+

WO1996006655A1 - Catheter de defibrillation extremement fin - Google Patents

Catheter de defibrillation extremement fin Download PDF

Info

Publication number
WO1996006655A1
WO1996006655A1 PCT/US1995/010926 US9510926W WO9606655A1 WO 1996006655 A1 WO1996006655 A1 WO 1996006655A1 US 9510926 W US9510926 W US 9510926W WO 9606655 A1 WO9606655 A1 WO 9606655A1
Authority
WO
WIPO (PCT)
Prior art keywords
electrode
catheter
defibrillation
coil
low profile
Prior art date
Application number
PCT/US1995/010926
Other languages
English (en)
Inventor
Kenneth M. Anderson
Mark W. Kroll
Original Assignee
Angeion Corporation
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 Angeion Corporation filed Critical Angeion Corporation
Priority to AU36252/95A priority Critical patent/AU3625295A/en
Publication of WO1996006655A1 publication Critical patent/WO1996006655A1/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
    • A61N1/0563—Transvascular endocardial electrode systems specially adapted for defibrillation or cardioversion

Definitions

  • the present invention pertains to a defibrillation device and, more particularly, refers to a low profile defibrillation catheter where at least one of the current conductors is utilized as a defibrillation electrode.
  • the implantable defibrillator requires the use of electrodes to conduct large currents through the human heart. Previously, these electrodes have typically been two or more patches stitched to the heart. These are referred to as epicardial-patch electrodes and require the surgeon to open the chest cavity for placement.
  • electrode coils are sometimes inserted into the heart chambers via venous routes using various procedures known within the medical and surgical arts.
  • a vein such as the subclavian vein, the right or left cephalic vein or the internal or external jugular vein is selected for insertion.
  • the selected vein is exposed by a standard surgical cutdown procedure.
  • the tapered end of a vein pick is inserted into the incised, selected vein.
  • An introducer is then pushed underneath the vein pick into the vein.
  • the defibrillation catheter is then slid into the introducer and the introducer, with the inserted catheter lead, is then gently fed into the vein.
  • the 6655 9 1 The 6655 9 1
  • introducer is then peeled away and discarded.
  • the catheter is then gently pushed through the vein into the vena cava and thence into the heart, where it is positioned.
  • Defibrillation coils used to deliver the electrical current to defibrillate the heart muscle, are often mounted or integral with other functional elements in defibrillation catheters. These coils are known as transvenous electrodes. One coil generally sits just above the right atrium (RA) in a location within the superior vena cava (SVC). The other coil generally lies within the right ventricle at the right ventricular apex (RVA).
  • RA right atrium
  • SVC superior vena cava
  • RVVA right ventricular apex
  • catheter electrodes are often unable to direct sufficient current through enough of the heart muscle to effect defibrillation. For this reason, a small patch is often inserted just under the skin, on the patient's left side, thus requiring additional, but minimal, surgery.
  • This "subcutaneous patch" is not in direct contact with the heart, but provides for a current vector between the transvenous electrode to the subcutaneous patch, thereby passing through the heart muscle. Thus, the subcutaneous patch assists in directing electric current through the heart muscle, and hence, facilitates defibrillating the heart.
  • the primary barrier to increased utilization of catheter electrodes for defibrillation relates to the ability to successfully lower electrode resistances.
  • the present invention is a cardioversion defibrillation transvenous catheter having at least two electrode coils, each electrode coil having a maximum diameter of less than about 6 French.
  • the electrode coils are longitudinally positioned and coaxial with each other in the catheter.
  • the first electrode coil surrounds a conductor coil for a portion of the catheter length where both the first electrode coil and conductor coil are within a dielectric material and terminates at a first electrode coil not having a dielectric material surrounding the first electrode coil.
  • the second conductor coil extends beyond the first electrode coil where the second conductor coil is within the dielectric material and terminates at the distal end of the catheter, where it is either integral with or bonded to the second electrode coil, which is then wound over the conductor coil.
  • the cardioversion defibrillation transvenous catheter has an exposed length of at least one of the at least two electrode coils which is over 30 times, and preferably over 35 times, the maximum catheter electrode diameter.
