US3788329A - Body implantable lead - Google Patents

Body implantable lead Download PDF

Info

Publication number
US3788329A
US3788329A US3788329DA US3788329A US 3788329 A US3788329 A US 3788329A US 3788329D A US3788329D A US 3788329DA US 3788329 A US3788329 A US 3788329A
Authority
US
Grant status
Grant
Patent type
Prior art keywords
means
lead
indifferent electrode
conductor
encapsulating
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
Inventor
H Friedman
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Medtronic Inc
Original Assignee
Medtronic Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Grant date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/02Details
    • A61N1/04Electrodes
    • A61N1/05Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/056Transvascular endocardial electrode systems
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/02Details
    • A61N1/04Electrodes
    • A61N1/05Electrodes for implantation or insertion into the body, e.g. heart electrode

Abstract

A flexible, body-implantable lead section which can be employed as an integral part of a monoplanar electrode system or alternatively as a separate means used to convert bipolar electrode system to a monopolar system. The lead section has at least one electrical conductor. The conductor is covered substantially over its entire length with an insulating material substantially inert to body fluids and tissue. The distal end of the conductor is adapted to be connected to an active electrode adapted to be located at a selected location inside the body. Indifferent electrode means are also provided. The indifferent electrode means are secured to at least a portion of the length along the surface of the inert material. In the preferred embodiment the indifferent electrode means is securely wrapped around at least a portion of the length of the inert material. This lead section with the indifferent electrode means can be employed with various configurations active electrodes for monitoring electrical activity and/or stimulating various types of tissue, including muscle and nerve tissue.

Description

United States Patent [191 Friedman Jan. 29, 1974 21 Appl. No.: 244,842

[52] US. Cl. 128/418, 128/419 P, 128/404 [51] Int. Cl A61n 1/04 [58] Field of Search.... 128/418, 419 P, 419 C, 417,

128/416, 410, 411, DIG. 4, 2.1 E, 2.06 E, 404

[56] References Cited UNITED STATES PATENTS 2,583,853 l/l952 Kazdin 128/404 3,249,103 5/1966 Woodhouse l28/2.1 E 3,253,595 5/1966 Murphy et a1. 128/418 3,416,533 12/1968 Fisher et a1. 128/404 3,421,511 l/l969 Schwartz et al. 128/418 3,472,234 10/1969 Tachick 128/418 3,478,746 11/1969 Greatbatch 128/419 P 3,485,247 12/1969 Ackerman 128/419 P 3,580,242 5/1971 La Croix.. 128/D1G. 4 3,596,662 8/1971 Bolduc 128/418 3,650,276 3/1972 Burghele 128/418 X 3,654,933 4/1972 Hagfors 128/418 3,664,347 5/1972 l-larmjanz 128/419 PX OTHER PUBLICATIONS Electrode Fixation Using a Plastic Adhesive, Methyl- 2-Cyanoacrylate, Electroencephalography and Clinical Neurophysiology, 1964, Vol. 17, p. 696-697.

Primary Examiner-Richard A. Gaudet Assistant Examiner-Lee S. Cohen Attorney, Agent, or Firmlrving S. Rappaport; Lew Schwartz; Wayne Sivertson [5 7] ABSTRACT A flexible, body-implantable lead section which can be employed as an integral part of a monoplanar electrode system or alternatively as a separate means used to convert bipolar electrode system to a monopolar system. The lead section has at least one electrical conductor. The conductor is covered substantially over its entire length with an insulating material substantially inert to body fluids and tissue. The distal end of the conductor is adapted to be connectedto an active electrode adapted to be located at a selected location inside the body. Indifferent electrode means are also provided. The indifferent electrode means are secured to at least a portion of the length along the sur- 13 Claims, 4 Drawing Figures PATENTED 3.7884329 sum 1 or 4 TO ACTIVE ELECTRODE FIG. I

ELECTRICAL ENERGY OR MONITORING EQUIPMENT Lu 0 05 D O (I) PATENTEB JAN 2 9 I974- sum 3 or 4 Pmimanme 3.788.329

sum u or 4 FIG. 4

BODY IMPLANTABLE LEAD BACKGROUND OF THE INVENTION In the field of implantable electromedical devices, and in particular, in pulse generators used for muscle and nerve stimulation, the leads used to transmit the stimulating pulse from the pulse generator to the selected portion of the body to be stimulated may employ monopolar or bipolar electrode configurations. In a bipolar electrode configuration the electrical stimulating impulse occurs between a pair of fairly closely spaced active electrodes, both located generally near the distal end of the lead. In a monopolar electrode configuration, often used with body implantable pulse generators, there is a single active electrode near the distal end of the lead. An indifferent electrode, often in the form ofa relatively large, flat, metal plate, is located on the exterior of the pulse generator. The electrical impulses in such a monopolar system occur between the single electrode at the distal end of the lead and the plate on the outer surface of the pulse generator. In these systems a bipolar lead must be used with a pulse generator designed to operate with a bipolar lead and a monopolar lead must be used with a pulse generator having the plate and designed to operate with a monopolar lead. Therefore, it is difficult to interchange monopolar and bipolar systems without changing both the pulse generator and the corresponding lead.

The present invention overcomes the above cited shortcomings of prior art systems by providing a lead of monopolar construction which may be employed with a pulse generator designed to operate with a bipolar lead so as to form a monopolar system. The lead of the present invention eliminates the need for employing the plate on the outer surface of a body implantable monopolar pulse generator and permits a bipolar pulse generator to be easily converted to a monopolar operating system. By eliminating the indifferent plate, the problems currently associated with bonding the plate to the implantable pulse generators expoxy covering and of welding or bonding leads to the plate are avoided. Also, with the use of the lead of the present invention the problem of muscle stimulation occurring at the edges of the plate are substantially eliminated. A sufficient length ofindifferent electrode in accordance with the present invention, properly arranged and exposed, insures against a high energy density which could otherwise cause local tissue stimulation. The present invention provides a monopolar electrode lead which can be used with single or multi-channel nerve stimulators. The lead configuration of the present invention can also be employed for physiological monitoring, such as, for example, monitoring the electrical activity of the heart such as used in cardiac pacemaking, as well as various types of tissue stimulation.

SUMMARY OF THE INVENTION The above features, advantages and objects of the present invention. as well as others, are accomplished by providing a flexible body-implantable lead section comprising: at least one electrical conductor; and adapted to be connected at its distal end to an active electrode, which is adapted to be located at a selected location inside the body, the conductor being substantially covered over its length with an insulating material inert to body fluids and tissue; and indifferent electrode means, the indifferent electrode means being secured to at least a portion of the length along the surface of the inert material.

The lead section of the present invention can be employed in various leads with different, active electrode configurations. This is accomplished by constructing the lead section as an integral part of a flexible bodyimplantable lead comprising: at least one electrical conductor, the conductor being substantially covered over its length with an insulating material substantially inert to body fluids and tissue; active electrode means electrically connected at substantially the distal end of the electrical conductor, the electrode means adapted to be located at a selected location inside the body; and indifferent electrode means, the indifferent electrode means being secured to at least a portion of the length along the surface of the inert material.

