US3844292A - Intravascular lead assembly - Google Patents

Intravascular lead assembly Download PDF

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Publication number
US3844292A
US3844292A US00261156A US26115672A US3844292A US 3844292 A US3844292 A US 3844292A US 00261156 A US00261156 A US 00261156A US 26115672 A US26115672 A US 26115672A US 3844292 A US3844292 A US 3844292A
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United States
Prior art keywords
electrode
lead
tissue
allowing
outer tube
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
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US00261156A
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English (en)
Inventor
L Bolduc
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Medtronic Inc
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Medtronic Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Medtronic Inc filed Critical Medtronic Inc
Priority to US00261156A priority Critical patent/US3844292A/en
Priority to CA172,091A priority patent/CA1003502A/en
Priority to AR248393A priority patent/AR197903A1/es
Priority to GB2699973A priority patent/GB1437354A/en
Priority to DE2328996A priority patent/DE2328996A1/de
Priority to NL7308020A priority patent/NL7308020A/xx
Priority to FR7320916A priority patent/FR2187365B1/fr
Priority to JP48064598A priority patent/JPS4956488A/ja
Application granted granted Critical
Publication of US3844292A publication Critical patent/US3844292A/en
Priority to SE7705349A priority patent/SE7705349L/xx
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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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
    • A61N1/057—Anchoring means; Means for fixing the head inside the heart
    • A61N1/0573—Anchoring means; Means for fixing the head inside the heart chacterised by means penetrating the heart tissue, e.g. helix needle or hook
    • 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