  • the cardioversion defibrillation transvenous catheter has an exposed length of at least one of the at least two electrode coils which runs along substantially all of the entire inner distance of an average adult human right ventricle, from the right ventricular apex to the entrance of the right ventricle at the coronary tricuspid valve.
  • the catheter of the present invention may have a single electrode coil, the electrode coil having a maximum diameter of less than about 6 French.
  • the single electrode has an exposed length of the electrode coil which is over 30 times, and preferably over 35 times, the maximum catheter electrode diameter.
  • the cardioversion defibrillation transvenous catheter may have an exposed length of electrode coil which runs along substantially all of the entire inner distance of an average adult human right ventricle, from the right ventricular apex to the entrance of the right ventricle at the tricuspid valve.
  • Figure 1 illustrates a schematic representation of a defibrillating system of the prior art with the pulse generator implanted in the abdominal cavity and epicar dial-patch electrodes attached directly to the heart;
  • Figure 2 illustrates a schematic representation of a defibrillating system of the present invention having a SVC electrode, a RVA electrode and one subcutaneous-patch electrode;
  • Figure 3 illustrates a model for estimation of epicardial patch electrode resistance
  • Figure 4 illustrates a model for estimation of electrical resistance with respect to a cylindrical shell
  • Figure 5 illustrates a plan view of a low profile defibrillation catheter according to the present invention
  • Figure 6 illustrates a cross-sectional view of a low profile defibrillation catheter according to the present invention
  • Figure 7 illustrates a cross-sectional view of a second embodiment of a low profile defibrillation catheter according to the present invention
  • Figure 8 illustrates a cutaway view of the distal portion of a second embodiment of a low profile defibrillation catheter tip showing the attachment of the conductor coil to the electrode coil;
  • Figure 9 illustrates a cutaway view of the distal portion of a second embodiment of a low profile defibrillation catheter tip showing the winding direction of the conductor coil and electrode coil.
  • Figure 10 illustrates a plan view of a single electrode embodiment of the low profile defibrillation catheter according to the present invention.
  • FIG. 1 illustrates a schematic drawing of a patient 10 fitted with a defibrillating system of the prior art consisting of a pulse generator 12 implanted in the abdominal cavity and connected to epicardial-patch electrodes 14 and 16 by electrical-lead harness 18.
  • the placement of epicardial-patch electrodes onto the surface of the heart requires that the surgeon open the chest cavity for placement. This is a much more risky procedure than the procedure required to emplace the present invention.
  • patients in need of defibrillating catheters often are poor candidates for surgical procedures requiring that the chest cavity be opened, thereby precluding them from obtaining the life saving benefits that could otherwise result from inventions of the prior art.
  • Fig. 2 illustrates a schematic drawing of a patient 20 implanted with a defibrillating system of the present invention, including a subcutaneously implanted pulse generator 22 in a subclavian position, a subcutaneous patch electrode 24, and a transvenous catheter 26, carrying a SVC electrode coil 28, and a RVA electrode coil 30.
  • electrode coils 28 and 30 are passed transvenously into the heart chambers usually following the subclavian vein to the superior vena cava and into the heart. Electrode coil 28 sits just above the right heart in the superior vena cava at or near its entrance to the right atrium and coil electrode 30 lies in the right ventricular apex.
  • subcutaneous patch electrode 24 is inserted just under the skin, on the patient's left side. This requires additional, but minimal, surgery. This "subcutaneous patch” is not in direct contact with the heart, but enables a current vector starting at a transvenous electrode to pass through the heart muscle. Thus, subcutaneous patch electrode 24 assists in directing current through the heart muscle, and hence, in defibrillating the heart.
  • the resistance be low enough to provide passage of a sufficiently large current through the heart muscle.
  • the second requirement is that the current field lines pass through the vast majority of the heart muscle. This requirement is usually met by having electrodes of sufficient extent. Thus, the primary opportunity for optimization is in lowering the electrode resistance.
  • the resistance for epicardial patch electrodes can be estimated by using standard formulas from physics and the dimensions of the epicardial patches.
