WO1980002231A1 - Cable d'electrode flexible a longue duree - Google Patents

Cable d'electrode flexible a longue duree Download PDF

Info

Publication number
WO1980002231A1
WO1980002231A1 PCT/US1980/000473 US8000473W WO8002231A1 WO 1980002231 A1 WO1980002231 A1 WO 1980002231A1 US 8000473 W US8000473 W US 8000473W WO 8002231 A1 WO8002231 A1 WO 8002231A1
Authority
WO
WIPO (PCT)
Prior art keywords
electrode
wire
inch
lead wire
lead
Prior art date
Application number
PCT/US1980/000473
Other languages
English (en)
Inventor
J Donachy
G Tyers
R Brownlee
H Hughes
Original Assignee
J Donachy
G Tyers
R Brownlee
H Hughes
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
Application filed by J Donachy, G Tyers, R Brownlee, H Hughes filed Critical J Donachy
Priority to AU59979/80A priority Critical patent/AU5997980A/en
Publication of WO1980002231A1 publication Critical patent/WO1980002231A1/fr

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

Definitions

  • Conventional pacemaker electrode leads are formed of coiled, insulated wires having tip and terminal elec- trodes connected at their opposite ends.
  • the wire itself has a diameter of 0.010 inch and the external coil diam ⁇ eter ranges from 0.037 to 0.039 inch.
  • thin guide wires are passed axially through these coils, but due to their small diameter provide the implanting physician with minimal torque control of the electrode tip and no remote flex control.
  • the insu ⁇ lation is in the form of silicone rubber tubing into which the wire coil is inserted during manufacture, and which encapsulates, but usually is not anchored or bonded to, the wire.
  • the thin ⁇ ner layer of insulation results in a final electrode lead no larger, and usually smaller,, than those currently available, but differing substantially in that it may be made up of a large conductor with a • small layer of insu ⁇ lation, in contrast with previous leads having a relatively tenuous conductor encased in a very large layer of insu ⁇ lation. Also, the coating process offers better control of electrode lead flexibility by permitting variations in thickness along the length.
  • a method of manufacturing the lead has been de ⁇ veloped involving dipping which is easily applicable to mass production of the lead and therefore should make the cost comparable with or even less than currently- available mechanically and functionally inferior elec ⁇ trode leads.
  • the electrodes can be con- " . veniently manufactured in volume using one or more con ⁇ trolled dipping machines. These machines in their pres ⁇ ently commercially-obtainable form can be readily modi- fied to dip four to six leads at a time, and two of these machines may be disposed at a time under a conventional laminar flow hood.
  • a single operator can suitably con ⁇ trol at least four dipping machines at a time which will permit the simultaneous production of at least 16 elec- trodes per worker.
  • the segmented polyurethane- coated electrode lead may also be made much smaller (e.g. 0.050 inch O.D.) than current silicone-coated electrodes to accommodate it to special applications such as in elderly patients with very tiny friable veins or in - youger children.
  • Such an external diameter is signifi- cantly smaller than any heretofore achieved with a re ⁇ liable permanent electrode, and facilitates percutaneous insertion.
  • This invention also permits the development of multipolar concentric leads, no larger than current stan- dard unipolar leads, with the further advantage that a single slot in the pacemaker connector block may be used for connecting multiple electrically active members, thus avoiding the bulky configuration of existing bipolar con ⁇ nectors.
  • Fig. 1 is a diagrammatic view in section of a long- life electrode lead constructed in accordance with the present invention.
  • Fig. 2a is a plan view of an electrode lead of the type shown in Fig. 1 in combination with an electrode steering device in accordance with the present invention.
  • Fig. 2b is a side view of the lead and steering device of Fig. 2a.
  • Fig. 3 is a diagrammatic view in section of a concentric bipolar type electrode lead connected to a pacer connector block in accordance with the present in ⁇ vention.
  • Fig. 4a is a perspective view of a pacemaker hav ⁇ ing a connector block with a single port and two elec ⁇ trode-connecting set screws arranged linearly therealong for use with the bipolar electrode lead shown in Fig. 3.
  • Fig. 4b is a perspective view of a prior art pacer having a connector block with a double port arrangement and two electrode-connecting set screws arranged thereon in the manner of the prior art.
  • a long-life pacer electrode lead in accordance with the present invention is shown in section in Fig .1.
  • the electrode lead member 1 is constructed with an elec ⁇ trode tip 2 at one end for contacting the heart of a patient and with a terminal electrode 4 at the other end which is connected to the pacer.
  • a coiled or helical lead wire 3 is connected between the electrodes 2 and 4 with its opposite coiled ends accommodated in appropriate cavities formed within cylindrical portions or extensions 2a and 4a on the electrodes.
