US3735766A - Optional unipolar-bipolar body organ stimulator - Google Patents

Optional unipolar-bipolar body organ stimulator Download PDF

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Publication number
US3735766A
US3735766A US00135069A US3735766DA US3735766A US 3735766 A US3735766 A US 3735766A US 00135069 A US00135069 A US 00135069A US 3735766D A US3735766D A US 3735766DA US 3735766 A US3735766 A US 3735766A
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indifferent electrode
insulating
stimulator
connector
set forth
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Expired - Lifetime
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US00135069A
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English (en)
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D Bowers
J Mohalski
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General Electric Co
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General Electric Co
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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
    • A61N1/18—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
    • A61N1/37512—Pacemakers

Definitions

  • ABSTRACT A body organ stimulator such as an electronic cardiac stimulator has the customary connector for attaching intra-cardiac catheter leads or myocardial leads to operate the stimulator in a bipolar mode.
  • an indifferent electrode plate which connects internally of the device with one of the connector terminals.
  • the plate in the stimulator or the adapter is dipped in medical grade silicone sealant.
  • An insulating label or strip is then superposed over the sealant coated plate and it is clipped and cured again.
  • the physician has the option of stripping the label to expose the plate so the stimulator may be operated in the unipolar mode or leave the strip in place for operation in the bipolar mode.
  • the pulse or stimulus signal generating circuitry in a stimulator is usually encapsulated in resin along with batteries.
  • a suitable connector extends from the encap sulation.
  • the connector usually has two terminals although certain prior stimulators which have a built-in indifferent electrode employ a one-terminal connector.
  • suitable flexible conductive leads are attached to the organ which is to be stimulated and to the stimulator connector.
  • Various types of leads are used.
  • One type has two conductor elements and a connector on one end that couples with the stimulator connector. The other end of the conductors are bared and adapted for suturing directly into the myocardium in which case stimulating pulse current from the stimulator flows through active tissue between the bared ends.
  • the leads just described are commonly called myocardial leads.
  • Intra-cardiac catheter leads are another type. This type usually has two flexible concentric conductors which are insulated from each other and terminate at one end in a stimulator connector and at the other end in a pair of metal terminals which are spaced apart and insulated from each other. Leads of this type extend from the stimulator through a blood vessel to the interior of the heart. Current pulses which flow between the exposed terminals stimulate the heart.
  • the operating mode is characterized as bipolar because both poles or terminals of the stimulus signal generator are connected directly on or near the heart.
  • unipolar stimulation is physiologically indicated or preferred by the physician.
  • Unipolar stimulation implies connecting only one of the output terminals from the stimulus signal generator directly to the heart and using as the other terminal a large area metal plate, called an indifferent electrode, which is implanted at some distance from the heart, usually in subcutaneous tissue, providing a return conductive path from the heart to the stimulator by way of the indifferent electrode.
  • Some presently available stimulators have an indifferent electrode plate embedded in the insulating encapsulation so that the plate will contact body tissue when the stimulator is implanted. With this arrangement the stimulator will operate in the unipolar mode if it is used in conjunction with an appropriate single conductor lead. If bipolar stimulation is indicated for a particular patient, however, the unipolar type of stimulator just described cannot be used since the indifferent electrode 'would be exposed and active. Thus, it is evident that up to this time manufacturers have had to provide one type of stimulator having no exposed electrode plate and another with such a plate in order to fulfill the physicians requirements and needs in all cases.
  • Available adapters customarily comprise two conductive leads each of which terminates at a corresponding end in a connector which mates with the connector on the stimulator.
  • the distal tip of one lead is attached to or in contact with the interior of the heart.
  • the other lead terminates in an exposed metal plate constituting an indifferent electrode which is usually implanted in body tissue in proximity with the stimulator.
  • stimulating current flows from the distal tip of the lead and returns through body tissue to the indifferent electrode and the stimulator.
  • An object of the present invention is to overcome the above-noted disadvantages by providing a body organ stimulator which is adapted for optional use in either the bipolar or unipolar operating modes without employing any adapter or other special accessories.
  • Another object of the invention is to enable a manufacturer to reduce the number of types of body organ stimulators and adapters that are in production by making types of stimulators and adapters that are originally adapted for bipolar stimulation and which can be readily converted by the user for unipolar stimulation.
  • a more specific object of this invention is to equip stimulators and adapters with an indifferent electrode, for unipolar stimulation, which may be maintained in an inactive state if desired so that immediately before implantation, or even after, the stimulator may be converted from bipolar to unipolar or from unipolar to bipolar operation.
  • a more specific object of this invention is to incorporate in or at a remote location from the stimulator an indifferent electrode which is covered and insulated by an adhesive but removable strip or insulating membrane which may remain in place for bipolar stimulation but can be removed for unipolar stimulation.
  • one concept involves embedding an indifferent electrode in the form of a metal plate in the surface of the resinous material in which the electronic components of the stimulator are encapsulated.
  • An insulating adhesive membrane sealant coating is applied to the plate and to give added strength to the membrane an insulating strip is applied to the adhesive membrane sealant.