  • a typical impedance for epicardial patches across the heart is:
  • FIG. 4 depicts a catheter electrode of radius, r; length, L; and spaced a distance, R, from a patch electrode, W x W.
  • L and the patch W x W is an infinitesimal volume, V*, with a yet to be determined impedance dZ which can be summed to give an overall impedance Z.
  • This volume V* is situated in a general, but moveable distance r* from the center of the rod and has an infinitesimal thickness (that is,
  • the catheter electrode preferably has a maximum diameter of less than about 6 French (i.e., a maximum diameter ⁇ 2 mm) and an overall length of 30 times, and preferably 35 times, the maximum diameter of the catheter electrode for a multiple electrode configuration.
  • the maximum diameter of the electrode is less than about 6 French and preferably less than about 4 French and the overall length of the electrode is at least 30 times, and preferably at least 35 times, the maximum diameter of the catheter electrode.
  • Figures 5 and 6 illustrate the details of the construction of the present catheter. Note that one of the conductors is wound continuously to the end of the catheter and is then either rewound back over itself to form the actual conductive surface or is electrically bonded to another coil which is wound over the conductor coil.
  • Figure 5 depicts a plan view of visible members of the low profile defibrillation catheter 40 including a junction member 42, electrical connectors 44 and 46 extending from the proximal end of junction member 42, a dielectric flexible plastic tubular member 48 extending from the distal end of junction member 42, a flexible wound electrode coil member 50 extending from the interior of flexible plastic tubular member 48, a flexible dielectric plastic tubular covering 52 having flared ends 54 and 56, of which flared end 54 accommodates the distal end of flexible wound coil electrode member 50, flexible wound electrode coil member 158 extending from the interior of flared end 56 and terminating within tined metal catheter tip 60 at the distal end of flexible wound electrode coil member 158.
  • Connector 44 communicates electrically with flexible wound electrode coil member 50 and connector 46 communicates electrically with flexible wound electrode coil member 158.
  • Flexible wound electrode coil member 50 and conductor coil 58 align coaxially within flexible tubular member 48 and then within flared end member 54 as depicted in Figure 6.
  • Figure 6 depicts a cross-sectional view of the major elements of low profile defibrillation catheter 40.
  • Flexible wound electrode coil 50, flexible plastic tube 62 and flexible wound conductor coil member 58 are arranged in a coaxial fashion extending through flexible tubular member 48 and continuing past the distal end of flexible tubular member 48 to expose flexible wound electrode coil member 50 whose distal end secures and terminates suitably within the confines of flared end 54 of flexible plastic tubular member 52.
  • Flexible wound conductor coil member 58 reverses direction at tined metal catheter tip 60 and is wound back over flexible plastic tube 62 and, ultimately, over itself, thus forming electrode coil 158, which is therefore integral to conductor coil member 58.
  • the flexible wound diameter winding which is aligned within the confines of flexible plastic tube 62, as just described, and a major diameter winding which is aligned over and about the outer periphery of flexible plastic tube 62 and subsequently about itself at a finitely spaced distance. After reversal of direction, the major diameter winding of flexible wound electrode coil member 158 is appropriately terminated between flexible plastic tube 62 and flare 56 of flexible plastic tubular member 52. As depicted in Figure 5, the exposure length of exposed electrode coil wires 50 and 158 is extensive along the length of low profile defibrillation catheter 40.
  • Figures 7, 8 and 9 illustrate the details of the construction of a second embodiment, catheter 140.
  • conductor coil 58 is wound continuously to the end of the catheter and is then electrically and physically connected to electrode coil 158 by crimping or welding or crimping and welding conductor coil 58 to either pin 112 or tube 122 then crimping or welding either pin 112 or tube 122 to electrode coil 158.
  • Figure 7 depicts a cross-sectional view of the major elements of low profile defibrillation catheter 140, a second embodiment of the present invention.
  • Flexible wound electrode coil 50, flexible plastic tube 62 and flexible wound conductor coil member 58 are arranged in a coaxial fashion within flexible tubular member 48 and continue past the distal end of flexible tubular member 48 to expose flexible wound electrode coil member 50 whose distal end secures and terminates suitably within the confines of flared end 54 of flexible plastic tubular member 52.