  • the coiled ends of the lead wire 3 are conductively connected to the portions 2a and 4a by a low-temperature silver solder or other suitable means 7.
  • the lead wire 3 and the portions 2a and 4a are covered with an insulating material 5, and the terminal end may also be provided with a flex stress resisting, tapered shield member 6 for connecting the lead member 1 to the connector on the pacemaker.
  • An axial channel or lumen 8 is formed within the electrode lead and permits the insertion of a steering mechanism or other guiding tool as will be more fully explained in connection with Figures 2a-b.
  • Multifilar helical coils may be used rather than monofilar, and MP35N or pl ' atinum-iridium may be used instead of Elgiloy.
  • the outside diameter of the coil or helix is made larger such as at least 0.040 inch and preferably much larger, for example, 0.065 or 0.100 inch. The larger diameter reduces the stress on the wire during flexure as compared with that imposed on a lead with a smaller diameter.
  • the insulation 5 is of a polymer which will bond to the wire, preferably segmented polyurethane.
  • Seg ⁇ mented polyurethane has been tested intravascularly in left heart bypass pumps in both patients and animals and found suitable in this environment, as reported in the medical literature and has proven successful in unpub ⁇ lished animal electrode tests.
  • This preferred material is much tougher than the conventionally used silicone rubber while having an elasticity which adds to the mechanical function of the electrode member already im ⁇ proved by the larger outside diameter wire coil.
  • Seg ⁇ mented polyurethane also has a memory so that by heat setting, specific memory effects can be induced into the electrode lead structure for regulating its shape and stiffness. This feature is of value, for example, in right atrial applications where a hook- or J-shaped
  • a suitable process for manufacturing an electrode lead member in accordance with the present invention involves the following steps.
  • the lead wire 3 which has been coiled to the desired enlarged diameter is thoroughly cleaned and its coiled ends conductively con ⁇ nected to the tip portion 2a and terminal portion 4a using low temperature silver solder.
  • Suitable welding techniques, heliarcing,electroplating, or the like may also be used in making this connection or even a mechan ⁇ ical crimp as in current art can be used, although this last technique is- not preferred.
  • the tip and terminal electrode connections to the coil 3 may be made inside the coil, rather than outside as shown, or optimally, the tip portion 2a may be disposed inside to permit reduction of the tip diameter, while the terminal or hub portion may be attached outside the coil, to maximize the size of the steerable guide wire that can be inserted in the channel 8. In any event, a secure permanent attach- ment of the lead wire and the electrodes is performed be ⁇ fore application of the insulation.
  • the lead wire and the portions 2a and 4a are again cleaned with propyl al ⁇ cohol and treated with a primer such as 607 Chemlock primer after which a 15 to 20 minute drying time is al ⁇ lowed.
  • the lead wire 3 and the end portions 2a and 4a are then mounted on a mandrel, which extends axially therethrough, and dipped in the polymer, that is seg ⁇ mented polyurethane,-whose viscosity will be controlled in accordance with the diameter of the wire being dipped. After dipping, the polymer is cured for from 45 minutes to 1 hour at 150° F. The same dipping procedure is then repeated until the proper wall thickness is obtained.
  • a single wall thickness of 0.005 to 0.007 inch, or 0.014 inch total additional diameter, will be suffi- • cient, but the ' electrode member can be coated to any thickness desired, depending upon the application planned for the finished electrode member. Normally the viscosity of the polymer will be such that 0.002 inch is applied with each dipping.
  • a special anchor or tip such as a flange or tine, can be molded on the op ⁇ posite end of the lead for fixing it to the heart of a patient.
  • the finished electrode lead can then be cleaned and inspected and will be ready for use.
  • the stiffness of the lead can be controlled by the spacing of the wire coils and the thickness of the polymer coat ing, a tightly wound helical coil being stiffer than one that has each coil spaced at a specific dimension.
  • the stiffness can be varied along the full length of the member or in any specified area, for example, towards the * tip end to provide increased flexibility and reduce the risk of perforation.
  • the manufacturing operation lends itself to mass production as the dipping may be conveniently carried out in a controlled dipping machine.
  • currently-available machines of this type can be readily modified by the skilled artisan to dip four to six leads at a time under a normal laminar flow hood, which in turn can hold two machines.
  • one operator can productively control at least four machines at a time, one person should be able to polymer coat at least 16 electrode leads at one time.
  • the stimulating electrode tip 2 may be in the form of a ball tip, spher ⁇ ical, bullet shaped, cylindrical or other similar con- figuration and of Elgiloy, platinum, platinum-iridium or other biocompatible material;
