US3757789A - Electromedical stimulator lead connector - Google Patents

Electromedical stimulator lead connector Download PDF

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US3757789A
US3757789A US00192151A US3757789DA US3757789A US 3757789 A US3757789 A US 3757789A US 00192151 A US00192151 A US 00192151A US 3757789D A US3757789D A US 3757789DA US 3757789 A US3757789 A US 3757789A
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socket
electrical
electrical connector
plug
conductor
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I Shanker
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    • 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
    • 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 system includes a socket having first coupling means.
  • the socket forms an electrical output terminal of the electro-medical device.
  • a plug forms a part of the system and is disposed on the proximal end of an electrical conductor which also forms a part of the system.
  • the plug comprises an electrical connector secured to the conductor and having second coupling means, and a compressible resilient means.
  • the resilient means provides a locking biasing force between the first and second coupling means when the plug and socket are coupled.
  • This invention relates to an electrode system.
  • the invention will here be described in most detail in association with a catheter of the type utilized in connecting a body organ electric stimulator, such as a cardiac pacer, to a body organ since the electrode system according to the invention has been particularly developed for use with such cardiac pacers.
  • the electrode system may be used in conjunction with other electro-medical devices. It might perhaps be used in conjunction with an artificial heart pump system.
  • implantable cardiac pacers have been developed for artificially stimulating a heart which is beating improperly or which has stopped beating entirely. Essentially, this is accomplished by conducting current from an implanted cardiac pacer to the heart muscle by a suitable electrode system or catheter.
  • a catheter typically comprises an elongated tube of body compatable, nonconductive material which contains a helical coil of conductive material.
  • An electrode tip is secured, as by welding, to the distal end of the helical coil and a connector of some type is provided on the proximal end of the catheter for electrically connecting the helical coil of the catheter with the cardiac pacer.
  • a stylet is generally located in the lumina of the helical coil to provide additional stiffness during manipulation of the catheter.
  • One surgical procedure used for the implantation of a pacer includes advancing a catheter transvenously, such as through the jugular vein, until its distal end, i.e., the electrode tip, reaches the apex of the right ventricle of the patients heart where it is impacted in the multiple trabeculae seen in this area, so that the electrode tip makes firm contact with the ventricular myocardium.
  • the stylet is withdrawn and the pacer is connected to the catheter by means of the connector provided on the proximal end of the catheter.
  • One form of a pacer-catheter connection that is presently used requires inserting of a catheter connector or contact provided on the proximal end of the catheter into a socket provided in the pacer; tightening a set screw provided on the pacer adjacent to the socket thereof to make electrical contact; tightening a sealing screw onto an o ring, which sealing screw and o ring are also provided on the pacer; then sealing the screw heads with a sealing compound is required; and finally, the catheter tube must be sealed in a rubber boot cemented into the pacer by tying the boot with sutures.
  • This type connector and these elaborate procedures are required, in part, to assure that the juncture of the catheter and pacer is sealed against the entrance of body fluids into the pacer which, if not prevented, would seriously affect the electronic circuitry of the pacer.
  • the present invention provides an electrode system for efiecting the electrical connection between an electro-medical device, i.e., a pacer, and a patient.
  • the electrode system includes an electrical conductor having proximal and distal ends. The distal end of the conductor is adapted for contact with a body organ of the patient.
  • Socket means are provided which include pin means. The socket means is constructed and arranged to form an electrical output terminal of the electro-medical device.
  • plug means are provided. The plug means is disposed. on the proximal end of the electrical conductor and comprises an electrical connector and a compressible resilient means.
  • the electrical connector is secured to the proximal end of the electrical conductor and has coupling means cooperable with the pin means of the socket means to effect a releasable electrical and mechanical coupling between the socket means and the plug means.
  • the compressible resilient means partially extends over the electrical connector and has portions thereof engageable with coooperating portions of the electro-medical device. The compressible resilient means provides a locking biasing force between the coupling means of the electrical connector and the pin means of the socket means when the plug means and the socket means are coupled.
  • FIG. 1 is a view partially in section and partially in elevation illustrating the electrode system in accordance with the invention in assembled relation with a pacer;
  • FIG. 2 is a side elevational view of the electrical connector in accordance with the invention.
  • FIG. 3 is a view taken along the line III-III of FIG.
  • FIG. 4 is a longitudinal sectional view of the electrical connector of FIG. 2;
  • FIG. 5 is top elevational view of the socket in accordance with the invnetion
  • FIG. 6 is a longitudinal sectional view of the socket of FIG. 5;
  • FIG. 7 is a view taken along the lines VIIVII of FIG. 6;
  • FIG. 8 is an enlargement of a portion of FIG. l'in the vicinity of the socket and plug means in accordance with the invention.
  • the connector 10 is preferably fabricated from stainless steel such as 316 stainless steel.
  • the connector 10 is provided with a generally cylindrical outer surface 12 and an axial passage 14.
  • the right end of the connector 10, as viewed in FIG. 2 is provided with an enlarged, generally hexagonal surface 16 which projects radially outwardly from the surface 12.
