US3656487A - Electronic demand heart pacemaker with different pacing and standby rates - Google Patents

Electronic demand heart pacemaker with different pacing and standby rates Download PDF

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US3656487A
US3656487A US1178A US3656487DA US3656487A US 3656487 A US3656487 A US 3656487A US 1178 A US1178 A US 1178A US 3656487D A US3656487D A US 3656487DA US 3656487 A US3656487 A US 3656487A
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capacitor
pulse generator
resistor
pulse
sensing
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David H Gobeli
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Medtronic Inc
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Medtronic Inc
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential

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  • ABSTRACT A demand type heart pacer which provides electronically generated stimulating pulses to the heart at a first frequency in the continued absence of natural heartbeats, but which inhibits output pulses once the natural heart rate exceeds the first frequency, and allows the heart to beat naturally at any rate above a second, lower frequency before again providing stimulating pulses, thereby creating a different standby frequency.
  • the pacer also reverts to a third frequency in a non-demand type operation in the presence of an interfering electrical noise pattern.
  • This invention is concerned with electronic heart pacing apparatus, and in particular a demand type heart pacer.
  • Demand pacers are known in the art to be the type of pacer which provides electrical pulses to stimulate the heart only in the absence of normal heartbeats.
  • Prior art demand pacers generate pulses at a fixed frequency, the generated pulses being prevented if a natural heartbeat appeared during the period between generated pulses.
  • the heart monitoring pacer it would obviously be advantageous for the heart monitoring pacer to be able to wait a longer period of time than that provided by its normal pulse generation frequency, once a natural heartbeat has occurred, to be certain that it does not provide an unnecessary external pulse.
  • the heart monitoring pacer must be certain not to allow the heartbeat rate to fall below a minimum frequency.
  • the apparatus of this invention provides, with novel circuitry, the advantages described above, and in addition provides circuitry for eliminating dangers due to continuous external noise electrical signals which may enter the electrical system of the demand pacer.
  • the apparatus of this invention comprises a demand pacer having a pulse generator and an amplifier connected to the heart through a pair of electrodes.
  • the pulse generator provides controlled pulses to the heart through the electrodes, while the amplifier senses signals from the heart through the electrodes, for controlling the pulse generator.
  • the normal frequency of the pulse generator is controlled by apparatus including the charging time, of acapacitor.
  • further apparatus including another capacitor is connected between the pulse generator and the sensing amplifier. This second capacitor is selectively connected in parallel with the pulse generator frequency determining capacitor on occurrence of a natural heartbeat, and thus increases the charging time of the capacitance for the pulse generator frequency determining apparatus, to thus lower the frequency of pulses generated.
  • the second capacitor is not connected to the pulse frequency determining capacitor, and the pulse generator runs at its fixed higher frequency.
  • the further apparatus is connected to the output of the pulse generator such that the second capacitor is selectively charged during each stimulating pulse to the heart.
  • the second capacitor is connected to the pulse generator frequency determining capacitor so as to add its charge to that of the power supply and thus decrease the charging time, to increase the frequency of the pulse generator in the absence of a natural heartbeat.
  • the demand pacer apparatus of this invention will proceed to supply pulses to the heart at a normal pacing rate of a first frequency until it senses an ectopic beat, after which it will wait a longer period than the normal pacing frequency period before it pulses again. If no further ectopic beats are sensed it will return to the normal pacing rate after the next generated pulse. It is important to note that with an irregular heart rate causing many ectopic beats, the apparatus of this invention will be alternately inhibited and then pacing. However, the minimum average pacing rate must be the standby pacing rate. Further, any sinus rhythm above the standby rate completely inhibits the unit.
  • the apparatus of this invention will allow normal sinus rhythm to control at a rate below or above its own normal pacing frequency, yet provides a minimum rate determined by the standby frequency unless repetitive interference is present.
  • the pacer circuitry causes the device to revert to asynchronous operation at a rate somewhat lower than the standby rate.
  • FIG. 1 is a schematic diagram showing the electronic circuitry of a first embodiment of the apparatus of this invention.
  • FIG. 2 is a variation of a portion of the schematic of FIG. 1 showing a second embodiment of this invention.
  • transistors 19 and 20 each having an emitter connected through a resistor 23 to negative bus 13.
  • the collector of transistor 19 is connected to positive bus 12, while the base of transistor 19 is connected through a resistor 21 to bus 12 and through a resistor 22 to bus 13.
  • the collector of transistor 20 is connected through a resistor 24 to bus 12, and through a capacitor 25 to bus 12.
