a combination of a low-resistivity material and a high- resistivity material, the latter devised to carry the low-resistivity material.
- a low-resistivity material or a material which is a combination of a low-resistivity material and a high- resistivity material, the latter devised to carry the low-resistivity material.
- such low-resistivity wires have limiting mechanical properties .
- Preferred embodiments of the electrode cable according to the invention can also display the features set forth in the dependent claims .
- a primary distinguishing feature of the electrode cable according to the invention is that the cable is a hybrid containing at least a first set of electrically conductive wires, this first set of wires, resp. each set of wires, including at least one wire devised as a low-resistivity electrical conductor and at least one, preferably at least two or three, wire(s) devised as (a) high-resistivity electrical conductor (s) , and all the low- resistivity and high-resistivity wires in each set of wires are conductors with the same diameter in the 0.05 to 0.20 rrm range and arranged side-by- side in a strip running parallel to the exterior of the cable sheath and extending helically along the cable's length.
- a low-resistivity wire As an example of a low-resistivity wire , assume we have a 5.8 m long wire with a cross-sectional area of 0.00785 ⁇ m 2 in which a low-resistivity material (silver) constitutes 28% of the conductive material and a high- resistivity material ( P35N) constitutes 72%. This results in a wire (conductor wire) with resistivity on the order of 5.4 x 10 "8 ⁇ m. A high- resistivity wire with the exact same geometry as the low-resistivity wire but made only of the said high-resistivity material (MP35N) will then have a resistivity on the order of about 2.5 x 10 " ' ⁇ m. The ratio between the resistivity of the high-resistivity wire and the low-resistivity wire according to this example will then amount to about 4.6.
- wire connecting means are arranged on each cable end and accomplish electrical interconnection of all the wires in the respective wire set, thereby achieving their parallel connection in the cable. In this manner, a low-resistivity helical wire is obtained with good mechanical properties .
- the wire connecting means on each cable end can e.g. be seme appropriate type of metallic clamping means which achieve surface contact with each low- resistivity wire and one or more of the high-resistance wires.
- the clamping means can also be made of a pair of interacting parts which grip in/on the wire spiral .
- the wire connecting means can consist of wire- connecting welded or soldered joints on the ends of the cable connecting the wires .
- the high-resistivity wires in each wire set suitable are conductors made of the same material
- the low-resistivity wire in each wire set suitably is a wire conductor with a core of low-resistivity material (e.g. silver, gold, copper, platinum etc.), said core being encased in an external sheath made of the same kind of material as the material in the high-resistivity wires.
- the latter material could be e.g. a cobalt alloy such as MP35N or the like.
- Material in the external sheath of each low-resistivity wire comprises appropriately 65% to 80% of the wire's total volume. It has been shown that particularly good properties are achieved when the latter percentage amounts to about 72%.
- the invention it also becomes possible to minimize the use (i.e. the required quantity) of a corrosible material (e.g. silver, ccpper etc.) in the electrode cable.
- a corrosible material e.g. silver, ccpper etc.
- the low-resistivity material risks becoming corroded or forming a cathode, the surrounding material becoming anodic, which may cause corrosion.
- the amount of mixed material can be reduced, thereby increasing the percentage of material such as MP35N, thus also improving the conditions for obtaining an effective welded joint.
- An electrode cable according to the invention can consist of a unipolar cable, but the electrode cable can alternately contain additional electrical conductors (poles) , the cable thus becoming bipolar or multipolar.
- Claim 7 provides an example of an electrode cable devised as a bipolar cable according to the invention.
- the cable also contains a second set of helical wires forming the cable's second pole.
- Claim 8 sets forth an embodiment of a bipolar electrode cable which is hollow throughout its length by having a longitudinal channel into which a stylet unit can be inserted. The stylet unit is temporarily inserted into the electrode cable during cable implantation to facilitate advancement of the cable through the vascular system to the desired location in the heart.
- the drawing in the FIGURE only shows a short section of the bipolar electrode cable as a highly schematic longitudinal section.
- the drawing shows a short section of a bipolar electrode cable according to the invention.
- This cable contains a pair of coaxially arranged, mutually insulated electrical conductor means forming the cable's two poles at either end of the cable.
- Each of these two conductor means generally designated 2 and 4 respectively, consists of four helically and cylindrically arranged wires, placed side-by-side, each wire of which constituting an electrical conductor.