  • the left end of the connector, as viewed in FIG. 2 is provided with a coupling means in the form of oppositely disposed axial aligning grooves 18 and 20 and radial locking grooves 22 and 24 which are all provided in the outer surface 12 of the connector 10.
  • the locking grooves 22 and 24 extend circumferentially in the same direction.
  • Disposed within the axial passage 14 is a generally tubular member 26 which is secured therein as by soldering.
  • the socket means in accordance with the invention is shown generally at 30 in FIGS. -7.
  • the socket 30 is also preferably fabricated from stainless steel such as 316 stainless steel.
  • the socket 30 is provided with a generally hexagonal outer surface 32 and a cylindrical cavity 34.
  • the outer surface 32 has a pair of openings 36 and 38 provided therein and press fitted within each opening is a coupling means or pin member 40 each of which extends into the cavity 34.
  • a tapped hole 42 is also provided in the socket 30 into which a screw (not shown) may be screwed.
  • the screw and tapped hole 42 serve as a means of making an electrical connection to the socket 30.
  • FIGS. 1 and 8 there is illustrated the electrode system, in accordance with the invention, in assembled relation with an electro-medical device 43, i.e., a pacer.
  • a catheter is shown generally at 44.
  • the catheter 44 preferably comprises an electrical conductor 46 having proximal and distal ends, 48 and 50 respectively.
  • the electrical conductor 46 may be fabricated of any suitable electrically conductive material but is preferably fabricated of Elgiloy and, it is preferably constructed in the form of a helix.
  • the distal end 50 of the conductor 46 is provided with an electrode tip 52 which may be suitably secured to the distal end by conventional means.
  • the electrode tip 52 is that portion of the catheter via which electrical impulses are applied to a body organ, i.e., the heart in the case of a pacer, as it is the portion of the pacer which is in electrical contact with the patient.
  • the remaining portions of the electrical conductor 46 are insulated from contact with the patient.
  • the conductor 46 is coated with an insulating sheath 54 which coats substantially the entire length of the conductor 46 with the exception of exposed electrode tip 52 and the proximal end 48 which is disposed within the tube 26 of connector 10.
  • the insulating sheath 54 is enlarged at the left end, as viewed in FIG. 8 and partially extends over the electrical connector terminating short of the left end of the connector 10 in a frusto-conical surface 56.
  • the enlarged end of the catheter together with the connector 10 forms a plug means 55 by which a connection between the pacer per se and the conductor 46 is made.
  • the sheath 54 while characterized as a coating, may be formed on the conductor 46 and connector 10 in any suitable manner, as for example, it may be molded onto these parts in a one step operation or in multiple molding operations.
  • the sheath 54 is preferably comprised of a compressible resilient material, i.e., polysiloxane such as silicon rubber.
  • the socket 30 is molded into the encapsulation material 58 which encapsulates the pacer electronic circuitry and the batteries thereof (not shown), and forms an electrical output terminal for the pacer. An electrical connection is made between the pacer circuitry, and the socket 30 via the tapped hole 42, as described, prior to the encapsulation of the pacer circuitry.
  • the pacer can be entirely encapsulated with a suitable body implantable material with the exception of the cavity 34 which is left exposed for later insertion of the connector 10. Accordingly, upon subsequent implantation of the pacer, there will be a minimum opportunity for body fluids to enter into the pacer via any screw holes or openings that would otherwise be required in the absence of the present invention.
  • the plug 55 and the socket 30 are simply and quickly brought in operative engagement by inserting the connector 10 of the plug 55 into the cavity 34 with the axial grooves 18 and 20 of the connector 10 being aligned with the pins 40.
  • the plug 55 is forced into the cavity until the radial grooves 22 and 24 are in alignment with the pins 40 which will occur automatically when the extreme left end 60 of the connector abuts the back wall 62 of the cavity 34.
  • This action will impose a compressive force on the enlarged portion of the catheter, i.e., the plug 55, due to the frustoconical portion of the plug being engaged with the mating and cooperating portions of the pacer in the vicinity of the socket 30.
  • the plug When the radial grooves are aligned with the pins 40, the plug is partially rotated so that the pins 40 are located opposite the regressed portions 64 and 65 of the grooves 22 and 24. Again, this will automatically occur when the plug is rotated and the pins 40 abut the side walls of the radial grooves.
  • the force being used to insert the plug 55 is then relaxed, and the pins will enter the regressed portions 64 and 65 of the radial grooves 22 and 24.
  • the plug 55 or more specifically, the compressible resilient portion thereof, will then provide a locking biasing force between the side walls of the regressed portions of the radially grooves of the connector 10 and the pins 40.