  • a transistor 26 has an emitter connected directly to bus 12, a base connected to the collector of transistor 20, and a collector connected to a junction 10.
  • Junction 10 is connected through a serial combination of a resistor 27 and a capacitor 28 to the base of transistor 20.
  • a transistor 30 has an emitter connected to negative bus 13, a collector connected through a resistor 31 to the base of transistor 20, and a base connected through a serial combination of a resistor 33 and a diode 32 to junction 10. Junction 10 is also connected through a resistor 29 to the base of transistor 15.
  • the collector of transistor 30 is also connected to a variable resistor 36.
  • the wiper arm of resistor 36 is connected through a resistor 37 to positive bus 12.
  • the collector of transistor 30 is connected to negative bus 13 through each of a pair of capacitors 34 and 35.
  • a transistor 40 has an emitter connected to negative bus 13, a collector connected through a diode 38 to the collector of transistor 30, and a base connected through the serial combination of a diode 41 and a resistor 42 to negative bus 13.
  • the collector of transistor 40 is also connected through a capacitor 39 to bus 13, while the base of transistor 40 is also connected to bus 13 through a resistor 43.
  • a transistor 48 has an emitter connected to positive bus 12, and a collector connected through a resistor 46 to negative bus 13. The collector of transistor 48 is also connected to negative bus 13 through a capacitor 45, and is connected to the base of transistor 40 through a capacitor 44.
  • a resistor 51 a capacitor 52 and a resistor 53 are serially connected between positive bus 12 and negative bus 13.
  • a field effect transistor 55 has a gate connected to a junction between capacitor 52 and resistor 53, a source connected to positive bus 12, and a drain connected to the base of transistor 48.
  • a diode 57 is connected between the source and drain of field effect transistor 55.
  • a transistor 60 has an emitter connected to positive bus 12 through each of a resistor 61 and a capacitor 62.
  • the collector of transistor 60 is connected through a resistor 63 to negative bus 13, and through a capacitor 58 to the base of transistor 48.
  • the base of transistor 60 is connected through a resistor 66 to positive bus 12.
  • a field effect transistor 65 has a drain connected to the base of transistor 60, and a source connected to negative bus 13 through each of a resistor 67 and a capacitor 68.
  • the gate of field effect transistor 65 is connected to negative bus 13 through each of a pair of oppositely poled diodes 71 and 72.
  • Electrode 75 is connected through the serial combination of a capacitor 76 and a resistor 78 to the gate of field effect transistor 65
  • a resistor 77 is connected from a point intermediate capacitor 76 and resistor '78 to negative bus 13.
  • Another electrode 80 is connected to negative bus 13.
  • junction is connected through a diode 79 to the junction between capacitor 52 and resistor 53.
  • the pulse generator can be generally described as including transistors 19, 20, 26 and 30, along with their associated components including in particular capacitors 28 and 35.
  • Transistor comprises the output transistor.
  • capacitor 74 will have discharged for a period of time determined by the pulse generator. With the pulse generator off during the period between pulses, transistor 15 will be off, and capacitor 74 will recharge through the path comprising battery 11, bus line 12, resistor 16, capacitor 74 itself, the heart through electrodes 75 and 80, and through bus line 13 to battery 11. This will cause the plate of capacitor 74 connected to the collector of transistor 15 to be positive with respect to its opposite plate.
  • Capacitor 35 is charged through variable resistor 36 and resistor 37.
  • Capacitor 39 will have charged at some previous time, and will not have discharged during the last pulse in the absence of a natural heartbeat, for reasons more fully described below, capacitor 39 will have no significant affect on the time for the charge of capacitor 35.
  • Capacitor 34 is selected to be an RF bypass capacitor to prevent turn-on of the pulse generator from stray pickup, and will, therefore, be sufficiently smaller than capacitor 35 so as to be essentially ignored in considering the timing ofthe pulse generator.
  • Capacitor 25 is a bypass capacitor connected across resistor 24.
  • the positive potential at junction 10 will be felt through capacitor 28 to provide positive feedback to the base of transistor 20 to turn it on stronger and keep in on.
  • the positive potential at junction 10 will be felt through diode 32 and resistor 33 on the base of transistor to turn it on, causing the discharge of capacitor 35.
  • the positive potential at junction 10 will be felt through resistor 29 on the base of output transistor 15 to turn it on, causing capacitor 74 to discharge through the collector-emitter path of transistor 15, and through electrode 80 to the heart and back through electrode 75 to capacitor 74.
  • the positive potential at junction 10 will be felt through diode 79 to cause an inhibit signal to prevent the preamplifier from sensing the pacemaker pulse as though it were a natural heartbeat, or R wave, in a manner to be more fully described below.
