CA1085931A - Implantable unipolar pacemaker with improved outer electrode plate - Google Patents
Implantable unipolar pacemaker with improved outer electrode plateInfo
- Publication number
- CA1085931A CA1085931A CA269,779A CA269779A CA1085931A CA 1085931 A CA1085931 A CA 1085931A CA 269779 A CA269779 A CA 269779A CA 1085931 A CA1085931 A CA 1085931A
- Authority
- CA
- Canada
- Prior art keywords
- plate
- strip
- area
- conductive
- improvement
- 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
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—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
- A61N1/378—Electrical supply
-
- 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
Abstract
IMPLANTABLE UNIPOLAR PACEMAKER WITH IMPROVED
OUTER ELECTRODE PLATE
ABSTRACT OF THE DISCLOSURE
A unipolar living tissue stimulator of the implant-able type with an outer plate electrode which in one embodi-ment consists of a flat metal plate slotted by slots to form a plurality of electrically conductive strips. Each strip is electrically in contact with any other strip through only a single path. The strips are dimensioned so that any substan-tially square or circular surface area on any strip is signi-ficantly smaller than the total conductive surface area of the plate. Consequently, the heating of the slotted plate due to an external alternating magnetic field is reduced signifi-cantly.
OUTER ELECTRODE PLATE
ABSTRACT OF THE DISCLOSURE
A unipolar living tissue stimulator of the implant-able type with an outer plate electrode which in one embodi-ment consists of a flat metal plate slotted by slots to form a plurality of electrically conductive strips. Each strip is electrically in contact with any other strip through only a single path. The strips are dimensioned so that any substan-tially square or circular surface area on any strip is signi-ficantly smaller than the total conductive surface area of the plate. Consequently, the heating of the slotted plate due to an external alternating magnetic field is reduced signifi-cantly.
Description
1~85931 BACICGROU~`~D OF TIIE INVE:NTION
1. Field of the Invention:
The present invention generally relates to body stimulators 2nd, more particularly, to an improved body tissue stimulator of the unipolar type which is rechargeable by a magnetic field.
1. Field of the Invention:
The present invention generally relates to body stimulators 2nd, more particularly, to an improved body tissue stimulator of the unipolar type which is rechargeable by a magnetic field.
2. Description of the Prior Art:
Although the invention relates to various types of body tissue stimulators which are implantable in the body, it will be described in connection with a cardiac stimulator, generally referred to as a pacemaker, for ~planatory purposes only, rather than to limit the invention thereto.
As is appreciated, a pacemaker is a device which applies stimulating pulses to the heart. In recent years great advances were made in the development of such pacemakers.
At present a pacemaker is available which is implantable in the body and which includes a source of energy, such as a battery, which is rechargeable by an external alternating magnetic field, so that the pacemaker does not have to be removed periodically from the body for battery replacement, thus eliminating the need for frequent surgical operations. One available pace-maker is sealed in a hermetic container so as to extend the life of the pacemaker. During recharging the external magnetic field passes through the hermetic container and is picked up by a pickup coil, which forms part o~ the recharging circuitry inside the hermetic container.
The aforedescribed hermetically-sealed rechargeable pacemaker is of two types. These include the bipolar type and the unipolar type. As is known in the bipolar type, two electrodes extend from the pacemaker to the heart and each ~-d V.,,~
~ , , - ' ' -- ~08593'1 pulse is applied between them. In the unipolar type only one electrode extends to the heart. The o-ther electrode is in the form of ~n outer electrically conductive metal plate on the side of the pacemaker. The body saline solution ana body tissue, which are electrically conductive, provide the return electric path between the electrode in or on the heart and the outer plate, which i9 electrically connected to the circuitry inside the hermetic container. The outer plate is usually in direct contact with the skin or other body tissue inside the body. One example of a prior art unipolar~pacemaker is ~escribed in U.S. Patent No. 3,735,766. In the prior art the outer electrode is formed of a continuous sheet of a biocom-patible metal of a sufficiently large area, e.g., several square inches in order to minimize the current density thereat.
In the rechargeable unipolar pacemaker the recharg-ing alternating magnetic field is provided from an external recharging head, which is placed against the body near the location of ~he implanted pacemaker. Quite often the head is located with respect to the pacemaker so that adequate recharg-20- ing takes place while part of the magnetic field passes through the outer plate.
OBJECTS AND SUMMARY OF ~IE INVENTION
It is a primary object of the present invention to provide a new implanta~le unipolar pacemaker in which the effects of an external alternating magnetic field on the pace-maker outer plate are minimized.
75~3ss ,..~
10~5~31 ~nothet o~ject or the present invention is to provide a novel implantable unipolar pacemaker of the type rcchargeable by ~n external alternating magne~ic field in which the heating of the outer electrode is minimized.
These and other objects of the invention are achieved by providing a pacemaker of the unipolar t~pe with an outer electrode plate designed so that any substantially square area of the surface of the plate is a very small frac-tion of the total conductive surface area of the plate. In one embodiment this is achieved by slotti,~g the outer electrode metal plate with narrow slots so that the plate effectively defines elongated rectangular narr~w strips. Each of the strips is electrically connected to any other strip through only a single conductive path, with all strips being electrically connected to a common junction.
The novel features of the invention are set forth with particularity in the appended claims. The inve~tion will best be understood from the following description when read in conjunction with the acccmpanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
Figures 1 and 2 are diagrams useful in explaining a prior art implantable unipolar pacemaker with a conventional outer electrode plate;
Figures 3-9 are top views of different embodiments of the novel outer electrode plate in accordance with the present in~ention; and ~08S931 Figure 10 is a side view of another embodiment of a unipolar pacemaker in accordance with the present invention.
DESCRIPTION OF T~ PF~EFEP~RED EMBODIMENTS
The novel features of the invention and the signifi-cant advantages derived therefrom ma~ best be appreciated by first describing a specific embodiment of a prior art implant-able unipolar pacemaker. The front view of the prior art pace-maker is shown in Figure 1, and a cross-sectional view is shown in Figure 2. The pacemaker, is assumed to be of the recharge-able type by means of an external alternating magnetic field, and hermetically sealed by a hermetic container 10. me latter contains conventional pulse generating circuitry 12, a power source, e.g., a battery 13 and recharging circuitry 14 which are encapsulated by encapsulating matter, e.g., epoxy 15. The recharging circuitry 14 includes a pickup coil, designated by 14a, which picks up the external alternating magnetic field, thereby enabling circuitry 14 to recharge battery 13. The container 10 effectively hermetically seals the contents of the pacemaker from the body saline solution.