  • An electrical connector assembly for providing an electrical connection between an electromedical device and an electrical conductor, the electrical conductor having proximal and distal ends with the distal end of the conductor being adapted for contact with a body organ of a patient, the electrical connector assembly comprising:
  • socket means constructed and arranged to form an electrical output terminal of the electromedical device, the socket means having a cylindrical cavity and pair of spaced, oppositely disposed pin means extending into the cavity;
  • plug means comprising i. an electrical connector secured to the proximal end of the conductor, the electrical connector being cylindrical and having coupling means cooperable with each of the pin means of the socket electrical connector, when the plug means and means to effect a electrical and positive locking 5 coupling between the socket means and the plug means, the coupling means of the electrical connector comprising a pair of oppositely disposed axial and a pair of oppositely disposed radial grooves all located in the cylindrical outer sur- 10 face of the connector, the radial grooves extending circumferentially in the same direction and v each having a regressed portion into which apin 3.

Abstract

An electrode system for use in conjunction with body implantable electro-medical devices is disclosed. The system includes a socket having first coupling means. The socket forms an electrical output terminal of the electro-medical device. A plug forms a part of the system and is disposed on the proximal end of an electrical conductor which also forms a part of the system. The plug comprises an electrical connector secured to the conductor and having second coupling means, and a compressible resilient means. The resilient means provides a locking biasing force between the first and second coupling means when the plug and socket are coupled.

Description

United States Patent 11 1 Shanker 1 Sept. 11, 1973 [5 1 ELECTROMEDICAL STIMULATOR LEAD CONNECTOR [75] Inventor: Irvin P. Shanker, Huntingdon Valley, Pa.
[73] Assignee: ESB Incorporated, Philadelphia, Pa.
[22] Filed: Oct. 26, 1971 l 211 App]. No.1 192,151
Thomas 339/90 R Senior, Jr 339/60 R [57] ABSTRACT An electrode system for use in conjunction with body implantable electro-medical devices is disclosed. The system includes a socket having first coupling means. The socket forms an electrical output terminal of the electro-medical device. A plug forms a part of the system and is disposed on the proximal end of an electrical conductor which also forms a part of the system. The plug comprises an electrical connector secured to the conductor and having second coupling means, and a compressible resilient means. The resilient means provides a locking biasing force between the first and second coupling means when the plug and socket are coupled.
4 Claims, 8 Drawing Figures BACKGROUND OF THE INVENTION 1. Field of the Invention This invention relates to an electrode system. The invention will here be described in most detail in association with a catheter of the type utilized in connecting a body organ electric stimulator, such as a cardiac pacer, to a body organ since the electrode system according to the invention has been particularly developed for use with such cardiac pacers. The electrode system, however, may be used in conjunction with other electro-medical devices. It might perhaps be used in conjunction with an artificial heart pump system.
2. Description of the Prior Art.
It may be explained that in the past decade body implantable cardiac pacers have been developed for artificially stimulating a heart which is beating improperly or which has stopped beating entirely. Essentially, this is accomplished by conducting current from an implanted cardiac pacer to the heart muscle by a suitable electrode system or catheter.
Various types of cardiac pacers as well as various types of catheters have been heretofore developed. The various designs of both the pacers and the catheters have in some respects simplified the surgical procedures required during the implantation of the pacers.
Typically, a catheter comprises an elongated tube of body compatable, nonconductive material which contains a helical coil of conductive material. An electrode tip is secured, as by welding, to the distal end of the helical coil and a connector of some type is provided on the proximal end of the catheter for electrically connecting the helical coil of the catheter with the cardiac pacer. A stylet is generally located in the lumina of the helical coil to provide additional stiffness during manipulation of the catheter.
One surgical procedure used for the implantation of a pacer includes advancing a catheter transvenously, such as through the jugular vein, until its distal end, i.e., the electrode tip, reaches the apex of the right ventricle of the patients heart where it is impacted in the multiple trabeculae seen in this area, so that the electrode tip makes firm contact with the ventricular myocardium. Once the electrode tip has been properly positioned the stylet is withdrawn and the pacer is connected to the catheter by means of the connector provided on the proximal end of the catheter.
One form of a pacer-catheter connection that is presently used requires inserting of a catheter connector or contact provided on the proximal end of the catheter into a socket provided in the pacer; tightening a set screw provided on the pacer adjacent to the socket thereof to make electrical contact; tightening a sealing screw onto an o ring, which sealing screw and o ring are also provided on the pacer; then sealing the screw heads with a sealing compound is required; and finally, the catheter tube must be sealed in a rubber boot cemented into the pacer by tying the boot with sutures. This type connector and these elaborate procedures are required, in part, to assure that the juncture of the catheter and pacer is sealed against the entrance of body fluids into the pacer which, if not prevented, would seriously affect the electronic circuitry of the pacer.
SUMMARY or THE INVENTION The present inventioneliminates the loose hardware,
i.e., screws, 0 rings, etc., and the required suturing for sealing of the juncture of the catheter and pacer while at the same time providing a sealed but releaseable electrical and mechanical coupling at the juncture 1 of the catheter and pacer.