Other features, advantages and objects of the present invention will hereinafter become more fully apparent from the following description of the drawings, which illustrate several embodiments of the present invention.

BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a diagram of a section of a lead in accordance with the present invention.

FIG. 2 shows a lead of the present invention for use as an endocardial lead with a monopolar pulse generator or for converting a bipolar pulse generator of a cardiac pacemaker system to a monopolar configuration.

FIG. 3 is a diagram of another embodiment of a lead in accordance with the present invention for use in a nerve stimulating system; and

FIG. 4 shows another embodiment of a lead in accordance with the present invention for use in a system for stimulating the dorsal column of the spine.

DESCRIPTION OF THE PREFERRED EMBODIMENTS Before describing the present invention in detail, the meaning of certain terminology used herein should be clearly understood. The terminology distal end is used in referring to that portion of the lead toward the end to which the active electrode is attached. The terminology proximal end is used in referring to that portion of the lead toward the end which is connected to the source of electrical energy or monitoring equipment. The term active electrode" as used herein generally refers to the electrode at which stimulation is desired to be achieved (most often of negative polarity) or the electrode at whose location electrical activity of tissue is to be monitored. The term indifferent elec trode" as used herein is intended to refer to that electrode which is common to a system or at system ground. For a tissue stimulation system the indifferent electrode will often be of positive electrical potential with respect to the active electrode.

FIG. 1 shows section 10 of a flexible lead which may be used with an electro-medical device for implantation in the body. Section 10 comprises an electrical conductor 12 having a distal end 14, which is adapted to connect to an active electrode which may be used to supply electrical energy to or monitor electrical activity at a selected portion of the body. A proximal end 16 is provided, which is adapted to be connected to a source of electrical energy or monitoring equipment. Electrical conductor 12 is embedded in an insulating covering material 18 which is substantially inert to body fluids and tissue, such as, for example, silicone rubber. Another electrical conductor 20, which serves as an indifferent electrode, is partially embedded in the outer surface of material 18 to hold conductor 20 in fixed position. Conductor 20 is wrapped in a helical configuration around material 18. The proximal end 22 of conductor 20 is adapted to be connected to a source of electrical energy or monitoring equipment. The distal end 24 of conductor 20 is terminated by projecting inside material 18 at a point 26 on the outer surface of material 18.

Conductors l2 and 20 are made ofa conductive material which is substantially inert to body fluids and tissue, such as, for example, platinum or platinum-iridium alloy. Conductors 12 and 20 may, for example, be made in a configuration and of a construction the same as that of the lead described in U.S. Pat. No. 3,572,344. This lead construction has excellent mechanical strength and flex characteristics and at the same time is an excellent electrical conductor.

Section may, for example, be used in converting a bipolar lead and pulse generator to a monopolar system without having to replace the lead or the pulse generator. Both ends of section 10 may be titted with appropriate male and female adapters (not shown), to permit section 10 to be electrically connected distally to a bipolar lead and proximally to an electrical energy source or monitoring equipment. Conductor 12 of section 10 is adapted to be connected at its distal end 14 to a conductor connected to the active electrode of a bipolar lead and specifically, if for tissue stimulation, at its proximal end 16 to a source of electrical energy, generally to the negative polarity signal. Conductor serves as an indifferent electrode and is adapted to be connected at its proximal end 22 to a common or ground potential. Conductor 20 should be of sufficient length and surface area and the helical turns adequately spaced from one another such as to insure sufficiently low energy density to substantially eliminate local tissue stimulation. Conductor 20 should have the same properties so as to avoid picking up local tissue electrical activity when adapted for use in certain monitoring systems.

FIG. 2 shows a flexible, body-implantable endocardial lead 30 for use with a bipolar pulse generator or for converting a bipolar generator to a monopolar system. Lead 30 has an electrical conductor 32 which is embedded in an insulating convering material 34 which is substantially inert to body fluids and tissue, such as, for example, silicone rubber. Conductor 32 projects through the outer surface of material 34 at point 36. From point 36, conductor 32 is closely wrapped for several turns in a helical configuration around'material 34 to form the active electrode of monopolar lead 30. The wrapped turns of conductor 32 are partially embedded in the outer surface of material 34 so as to maintain the turns in fixed position. Distal end 38 of conductor 32 is terminated by projecting into material 34 at point 40. Proximal end 42 of conductor 32 is connected to a connector pin 44 which projects beyond material 34 and is adaptedto be connected to a source of electrical energy. such as, for example, a pulse generator. The active electrode formed near the distal end of conductor 32 may si-multaneously'serve to monitor electrical activity of the heart in ademand pacemaker.

Also embedded in material 34 is a closely wound helical coil spring 46 which defines a lumen therein. Spring 46 is open at its proximal end 48 so as to permit a stylet (not shown) to be inserted therein so as to provide lead 30 with sufficient rigidity to be inserted into and guided through a body vessel to a desired location inside the body. Spring 46 is closed at its distal end 50 to limit the distance of insertion of the stylet.

Lead 30 also is provided with another electrical conductor 52 having a proximal portion 54 which is embedded in material 34 and is connected to a connector pin 56. Conductor 52 projects through the outer surface of material 34 at a point 58 and is wrapped for several spaced turns in a helical configuration around material 34. The wrapped turns of conductor 52 are partially embedded in the outer surface of material 34 so as to maintain them in fixed position. Distal end 60 of conductor 52 is terminated by projecting inside material 34 at a point 62. The wrapped turns of conductor 52 may, for example, extend for approximately 2% inches or so along the length of material 34 and the turns are approximately three-eighths inch between centers. The exposed length and surface area and the spacing between the helical turns of conductor 52 should be determined according to the same criteria as described regarding the characteristics of conductor 20 in FIG. 1.

Conductors 32 and 52 are made of materials which are substantially inert to body fluids and tissue, such as, for example, platinum or a platinum-iridium alloy. Pins 44 and 56 and spring 46 may, for example, be made of stainless steel alloys. The construction and configuration of conductors 32 and 52 may be that of the lead described in US. Pat. No. 3,572,344.

FIG. 3 shows a flexible, body-implantable lead for use in a multi-channel nerve stimulator. Lead 70 has a pair of electrical conductors 72 and 74 spaced from one another and embedded in an insulating covering material 76 which is substantially inert to body fluids and tissue, such as, for example, silicone rubber. Distal ends 78 and 80 of conductors 72 and 74 are terminated in such a way as to form monopolar electrodes 82 and 84 respectively. Electrodes 82 and 84 are partially exposed and partially embedded in base portions 86 and 88 respectively which are formed integrally with material 76. Electrodes 82 and 84 and corresponding base portions 86 and 88 are adapted to be wrapped around the nerves which are to be stimulated as, for example, the carotid sinus nerves. Conductors 72 and 74 are connected to connector pins 90 and 92 respectively which are adapted to be connected to a bodyimplantable receiver (not shown). The receiver is designed to receive stimulating pulses from an RF coupled external transmitter and apply these pulses to the nerves through electrodes 82 and 84.