  • Flexible wound conductor coil member 58 resides coaxially within flexible plastic tube 62.
  • Flexible plastic tube 62 coaxially resides within flexible electrode coil member 158, flexible tubular member 52, or flexible wound electrode coil 50.
  • Flexible wound conductor coil member 58 continues distally, terminating at tined metal catheter tip 60 where it is electrically bonded to flexible wound electrode coil member 158, which is wound in the same direction as flexible wound conductor coil member 58.
  • Flexible wound electrode coil member 158 is appropriately terminated between flexible plastic tube 62 and flare 56 of flexible plastic tubular member 52. As depicted for the first embodiment of this invention in Figure 5, the exposure length of exposed electrode coil wires 50 and 158 is extensive along the length of low profile defibrillation catheter 40.
  • Figure 8 illustrates a cutaway view of the distal tip portion of low profile defibrillation catheter 140, a second embodiment of the present invention, showing the attachment of conductor coil 58 to electrode coil 158 at the distal end of catheter 140.
  • the distal connection consists of conductor coil 58 (shown in Fig. 9), electrode coil 158 and two machined pieces, pin 112 and tube 122, joined by laser welding, resistance welding, crimping, or a combination of these processes.
  • Conductor coil 58 consists of a coiled wire, either unifilar or multifilar, commencing at the proximal end of the lead and terminating at the distal end. It provides a durable, conductive path from the pulse generator to the distal, right ventricular electrode.
  • Electrode coil 158 consists of a coiled wire, round or flat in cross section, commencing at the distal end of the lead and extending proximally for the designated length of the exposed electrode.
  • One machined pin 112 is inserted into the distal end of conductor coil 58 and provides a positive stop for the stylet used for implantation as well as a stop for a crimp joint.
  • the second machined piece is a thin walled tube 122 placed over conductor coil 58. The assembly, conductor coil 58, pin 112 and tube 122 is then crimped.
  • tube 122 may be welded onto conductor coil 58. Tube 122 is then welded to pin 112.
  • electrode coil 158 is then welded, laser or resistance, to tube 122 or pin 112.
  • Alternate constructions to the weld include: (1) welding conductor coil 58 and electrode coil 158 to the surface of pin 112 or tube 122 or (2) welding conductor coil 58 and electrode coil 158 to the end of the pin 112.
  • the conductor and electrode coils may be constructed from any material used for the purpose, including platinum-iridium wire, MP35NTM wire, silver cored MP35NTM wire, or noble metal coated MP35NTM wire (with or without a silver core).
  • Pin 112 and tube 122 can be made of the same material which may be MP35NTM , titanium, or stainless steel.
  • MP35NTM is an alloy comprising nickel, cobalt, chromium and molybdenum and is manufactured by Maryland Specialty Wire Company of Cockeysville, Maryland.
  • This assembly provides a physical and electrical connection that maintains the same diameter as the electrode (i.e. isodiametric), thereby allowing a low profile distal tip of the lead, which aids in insertion of the lead into a vein during implantation. It also allows the conductor coil and the electrode coil to be wound in the same direction ( Figure 9). It also provides a stop for a stylet when placed for introduction of the lead into a vein during implantation.
  • FIG. 10 illustrates a plan view of a single electrode embodiment of the low profile defibrillation catheter 140 according to the present invention.
  • junction member 142 is not bifurcated, connecting electrical connector 44, the only electrical connector necessary, to conductor coil 58.
  • Conductor coil 58 extends from the distal end of junction member 142 terminating within the cavity of tined metal catheter tip 60 as previously described.
  • Conductor coil 58 resides coaxially within flexible plastic tube 62 the entire length of the catheter.
  • Flexible plastic tube 62 resides coaxially within electrode coil 158.
  • Electrode coil 158 is electrically bonded to conductor coil 58 in teh same fashion as depicted and described in the two electrode embodiment of the present invention described above.
  • Electrode coil 158 extends proximally from tined metal catheter tip 60 along a substantial portion of catheter 140 terminating in the distal end of flexible tubular member 48.
  • the distal end of tubular member 48 may also possess a flared end to better provide for securing electrode coil between tubular member 48 and flexible plastic tube 62.
  • the materials used in this single electrode embodiment are identical to those used and described above with respect to the two electrode embodiment with the exception of junction member 142.