Briefly, the present invention provides an electrode system for efiecting the electrical connection between an electro-medical device, i.e., a pacer, and a patient. The electrode system includes an electrical conductor having proximal and distal ends. The distal end of the conductor is adapted for contact with a body organ of the patient. Socket means are provided which include pin means. The socket means is constructed and arranged to form an electrical output terminal of the electro-medical device. Finally, plug means are provided. The plug means is disposed. on the proximal end of the electrical conductor and comprises an electrical connector and a compressible resilient means. The electrical connector is secured to the proximal end of the electrical conductor and has coupling means cooperable with the pin means of the socket means to effect a releasable electrical and mechanical coupling between the socket means and the plug means. The compressible resilient means partially extends over the electrical connector and has portions thereof engageable with coooperating portions of the electro-medical device. The compressible resilient means provides a locking biasing force between the coupling means of the electrical connector and the pin means of the socket means when the plug means and the socket means are coupled.
Other features and advantages of the invention will appear in the ensuing description of the preferred embodiment when taken together with the accompanying drawings which form a part of this specification.
DESCRIPTION OF THE DRAWINGS FIG. 1 is a view partially in section and partially in elevation illustrating the electrode system in accordance with the invention in assembled relation with a pacer;
FIG. 2 is a side elevational view of the electrical connector in accordance with the invention;
FIG. 3 is a view taken along the line III-III of FIG.
FIG. 4 is a longitudinal sectional view of the electrical connector of FIG. 2;
FIG. 5 is top elevational view of the socket in accordance with the invnetion;
FIG. 6 is a longitudinal sectional view of the socket of FIG. 5;
FIG. 7 is a view taken along the lines VIIVII of FIG. 6; and
FIG. 8 is an enlargement of a portion of FIG. l'in the vicinity of the socket and plug means in accordance with the invention.
DESCRIPTION OF THE PREFERRED EMBODIMENTS Referring now to the drawings wherein like reference numerals refer to like parts throughout the several views, the electrical connector in accordance with the invention is shown generally at 10. The connector 10 is preferably fabricated from stainless steel such as 316 stainless steel. The connector 10 is provided with a generally cylindrical outer surface 12 and an axial passage 14. The right end of the connector 10, as viewed in FIG. 2, is provided with an enlarged, generally hexagonal surface 16 which projects radially outwardly from the surface 12. The left end of the connector, as viewed in FIG. 2, is provided with a coupling means in the form of oppositely disposed axial aligning grooves 18 and 20 and radial locking grooves 22 and 24 which are all provided in the outer surface 12 of the connector 10. The locking grooves 22 and 24 extend circumferentially in the same direction. Disposed within the axial passage 14 is a generally tubular member 26 which is secured therein as by soldering.
The socket means in accordance with the invention is shown generally at 30 in FIGS. -7. The socket 30 is also preferably fabricated from stainless steel such as 316 stainless steel. The socket 30 is provided with a generally hexagonal outer surface 32 and a cylindrical cavity 34. The outer surface 32 has a pair of openings 36 and 38 provided therein and press fitted within each opening is a coupling means or pin member 40 each of which extends into the cavity 34. A tapped hole 42 is also provided in the socket 30 into which a screw (not shown) may be screwed. The screw and tapped hole 42 serve as a means of making an electrical connection to the socket 30.
Referring now to FIGS. 1 and 8, there is illustrated the electrode system, in accordance with the invention, in assembled relation with an electro-medical device 43, i.e., a pacer. A catheter is shown generally at 44. The catheter 44 preferably comprises an electrical conductor 46 having proximal and distal ends, 48 and 50 respectively. The electrical conductor 46 may be fabricated of any suitable electrically conductive material but is preferably fabricated of Elgiloy and, it is preferably constructed in the form of a helix. The distal end 50 of the conductor 46 is provided with an electrode tip 52 which may be suitably secured to the distal end by conventional means. The electrode tip 52 is that portion of the catheter via which electrical impulses are applied to a body organ, i.e., the heart in the case of a pacer, as it is the portion of the pacer which is in electrical contact with the patient. The remaining portions of the electrical conductor 46 are insulated from contact with the patient. To this end, the conductor 46 is coated with an insulating sheath 54 which coats substantially the entire length of the conductor 46 with the exception of exposed electrode tip 52 and the proximal end 48 which is disposed within the tube 26 of connector 10. The insulating sheath 54 is enlarged at the left end, as viewed in FIG. 8 and partially extends over the electrical connector terminating short of the left end of the connector 10 in a frusto-conical surface 56. As will be more apparent hereinafter, the enlarged end of the catheter together with the connector 10 forms a plug means 55 by which a connection between the pacer per se and the conductor 46 is made. The sheath 54, while characterized as a coating, may be formed on the conductor 46 and connector 10 in any suitable manner, as for example, it may be molded onto these parts in a one step operation or in multiple molding operations. The sheath 54 is preferably comprised of a compressible resilient material, i.e., polysiloxane such as silicon rubber.
The socket 30 is molded into the encapsulation material 58 which encapsulates the pacer electronic circuitry and the batteries thereof (not shown), and forms an electrical output terminal for the pacer. An electrical connection is made between the pacer circuitry, and the socket 30 via the tapped hole 42, as described, prior to the encapsulation of the pacer circuitry.
