CA1100188A

CA1100188A - Detachable power source

Info

Publication number: CA1100188A
Application number: CA289,608A
Authority: CA
Inventors: Thomas L. Jirak
Original assignee: Medtronic Inc
Current assignee: Medtronic Inc
Priority date: 1976-10-27
Filing date: 1977-10-26
Publication date: 1981-04-28
Also published as: AU2986977A; DE2748006A1; US4119103A; FR2368944A1; NL7711727A; GB1582760A

Abstract

DETACHABLE POWER SOURCE

ABSTRACT
A pulsed energy coupling system for transfer-ring energy from a detachable power source to a pulse generator module of an electromedical device. Periodi-cally energy is transferred through coupling members to an energy storage device in the pulse generator module.
Leakage current losses between coupling members at dif-ferent electrical potentials is minimized by maintaining coupling members at the same potential during the time intervals between energy transfers. Energy transfers are triggered and effected either at independent, fixed intervals ox as energy necessary to power the pulse generator module is dissipated from the energy storage device.

Description

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BACKGROUND OF THE INVENTION
This invention relates to the field of implant-able electromedical devices. In particular, it relates to an implantable electromedical device having a replace-able power supply module.
Implantable electromedical devices such as cardiac pacemakers have been known and commercially used for many years. In time, the power supply depletes and the entire pacemaker system, consisting of a power supply module and electronic stimulating signal generating module, is xeplaced. There are several advantages to be obtained in simply replacing the depleted power supply. One is the cost savings in retaining the original signal gener-ating module~ Another is the convenience and minimization of risk which results from not ha~ing to disturb the im-planted signal generating module and its associated leads .
connected to the tissue to be stimulated. A third is flexibility in instrumentation aforded by replacing one power supply with another of a diferent type should the patient's requirements change.
While the general concept of a replaceable power supply for electromedical devices is not new, there is a significant barrier to its adaptation to the field of implantable electromedical devices. This barrier is the result of the hostile environment presented by electro-lytic body fluids. These conductive fluids inevitably infiltrate the junction between the power supply and signal generating modules, permitting current leakage from the power supply via the connector pins or other means for electrically joining the two modules. ~his

-2-current leakage substantially reduces the active life ~ d ~ <DJe~
of the device as-~Y~ e~.~s~-the connector pins.

SUMMARY OF THE INVENTION
The present invention overcomes this barrier not by eliminating exposure of the connecti.ng parts of the modules to body fluid but by reducing t:he time energy it transferred be-tween modules to a fraction of the time the signal generating module would conventiLonally draw energy during its implanted lifeO As a consequence 7 cur-rent leakage is proportionally reduced to an acceptable level since leakage only occurs during the time o energy transfer between modules. Corrosion of connecting-parts, a function of current leakage, is likewise substantially reduced to an acceptable level. Several embodiments of the invention have been devised, all utili:zing internal electronic means to limit energy transfer between the modules to a brief enough time to reduce current leakage substantially, yet sufficient to maintain the energy in the signal generating module at an operating level. In general, the power supply module contains an energy source (such as a battery) and energy transfer means for periodi-cally transferring energy to the signal generating module producing the stimulating signal. Located in either the .~: :
power supply module or the signal generating module, or both, lS electronic~circuitry for triggerin.g or activat-ing the energy transfer means to:allow sufficient trans-fer of energy in a short time to maint~in the signal generating circuitry at an operating level. The trig-gering circuitry may be an oscillator ~hich provides for .