  • a body-implantable, intravascular lead assembly which isadapted to be connected to a source of electrical energy at its proximal end. At the distal end of the lead is affixed an electrically conductive barb. Means are provided for inserting the lead in and guiding it through a body vesselto a desired-location'inside the body. Further means are provided for lodging and permanently securing the barb to body tissue at the desired location. Part of the assembly is withdrawn from the vessel after the barbis lodged and secured in the tissue. The lead and a portion of the barb are sealed from body fluids and tissue by a material substantially inert to body fluids and tissue.
  • endocardial leads currently in use are difficult to place and to maintain in proper position and do not insure the best electrical contact since the electrode merely rests against the inner wall of the heart at the apex of the right ventricle.
  • the electrodes of such prior art leads tend to become dislodged from their proper position, often resulting in loss of heart capture and thus loss of stimulation of the patient's heart.
  • the lead tends to move with each contraction of the heart muscle, thereby forming an undesirable callous or fibrotic growth on the inner wall of the right ventricle.
  • Another problem is that with the contraction of the heart, the tip or distal electrode may occasionally puncture the heart wall, resulting in serious injury to the heart and a loss of heart capture.
  • the body-implantable lead of the present invention combines all the advantages of both the myocardial and e ndocardial leads with none of the attendant disadvantages of each of these leads as currently found in the prior art.
  • One of the features of the present invention is the provision of a body-implantable intravascular lead which can be lodged in and permanently secured to the body tissue which it is desired to stimulate.
  • Another feature of the present invention is an extremely thin, durable, very flexible lead with excellent electrical and mechanical properties.
  • An advantage of the present invention is the fact that the electrode is lodgedin and permanently secured to the tissue so that puncturing of the surrounding tissue and formation of a callous or fibrotic growth cannot occur.
  • Still another feature of the present invention is the provision of a very simple, easily operable means for inserting the lead into and guiding it through a body vessel to the desired location.
  • An advantage is realized from the fact that the insertion and guidance means imparts sufficient rigidity to the lead to facilitate its placement, thereby eliminating the need for a stylette and thus allowing the lead to be made thinner and more flexible than would otherwise be possible.
  • Yet another feature is the means for lodging and permanently securing the electrode to the selected body tissue once the lead is in proper position.
  • the insertion and guiding means and the lodging and securing means may be made as an integral, disposable unit which is very simple to manufacture, and extremely easy to operate. Once the electrode is secured in the tissue at the desired location, this unit is easily removed and can be disposed.
  • a body-implantable, intravascular lead comprising electrically conductive lead means adapted to be connected at one end to a source of electrical energy and electrode means affixed to the opposite end of the lead means and adapted to be firmly lodged in and permanently secured to tissue inside the body at a desired location.
  • the lead means and the portion of the electrode means affixed to the lead means are sealed from living animal body fluids and tissue by a material substantially inert to body fluids and tissue.
  • Further means are provided for permitting the lead means and electrode means to be inserted into and guided through a body vessel to a desired location and position inside the body.
  • Means are also provided for permitting the electrode means to be firmly lodged in and permanently secured to body tissue at the desired location.
  • FIG. 5 shows the lead assembly of FIG. 3 in another position for the lodging and securing of the electrode of the lead into the body tissue at the desired location inside the body;
  • FIG. 6 shows the lead assembly of FIGS. 3 and 4 with the electrode of thelead lodged in and permanently secured in the tissue forming the apex of the right ventricle of a heart.
  • FIG. 1 shows a lead 10 having an electrical conductor 12 which may, for example, be of a configuration and construction as the lead described in US. Pat. No. 3,572,344.
  • Affixed to the distal end 14 of conductor 12 is an electrically conductiveelectrode 16 having a sharply-pointed electrically conductive barb 18 formed on the end thereof, both of which may be metallic.
  • Electrode l6 and barb 18 are made of a metal which is substantially inert to body fluids and tissue, such as platinum or a platinum-iridium alloy.
  • Conductor 12 has a covering 20 which is made of a material substantially inert to body fluids and tissue such as, for example, silicone rubber.
  • a substantially cylindrical sleeve 22 Surrounding the distal end 14 of conductor 12 and a portion of electrode 16 is a substantially cylindrical sleeve 22 having three spaced ridges 24 formed integrally therewith along its length.
  • Sleeve 22 and ridges 24 are formed as an integral sleeve and may be made of a material substantially inert to body fluids and tissue, such as silicone rubber.
  • Proximal end 28 of conductor I2 may be fitted with a connector pin (not shown) or in any other manner adapted for connection to a source of electrical energy such as a pulse generator.
  • FIG. 2 shows a cross sectional view of a device 30 which may be used for positioning the lead 10 of FIG. I at the desired location within the body as will be described hereinafter.
  • Device 30 has a pair of concentric, substantially cylindrical'hollow tubes 32 and 34.
  • Tubes 32 and 34 are made of a pliant material, such as, for example, teflon.
  • Outer tube 32 is maintained in a fixed position by a substantially cylindrical, hollow sleeve 38 having a flat plate 40 formed integrally therewith.
  • Sleeve 38 and plate 40 may be made of a machineable polymer such as Delrin or Nylon.
  • Inner tube 34 is axially movable within outer tube 32 and sleeve 38.
  • a plunger 42 Projecting through an opening in plate 40 is a plunger 42, also made of a machineable polymer such as Delrin or Nylon. Plunger 42 has an opening 44 passing therethrough. Plunger 42 has an end 46 to which is affixed inner tube 34. Tube 34 and opening 44 define a passageway in which lead 10 is placed as willbe described later; As plunger 42 is pushed toward plate 40, when the appropriate locking mechanisms are unlocked, tube 34 moves axially within and toward the distal end 48.0f tube 32.
  • Locking mechanism 49 comprises a slide 50 having a pin 52 projecting from one end thereof.
  • Sleeve 38 and plunger 42 have aligning openings in one side thereof through which pin 52 passes for providing this first locking mechanism. With pin 52 in the aligned openings, plunger 42 cannot be moved in either direction.
  • a screw 53 shown in FIG. 2 passes through an elongated opening through plate 40 and into slide 50 and allows slide 50 to move so that pin 52 may be engaged with. or disengaged from, the openings in the sides of sleeve 38 and plunger 42.
  • Device 30 has a second locking mechanism 54 comprising a second slide 56 having a lip 58 which may be grasped for engaging and disengaging an edge 60 of slide 56 with the opposing face of plunger 42.
  • Slide 56 has a pair of legs 62 between which plunger 42 is located.
  • Slide 56 has an elongated opening.
  • a screw 64 passes through plate 40 and slide 56 and together with legs 62 allows slide 56 to have edge 60 engage with and disengage from a groove 66 located in the opposing face of plunger 42.