  • the end terminal 4 may be of Elgiloy, 316L stainless steel, vitalium, or other corrosion-resistant material; and
  • the flex-stress resist ⁇ ing tapered connector and shield 6 may be of silicone rubber, segmented polyurethane, AVCOTHANE or other bio ⁇ compatible material.
  • the thickness of the segmented polyurethane coat ⁇ ing can be tapered toward the tip of a transvenous or transthoracic version of the electrode member to provide maximum tip flexibility and decrease cardiac tissue trauma and the risk of perforation.
  • the coat ⁇ ing can be gradually thickened toward the terminal con ⁇ nector end to maximize fracture resistance.
  • transvenous lead If a transvenous lead is too flexible, it will not stay in position, but will provide maximal fracture resistance. If the coil diameter is made much larger than 0.065 inch, it has limitations with respect to peripheral vein size, even though much larger bipolar transvenous leads are presently available. Transthoracic leads on the other hand, may have diameters up to a centimeter (0.394 inch), although a somewhat smaller diameter would be optimal. Consequently, coil diameters in the range from 0.040 inch to about 0.100 inch are regarded as optimal with 0.065 inch particularly preferred.
  • a larger channel 8 is available within the wire coil 3 than previously obtainable.
  • the larger channel allows the insertion of a much larger guide wire or a steerable flex-torque control mechanism through the lead to the tip or distal end, thus permitting the application of better torque and angle changes to the electrode tip when manipulating and implanting the electrode apparatus.
  • Am improved steering mechanism 20 for this purpose is shown in Figs. 2a-b.
  • the mechanism 20 has a handle composed of three rings 21a, 21b and 21c for re- spectively receiving the index, thumb and middle fingers of an operator who, in the present case, would be the physician implanting the electrode lead in the heart of a patient.
  • the " rings 21a and 21c are mounted on the op ⁇ posite ends of a crosspiece 22 which is slidable along a rod-like member 23 having ring 21b on one end.
  • the other end of the rod-like member 23 is connected to or integral with a body portion 24 having a longitudinal bore 24a therein.
  • a guide wire member 25 of the flex type is connected to crosspiece 22, by block 22' and set screw 22", and extends through bore 24a into the channel 8 in the electrode lead 1.
  • This three-ring handle and controlled flex guide wire arrangement is essentially kn ⁇ wn,in the art, particularly for use in selective vascu ⁇ lar radiology and bronchial brushing techniques and may be of the type " manufactured by €ook Inc., Bloomington, Ind., as Deflecting Handle, Cat. No. TDH100.
  • body portion 24 is modi ⁇ fied for use with the improved electrode lead. More par ⁇ ticularly, the body portion 24 is adapted at the forward end of the bore 24a to receive the hub or terminal end of an electrode lead, and a bore 27 is provided, which
  • the 10 communicates with the bore 24 and receives a set screw 26.
  • the set screw 26 may be used to engage and fix the end of the lead in the bore 24a so that the lead 1 will fol ⁇ low rotational motion of the handle.
  • the flex guide wire 25 is in ⁇ serted into the channel or lumen 8 in the lead and may . be extended as far as the electrode tip end.
  • the oppo ⁇ site or hub end of the electrode lead is inserted in the handle bore 24a, and the set screw 26 is tightened there-
  • the set screw 26 is released, and the guide wire 25 is removed from the interior of the lead by withdrawing the hub or terminal end of the lead from the three ring handle body. The terminal end of the lead may then be inserted into the receptacle or port in the connector block of a pace ⁇ maker.
  • An additional advantage of the improved manufac ⁇ turing technique and construction is the enhancement of the ability to construct redundant electrodes as required for EMI protection sheaths, bipolar pacing, and/or when separate electrodes are used for pacing and sensing, and/or unipolar pacing and bipolar sensing as disclosed in U.S. Pat. No. 3,977,411.
  • the embodiment of the inven ⁇ tion shown in Fig. 3 represents one multipolar electrode
  • OMPI construction while permitting greater variability of coil size also lends itself to adaptation to simplified, small ⁇ er bipolar electrode leads, the- use of smaller diameter electrodes and the unprecedented application of 360° torque control and over 90° flex control to the electrode tip by means of an improved steering device.
  • the larger coil diameter also facilitates the incorporation of a re ⁇ motely (hub) operated lead tip myocardial grasping mech ⁇ anism to fully take advantage of permanent electrode po ⁇ sitioning in any of the unprecedented variety of locations enabled by the flex torque control mechanism.
  • the leads can be used in a wide variety of applications as well as with pacemakers and other organ stimulators.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Cardiology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Electrotherapy Devices (AREA)