- the outer conductor means 2 as seen in the radial direction of the cable, consist in this instance of a first set of electrically conductive wires 10, 12, 14 and 16.
- the wire designated 16 is devised as a low-resistivity electrical conductor wire, whereas the wires 10, 12, 14 are all devised as high-resistivity electrical conductor wires providing lateral support for the low-resistivity wire 16 in addition to serving as conductors.
- the cable is externally provided with a tubular sheath 6 made of an electrically insulating material, such a silicon rubber or polyurethane.
- a tubular sheath 8 made of an electrically insulating material is also arranged between the cable's two poles, i.e. between the first, outer set of wires, generally designated 2, and the inner set of wires, generally designated 4.
- the electrode cable is hollow throughout its length because the inner, second set of wires, generally designated 4, with its four helical wires, forms a longitudinal channel inside the cable. Thanks to this longitudinal channel, a stylet unit for cable maneuvering can be inserted into the interior of the electrode cable.
- the ability to maneuver the electrode cable is needed, in practice, when the cable is to serve as an electrical connection between a heart stimulator connectable to the proximal end of the cable, on the one hand, and an electrode on the distal end of the cable, which is to be advanced into a cavity of the heart and affixed to the cavity wall, on the other hand.
- Wire connecting means are arranged on both cable ends (the proximal end and distal end respectively) . Their task is to accomplish mutual electrical connection between all the wires in the respective wire sets so as to achieve parallel coupling of the wires in the respective wire set.
- the wire connecting means consist of a U-shaped metallic clamping means 18 with two parallel jaws which achieve direct surface contact with the wires in a set of wires.
- a clamping device of this kind is schematically shown in a side view of the set 2 of wires and in a axial longitudinal section of the inner set of wires 4 (at the right end of the inner set 4 of wires) .
- An alternative type of wire connection means at each end of the cable can consist of welded or soldered joints 20 between the wires in the set of wires.
- One such embodiment of the wire connecting means is shown to the left m FIGURE at the end of the outer set 2 of wires.
- the first, outer set 2 of wires consists of the low- resistivity wire 16 and three high-resistivity wires 10, 12, 14 All four of the wires in this wire set consist of conductor wires with the same diameter in the 0.05 to 0.20 range.
- the wires 10, 12, 14 and 16 are located side-by-side in a strip, running " parallel" to the cable's external sheath 6 and extending helically along the length of the cable, located on the surface of an imaginary circular cylinder coaxial to the electrode cable's midlme.
- the three high-resistivity wires 10, 12, 14 in the set 2 of wires consist of conductor wires made of the same material, e g MP35N, and the only low- resistivity wire 16 in the set 2 of wires is a conductor wire with a core 22 made of a low-resistivity material, such as silver, as shown in a highly enlarged cross-section of the wire 16 at the bott n of the FIGURE.
- the core 22 has a sheath 24 made of the same material as the material in the high-resistivity wires 10, 12, 14, i.e. MP35N m this instance.
- the above-described construction according to the invention achieves the advantage that only one of the four wires in the set 2 of wires, viz. the low-resistivity wire 16, is an expensive type with a core 22 of silver encased in a sheath 24 surrounding the core, made of the much cheaper cobalt alloy. All the other three of wires 10, 12, 14 m the set 2 of wires are also made of the cheaper cobalt alloy, so the entire electrode cable is cheaper than if all the wires were of the same expensive type as the wire 16. All told, an electrode cable is achieved which is cheaper to make and m which expensive material is only used to optimize the cable's electrical conductivity, and cheaper material being used for the wires whose primary task is to give the cable the desired strength.
- the cheaper-to-make high- resistivity wires 10, 12, 14 have the double task of providing lateral support for the expensive low-resistivity wire 16 employed as the primary conductor, and serving as reserve (secondary) cable conductors if the low- resistivity wire or conductor 16 should break, e.g. due to a fatigue stress.
- This reserve function for the wires 10, 12, 14 is also the reason why they are made of an electrically conductive material, even though the material displays poorer conductivity than the material in the wire's 16 low- resistlvity core 22.
- a hybrid type of helically wound electrode cable devised according to the invention and containing three high-resistivity wires and one low- resistivity wire can be expected to be 3-5 times more conductive than a geometrically identical, conventional, helically wound electrode cable.
- the cable in the FIG. which is a bipolar cable, also has an inner, second set 4 of helical wires forming the cable's second pole, in addition to the first set 4 of wires serving as one of the cable's poles.