As will be evident from this description, the pacer can be entirely encapsulated with a suitable body implantable material with the exception of the cavity 34 which is left exposed for later insertion of the connector 10. Accordingly, upon subsequent implantation of the pacer, there will be a minimum opportunity for body fluids to enter into the pacer via any screw holes or openings that would otherwise be required in the absence of the present invention.
The plug 55 and the socket 30 are simply and quickly brought in operative engagement by inserting the connector 10 of the plug 55 into the cavity 34 with the axial grooves 18 and 20 of the connector 10 being aligned with the pins 40. The plug 55 is forced into the cavity until the radial grooves 22 and 24 are in alignment with the pins 40 which will occur automatically when the extreme left end 60 of the connector abuts the back wall 62 of the cavity 34. This action of course, will impose a compressive force on the enlarged portion of the catheter, i.e., the plug 55, due to the frustoconical portion of the plug being engaged with the mating and cooperating portions of the pacer in the vicinity of the socket 30. When the radial grooves are aligned with the pins 40, the plug is partially rotated so that the pins 40 are located opposite the regressed portions 64 and 65 of the grooves 22 and 24. Again, this will automatically occur when the plug is rotated and the pins 40 abut the side walls of the radial grooves. The force being used to insert the plug 55 is then relaxed, and the pins will enter the regressed portions 64 and 65 of the radial grooves 22 and 24. The plug 55, or more specifically, the compressible resilient portion thereof, will then provide a locking biasing force between the side walls of the regressed portions of the radially grooves of the connector 10 and the pins 40.
To separate the plug 55 from the socket 30 requires that the plug 55 be depressed into the socket and a reverse rotation that effected from that utilized in joining of the plug and socket. The required dual combined motion, i.e., axial insertion of the plug into the socket and the rotation thereof to effect a mechanical coupling, prevents inadvertent disconnection. Further, at the time of joining of the plug and socket together, if the socket and plug are not properly joined, when pressure is released during assembly, the plug and socket will immediately separate. Accordingly, if they do not separate, the surgeon can be assured that there is in fact a mechanical coupling between the plug and socket.
Having thus described my invention, I claim:
1. An electrical connector assembly for providing an electrical connection between an electromedical device and an electrical conductor, the electrical conductor having proximal and distal ends with the distal end of the conductor being adapted for contact with a body organ of a patient, the electrical connector assembly comprising:
a. socket means constructed and arranged to form an electrical output terminal of the electromedical device, the socket means having a cylindrical cavity and pair of spaced, oppositely disposed pin means extending into the cavity; and
b. plug means, the plug means comprising i. an electrical connector secured to the proximal end of the conductor, the electrical connector being cylindrical and having coupling means cooperable with each of the pin means of the socket electrical connector, when the plug means and means to effect a electrical and positive locking 5 coupling between the socket means and the plug means, the coupling means of the electrical connector comprising a pair of oppositely disposed axial and a pair of oppositely disposed radial grooves all located in the cylindrical outer sur- 10 face of the connector, the radial grooves extending circumferentially in the same direction and v each having a regressed portion into which apin 3. ln apparatus so defined in claim 1 wherein the means f the Socket means is disposed when the compressible resilient means comprises a body compatplug means and the socket means are coupled; ible material' a d 4. In apparatus as defined in claim 3 wherein the ii. compressible resilient means partially extending compressible resilient means comprises silicon rubber.
over the electrical connector and having portions the socket means are coupled.
2. An electrical connector assembly as defined in claim 1 wherein the electrical connector has an axial passage therethrough and includes a tubular member disposed within the axial passage, the proximal end of the conductor being located within the tubular member and secured thereto.

Claims (4)

1. An electrical connector assembly for providing an electrical connection between an electromedical device and an electrical conductor, the electrical conductor having proximal and distal ends with the distal end of the conductor being adapted for contact with a body organ of a patient, the electrical connector assembly comprising: a. socket means constructed and arranged to form an electrical output terminal of the electromedical device, the socket means having a cylindrical cavity and pair of spaced, oppositely disposed pin means extending into the cavity; and b. plug means, the plug means comprising i. an electrical connector secured to the proximal end of the conductor, the electrical connector being cylindrical and having coupling means cooperable with each of the pin means of the socket means to effect a electrical and positive locking coupling between the socket means and the plug means, the coupling means of the electrical connector comprising a pair of oppositely disposed axial and a pair of oppositely disposed radial grooves all located in the cylindrical outer surface of the connector, the radial grooves extending circumferentially in the same direction and each having a regressed portion into which a pin means of the socket means is disposed when the plug means and the socket means are coupled; and ii. compressible resilient means partially extending over the electrical connector and having portions thereof engageable with cooperating portions of the electromedical device for providing a locking biasing force between the socket means and the electrical connector when the plug means and the socket means are coupled.
2. An electrical connector assembly as defined in claim 1 wherein the electrical connector has an axial passage therethrough and includes a tubular member disposed within the axial passage, the proxiMal end of the conductor being located within the tubular member and secured thereto.
