WO2000004948A2 - Electrode vissee a deploiement/retraction - Google Patents

Electrode vissee a deploiement/retraction Download PDF

Info

Publication number
WO2000004948A2
WO2000004948A2 PCT/US1999/016551 US9916551W WO0004948A2 WO 2000004948 A2 WO2000004948 A2 WO 2000004948A2 US 9916551 W US9916551 W US 9916551W WO 0004948 A2 WO0004948 A2 WO 0004948A2
Authority
WO
WIPO (PCT)
Prior art keywords
lead
sleeve
recited
terminal pin
disposed
Prior art date
Application number
PCT/US1999/016551
Other languages
English (en)
Other versions
WO2000004948A3 (fr
Inventor
David M. Flynn
Carol Werlein
Christopher Paul Knapp
Gregory R. Ley
Jason Alan Shiroff
Brian David Soltis
Michael Brenzel
Jason Skubitz
Larry L. Hum
Original Assignee
Cardiac Pacemakers, 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
Priority claimed from US09/121,005 external-priority patent/US6141594A/en
Application filed by Cardiac Pacemakers, Inc. filed Critical Cardiac Pacemakers, Inc.
Priority to AU51217/99A priority Critical patent/AU5121799A/en
Priority to EP99935821A priority patent/EP1105186A2/fr
Publication of WO2000004948A2 publication Critical patent/WO2000004948A2/fr
Publication of WO2000004948A3 publication Critical patent/WO2000004948A3/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
    • 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
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/375—Constructional arrangements, e.g. casings
    • A61N1/3752—Details of casing-lead connections