~xtending from a connector 16, which is attached to the pacemaker container 10 is a single electrode 17 which is connected to the pulse generating circuitry 12 through the connector 16. The electrode lead~18 is sufficiently long so that the electrode can extend to the patient's heart which is to be pulsed. To simplify Figure 2 the connector 16 is not shown. Only lead 18 is shown connected at one end to circuitry 12. It is obvious that the other end of lead 18 terminates in electrode 17, as shown in Figure 1. In Figure 2, the container 75/~59 ` 1085931 lO is shown surrouncled by a layer of insulating material 20.
Such a layer may be used to provide an optimum biocompa~ible surface around the container lO and to provide electrical and/
or heat insulation, if that is required.
The unipolar pacemaker, which is generally implanted against the patient's skin 22, includes an outer electrode in the form of an electrically conductive metal plate 25, which ifi electrically connected to the pulse generating circuitry 12, such as by lead 26. Generally, the lead 26 passes into the container through an appropriate insulated feedthrough.
However, with a metal container lO, an alternative to a feed-through is for lead 26 to be connected to the outer surface of the container, which is internally connected to pulse generating circuitry 12.
The body saline solution, which is electrically conductive, provides an electrically conductive return path for the current pulses between the electrode 17 and the outer plate 25 which is exposed to and in contact with the body solu-tion. Since the outer metal comes in contact with the ~ody saline solution and/or body tissue it is formed of a biocom-patible metal which provides satisfactory electrical coupling with the saline solution. Some examples of such metals are -~
stainless steel (SS) such as SS 304, cobalt-chromium alloys, titanium, platinum, zirconium and niobium as well as alloys-of these metals. Such metals exhibit a resistivity in the microhm-cm range, e.g., from about 60 microhm-cm to about 200 microhm-cm. The typical thickness of a prior art outer electrode plate 25 is on the order of lO mils or more, with the plate 7s/359 , .
~08593~
being formed of a continuous sheet of metal of significant surface area, e.g., 2-3 sq. inches. This relatively large surface area is desirable in order to minimize the current density at the plate, so that stimulation, due to the pulses, does not occur at the location of the outer metal plate. In the prior art, the plate is typically circularly shaped or in the shape of a square or wide rectangle.
Experience with the prior art unipolar rechargeable pacemaker has shown that adequate recharging takes place even when the external recharging head, which provides the external magnetic field, is positioned with respect to the implanted pacemaker, so that at least part of the magnetic field passes through the outer plate 25. The alternating magnetic field passing through plate 25 is represented by dots 29 in Figure 1 and by lines 29 in Figure 2. Purthermore, it has been found that with the prior art unipolar pacemaker with the plate 25 formed from a continuous sheet of metal when a relatively strong alternating magnetic field is applied for battery recharging purposes, the magnetic field passing through piate 25 generates significant heat in the plate. When the pow~r of the external alternating magnetic field is sufficient to induce power in the pacemaker on the order of about .5 watt or more, e.g~, 2-3 watts, the plate heating ca~ be sufficiently great to cause patient discomfort as well as a potential source of damage to body tissue.
~ The heating of the outer matal plate 25 due to the passage of an alternating magnetic field through it, which is most undesirable, is greatly minimized, if not completely eliminated, by the present invention. In accordance with the , ~os593~
pres~nt inv~n~ion an outer ~tal plate 25 is provided in which the maximum continuous area enclosed by a square or circular boundary on the surface of the plate is restricted to a maxi-mum small value, i.e., is restricted to be very small. The maximum enclosed square or circular area is a very s~all frac-tion of the total conductive surface area of the plate 25.
Since the largest circular area enclosed within a square area is 3.14/4 o the square area, hereinafter the term ~substantially square area" is intended to refer to a square area or to the largest circular area enclosed therein. ~
Attention is now directed to Figure 3 whic~ is a top view of one embodiment of the outer plate 25. For explanatory purposes the plate dimensions are assumed to be 1.5 inch x 2 inches. Thus, the total conductive su~face of the plate is 3 sq. inches. The plate 25 is slotted by a plurality of narrow slots 31, shown extending from opposite sides of the plate.
These slots effectively convert the plate from a single contin-uous metal sheet of 3 sq. inches into a plurality of elongated rectangular shaped conductive strips 32. The slots ~1 do not extend along the entire plate width in order not to separate the plate into electrically disconnected strips. Rather, each slot 31 extends from one end or side of the plate up to near the opposite plate side. This insures a continuous electrically conductive path for each strip 32 to a common junction 30 to which the lead 26 is connected. The slots 31 in effect convert the plate 25 into the narrow elongated rectangular strips 32. The width W of each strip 32 is quite s~all as eompared with any of the outer dimensions of the total plate 25. Consequently, any substantially square continuous surface area on any of the strips is much smaller than the total surface area of the plate 25.
It has been discovered that by maintaining the maximum substantially square area on the surface of any strip to a small maximum value, the heating of the slotted plate by an external alternating magnetic field is reduced greatly, as compared with the heating of a non-slotted plate of the same metal and thickness when subjected to the same external alternating field. The heating can be reduced to any accept-able maximum level by merely reducing the maximum substantially square area on the surface of any of the strips. Thi~ can easily be achieved by merely increasing the number of slots 31.
The slots 31 can be made very narrow, e.g., 0.001 inch wide.
Thus, their effect on the total conductive surface area of the plate 25 is negligible.
The significant reduction of plate heating in the slotted plate may be highlighted by the following example in which the non-slotted plate is again assumed to be 2 inches by 1.5 inch with a total surface area of 3 sq. inches. By slotting the plate with equally spaced slots extending ~rom the 2 inch sides, 16 separate strLps are formed. Neglecting the slots' widths, the width of each 5trip is about 2~16 = .125 inch. Thus, the maximum square area on any strip surface is only (.125)2 =
0.0156 sq. inch. On the other hand, the maximum square area of the non-slotted plate is (1.5)2 = 2.25 sq. inches. Thus, ~08S93~
with th~ slot~ the maximum square area is reduced by a factor of 144. When compared with the total conductivé
surface area of plate 25 which is 3 5q. inches, the maximum square area ~of 0.0156 sq. inch) represent~ a reduction by a factor of 190.
It should be apparent that by simply increasing the number of slots the maximum substantially square area on the surface of any strip 32 may be made extremely small thereby minimizing the heating of the plate. In the embodiment shown in Figure 3 by simply doubling the number of equally spaced slots 31, W is reduced by a factor of two so that the substan-tially square area is reduced by a factor of four. In any practical case the actual maximum substantially square area on any strip surface depends on the heat which is permitted to be generated. Under some conditions a heat reduction by a factor of two from the heat generated in a non-slotted plate may be sufficient. However, it is believed that in most practical applications the plate 25 will be formed so that the substantially square area on any strip will not be more than l/n of the total conductive surface area of the plate, where n will be on the order of not less than 5 and in some cases may be as high as 100 or more.