Lead 70 is provided with a third electrical conductor 94 which is embedded in material 76 at its proximal end 96 where it is connected to a connector pin 98. Conductor 94 projects through the outer surface of material 76 at point 100 and is wrapped for several turns around material 76 in a helical configuration similar to that of conductor 52 in FIG. 2. The spaced turns of conductor 94 are partially embedded in material 76 so as to'maintain them in fixed position. Material 76 has a somewhat greater cross section near its proximal end in the section where the spaced turns of conductor 94 are partially embedded. The distal end 102 of conductor 94 terminates in material 76 by projecting through the outer surface at point 104.

In lead 70, electrodes 82 and 84 form the active electrodes and are connected via conductors 72 and 74 and pins 90 and 92 respectively to the implantable receiver. The spaced turns of conductor 94 form an indifferent electrode which is connected via pin 98 to either an electrical common or ground. The exposed length and surface area and the spacing between the turns of conductor 94 should be determined according to the same criteria as described regarding the characteristics of conductor in FIG. 1.

FIG. 4 shows a flexible, body-implantable lead 110 incorporating the present invention and particularly designed for stimulating the dorsal column of the spine. Lead 110 has a conductor 112 embedded in an insulating covering material 114 which is substantially inert to body fluids and tissue, such as, for example, silicone rubber. Conductor 112 is terminated at its distal end in a spiral configuration to form an active electrode 116 which is partially embedded in a base portion 118 which is formed integrally with covering material 114. Material 114 is shown to intersect the base portion 118 at some angle other than 90 because such a configuration has been found easier to work with in attaching the active electrode 116 formed by the spiral configuration to the dorsal column. Spiral configuration 116 is partially embedded in base portion 118 to maintain the spiral configuration in fixed position. Although configuration 116 is shown to be a spiral, other configurations for the active electrode are possible. Proximal end 120 of conductor 112 is connected to a connector pin 122 which is adapted to be connected to a body implantable receiver (not shown) which may receive pulses which are RF coupled from an external transmitter. Active electrode 116 is generally connected to a negative polarity signal through conductor 112 and pin 122.

A second conductor 124 is provided with its proximal end 126 embedded in material 114 and connected to a connector pin 128 which is adapted to be connected to the receiver (not shown). Proximal end 126 of conductor 124 projects through the outer surface of material 114 at point 130 and is wrapped in a helical configuration for several spaced turns around material 114. The exposed length and surface area and the spacing between the turns of conductor 124 should be determined according to the same criteria as described regarding the characteristics of conductor 20 in F 1G. 1. The turns of conductor 124 are partially embedded in the outer surface of material 114 to maintain the turns in fixed position. The distal end 132 of conductor 124 is terminated by projecting into material 114 at point 134. Conductor 124 forms an indifferent electrode which is generally connected via pin 128 to ground potential which commonly is of positive polarity.

Conductors 112 and 124 may be made in the structure and configuration of the lead described in US. Pat. No. 3,572,344. Conductors 112 and 124 and pins 122 and 128 are made of a material substantially inert to body fluids and tissue. Although electrode 116 has been shown and described as having a spiral configuration, other configurations for the active electrode could be employed.

Also, it should be understood that although the four embodiments shown have the indifferent electrode wrapped around the covering material, the indifferent electrode could be partially embedded in the outer surface of the covering material in any desired configuration. Instead of having the indifferent electrode wrapped around the inert material containing one or more electrical conductors, the inert material could be securely wrapped around the indifferent electrode. In a broad sense the indifferent electrode and at least a portion of the length of the inert material are securely wrapped relative to one another. It should also be understood that although the preferred embodiments of the invention show the indifferent electrodes securely wrapped around the inert material in a helical configuration, any other means of securing the indifferent electrode to the surface of the inert material would be satisfactory. Although the indifferent electrode is shown located near the proximal end of the lead, it could be secured anywhere along the length of the lead.

FIGS. 1-4 show several embodiments of bodyimplantable leads which can be used in various applications. it should be understood, of course, that the foregoing disclosure relates to only a few configurations which the present invention may take and that numerous modifications may be made therein without departing from the spirit and scope of the invention as set forth in the appended claims.

I claim:

1. A body implantable lead comprising:

an elongated flexible body member of an insulating material which is generally inert to body fluids and tissues;

at least one active electrode means attached to said flexible body member towards one end thereof;

a lead section of generally uniform cross-section formed of a flexible insulating member which is generally inert to body fluids and tissue, said lead section being attached to and extending from another end of said flexible body member;

first electrical conductor means for connection to an external device encapsulated by said flexible body member and said lead section and extending generally through their entire length into electrical contact with said active electrode; and

indifferent electrode conductor means for connection to an external device encapsulated by a portion of said lead section and electrically insulated from said first electrical conductor means, said indifferent conductor means projecting through the surface of said lead section and being wrapped at least once around the periphery of said lead section while being partially embedded within its surface such that said indifferent electrode conductor means is electrically exposed only at the location of said wrapping and is so exposed around the entire periphery of said lead section, the terminus of said indifferent electrode conductor means being totally embedded within said lead section.

2. The lead of claim 1 wherein the exposed portion of said indifferent electrode conductor means has sufficient area to insure an energy density sufficiently low to substantially eliminate local tissue stimulation.

3. The lead of claim 2 wherein said indifferent electrode conductor means is wrapped and exposed for more than one turn around the periphery of said lead section.

4. A lead as set forth in claim 3 further including means for inserting in and guiding said lead through a selected body vessel.

5. A lead as set forth in claim 3 wherein said last mentioned means includes a coil spring embedded in the material and defining a lumentherein, said spring being adapted to receive a stylet to provide said lead with sufficient rigidity to facilitate its insertion and guidance through the selected body vessel.

6. A lead as set forth in claim 3 wherein said active electrode means is configured to provide electrical energy to cardiac tissue.

7. A lead as set forth in claim 3 wherein said active electrode means is configured to provide electrical energy to selected nerve tissue.

8. In combination with a body implantable lead, an indifferent electrode forming lead section which comprises:

encapsulating means of a flexible insulating material which is generally inert to body fluids and tissue; and

indifferent electrode conductor means for connection to an external device projecting through the surface of said encapsulating means and being wrapped at least once around the periphery of said encapsulating means while being at least partially embedded within its surface such that the indifferent electrode conductor means is electrically exposed only at the location of said wrapping and is so exposed around the entire periphery of said encapsulating material, the terminus of said indifferent electrode conductor means is totally embedded within said encapsulating means.

9. The combination of claim 8 wherein, the surface .area of the exposed portion of said indifferent electrode conductor means has sufficient area to insure an energy density sufficiently low to substantially eliminate local tissue stimulation.

10. The combination of claim 9 wherein said indifferent electrode conductor means is exposed and wrapped for more than one turn around the periphery of said encapsulating means.