Definitions

  • the present invention relates generally to implantable leads. More particularly, it pertains to leads having an extendable and retractable fixation mechanism.
  • Electrodes have been used to stimulate contraction of the heart or to reverse certain life threatening arrhythmias, where electrical energy is applied to the heart via the electrodes to return the heart to normal rhythm. Electrodes have also been used to sense and deliver pacing pulses to the atrium and ventricle. Cardiac pacing may be performed by a transvenous method or by electrodes implanted directly onto the epicardium. For transvenous pacing systems, a lead having an electrode is positioned in the right ventricle and/or in the right atrium through a subclavian vein, and the proximal electrode terminals are attached to a pacemaker which is implanted subcutaneously.
  • Some lead designs have "floating" electrodes or electrodes which are not attached to the endocardial wall of the heart.
  • the floating electrodes lay in the blood pool or against the endocardial wall of the heart and the electrode may move slightly within the heart. Since the location of floating electrodes is not fixed with respect to the endocardial wall, the electrical performance of these electrodes varies and is generally less than optimal. Both the electrical sensing capability as well as the pacing delivery capability of such electrodes are suboptimal. The pacing parameters of such a floating electrode are also suboptimal. In addition, the floating electrodes can require increased voltage which unnecessarily drains the battery.
  • leads have been provided with passive fixation elements that affix the electrode to the endocardial wall over time. With passive fixation elements, it can be difficult to determine whether the lead will affix in the location at which it is implanted.
  • Active fixation elements such as a helix
  • a helix have also been provided with distal ends of leads which allow a lead to be affixed to the endocardial wall.
  • the helix is rotated to screw the lead into the endocardial wall.
  • a stylet is disposed within the lead and rotated.
  • the active fixation element may jump out of the end of the lead and damage tissue, and/or the helix.
  • a cardiac pacing system typically includes a pulse generator which supplies the electrical energy to the lead.
  • the pulse generator may be implanted into a subcutaneous pocket made in the wall of the chest.
  • a lead coupled with the pulse generator is routed subcutaneously from the pocket to the shoulder or neck where the lead enters a major vein, such as the subclavian vein, and into the heart.
  • the proximal end of the lead is coupled both electrically and mechanically with the pulse generator at A distal end of the lead is placed within the heart, and a proximal end is placed within a pacemaker.
  • the conductors are individually and electrically coupled with the pulse generator at a proximal end of the multiple conductors.
  • the multiple conductors at the proximal end are electrically insulated from each other to prevent shorts and limit electrical leakage between conductors.
  • Medical adhesive is used to insulate the multiple conductors at the proximal end of the lead.
  • the process of using medical adhesive is timely and costly to assemble.
  • the proximal end of the lead includes a terminal connection which provides the electrical and mechanical connection between the pacemaker and the proximal end of the lead.
  • a terminal connection which provides the electrical and mechanical connection between the pacemaker and the proximal end of the lead.
  • the components of the terminal connection undergo axial stress as the implanter forces the proximal end of the lead into the pacemaker.
  • the implanter may pull on the lead to ensure the terminal end is sufficiently seated in the pacemaker, placing additional axial stress on the terminal connection.
  • An extendable and retractable lead includes a lead body which extends from a distal end to a proximal end.
  • a conductor is disposed within the lead body and extends from the distal end to the proximal end of the lead body.
  • the lead includes an electrode base coupled with the conductor proximate to the distal end of the lead body.
  • the electrode base is threadingly coupled with an outer threaded shell.
  • the electrode base includes external threads disposed thereon.
  • the lead also includes an active fixation element coupled with the electrode base and the outer threaded shell.
  • the lead includes a movement assembly which is configured to extend and retract the active fixation mechanism.
  • the movement assembly includes a housing having an internally threaded portion and an externally threaded collar which is engaged with the internally threaded portion.
  • the movement assembly further includes an internally threaded insert disposed within the lead, where the threaded collar is engaged with the threaded insert.
  • the outer threaded shell is formed of polyetheretherketone.
  • the lead further includes a second outer shell coupled with the outer threaded shell, where the second outer shell forms a stop for the electrode base.
  • the second outer shell is formed of polyetheretherketone.
  • the outer threaded shell is coupled with the second outer shell, for example, with epoxy.
  • the epoxy comprises, in one embodiment, a mixture of one part EPOTEK 353ND to 1.75 parts EPOTEK 353ND-T.
  • the lead further includes a fluoroscopic ring disposed about the fixation helix.
  • a lead includes a lead body extending from a distal end to a proximal end. At least one conductor is disposed within the lead body and extends from the distal end to the proximal end of the lead body.
  • An outer terminal ring is coupled with the lead body, and a sleeve is coupled with the outer terminal ring, and is also coupled with a terminal pin. The coupling allows for rotational movement between the outer terminal ring and the terminal pin.
  • the sleeve is coupled with the outer terminal ring or the terminal pin with a snap-fit coupling.
  • the snap-fit coupling in one embodiment, comprises a first and second set of cantilevered hooks. In another embodiment, the snap-fit coupling comprises an annular flange received in a recess.
  • a lead in another embodiment, includes a lead body extending from a distal end to a proximal end. At least one conductor is disposed within the lead body and extends from the distal end to the proximal end of the lead body.
  • An outer terminal ring is coupled with the lead body, and a sleeve is coupled with the outer terminal ring, and is also coupled with a terminal pin. The sleeve is coupled with the terminal pin with a snap-fit connection.
  • a lead in yet another embodiment, includes a lead body extending from a distal end to a proximal end. At least one conductor is disposed within the lead body and extends from the distal end to the proximal end of the lead body.
  • An outer terminal ring is coupled with the lead body, and a sleeve is coupled with the outer terminal ring, and is also coupled with a terminal pin. The sleeve is coupled with the outer terminal ring or the terminal pin with a press-fit coupling.
  • a lead includes, in another embodiment, a lead body which is coupled with an outer terminal ring.
  • the outer terminal ring is coupled with a terminal pin with a snap-fit connection.
  • An insulator is disposed between the outer terminal ring and the terminal pin, and in one embodiment comprises a non-conductive coating.
  • the outer terminal ring is rotatably coupled with the terminal pin.
  • a system in yet another embodiment, includes an electronics system which has a pulse generator.
  • the pulse generator is electrically coupled with a lead which includes a lead body extending from a distal end to a proximal end. At least one conductor is disposed within the lead body and extends from the distal end to the proximal end of the lead body.
  • An outer terminal ring is coupled with the lead body, and a sleeve is coupled with the outer terminal ring, and is also coupled with a terminal pin. The coupling allows for rotational movement between the outer terminal ring and the terminal pin.
  • the sleeve is coupled with the outer terminal ring or the terminal pin with a snap-fit coupling.
  • the snap-fit coupling in one embodiment, comprises a first and second set of cantilevered hooks.
  • the snap-fit coupling comprises an annular flange received in a recess.