  • another coating of sealant is applied to help retain the protective strip.
  • the user merely peels off the strip or rubs off the membrane coating covering the plate, thereby exposing the indifferent electrode plate and rendering it active.
  • Another concept is to have the indifferent electrode at a remote location in the body to apply an insulating membrane or strip to the electrode.
  • FIG. I is a plan view of a body organ stimulator incorporating the invention.
  • FIG. 2 is a view of the right side of FIG. 1;
  • FIG. 3 is a plan view of the internal components of the stimulator shown in the preceding figures before the components are encapsulated, some of the compo- .nents being represented schematically;
  • FIG. 4 is a vertical cross section taken on a line corresponding with 4-4 in FIG. 1;
  • FIG. 5 is a magnified view of a partial cross section of the stimulator taken on a line corresponding with 5-5 in FIG. 4;
  • FIG. 6 is a plan view of an intra-cardiac catheter electrode which exemplifies electrodes with which the new stimulator may be used;
  • FIG. 7 is an isolated plan view of the insulating element or removable strip which is used to maintain the indifferent electrode in an inactive state
  • FIG. 8 is a magnified cross section of the insulating element shown in the preceding figure.
  • FIG. 1 The configuration shown in FIG. 1 is that of a cardiac stimulator which typifies stimulators in which the invention may be incorporated.
  • the internal components of the stimulator are in a resinous encapsulation 10 which is conventional.
  • the encapsulation 10 serves as electrical insulation and as a body fluid impervious barrier.
  • the battery pack subassembly for furnishing electric power to the encapsulated electronic components of the stimulator is represented by the broken line marked 11.
  • the battery pack is also in an encapsulation. There will be a further discussion of the battery pack 11 later in reference to FIG. 3.
  • the electronic components of the stimulus signal generating means are not shown in detail but it will be understood that they are mounted on printed circuit board 14 and are encompassed in the space which is defined by the dash-dot rectangle l5.
  • connector assembly 16 Secured to printed circuit board 14 is an electric connector assembly which is generally designated by the reference numeral 16.
  • One part 17 of connector assembly 16 is embedded in resinous encapsulating material 10 and another tubular part 18 extends therefrom.
  • insulating block 19 inside of exposed tubular extension 18 is an insulating block 19 in which there are two small connector pin sockets 20 and 21. These connectorpin sockets are optionally available for connecting either single or double conductor organ attachment leads to the stimulator as will be described shortly hereinafter in reference to FIG. 6.
  • the electrical conductors for delivering electric stimulus signals from the printed circuit board mounted stimulus signal generator to the output terminals comprising connector pin sockets and 21 may be seen most clearly in FIG. 3 where these conductors are represented schematically by dashed lines.
  • the battery pack I I, printed circuit board 14, conducting supporting posts 12 and 13 and connector assembly 16 are shown in solid outline.
  • the rectangle 15 in which the electronic components are encompassed is shown in dash-dot lines.
  • a conductor 24, shown in dashed lines, makes one of the connections between printed circuit board 14 and a connector pin socket 20 within connector assembly 16.
  • a conductor comprising sections 25 and 26 makes another connection from printed circuit board 14 to the other pin 21 in connector assembly 16.
  • stimulating signals may be delivered from signal generator 15 to each of the connected output terminal sockets 20 and 21.
  • the stimulator will function in the bipolar mode as it is called with both active conductor ends terminated in the organ which is to be stimulated.
  • the battery pack 11 shown in FIG. 3 comprises four batteries 31, 32, 33 and 34 whose electrical connections are omitted for the sake of clarity. The batteries are in a resin encapsulation 35 from which conductors 12, 13 and 29 extend. After battery pack 11 is attached to printed circuit board 14 agd after electronic components 15 and the connector assembly 16 are in place, the unit shown in FIG. 3 is plaqed in a mold, not shown, and molded into encapsulatiri'g material 10 so that the final product has the configuration shown in FIGS. 1 and 2.
  • indifferent electrode plate 37 is also embedded in the surface of encapsulation 10 shown in FIG. 2.
  • indifferent electrode plate 37 is only active when the unipolar stimulating mode is desired.
  • contact pin assembly 36 which inserts into cylindrical contact element 30 and makes a sound electrical connection therewith.
  • Other suitable means for making a connection between plate 37 and printed circuit board 14 and its associated signal generating circuitry 15 may also be employed as long as the plate is electrically connected with an output terminal of the stimulus signal generator and to one of the terminals or pin sockets in connector assembly 16.
  • FIG. 4 shows in cross section the stainless steel indifferent electrode plate 37 embedded in a surface of encapsulating material 10.
  • the stimulator when construction of the stimulator has been advanced to this pint, it is dipped in a silicone rubber compound which is characterized by curing or vulcanizing in air.
  • the ordinary medical grade room temperature vulcanizing silicone compound which is now commonly used in connection with making implantable stimulators is a suitable material for dipping as just described.
  • a coating of silicone material 38 about ten to twenty mils thick remains on the object. This coating does not feel tacky when touched but any thin lightweight object can be made to adhere to it, at least temporarily, by merely pressing the object against coating 38.