11. A flexible, body implantable lead section for converting a bipolar electrode system to a monopolar sys tem comprising:

encapsulating means of a flexible insulating material which is generally inert to body fluids and tissues, said encapsulating means having a generally uniform cross section; and

indifferent electrode means for connection to an external device projecting through the surface of said encapsulating means and being wrapped at least once around the periphery of said encapsulating means while being at least partially embedded within its surface such that the indifferent electrode means is electrically exposed only at the location of said wrapping and is so exposed around the entire periphery of said encapsulating material, the terminus of said indifferent electrode means being totally embedded within said encapsulating means.

12. The lead section of claim 11 wherein the exposed portion of said indifferent electrode means has a surface area sufficient to insure an energy density sufficiently low to substantially eliminate local tissue stimulation.

13. The lead section of claim 12 wherein the exposed portion of said indifferent electrode means is wrapped more than one turn around the periphery of said encapsulating means.

Claims (13)

1. A body implantable lead comprising: an elongated flexible body member of an insulating material which is generally inert to body fluids and tissues; at least one active electrode means attached to said flexible body member towards one end thereof; a lead section of generally uniform cross-section formed of a flexible insulating member which is generally inert to body fluids and tissue, said lead section being attached to and extending from another end of said flexible body member; first electrical conductor means for connection to an external device encapsulated by said flexible body member and said lead section and extending generally through their entire length into electrical contact with said active electrode; and indifferent electrode conductor means for connection to an external device encapsulated by a portion of said lead section and electrically insulated from said first electrical conductor means, said indifferent conductor means projecting through the surface of said lead section and being wrapped at least once around the periphery of said lead section while being partially embedded within its surface such that said indifferent electrode conductor means is electrically exposed only at the location of said wrapping and is so exposed around the entire periphery of said lead section, the terminus of said indifferent electrode conductor means being totally embedded within said lead section.
2. The lead of claim 1 wherein the exposed portion of said indifferent electrode conductor means has sufficient area to insure an energy density sufficiently low to substantially eliminate local tissue stimulation.
3. The lead of claim 2 wherein said indifferent electrode conductor means is wrapped and exposed for more than one turn around the periphery of said lead section.
4. A lead as set forth in claim 3 further including means for inserting in and guiding said lead through a selected body vessel.
5. A lead as set forth in claim 3 wherein said last mentioned means includes a coil spring embedded in the material and defining a lumen therein, said spring being adapted to receive a stylet to provide said lead with sufficient rigidity to facilitate its insertion and guidance through the selected body vessel.
6. A lead as set forth in claim 3 wherein said active electrode means is configured to provide electrical energy to cardiac tissue.
7. A lead as set forth in claim 3 wherein said active electrode means is configured to provide electrical energy to selected nerve tissue.
8. In combination with a body implantable lead, an indifferent electrode forming lead section which comprises: encapsulating means of a flexible insulating material which is generally inert to body fluids and tissue; and indifferent electrode conductor means for connection to an external device projecting through the surface of said encapsulating means and being wrapped at least once around the periphery of said encapsulating means while being at least partially embedded within its surface such that the indifferent electrode conductor means is electrically exposed only at the location of said wrapping and is so exposed around the entire periphery of said encapsulating material, the terminus of said indifferent Electrode conductor means is totally embedded within said encapsulating means.
9. The combination of claim 8 wherein the surface area of the exposed portion of said indifferent electrode conductor means has sufficient area to insure an energy density sufficiently low to substantially eliminate local tissue stimulation.
10. The combination of claim 9 wherein said indifferent electrode conductor means is exposed and wrapped for more than one turn around the periphery of said encapsulating means.
11. A flexible, body implantable lead section for converting a bipolar electrode system to a monopolar system comprising: encapsulating means of a flexible insulating material which is generally inert to body fluids and tissues, said encapsulating means having a generally uniform cross section; and indifferent electrode means for connection to an external device projecting through the surface of said encapsulating means and being wrapped at least once around the periphery of said encapsulating means while being at least partially embedded within its surface such that the indifferent electrode means is electrically exposed only at the location of said wrapping and is so exposed around the entire periphery of said encapsulating material, the terminus of said indifferent electrode means being totally embedded within said encapsulating means.
12. The lead section of claim 11 wherein the exposed portion of said indifferent electrode means has a surface area sufficient to insure an energy density sufficiently low to substantially eliminate local tissue stimulation.
13. The lead section of claim 12 wherein the exposed portion of said indifferent electrode means is wrapped more than one turn around the periphery of said encapsulating means.
US3788329A 1972-04-17 1972-04-17 Body implantable lead Expired - Lifetime US3788329A (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US24484272 true 1972-04-17 1972-04-17

Publications (1)

Publication Number Publication Date
US3788329A true US3788329A (en) 1974-01-29

Family

ID=22924339

Family Applications (1)

Application Number Title Priority Date Filing Date
US3788329A Expired - Lifetime US3788329A (en) 1972-04-17 1972-04-17 Body implantable lead

Country Status (7)

Country Link
US (1) US3788329A (en)
JP (1) JPS4920984A (en)
CA (1) CA995764A (en)
DE (1) DE2319500A1 (en)
FR (1) FR2180908B1 (en)
GB (1) GB1423262A (en)
NL (1) NL7305358A (en)