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energy transfer at Eixed intervals, or a voltage sensing device located in the signal generating module that senses the level of energy in an energy storage device supplying the signal generating circuitry. A preferred embodiment, especially for cardiac pacemakers, is electronic means which activates the electronic switching means in response to generation of a tissue stimulating output signal or in response to an electrical signal received from the tissue to be stimulated, or both.
Thus, in accordance with the broadest aspect of the invention there is provided a body-implantable electromedical device of the type having elec-trical energy source means for developing electrical energy, generating means adapted to receive and responsive to electrical energy for periodically gene-rating a tissue stimulating signal, said genera~ing means having output means adopted to be coupled to electrode means for transmitting the stimulating sig-nal to body tissue, coupling means for detachably coupling said electrical energy source means to said generating means, and limiting means for reducing the leakage of electrical energy from said coupling means comprising: means for periodically transferring electrical energy from said electrical energy source means to said generating means.
BRIEF DESGRIPTION OF THE DRAWINGS
In the drawings: -Figure 1 is a pictorial view of an implantable device of this inven-tion with the power supply and signal generating modules separated to show ~he coupling mechanism;
Figure 2 is a circuit diagram showing the various electronic func-tions of a preferred embodiment of the invention;
Figure 3 is a composite of plots of three voltage waveforms that occur in the circuit depicted in Figure 3, Figure 4 is a circuit diagram of a second embodiment of the inven-tion; and Figure 5 is a circuit diagram of still another embodiment of the invention.
DESCRIPTION OF THE PREFERR_D EMBODIMENTS
Referring to Figure 1, an implantable device 10 of this invention is depicted comprising a power supply - 4a -module 12 and a signal generating module 14. The module 12 is cylindrically shaped to fit in cavity 16 o~ module 14. Extending outwardly from surface 18 o:E module 12 and perpendicular thereto are cylindricall~ shaped male pins 20, 22, and 24. Pin 20 is connected 1:o the energy source, and pins 22 and 24 are connected to the electronic switch which will be specifically described with respect to Figures 2 and 3, hereinafter. Module 12 is provided with a lip 26 and 0-ring 28 which fit into a complemen-tary annular shaped recess 30 in module 14. Located onthe opposite surface 19 of module 12 is a ta~ 32 to facil-itate gripping and removal of the module 12 from connec-tion with module 14.
Signal generating module 14 includes housing 34 containing the electronic circuitry for converting the power supplied by module 12 to a suitable stimulating sig-nal as is known in the art. Suitable circuitry includes the circuitry for producing a heart pacemakler pulse, such as the circuitry in the Medtronic~ Model 5950 Implantable -Bipolar Demand Pulse &enerator. Located in face 36 of cavity 16 are three female receptacles 38, 40 and 42 for receiving male pins 20, 22 and 24. In certain embodiments of the invention, such as that depicted in Figure 5, for example, only two connector pins and receptacles-, or their equivalent are needed. Housing 34 also incLudes a boot 44 providing a pair of apertures 46 and 48 i~or receiving conventionaI electrical leads 50 and 52, respectively.
In Figure 2, there is shown, part:Ly in block form, the electronic circuitry of a preerred embodiment of the invention. Inside the power source module 12 is .

the electrical energy source 54 which may consist of mer-cury, lithium, silver, nuclear or other power source. A
typical mercury power source, used in the preferred embod-iment, provides an output voltage of 5.4 volts. This electrical energy source supplies the signal generating module l4 wi-th energy, allowing the normal function of the pacemaker when the power source module 12 is connected to the signal generating module 14. The electrical con-tacts 20, 22 and 24 on module 12 mate with the correspond-ing contacts 38, 40 and 42, respectively, on the signal generating module 14.
Vpon connection of the power source module 12to the signal generating module 14, one terminal of elec-trical energy source 54 is connected by mated pins and receptacles, or contacts, 20/38.to one terminal of the energy~storage device, or capacitor, 56. The other ter-minal of the capacitor 56 is connected via diode 58 and .:
mated contacts 22/40 to the electronic switch, or trans- .
istor, 60. Energy, or current, from the electrical energy source 54 may transfer through diode 58 to charge capacitor 56 when transistor 60 is conductive. The inltial energy t~ransfer is enough to bring the charge on capacitor 56 to a level necessary for the pulse generator circuitry 62, cvn-nected in parallel with capacitor 56, to operate normally.
After a predetermined time, the electronic swikch 60 is rendered nonconductive and current is no longer supplied to the energ~ storage device 56. By limiting the power delivery duky ratio ko less than 20%, preferably 10~ or less, the amounk of Leakage current and corrosion that would~otherwise occur at the contacts is correspondingly ' .