  • silicone rubber coating layer 38 covers plate 37 without any discontinuities. This coating 38 is sufficient to insulate the plate 37 but does not have the strength to resist tearing when sharp objects come in contact such as medical instruments.
  • FIG. 7 A plan view of insulating element or label 39, which is comprised of two thin plastic lamina, is shown in FIG. 7 and a cross section thereof is shown in FIGS. 4, 5, 7 and 8.
  • Insulating element 39 should have substantially the same shape and size as indifferent electrode plate 37 in which case element 39 will be substantially congruent with plate 37 when the insulating element is properlyplaced on the first silicone coating 38.
  • the margins of insulating element 39 may, however, extend beyond the margins of plate 37 if desired. It should be evident from inspection of FIG. 4 that the inner and outer silicone coatings 30 and 40 plus the intervening laminated plastic insulating element 39 will prevent conduction'between plate 37 and body tissue in the event the unit is implanted in the body in this condition.
  • the label is only intended to be removed when unipolar pacing is desired.
  • a corner 41 of the element is shaded as shown.
  • the user may insert the tip of a scalpel at the edge of the shaded area to raise the element 39 insufficiently to allow gripping its corner with the fingers or other suitable instruments and tearing it off.
  • the properties of the insulating element or label 39 are such that the layer of silicone rubber 38 which intervenes between the label and plate 37 peels off with the label as does that area of the outer coating 40 which is congruent with the label.
  • the resin provides a good bonding surface for the silicone coating and makes a clean parting line between the plate and resin during removal.
  • the two silicone coatings 38 and 40 will remain with the label 39 and the electrode plate 37 will be exposed and substantially clear of any.silicone coating or insulating 7 material. If any residual fragments of coating remain,
  • the stimulator is adapted for operation in the unipolar mode dividual plastic film layers 39' and 39".
  • the bottom of layer 39 it should be noted, is roughened to improve its adhesive properties with respect to silicone layer 38 on which it is adhered.
  • the degree of roughening is not particularly important but it should be sufficient to remove any signs of glossiness from the surface which interfaces with the silicone coating 38 that is on metal plate 37.
  • the metal plate 37 is smooth and free of surface marks which could cause adhering of the silicone rubber.
  • the lamina 39 and 39' comprising the label 39 have been made of polyester film each about three mils thick in a commercial embodiment.
  • Duponts Mylar is a suitable material although any non-toxic flexible inert material with good moisture and electrical insulating properties may be used.
  • the top lamina 39' has been made of clear Mylar and the legend which appears in FIG. 7 has been printed directly on the backside of lamina'39' or on its interface 42 with lamina 39". After the legend is printed on the bottom side of lamina 39, that side is coated with adhesive and the lower lamina 39"- is pressed onto it.
  • the legend is made easy to read and there is further assurance that if either the ink or the adhesive between the lamina is even slightly toxic there will be no danger of toxic material ever coming into contact with body tissue.
  • the ink and adhesives used in the label 39 are chosen from materials which are non-toxic in the light of present knowledge and experimental testing.
  • the label for insulating the indifferent electrode be laminated. It could just as well be a single layer of flexible or relatively inflexible impervious insulating material and it could be opaque if desired.
  • the illustration of the invention will suggest to those skilled in the stimulator art that various means may be used for concealing or electrically isolating the indifferent electrode with an insulating element that is held in place with a rupturable adhesive membrane sealant. It will be evident to those skilled in the art that an indifferent elec trode in an adapter may also be provided with removable insulation similarly to the manner just discussed in respect to an electrode in the stimulator.
  • a lead assembly that will serve as a basis for describing how the new stimulator may be used is shown in FIG. 6 and is indicated generally by the numeral 45.
  • the leads here depicted comprise an elongated flexible conductor assembly 46 which may take many forms but in this case comprises two electrically isolated coaxial conductors, not shown, which are electrically insulated from each other and surrounded by insulation in a wellknown manner.
  • the proximal end of the conductor assembly terminates in a self-sealing connector 47 which may be plugged into the connector assembly 16 of the stimulator.
  • the distal end of the conductor assembly terminates in a metal tip 48 which is spaced from a metal ferrule 49.
  • the metal tip and ferrule are separated by an insulating section 50.
  • the distal end of the conductor assembly having the tip and ferrule may terminate in one of the chambers of the heart in connection with cardiac stimulation.
  • Current delivered by the stimulator flows between the tip 48 and ferrule 49 and any tissue or blood that intervenes between them for the purpose of conducting current through the organ and stimulating it.
  • the lead assembly of FIG. 6 may be joined with connector assembly 16 of the stimulator for operation in the bipolar stimulating mode if insulating element or label 39 is intact with indifferent electrode plate 37.
  • a suitable converter may also be used to facilitate connecting a single conductor organ lead to a two-terminal connector such as 16.
  • Lead assemblies very similar to that shown in FIG. 6 are also provided with a single conductor terminating in a single conductive tip such as tip 48.