3. In apparatus so defined in claim 1 wherein the compressible resilient means comprises a body compatible material.
4. In apparatus as defined in claim 3 wherein the compressible resilient means comprises silicon rubber.
US00192151A 1971-10-26 1971-10-26 Electromedical stimulator lead connector Expired - Lifetime US3757789A (en)

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Cited By (46)

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US3871382A (en) * 1973-02-15 1975-03-18 Pacesetter Syst Heart stimulator system for rapid implantation and removal with improved integrity
US3880169A (en) * 1974-01-02 1975-04-29 American Hospital Supply Corp Controlled entry pacemaker electrode for myocardial implantation
DE2652192A1 (en) * 1975-11-19 1977-06-02 Vitatron Medical Bv DEVICE FOR CONNECTING A PACEMAKER TO AN ELECTRODE
US4105037A (en) * 1977-05-06 1978-08-08 Biotronik Mess- Und Therapiegerate Gmbh & Co. Releasable electrical connecting means for the electrode terminal of an implantable artificial cardiac pacemaker
US4135518A (en) * 1976-05-21 1979-01-23 Medtronic, Inc. Body implantable lead and electrode
EP0002607A1 (en) * 1977-12-13 1979-06-27 Philip O.(deceased) legally represented by Bates H. Richard Littleford A device for making implants in the human body
FR2421626A1 (en) * 1978-02-01 1979-11-02 Anvar Multiple contact heart stimulating electrode - has coiled wire inside sleeve interrupted for intermediate contacts, terminating in spherical final contact
WO1980002231A1 (en) * 1979-04-24 1980-10-30 J Donachy Long-life flexible electrode lead
US4235246A (en) * 1979-02-05 1980-11-25 Arco Medical Products Company Epicardial heart lead and assembly and method for optimal fixation of same for cardiac pacing
US4310001A (en) * 1980-04-21 1982-01-12 Medtronic, Inc. Connector assembly for body implantable medical systems
US4357947A (en) * 1980-07-14 1982-11-09 Littleford Philip O Electrode and method for endocardial atrial pacing
US4461194A (en) * 1982-04-28 1984-07-24 Cardio-Pace Medical, Inc. Tool for sealing and attaching a lead to a body implantable device
US4601528A (en) * 1985-08-20 1986-07-22 Spier Martin I Hermetic self-locking electrical connector
EP0191238A1 (en) * 1985-01-16 1986-08-20 Intermedics, Inc. Pacemaker lead with enhanced sensitivity
US4614395A (en) * 1985-04-04 1986-09-30 Cordis Corporation Quick connector to medical electrical lead
US4895529A (en) * 1982-12-27 1990-01-23 Amp Incorporated Environmentally sealed connector
US4896671A (en) * 1988-08-01 1990-01-30 C. R. Bard, Inc. Catheter with contoured ablation electrode
US4934381A (en) * 1975-05-09 1990-06-19 Macgregor David C Porous carbon pacemaker electrode
US5036862A (en) * 1987-04-06 1991-08-06 Cordis Corporation Implantable, self-retaining lead
US5282841A (en) * 1989-11-20 1994-02-01 Siemens Pacesetter, Inc. Implantable stimulation device and method of making same
US5447533A (en) * 1992-09-03 1995-09-05 Pacesetter, Inc. Implantable stimulation lead having an advanceable therapeutic drug delivery system
US6039685A (en) * 1998-09-14 2000-03-21 St. Croix Medical, Inc. Ventable connector with seals
US6183305B1 (en) 1998-12-04 2001-02-06 Pacesetter, Inc. High strength connector design for passive fixation pacing lead
US20060054719A1 (en) * 2003-09-25 2006-03-16 3M Innovative Properties Company Security clip for spray gun connector
US7110819B1 (en) * 2002-03-05 2006-09-19 Pacesetter, Inc. Implantable medical device having a protected connection header
US20080262585A1 (en) * 2007-04-20 2008-10-23 Medtronic, Inc. Implantable medical electrical lead and connector assembly
US20090233491A1 (en) * 2008-03-12 2009-09-17 Boston Scientific Neuromodulation Corporation Low-profile connector for a neurostimulation lead
US20120261183A1 (en) * 2011-04-15 2012-10-18 Bernd Pretzlaff Lead feedthrough and electrical functional unit
US20140163659A1 (en) * 2002-04-15 2014-06-12 Neuropace, Inc. Reinforced sensing and stimulation leads and use in detection systems
US20150155648A1 (en) * 2013-12-04 2015-06-04 GiMer Medical Co., Ltd. Water resistant connector
US9956394B2 (en) 2015-09-10 2018-05-01 Boston Scientific Neuromodulation Corporation Connectors for electrical stimulation systems and methods of making and using
US10201713B2 (en) 2016-06-20 2019-02-12 Boston Scientific Neuromodulation Corporation Threaded connector assembly and methods of making and using the same
US10307602B2 (en) 2016-07-08 2019-06-04 Boston Scientific Neuromodulation Corporation Threaded connector assembly and methods of making and using the same
US10342983B2 (en) 2016-01-14 2019-07-09 Boston Scientific Neuromodulation Corporation Systems and methods for making and using connector contact arrays for electrical stimulation systems