limited. (Duty ratio is equal to 100% times the dura-tion of power delivery pulses divided by the period of power delivery pulsesO) Further limiting oi. leakage current may be obtained by the optional use of leakage current limiting resistor 64 which is connected across contac~s 20/38 and 22/40, bringing them bot1n to the same potential as source 54 less the emitter to collector drop in electronic switch transistor 60. The high resis-tance of resistor 64 limits current loss thereacross.
In addition, the device may be provided with a restart switch 66. .At the time of initial operational mating o~ modules 12 and 14, should electronic swi~ch 60 be opened before the minimum energy to power the pulse generator circuit 62 has been stored in the energy storage device 56, magnetic reed switch 66 can~be actu-ated by an external magnet (not shown~. This will pro-vide a bypass circuit directly between the energy source 54 and contacts 22/40 to allow initial transer of sufficient energy to energy storage device 56.
~fter the energy storage device 56 is: initially charged to a functioning voltage, further energization in the course of operation of the device is accomplished by the triggered transfer of energy fxom the power source module 12 to the signal generating module :L4 at pre-determined intervals in accordance with the above defined objects.
Referring again to Figure 2, whe~ the power supply module 12 is connected to the signa:l yenerating ~ module 14, and upon closure of sw~tch 66 i:E necessary, pulse generator circuit 62 will b2 eneLgized and capable of producing output pulses across t:erminals 50 and 52.
It is characteristic of demand p~lse generators, such as circuit 62, that an output pulse will be produced across terminals 50 and 52 only if the patient's heart is not beating at an acceptable rate. Since some patients' hearts may beat at acceptable rates for several hours or several days, the Olltput signal at terminals 50 and 52 cannot be relied upon to drive an energy transfer sys-tem. However, certain signals are available in typicaldemand pulse generators that occur each time the patient's heart beats, whether the beat is spontaneous or in response to an output pulse. For example, the pulse interval tim-ing capacitor in the Medtronic~ 5950 demand pulse gener-ator is reset each time a pace pulse is generated and each time the patient's heart beats naturally. A similar signal from pulse generator 62 is applied to the base of transistor 70 via resistor 68. 5ince this signal occurs each time the patient's heart beats, there is no danger of capacitor 56 losing its charge during a lon~
period of spontaneous cardiac activity. The collector of switching transistor 70 is connected by resistor 72 and contacts 20/38 to power sourGe 54. Resistor 72 (lOOK ohms) and transistor 70 comprise the elements of an electronic switch trigger respectively, connected by contacts 24/42 and capacitor 74 to the base o~ trans-istor 60. Diode 76 and resistor 78 connect the base of transistor 60 to its emikter and to the low potential side of power source 54.