  • the lead further includes a movement assembly which is configured to extend and retract an active fixation mechanism.
  • the movement assembly includes a housing having an internally threaded portion and an externally threaded collar which is engaged with the internally threaded portion.
  • the movement assembly further includes an internally threaded insert disposed within the lead, where the threaded collar is engaged with the threaded insert.
  • the lead assembly described above provides several advantages, for example, ease of manufacturability is increased and through put times are reduced.
  • the individual components can be snapped together, as opposed to waiting for messy bonding or long cure times.
  • Bonding blocks, used for the bonding process are eliminated, which are expensive, difficult and costly to clean.
  • a consistent and increased strength of coupling is achieved using the snap fit design since bonding is variable based on the operator.
  • the geometiy of the snap fit connector provides an insulation with a known thickness, which allows for a repeatable dielectric strength.
  • Figure 1 is a block diagram illustrating a system for delivering and/or receiving signals to and from the heart constructed in accordance with one embodiment.
  • Figure 2 is a cross-section illustrating a terminal end of a lead constructed in accordance with one embodiment.
  • Figure 3 is a cross-section illustrating a distal end of a lead constructed in accordance with one embodiment.
  • Figure 4 is a cross-section illustrating a distal end of a lead constructed in accordance with another embodiment.
  • Figure 5 is a cross-section illustrating a distal end of a lead constructed in accordance with another embodiment.
  • Figure 6 is a perspective view illustrating a portion of a movement assembly end of a lead constructed in accordance with another embodiment.
  • Figure 7 A is a block diagram of a system with a lead for use with a heart and constructed in accordance with one embodiment.
  • Figure 7B is an elevational view of an example of a lead for use in the system shown in Figure 7 A.
  • Figure 7C is a cross-sectional view of a lead coupled with a pulse generator constructed in accordance with one embodiment.
  • Figure 8 is an exploded perspective view of an assembly constructed in accordance with one embodiment.
  • Figure 9 A is an unexploded cross-sectional view of the assembly shown in Figure 8 constructed in accordance with one embodiment.
  • Figure 9B is a cross-section view of a portion of a lead constructed in accordance with another embodiment.
  • Figure 10 is an exploded perspective view of an assembly constructed in accordance with another embodiment.
  • Figure 11 is an unexploded cross-sectional view of the assembly shown in Figure 10 constructed in accordance with one embodiment.
  • Figure 12 is an exploded perspective view of an assembly constructed in accordance with yet another embodiment.
  • Figure 13 is an unexploded cross-sectional view of the assembly shown in Figure 13 constructed in accordance with one embodiment.
  • Figure 14 is an exploded perspective view of an assembly constructed in accordance with one embodiment.
  • Figure 15 is an unexploded cross-sectional view of the assembly shown in Figure 14 constructed in accordance with one embodiment.
  • Figure 16 is an exploded cross-sectional view of an assembly constructed in accordance with one embodiment.
  • Figure 17 is a cross-sectional view of an assembly constructed in accordance with one embodiment.
  • Figure 18 is a cross-sectional view of an assembly constructed in accordance with another embodiment.
  • Figure 19 is an unexploded cross-sectional view of an assembly constructed in accordance with one embodiment.
  • FIG. 1 is a block diagram of a system 100 for delivering and/or receiving electrical pulses or signals to stimulate and/or sense the heart 102.
  • the system 100 includes a pulse generator 105 and a lead 110.
  • the pulse generator 105 includes a source of power as well as an electronic circuitry portion.
  • the pulse generator 105 is a battery-powered device which generates a series of timed electrical discharges or pulses.
  • the pulse generator 105 is generally implanted into a subcutaneous pocket made in the wall of the chest. Alternatively, the pulse generator 105 is placed in a subcutaneous pocket made in the abdomen, or in other locations.
  • the lead 110 includes a lead body 113 which extends from a proximal end 112, where it is coupled with the pulse generator 105, as further discussed below.
  • the lead 110 extends to a distal end 114, which is coupled with a portion of a heart 102, when implanted.
  • the distal end 114 of the lead 110 includes at least one electrode 116 ( Figure 2) which electrically couples the lead 110 with the heart 102.
  • At least one electrical conductor 118 ( Figure 2) is disposed within the lead 110 and extends from the proximal end 112 to the distal end 114 of the lead 100.
  • the at least one electrical conductor 118 electrically couples the electrode 116 with the proximal end 112 of the lead 110.
  • the electrical conductors carry electrical current and pulses between the pulse generator 105 and the electrode 116.
  • Figures 2 and 3 illustrate one embodiment of the distal end 114 of the lead 110 in greater detail, where Figure 2 illustrates the lead 110 in a retracted position and Figure 3 illustrates the lead 110 in an extended position.
  • the electrode 116 comprises a fixation helix 120 which allows for the distal end 114 of the lead 110 to be affixed to the heart 102 ( Figure 1).
  • the fixation helix 120 is mechanically and electrically coupled with an electrode base 122.
  • the electrode base 122 is mechanically coupled with the at least one electrical conductor 118, such that as the conductor 118 is rotated, the electrode base 122 translates along an axis 113 of the lead 110, as will be further discussed below.
  • the electrode base 122 is electrically coupled with the at least one electrical conductor 118, and the electrode base 122 is formed of an electrically conductive material, such as metal.
  • Disposed about the electrode base 122 are external threads 124, which allow the electrode base 122 to rotate and translate the fixation helix 120.
  • the electrode base 122 is coupled with an outer threaded shell 140.
  • a steroid collar 151 is disposed within the distal end 114 of the lead 110.
  • the threaded shell 140 has internal threads 142 therein.
  • the internal threads 142 provide a path for the external threads 124 of the electrode base 122.
  • the external threads 124 engage with the internal threads 142 and translate the electrode base 122 along the axis 113 of the lead 110.
  • the lead 110 includes a stop to prevent the fixation helix 120 from over-extension.
  • the stop comprises, in one embodiment, a stop 144 on the internal threads 142 which blocks the rotation of the external threads 124. Once the external threads 124 reach the stop 144, the electrode base 122 can no longer be rotated and translated out of the lead 110, which prevents the fixation helix 120 from being overextended into tissue of, for example, a heart.
  • the stop comprises a stop 146 formed on an outer shell 145 which is disposed adjacent to the electrode collar 130 (discussed below).
  • the outer threaded shell 140 and/or the outer shell 145 in one embodiment, is formed of polyetheretherketone (PEEK).
  • the outer threaded shell 140 is formed of PEEK 150G, low melt viscosity.
  • the melt viscosity ranges from about .12 - .18 KNs/m 2 , and the tensile strength is greater than or equal to 90 MPa.
  • the threaded shell 140 in another embodiment, comprises PEEK 450G, standard melt viscosity.
  • the melt viscosity ranges from about .38 - .50 KNs/m 2 , and the tensile strength is greater than or equal to 90 MPa.
  • the PEEK allows for the outer threaded shell 140 to be molded, extruded, or machined for tighter tolerances or providing precision structures.
  • PEEK is a tough rigid thermoplastic material which is biocompatible.
  • a fluoroscopy ring 150 Proximate to the distal end 114 of the lead 110 is a fluoroscopy ring 150, which is disposed about the fixation helix 120.
  • the electrode base 122 has, in one embodiment, an electrode collar 130 coupled therewith, such that as the electrode base 122 is translated, the electrode collar 130 translates along the axis 113.