  • Plunger 42 also has a pair of shoulders 67 on opposite sides thereof which are designed to engage legs 62 when locking mechanism 54 is unlocked and plunger 42 is fully depressed.
  • Lead assembly 70 will be described in the application of using lead 10 as a lead positioned intravenously into the heart for use as a cardiac pacemaker lead.
  • lead I is positioned in the opening defined by tube 34 and opening 44 in plunger 42.
  • Pin 52 of slide 50 is positioned in the aligned openings in sleeve 38 and plunger 42 and slide 56 is in the locked position whereby edge 60 abuts against groove 66 in the opposing face of plunger 42.
  • With locking mechanisms 49 and 54 in their locked positions as shown in FIG.
  • electrode 16 and barb 18 are located well inside outer tube 32 with the sleeve 22 abutting against'the distal end of tube 34. Ridges 24 of sleeve 22 engage the inner wall of tube 32 thereby forming a seal to prevent the back-up of blood into tubes 32 and 34 when device 30 with lead 10 carried thereby is inserted into a body vessel. With the locking mechanisms 49 and 54 in their locked positions, as shown in FIG. 3, the distal end 48 of tube 32 is inserted,
  • Device 30 serves as a means for inserting lead 10 into the vein and guiding it to the desired position in the heart.
  • locking mechanism 49 is unlocked as shown in FIG. 4 by pulling slide 50 so that pin 52 is disengaged from the aligned openings in sleeve 38 and plunger 42.
  • Plunger 42 may then be depressed to move inner tube 34 and lead 10 to a position, shown in FIG. 4, where the edge defined by groove 66 in plunger 42 is stopped by edge of locking mechanism 54. In this position barb 18 just barely extends beyond the end 48 of tube 32 so that the necessary threshold measurements may be taken.
  • the threshold measurements are used to determine whether the electrode position in relation to the heart tissue is adequate or not. Good electrode positioning is important, as only with good positioning can the patients heart be maintained in capture at-low voltages.
  • locking mechanism 54 is unlocked, as shown in FIG. 5,'by moving slide 56 in a direction away from plunger 42. Movement of slide 56 disengages edge 60 of slide 56 from plunger 42. This disengagement allows plunger 42 to be further depressed until shoulders 67 of'plunger 42 engage legs 62 of slide 56, thereby moving electrode 16 a predetermined distance out of tube 32 and driving barb 18 a predetermined distance into the tissue of the heart.
  • FIG. 5 shows plunger 42 in its fully depressed posi- I tion with shoulders 67 abutting legs 62 and with electrode 16 extended beyond end 48 of tube 32.
  • FIG. 6 shows barb l8lodged in and permanently secured in heart tissue and with device 30 partially withdrawn. After device 30 is fully withdrawn from the vein, the proximal end 28 of lead 10 is ready to be connected to the pulse generator for applying stimulating pulses through lead 10 and electrode 16 to the heart.
  • a single lead 10 would be used in a monopolar pacing system. Use of a pair of leads 10 would permit use I claims.
  • a body-implantable, intravascular lead adapted to f be connected at its proximal end to a source of electrical energy and permanently secured at its distal end through the endothelial tissue of a living animal body for electrical stimulation thereof comprising:
  • electrically conductive lead means for insertion in and guidance through a body vessel to a desired location and position inside an organ of a living animal body the lead means having a cross-section which will fit within a body vessel; electrode means affixed to the distalend of said lead means and adapted to supply electrical impulses to tissue at a desired location inside the living animal body, said electrode means including a tissue piercing portion and further including separate tissue engaging means for allowing said electrode means to be firmly lodged in and permanently secured through the endothelial tissue at the desired location; and material means substantially inert to body fluids and tissue encasing said lead means and a portion of said electrode means for sealing them from living animal body fluids and tissue.
  • the means for allowing the electrode means to be firmly lodged in and permanently secured through endothelial tissue comprises means for allowing the el'ectrode'means to be firmly lodged in and permanently secured through endocardial tissue.
  • electrically conductive lead means of a cross-section which will fit within a body vessel having electrode means affixed to its distal end and adapted to be electrically connected at its proximal end to a source of electrical power, said electrode means including a tissue piercing portion and further including separate tissue engaging means for allowing said electrode means to be firmly lodged in and permanently secured through the endothelial tissue of selected organs of living animal bodies; means for inserting and guiding said lead means in and through a body vessel to a desired location and position inside the living animal body organ;
  • said sleeve means has at least one ridge formed on the outer surface thereof the diameter of said ridge being substantially equal to the inside diameter of said outer tube and forming a seal with the inside wall of said outer tube to prevent the back flow of body fluids into said tubes when said sleeve is within said outer tube.
  • said means for lodging and securing includes plunger means connected to said inner tube, said plunger means being adapted to forceably move the inner tube and lead means a predetermined distance so that the electrode means of said lead means moves from a position within the outer tube to a position outside the outer tube, said plunger forceable movement being used to firmly lodge and permanently secure the electrode means through the endothelial tissue of the selected body organ.
  • the lead assembly of claim 3 wherein the means for firmly lodging and permanently securing the electrode means through the endothelial tissue of a selected body organ comprises means for firmly lodging and permanently securing the electrode through endocardial tissue.
  • plunger means for allowing said electrode to be moved a distance, greater than said locking means for firmly lodging and permanently securing said electrode through the endothelial tissue of the selected organ at the desired location.
  • a device as set forth in claim 12 wherein said insertion and guide means comprises inner and outer concentric, flexible tubes, said inner and outer tubes encasing a substantial portion of said lead, said outer tube being constructed and adapted to encase said electrode.
  • a device as set forth in claim 14 further including additional locking means for insuring that said electrode cannot be inadvertently lodged in and secured to body tissue; and said plunger means including means for allowing said electrode to move only a predetermined distance from said outer tube when lodging and securing the electrode in the tissue so as to prevent injury to the tissue.
  • the means for allowing the electrode to be moved a predetermined distance for firmly lodging and permanently securing the electrode through endothelial tissue comprises means for allowing the electrode to be moved a predetermined distance for firmly lodging and permanently securing theelectrode through endocardial tissue.
  • a body-implantable, intravascular lead assembly for use in conjunction with an electro-medical device
  • said lead assembly comprising:
  • electrically conductive lead means of a cross-section which will fit within a body vessel having electrode means affixed to its distal end and adapted to be electrically connected 4 at its proximal end to a source of electrical power, said electrode means including a tissue piercing portion and further including separate tissue engaging means for allowing said electrode means to be firmly lodged in and permanently secured through the endothelial tissue of selected organs of living animal bodies;