  • single conductor lead assemblies are adapted for use as a cathode; in other words, they must be connected to the negative terminal of the stimulator since the leads of some manufacturers are made of materials that will be seriously eroded by electrolytic action if they are used as an anode.
  • the single conductor type of lead must cooperate with an indifferent electrode which is made available either through being built into the stimulator or as part of an adapter as mentioned when discussing the background of the invention. In the present example, only the negative of the connector pins 20 or 21 in stimulator connector assembly 16 is electrically connected with the single conductor in the lead assembly shown in FIG.
  • the indifferent electrode 37 is activated by removing the label 39 from over it as described above.
  • the indifferent electrode 37 will be in conductive contact with body tissue and in an active state for unipolar stimulation/As mentioned earlier, the ability to convert the stimulator from bipolar to unipolar operation enables the manufacturer to produce only one style of stimulator for making these operating modes available and the user is required to stock only the one style without sacrificing the ability to provide either or both modes of stimulation on short notice, such as during stimulator implantation.
  • the bipolar electrodes'and the indifferent electrode may be used at the same time and that in other cases, particularly in experimental or precautionary implants the stimulator may be implanted with the indifferent electrode concealed and in readiness for activation on a propitious occasion by gaining access for peeling off the insulating element or label by way of minor surgery under local anesthesia.
  • the indifferent electrode may also have forms other than a plate. For instance, it could be one or more pins, a ring, a sleeve, or a metallic casing that houses the electronics and batteries.
  • Rupturable adhesive sealants other than selfcuring single component silicone systems can also be used as long as they approximate the properties of medical grade silicones such as body compatibility, fluid impermeability, good electrical insulation, pliability, adhesiveness without permanent bonding and rupturability within limits.
  • the invention is applicable to any type of indifferent electrode whether it is associated directly with or located remotely from the stimulator.
  • a body-implantable organ stimulator comprising:
  • a. stimulus signal generating means having at least one output terminal which is adapted to be connected to a body organ and having another output terminal
  • indifferent electrode means and an insulating support therefor and including means for connecting said electrode means to said other output terminal for receiving a signal therefrom, and
  • insulating means adapted to adhere over said indifferent electrode means sealingly with said insulating support and to jointly cover the entire conductive area thereof, said insulating means being optionally removable to activate said indifferent electrode means and to expose the same to a conductive medium.
  • said insulating support for said indifferent electrode means comprises a material encapsulating said generating means, said indifferent electrode means being set in said material,
  • said insulating means being a membrane means which covers the said indifferent electrode means.
  • said first and second layers are comprised of silicone rubber.
  • said flexible strip means is comprised of polyester film which is roughened on at least the one side thereof which interfaces with said first membrane layer.
  • said indifferent electrode means comprises a conductive stainless steel plate.
  • a body-implantable organ stimulator comprising:
  • a. stimulus signal generating means having at least two output terminals
  • a connector means having at least two terminals which are supplied from the aforesaid output terminals, said connector means being adapted to connect with insulated leads that supply an organ,
  • an indifferent electrode means set in the external surface of said encapsulating material and connected with at least one of said output terminals inside of said encapsulating material
  • insulating means adapted to separably adhere to said indifferent electrode means and to cover said electrode means, said insulating element being optionally removable to activate said indifferent electrode rneans.
  • said insulating means comprises a rupturable membrane.
  • said insulating means comprises at least two flexible films laminated together, and
  • a silicone rubber membrane is on said indifferent electrode to which membrane said laminated insulating films adhere.
  • said indifferent electrode means comprises a conductive stainless steel plate.
  • An implantable electric body organ stimulator that is characterized by being operable in either bipolar or unipolar modes, comprising:
  • connector means accessible from the exterior of said encapsulation and having at least two terminals which are connected with said generator to receive stimulus signals therefrom and which are adapted to connect with leads for stimulating an organ in the bipolar mode
  • An implantable body organ stimulator compris- 10 ing:
  • a stimulus pulse generator having first and second output terminals and first and second connector means connected respectively with said terminals
  • lead means including a third connector means for coupling with said output terminal connector means, said lead means including at least one conductor extending from said third connector means and connecting with said first connector means when coupled and an organ engaging conductive electrode element attached to said conductor, said conductor having insulation thereon,
  • insulation means covering the entire conductive area of said indifferent electrode element, a portion of said insulation means being optionally separable from the remainder thereof to expose said indifferent electrode element for enabling contact with body tissue.