Abstract

Un cable flexible d'electrode (1) pour l'utilisation avec des stimulateurs cardiaques et autres et un procede de preparation du cable, dans lesquels une resistance amelioree a la flexion est obtenue par l'utilisation d'un enroulement de fil conducteur (31) de diametre plus grand avec un diametre se situant dans la gamme de 0,040 a environ 0,100 pouce, de preference d'environ 0,065 pouce, l'extremite (2) et la borne (4) des electrodes etant connectees solidement avant l'application de l'isolement (5) et dans lequel l'isolement est en polyurethane segmente qui est soude au fil et aux electrodes ameliorant la duree et permettant une reduction dans le diametre hors-tout du cable. La reduction en diametre du cable permet aussi la construction de cables concentriques multipolaires (1') pas plus encombrants que les cables standard unipolaires couramment disponibles avec l'avantage supplementaire qu'un bloc de connection (50) de stimulateur avec une seule ouverture peut etre utilise pour relier des pieces multiples actives electriquement. De plus, le plus grand diametre du cable resulte en un canal ou lumiere (8) plus grand de facon marquee a l'interieur de l'enroulement conductif (0,045 pouce ou plus) permettant l'insertion d'un mecanisme de guidage ameliore (20) qui permet un controle jusqu'alors inegale du couple et de la flexion de l'extremite de l'electrode. Finalement, la technique de revetement peut etre utilisee avec des enroulements de diametre standard externe d'environ 0,039 pouce pour aboutir a des conducteurs avec des diametres externes totaux tres petits (par exemple 0,050 pouce) convenant a des utilisations pediatriques et autres necessitant l'acces au travers de tres petites veines ou au travers d'une aiguille intravasculaire ou de protection guide.
PCT/US1980/000473 1979-04-24 1980-04-24 Cable d'electrode flexible a longue duree WO1980002231A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU59979/80A AU5997980A (en) 1979-04-24 1980-04-24 Long-life flexible electrode lead

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US3273179A 1979-04-24 1979-04-24
US32731 1998-02-27

Publications (1)

Publication Number Publication Date
WO1980002231A1 true WO1980002231A1 (fr) 1980-10-30

Family

ID=21866514

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1980/000473 WO1980002231A1 (fr) 1979-04-24 1980-04-24 Cable d'electrode flexible a longue duree

Country Status (2)

Country Link
EP (1) EP0027465A4 (fr)
WO (1) WO1980002231A1 (fr)