In the embodiment shown in Figure 3 except for one conductive strip 32 to which the lead 26 is directly connected at junction 30 each other strip 32 is electrically cannected to lead 26 through another strip 32. Figure 4 is a top view of another embodiment of plate 25. It differs from that shown in Figure 3 only in that the slots 31 all extend inwardly from one side of plate 25. In the embodiment o~ Figure 4 each strip 32 is effectively electrically connected to lead 26 through the lower part 25a of the plate 25 rather than through another strip 32. An embodiment similar to that shown in Figure 4 is shown in Figure 5. In the embodiment s~own in Figure 5 the slots extend inwardly from three sides of the - plate 25.
It should be pointed out that the slotted plate 25 need not serve or function as an electrostatic shield. Rather, it serves as an electrically conductive outer plate for a unipolar pacemaker. When in use it is located in and is in contact with the body saline solution and conducts currents to and from the body saline solution and/or body tissue. In order for each conductive strip 32 to contribute to and form part of the electrically conductive plate 25 it has to have an elec-trically conductive path to the lead 26 which connects the plate 25 to the pulse generating circuitry 12. It should be stressed however, that each strip 32 should be connected to the lead 26 through a single electrically conductive path without a return current path between any two strips. It is recognized that when in use body saline solution which is electrically conductive is present in the slots 31. However, the resistivity of the metal plate is in the microhm-cm range e.g., 80-200 microhm-cm, while the resistivity of the saline solution is generally on the order of about 20 ohm-cm. Con-sequently, due to the extremely high resistance of the saline solution as compared with that of the metal plate 25 .
lV~593~
~he body saline solution in the slots 31 does not act as a meaningful current conductor ~etween adjacent strips 32.
~ nother embodiment of the slotted plate 25 is shown in Figure 6. Therein, a single continuous slot 31 in the shape of a spiral i5 formed in the plate 25. It effectively converts the plate into a single long continuous spiral shaped strip 32 whose opposite ends are designated by 32a and 32b of a width W. It should be apparent that the maximum substantially square area on the surface of the strip 32 is not greater than W , which is only a small fraction of the total surface area of the plate 25. It should further be apparent that if desired instead of using a slotted plate 25 the outer electrode plate may be formed as an elongated narrow electrically conductive strip or wire which may be wrapped around the pacemaker as a coil. The strip should be narrow as compared with its total electrically conductive surface area, so that the largest substantially square area on the strip surface is significantly smaller than its total conductive surface area.
In each of the above described embodiments the sep-arate one or more conductive strips 32 are formed by cuttingone or more slots 31 in the plate 25. If desired, the plate 25 may be formed of separate small metallic plate members 40 which are interconnected at junction 43 to lead 26 by electrically conductive wires 41, as shown in Figure 7. If desired, instead of connecting some of the plate members 40 to lead 26 through other plate members, each plate member 40 may be connected through a separate conductive wire 41 to a common wire 45 to which lead 26 is also connected as shown in Figure 8. In the embodiment shown in Figures 7 and 8 the total 1~)85931 conductive surface area of the outer plate consists essentially o~ the surface areas of all the plate members 40. Prefer`ably, each plate member 40 should be shaped as an elo~gated rectangle, so that any substantially square or circular area on the plate member is small compared to the total area of the plate member.
As shown in Figure 9 the outer plate 25, providing the advantages hereinbefore discussed, namely reduced heating, may also be formed as a matrix of electrically conductive wires 47. Each wire can be viewed as a long rectangle of minimal width. If one wanted to permit an electrostatic field to pass through the conductive plate with little or no impedi-ment, yet couple the conductive plate to the tissue without generating heat, it can be accomplished here by separating the wires sufficiently to permit electrostatic fields to pass between the wires. Each of these wires may be connected to lead 26 directly or through one of the other wires. However, it should again be stressed that each wire should be electrically connected to any other wire only at one point, so as not to provide a large substantially square or circular loop of continuous wire which would generate hoat due to the magnetic field. In the embodiment shown in Figure 9, the total conduc-tive surface area of the plate 25 consists of the exposed surface areas of all the wires 47.
me novel outer plate of the present invention is also advantageous when forming part of an implantable unipolar pacemaker which is not of the rechargeable type by an external magnetic field. A patient with an implantable unipolar ~085931 pacemaker ma~ be present where an external magnetic field is present. Such a field maS~ pass through the skin and heat a conventional outer plate. However, when the outer plate of the pres~nt invention is used the heating of the plate by such a field would be minimal. Thus, the novel plate effectively protects the patient from discomfort or damage to body tissue even when the patient happens to be present where an external magnetic field exists.
It has been found that when the external alternating magnetic field is relatively strong, such as being large enough to induce 2 watts or more of power in the pacemaker, the maxi-mum substantially square area should not exceed .125 square inch in order to minimize plate heating and thereby prevent patient discomfort or potential injury to body tissue. In situations where the external alternating magnetic field is relatively weak, e.g., capable of inducing 0.5 watt or less in the pacemaker, a conventional outer plate, i.e., one formed of a continuous sheet of metal may be used. However, to mini-mize any patient discomfort or damage to body tissue due to localized heating in the plate, called "hot spots", the con-ventional outer plate should be coated with an outer layer of plastic type matter which has reasonably low thermal conduc- -tivity and is electrically conductive plastic, which comes in contact with the patient skin or other body tissue. A sid~
view of such an arrangement is shown in Figure 10. The outer plate is designated by 25 and the outer layer of the plastic matter is designated by 50 with the skin being designated by 22. The plastic layer 50 serves two functions. Due to its electrical conductivity, it provides a conductive path between !
7~/359 ~085931 the ~ody saline solution and body tissue to the outer plate 25 due to its low thermal conductivity. In addition, it tends to spread any heating of the plate 25, particularly due to hot spots, over its large surface area, to thereby minimize damage to body tissue or patient discomfort, due to the heating of the plate 25.