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  • Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Heart & Thoracic Surgery (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)
  • Surgical Instruments (AREA)
US00261156A 1972-06-09 1972-06-09 Intravascular lead assembly Expired - Lifetime US3844292A (en)

Priority Applications (9)

Application Number Priority Date Filing Date Title
US00261156A US3844292A (en) 1972-06-09 1972-06-09 Intravascular lead assembly
CA172,091A CA1003502A (en) 1972-06-09 1973-05-24 Intravascular lead assembly
AR248393A AR197903A1 (es) 1972-06-09 1973-06-04 Dispositivo para establecer vinculacion electromedida entre una fuente de energia externa y un organo de un cuerpo vivo
GB2699973A GB1437354A (en) 1972-06-09 1973-06-06 Bodyimplantable leads
DE2328996A DE2328996A1 (de) 1972-06-09 1973-06-07 Intravaskulaere leitungsanordnung
NL7308020A NL7308020A (enrdf_load_stackoverflow) 1972-06-09 1973-06-08
FR7320916A FR2187365B1 (enrdf_load_stackoverflow) 1972-06-09 1973-06-08
JP48064598A JPS4956488A (enrdf_load_stackoverflow) 1972-06-09 1973-06-08
SE7705349A SE7705349L (sv) 1972-06-09 1977-05-09 Implanterbart, intravaskulert ledaraggregat

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Application Number Priority Date Filing Date Title
US00261156A US3844292A (en) 1972-06-09 1972-06-09 Intravascular lead assembly

Publications (1)

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US3844292A true US3844292A (en) 1974-10-29

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US00261156A Expired - Lifetime US3844292A (en) 1972-06-09 1972-06-09 Intravascular lead assembly