  • the electrode collar 130 translates toward the fluoroscopy ring 150 until the electrode collar 130 abuts a portion the fluoroscopy ring 150, at which point the fixation helix 120 is fully extended.
  • the collar 130 and the ring 150 allows the implanter to view, under fluoroscopy, when the fixation helix 120 is fully extended.
  • the outer shell 145 provides a stop for the translation of the electrode collar 130.
  • the outer shell 145 is coupled with the outer threaded shell 140.
  • Epoxy 190 in one embodiment, is disposed between the outer threaded shell 140 and the outer shell 145.
  • the epoxy 190 comprises a blend of two different epoxies.
  • the two different epoxies are EPOTEK® 353ND and EPOTEK® 353ND-T made by Epoxy Technology.
  • the two epoxies are mixed in the ratio of 1 part EPOTEK® 353ND to 1.75 parts EPOTEK® 353ND-T.
  • the epoxy is cured at a temperature of 150° C for one hour.
  • FIGS. 4 and 5 illustrate another embodiment of a lead 200.
  • the lead 200 includes a retractable active fixation element 270, which assists in avoiding injury to the patient during implantation. Alternatively, the active fixation element 270 rotates without translating along the lead 200.
  • the lead 200 further includes a movement assembly 202 disposed at a distal end 214 of the lead 200, where the movement assembly 202 is adapted to transport the active fixation element 270 in and out of the lead 200 as the active fixation element 270 is rotated.
  • the movement assembly 202 includes external threads 220 associated therewith.
  • the external threads 220 are disposed about a collar 222 of the lead 200.
  • the external threads 220 are adapted to engage with internal threads 226 disposed within a housing 224 of the lead 200.
  • the internal threads 226 provide a helical path for the external threads 220.
  • the movement assembly 202 is not, however, limited to the components described herein.
  • the external threads 220 and the internal threads 226 can be provided on alternative components, and still be considered within the scope of the invention.
  • an insert 230 is provided for the internal threads 226, as shown in Figure 5. As shown in
  • the insert 230 comprises a semi-cylindrical collar 233, where the collar 233 is disposed within the lead 200.
  • a two-piece insert is provided which includes a first half and a second half. The first half and the second half are coupled together to form a cylindrical collar in which there are internal threads.
  • the first half and the second half are molded from plastic material.
  • the first half and the second half are machined from, for example, hard plastic materials or metal, or the materials discussed above.
  • the insert 230 contains internal threads 226 which are adapted to engage with the external threads 220 of the collar 222. During use, a terminal pin
  • the movement assembly 202 can be used with a wide variety of leads implementing active fixation, including, but not limited to, single pass dual chamber pacing leads, single pass dual chamber pacing/defibrillator leads, single chamber pacing leads, and single chamber pacing/defibrillator leads.
  • a mesh screen 240 is provided at a distal end 214 of the lead 200. The mesh screen 240 allows for better tissue in-growth, as well as enhanced sensing capabilities.
  • the mesh screen 240 is disposed proximate to the active fixation element 270.
  • mesh screen 240 moves with the active fixation element 270.
  • the fixation element 270 engages the heart tissue and draws the mesh screen 240 into contact with the surface of the heart.
  • a steroid 242 is disposed within the distal end 214 of the lead 200.
  • Figure 6 illustrates one embodiment of the proximal end 112 of a lead 300 in greater detail.
  • the lead 300 incorporates the embodiments discussed for the distal end discussed above and below.
  • the proximal end 112 of lead 300 includes a terminal pin 310 which provides the electrical connection between the pulse generator 105 ( Figure 1) and the lead 300.
  • the terminal pin 310 is mechanically coupled with a conductor coil 312. As the terminal pin 310 is rotated, the conductor coil 312 rotates, thereby rotating the electrode base ( Figures 2 and 3) as discussed above.
  • the lead 300 further includes an outer terminal ring 314 which is coupled with a lead body 316.
  • An insulator sleeve 318 is disposed over at least a portion of the terminal pin 310, and the insulator sleeve 318 insulates the terminal pin 310 from the outer terminal ring 314.
  • the sleeve 318 is rotatably coupled with the outer terminal ring 314.
  • the sleeve 318 in another embodiment, is coupled with the terminal pin 310 with a snap-fit connection.
  • the sleeve 318 is coupled with the terminal pin 310 and/or the outer terminal ring 314 with a snap-fit connection.
  • the sleeve 318 includes at least one projection 320.
  • the at least one projection 320 is engaged with a recess 330 of the terminal pin 310, and prevents the terminal pin 310 from moving axially.
  • the projection 320 in one embodiment, comprises an annular projection disposed about the circumference of the sleeve 318, which allows the terminal pin 310 to rotate relative to the outer terminal ring 314.
  • the sleeve 318 further includes at least one recess 322 disposed adjacent to the projection 320. The at least one recess 322 receives therein a projection 324 of the terminal pin 310.
  • the additional mating male and female components provide increased axial strength to the connection between the lead 300 and the pulse generator ( Figure 1).
  • the sleeve 318 further includes a stop 360 for the outer terminal ring 314.
  • the sleeve 318 is formed of non-conductive material.
  • the sleeve 318 is formed of polyetheretherketone (PEEK).
  • the sleeve 318 is formed of PEEK 150G, low melt viscosity.
  • the melt viscosity ranges from about .12 - .18 KNs/m 2 , and the tensile strength is greater than or equal to 90 MPa.
  • the sleeve 318 in another embodiment, comprises PEEK 450G, standard melt viscosity.
  • the melt viscosity ranges from about .38 - .50 KNs/m 2 , and the tensile strength is greater than or equal to 90 MPa.
  • the PEEK allows for the sleeve 318 to be molded, extruded, or machined for tighter tolerances or providing precision structures.
  • PEEK is a tough rigid thermoplastic material which is biocompatible.
  • Figures 7 A - 19 illustrate additional embodiments of the lead and lead system.
  • Figure 7 A is a block diagram of a system 1100 for delivering and/or receiving electrical pulses or signals to stimulate and/or sense the heart.
  • the system for delivering pulses 1100 includes a pulse generator 1105 and a lead 1110.
  • the pulse generator 1105 includes a source of power as well as an electronic circuitry portion.
  • the pulse generator 1105 is a battery-powered device which generates a series of timed electrical discharges or pulses used to initiate depolarization of excitable cardiac tissue.
  • the pulse generator 1105 is generally implanted into a subcutaneous pocket made in the wall of the chest. Alternatively, the pulse generator 1105 is placed in a subcutaneous pocket made in the abdomen, or in other locations.
  • the lead 1110 shown in more detail in Figure 7B, extends from a proximal end 1112, where it is coupled with the pulse generator 1105, and extends to a distal end 1114, which is coupled with a portion of a heart 1115, in the implanted condition ( Figure 7A).
  • the proximal end 1112 of the lead 1110 includes an ovennolded portion 1124 which assists in sealing the lead 1110 to the pulse generator 1105.
  • the distal end 1114 of the lead 1110 includes at least one electrode 1116 which electrically couples the lead 1110 with the heart 1115.
  • the electrode 1116 is either a unipolar or bipolar type electrode.
  • At least one electrical conductor (Figure 9B) is disposed within the lead 1110 and electrically couples the electrode 1116 with the proximal end 1112 of the lead 1110.
  • the electrical conductors carry electrical current and pulses between the pulse generator 1105 and the electrode 1116 located in the distal end 1114 of the lead 1110.
  • the body 1111 of the lead 1110 in one embodiment, is cylindrical in shape, and is made of a tubing material formed of a biocompatible polymer suitable for implementation within the human body. Although not required, the tubing is made from a silicone rubber type polymer.