The conductive plastic 50 should be of the biocom-patible type, resistant to corrosion by the body saline solu-tion, and provide good electrical coupling to the body saline solution. In general its minimum electric~ resistivity should be greater than that of the metal plate 25 by a factor x, where x is on the order of 10 or more. Its maximum elec-trical resistivity should be on the order of about 40 times the electrical resistivity of the body saline solution, e.g., 400 ohm-cm. Layer 50 may be formed from implantable medical grade plastics, like silicon rubber, epoxy and like materials containing metallic matter. For example, layer 50 may be formed from epoxy containing steel or zirconium. Preferably, the thickness of the plastic layer 50 should be on the order -of 25 mils. If the plastic layer 50 is resistant to flaking or cracking, in some applications it can be used as thè outer plate of a unipolar pacemaker even without the underlying metal plate 25. Clearly, when the plastic layer 50 ser~es as the outer electrode means it has to be electrically connected to the pulse generating circuitry, such as by lead 26 as hereinbefore described. In either embodiment including layer 50 the heating of the outer electrode means due to the external magnetic field is reduced significantly.
.
. 75/359 ~08593~
Althou~h particular embodiments of the invention have been described and illustrated herein, it is recognized that modifications and variations may readily occur to those skilled in the art and consequently, it is intended that the claims be interpreted to cover such modifications ana equiva-lents.
Although the invention relates to various types of body tissue stimulators which are implantable in the body, it will be described in connection with a cardiac stimulator, generally referred to as a pacemaker, for ~planatory purposes only, rather than to limit the invention thereto.
As is appreciated, a pacemaker is a device which applies stimulating pulses to the heart. In recent years great advances were made in the development of such pacemakers.
At present a pacemaker is available which is implantable in the body and which includes a source of energy, such as a battery, which is rechargeable by an external alternating magnetic field, so that the pacemaker does not have to be removed periodically from the body for battery replacement, thus eliminating the need for frequent surgical operations. One available pace-maker is sealed in a hermetic container so as to extend the life of the pacemaker. During recharging the external magnetic field passes through the hermetic container and is picked up by a pickup coil, which forms part o~ the recharging circuitry inside the hermetic container.
The aforedescribed hermetically-sealed rechargeable pacemaker is of two types. These include the bipolar type and the unipolar type. As is known in the bipolar type, two electrodes extend from the pacemaker to the heart and each ~-d V.,,~
~ , , - ' ' -- ~08593'1 pulse is applied between them. In the unipolar type only one electrode extends to the heart. The o-ther electrode is in the form of ~n outer electrically conductive metal plate on the side of the pacemaker. The body saline solution ana body tissue, which are electrically conductive, provide the return electric path between the electrode in or on the heart and the outer plate, which i9 electrically connected to the circuitry inside the hermetic container. The outer plate is usually in direct contact with the skin or other body tissue inside the body. One example of a prior art unipolar~pacemaker is ~escribed in U.S. Patent No. 3,735,766. In the prior art the outer electrode is formed of a continuous sheet of a biocom-patible metal of a sufficiently large area, e.g., several square inches in order to minimize the current density thereat.
In the rechargeable unipolar pacemaker the recharg-ing alternating magnetic field is provided from an external recharging head, which is placed against the body near the location of ~he implanted pacemaker. Quite often the head is located with respect to the pacemaker so that adequate recharg-20- ing takes place while part of the magnetic field passes through the outer plate.
OBJECTS AND SUMMARY OF ~IE INVENTION
It is a primary object of the present invention to provide a new implanta~le unipolar pacemaker in which the effects of an external alternating magnetic field on the pace-maker outer plate are minimized.
75~3ss ,..~
10~5~31 ~nothet o~ject or the present invention is to provide a novel implantable unipolar pacemaker of the type rcchargeable by ~n external alternating magne~ic field in which the heating of the outer electrode is minimized.
These and other objects of the invention are achieved by providing a pacemaker of the unipolar t~pe with an outer electrode plate designed so that any substantially square area of the surface of the plate is a very small frac-tion of the total conductive surface area of the plate. In one embodiment this is achieved by slotti,~g the outer electrode metal plate with narrow slots so that the plate effectively defines elongated rectangular narr~w strips. Each of the strips is electrically connected to any other strip through only a single conductive path, with all strips being electrically connected to a common junction.
The novel features of the invention are set forth with particularity in the appended claims. The inve~tion will best be understood from the following description when read in conjunction with the acccmpanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
Figures 1 and 2 are diagrams useful in explaining a prior art implantable unipolar pacemaker with a conventional outer electrode plate;
Figures 3-9 are top views of different embodiments of the novel outer electrode plate in accordance with the present in~ention; and ~08S931 Figure 10 is a side view of another embodiment of a unipolar pacemaker in accordance with the present invention.
DESCRIPTION OF T~ PF~EFEP~RED EMBODIMENTS
The novel features of the invention and the signifi-cant advantages derived therefrom ma~ best be appreciated by first describing a specific embodiment of a prior art implant-able unipolar pacemaker. The front view of the prior art pace-maker is shown in Figure 1, and a cross-sectional view is shown in Figure 2. The pacemaker, is assumed to be of the recharge-able type by means of an external alternating magnetic field, and hermetically sealed by a hermetic container 10. me latter contains conventional pulse generating circuitry 12, a power source, e.g., a battery 13 and recharging circuitry 14 which are encapsulated by encapsulating matter, e.g., epoxy 15. The recharging circuitry 14 includes a pickup coil, designated by 14a, which picks up the external alternating magnetic field, thereby enabling circuitry 14 to recharge battery 13. The container 10 effectively hermetically seals the contents of the pacemaker from the body saline solution.
~xtending from a connector 16, which is attached to the pacemaker container 10 is a single electrode 17 which is connected to the pulse generating circuitry 12 through the connector 16. The electrode lead~18 is sufficiently long so that the electrode can extend to the patient's heart which is to be pulsed. To simplify Figure 2 the connector 16 is not shown. Only lead 18 is shown connected at one end to circuitry 12. It is obvious that the other end of lead 18 terminates in electrode 17, as shown in Figure 1. In Figure 2, the container 75/~59 ` 1085931 lO is shown surrouncled by a layer of insulating material 20.
Such a layer may be used to provide an optimum biocompa~ible surface around the container lO and to provide electrical and/
or heat insulation, if that is required.
The unipolar pacemaker, which is generally implanted against the patient's skin 22, includes an outer electrode in the form of an electrically conductive metal plate 25, which ifi electrically connected to the pulse generating circuitry 12, such as by lead 26. Generally, the lead 26 passes into the container through an appropriate insulated feedthrough.
However, with a metal container lO, an alternative to a feed-through is for lead 26 to be connected to the outer surface of the container, which is internally connected to pulse generating circuitry 12.