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US (1) US3844292A (enrdf_load_stackoverflow)
JP (1) JPS4956488A (enrdf_load_stackoverflow)
AR (1) AR197903A1 (enrdf_load_stackoverflow)
CA (1) CA1003502A (enrdf_load_stackoverflow)
DE (1) DE2328996A1 (enrdf_load_stackoverflow)
FR (1) FR2187365B1 (enrdf_load_stackoverflow)
GB (1) GB1437354A (enrdf_load_stackoverflow)
NL (1) NL7308020A (enrdf_load_stackoverflow)
SE (1) SE7705349L (enrdf_load_stackoverflow)

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US3974834A (en) * 1975-04-23 1976-08-17 Medtronic, Inc. Body-implantable lead
USRE28990E (en) * 1972-12-04 1976-10-05 Corometrics Medical Systems, Inc. Bipolar electrode structure for monitoring fetal heartbeat and the like
US4058128A (en) * 1976-08-26 1977-11-15 Frank Howard A Electrode
US4066085A (en) * 1975-01-14 1978-01-03 Cordis Corporation Contact device for muscle stimulation
US4142530A (en) * 1978-03-06 1979-03-06 Vitatron Medical B. V. Epicardial lead
US4146035A (en) * 1977-09-23 1979-03-27 Edward Basta Endocardial electrode and applicator therefor
EP0013605A1 (en) * 1979-01-05 1980-07-23 Medtronic, Inc. Stylet insertion assembly for body implantable lead
DE2926744A1 (de) * 1979-07-03 1981-01-08 Rainer Ing Grad Koch Thermosonde mit integriertem vorverstaerker in multichiptechnik und elektronisch ausfahrbarer mikroelektrode zur einzelzellableitung und einzelzellreizung waehrend stereotaktischer hirneingriffe
FR2462171A1 (fr) * 1979-07-26 1981-02-13 Cardiofrance Co Dispositif d'introduction et de mise en place d'une sonde ou electrode, perfectionnements apportes aux sondes ou electrodes et outil constituant le dispositif
US4257428A (en) * 1977-12-09 1981-03-24 Barton Steven A Retractable stimulation electrode apparatus and method
US4321931A (en) * 1978-04-10 1982-03-30 Hon Edward D Electrode structure and applicator therefor
US4381013A (en) * 1981-03-19 1983-04-26 Medtronic, Inc. "J" Stylet wire
US4452254A (en) * 1981-07-13 1984-06-05 Goldberg Edward M Cardiac electrode and method for installing same
US4467817A (en) * 1981-04-20 1984-08-28 Cordis Corporation Small diameter lead with introducing assembly
US4501276A (en) * 1982-07-16 1985-02-26 Illinois Tool Works Inc. Fetal electrode apparatus
US4567900A (en) * 1984-06-04 1986-02-04 Moore J Paul Internal deployable defibrillator electrode
US4590949A (en) * 1984-11-01 1986-05-27 Cordis Corporation Neural stimulating lead with stabilizing mechanism and method for using same
USRE32227E (en) * 1981-03-19 1986-08-19 Medtronic, Inc. "J" Stylet wire
US4649938A (en) * 1985-04-29 1987-03-17 Mcarthur William A Tissue-stimulating electrode having sealed, low-friction extendable/retractable active fixation means
US4827940A (en) * 1987-04-13 1989-05-09 Cardiac Pacemakers, Inc. Soluble covering for cardiac pacing electrode
US4841971A (en) * 1987-05-26 1989-06-27 Cordis Leads, Inc. Endocardial lead with projections having saw tooth formation
US5231996A (en) * 1992-01-28 1993-08-03 Medtronic, Inc. Removable endocardial lead
US5246014A (en) * 1991-11-08 1993-09-21 Medtronic, Inc. Implantable lead system
US5282845A (en) * 1990-10-01 1994-02-01 Ventritex, Inc. Multiple electrode deployable lead
US5314462A (en) * 1992-05-27 1994-05-24 Cardiac Pacemakers, Inc. Positive fixation device
WO1994021165A1 (en) * 1993-03-16 1994-09-29 Ep Technologies, Inc. Guide sheaths for cardiac mapping and ablation
US5383922A (en) * 1993-03-15 1995-01-24 Medtronic, Inc. RF lead fixation and implantable lead
US5441504A (en) * 1992-04-09 1995-08-15 Medtronic, Inc. Splittable lead introducer with mechanical opening valve
US5571160A (en) * 1993-07-22 1996-11-05 Pacesetter Ab Permanently curved sleeve for shaping an electrode cable, and method for implanting the cable with the sleeve
WO1998047560A1 (en) 1997-04-21 1998-10-29 Medtronic, Inc. Medical electrical lead
US5851226A (en) * 1996-10-22 1998-12-22 Medtronic, Inc. Temporary transvenous endocardial lead
US5897585A (en) * 1997-12-18 1999-04-27 Medtronic, Inc. Stretchable pacing lead
US5942276A (en) * 1998-01-16 1999-08-24 Medtronic, Inc. Method of manufacturing x-ray visible soluble covering
US6018683A (en) * 1997-04-21 2000-01-25 Medtronic, Inc. Medical electrical lead having coiled and stranded conductors
WO2001002053A1 (en) * 1999-07-07 2001-01-11 Cardiac Pacemakers, Inc. Endocardial electrode assembly having conductive fixation features
WO2001080941A2 (en) 2000-04-26 2001-11-01 Medtronics, Inc. Medical electrical lead with fiber core
US20020177888A1 (en) * 2000-04-26 2002-11-28 Medtronic, Inc. Helix rotation by traction
US20030018364A1 (en) * 2001-07-17 2003-01-23 Medtronic, Inc. Enhanced method and apparatus to identify and connect a small diameter lead with a low profile lead connector
WO2003008037A2 (en) 2001-07-17 2003-01-30 Medtronic,Inc. Automatic implantable medical lead recognition and configuration
US20030120264A1 (en) * 2001-12-08 2003-06-26 Lattouf Omar M. Treatments for a patient with congestive heart failure
US6785576B2 (en) 1997-04-21 2004-08-31 Medtronic, Inc. Medical electrical lead
US20040210245A1 (en) * 2002-07-26 2004-10-21 John Erickson Bendable needle with removable stylet
US20060089692A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead with stylet guide tube
US20060089697A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead
US20060089695A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead with helical reinforcement
US20060089691A1 (en) * 2004-10-21 2006-04-27 Medtronic, Inc. Implantable medical lead with axially oriented coiled wire conductors
WO2012094058A1 (en) 2010-11-12 2012-07-12 Medtronic, Inc. Connectivity detection and type identification of an implanted lead for an implantable medical device
US9999442B2 (en) 2001-12-08 2018-06-19 Trans Cardiac Therapeutics, Inc. Methods for accessing a left ventricle