  • the lead 1110 travels from the pulse generator 1105 and into a major vein and the distal end 1114 of the lead 1110, in one embodiment, is placed inside the heart 1115.
  • the lead will be either actively or passively affixed to the endocardial wall of a chamber of the heart, depending on the embodiment.
  • FIGs 8, 9 A, and 9B illustrate another embodiment of the lead including a press-fit design.
  • the assembly 1200 includes a terminal pin 1210, a sleeve 1230, and an outer terminal ring 1260, which are all coupled together such that, after assembly, axial movement of the individual components is prevented, as further described below.
  • the terminal pin 1210 and the outer terminal ring 1260 each provide an electrical connection in between the lead 1110 and the pulse generator 1105, as shown in Figure 7C, and as furth : discussed below.
  • the terminal pin 1210 extends from a first end 1212 to a second end 1214.
  • the second end 1214 is adapted for coupling with the pulse generator 1105, as discussed above ( Figures 7A and 7C).
  • the first end 1212 is adapted to be inserted into other components of the assembly 1200, specifically the sleeve 1230, as will be further described below.
  • the first end 1212 of the terminal pin 1210 includes a tapered portion 1216 which facilitates insertion of the terminal pin 1210 into the sleeve 1230.
  • the terminal pin 1210 includes an assembly portion 1220 which is disposed near the first end 1212.
  • the assembly portion 1220 in one embodiment, includes an outer surface 1222 which extends toward an annular ridge 1224.
  • the outer surface 1222 is adapted to be received within the sleeve 1230, as described below.
  • the outer surface 1222 is tapered from the first end 1212 towards the annular ridge 1224.
  • the annular ridge 1224 forms an engaging surface which is received and retained by the sleeve, as further described below.
  • the terminal pin 1210 also includes an internal surface 1218 which defines a lumen 1219 therein.
  • the lumen 1219 extends through the terminal pin 1210 from the first end 1212 to the second end 1214 and allows for instruments, such as catheters, stylets, or guidewires, to be inserted through the terminal pin 1210 and through the lead 1110 (Figure 7B).
  • the internal surface 1218 of the terminal pin 1210 provides a coupling surface for a first conductor 1280, as illustrated in Figure 9B, whereat the first conductor 1280 is electrically coupled with the terminal pin 1210.
  • the first conductor 1280 provides an electrical connection between the terminal pin 1210 and an electrode of the lead 1110.
  • the assembly 1200 also includes a sleeve 1230.
  • the sleeve 1230 is an insulator between the terminal pin 1210 and the outer terminal ring 1260, where the sleeve 1230 electrically insulates the terminal pin 1210 from the outer terminal ring 1260.
  • the sleeve 1230 provides a mechanical connection between the terminal pin 1210 and the outer terminal ring 1260.
  • the sleeve 1230 extends from a first end 1234 to a second end 1236, where the first end 1234 of the sleeve 1230 couples with the outer terminal ring 1260.
  • the second end 1236 is adapted to couple with the terminal pin 1210.
  • a bore 1232 Disposed through the sleeve 1230 is a bore 1232, where the bore 1232 is adapted to receive the terminal pin 1210 therein.
  • the bore 1232 allows for instruments, such as catheters, stylets, or guidewires, to be inserted through the sleeve 1230 and through the lead 1110 ( Figure 1 IB).
  • the bore 1232 includes an internal surface 1238 which has a coupling feature 1242 thereon.
  • the coupling feature 1242 includes an annular shoulder 1244.
  • the shoulder 1244 engages the annular ridge 1224 of the terminal pin 1210.
  • the sleeve 1230 also includes an external surface 1240.
  • the external surface 1240 in one embodiment, is engaged by the outer terminal ring 1260, and is tapered. In one embodiment, the taper extends from the second end 1236 toward the first end 1234 of the sleeve 1230.
  • the assembly 1200 also includes an outer terminal ring 1260 which extends from a first end 1262 to a second end 1264.
  • the outer terminal ring 1260 includes a coupling portion 1266 which is formed, in one embodiment, on an internal surface 1268 of the outer terminal ring 1260.
  • the internal surface 1268 of the outer terminal ring 1260 is sized to receive the external surface 1240 of the sleeve 1230 therein, such that an interference fit or a press-fit is created thereby.
  • the interference fit between the sleeve 1230 and the outer terminal ring 1260 retains the sleeve 1230 axially to the outer terminal ring 1260.
  • the sleeve 1230 is inserted into the second end 1236 of the sleeve 1230.
  • the terminal pin 1210 is inserted until the annular ridge 1224 engages with the shoulder 1244 of the sleeve 1230.
  • the sleeve 1230 is then coupled with the outer terminal ring 1260 and axial movement between the sleeve 1230 and the outer terminal ring 1260 is prevented.
  • the first end 1234 of the sleeve 1230 is inserted into the second end 1264 of the outer terminal ring 1260.
  • the sleeve 1230 is inserted into the outer terminal ring 1260 until the interference fit is created between the two.
  • the sleeve 1230 can be assembled first with the outer terminal ring 1260 prior to insertion of the terminal pin 1210 into the sleeve 1230.
  • the terminal pin 1210 and the outer terminal ring 1260 are both formed from conductive material.
  • the sleeve 1230 is formed from a nonconductive material, and acts as an insulator between the terminal pin 1210 and the outer terminal ring 1260.
  • the sleeve 1230 can be formed from various high- performance engineering plastics, unreinforced and reinforced materials including, but not limited to polysulfone, polyimide, polyamide, polyacetal, polyketone, polyester, polycarbonate, polyolefin, or liquid crystal polymers.
  • the sleeve 1230 is formed from the materials discussed in the above embodiments. These materials are appropriate for the sleeve 1230 described for Figures 8 and 9, and also for all of the embodiments discussed above and below.
  • Figures 16 and 17 illustrate another embodiment of a snap-fit assembly
  • the terminal pin 1310 which generally includes a terminal pin 1310, a sleeve 1340, and an outer terminal ring 1360.
  • the terminal pin 1310 is adapted to be coupled with the pulse generator 1105 as shown in Figure 7C.
  • the sleeve 1340 is adapted to coupled with the terminal pin 1310 and the outer terminal ring 1360.
  • the terminal pin 1310 extends from a first end 1312 to a second end 1314, and includes a coupling portion 1320 integral therewith.
  • the coupling portion 1320 is formed on an external surface of the terminal pin 1310, and in one embodiment, comprises an annular flange 1322.
  • the annular flange 1322 which can partially or completely encircle the outer surface of the terminal pin 1310, includes mating surfaces 1324 which are adapted to engage with the sleeve 1340, as will be described below.
  • the sleeve 1340 extends from a first end 1342 to a second end 1344, and includes a first set of coupling features 1345.
  • the first set of coupling features 1345 include a first set of cantilever hooks 1346.
  • the first set of cantilever hooks 1346 are adapted to deflect from a hinge point 1347 and are also adapted to couple with a portion of the outer terminal ring 1360.
  • the first set of cantilever hooks 1346 further include, in another embodiment, mating surfaces 1348.
  • the mating surfaces 1348 are disposed proximate to tapered portions 1349 of the first set of cantilever hooks 1346. It should be noted that the first set of cantilever hooks
  • the second set of coupling features 1356 comprise a second set of cantilever hooks 1350.
  • the second set of cantilever hooks 1350 are adapted to couple with the coupling portion 1320 of the terminal pin 1310.
  • the second set of cantilever hooks 1350 in another embodiment, each include a recess 1352 formed therein.
  • the recess 1352 of each of the second set of cantilever hooks 1350 is adapted to receive the annular flange 1322 therein. It should be noted that although a second set of cantilever hooks 1350 are described herein, a single cantilever hook can also be used.
  • a tapered ingress 1358 is formed on the second set of cantilever hooks 1350 to facilitate insertion of the terminal pin 1310 therethrough.
  • the sleeve 1340 also includes a positive stop 1354.