Cited By (69)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3893461A (en) * 1972-11-28 1975-07-08 Thomas A Preston Pacing apparatus and method utilizing improved catheter
US3911928A (en) * 1973-04-14 1975-10-14 Hans Lagergren Endocardial electrode
US3915174A (en) * 1972-11-28 1975-10-28 Thomas A Preston Pacing apparatus and improved catheter
US3935864A (en) * 1973-07-04 1976-02-03 Hans Lagergren Endocardial electrode
US3964473A (en) * 1972-09-21 1976-06-22 Telectronics Pty. Limited Bone prosthesis
US4006748A (en) * 1976-01-29 1977-02-08 Pacestter Systems, Inc. Implantable unipolar pacemaker with improved outer electrode plate
US4010755A (en) * 1972-11-28 1977-03-08 Preston Thomas A Unipolar pacing catheter with plural distal electrodes
US4044774A (en) * 1976-02-23 1977-08-30 Medtronic, Inc. Percutaneously inserted spinal cord stimulation lead
US4125116A (en) * 1977-02-14 1978-11-14 The Johns Hopkins University Human tissue stimulation electrode structure
US4149542A (en) * 1976-03-26 1979-04-17 Siemens Aktiengesellschaft Endocardial electrode
US4161952A (en) * 1977-11-01 1979-07-24 Mieczyslaw Mirowski Wound wire catheter cardioverting electrode
US4261372A (en) * 1977-11-22 1981-04-14 Hansen Carl C Electrode for implantation into cochlea
US4381013A (en) * 1981-03-19 1983-04-26 Medtronic, Inc. "J" Stylet wire
US4444195A (en) * 1981-11-02 1984-04-24 Cordis Corporation Cardiac lead having multiple ring electrodes
US4445511A (en) * 1982-06-24 1984-05-01 Telectronics Pty. Ltd. Pacer electrode connector assembly
EP0109178A2 (en) * 1982-10-14 1984-05-23 Baxter International Inc. Flexible tip cardiac pacing catheter
US4481953A (en) * 1981-11-12 1984-11-13 Cordis Corporation Endocardial lead having helically wound ribbon electrode
USRE32204E (en) * 1980-06-09 1986-07-15 Mansfield Scientific, Inc. Electrode assembly for temporary pacing and heart measurements
USRE32227E (en) * 1981-03-19 1986-08-19 Medtronic, Inc. "J" Stylet wire
US4759378A (en) * 1982-10-14 1988-07-26 American Hospital Supply Corporation Flexible tip cardiac pacing catheter
US4817634A (en) * 1987-06-18 1989-04-04 Medtronic, Inc. Epicardial patch electrode
US4819661A (en) * 1987-10-26 1989-04-11 Cardiac Pacemakers, Inc. Positive fixation cardiac electrode with drug elution capabilities
US4860446A (en) * 1988-02-16 1989-08-29 Medtronic, Inc. Medical electrical lead and method of manufacture
US4938231A (en) * 1985-10-22 1990-07-03 Telectronics N.V. Defibrillator electrode
US4947866A (en) * 1988-02-16 1990-08-14 Medtronic, Inc. Medical electrical lead
US4971070A (en) * 1987-06-18 1990-11-20 Medtronic, Inc. Epicardial patch electrode
US5040544A (en) * 1988-02-16 1991-08-20 Medtronic, Inc. Medical electrical lead and method of manufacture
US5231996A (en) * 1992-01-28 1993-08-03 Medtronic, Inc. Removable endocardial lead
US5324321A (en) * 1992-12-22 1994-06-28 Medtronic, Inc. Medical electrical lead having sigmoidal conductors and non-circular lumens
US5439485A (en) * 1993-09-24 1995-08-08 Ventritex, Inc. Flexible defibrillation electrode of improved construction
US5531779A (en) * 1992-10-01 1996-07-02 Cardiac Pacemakers, Inc. Stent-type defibrillation electrode structures
US5674272A (en) * 1995-06-05 1997-10-07 Ventritex, Inc. Crush resistant implantable lead
US5755757A (en) * 1996-05-01 1998-05-26 Teague; Thomas Wade Apparatus for localized neutralization of poison
WO1998034678A1 (en) 1997-02-10 1998-08-13 Medtronic, Inc. Coiled wire conductor insulation for biomedical lead
US5902331A (en) * 1998-03-10 1999-05-11 Medtronic, Inc. Arrangement for implanting an endocardial cardiac lead
EP0927561A3 (en) * 1997-12-29 2000-03-08 BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin Defibrillation electrode device
US6132456A (en) * 1998-03-10 2000-10-17 Medtronic, Inc. Arrangement for implanting an endocardial cardiac lead
US6161029A (en) * 1999-03-08 2000-12-12 Medtronic, Inc. Apparatus and method for fixing electrodes in a blood vessel
WO2001023034A1 (en) * 1999-09-24 2001-04-05 Cardiac Pacemakers, Inc. High impedance electrode assembly
US6253111B1 (en) 1998-03-30 2001-06-26 Pacesetter, Inc. Multi-conductor lead
US20030093136A1 (en) * 2001-11-09 2003-05-15 Osypka Thomas P. Cardiac lead with steroid eluting ring
US6615085B1 (en) * 1998-10-26 2003-09-02 Birinder R. Boveja Apparatus for adjunct (add-on) therapy of Dementia and Alzheimer's disease utilizing an implantable lead and an external stimulator
WO2004060440A2 (en) 2002-12-16 2004-07-22 Medtronic, Inc. Bilumen guide catheters for addessing cardiac sites
US20050070972A1 (en) * 2003-09-26 2005-03-31 Wahlstrand Carl D. Energy shunt for producing an MRI-safe implantable medical device
US20050222647A1 (en) * 2004-03-30 2005-10-06 Wahlstrand Carl D Lead electrode for use in an MRI-safe implantable medical device
US20050222642A1 (en) * 2004-03-30 2005-10-06 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US20050222659A1 (en) * 2004-03-30 2005-10-06 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US20050222658A1 (en) * 2004-03-30 2005-10-06 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US20050222657A1 (en) * 2004-03-30 2005-10-06 Wahlstrand Carl D MRI-safe implantable lead
US20050222656A1 (en) * 2004-03-30 2005-10-06 Wahlstrand Carl D MRI-safe implantable medical device
WO2005102447A1 (en) * 2004-03-30 2005-11-03 Medtronic, Inc. Mri-safe implantable lead
US20060155345A1 (en) * 2005-01-07 2006-07-13 Williams Jeffrey M Implantable neuromodulation system and method
US20060200218A1 (en) * 2005-02-01 2006-09-07 Wahlstrand Carl D Extensible implantable medical lead
WO2006101616A1 (en) * 2005-03-23 2006-09-28 Arrow International, Inc. Multi-lumen catheter having external electrical leads
US20060247747A1 (en) * 2005-04-29 2006-11-02 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US20060253180A1 (en) * 2005-05-06 2006-11-09 Cardiac Pacemakers, Inc. Cable electrode assembly for a lead terminal and method therefor
US20060265038A1 (en) * 2005-05-19 2006-11-23 Cvrx, Inc. Implantable electrode assembly having reverse electrode configuration
US20080195187A1 (en) * 2007-02-14 2008-08-14 Bernard Li Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding
US20080195186A1 (en) * 2007-02-14 2008-08-14 Bernard Li Continuous conductive materials for electromagnetic shielding
US20080269863A1 (en) * 2007-04-25 2008-10-30 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US20090012591A1 (en) * 2007-07-05 2009-01-08 Advanced Bionics Corporation Lead with contacts formed by coiled conductor and methods of manufacture and use
EP2246092A1 (en) * 2009-04-29 2010-11-03 Biotronik CRM Patent AG Method for manufacturing an electrode cable
US20100304626A1 (en) * 2009-05-27 2010-12-02 Boston Scientific Neuromodulation Corporation Systems and methods for forming an end of an elongated member of an electrical stimulation system
US8027736B2 (en) 2005-04-29 2011-09-27 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US9186499B2 (en) 2009-04-30 2015-11-17 Medtronic, Inc. Grounding of a shield within an implantable medical lead
US9463317B2 (en) 2012-04-19 2016-10-11 Medtronic, Inc. Paired medical lead bodies with braided conductive shields having different physical parameter values
US9731119B2 (en) 2008-03-12 2017-08-15 Medtronic, Inc. System and method for implantable medical device lead shielding
US9993638B2 (en) 2013-12-14 2018-06-12 Medtronic, Inc. Devices, systems and methods to reduce coupling of a shield and a conductor within an implantable medical lead
US10035014B2 (en) 2010-04-27 2018-07-31 Medtronic, Inc. Steering an implantable medical lead via a rotational coupling to a stylet