US10543374B2 (en) 2016-09-30 2020-01-28 Boston Scientific Neuromodulation Corporation Connector assemblies with bending limiters for electrical stimulation systems and methods of making and using same
US10603499B2 (en) 2017-04-07 2020-03-31 Boston Scientific Neuromodulation Corporation Tapered implantable lead and connector interface and methods of making and using
US10639485B2 (en) 2017-09-15 2020-05-05 Boston Scientific Neuromodulation Corporation Actuatable lead connector for an operating room cable assembly and methods of making and using
US10814136B2 (en) 2017-02-28 2020-10-27 Boston Scientific Neuromodulation Corporation Toolless connector for latching stimulation leads and methods of making and using
US10905871B2 (en) 2017-01-27 2021-02-02 Boston Scientific Neuromodulation Corporation Lead assemblies with arrangements to confirm alignment between terminals and contacts
US10918873B2 (en) 2017-07-25 2021-02-16 Boston Scientific Neuromodulation Corporation Systems and methods for making and using an enhanced connector of an electrical stimulation system
US11045656B2 (en) 2017-09-15 2021-06-29 Boston Scientific Neuromodulation Corporation Biased lead connector for operating room cable assembly and methods of making and using
US11052259B2 (en) 2018-05-11 2021-07-06 Boston Scientific Neuromodulation Corporation Connector assembly for an electrical stimulation system and methods of making and using
US11103712B2 (en) 2018-01-16 2021-08-31 Boston Scientific Neuromodulation Corporation Connector assemblies with novel spacers for electrical stimulation systems and methods of making and using same
US11139603B2 (en) 2017-10-03 2021-10-05 Boston Scientific Neuromodulation Corporation Connectors with spring contacts for electrical stimulation systems and methods of making and using same
US11357992B2 (en) 2019-05-03 2022-06-14 Boston Scientific Neuromodulation Corporation Connector assembly for an electrical stimulation system and methods of making and using
US11951317B2 (en) 2021-06-09 2024-04-09 Boston Scientific Neuromodulation Corporation Biased lead connector for operating room cable assembly and methods of making and using

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Cited By (55)

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US3871382A (en) * 1973-02-15 1975-03-18 Pacesetter Syst Heart stimulator system for rapid implantation and removal with improved integrity
US3880169A (en) * 1974-01-02 1975-04-29 American Hospital Supply Corp Controlled entry pacemaker electrode for myocardial implantation
US4934381A (en) * 1975-05-09 1990-06-19 Macgregor David C Porous carbon pacemaker electrode
DE2652192A1 (en) * 1975-11-19 1977-06-02 Vitatron Medical Bv DEVICE FOR CONNECTING A PACEMAKER TO AN ELECTRODE
US4027678A (en) * 1975-11-19 1977-06-07 Vitatron Medical B.V. Pacing system with connector for connecting electrode to pacer
US4135518A (en) * 1976-05-21 1979-01-23 Medtronic, Inc. Body implantable lead and electrode
US4105037A (en) * 1977-05-06 1978-08-08 Biotronik Mess- Und Therapiegerate Gmbh & Co. Releasable electrical connecting means for the electrode terminal of an implantable artificial cardiac pacemaker
EP0002607A1 (en) * 1977-12-13 1979-06-27 Philip O.(deceased) legally represented by Bates H. Richard Littleford A device for making implants in the human body
FR2421626A1 (en) * 1978-02-01 1979-11-02 Anvar Multiple contact heart stimulating electrode - has coiled wire inside sleeve interrupted for intermediate contacts, terminating in spherical final contact
US4235246A (en) * 1979-02-05 1980-11-25 Arco Medical Products Company Epicardial heart lead and assembly and method for optimal fixation of same for cardiac pacing
WO1980002231A1 (en) * 1979-04-24 1980-10-30 J Donachy Long-life flexible electrode lead
US4310001A (en) * 1980-04-21 1982-01-12 Medtronic, Inc. Connector assembly for body implantable medical systems
US4357947A (en) * 1980-07-14 1982-11-09 Littleford Philip O Electrode and method for endocardial atrial pacing
US4461194A (en) * 1982-04-28 1984-07-24 Cardio-Pace Medical, Inc. Tool for sealing and attaching a lead to a body implantable device
US4895529A (en) * 1982-12-27 1990-01-23 Amp Incorporated Environmentally sealed connector
EP0191238A1 (en) * 1985-01-16 1986-08-20 Intermedics, Inc. Pacemaker lead with enhanced sensitivity
US4662382A (en) * 1985-01-16 1987-05-05 Intermedics, Inc. Pacemaker lead with enhanced sensitivity
US4614395A (en) * 1985-04-04 1986-09-30 Cordis Corporation Quick connector to medical electrical lead
US4601528A (en) * 1985-08-20 1986-07-22 Spier Martin I Hermetic self-locking electrical connector
US5036862A (en) * 1987-04-06 1991-08-06 Cordis Corporation Implantable, self-retaining lead
US4896671A (en) * 1988-08-01 1990-01-30 C. R. Bard, Inc. Catheter with contoured ablation electrode
EP0356009A1 (en) * 1988-08-01 1990-02-28 C.R. Bard, Inc. Catheter with contoured ablation electrode