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DE2533766C2 (de) * 1975-07-29 1986-01-23 Hans-Jürgen Dipl.-Ing. 5100 Aachen Bisping Implantierbare transvenös einführbare Herzschrittmacherleitung
DE2732547A1 (de) 1977-07-19 1979-02-01 Bisping Hans Juergen Implantierbare elektrode
FR2423231A1 (fr) * 1978-04-19 1979-11-16 Synthelabo Sonde de stimulation cardiaque endocavitaire
SE8405544L (sv) * 1984-11-05 1986-05-06 Ewa Herbst Metod for att kunna fastsetta en elektrisk elektrod till en benvevnad och elektrisk elektrod lemplig vid genomforande av en sadan metod
EP0416793A1 (en) * 1989-08-30 1991-03-13 Angeion Corporation Catheter
US5358516A (en) * 1992-12-11 1994-10-25 W. L. Gore & Associates, Inc. Implantable electrophysiology lead and method of making

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Cited By (84)

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Publication number Publication date
SE7705349L (sv) 1977-05-09
AR197903A1 (es) 1974-05-15
FR2187365B1 (enrdf_load_stackoverflow) 1977-12-30
DE2328996A1 (de) 1973-12-20
JPS4956488A (enrdf_load_stackoverflow) 1974-05-31
CA1003502A (en) 1977-01-11
NL7308020A (enrdf_load_stackoverflow) 1973-12-11
GB1437354A (en) 1976-05-26
FR2187365A1 (enrdf_load_stackoverflow) 1974-01-18

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