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When -the power supply module 12 and pulse gen-erator module 14 are mated with capacitor 74 discharge current will flow from the positive terminal of electri-cal energy source 54 across contacts 20/38 through res-istor 72 to mated contacts 24/42. Negligible current will flow into the pulse generator circuit 62 because transistor 60 will be nonconductive at this time. Low capacitance (0.05 microfarad) capacitor 74 will, how-ever, begin charging by the current passing through resistor 72. The anode of the diode 76 is connected to resistor 78, the emitter of transistor 60; and the negative terminal of the electrical energy source 54.
The capacitor 74 charging current will be blocked by diode 76 and flow through resistor 78 and into -the base of transistor 60. Registor 78 is chosen so that it is very large in value (lOK ohmsl compared to the input impedance of transistor 60. l'herefore, most of the capacitor charging current will return to the negative terminal of the electrical energy source 54 through~the base of transistor 60. ~en enough current flows into the base oE transistor 60 it will turn on and conduct current between its collector and emitter terminals.
Since the collector of transistor 60 is connected to mated contacts 22/40, these contacts will be effectively ; short circuited ko the negative terminal of the electri-cal energy source 54. With transistor 60 kurned on, currenk can pass from the positive terminal of the electrical energy source 54 through contacts 20/38 to high capacity storage device 56 (22 microfarads). The anode of diode 58 lS connected to capacitor 56 and ~9--the cathode of diode 58 is connected to contacts 22/40. Diode 58 completes the charging current path between capacitor 56 and electrical energy source 54. The capacitor 56 will continue to charge through transistor 60 as long as capacitor 74 continues to charge through resistor 72. But, onGe capacitor 74 has become fully charged, the base current for transistor 60 will be reduced and it will cease conducting current between its collector and emitter termi-nals. Therefore, the RC charge time of capacitor 74 will determine the time period of energy transfer from power supply module 12 to signal generating module 14.
~e.nde~æd 10 ~ After ~ransistor 60 has been ~e~e~ed non-conductive, or turned off~
current no longer passes from the positive terminal of electrical energy source 54 through contacts 20/38 to capacitor 56. Capacitor 56 will now supply energy to the pulse generator circuit 64, and diode 58 now presents a high impedance current path to the negative terminal o power source 54. Leakage current resistor 64 remains connected across contacts 20/38 and 22/40 to ensure that both contacts remain at approximately the same positive ]?otential to reduce leakage current and contact corrosion. Any current leakage resulting from a residual potential difference between the contact 20/38 and 22/40 upon cut-off of transistor 60 will flow through the resistor 64, rather than between the contacts. Diode 58 also presents a high impedance between the positive poten-tial and the output terminal 52.
~y choosing transistor 60 with the proper gain and the proper values for capacitor 74 and resistor 72, enough energy is stored on capacitor 56 to power the pulse generator circuit 62 ~mtil the next ~riggered inter-module pulsed energy transfer takes place. If the stimulator signal circuitry 62 is that employed in a cardiac pacemaker of the demand type, a trigger pulse can be derived from either of two events.
One event occurs when the demand pacemaker produces a stimulating pulse and another occurs when a natural heart beat is sensed. In either case, the trigger pulse conducted to the base of transistor 70 ~ill turn it on, discharging capacitor 74 through its emitter to collector path and to the low potential terminal of capacitor 56. After transistor 70 turns o~f, capacitor 74 will have been almost fully discharged, and it can begin to charge again through resistor 72. As described before, this changing current will turn transistor 60 on, and energy will be transferred from the electrical energy source 54 into capacitor 56. Capacitor 56 will continue to charge until capacitor 74 becomes fully charged and transistor 60 turns off.
The ratio of transistor 60 on time to off time can be determined by the values of capacitor 74 and resistor 70. By proper choice of thesP ~alues, leakage current and corrosion rates at the electrical contacts can easily be reduced five or tenfold.
It is important to note that the system des-cribed a~ove may be self-starting on condition that capacitor 74 is completely discharged beEore the power : supply module 12 and signal generating module 14 are mated. If, ~or some reason capacitor 74 is not com-pletely discharged, transistor 60 would not be turned on. As a precaution, there~ore, the normally open magnetic reed switch 66 can be closed by placing a magnet ove.r the implanted device to complete the chang-ing path of capacitor 56.
Figure 3 is a plot of three voltage waveforms that occur in the device having the electronic circuitry of Figure 2. The first waveform, plot A, is the volt-age waveform over time that exists across the capacitor 56. The second waveform, plot B, is the voltage wave-foxm over a corresponding time period between the base and emitter of transistor 70. The third waveform, plo-t C, is the waveform over the corresponding time period of the voltage across capac~itor 74.
Upon initial mating of modules 12 and 14 at time 0 in Figure 3, the following circuit paths exist:
tl.) positive terminal of battery 54 to contacts 20/38 to resistor 72 to contacts 24/4Z to capacitor 74 to base-emitter junction of transistor 60 to the negative termlnal of battery 54; and (2.) positive terminal of battery 54, to contacts 20/38, to capacitor 56 to . dioae 58, to contacts 22/40, to collector-emitter of transistor 60, and then to the negative terminal of battery 54. The second current path causes capacitor ~56 to charge to Vl as.shown in plot A,~and the voltage on capacitor~56 will, if circuit element values have : been chosen properly, remain above a minimum voltage, V min, necessary to operate pulse genexa~or circuit : 62 over the period T~ Energy will be transferred from the:power~supply module 12 to module 14 ~o a time t determined by the time it takes capacitor 74 to charge ~- ; to VB60, approxi.mately the voltage of battery 54, ~ thereby turning transistor 60 off. In other words, ,, t -~ is related to the RC time constant oE re,istor 72 and capacitor 74.
A~ter initial mating, the pulse generator cir-cuitry will be capable of operation~ Two possibilities can then occur either a natural heartbeat is sensed by the pacemaker, or the pacemaker applies a pulse to the heart. In either case, the pulse in plot :B is applied to the base of transistor 70 closing the following current path: capacitor 74 to contacts 24/42, to collector-emitter of transistor 70, to diode 58, to contacts 22/40, to the collector-emitter of transistor 60, and the terminal of battery 54, thereby nearly com-pletely discharging the capacitor 74. This low resis-tance path causes capacitor 74 to discha.rge quickly andG~
again allows transistor ~ to condu~ct and further charge capacitor 56 in the time T. Capacitor 9~2 then succes~
sively charges to higher and higher voltagls levels depicted in plot A, levels that are well a]~ove the min-imum operating voltage level V min for puI~3e generator circuit 62. The time between waveforms in plot B is q.'.
The energy transfer across connec.tor pins 2'0/38 and 22/40 (plot C) occurs for lO0 x t/. percent of the time, limiting leakage curren~ to that percent of the .
time. Preferably, t should be l/5 or less of T, most preferably l/10 or less.
In the event that the capacitor 56 is not charged or maintained above V min, it may be necessary to close switch 66 to fully charge capacitcir 66 to commence operation o~ the pulse generator 62.