- the four wires in the second set 4 of wires are designated 26, 28, 30 and 32.
- These four wires can also be devised as a hybrid, i.e. only one of the wires in the inner set of wires 4 can be devised as a low-resistivity conductor containing an expensive material, whereas the other wires can be made of a material which gives the set of wires the desired strength.
- s/D and d/D must be as small as possible.
- d/D 0.5 is very large, whereas d/D ⁇ 0.1 is small.
- the material MP35N has a breaking point at about 1850 MPa and a yield point of about 1250 MPa at a 0.2% offset.
- a wire has a filled core (e.g. a silver filling)
- a hybrid spiral according to the invention with only one silver-filled wire is used, strength and resistance are optimized compared to the use of three or four wires filled with silver.
Abstract
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE69704625T DE69704625T2 (en) | 1996-09-12 | 1997-09-03 | ELECTRODE CABLE FOR ELECTRICAL STIMULATION |
US09/254,605 US6720497B1 (en) | 1996-09-12 | 1997-09-03 | Electrode cable for electrical stimulation |
EP97940511A EP0929343B1 (en) | 1996-09-12 | 1997-09-03 | Electrode cable for electrical stimulation |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
SE9603318A SE9603318D0 (en) | 1996-09-12 | 1996-09-12 | Electrode cable for electrical stimulation |
SE9603318-8 | 1996-09-12 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1998010826A1 true WO1998010826A1 (en) | 1998-03-19 |
Family
ID=20403859
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/SE1997/001470 WO1998010826A1 (en) | 1996-09-12 | 1997-09-03 | Electrode cable for electrical stimulation |
Country Status (5)
Country | Link |
---|---|
US (1) | US6720497B1 (en) |
EP (1) | EP0929343B1 (en) |
DE (1) | DE69704625T2 (en) |
SE (1) | SE9603318D0 (en) |
WO (1) | WO1998010826A1 (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE102009009558A1 (en) * | 2009-02-19 | 2010-08-26 | W.C. Heraeus Gmbh | Wound tape as electrical conductor for stimulation electrodes |
Families Citing this family (17)
Publication number | Priority date | Publication date | Assignee | Title |
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JP4204066B2 (en) * | 2002-12-05 | 2009-01-07 | 保雄 田野 | Artificial vision system |
US7138582B2 (en) * | 2003-06-24 | 2006-11-21 | Medtronic, Inc. | Medical electrical lead conductor formed from modified MP35N alloy |
US8048369B2 (en) * | 2003-09-05 | 2011-11-01 | Ati Properties, Inc. | Cobalt-nickel-chromium-molybdenum alloys with reduced level of titanium nitride inclusions |
US7280875B1 (en) * | 2004-02-04 | 2007-10-09 | Pacesetter, Inc. | High strength, low resistivity electrode |
JP4452724B2 (en) * | 2004-02-11 | 2010-04-21 | フォート ウェイン メタルス リサーチ プロダクツ コーポレイション | Stretched strand-filled tube wire |
US7571010B2 (en) | 2005-05-06 | 2009-08-04 | Cardiac Pacemakers, Inc. | Cable electrode assembly for a lead terminal and method therefor |
EP2254656A1 (en) * | 2008-02-29 | 2010-12-01 | Fort Wayne Metals Research Products Corporation | Alternating core composite wire |
CN102186534B (en) * | 2008-10-15 | 2015-12-16 | 沙皮恩斯脑部刺激控制有限公司 | For the probe of implantable medical device |
DE102009009557A1 (en) | 2009-02-19 | 2010-09-02 | W.C. Heraeus Gmbh | Electrically conductive materials, leads and cables for stimulation electrodes |
US8639352B2 (en) * | 2009-04-06 | 2014-01-28 | Medtronic, Inc. | Wire configuration and method of making for an implantable medical apparatus |
US8471149B2 (en) * | 2010-03-04 | 2013-06-25 | Technical Services For Electronics, Inc. | Shielded electrical cable and method of making the same |
US8340759B2 (en) | 2011-04-22 | 2012-12-25 | Medtronic, Inc. | Large-pitch coil configurations for a medical device |
US8660662B2 (en) * | 2011-04-22 | 2014-02-25 | Medtronic, Inc. | Low impedance, low modulus wire configurations for a medical device |