Cited By (33)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0044688A1 (fr) * 1980-07-14 1982-01-27 Philip O.(deceased) legally represented by Bates H. Richard Littleford Electrode pour insertion endocardiaque
US4387727A (en) * 1981-03-30 1983-06-14 Medtronic, Inc. Coaxial service kit
US4458695A (en) * 1982-07-16 1984-07-10 Cordis Corporation Multipolar electrode assembly for pacing lead
EP0126981A1 (fr) * 1983-04-28 1984-12-05 Medtronic, Inc. Electrode à polarisation basse et à seuil bas
US4552127A (en) * 1983-04-01 1985-11-12 Peter Schiff Percutaneous intra-aortic balloon having an EKG electrode and a twisting stylet for coupling the EKG electrode to monitoring and/or pacing instrumentation external to the body
US4559951A (en) * 1982-11-29 1985-12-24 Cardiac Pacemakers, Inc. Catheter assembly
EP0215726A2 (fr) * 1985-08-19 1987-03-25 The University Of Melbourne Groupe d'électrodes pour une prothèse
US4660571A (en) * 1985-07-18 1987-04-28 Cordis Corporation Percutaneous lead having radially adjustable electrode
EP0221271A2 (fr) * 1985-09-03 1987-05-13 Monaghan Medical Corporation Electrode pour endoscopes à fibres optiques
WO1987004355A1 (fr) * 1986-01-22 1987-07-30 Westmed Pty. Ltd. Conducteur de stimulation epicardiaque
US4784161A (en) * 1986-11-24 1988-11-15 Telectronics, N.V. Porous pacemaker electrode tip using a porous substrate
WO1989000870A1 (fr) * 1987-07-24 1989-02-09 Cochlear Pty. Ltd. Appareil et procede d'introduction d'une unite a electrode cochleaire
US4840186A (en) * 1987-06-01 1989-06-20 Siemens Aktiengesellschaft Implantable multi-pole coaxial lead
US4844099A (en) * 1986-11-24 1989-07-04 Telectronics, N.V. Porous pacemaker electrode tip using a porous substrate
US4898183A (en) * 1987-07-24 1990-02-06 Cochlear Pty. Limited Apparatus and method for insertion of cochlear electrode assembly
US5016646A (en) * 1988-11-29 1991-05-21 Telectronics, N.V. Thin electrode lead and connections
GB2274736A (en) * 1993-01-28 1994-08-03 Intravascular Res Ltd A micro-coaxial cable
US5363861A (en) * 1991-11-08 1994-11-15 Ep Technologies, Inc. Electrode tip assembly with variable resistance to bending
US5855560A (en) * 1991-11-08 1999-01-05 Ep Technologies, Inc. Catheter tip assembly
US5935465A (en) * 1996-11-05 1999-08-10 Intermedics Inc. Method of making implantable lead including laser wire stripping
EP1547647A1 (fr) * 2003-10-20 2005-06-29 Greatbatch-Hittman, Incorporated Fil électrique implantable
EP1740267A2 (fr) * 2004-04-28 2007-01-10 Transoma Medical, Inc. Dispositifs medicaux implantables et procedes correspondants
WO2010078401A3 (fr) * 2009-01-02 2010-10-21 Medtronic, Inc. Système et procédé pour conducteur cardiaque
US8180438B2 (en) 2008-01-30 2012-05-15 Greatbatch Ltd. Minimally invasive physiologic parameter recorder and introducer system
US8452421B2 (en) 2009-07-08 2013-05-28 Advanced Bionics, Llc Lead insertion tools
US8753352B2 (en) 2010-06-25 2014-06-17 Advanced Bionics Ag Tools, systems, and methods for inserting a pre-curved electrode array portion of a lead into a bodily orifice
US8753353B2 (en) 2010-06-25 2014-06-17 Advanced Bionics Ag Tools, systems, and methods for inserting an electrode array portion of a lead into a bodily orifice
US8774944B2 (en) 2010-06-25 2014-07-08 Advanced Bionics Ag Tools, systems, and methods for inserting an electrode array portion of a lead into a bodily orifice
US9161775B1 (en) 2012-05-08 2015-10-20 Greatbatch Ltd. Tunneling tool for deliberate placement of an ILR
US9474546B1 (en) 2008-04-18 2016-10-25 Advanced Bionics Ag Pre-curved electrode array insertion tools
US9907952B2 (en) 2012-06-01 2018-03-06 Medtronic, Inc. Active fixation medical electrical lead
US10052489B2 (en) 2015-03-23 2018-08-21 Greatbatch Ltd. Apparatus and method for implanting an implantable device
CN110087725A (zh) * 2016-12-16 2019-08-02 美敦力公司 模块化引线

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US3568660A (en) * 1967-11-20 1971-03-09 Battelle Development Corp Pacemaker catheter
US3682162A (en) * 1968-12-13 1972-08-08 Wellcome Found Combined electrode and hypodermic syringe needle
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US3757789A (en) * 1971-10-26 1973-09-11 I Shanker Electromedical stimulator lead connector
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US4046151A (en) * 1976-04-30 1977-09-06 Medtronic, Inc. Body implantable lead with stiffening stylet
US4103690A (en) * 1977-03-21 1978-08-01 Cordis Corporation Self-suturing cardiac pacer lead
US4135518A (en) * 1976-05-21 1979-01-23 Medtronic, Inc. Body implantable lead and electrode
US4142531A (en) * 1977-01-04 1979-03-06 Coratomic, Inc. Catheter
US4146036A (en) * 1977-10-06 1979-03-27 Medtronic, Inc. Body-implantable lead with protector for tissue securing means