Families Citing this family (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE2910749C2 (en) * 1979-03-19 1982-11-25 Dr. Eduard Fresenius, Chemisch-Pharmazeutische Industrie Kg, 6380 Bad Homburg, De
EP0022556A1 (en) * 1979-07-13 1981-01-21 Gerhard J. Prof. Dr. Müller Implantable electrical conductor, especially stimulation electrode conductor and/or electrode
US4289138A (en) * 1980-06-09 1981-09-15 Medical Testing Systems, Inc. Electrode assembly for temporary pacing and heart measurements
US4574807A (en) * 1984-03-02 1986-03-11 Carl Hewson Method and apparatus for pacing the heart employing external and internal electrodes
US4603705A (en) * 1984-05-04 1986-08-05 Mieczyslaw Mirowski Intravascular multiple electrode unitary catheter
DE3530269C2 (en) * 1985-08-22 1997-01-16 Biotronik Mess & Therapieg The implantable indifferent electrode for cardiac pacing
US4860769A (en) * 1987-11-12 1989-08-29 Thomas J. Fogarty Implantable defibrillation electrode
US4865037A (en) * 1987-11-13 1989-09-12 Thomas J. Fogarty Method for implanting automatic implantable defibrillator
US5052407A (en) * 1988-04-14 1991-10-01 Mieczyslaw Mirowski Cardiac defibrillation/cardioversion spiral patch electrode
US5324328A (en) * 1992-08-05 1994-06-28 Siemens Pacesetter, Inc. Conductor for a defibrillator patch lead
US5328442A (en) * 1992-11-20 1994-07-12 Siemens Pacesetter, Inc. System and method for stimulating a heart having undergone cardiac myoplasty using a single-chamber pacemaker
US9468755B2 (en) * 2009-09-30 2016-10-18 Respicardia, Inc. Medical lead with preformed bias

Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2583853A (en) * 1950-08-08 1952-01-29 Frank W Kazdin Diathermy electrode
US3249103A (en) * 1963-01-21 1966-05-03 Charles F Woodhouse Method and apparatus for measuring bioelectronic parameters
US3253595A (en) * 1963-08-07 1966-05-31 Cordis Corp Cardiac pacer electrode system
US3416533A (en) * 1966-05-20 1968-12-17 Gen Electric Conductive catheter
US3421511A (en) * 1965-12-10 1969-01-14 Medtronic Inc Implantable electrode for nerve stimulation
US3472234A (en) * 1967-08-15 1969-10-14 Gen Electric Body organ electrode
US3478746A (en) * 1965-05-12 1969-11-18 Medtronic Inc Cardiac implantable demand pacemaker
US3485247A (en) * 1965-08-16 1969-12-23 Electro Catheter Corp Cardiac catheterization apparatus and method
US3580242A (en) * 1968-04-01 1971-05-25 George E La Croix Fetal scalp electrode unit
US3596662A (en) * 1968-09-04 1971-08-03 Medtronic Inc Electrode for cardiac stimulator
US3650276A (en) * 1969-03-26 1972-03-21 Inst Demedicina Si Farmacie Method and apparatus, including a flexible electrode, for the electric neurostimulation of the neurogenic bladder
US3654933A (en) * 1968-11-18 1972-04-11 Medtronic Inc Implatable electrode
US3664347A (en) * 1968-07-27 1972-05-23 Dietrich Harmjanz Electric heart stimulation method and electrode

Patent Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2583853A (en) * 1950-08-08 1952-01-29 Frank W Kazdin Diathermy electrode
US3249103A (en) * 1963-01-21 1966-05-03 Charles F Woodhouse Method and apparatus for measuring bioelectronic parameters
US3253595A (en) * 1963-08-07 1966-05-31 Cordis Corp Cardiac pacer electrode system
US3478746A (en) * 1965-05-12 1969-11-18 Medtronic Inc Cardiac implantable demand pacemaker
US3485247A (en) * 1965-08-16 1969-12-23 Electro Catheter Corp Cardiac catheterization apparatus and method
US3421511A (en) * 1965-12-10 1969-01-14 Medtronic Inc Implantable electrode for nerve stimulation
US3416533A (en) * 1966-05-20 1968-12-17 Gen Electric Conductive catheter
US3472234A (en) * 1967-08-15 1969-10-14 Gen Electric Body organ electrode
US3580242A (en) * 1968-04-01 1971-05-25 George E La Croix Fetal scalp electrode unit
US3664347A (en) * 1968-07-27 1972-05-23 Dietrich Harmjanz Electric heart stimulation method and electrode
US3596662A (en) * 1968-09-04 1971-08-03 Medtronic Inc Electrode for cardiac stimulator
US3654933A (en) * 1968-11-18 1972-04-11 Medtronic Inc Implatable electrode
US3650276A (en) * 1969-03-26 1972-03-21 Inst Demedicina Si Farmacie Method and apparatus, including a flexible electrode, for the electric neurostimulation of the neurogenic bladder

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
Electrode Fixation Using a Plastic Adhesive, Methyl-2-Cyanoacrylate, Electroencephalography and Clinical Neurophysiology, 1964, Vol. 17, p. 696 697. *