Landscapes

  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Cardiology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Vascular Medicine (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

Dans cette invention, un cathéter de défibrillation extrêment fin (40) est présenté et revendiqué, cathéter qui est beaucoup plus fin que les dispositifs existants. On obtient cette structure fine en utilisant la bobine du conducteur de courant comme bobine de première électrode (5) et les mêmes matériaux que le conducteur de courant pour la seconde électrode. On forme la bobine d'électrode la plus distale (158) en inversant l'enroulement, puis en enroulant la bobine d'électrode sur elle-même, de façon à former une section de cathéter ayant un diamètre constant sur toute sa longueur. Dans un autre mode de réalisation, la bobine d'électrode la plus distale est fixée à la seconde bobine conductrice et elle est enroulée dans la même direction, formant ainsi également une section de cathéter ayant un diamètre constant sur toute sa longueur. La raison d'être de cette conception fine est motivée par une analyse de champ électrique qui révèle que la longueur du cathéter constitue un facteur important pour déterminer sa capacité de défibrillation et que le grand rayon et la grande superficie des dispositifs de la technique actuelle ne sont pas bénéfiques.
PCT/US1995/010926 1994-08-29 1995-08-29 Catheter de defibrillation extremement fin WO1996006655A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU36252/95A AU3625295A (en) 1994-08-29 1995-08-29 Low profile defibrillation catheter

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US29821394A 1994-08-29 1994-08-29
US08/298,213 1994-08-29

Publications (1)

Publication Number Publication Date
WO1996006655A1 true WO1996006655A1 (fr) 1996-03-07

Family

ID=23149524

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1995/010926 WO1996006655A1 (fr) 1994-08-29 1995-08-29 Catheter de defibrillation extremement fin

Country Status (2)

Country Link
AU (1) AU3625295A (fr)
WO (1) WO1996006655A1 (fr)