The body saline solution, which is electrically conductive, provides an electrically conductive return path for the current pulses between the electrode 17 and the outer plate 25 which is exposed to and in contact with the body solu-tion. Since the outer metal comes in contact with the ~ody saline solution and/or body tissue it is formed of a biocom-patible metal which provides satisfactory electrical coupling with the saline solution. Some examples of such metals are -~
stainless steel (SS) such as SS 304, cobalt-chromium alloys, titanium, platinum, zirconium and niobium as well as alloys-of these metals. Such metals exhibit a resistivity in the microhm-cm range, e.g., from about 60 microhm-cm to about 200 microhm-cm. The typical thickness of a prior art outer electrode plate 25 is on the order of lO mils or more, with the plate 7s/359 , .
~08593~
being formed of a continuous sheet of metal of significant surface area, e.g., 2-3 sq. inches. This relatively large surface area is desirable in order to minimize the current density at the plate, so that stimulation, due to the pulses, does not occur at the location of the outer metal plate. In the prior art, the plate is typically circularly shaped or in the shape of a square or wide rectangle.
Experience with the prior art unipolar rechargeable pacemaker has shown that adequate recharging takes place even when the external recharging head, which provides the external magnetic field, is positioned with respect to the implanted pacemaker, so that at least part of the magnetic field passes through the outer plate 25. The alternating magnetic field passing through plate 25 is represented by dots 29 in Figure 1 and by lines 29 in Figure 2. Purthermore, it has been found that with the prior art unipolar pacemaker with the plate 25 formed from a continuous sheet of metal when a relatively strong alternating magnetic field is applied for battery recharging purposes, the magnetic field passing through piate 25 generates significant heat in the plate. When the pow~r of the external alternating magnetic field is sufficient to induce power in the pacemaker on the order of about .5 watt or more, e.g~, 2-3 watts, the plate heating ca~ be sufficiently great to cause patient discomfort as well as a potential source of damage to body tissue.
~ The heating of the outer matal plate 25 due to the passage of an alternating magnetic field through it, which is most undesirable, is greatly minimized, if not completely eliminated, by the present invention. In accordance with the , ~os593~
pres~nt inv~n~ion an outer ~tal plate 25 is provided in which the maximum continuous area enclosed by a square or circular boundary on the surface of the plate is restricted to a maxi-mum small value, i.e., is restricted to be very small. The maximum enclosed square or circular area is a very s~all frac-tion of the total conductive surface area of the plate 25.
Since the largest circular area enclosed within a square area is 3.14/4 o the square area, hereinafter the term ~substantially square area" is intended to refer to a square area or to the largest circular area enclosed therein. ~
Attention is now directed to Figure 3 whic~ is a top view of one embodiment of the outer plate 25. For explanatory purposes the plate dimensions are assumed to be 1.5 inch x 2 inches. Thus, the total conductive su~face of the plate is 3 sq. inches. The plate 25 is slotted by a plurality of narrow slots 31, shown extending from opposite sides of the plate.
These slots effectively convert the plate from a single contin-uous metal sheet of 3 sq. inches into a plurality of elongated rectangular shaped conductive strips 32. The slots ~1 do not extend along the entire plate width in order not to separate the plate into electrically disconnected strips. Rather, each slot 31 extends from one end or side of the plate up to near the opposite plate side. This insures a continuous electrically conductive path for each strip 32 to a common junction 30 to which the lead 26 is connected. The slots 31 in effect convert the plate 25 into the narrow elongated rectangular strips 32. The width W of each strip 32 is quite s~all as eompared with any of the outer dimensions of the total plate 25. Consequently, any substantially square continuous surface area on any of the strips is much smaller than the total surface area of the plate 25.
It has been discovered that by maintaining the maximum substantially square area on the surface of any strip to a small maximum value, the heating of the slotted plate by an external alternating magnetic field is reduced greatly, as compared with the heating of a non-slotted plate of the same metal and thickness when subjected to the same external alternating field. The heating can be reduced to any accept-able maximum level by merely reducing the maximum substantially square area on the surface of any of the strips. Thi~ can easily be achieved by merely increasing the number of slots 31.
The slots 31 can be made very narrow, e.g., 0.001 inch wide.
Thus, their effect on the total conductive surface area of the plate 25 is negligible.
The significant reduction of plate heating in the slotted plate may be highlighted by the following example in which the non-slotted plate is again assumed to be 2 inches by 1.5 inch with a total surface area of 3 sq. inches. By slotting the plate with equally spaced slots extending ~rom the 2 inch sides, 16 separate strLps are formed. Neglecting the slots' widths, the width of each 5trip is about 2~16 = .125 inch. Thus, the maximum square area on any strip surface is only (.125)2 =
0.0156 sq. inch. On the other hand, the maximum square area of the non-slotted plate is (1.5)2 = 2.25 sq. inches. Thus, ~08S93~
with th~ slot~ the maximum square area is reduced by a factor of 144. When compared with the total conductivé
surface area of plate 25 which is 3 5q. inches, the maximum square area ~of 0.0156 sq. inch) represent~ a reduction by a factor of 190.
It should be apparent that by simply increasing the number of slots the maximum substantially square area on the surface of any strip 32 may be made extremely small thereby minimizing the heating of the plate. In the embodiment shown in Figure 3 by simply doubling the number of equally spaced slots 31, W is reduced by a factor of two so that the substan-tially square area is reduced by a factor of four. In any practical case the actual maximum substantially square area on any strip surface depends on the heat which is permitted to be generated. Under some conditions a heat reduction by a factor of two from the heat generated in a non-slotted plate may be sufficient. However, it is believed that in most practical applications the plate 25 will be formed so that the substantially square area on any strip will not be more than l/n of the total conductive surface area of the plate, where n will be on the order of not less than 5 and in some cases may be as high as 100 or more.
In the embodiment shown in Figure 3 except for one conductive strip 32 to which the lead 26 is directly connected at junction 30 each other strip 32 is electrically cannected to lead 26 through another strip 32. Figure 4 is a top view of another embodiment of plate 25. It differs from that shown in Figure 3 only in that the slots 31 all extend inwardly from one side of plate 25. In the embodiment o~ Figure 4 each strip 32 is effectively electrically connected to lead 26 through the lower part 25a of the plate 25 rather than through another strip 32. An embodiment similar to that shown in Figure 4 is shown in Figure 5. In the embodiment s~own in Figure 5 the slots extend inwardly from three sides of the - plate 25.