Cited By (105)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3964473A (en) * 1972-09-21 1976-06-22 Telectronics Pty. Limited Bone prosthesis
US3893461A (en) * 1972-11-28 1975-07-08 Thomas A Preston Pacing apparatus and method utilizing improved catheter
US3915174A (en) * 1972-11-28 1975-10-28 Thomas A Preston Pacing apparatus and improved catheter
US4010755A (en) * 1972-11-28 1977-03-08 Preston Thomas A Unipolar pacing catheter with plural distal electrodes
US3911928A (en) * 1973-04-14 1975-10-14 Hans Lagergren Endocardial electrode
US3935864A (en) * 1973-07-04 1976-02-03 Hans Lagergren Endocardial electrode
US4006748A (en) * 1976-01-29 1977-02-08 Pacestter Systems, Inc. Implantable unipolar pacemaker with improved outer electrode plate
US4044774A (en) * 1976-02-23 1977-08-30 Medtronic, Inc. Percutaneously inserted spinal cord stimulation lead
US4149542A (en) * 1976-03-26 1979-04-17 Siemens Aktiengesellschaft Endocardial electrode
US4125116A (en) * 1977-02-14 1978-11-14 The Johns Hopkins University Human tissue stimulation electrode structure
US4161952A (en) * 1977-11-01 1979-07-24 Mieczyslaw Mirowski Wound wire catheter cardioverting electrode
US4261372A (en) * 1977-11-22 1981-04-14 Hansen Carl C Electrode for implantation into cochlea
USRE32204E (en) * 1980-06-09 1986-07-15 Mansfield Scientific, Inc. Electrode assembly for temporary pacing and heart measurements
US4381013A (en) * 1981-03-19 1983-04-26 Medtronic, Inc. "J" Stylet wire
USRE32227E (en) * 1981-03-19 1986-08-19 Medtronic, Inc. "J" Stylet wire
US4444195A (en) * 1981-11-02 1984-04-24 Cordis Corporation Cardiac lead having multiple ring electrodes
US4481953A (en) * 1981-11-12 1984-11-13 Cordis Corporation Endocardial lead having helically wound ribbon electrode
US4445511A (en) * 1982-06-24 1984-05-01 Telectronics Pty. Ltd. Pacer electrode connector assembly
EP0109178A2 (en) * 1982-10-14 1984-05-23 Baxter International Inc. Flexible tip cardiac pacing catheter
US4759378A (en) * 1982-10-14 1988-07-26 American Hospital Supply Corporation Flexible tip cardiac pacing catheter
EP0109178A3 (en) * 1982-10-14 1984-12-27 American Hospital Supply Corporation Flexible tip cardiac pacing catheter
US4938231A (en) * 1985-10-22 1990-07-03 Telectronics N.V. Defibrillator electrode
US4817634A (en) * 1987-06-18 1989-04-04 Medtronic, Inc. Epicardial patch electrode
US4971070A (en) * 1987-06-18 1990-11-20 Medtronic, Inc. Epicardial patch electrode
US4819661A (en) * 1987-10-26 1989-04-11 Cardiac Pacemakers, Inc. Positive fixation cardiac electrode with drug elution capabilities
US5040544A (en) * 1988-02-16 1991-08-20 Medtronic, Inc. Medical electrical lead and method of manufacture
US4860446A (en) * 1988-02-16 1989-08-29 Medtronic, Inc. Medical electrical lead and method of manufacture
US4947866A (en) * 1988-02-16 1990-08-14 Medtronic, Inc. Medical electrical lead
US5231996A (en) * 1992-01-28 1993-08-03 Medtronic, Inc. Removable endocardial lead
US5531779A (en) * 1992-10-01 1996-07-02 Cardiac Pacemakers, Inc. Stent-type defibrillation electrode structures
US5324321A (en) * 1992-12-22 1994-06-28 Medtronic, Inc. Medical electrical lead having sigmoidal conductors and non-circular lumens
US5439485A (en) * 1993-09-24 1995-08-08 Ventritex, Inc. Flexible defibrillation electrode of improved construction
US5542173A (en) * 1993-09-24 1996-08-06 Ventritex, Inc. Method of making flexible defibrillation electrode
US5674272A (en) * 1995-06-05 1997-10-07 Ventritex, Inc. Crush resistant implantable lead
US5755757A (en) * 1996-05-01 1998-05-26 Teague; Thomas Wade Apparatus for localized neutralization of poison
WO1998034678A1 (en) 1997-02-10 1998-08-13 Medtronic, Inc. Coiled wire conductor insulation for biomedical lead
US5796044A (en) * 1997-02-10 1998-08-18 Medtronic, Inc. Coiled wire conductor insulation for biomedical lead
EP0927561A3 (en) * 1997-12-29 2000-03-08 BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin Defibrillation electrode device
US5902331A (en) * 1998-03-10 1999-05-11 Medtronic, Inc. Arrangement for implanting an endocardial cardiac lead
US6132456A (en) * 1998-03-10 2000-10-17 Medtronic, Inc. Arrangement for implanting an endocardial cardiac lead
US6868291B1 (en) 1998-03-10 2005-03-15 Medtronic, Inc. Arrangement for implanting an endocardial cardiac lead
US6253111B1 (en) 1998-03-30 2001-06-26 Pacesetter, Inc. Multi-conductor lead
US6615085B1 (en) * 1998-10-26 2003-09-02 Birinder R. Boveja Apparatus for adjunct (add-on) therapy of Dementia and Alzheimer's disease utilizing an implantable lead and an external stimulator
US6161029A (en) * 1999-03-08 2000-12-12 Medtronic, Inc. Apparatus and method for fixing electrodes in a blood vessel
US6363286B1 (en) 1999-09-24 2002-03-26 Cardiac Pacemakers, Inc. High impedance electrode assembly
US20020058981A1 (en) * 1999-09-24 2002-05-16 Cardiac Pacemakers, Inc. High impedance electrode assembly
WO2001023034A1 (en) * 1999-09-24 2001-04-05 Cardiac Pacemakers, Inc. High impedance electrode assembly
US6889092B2 (en) 1999-09-24 2005-05-03 Cardiac Pacemakers, Inc. High impedance electrode assembly
US20030093136A1 (en) * 2001-11-09 2003-05-15 Osypka Thomas P. Cardiac lead with steroid eluting ring
US6671562B2 (en) 2001-11-09 2003-12-30 Oscor Inc. High impedance drug eluting cardiac lead
US7187980B2 (en) 2001-11-09 2007-03-06 Oscor Inc. Cardiac lead with steroid eluting ring
WO2004060440A2 (en) 2002-12-16 2004-07-22 Medtronic, Inc. Bilumen guide catheters for addessing cardiac sites
US20050070972A1 (en) * 2003-09-26 2005-03-31 Wahlstrand Carl D. Energy shunt for producing an MRI-safe implantable medical device
WO2005102447A1 (en) * 2004-03-30 2005-11-03 Medtronic, Inc. Mri-safe implantable lead
US20050222659A1 (en) * 2004-03-30 2005-10-06 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US20050222658A1 (en) * 2004-03-30 2005-10-06 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US20050222657A1 (en) * 2004-03-30 2005-10-06 Wahlstrand Carl D MRI-safe implantable lead
US20050222642A1 (en) * 2004-03-30 2005-10-06 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7174219B2 (en) 2004-03-30 2007-02-06 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US9302101B2 (en) 2004-03-30 2016-04-05 Medtronic, Inc. MRI-safe implantable lead
US9155877B2 (en) 2004-03-30 2015-10-13 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US8989840B2 (en) 2004-03-30 2015-03-24 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7877150B2 (en) 2004-03-30 2011-01-25 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7844343B2 (en) 2004-03-30 2010-11-30 Medtronic, Inc. MRI-safe implantable medical device
US7844344B2 (en) 2004-03-30 2010-11-30 Medtronic, Inc. MRI-safe implantable lead
US20050222656A1 (en) * 2004-03-30 2005-10-06 Wahlstrand Carl D MRI-safe implantable medical device
US20050222647A1 (en) * 2004-03-30 2005-10-06 Wahlstrand Carl D Lead electrode for use in an MRI-safe implantable medical device
US7729772B2 (en) * 2005-01-07 2010-06-01 Uroplasty, Inc. Implantable neuromodulation system and method
US20060155345A1 (en) * 2005-01-07 2006-07-13 Williams Jeffrey M Implantable neuromodulation system and method
US8280526B2 (en) 2005-02-01 2012-10-02 Medtronic, Inc. Extensible implantable medical lead
US20060200218A1 (en) * 2005-02-01 2006-09-07 Wahlstrand Carl D Extensible implantable medical lead
US20060217791A1 (en) * 2005-03-23 2006-09-28 Arrow International, Inc. Multi-lumen catheter having external electrical leads
WO2006101616A1 (en) * 2005-03-23 2006-09-28 Arrow International, Inc. Multi-lumen catheter having external electrical leads
US8027736B2 (en) 2005-04-29 2011-09-27 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7853332B2 (en) 2005-04-29 2010-12-14 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US20060247747A1 (en) * 2005-04-29 2006-11-02 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7571010B2 (en) * 2005-05-06 2009-08-04 Cardiac Pacemakers, Inc. Cable electrode assembly for a lead terminal and method therefor
US20060253180A1 (en) * 2005-05-06 2006-11-09 Cardiac Pacemakers, Inc. Cable electrode assembly for a lead terminal and method therefor
US7395119B2 (en) * 2005-05-19 2008-07-01 Cvrx, Inc. Implantable electrode assembly having reverse electrode configuration
US20080140167A1 (en) * 2005-05-19 2008-06-12 Cvrx, Inc. Implantable electrode assembly having reverse electrode configuration
US20070276442A1 (en) * 2005-05-19 2007-11-29 Cvrx, Inc. Implantable electrode assembly having reverse electrode configuration
US20060265038A1 (en) * 2005-05-19 2006-11-23 Cvrx, Inc. Implantable electrode assembly having reverse electrode configuration
US9044593B2 (en) 2007-02-14 2015-06-02 Medtronic, Inc. Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding
US20080195186A1 (en) * 2007-02-14 2008-08-14 Bernard Li Continuous conductive materials for electromagnetic shielding
US20080195187A1 (en) * 2007-02-14 2008-08-14 Bernard Li Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding
US8483842B2 (en) 2007-04-25 2013-07-09 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US9259572B2 (en) 2007-04-25 2016-02-16 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US20080269863A1 (en) * 2007-04-25 2008-10-30 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US20090012591A1 (en) * 2007-07-05 2009-01-08 Advanced Bionics Corporation Lead with contacts formed by coiled conductor and methods of manufacture and use
US7899548B2 (en) * 2007-07-05 2011-03-01 Boston Scientific Neuromodulation Corporation Lead with contacts formed by coiled conductor and methods of manufacture and use
US9731119B2 (en) 2008-03-12 2017-08-15 Medtronic, Inc. System and method for implantable medical device lead shielding
US20100280583A1 (en) * 2009-04-29 2010-11-04 Biotronik Crm Patent Ag Electrode Element, Electrode Lead Comprising An Electrode Element, Method For The Production Of An Electrode Lead
EP2246092A1 (en) * 2009-04-29 2010-11-03 Biotronik CRM Patent AG Method for manufacturing an electrode cable
US9186499B2 (en) 2009-04-30 2015-11-17 Medtronic, Inc. Grounding of a shield within an implantable medical lead
US9216286B2 (en) 2009-04-30 2015-12-22 Medtronic, Inc. Shielded implantable medical lead with guarded termination
US9220893B2 (en) 2009-04-30 2015-12-29 Medtronic, Inc. Shielded implantable medical lead with reduced torsional stiffness
US9629998B2 (en) 2009-04-30 2017-04-25 Medtronics, Inc. Establishing continuity between a shield within an implantable medical lead and a shield within an implantable lead extension
US9272136B2 (en) 2009-04-30 2016-03-01 Medtronic, Inc. Grounding of a shield within an implantable medical lead
US9452284B2 (en) 2009-04-30 2016-09-27 Medtronic, Inc. Termination of a shield within an implantable medical lead
US9205253B2 (en) 2009-04-30 2015-12-08 Medtronic, Inc. Shielding an implantable medical lead
US8910376B2 (en) 2009-05-27 2014-12-16 Boston Scientific Neuromodulation Corporation Systems and methods for forming an end of an elongated member of an electrical stimulation system
US20100304626A1 (en) * 2009-05-27 2010-12-02 Boston Scientific Neuromodulation Corporation Systems and methods for forming an end of an elongated member of an electrical stimulation system
US10035014B2 (en) 2010-04-27 2018-07-31 Medtronic, Inc. Steering an implantable medical lead via a rotational coupling to a stylet
US9463317B2 (en) 2012-04-19 2016-10-11 Medtronic, Inc. Paired medical lead bodies with braided conductive shields having different physical parameter values
US9993638B2 (en) 2013-12-14 2018-06-12 Medtronic, Inc. Devices, systems and methods to reduce coupling of a shield and a conductor within an implantable medical lead