Cited By (25)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998048887A1 (fr) * 1997-04-29 1998-11-05 Medtronic, Inc. Systeme de defibrillation intracardiaque
WO2000027471A1 (fr) * 1998-11-10 2000-05-18 Intermedics Inc. Derivation cardiaque avec fil spirale dbs recouvert d'etfe
WO2000027469A3 (fr) * 1998-11-09 2000-08-31 Medtronic Inc Conducteur medical implantable extractible
US6141593A (en) * 1998-11-10 2000-10-31 Intermedics Inc. Cardiac lead with ETEE coated DBS coil
KR20030040820A (ko) * 2001-11-16 2003-05-23 김도균 바지
US7239923B1 (en) 2000-08-01 2007-07-03 Cardiac Pacemakers, Inc. Lead having varying stiffness and method of manufacturing thereof
WO2008115383A2 (fr) * 2007-03-19 2008-09-25 Boston Scientific Neuromodulation Corporation Procédés et appareil de fabrication de fils à partir de conducteurs et configurations de fil souple concernées
WO2013066505A1 (fr) * 2011-11-04 2013-05-10 Cardiac Pacemakers, Inc. Sonde pour dispositif médical implantable comprenant une bobine intérieure à enroulement inverse de celui de la bobine destinée à envoyer des impulsions électriques
US8666508B2 (en) 2008-02-06 2014-03-04 Cardiac Pacemakers, Inc. Lead with MRI compatible design features
US8670840B2 (en) 2006-11-30 2014-03-11 Cardiac Pacemakers, Inc. RF rejecting lead
EP2705874A1 (fr) * 2007-03-19 2014-03-12 Boston Scientific Neuromodulation Corporation Fils compatibles IRM et RF
US8676351B2 (en) 2009-12-31 2014-03-18 Cardiac Pacemakers, Inc. MRI conditionally safe lead with low-profile multi-layer conductor for longitudinal expansion
US8688236B2 (en) 2008-05-09 2014-04-01 Cardiac Pacemakers, Inc. Medical lead coil conductor with spacer element
US8731685B2 (en) 2007-12-06 2014-05-20 Cardiac Pacemakers, Inc. Implantable lead having a variable coil conductor pitch
US8744600B2 (en) 2009-06-26 2014-06-03 Cardiac Pacemakers, Inc. Medical device lead including a unifilar coil with improved torque transmission capacity and reduced MRI heating
US8798767B2 (en) 2009-12-31 2014-08-05 Cardiac Pacemakers, Inc. MRI conditionally safe lead with multi-layer conductor
US8825181B2 (en) 2010-08-30 2014-09-02 Cardiac Pacemakers, Inc. Lead conductor with pitch and torque control for MRI conditionally safe use
US8825179B2 (en) 2012-04-20 2014-09-02 Cardiac Pacemakers, Inc. Implantable medical device lead including a unifilar coiled cable
US8954168B2 (en) 2012-06-01 2015-02-10 Cardiac Pacemakers, Inc. Implantable device lead including a distal electrode assembly with a coiled component
US8958889B2 (en) 2012-08-31 2015-02-17 Cardiac Pacemakers, Inc. MRI compatible lead coil
US8983623B2 (en) 2012-10-18 2015-03-17 Cardiac Pacemakers, Inc. Inductive element for providing MRI compatibility in an implantable medical device lead
US9084883B2 (en) 2009-03-12 2015-07-21 Cardiac Pacemakers, Inc. Thin profile conductor assembly for medical device leads
US9254380B2 (en) 2009-10-19 2016-02-09 Cardiac Pacemakers, Inc. MRI compatible tachycardia lead
US9504821B2 (en) 2014-02-26 2016-11-29 Cardiac Pacemakers, Inc. Construction of an MRI-safe tachycardia lead
US9750944B2 (en) 2009-12-30 2017-09-05 Cardiac Pacemakers, Inc. MRI-conditionally safe medical device lead

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5265623A (en) * 1992-07-16 1993-11-30 Angeion Corporation Optimized field defibrillation catheter

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5265623A (en) * 1992-07-16 1993-11-30 Angeion Corporation Optimized field defibrillation catheter