  • said separable portion of said insulation means comprises rupturable membrane means.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biophysics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Electrotherapy Devices (AREA)
US00135069A 1971-04-19 1971-04-19 Optional unipolar-bipolar body organ stimulator Expired - Lifetime US3735766A (en)

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JP (1) JPS5539345B1 (enrdf_load_stackoverflow)
CA (1) CA991272A (enrdf_load_stackoverflow)
DE (1) DE2218619A1 (enrdf_load_stackoverflow)
FR (1) FR2133835B1 (enrdf_load_stackoverflow)
GB (1) GB1378246A (enrdf_load_stackoverflow)
IT (1) IT951364B (enrdf_load_stackoverflow)
NL (1) NL7204941A (enrdf_load_stackoverflow)
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Cited By (48)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3866616A (en) * 1973-07-12 1975-02-18 Coratomic Heart pacer
US3906959A (en) * 1974-02-14 1975-09-23 American Optical Corp Liquid leak stop for an implantable heart pacer
US3957056A (en) * 1974-11-25 1976-05-18 Medtronic, Inc. Power-source canister
US4006748A (en) * 1976-01-29 1977-02-08 Pacestter Systems, Inc. Implantable unipolar pacemaker with improved outer electrode plate
USD255148S (en) 1978-02-24 1980-05-27 C. R. Bard, Inc. Electrosurgical current suppressor
USD258987S (en) 1978-03-10 1981-04-21 Medtronic, Inc. Medical electrical equipment case
US4301805A (en) * 1980-07-30 1981-11-24 Cordis Corporation Cardiac pacer connector system
US4369791A (en) * 1979-10-01 1983-01-25 Medtronic, Inc. Body implantable electrode
US4413636A (en) * 1979-11-19 1983-11-08 Phillip R. Beutel Catheter
US4445511A (en) * 1982-06-24 1984-05-01 Telectronics Pty. Ltd. Pacer electrode connector assembly
US4461194A (en) * 1982-04-28 1984-07-24 Cardio-Pace Medical, Inc. Tool for sealing and attaching a lead to a body implantable device
US4471783A (en) * 1981-03-27 1984-09-18 Cardiofrance-Compagnie Francaise D'electrocardiologie Method of making a cardiac stimulator with a single enclosure for separating the electric current and pulse generating means
US4532931A (en) * 1984-06-29 1985-08-06 Cardiac Pacemakers, Inc. Pacemaker with adaptive sensing means for use with unipolar or bipolar leads
US4602637A (en) * 1983-01-11 1986-07-29 Siemens Aktiengesellschaft Heart pacemaker system
US4679572A (en) * 1986-03-11 1987-07-14 Intermedics, Inc. Low threshold cardiac pacing electrodes
US4762136A (en) * 1987-02-19 1988-08-09 Intermedics, Inc. Low polarization pacing electrodes for capture verification
US5220929A (en) * 1991-10-02 1993-06-22 Ventritex, Inc. Bio-compatible boot for implantable medical device
US5245999A (en) * 1990-05-15 1993-09-21 Siemens Aktiengesellschaft Method of establishing a feedthrough and a feedthrough in an implantable apparatus for stimulating living tissue
US5282841A (en) * 1989-11-20 1994-02-01 Siemens Pacesetter, Inc. Implantable stimulation device and method of making same
US5433730A (en) * 1989-05-03 1995-07-18 Intermedics, Inc. Conductive pouch electrode for defibrillation
US5531766A (en) * 1995-01-23 1996-07-02 Angeion Corporation Implantable cardioverter defibrillator pulse generator kite-tail electrode system
US5562715A (en) * 1994-12-01 1996-10-08 Czura; John J. Cardiac pulse generator
US5814090A (en) * 1995-06-07 1998-09-29 Angeion Corporation Implantable medical device having heat-shrink conforming shield
US5913881A (en) * 1996-10-23 1999-06-22 Biotronik Mess-Und Therapiegeraete Gmbh & Co. Metallic housing for implant with recesses for eddy current reduction
US20020165589A1 (en) * 2001-05-01 2002-11-07 Imran Mir A. Gastric treatment and diagnosis device and method
US20030120320A1 (en) * 2001-12-20 2003-06-26 Medtronic,Inc. Implantable medical device having a housing or component case with an insulating material formed thereon, and methods of making same
US20050038476A1 (en) * 2003-08-14 2005-02-17 Team Brown Enterprises, Llc Coating/covering materials for the enhancement of defibrillation thresholds of implantable defibrillators/leads
US20050143784A1 (en) * 2001-05-01 2005-06-30 Imran Mir A. Gastrointestinal anchor with optimal surface area
US20060030224A1 (en) * 2004-08-09 2006-02-09 Degroot Paul J Means for augmenting medical electrical systems
US20060074458A1 (en) * 2001-05-01 2006-04-06 Imran Mir A Digestive organ retention device
US20060070334A1 (en) * 2004-09-27 2006-04-06 Blue Hen, Llc Sidewall plank for constructing a trailer and associated trailer sidewall construction