It should be pointed out that the slotted plate 25 need not serve or function as an electrostatic shield. Rather, it serves as an electrically conductive outer plate for a unipolar pacemaker. When in use it is located in and is in contact with the body saline solution and conducts currents to and from the body saline solution and/or body tissue. In order for each conductive strip 32 to contribute to and form part of the electrically conductive plate 25 it has to have an elec-trically conductive path to the lead 26 which connects the plate 25 to the pulse generating circuitry 12. It should be stressed however, that each strip 32 should be connected to the lead 26 through a single electrically conductive path without a return current path between any two strips. It is recognized that when in use body saline solution which is electrically conductive is present in the slots 31. However, the resistivity of the metal plate is in the microhm-cm range e.g., 80-200 microhm-cm, while the resistivity of the saline solution is generally on the order of about 20 ohm-cm. Con-sequently, due to the extremely high resistance of the saline solution as compared with that of the metal plate 25 .
lV~593~
~he body saline solution in the slots 31 does not act as a meaningful current conductor ~etween adjacent strips 32.
~ nother embodiment of the slotted plate 25 is shown in Figure 6. Therein, a single continuous slot 31 in the shape of a spiral i5 formed in the plate 25. It effectively converts the plate into a single long continuous spiral shaped strip 32 whose opposite ends are designated by 32a and 32b of a width W. It should be apparent that the maximum substantially square area on the surface of the strip 32 is not greater than W , which is only a small fraction of the total surface area of the plate 25. It should further be apparent that if desired instead of using a slotted plate 25 the outer electrode plate may be formed as an elongated narrow electrically conductive strip or wire which may be wrapped around the pacemaker as a coil. The strip should be narrow as compared with its total electrically conductive surface area, so that the largest substantially square area on the strip surface is significantly smaller than its total conductive surface area.
In each of the above described embodiments the sep-arate one or more conductive strips 32 are formed by cuttingone or more slots 31 in the plate 25. If desired, the plate 25 may be formed of separate small metallic plate members 40 which are interconnected at junction 43 to lead 26 by electrically conductive wires 41, as shown in Figure 7. If desired, instead of connecting some of the plate members 40 to lead 26 through other plate members, each plate member 40 may be connected through a separate conductive wire 41 to a common wire 45 to which lead 26 is also connected as shown in Figure 8. In the embodiment shown in Figures 7 and 8 the total 1~)85931 conductive surface area of the outer plate consists essentially o~ the surface areas of all the plate members 40. Prefer`ably, each plate member 40 should be shaped as an elo~gated rectangle, so that any substantially square or circular area on the plate member is small compared to the total area of the plate member.
As shown in Figure 9 the outer plate 25, providing the advantages hereinbefore discussed, namely reduced heating, may also be formed as a matrix of electrically conductive wires 47. Each wire can be viewed as a long rectangle of minimal width. If one wanted to permit an electrostatic field to pass through the conductive plate with little or no impedi-ment, yet couple the conductive plate to the tissue without generating heat, it can be accomplished here by separating the wires sufficiently to permit electrostatic fields to pass between the wires. Each of these wires may be connected to lead 26 directly or through one of the other wires. However, it should again be stressed that each wire should be electrically connected to any other wire only at one point, so as not to provide a large substantially square or circular loop of continuous wire which would generate hoat due to the magnetic field. In the embodiment shown in Figure 9, the total conduc-tive surface area of the plate 25 consists of the exposed surface areas of all the wires 47.
me novel outer plate of the present invention is also advantageous when forming part of an implantable unipolar pacemaker which is not of the rechargeable type by an external magnetic field. A patient with an implantable unipolar ~085931 pacemaker ma~ be present where an external magnetic field is present. Such a field maS~ pass through the skin and heat a conventional outer plate. However, when the outer plate of the pres~nt invention is used the heating of the plate by such a field would be minimal. Thus, the novel plate effectively protects the patient from discomfort or damage to body tissue even when the patient happens to be present where an external magnetic field exists.
It has been found that when the external alternating magnetic field is relatively strong, such as being large enough to induce 2 watts or more of power in the pacemaker, the maxi-mum substantially square area should not exceed .125 square inch in order to minimize plate heating and thereby prevent patient discomfort or potential injury to body tissue. In situations where the external alternating magnetic field is relatively weak, e.g., capable of inducing 0.5 watt or less in the pacemaker, a conventional outer plate, i.e., one formed of a continuous sheet of metal may be used. However, to mini-mize any patient discomfort or damage to body tissue due to localized heating in the plate, called "hot spots", the con-ventional outer plate should be coated with an outer layer of plastic type matter which has reasonably low thermal conduc- -tivity and is electrically conductive plastic, which comes in contact with the patient skin or other body tissue. A sid~
view of such an arrangement is shown in Figure 10. The outer plate is designated by 25 and the outer layer of the plastic matter is designated by 50 with the skin being designated by 22. The plastic layer 50 serves two functions. Due to its electrical conductivity, it provides a conductive path between !
7~/359 ~085931 the ~ody saline solution and body tissue to the outer plate 25 due to its low thermal conductivity. In addition, it tends to spread any heating of the plate 25, particularly due to hot spots, over its large surface area, to thereby minimize damage to body tissue or patient discomfort, due to the heating of the plate 25.
The conductive plastic 50 should be of the biocom-patible type, resistant to corrosion by the body saline solu-tion, and provide good electrical coupling to the body saline solution. In general its minimum electric~ resistivity should be greater than that of the metal plate 25 by a factor x, where x is on the order of 10 or more. Its maximum elec-trical resistivity should be on the order of about 40 times the electrical resistivity of the body saline solution, e.g., 400 ohm-cm. Layer 50 may be formed from implantable medical grade plastics, like silicon rubber, epoxy and like materials containing metallic matter. For example, layer 50 may be formed from epoxy containing steel or zirconium. Preferably, the thickness of the plastic layer 50 should be on the order -of 25 mils. If the plastic layer 50 is resistant to flaking or cracking, in some applications it can be used as thè outer plate of a unipolar pacemaker even without the underlying metal plate 25. Clearly, when the plastic layer 50 ser~es as the outer electrode means it has to be electrically connected to the pulse generating circuitry, such as by lead 26 as hereinbefore described. In either embodiment including layer 50 the heating of the outer electrode means due to the external magnetic field is reduced significantly.
.
. 75/359 ~08593~
Althou~h particular embodiments of the invention have been described and illustrated herein, it is recognized that modifications and variations may readily occur to those skilled in the art and consequently, it is intended that the claims be interpreted to cover such modifications ana equiva-lents.