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Although one form of energy transfer circuit is depicted in Figure 2, it will be recognized that several other means may be devised to effect the energy transfer. Another means for accomplishing predekermined intermodule energy transfer may be circuitry responsive to the amount of energy stored in ener~y storage device 56, such means causing transfer of energy from module 12 to module 14 only when the energy level to device 56 is reduced to a predetermined level. Such means would sense this reduction and close electronic switch 60 to provide the requisite e~ergy transfer as described above.
Figure 4 depicts how a voltage sensor circuit 80 may be added to the pulse generator module 14 to modify the pulse generator so that intermodule energy transfer is responsive to the energy level in the energy storage device 56~ In thls embodlment, transistor 70 does not conduct and discharge capacitor 74 unless the~
storage capacitor 56 has discharged to some predetermined value~ The voltage sensor circuit 80 is inserted be-tween resistor 68 and transistor 70 of the embodiment depicted in Figure 1. The combined cir~uit operates in ;`~
~he same manner as the embodiment of Figure 1 when the modules are initially mated~ When pulse generator 62 is operating, eithe~ a naturally occurrin~ heartbeat or a pace output pulse will cause an output pulse from pulse generator 62 that will be coupled via resistor 68 to turn-on transistor 84 ~just as transistor 70 was turned on in the embodiment of Figure 1). Transistor 84 will conduct, putting the full capacitor 56 voltage ' :

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across the voltage divider formed by resi.stors 88 and 96 t as well as bias diode 94 into conduction via resis-tor 92. If the capacitor 56 voltage is above a pre-determined threshold, the voltage divider formed by resistors 88 and 96 will bias the emitter of transistor 82 negative with respect to its base (the voltage at the base of transistor 82 is determined by the forward drop of diode 94, a LED having a typical forward drop of one and one-half volts). If the emitter of tran.sistor 82 is biased negatively with respect to its bas,e~ the tran-sistor 82 is said to be cut off and will not deliver a pulse to the base of transistor 70. Consequently, no intermodule energy transfer will take place.. If, how-ever, the voltage on capacitor 56 has fallerl below the predetermined threshold, the voltage delivered to the emitter of transistor 82 by the voltage divider action of resistors 88 and g6 will be insufficient to cut of~
transistor 82. Under these conditions, transistor 82 will conduct, delivering a pulse to the base of trans-istor 70. Transistor 70 will then trigger an inter-module energy transfer in the same manner as it did in the embodiment shown in Figure 1. Capacitor 90 in the voltage sensor 80 circuit is used to filter the switch-ing noise pulses generated bv transistor 84 and keep them from turning on transistor B2 unless t]he voltage on capacitor 56 has fallen below the predetermined threshold. Thus, the voltage sensor 80 blocks pulse generator circuit 62 pulses from turning on transistor 70 and triggering intermodule energy transfers unless the voltage of across capacitor 56 has fallen below -some predetermined threshold. Once the voltage on capacitor 56 has fallen below the predetermined thresh-old, voltage sensor 80 passes the trigger pulses until the capacitor 56 voltage has risen above the threshold.
Since the voltage sensor circuit is turned on only during each pulse generator 62 energy transfer trigger pulse, it does not consume an appreciable amount of energy. Since energy transfer is not trigc~ered unless it is needed the amount of exposure to corrosion of the coupling pins 38, 40, and 42 is also reduced.
Referring now to Figure 5, there is shown a further embodiment of the charge transfer circuitry of the present invention. In this embodiment" an oscil-lator 84 located in power supply module 12 is provided, eliminating the need for contacts 24/42, the associated circuitry and the restar~ switch 66 shown in preceding embodiments~ A suitable oscillator 94 may be one of a variety of askable oscilla-tors having a repetition rate of about 75 pulses per minute, and a pulse width of from 50 to 2~0 milliseconds. Each time the oscillator produces a pulse, the transistor 60 is thereby rendered conductive to close the charge path for capacitor 56 for the pulse width deviation.
The disclosure and description heretofore of three embodiments of the invention has been by way of illustration and not of limitation of the wide scope of the invention and est~blishes that man~ other embod-iments of the present invention are possible. It is therefore to be understood, that all modifications and variations on the invention oacurring to those skilled -16~

in the art are intended to be included within the scope of the appended claims.