US5282841A (en) * 1989-11-20 1994-02-01 Siemens Pacesetter, Inc. Implantable stimulation device and method of making same
US5447533A (en) * 1992-09-03 1995-09-05 Pacesetter, Inc. Implantable stimulation lead having an advanceable therapeutic drug delivery system
US6039685A (en) * 1998-09-14 2000-03-21 St. Croix Medical, Inc. Ventable connector with seals
US6183305B1 (en) 1998-12-04 2001-02-06 Pacesetter, Inc. High strength connector design for passive fixation pacing lead
US7110819B1 (en) * 2002-03-05 2006-09-19 Pacesetter, Inc. Implantable medical device having a protected connection header
US20140163659A1 (en) * 2002-04-15 2014-06-12 Neuropace, Inc. Reinforced sensing and stimulation leads and use in detection systems
US9162050B2 (en) * 2002-04-15 2015-10-20 Neuropace, Inc. Reinforced sensing and stimulation leads and use in detection systems
US20060054719A1 (en) * 2003-09-25 2006-03-16 3M Innovative Properties Company Security clip for spray gun connector
US20080262585A1 (en) * 2007-04-20 2008-10-23 Medtronic, Inc. Implantable medical electrical lead and connector assembly
WO2008130408A1 (en) * 2007-04-20 2008-10-30 Medtronic, Inc. Implantable medical electrical lead and connector assembly
US20090233491A1 (en) * 2008-03-12 2009-09-17 Boston Scientific Neuromodulation Corporation Low-profile connector for a neurostimulation lead
US7798864B2 (en) 2008-03-12 2010-09-21 Boston Scientific Neuromodulation Corporation Low-profile connector for a neurostimulation lead
US20120261183A1 (en) * 2011-04-15 2012-10-18 Bernd Pretzlaff Lead feedthrough and electrical functional unit
US8941020B2 (en) * 2011-04-15 2015-01-27 Litronik Entwicklungs Gmbh Lead feedthrough and electrical functional unit
US20150155648A1 (en) * 2013-12-04 2015-06-04 GiMer Medical Co., Ltd. Water resistant connector
US9130300B2 (en) * 2013-12-04 2015-09-08 GiMer Medical Co., Ltd. Water resistant connector
US9956394B2 (en) 2015-09-10 2018-05-01 Boston Scientific Neuromodulation Corporation Connectors for electrical stimulation systems and methods of making and using
US10342983B2 (en) 2016-01-14 2019-07-09 Boston Scientific Neuromodulation Corporation Systems and methods for making and using connector contact arrays for electrical stimulation systems
US10201713B2 (en) 2016-06-20 2019-02-12 Boston Scientific Neuromodulation Corporation Threaded connector assembly and methods of making and using the same
US10307602B2 (en) 2016-07-08 2019-06-04 Boston Scientific Neuromodulation Corporation Threaded connector assembly and methods of making and using the same
US10543374B2 (en) 2016-09-30 2020-01-28 Boston Scientific Neuromodulation Corporation Connector assemblies with bending limiters for electrical stimulation systems and methods of making and using same
US10905871B2 (en) 2017-01-27 2021-02-02 Boston Scientific Neuromodulation Corporation Lead assemblies with arrangements to confirm alignment between terminals and contacts
US10814136B2 (en) 2017-02-28 2020-10-27 Boston Scientific Neuromodulation Corporation Toolless connector for latching stimulation leads and methods of making and using
US10603499B2 (en) 2017-04-07 2020-03-31 Boston Scientific Neuromodulation Corporation Tapered implantable lead and connector interface and methods of making and using
US10918873B2 (en) 2017-07-25 2021-02-16 Boston Scientific Neuromodulation Corporation Systems and methods for making and using an enhanced connector of an electrical stimulation system
US10639485B2 (en) 2017-09-15 2020-05-05 Boston Scientific Neuromodulation Corporation Actuatable lead connector for an operating room cable assembly and methods of making and using
US11045656B2 (en) 2017-09-15 2021-06-29 Boston Scientific Neuromodulation Corporation Biased lead connector for operating room cable assembly and methods of making and using
US11139603B2 (en) 2017-10-03 2021-10-05 Boston Scientific Neuromodulation Corporation Connectors with spring contacts for electrical stimulation systems and methods of making and using same
US11103712B2 (en) 2018-01-16 2021-08-31 Boston Scientific Neuromodulation Corporation Connector assemblies with novel spacers for electrical stimulation systems and methods of making and using same
US11052259B2 (en) 2018-05-11 2021-07-06 Boston Scientific Neuromodulation Corporation Connector assembly for an electrical stimulation system and methods of making and using
US11357992B2 (en) 2019-05-03 2022-06-14 Boston Scientific Neuromodulation Corporation Connector assembly for an electrical stimulation system and methods of making and using
US11612755B2 (en) 2019-05-03 2023-03-28 Boston Scientific Neuromodulation Corporation Connector assembly for an electrical stimulation system and methods of making and using
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