Claims (12)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. In a unipolar implantable living tissue stimulator of the type including pulse generating means, a stimulating electrode electrically con-nected to said pulse generating means and locatable at the tissue to be stimulated by pulses supplied to said stimulating electrode by said generat-ing means, and outer electrode means connected to said generating means and in direct electrical contact with body saline solution which extends from said stimulating electrode to said outer electrode means to thereby provide an electrical conductive path therebetween, the improvement comprising:
outer electrode means defining an electrically conductive surface of preselected area which is in direct electrical contact with the body saline solution when said stimulator is implanted in a body, said outer elec-trode means defining a plurality of electrically conductive elements whereby any substantially square area on the surface of any of said elements does not exceed a preselected maximum value which is significantly smaller than the total area of the conductive surface of said outer electrode means.
outer electrode means defining an electrically conductive surface of preselected area which is in direct electrical contact with the body saline solution when said stimulator is implanted in a body, said outer elec-trode means defining a plurality of electrically conductive elements whereby any substantially square area on the surface of any of said elements does not exceed a preselected maximum value which is significantly smaller than the total area of the conductive surface of said outer electrode means.
2. The improvement as described in Claim 1 wherein said outer electrode means is a metal plate, with a plurality of slots defined therein to separate said plate into a plurality of electrically conductive strips, defining said electrically conductive elements, each strip being electrically connected to any other strip only through a single electrically conductive path, the strips having dimensions whereby any substantially square area of the surface of any strip does not exceed said preselected maximum value which is significantly smaller than the total area of the conductive surface of said metal plate.
3. The improvement as described in Claim 1 wherein said outer electrode means is a plate of a biocompatible metal with a plurality of slots extending inwardly from at least one side of said metal plate, to thereby separate said plate into a plurality of electrically conductive elongated substantially rectangular shaped strips, defining said electrically conductive elements, each strip being electrically connected to any other strip through a single conductive path without a return path therebetween, the strips having di-mensions whereby the largest substantially square area on the conductive surface of any strip is smaller than the total conductive surface area of said plate by a factor n, where n is not less than 10.
4. The improvement as described in Claim 3 wherein n is not less than 100.
5. The improvement as described in Claim 1 wherein said outer elec-trode means comprises a plurality of individual electrically conductive metal plates, each of said plates being electrically connected to any other plate through a single electrically conductive path, with any substantially square area on any of said metal plates being significantly smaller than the total surface area of said metal plates, by a factor not less than 10.
6. The improvement as described in Claim 5 wherein the substantially square or circular area on any of said metal plates is smaller than the total area of said metal plates by a factor of not less than 100.
7. The improvement as described in Claim 5 wherein each of said metal plates is in the shape of an elongated rectangle.
8. The improvement as described in Claim 1 wherein said outer electrode means comprises an array of individual electrically conductive wires, each wire being electrically connected to any other wire through a single electri-cally conductive path, without a current return path therebetween, with the total conductive surface areas of said wires defining the area of the conduc-tive surface of said outer electrode means.
9. The improvement as described in Claim 1 wherein said pulse generat-ing means is powered by a source of power which is rechargeable by an external magnetic field adapted to induce power in said stimulator, and wherein any substantially square area on the surface of any of said elements is smaller than the total conductive surface area of said elements by a factor n, where n is not less than 5.
10. The improvement as described in Claim 9 wherein said outer elec-trode means is a plate of a biocompatible metal with a plurality of slots extending inwardly from at least one side of said metal plate, to thereby separate said plate into a plurality of electrically conductive elongated substantially rectangular shaped strips, defining said electrically conduc-tive elements, each strip being electrically connected to any other strip through a single conductive path without a return path therebetween, the strips having dimensions whereby the largest substantially square area on the conductive surface of any strip is smaller than the total conductive surface area of said plate by the factor n, where n is not less than 10.
11. The improvement as described in Claim 1 wherein said pulse generat-ing means is powered by a source of power in said stimulator which is re-chargeable by an external magnetic field adapted to induce power on the order of not less than 2 watts in said stimulator and wherein said outer electrode means is a plate of a biocompatible metal with a plurality of slots extending inwardly from at least one side of said metal plate, to thereby separate said plate into a plurality of electrically conductive elongated substantially rectangular shaped strips, defining said electrically conductive elements, each strip being electrically connected to any other strip through a single conductive path without a return path therebetween, the strips having di-mensions whereby the largest substantially square area on the conductive sur-face of any strip is smaller than the total conductive surface area of said plate by a factor n, where n is not less than 10.
12. The improvement as recited in Claim 11 wherein the total square area of the surface of said plate is not less than 2 square inches and n is not less than 100.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US653,463 | 1976-01-29 | ||
| US05/653,463 US4006748A (en) | 1976-01-29 | 1976-01-29 | Implantable unipolar pacemaker with improved outer electrode plate |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1085931A true CA1085931A (en) | 1980-09-16 |
Family
ID=24620992
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA269,779A Expired CA1085931A (en) | 1976-01-29 | 1977-01-14 | Implantable unipolar pacemaker with improved outer electrode plate |
Country Status (6)
| Country | Link |
|---|---|
| US (1) | US4006748A (en) |