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US3568660A (en) * 1967-11-20 1971-03-09 Battelle Development Corp Pacemaker catheter
US3682162A (en) * 1968-12-13 1972-08-08 Wellcome Found Combined electrode and hypodermic syringe needle
US3757789A (en) * 1971-10-26 1973-09-11 I Shanker Electromedical stimulator lead connector
US3757768A (en) * 1972-04-07 1973-09-11 Medical Evaluation Devices And Manipulable spring guide-catheter and tube for intravenous feeding
US3866615A (en) * 1973-01-15 1975-02-18 Daigle Claude W Portable electronic cardiac stimulator
US4033357A (en) * 1975-02-07 1977-07-05 Medtronic, Inc. Non-fibrosing cardiac electrode
US3977411A (en) * 1975-06-12 1976-08-31 Research Corporation Cardiac pacer system and method
US4030508A (en) * 1976-02-04 1977-06-21 Vitatron Medical B.V. Low output electrode for cardiac pacing
US4046151A (en) * 1976-04-30 1977-09-06 Medtronic, Inc. Body implantable lead with stiffening stylet
US4135518A (en) * 1976-05-21 1979-01-23 Medtronic, Inc. Body implantable lead and electrode
US4142531A (en) * 1977-01-04 1979-03-06 Coratomic, Inc. Catheter
US4103690A (en) * 1977-03-21 1978-08-01 Cordis Corporation Self-suturing cardiac pacer lead
US4146036A (en) * 1977-10-06 1979-03-27 Medtronic, Inc. Body-implantable lead with protector for tissue securing means

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Title
See also references of EP0027465A4 *

Cited By (45)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0044688A1 (fr) * 1980-07-14 1982-01-27 Philip O.(deceased) legally represented by Bates H. Richard Littleford Electrode pour insertion endocardiaque
US4387727A (en) * 1981-03-30 1983-06-14 Medtronic, Inc. Coaxial service kit
US4458695A (en) * 1982-07-16 1984-07-10 Cordis Corporation Multipolar electrode assembly for pacing lead
US4559951A (en) * 1982-11-29 1985-12-24 Cardiac Pacemakers, Inc. Catheter assembly
US4552127A (en) * 1983-04-01 1985-11-12 Peter Schiff Percutaneous intra-aortic balloon having an EKG electrode and a twisting stylet for coupling the EKG electrode to monitoring and/or pacing instrumentation external to the body
EP0126981A1 (fr) * 1983-04-28 1984-12-05 Medtronic, Inc. Electrode à polarisation basse et à seuil bas
US4660571A (en) * 1985-07-18 1987-04-28 Cordis Corporation Percutaneous lead having radially adjustable electrode
EP0215726A2 (fr) * 1985-08-19 1987-03-25 The University Of Melbourne Groupe d'électrodes pour une prothèse
EP0215726A3 (fr) * 1985-08-19 1989-04-19 The University Of Melbourne Groupe d'électrodes pour une prothèse
EP0221271A3 (fr) * 1985-09-03 1988-06-29 Monaghan Medical Corporation Electrode pour endoscopes à fibres optiques
EP0221271A2 (fr) * 1985-09-03 1987-05-13 Monaghan Medical Corporation Electrode pour endoscopes à fibres optiques
WO1987004355A1 (fr) * 1986-01-22 1987-07-30 Westmed Pty. Ltd. Conducteur de stimulation epicardiaque
US4784161A (en) * 1986-11-24 1988-11-15 Telectronics, N.V. Porous pacemaker electrode tip using a porous substrate
US4844099A (en) * 1986-11-24 1989-07-04 Telectronics, N.V. Porous pacemaker electrode tip using a porous substrate
US4840186A (en) * 1987-06-01 1989-06-20 Siemens Aktiengesellschaft Implantable multi-pole coaxial lead
WO1989000870A1 (fr) * 1987-07-24 1989-02-09 Cochlear Pty. Ltd. Appareil et procede d'introduction d'une unite a electrode cochleaire
US4898183A (en) * 1987-07-24 1990-02-06 Cochlear Pty. Limited Apparatus and method for insertion of cochlear electrode assembly
US5016646A (en) * 1988-11-29 1991-05-21 Telectronics, N.V. Thin electrode lead and connections
US5363861A (en) * 1991-11-08 1994-11-15 Ep Technologies, Inc. Electrode tip assembly with variable resistance to bending
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EP0027465A1 (fr) 1981-04-29
EP0027465A4 (fr) 1981-08-31

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