US20060074457A1 (en) * 2001-05-01 2006-04-06 Imran Mir A Pseudounipolar lead for stimulating a digestive organ
US20060089699A1 (en) * 2001-05-01 2006-04-27 Imran Mir A Abdominally implanted stimulator and method
US20060111753A1 (en) * 2001-05-01 2006-05-25 Imran Mir A Gastric stimulation anchor and method
US20070010862A1 (en) * 2005-04-26 2007-01-11 Thomas Osypka Apparatus and method for providing an electrical field to a targeted area
US20070049986A1 (en) * 2005-09-01 2007-03-01 Imran Mir A Randomized stimulation of a gastrointestinal organ
US20080065169A1 (en) * 2001-05-01 2008-03-13 Intrapace, Inc. Endoscopic Instrument for Engaging a Device
US7371215B2 (en) 2001-05-01 2008-05-13 Intrapace, Inc. Endoscopic instrument for engaging a device
US20090018606A1 (en) * 2005-10-12 2009-01-15 Intrapace, Inc. Methods and Devices for Stimulation of an Organ with the Use of a Transectionally Placed Guide Wire
US7509175B2 (en) 2006-08-03 2009-03-24 Intrapace, Inc. Method and devices for stimulation of an organ with the use of a transectionally placed guide wire
US20100087706A1 (en) * 2008-09-30 2010-04-08 Intrapace, Inc. Lead Access
US7702394B2 (en) 2001-05-01 2010-04-20 Intrapace, Inc. Responsive gastric stimulator
US20100234917A1 (en) * 2001-05-01 2010-09-16 Intrapace, Inc. Digestive Organ Retention Device
US20110034760A1 (en) * 2009-04-03 2011-02-10 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments
US20110046660A1 (en) * 2009-02-13 2011-02-24 Intrapace, Inc. Endoscopic Forceps With Removable Handle
US8934976B2 (en) 2004-09-23 2015-01-13 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments, optionally using multiple sensors
US9668690B1 (en) 2001-05-01 2017-06-06 Intrapace, Inc. Submucosal gastric implant device and method
US20220123408A1 (en) * 2020-10-19 2022-04-21 Duracell U.S. Operations, Inc. Sensor Assembly Comprising Conformable Battery Pack

Families Citing this family (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3071190D1 (en) * 1979-11-28 1985-11-21 Medtronic Inc Cardiac pacemaker with destructible means for output mode selection
FR2471789A1 (fr) * 1979-12-18 1981-06-26 Cardiofrance Co Stimulateur cardiaque implantable polyvalent et procede d'utilisation de ce stimulateur
EP0040658A3 (en) 1980-05-28 1981-12-09 Drg (Uk) Limited Patient plate for diathermy apparatus, and diathermy apparatus fitted with it
US4558702A (en) * 1983-01-21 1985-12-17 Cordis Corporation Cardiac pacer having input/output circuit programmable for use with unipolar and bipolar pacer leads

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3085577A (en) * 1961-06-12 1963-04-16 Vector Mfg Company Inc Body electrode
US3253595A (en) * 1963-08-07 1966-05-31 Cordis Corp Cardiac pacer electrode system
US3518984A (en) * 1967-10-12 1970-07-07 Univ Johns Hopkins Packaged diagnostic electrode device

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3085577A (en) * 1961-06-12 1963-04-16 Vector Mfg Company Inc Body electrode
US3253595A (en) * 1963-08-07 1966-05-31 Cordis Corp Cardiac pacer electrode system
US3518984A (en) * 1967-10-12 1970-07-07 Univ Johns Hopkins Packaged diagnostic electrode device

Cited By (87)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3866616A (en) * 1973-07-12 1975-02-18 Coratomic Heart pacer
US3906959A (en) * 1974-02-14 1975-09-23 American Optical Corp Liquid leak stop for an implantable heart pacer
US3957056A (en) * 1974-11-25 1976-05-18 Medtronic, Inc. Power-source canister
US4006748A (en) * 1976-01-29 1977-02-08 Pacestter Systems, Inc. Implantable unipolar pacemaker with improved outer electrode plate
USD255148S (en) 1978-02-24 1980-05-27 C. R. Bard, Inc. Electrosurgical current suppressor
USD258987S (en) 1978-03-10 1981-04-21 Medtronic, Inc. Medical electrical equipment case
US4369791A (en) * 1979-10-01 1983-01-25 Medtronic, Inc. Body implantable electrode
US4413636A (en) * 1979-11-19 1983-11-08 Phillip R. Beutel Catheter
US4301805A (en) * 1980-07-30 1981-11-24 Cordis Corporation Cardiac pacer connector system
US4471783A (en) * 1981-03-27 1984-09-18 Cardiofrance-Compagnie Francaise D'electrocardiologie Method of making a cardiac stimulator with a single enclosure for separating the electric current and pulse generating means
US4461194A (en) * 1982-04-28 1984-07-24 Cardio-Pace Medical, Inc. Tool for sealing and attaching a lead to a body implantable device
US4445511A (en) * 1982-06-24 1984-05-01 Telectronics Pty. Ltd. Pacer electrode connector assembly
US4602637A (en) * 1983-01-11 1986-07-29 Siemens Aktiengesellschaft Heart pacemaker system