  • the positive stop 1354 has a surface which rests against a portion of the outer terminal ring 1360, preventing further movement thereof.
  • the outer terminal ring 1360 which couples with the sleeve 1340, extends from a first end 1362 to a second end 1364, and has an intermediate portion 1363 therebetween.
  • the outer terminal ring 1360 includes coupling features 1366, which in one embodiment are disposed proximate to the intermediate portion 1363.
  • the coupling features 1366 in another embodiment, include cutouts 1368.
  • the number of cutouts 1368 corresponds to the number of hooks in the first set of cantilever hooks 1346 of the sleeve 1340.
  • the cutouts 1368 also correspond in shape to receive the first set of cantilever hooks 1346 therein.
  • the cutouts 1368 comprise circular apertures.
  • the coupling features 1366 each include a mating surface 1370, which is disposed adjacent the mating surfaces 1348 of the sleeve 1340 when the sleeve 1340 is assembled to the outer terminal ring 1360.
  • the terminal pin 1310 is coupled with the sleeve 1340, and the sleeve 1340 is coupled with the outer terminal ring 1360.
  • the terminal pin 1310 can be assembled first into the sleeve 1340, alternatively, the sleeve can first be coupled with the outer terminal ring 1360.
  • the first end 1312 of the terminal pin 1310 is inserted into the second end 1344 of the sleeve 1340.
  • the second set of cantilever hooks 1350 are deflected by the annular flange 1322.
  • the terminal pin 1310 is further inserted into the sleeve 1340 until the annular flange 1322 is seated within the recess 1352.
  • the terminal pin 1310 and the sleeve 1340 assembly is then coupled with the outer terminal ring 1360.
  • the first end 1342 of the sleeve 1340 is inserted into the second end 1364 of the outer terminal ring 1360.
  • the first set of cantilever hooks 1346 are deflected.
  • the sleeve 1340 is further inserted into the outer terminal ring 1360 until the tapered portion 1349 of the first set of cantilever hooks 1346 are seated within the cutouts 1368 of the outer terminal ring 1360.
  • the mating surfaces 1348 of the cantilever hooks 1346 are placed adjacent to the mating surface 1370 of the outer terminal ring 1360.
  • the terminal pin 1310 and the outer terminal ring 1360 are each formed of a conductive material.
  • the sleeve 1340 is formed from a nonconductive material, and acts as an insulator between the terminal pin 1310 and the outer terminal ring 1360, in one embodiment.
  • the sleeve 1340 can be formed from various high-performance engineering plastics, unreinforced and reinforced materials including, but not limited to polysulfone, polyimide, polyamide, polyacetal, polyketone, polyester, polycarbonate, polyolefin, or liquid crystal polymers.
  • Figures 12 and 13 illustrate another embodiment of a snap-fit assembly 1400 which generally includes a terminal pin 1410, a sleeve 1440, and an outer terminal ring 1470.
  • the sleeve 1440 is adapted for coupling with the outer terminal ring 1470 and the terminal pin 1410.
  • the terminal pin 1410 extends from a first end 1412 to a second end 1414 and includes a coupling portion 1420.
  • the coupling portion 1420 includes tapered projections 1422 which extend away from an external surface of the terminal pin 1410.
  • the tapered projections 1422 can have other shapes such as a rounded projection.
  • the tapered projections 1422 include at least one mating surface 1424, for coupling with a portion of the sleeve 1440, as discussed further below. Although a plurality of projections 1422 are discussed, a single projection can also be used.
  • the sleeve 1440 extends from a first end 1442 to a second end 1444, and includes a first set of coupling features 1445 for coupling with the outer terminal ring 1470.
  • the sleeve 1440 includes a second set of coupling features 1450 for coupling with the terminal pin 1410.
  • the second set of coupling features 1450 in one embodiment, comprise cutouts 1452 formed in cantilever panels 1453.
  • the cantilever panels 1453 are adapted to deflect when an internal or external force is placed thereon.
  • the cutouts 1452 correspond in size and shape and are adapted to receive therein the tapered projections 1422 of the terminal pin 1410.
  • the number of cutouts 1452 correspond to the number of tapered projections 1422.
  • the cutouts 1452 include mating surfaces 1454 which are adjacent to the mating surfaces 1424 of the terminal pin 1410 when the sleeve 1440 is assembled with the terminal pin 1410.
  • the sleeve 1440 also includes a first set of coupling features 1445 for coupling the sleeve 1440 with the outer terminal ring 1470.
  • the first set of coupling features 1445 which in one embodiment are disposed at the first end 1442 of the sleeve 1440, comprise cantilever hooks 1446 which include tapered portions 1447 and also mating surfaces 1448.
  • the cantilever hooks 1446 are adapted to deflect when an external or internal force is placed thereon.
  • the first set of coupling features 1445 are adapted to be received by the outer terminal ring 1470.
  • a positive stop 1456 is formed integral with the sleeve 1440 and is disposed adjacent to the first set of coupling features 1445.
  • the outer terminal ring extends from a first end 1474 to a second end 1476 and includes an inner surface 1472 which receives the sleeve 1440 therein.
  • the outer terminal ring 1470 further includes snap-fit coupling features 1478.
  • the snap-fit coupling features 1478 comprise a tapered surface 1484 formed proximate to the second end 1476 of the outer terminal ring 1470.
  • the tapered surface 1484 is formed near a ridge 1480, which engages with the first set of coupling features 1445 of the sleeve 1440.
  • the coupling features 1478 include a mating surface 1482 which is placed adjacent to the mating surfaces 1448 of the sleeve 1440.
  • the terminal pin 1410 is assembled with the sleeve 1440 and the sleeve 1440 is assembled with the outer terminal ring 1470.
  • the sleeve 1440 can be assembled with the outer terminal ring 1470 prior to assembly of the terminal pin 1410 with the sleeve 1440.
  • the first end 1412 of the terminal pin 1410 is inserted into and through the second end 1444 of the sleeve 1440. The first end 1412 is inserted until the tapered projections 1422 are seated within the second set of coupling features 1450 of the sleeve 1440.
  • the tapered projections 1422 deflect the cantilever panels 1453 outward of the sleeve 1440.
  • the cantilever panels 1453 are deflected until the tapered projections 1422 are seated within the cutouts 1452 of the sleeve, and the mating surfaces 1454 of the cutouts 1452 abut the mating surfaces 1424 of the terminal pin 1410.
  • the first end 1442 of the sleeve 1440 is inserted into the second end 1476 of the outer terminal ring 1470.
  • the first set of coupling features 1445 are deflected as they approach the tapered surface 1484 of the outer terminal ring.
  • the sleeve 1440 is further inserted until the mating surfaces 1448 are seated against the mating surface 1482 of the outer terminal ring.
  • the cantilever hooks 1446 are retained by the annular ridge 1480 of the outer terminal ring 1470.
  • the terminal pin 1410 and the outer terminal ring 1470 are each formed of a conductive material.
  • the sleeve 1440 is formed from a nonconductive material, and acts as an insulator between the terminal pin 1410 and the outer terminal ring 1470, in one embodiment.
  • the sleeve 1440 can be formed from various high-performance engineering plastics, unreinforced and reinforced materials including, but not limited to polysulfone, polyimide, polyamide, polyacetal, polyketone, polyester, polycarbonate, polyolefin, or liquid crystal polymers.
  • Figures 8 and 9 illustrate another embodiment of a snap-fit assembly 1500, which includes generally a terminal pin 1510, a sleeve 1540, and an outer terminal ring 1570.
  • the terminal pin 1510 extends from a first end 1512 to a second end 1514, and includes at least one coupling portion 1516.
  • the coupling portion 1516 is disposed between the first end 1512 and the second end 1514 of the terminal pin 1510.
  • the coupling portion 1516 comprises an annular projection 1518 which extends from an external surface of the terminal pin 1510.
  • the annular projection 1518 in another embodiment, includes a tapered surface 1522 and also a mating surface 1520.
  • the coupling portion 1516 allows for the terminal pin 1510 to be coupled with the sleeve 1540 using a snap-fit connection.