Cited By (40)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998048887A1 (fr) * 1997-04-29 1998-11-05 Medtronic, Inc. Systeme de defibrillation intracardiaque
WO2000027469A3 (fr) * 1998-11-09 2000-08-31 Medtronic Inc Conducteur medical implantable extractible
WO2000027471A1 (fr) * 1998-11-10 2000-05-18 Intermedics Inc. Derivation cardiaque avec fil spirale dbs recouvert d'etfe
WO2000027470A1 (fr) * 1998-11-10 2000-05-18 Intermedics Inc. Electrode cardiaque a manchon a sertissage interne reduit
US6141593A (en) * 1998-11-10 2000-10-31 Intermedics Inc. Cardiac lead with ETEE coated DBS coil
US7239923B1 (en) 2000-08-01 2007-07-03 Cardiac Pacemakers, Inc. Lead having varying stiffness and method of manufacturing thereof
KR20030040820A (ko) * 2001-11-16 2003-05-23 김도균 바지
US8670840B2 (en) 2006-11-30 2014-03-11 Cardiac Pacemakers, Inc. RF rejecting lead
US9248270B2 (en) 2007-03-19 2016-02-02 Boston Scientific Neuromodulation Corporation Methods and apparatus for fabricating leads with conductors and related flexible
KR101413679B1 (ko) 2007-03-19 2014-07-01 보스톤 사이언티픽 뉴로모듈레이션 코포레이션 Ｍｒｉ 및 ｒｆ 적합성 리드와 관련 리드 작동 방법 및 제조 방법
US10391307B2 (en) 2007-03-19 2019-08-27 Boston Scientific Neuromodulation Corporation MRI and RF compatible leads and related methods of operating and fabricating leads
WO2008115383A3 (fr) * 2007-03-19 2008-12-31 Boston Scient Neuromodulation Procédés et appareil de fabrication de fils à partir de conducteurs et configurations de fil souple concernées
EP2705875A1 (fr) * 2007-03-19 2014-03-12 Boston Scientific Neuromodulation Corporation Fils compatibles IRM et RF
EP2705874A1 (fr) * 2007-03-19 2014-03-12 Boston Scientific Neuromodulation Corporation Fils compatibles IRM et RF
US9630000B2 (en) 2007-03-19 2017-04-25 Boston Scientific Neuromodulation Corporation Methods and apparatus for fabricating leads with conductors and related flexible lead configurations
US9492651B2 (en) 2007-03-19 2016-11-15 MRI Interventions, Inc. MRI and RF compatible leads and related methods of operating and fabricating leads
WO2008115383A2 (fr) * 2007-03-19 2008-09-25 Boston Scientific Neuromodulation Corporation Procédés et appareil de fabrication de fils à partir de conducteurs et configurations de fil souple concernées
KR101413677B1 (ko) 2007-03-19 2014-07-01 엠알아이 인터벤션즈, 인크. 전도체를 갖는 리드 제조 방법 및 장치와 관련 가요성 리드 구성
US8731685B2 (en) 2007-12-06 2014-05-20 Cardiac Pacemakers, Inc. Implantable lead having a variable coil conductor pitch
US8666508B2 (en) 2008-02-06 2014-03-04 Cardiac Pacemakers, Inc. Lead with MRI compatible design features
US8688236B2 (en) 2008-05-09 2014-04-01 Cardiac Pacemakers, Inc. Medical lead coil conductor with spacer element
US9084883B2 (en) 2009-03-12 2015-07-21 Cardiac Pacemakers, Inc. Thin profile conductor assembly for medical device leads
US8744600B2 (en) 2009-06-26 2014-06-03 Cardiac Pacemakers, Inc. Medical device lead including a unifilar coil with improved torque transmission capacity and reduced MRI heating
US9254380B2 (en) 2009-10-19 2016-02-09 Cardiac Pacemakers, Inc. MRI compatible tachycardia lead
US9750944B2 (en) 2009-12-30 2017-09-05 Cardiac Pacemakers, Inc. MRI-conditionally safe medical device lead
US8676351B2 (en) 2009-12-31 2014-03-18 Cardiac Pacemakers, Inc. MRI conditionally safe lead with low-profile multi-layer conductor for longitudinal expansion
US8798767B2 (en) 2009-12-31 2014-08-05 Cardiac Pacemakers, Inc. MRI conditionally safe lead with multi-layer conductor
US9050457B2 (en) 2009-12-31 2015-06-09 Cardiac Pacemakers, Inc. MRI conditionally safe lead with low-profile conductor for longitudinal expansion
US9199077B2 (en) 2009-12-31 2015-12-01 Cardiac Pacemakers, Inc. MRI conditionally safe lead with multi-layer conductor
US8825181B2 (en) 2010-08-30 2014-09-02 Cardiac Pacemakers, Inc. Lead conductor with pitch and torque control for MRI conditionally safe use
WO2013066505A1 (fr) * 2011-11-04 2013-05-10 Cardiac Pacemakers, Inc. Sonde pour dispositif médical implantable comprenant une bobine intérieure à enroulement inverse de celui de la bobine destinée à envoyer des impulsions électriques
US8666512B2 (en) 2011-11-04 2014-03-04 Cardiac Pacemakers, Inc. Implantable medical device lead including inner coil reverse-wound relative to shocking coil
US8825179B2 (en) 2012-04-20 2014-09-02 Cardiac Pacemakers, Inc. Implantable medical device lead including a unifilar coiled cable
US9333344B2 (en) 2012-06-01 2016-05-10 Cardiac Pacemakers, Inc. Implantable device lead including a distal electrode assembly with a coiled component
US8954168B2 (en) 2012-06-01 2015-02-10 Cardiac Pacemakers, Inc. Implantable device lead including a distal electrode assembly with a coiled component
US8958889B2 (en) 2012-08-31 2015-02-17 Cardiac Pacemakers, Inc. MRI compatible lead coil
US8983623B2 (en) 2012-10-18 2015-03-17 Cardiac Pacemakers, Inc. Inductive element for providing MRI compatibility in an implantable medical device lead
US9504822B2 (en) 2012-10-18 2016-11-29 Cardiac Pacemakers, Inc. Inductive element for providing MRI compatibility in an implantable medical device lead
US9504821B2 (en) 2014-02-26 2016-11-29 Cardiac Pacemakers, Inc. Construction of an MRI-safe tachycardia lead
US9682231B2 (en) 2014-02-26 2017-06-20 Cardiac Pacemakers, Inc. Construction of an MRI-safe tachycardia lead