US4532931A (en) * 1984-06-29 1985-08-06 Cardiac Pacemakers, Inc. Pacemaker with adaptive sensing means for use with unipolar or bipolar leads
US4679572A (en) * 1986-03-11 1987-07-14 Intermedics, Inc. Low threshold cardiac pacing electrodes
US4762136A (en) * 1987-02-19 1988-08-09 Intermedics, Inc. Low polarization pacing electrodes for capture verification
US5433730A (en) * 1989-05-03 1995-07-18 Intermedics, Inc. Conductive pouch electrode for defibrillation
US5282841A (en) * 1989-11-20 1994-02-01 Siemens Pacesetter, Inc. Implantable stimulation device and method of making same
US5245999A (en) * 1990-05-15 1993-09-21 Siemens Aktiengesellschaft Method of establishing a feedthrough and a feedthrough in an implantable apparatus for stimulating living tissue
US5220929A (en) * 1991-10-02 1993-06-22 Ventritex, Inc. Bio-compatible boot for implantable medical device
US5562715A (en) * 1994-12-01 1996-10-08 Czura; John J. Cardiac pulse generator
US5531766A (en) * 1995-01-23 1996-07-02 Angeion Corporation Implantable cardioverter defibrillator pulse generator kite-tail electrode system
US5814090A (en) * 1995-06-07 1998-09-29 Angeion Corporation Implantable medical device having heat-shrink conforming shield
US5913881A (en) * 1996-10-23 1999-06-22 Biotronik Mess-Und Therapiegeraete Gmbh & Co. Metallic housing for implant with recesses for eddy current reduction
US7076305B2 (en) 2001-05-01 2006-07-11 Intrapace, Inc. Gastric device and instrument system and method
US20090149910A1 (en) * 2001-05-01 2009-06-11 Inrapace, Inc. Gastric Treatment/Diagnosis Device and Attachment Device and Method
US9668690B1 (en) 2001-05-01 2017-06-06 Intrapace, Inc. Submucosal gastric implant device and method
US20030164304A1 (en) * 2001-05-01 2003-09-04 Imran Mir A. Aendoscopic instrument system@
US20030167025A1 (en) * 2001-05-01 2003-09-04 Imran Mir A. Gastric treatment/diagnosis device and attachment device and method
US20040243195A1 (en) * 2001-05-01 2004-12-02 Imran Mir A. Endoscopic system for attaching a device to a stomach
US9517152B2 (en) 2001-05-01 2016-12-13 Intrapace, Inc. Responsive gastric stimulator
US20050143784A1 (en) * 2001-05-01 2005-06-30 Imran Mir A. Gastrointestinal anchor with optimal surface area
US20050236277A9 (en) * 2001-05-01 2005-10-27 Imran Mir A Aendoscopic instrument system@
US8364269B2 (en) 2001-05-01 2013-01-29 Intrapace, Inc. Responsive gastric stimulator
US7016735B2 (en) 2001-05-01 2006-03-21 Intrapace, Inc. Gastric anchor and method
US20060069414A1 (en) * 2001-05-01 2006-03-30 Imran Mir A Endoscopic instrument system for implanting a device in the stomach
US20060074458A1 (en) * 2001-05-01 2006-04-06 Imran Mir A Digestive organ retention device
US8239027B2 (en) 2001-05-01 2012-08-07 Intrapace, Inc. Responsive gastric stimulator
US20060074457A1 (en) * 2001-05-01 2006-04-06 Imran Mir A Pseudounipolar lead for stimulating a digestive organ
US20060089699A1 (en) * 2001-05-01 2006-04-27 Imran Mir A Abdominally implanted stimulator and method
US20060111753A1 (en) * 2001-05-01 2006-05-25 Imran Mir A Gastric stimulation anchor and method
US20060116735A1 (en) * 2001-05-01 2006-06-01 Imran Mir A Gastric device and endoscopic delivery system
US20020165589A1 (en) * 2001-05-01 2002-11-07 Imran Mir A. Gastric treatment and diagnosis device and method
US7107100B2 (en) 2001-05-01 2006-09-12 Intrapace, Inc. Aendoscopic instrument system@
US7120498B2 (en) 2001-05-01 2006-10-10 Intrapace, Inc. Method and device for securing a functional device to a stomach
US8190261B2 (en) 2001-05-01 2012-05-29 Intrapace, Inc. Gastrointestinal anchor in optimal surface area
US8019422B2 (en) 2001-05-01 2011-09-13 Intrapace, Inc. Gastric device and endoscopic delivery system
US20080065169A1 (en) * 2001-05-01 2008-03-13 Intrapace, Inc. Endoscopic Instrument for Engaging a Device
US7371215B2 (en) 2001-05-01 2008-05-13 Intrapace, Inc. Endoscopic instrument for engaging a device
US20090018605A1 (en) * 2001-05-01 2009-01-15 Intrapace, Inc. Gastric Treatment/Diagnosis Device and Attachment Device and Method
US7979127B2 (en) 2001-05-01 2011-07-12 Intrapace, Inc. Digestive organ retention device
US7483754B2 (en) 2001-05-01 2009-01-27 Intrapace, Inc. Endoscopic instrument system for implanting a device in the stomach
US7509174B2 (en) 2001-05-01 2009-03-24 Intrapace, Inc. Gastric treatment/diagnosis device and attachment device and method
US20100305656A1 (en) * 2001-05-01 2010-12-02 Intrapace, Inc. Gastric Simulation Anchor and Method