  • the sleeve 1540 is adapted to couple with both the terminal pin 1510 and also the outer terminal ring 1570, and extends generally from a first end 1542 to a second end 1544.
  • a first coupling feature 1546 Proximate to the first end 1542, is a first coupling feature 1546, which allows for the sleeve 1540 to be coupled with the outer terminal ring 1570.
  • the first coupling feature 1546 comprises an annular projection 1548 including a tapered surface 1550 and a mating surface 1552.
  • the sleeve 1540 also includes a second coupling feature 1554 which, in one embodiment, comprises an annular recess 1556.
  • the annular recess 1556 includes a ridge 1558 and also a mating surface 1560, which is adapted to couple with the annular proj ection 1518.
  • the outer terminal ring 1570 is adapted to couple with the sleeve 1540, and generally extends from a first end 1572 to a second end 1574.
  • the outer terminal ring 1570 is defined in part by an inner surface 1576 which is adapted to receive a portion of the sleeve 1540 therein.
  • the outer terminal ring 1570 further includes at least one snap-fit coupling feature 1578 which allows for the sleeve 1540 to be coupled with the outer terminal ring 1570.
  • the coupling feature 1578 includes a tapered ingress 1582 which extends to a ridge 1580.
  • the ridge 1580 includes a mating surface 1584, and is adapted to retain the first coupling feature 1546 of the sleeve 1540.
  • the tapered ingress 1582 and/or the ridge 1580 are formed on the inner surface 1576 of the outer terminal ring 1570.
  • the tapered ingress 1582 is formed annularly of the inner surface 1576.
  • the terminal pin 1510 is coupled with the sleeve 1540, and the sleeve 1540 is coupled with the outer terminal ring 1570. It should be noted however, that the sleeve 1540 can also be first coupled with the outer terminal ring 1570 and then the terminal pin 1510 is coupled with the sleeve 1540.
  • the first end 1512 of the terminal pin 1510 is inserted into the second end 1544 of the sleeve 1540.
  • the terminal pin 1510 is inserted until the coupling portion 1516 is seated within the second coupling feature 1554, of the sleeve.
  • the mating surface 1520 abuts the mating surface 1560 of the sleeve 1540.
  • the first end 1542 of the sleeve 1540 is inserted into the second end 1574 of the outer terminal ring 1570.
  • the tapered surface 1550 deflects the tapered ingress 1582 of the outer terminal ring 1570.
  • the sleeve 1540 is further inserted into the outer terminal ring 1570, until the mating surface 1552 of the first coupling feature 1546 abuts the mating surface 1584 of the outer terminal ring 1570.
  • the terminal pin 1510 and the outer terminal ring 1570 are each formed ' of a conductive material.
  • the sleeve 1540 is formed from a nonconductive material, and acts as an insulator between the terminal pin 1510 and the outer terminal ring 1570, in one embodiment.
  • the materials suitable for the sleeve 1540 are similar to those described for the sleeve discussed above in earlier embodiments
  • the snap-fit assembly 1500 provides several advantages in that the assembly allows for rotational movement, yet prevents axial movement of the terminal pin 1510 relative to the sleeve 1540, and the sleeve 1540 relative to the outer terminal ring 1570.
  • the rotational movement which is allowed by the snap-fit assembly 1500 is advantageous since the snap-fit assembly 1500 can be used in combination with retractable lead designs, or leads which otherwise require rotational movement and yet simultaneously prevent axial movement.
  • Figures 16, 17, and 18 illustrate another embodiment of a snap fit assembly 1600, which includes generally a terminal pin 1620 and an outer terminal ring 1660.
  • the terminal pin 1620 and the outer terminal ring 1660 are adapted to couple together at a snap-fit coupling, as further described below.
  • the terminal pin 1620 extends from a first end 1622 to a second end
  • the coupling portion 1626 is disposed between the first end 1622 and the second end 1624. It should be noted that the coupling portion 1626 can be disposed on an external surface or an internal surface of the terminal pin 1620.
  • the coupling portion 1626 comprises an annular projection 1640, as shown in Figure 17.
  • the annular projection 1640 has a semi-circular cross- section, as shown in Figure 16.
  • the coupling portion 1626 comprises at least one projection 1642, which does not extend completely around the outer surface of the terminal pin 1620, as illustrated in Figure 17.
  • a plurality of projections 1643 can also be provided, as shown in Figure 18. In another embodiment, the plurality of projections 1643 are spaced 90 degrees apart from one another. Disposed through the terminal pin 1620 a bore 1630, where the bore
  • an insulator is disposed between the terminal pin 1620 and the outer terminal ring 1660.
  • the insulator can be a shim, a tube, a wedge, or a coating placed between the terminal pin 1620 and the outer terminal ring 1660.
  • a dielectric coating 1628 is disposed on the interfacing surfaces between the terminal pin 1620 and the outer terminal ring 1660.
  • the coating is disposed over the coupling portion 1626.
  • the dielectric coating 1628 provides insulation for the coupling portion 1626 and/or the surface of the terminal pin 1620.
  • Various insulating materials are appropriate for use as the coating 1628 such as: tungsten carbide, aluminum oxide, chromium oxide, zirconium oxide, magnesium zirconate, acrylic, epoxy, parylene, polyurethane, silicone, teflon, or molybdenum disulfide. Other materials which are also dielectric, biocompatible, wear resistant, and has a low coefficient of friction would also be appropriate.
  • the coupling portion 1626 of the terminal pin 1620 is adapted to snap-fit with a coupling portion of the outer terminal ring 1660.
  • the outer terminal ring 1660 extends from a first end 1662 to a second end 1664, and includes a snap-fit coupling portion 1668.
  • the snap-fit coupling portion 1668 in one embodiment, is disposed on an intermediate portion 1665 of the outer terminal ring 1660. In another embodiment, the coupling portion 1668 is disposed on an inner surface 1666 of the outer terminal ring 1660.
  • the coupling portion 1668 comprises an annular recess 1670 which is sized and positioned to receive the snap-fit coupling portion 1626 of the terminal pin 1620 therein. To assemble the snap-fit assembly 1600, the terminal pin 1620 is coupled with the outer terminal ring 1660.
  • the first end 1622 of the terminal pin 1620 is inserted into the second end 1664 of the outer terminal ring 1660.
  • the terminal pin 1620 is inserted until the annular projection 1640 is seated within the annular recess 1670 of the outer terminal ring 1660. Once the projection 1640 is seated within the recess 1670, further axial movement is prevented. However, rotational movement of the terminal pin 1620 relative to the outer terminal ring 1660 is permitted.
  • the coupling features can be moved from internal to external surfaces and vice versa to accommodate the snap-fit features and/or the press-fit features.
  • the lead design is not limited to the particular embodiments shown or described above, and can be applied to various medical devices. It should be further noted that embodiments discussed for the distal end of the lead can be combined with any of the embodiments for the proximal end of the lead.
  • the lead assembly described above provides several advantages, for example, the ease of manufacturability is increased in that through-put times are reduced.
  • the individual components can be snapped together, as opposed to waiting for messy bonding or long cure times.
  • Bonding blocks, used for the bonding process would be eliminated, which are expensive and difficult and costly to clean.
  • a consistent and increased strength of coupling would be achieved using the snap fit design since bonding is variable based on the operator.
  • the geometry of the snap fit connector provides an insulation with a known thickness, which allows for a repeatable dielectric strength.
  • the active fixation element of the lead does not require the use of a stylet, since the terminal pin is used to extend and retract the active fixation element.
  • the movement assembly allows for the lead to withstand high shearing forces applied between the terminal pin and the outer terminal components such as the ring.