| JP (1) | JPS52146087A (en) |
| CA (1) | CA1085931A (en) |
| DE (1) | DE2703629C2 (en) |
| FR (1) | FR2339408A1 (en) |
| IT (1) | IT1076105B (en) |
Families Citing this family (40)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4305115A (en) * | 1979-03-14 | 1981-12-08 | Harry H. Leveen | Electrostatic shield |
| US4310000A (en) * | 1980-01-23 | 1982-01-12 | Medtronic, Inc. | Implantable pulse generator having separate passive sensing reference electrode |
| US5090422A (en) * | 1990-04-19 | 1992-02-25 | Cardiac Pacemakers, Inc. | Implantable electrode pouch |
| US5230337A (en) * | 1990-06-06 | 1993-07-27 | Cardiac Pacemakers, Inc. | Process for implanting subcutaneous defibrillation electrodes |
| US5203348A (en) * | 1990-06-06 | 1993-04-20 | Cardiac Pacemakers, Inc. | Subcutaneous defibrillation electrodes |
| US5284151A (en) * | 1990-11-30 | 1994-02-08 | Terumo Kabushiki Kaisha | Electrocardiograph system |
| US5193539A (en) * | 1991-12-18 | 1993-03-16 | Alfred E. Mann Foundation For Scientific Research | Implantable microstimulator |
| US5358514A (en) * | 1991-12-18 | 1994-10-25 | Alfred E. Mann Foundation For Scientific Research | Implantable microdevice with self-attaching electrodes |
| US5193540A (en) * | 1991-12-18 | 1993-03-16 | Alfred E. Mann Foundation For Scientific Research | Structure and method of manufacture of an implantable microstimulator |
| US5366496A (en) * | 1993-04-01 | 1994-11-22 | Cardiac Pacemakers, Inc. | Subcutaneous shunted coil electrode |
| US5782891A (en) * | 1994-06-16 | 1998-07-21 | Medtronic, Inc. | Implantable ceramic enclosure for pacing, neurological, and other medical applications in the human body |
| US5833714A (en) * | 1996-01-18 | 1998-11-10 | Loeb; Gerald E. | Cochlear electrode array employing tantalum metal |
| US5645572A (en) * | 1996-03-12 | 1997-07-08 | Angeion Corporation | Implantable cardioverter defibrillator with slew rate limiting |
| US5817130A (en) * | 1996-05-03 | 1998-10-06 | Sulzer Intermedics Inc. | Implantable cardiac cardioverter/defibrillator with EMI suppression filter with independent ground connection |
| DE19645371C1 (en) * | 1996-10-23 | 1997-12-18 | Biotronik Mess & Therapieg | Implant, e.g. heart pacemaker, for mounting in human tissue |
| US5957958A (en) * | 1997-01-15 | 1999-09-28 | Advanced Bionics Corporation | Implantable electrode arrays |
| US6164284A (en) * | 1997-02-26 | 2000-12-26 | Schulman; Joseph H. | System of implantable devices for monitoring and/or affecting body parameters |
| EP1424098B1 (en) * | 1997-08-01 | 2008-12-03 | Alfred E. Mann Foundation For Scientific Research | Implantable device with improved battery recharging and powering configuration |
| AU753694B2 (en) * | 1997-08-01 | 2002-10-24 | Advanced Bionics Corporation | Implantable device with improved battery recharging and powering configuration |
| US6308101B1 (en) | 1998-07-31 | 2001-10-23 | Advanced Bionics Corporation | Fully implantable cochlear implant system |
| US7020525B1 (en) * | 2002-06-14 | 2006-03-28 | Pacesetter, Inc. | Flexible electrical interconnect for an implantable medical device |
| US7349741B2 (en) * | 2002-10-11 | 2008-03-25 | Advanced Bionics, Llc | Cochlear implant sound processor with permanently integrated replenishable power source |
| WO2004052456A1 (en) | 2002-12-09 | 2004-06-24 | Medtronic, Inc. | Modular implantable medical device |
| US7596408B2 (en) * | 2002-12-09 | 2009-09-29 | Medtronic, Inc. | Implantable medical device with anti-infection agent |
| US8270647B2 (en) | 2003-05-08 | 2012-09-18 | Advanced Bionics, Llc | Modular speech processor headpiece |
| US8811643B2 (en) * | 2003-05-08 | 2014-08-19 | Advanced Bionics | Integrated cochlear implant headpiece |
| US7599508B1 (en) | 2003-05-08 | 2009-10-06 | Advanced Bionics, Llc | Listening device cap |
| US7263401B2 (en) * | 2003-05-16 | 2007-08-28 | Medtronic, Inc. | Implantable medical device with a nonhermetic battery |
| US7317947B2 (en) * | 2003-05-16 | 2008-01-08 | Medtronic, Inc. | Headset recharger for cranially implantable medical devices |
| US7729766B2 (en) | 2003-10-02 | 2010-06-01 | Medtronic, Inc. | Circuit board construction for handheld programmer |
| US7596399B2 (en) * | 2004-04-29 | 2009-09-29 | Medtronic, Inc | Implantation of implantable medical device |
| US20050245984A1 (en) * | 2004-04-30 | 2005-11-03 | Medtronic, Inc. | Implantable medical device with lubricious material |
| US7191013B1 (en) | 2004-11-08 | 2007-03-13 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Hand held device for wireless powering and interrogation of biomems sensors and actuators |
| US20070010862A1 (en) * | 2005-04-26 | 2007-01-11 | Thomas Osypka | Apparatus and method for providing an electrical field to a targeted area |
| US20070073286A1 (en) * | 2005-09-29 | 2007-03-29 | Dorin Panescu | Method and apparatus for an ocular procedure |
| US9084901B2 (en) | 2006-04-28 | 2015-07-21 | Medtronic, Inc. | Cranial implant |
| WO2008115383A2 (en) | 2007-03-19 | 2008-09-25 | Boston Scientific Neuromodulation Corporation | Methods and apparatus for fabricating leads with conductors and related flexible lead configurations |
| JP5568316B2 (en) | 2007-03-19 | 2014-08-06 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | Method for manipulating and making MRI / RF compatible leads and related leads |
| US9393432B2 (en) | 2008-10-31 | 2016-07-19 | Medtronic, Inc. | Non-hermetic direct current interconnect |
| US8326426B2 (en) | 2009-04-03 | 2012-12-04 | Enteromedics, Inc. | Implantable device with heat storage |
Family Cites Families (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3667477A (en) * | 1966-11-25 | 1972-06-06 | Canadian Patents Dev | Implantable vesical stimulator |
| US3606881A (en) * | 1970-02-20 | 1971-09-21 | Riley D Woodson | Conductive rubber electrode |
| US3735766A (en) * | 1971-04-19 | 1973-05-29 | Gen Electric | Optional unipolar-bipolar body organ stimulator |
| US3788329A (en) * | 1972-04-17 | 1974-01-29 | Medtronic Inc | Body implantable lead |
| DE2331499A1 (en) * | 1972-06-28 | 1974-01-17 | Univ Johns Hopkins | RECHARGEABLE PACEMAKER WITH AUTOMATIC BREAKS |
| DE2319054C3 (en) * | 1973-04-14 | 1980-03-06 | Hans Dr.Med. Stockholm Lagergren | Electrode arrangement |
| DE2334049C3 (en) * | 1973-07-04 | 1988-12-22 | Hans Dr Med Lagergren | ENDOCARD ELECTRODE ARRANGEMENT |
-
1976
- 1976-01-29 US US05/653,463 patent/US4006748A/en not_active Expired - Lifetime
-
1977
- 1977-01-14 CA CA269,779A patent/CA1085931A/en not_active Expired
- 1977-01-18 IT IT19419/77A patent/IT1076105B/en active
- 1977-01-27 FR FR7702308A patent/FR2339408A1/en active Granted
- 1977-01-28 JP JP859877A patent/JPS52146087A/en active Pending
- 1977-01-28 DE DE2703629A patent/DE2703629C2/en not_active Expired
Also Published As
| Publication number | Publication date |
|---|---|
| DE2703629A1 (en) | 1977-08-04 |
| DE2703629C2 (en) | 1986-11-06 |
| FR2339408B3 (en) | 1979-09-28 |
| FR2339408A1 (en) | 1977-08-26 |
| US4006748A (en) | 1977-02-08 |
| JPS52146087A (en) | 1977-12-05 |
| IT1076105B (en) | 1985-04-24 |
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