US20090099415A1 (en) * 2001-05-01 2009-04-16 Intrapace, Inc. Endoscopic Instrument System for Implanting a Device in the Stomach
US6535764B2 (en) 2001-05-01 2003-03-18 Intrapace, Inc. Gastric treatment and diagnosis device and method
US7590452B2 (en) 2001-05-01 2009-09-15 Intrapace, Inc. Endoscopic system for attaching a device to a stomach
US20100234917A1 (en) * 2001-05-01 2010-09-16 Intrapace, Inc. Digestive Organ Retention Device
US20090299434A1 (en) * 2001-05-01 2009-12-03 Intrapace, Inc. Endoscopic System For Attaching a Device to a Stomach
US7643887B2 (en) 2001-05-01 2010-01-05 Intrapace, Inc. Abdominally implanted stimulator and method
US7756582B2 (en) 2001-05-01 2010-07-13 Intrapace, Inc. Gastric stimulation anchor and method
US7747322B2 (en) 2001-05-01 2010-06-29 Intrapace, Inc. Digestive organ retention device
US7702394B2 (en) 2001-05-01 2010-04-20 Intrapace, Inc. Responsive gastric stimulator
US7689284B2 (en) 2001-05-01 2010-03-30 Intrapace, Inc. Pseudounipolar lead for stimulating a digestive organ
US20030120320A1 (en) * 2001-12-20 2003-06-26 Medtronic,Inc. Implantable medical device having a housing or component case with an insulating material formed thereon, and methods of making same
US20050038476A1 (en) * 2003-08-14 2005-02-17 Team Brown Enterprises, Llc Coating/covering materials for the enhancement of defibrillation thresholds of implantable defibrillators/leads
US20100076509A1 (en) * 2004-08-09 2010-03-25 Medtronic, Inc. Means for Augmenting Medical Electrical Systems
US20060030224A1 (en) * 2004-08-09 2006-02-09 Degroot Paul J Means for augmenting medical electrical systems
US7650188B2 (en) * 2004-08-09 2010-01-19 Medtronic, Inc. Means for augmenting medical electrical systems
US9662240B2 (en) 2004-09-23 2017-05-30 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments, optionally using multiple sensors
US8934976B2 (en) 2004-09-23 2015-01-13 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments, optionally using multiple sensors
US9259342B2 (en) 2004-09-23 2016-02-16 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments, optionally using multiple sensors
US20060070334A1 (en) * 2004-09-27 2006-04-06 Blue Hen, Llc Sidewall plank for constructing a trailer and associated trailer sidewall construction
US20070010862A1 (en) * 2005-04-26 2007-01-11 Thomas Osypka Apparatus and method for providing an electrical field to a targeted area
US7616996B2 (en) 2005-09-01 2009-11-10 Intrapace, Inc. Randomized stimulation of a gastrointestinal organ
US20070049986A1 (en) * 2005-09-01 2007-03-01 Imran Mir A Randomized stimulation of a gastrointestinal organ
US8032223B2 (en) 2005-09-01 2011-10-04 Intrapace, Inc. Randomized stimulation of a gastrointestinal organ
US20100023087A1 (en) * 2005-09-01 2010-01-28 Intrapace, Inc. Randomized stimulation of a gastrointestinal organ
US20090018606A1 (en) * 2005-10-12 2009-01-15 Intrapace, Inc. Methods and Devices for Stimulation of an Organ with the Use of a Transectionally Placed Guide Wire
US7509175B2 (en) 2006-08-03 2009-03-24 Intrapace, Inc. Method and devices for stimulation of an organ with the use of a transectionally placed guide wire
US20100087706A1 (en) * 2008-09-30 2010-04-08 Intrapace, Inc. Lead Access
US20110046660A1 (en) * 2009-02-13 2011-02-24 Intrapace, Inc. Endoscopic Forceps With Removable Handle
US8715181B2 (en) 2009-04-03 2014-05-06 Intrapace, Inc. Feedback systems and methods for communicating diagnostic and/or treatment signals to enhance obesity treatments
US20110087076A1 (en) * 2009-04-03 2011-04-14 Intrapace, Inc. Feedback systems and methods for communicating diagnostic and/or treatment signals to enhance obesity treatments
US20110034760A1 (en) * 2009-04-03 2011-02-10 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments
US20220123408A1 (en) * 2020-10-19 2022-04-21 Duracell U.S. Operations, Inc. Sensor Assembly Comprising Conformable Battery Pack
US12040500B2 (en) * 2020-10-19 2024-07-16 Duracell U.S. Operations, Inc. Sensor assembly comprising conformable battery pack

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SE378991B (enrdf_load_stackoverflow) 1975-09-22
CA991272A (en) 1976-06-15
DE2218619A1 (de) 1972-11-02
JPS5539345B1 (enrdf_load_stackoverflow) 1980-10-09
FR2133835A1 (enrdf_load_stackoverflow) 1972-12-01
FR2133835B1 (enrdf_load_stackoverflow) 1976-10-29
GB1378246A (en) 1974-12-27
NL7204941A (enrdf_load_stackoverflow) 1972-10-23
IT951364B (it) 1973-06-30

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