Abstract

Une électrode présentant un mécanisme de fixation capable de se déployer et de se rétracter comporte à son extrémité terminale une broche terminale rotative mettant en rotation le mécanisme de fixation à son extrémité distale. Lorsque la broche terminale est en rotation, la mécanisme de fixation est déployé ou replié depuis l'extrémité distale de l'électrode. Un collet fileté permet au mécanisme de fixation de se déployer ou de se rétracter doucement de l'électrode, et permet un rapport de nombre de tour 1:1 entre la broche terminale et le mécanisme de fixation. Une bague radioscopique disposée au niveau de l'extrémité distale de l'électrode fournit des informations pendant le processus d'implantation.
PCT/US1999/016551 1998-07-22 1999-07-22 Electrode vissee a deploiement/retraction WO2000004948A2 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
AU51217/99A AU5121799A (en) 1998-07-22 1999-07-22 Extendable/retractable screw-in lead
EP99935821A EP1105186A2 (fr) 1998-07-22 1999-07-22 Electrode vissee a deploiement/retraction

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US09/121,005 US6141594A (en) 1998-07-22 1998-07-22 Single pass lead and system with active and passive fixation elements
US09/121,005 1998-07-22
US18422698A 1998-11-02 1998-11-02
US09/184,226 1998-11-02

Publications (2)

Publication Number Publication Date
WO2000004948A2 true WO2000004948A2 (fr) 2000-02-03
WO2000004948A3 WO2000004948A3 (fr) 2000-06-02

Family

ID=26818980

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1999/016551 WO2000004948A2 (fr) 1998-07-22 1999-07-22 Electrode vissee a deploiement/retraction

Country Status (3)

Country Link
EP (1) EP1105186A2 (fr)
AU (1) AU5121799A (fr)
WO (1) WO2000004948A2 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6408214B1 (en) 2000-07-11 2002-06-18 Medtronic, Inc. Deflectable tip catheter for CS pacing
WO2003051455A2 (fr) * 2001-12-14 2003-06-26 Cardiac Pacemakers, Inc. Ensemble derivation a pression-rotation et procede associe

Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4282885A (en) * 1978-08-21 1981-08-11 Bisping Hans Juergen Electrode for implantation in the heart
US4258725A (en) * 1979-09-21 1981-03-31 Medtronic, Inc. Pacing lead with stylet and tapered terminal pin
US4577643A (en) * 1984-05-10 1986-03-25 Cordis Corporation Movable multi-contact electromechanical connection
FR2575925B1 (fr) * 1985-01-16 1988-12-09 Roudy Gil Electrode pour sonde cardiaque de stimulation et de detection
US4667686A (en) * 1985-05-16 1987-05-26 Cordis Corporation Pacer lead terminal assembly
DE3712082A1 (de) * 1987-04-09 1988-10-20 Bisping Hans Juergen Implantierbare elektrodensonde mit aus- und einfahrbarer schraubelektrode
US5007864A (en) * 1989-11-27 1991-04-16 Siemens-Pacesetter, Inc. Device for adapting a pacemaker lead to a pacemaker
US5300108A (en) * 1993-01-05 1994-04-05 Telectronics Pacing Systems, Inc. Active fixation lead with a dual-pitch, free spinning compound screw
US5439391A (en) * 1993-02-09 1995-08-08 Ventritex, Inc. Lead adapter

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
None

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6408214B1 (en) 2000-07-11 2002-06-18 Medtronic, Inc. Deflectable tip catheter for CS pacing
WO2002004062A3 (fr) * 2000-07-11 2002-07-11 Medtronic Inc Cathéter à extrémité béquillable pour stimulation du sinus coronarien
WO2003051455A2 (fr) * 2001-12-14 2003-06-26 Cardiac Pacemakers, Inc. Ensemble derivation a pression-rotation et procede associe
WO2003051455A3 (fr) * 2001-12-14 2003-10-16 Cardiac Pacemakers Inc Ensemble derivation a pression-rotation et procede associe
US6842649B2 (en) 2001-12-14 2005-01-11 Cardiac Pacemakers, Inc. Snap-spin lead assembly and method therefor
EP2133116A3 (fr) * 2001-12-14 2012-05-02 Cardiac Pacemakers, Inc. Ensemble sonde a pression-rotation et procede associe

Also Published As

Publication number Publication date
WO2000004948A3 (fr) 2000-06-02
AU5121799A (en) 2000-02-14
EP1105186A2 (fr) 2001-06-13

Similar Documents

Publication Publication Date Title
US7392095B2 (en) Extendable and retractable lead having a snap-fit terminal connector
US6501990B1 (en) Extendable and retractable lead having a snap-fit terminal connector
US6501994B1 (en) High impedance electrode tip
US6505082B1 (en) Single pass lead system
US5522874A (en) Medical lead having segmented electrode
US5716390A (en) Reduced diameter active fixation pacing lead using concentric interleaved coils
EP1948303B1 (fr) Conducteur implantable dote d une electrode de stimulation et d une electrode d ablation deconnectable
US6183305B1 (en) High strength connector design for passive fixation pacing lead
US6819959B1 (en) Extendable/retractable screw-in tip design with an improved thread/screw mechanism
EP1461116B1 (fr) Ensemble derivation a pression-rotation et procede associe
WO1999030772A2 (fr) Dispositif d'electrodes
WO2000004948A2 (fr) Electrode vissee a deploiement/retraction
EP2491975B1 (fr) Dérivation médicale implantable à fixation active
EP2651499B1 (fr) Fil implantable à fixation active avec entités d'arrêt en rotation
CN106621047B (zh) 主动心脏电导线
US20210001117A1 (en) Shaped monolithic controlled release device for improved drug release in implantable medical leads and leadless pacemakers

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A2

Designated state(s): AU CA JP

AL Designated countries for regional patents

Kind code of ref document: A2

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

121 Ep: the epo has been informed by wipo that ep was designated in this application
DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
AK Designated states

Kind code of ref document: A3

Designated state(s): AU CA JP

AL Designated countries for regional patents

Kind code of ref document: A3

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

WWE Wipo information: entry into national phase

Ref document number: 1999935821

Country of ref document: EP

WWP Wipo information: published in national office

Ref document number: 1999935821

Country of ref document: EP

WWW Wipo information: withdrawn in national office

Ref document number: 1999935821

Country of ref document: EP