US9409008B2 (en) | 2011-04-22 | 2016-08-09 | Medtronic, Inc. | Cable configurations for a medical device |
US9245668B1 (en) * | 2011-06-29 | 2016-01-26 | Cercacor Laboratories, Inc. | Low noise cable providing communication between electronic sensor components and patient monitor |
JP5986204B2 (en) * | 2011-08-12 | 2016-09-06 | カーディアック ペースメイカーズ, インコーポレイテッド | Medical device leads with conductor break prediction |
US9427571B2 (en) * | 2012-06-29 | 2016-08-30 | Nuvectra Corporation | Dynamic coil for implantable stimulation leads |
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US4640983A (en) * | 1984-04-09 | 1987-02-03 | Institut Straumann Ag | Conductor device, particularly for at least partial insertion in a human or animal body, comprising a spiral formed from at least one conductor |
EP0622090A1 (en) * | 1993-04-30 | 1994-11-02 | Medtronic, Inc. | Sintered electrode on a substrate |
US5483022A (en) * | 1994-04-12 | 1996-01-09 | Ventritex, Inc. | Implantable conductor coil formed from cabled composite wire |
WO1996026674A1 (en) * | 1995-02-27 | 1996-09-06 | Medtronic, Inc. | Implantable capacitive absolute pressure and temperature monitor system |
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EP0312495A3 (en) * | 1987-10-16 | 1989-08-30 | Institut Straumann Ag | Electrical cable for carrying out at least one stimulation and/or measurement in a human or animal body |
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US5203348A (en) * | 1990-06-06 | 1993-04-20 | Cardiac Pacemakers, Inc. | Subcutaneous defibrillation electrodes |
US5246014A (en) * | 1991-11-08 | 1993-09-21 | Medtronic, Inc. | Implantable lead system |
DE69326080T2 (en) * | 1993-02-01 | 2000-03-09 | Gore & Ass | IMPLANTABLE ELECTRODE |
US5374286A (en) * | 1993-03-31 | 1994-12-20 | Medtronic, Inc. | Torque indicator for fixed screw leads |
US5433744A (en) * | 1994-03-14 | 1995-07-18 | Medtronic, Inc. | Medical electrical lead with super austentic stainless steel conductor |
US5522875A (en) * | 1994-07-28 | 1996-06-04 | Medtronic, Inc. | Medical electrical lead system having a torque transfer stylet |
US5760341A (en) | 1996-09-10 | 1998-06-02 | Medtronic, Inc. | Conductor cable for biomedical lead |
-
1996
- 1996-09-12 SE SE9603318A patent/SE9603318D0/en unknown
-
1997
- 1997-09-03 WO PCT/SE1997/001470 patent/WO1998010826A1/en active IP Right Grant
- 1997-09-03 EP EP97940511A patent/EP0929343B1/en not_active Expired - Lifetime
- 1997-09-03 US US09/254,605 patent/US6720497B1/en not_active Expired - Fee Related
- 1997-09-03 DE DE69704625T patent/DE69704625T2/en not_active Expired - Lifetime
Patent Citations (4)
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US4640983A (en) * | 1984-04-09 | 1987-02-03 | Institut Straumann Ag | Conductor device, particularly for at least partial insertion in a human or animal body, comprising a spiral formed from at least one conductor |
EP0622090A1 (en) * | 1993-04-30 | 1994-11-02 | Medtronic, Inc. | Sintered electrode on a substrate |
US5483022A (en) * | 1994-04-12 | 1996-01-09 | Ventritex, Inc. | Implantable conductor coil formed from cabled composite wire |
WO1996026674A1 (en) * | 1995-02-27 | 1996-09-06 | Medtronic, Inc. | Implantable capacitive absolute pressure and temperature monitor system |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE102009009558A1 (en) * | 2009-02-19 | 2010-08-26 | W.C. Heraeus Gmbh | Wound tape as electrical conductor for stimulation electrodes |
DE102009009558B4 (en) * | 2009-02-19 | 2013-08-29 | Heraeus Precious Metals Gmbh & Co. Kg | Wound tape as electrical conductor for stimulation electrodes |
Also Published As
Publication number | Publication date |
---|---|
DE69704625T2 (en) | 2001-09-06 |
EP0929343B1 (en) | 2001-04-18 |
US6720497B1 (en) | 2004-04-13 |
SE9603318D0 (en) | 1996-09-12 |
DE69704625D1 (en) | 2001-05-23 |
EP0929343A1 (en) | 1999-07-21 |
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