Also Published As

Publication number Publication date
AU3625295A (en) 1996-03-22

Similar Documents

Publication Publication Date Title
US5649974A (en) Low profile defibrillation catheter
WO1996006655A1 (fr) Catheter de defibrillation extremement fin
US5044375A (en) Unitary intravascular defibrillating catheter with separate bipolar sensing
EP0428279B1 (fr) Conducteurs d'électrode tressés et cathéters pour leur utilisation
US4481953A (en) Endocardial lead having helically wound ribbon electrode
US7711437B1 (en) Lead fixation device
US5439485A (en) Flexible defibrillation electrode of improved construction
US6968237B2 (en) Implantable coronary sinus lead and lead system
US4355646A (en) Transvenous defibrillating lead
CA2141530C (fr) Electrode cardiaque installe a long terme eluant des steroides
US6684109B1 (en) Endocardial lead
CA1150775A (fr) Fils d'electrode munis de fourchons
US5534022A (en) Lead having an integrated defibrillation/sensing electrode
US5342414A (en) Transvenous defibrillation lead
US8688236B2 (en) Medical lead coil conductor with spacer element
CA1323666C (fr) Electrode de defibrillation implantable
US5488768A (en) Method of forming a defibrillation electrode connection
US20030220676A1 (en) Electrode arrangements for body implantable pacing and sensing leads
EP2044972B1 (fr) Conducteur de dispositif médical implantable
JPH0567310B2 (fr)
JP2006501028A (ja) 可撓性のアノードを有する心臓静脈リード及びその製造方法
WO2007001862A2 (fr) Derivation implantable a electrodes multiples et procede associe
US5713944A (en) Cardioversion-defibrillation catheter lead having selectively exposable outer conductors
EP2207588B1 (fr) Fil conducteur de stimulation et de détection à structure de fil non enroulé
US5454839A (en) Low profile defibrillation catheter

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AU CA JP

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): AT BE CH DE DK ES FR GB GR IE IT LU MC NL PT SE

DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
121 Ep: the epo has been informed by wipo that ep was designated in this application
122 Ep: pct application non-entry in european phase
NENP Non-entry into the national phase

Ref country code: CA

点击 这是indexloc提供的php浏览器服务，不要输入任何密码和下载