:~ .

Claims

THE EMBODIMENTS OF THE INVENTION IN WHICH AN EXCLUSIVE
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:

1. A body-implantable electromedical device of the type having electrical energy source means for developing electrical energy, generating means adapted to receive and responsive to electrical energy for periodically generating a tissue stimu-lating signal, said generating means having output means adopted to be coupled to electrode means for transmitting the stimulat-ing signal to body tissue, coupling means for detachably coupling said electrical energy source means to said generating means, and limiting means for reducing the leakage of electrical energy from said coupling means comprising: means for periodically transferring electrical energy from said electrical energy source means to said generating means.

2. The device of claim 1 wherein said transfer means further comprises: trigger means for periodically providing a trigger signal; and circuit means responsive two the trigger sig-nal for conducting electrical energy through said coupling means.

3. The device of claim 1 wherein said generating means further comprises electrical energy storage means for receiving and storing electrical energy transferred from said electrical energy source means by said transfer means.

4. The device of claim 3 wherein said transfer means further comprises: reference potential means for establishing a reference electrical potential; comparison means responsive to the reference electrical potential and the electrical potential of the electrical energy stored by said electrical energy stor-age means for developing a trigger signal when the stored electrical potential falls below the reference, electrical potential; and circuit means responsive to the trigger signal for conducting electrical energy through said coupling means.

5. The device of claim 2 wherein said circuit means further comprises: timing means responsive to the trigger sig-nal for rendering said circuit means conductive for a pre-determined duration.

6. The device of claim 2 wherein said trigger means further comprises: oscillator circuit means responsive to elec-trical energy from said electrical energy source means for developing the trigger signal at regular, fixed time intervals.

7. The device of claim 2 wherein said trigger means further comprises means responsive to the generation of a tissue stimulating signal by said generating means for producing a corresponding trigger signal.

8. The device of claim 2 further comprising sensing means responsive to electrical signals developed by a body organ for resetting the operation of said generating means for a predeter-mined time period.

9. The device of claim 8 wherein said trigger means further comprises means responsive to the reset of said genera-ting means by said sensing means for developing a corresponding trigger signal.

10. A body-implacable electromedical device of the type having electrical energy source means for developing electrical energy, generating means adapted to receive and responsive to electrical energy for generating a tissue stimulating signal, said generating means having output means adapted to be coupled to electrode means for transmitting the stimulating signal to body tissue, at least two coupling means for detachably coupling said electrical energy source means to said generating means, and means for reducing the leakage of electrical energy from said coupling means comprising: means for periodically trans-ferring electrical energy from said electrical energy source means to said generating means; and means for maintaining the coupling means at the same electrical potential in the time intervals between periodic energy transfers thereby preventing the leakage of electrical energy between said coupling means.

11. The device of claim 10 wherein said transfer means further comprises: trigger means for periodically providing a trigger signal; and circuit means responsive to the trigger signal for conducting electrical energy through said coupling means.

12. The device of claim 10 wherein said generating means further comprises electrical energy storage means for receiving and storing electrical energy transferred from said electrical energy source means by said transfer means.

13. The device of claim 12 wherein said transfer means further comprises: reference potential means for establishing a reference electrical potential; and comparison means respon-sive to the reference electrical potential and the electrical potential of the electrical energy stored by said electrical storage means for developing a trigger signal when the stored electrical potential falls below the reference electrical potential; and circuit means responsive to the trigger signal for periodically conducting electrical energy through said coupling means.

14. The device of claim 11 wherein said circuit means further comprises: timing means responsive to the trigger sig-nal for rendering said circuit means conductive for a pre-determined duration.

15. The device of claim 11 wherein said trigger means further comprises: oscillator circuit means responsive to electrical energy from said electrical energy source means for developing the trigger signal at regular, fixed time intervals.

16. The device of claim 11 wherein said trigger means further comprises means responsive to the generation of a tissue stimulating signal by said generating means for producing a corresponding trigger signal.

17. The device of claim 11 further comprising sensing means responsive to electrical signals developed by a body organ for resetting the operation of said generating means for a predetermined time period.

18. The device of claim 17 wherein said trigger means further comprises means responsive to the reset of said genera-ting means by said sensing means for developing a corresponding trigger signal.