Also Published As

Publication number Publication date Type
DE2319500A1 (en) 1973-11-08 application
GB1423262A (en) 1976-02-04 application
FR2180908A1 (en) 1973-11-30 application
CA995764A (en) 1976-08-24 grant
NL7305358A (en) 1973-10-19 application
JPS4920984A (en) 1974-02-23 application
FR2180908B1 (en) 1977-09-02 grant
CA995764A1 (en) grant

Similar Documents

Publication Publication Date Title
US3057356A (en) Medical cardiac pacemaker
US5143089A (en) Assembly and method of communicating electrical signals between electrical therapeutic systems and body tissue
US4624265A (en) Electro-catheter used in physiological cardiac stimulation simulative of the auriculo-ventricular sequence, featuring active engagement of the cardiac muscle
US5405374A (en) Transvenous defibrillation lead and method of use
US6078840A (en) Medical electrical lead having improved fixation
US4735205A (en) Method and apparatus including a sliding insulation lead for cardiac assistance
US5454837A (en) Implantable medical system with optical communication between a treatment site and a therapy-generating apparatus
US7130682B2 (en) Pacing and sensing vectors
US4590946A (en) Surgically implantable electrode for nerve bundles
US6212434B1 (en) Single pass lead system
US4819661A (en) Positive fixation cardiac electrode with drug elution capabilities
US6249709B1 (en) Endocardial defibrillation lead with multi-lumen body and axially mounted distal electrode
US5545201A (en) Bipolar active fixation lead for sensing and pacing the heart
US5423865A (en) Electrode system for a defibrillator
US6377857B1 (en) Apparatus for manufacturing an endocardial defibrillation lead with multi-lumen body and method
US6055455A (en) Filtered feedthrough for an implantable medical device
US5374286A (en) Torque indicator for fixed screw leads
US6501994B1 (en) High impedance electrode tip
US5662696A (en) One piece disposable threshold test can electrode for use with an implantable cardioverter defibrillator system
US7162304B1 (en) System for measuring cardiac rhythm parameters for assessment of spinal cord stimulation
US5092332A (en) Steroid eluting cuff electrode for peripheral nerve stimulation
US4858623A (en) Active fixation mechanism for lead assembly of an implantable cardiac stimulator
US5632770A (en) Implantable defibrillation system with lead having improved porous surface coating
US6366819B1 (en) Biostable small French lead
US6405091B1 (en) Lead assembly with masked microdisk tip electrode and monolithic controlled release device