  • transistor 30 will quickly discharge capacitor 35, and transistor 30 will stay on until the positive potential disappears at junction 10.
  • the positive potential to junction 10 will remain as long as transistor 26 is on, which is determined by the on time of transistor 20.
  • Transistor 20 will remain on for a period of time determined by the charge time of capacitor 28, through which the positive potential at junction 10 is felt. Therefore, the charge time of capacitor 28 determines the on time of the pulse generator, thus determining the on time of output transistor 15 and the output pulse width.
  • capacitor 28 When capacitor 28 has charged sufficiently so that the potential on the base of transistor 20 is no longer sufiicient to keep it on, transistor 20 will turn off to turn off transistor 26 and remove the positive potential from junction 10, thus causing the tumoff of transistor 30 and output transistor 15. Capacitors 74 and 35 will then again begin to charge in the manner described above, and the pulse generator cycle will be repeated, provided no natural heartbeat occurs, as described below.
  • the amplifier of the pacer of HO. 1 comprises field effect transistor 65, transistors 60 and 48, and their associated circuit components.
  • Resistors 46, 61, 63, 66 and 67 are bias resistors for their respective transistors.
  • Capacitors 62 and 68 are bypass capacitors.
  • Field effect transistor 65, and transistor 60, are so biased as to be class A amplifiers and to amplify input signals of either polarity.
  • Resistor 77 is a DC bias reference for the gate of field effect transistor 65.
  • Resistor 78 is a limiting resistor and works with diodes 71 and 72 to limit the input voltage to the gate of field effect transistor 65 When a pulse of either polarity appears at electrode 75, it will be felt through capacitor 76 and resistor 78 across the parallel combination diodes 71 and 72. As field effect transistor 65 is class A biased, a pulse of either polarity, limited by diodes 71 and 72 along with resistor 78, will be amplified by it. This will cause a change of potential on the drain electrode of field effect transistor 65, which will in turn be felt on the base of class A amplifier connected transistor 60 and further amplified by it.
  • Transistor 60 will then have a change of potential at its collector, which will be differentiated and passed through capacitor 58 to the base of transistor 48.
  • transistor 48 is class C connected, and will turn on when the negative portion of the differentiated signal through capacitor 58 reaches the base of transistor 48.
  • Diode 57 will prevent capacitor 58 from eventually charging due to a series of negative going potential changes at the collector of transistor 60.
  • the turn-on of transistor 48 causes its collector to go positive.
  • This positive signal passes through a reversion to fixed rate circuit which will be more fully described below. For the present, it is sufficient to recognize that the positive signal will pass through capacitor 44 to the base of transistor 40 to turn it on.
  • the turn-on of transistor 40 causes an interruption of the normal charge cycle of capacitor 35 and changes the pacer to its standby or sentinel frequency which is lower than that of the normal frequency of the pulse generator. This circuitry will also be more fully described below.
  • the above-described amplifier has a refractory period primarily caused by bypass capacitors 62 and 68. These capacitors are chosen to be of a value so that they will charge during the presence of an input signal passing through the amplifier, and the discharge time of capacitors 62 and 68 will constitute a refractory period for the amplifier. The capacitors must be chosen with care as they will also affect the gain of the amplifier.
  • an inhibit circuit which comprises field effect transistor 55 and its associated components resistor 51, capacitor 52 and resistor 53.
  • the positive potential at junction 10 which turns on output transistor 15 will also be felt through diode 79 to the inhibit circuit. This positive potential will be felt on the gate of field effect transistor 55 to raise the gate potential to substantially that of the source potential of field effect transistor 55, thus removing the reverse bias and turning on field effect transistor 55.
  • Capacitor 52 will be discharged by the pulse appearing from junction through diode 79, and in recharging will keep a positive potential on the gate of field effect transistor 55 to keep it on for a period of time determined by the resistance present in the charging path of capacitor 52.
  • the pacer of FIG. 1 will prevent its normal pulse generator output frequency from being affected by sensing of its own output pulse.
  • the standby or lower frequency used when a heartbeat is detected becomes substantially the lowest frequency at which the heart will be allowed to beat in the absence of repetitive noise signals. That is, the standby frequency normally sets a lower limit of heartbeat rate, though the pacer as a whole will allow the heart to beat naturally between that lower standby rate and the higher normal pulse generator frequency rate.
  • the normal pulse generator frequency to be such as to provide pulses for an equivalent heart rate of 72 bpm. If the apparatus of FIG. 1 is pacing, as in complete heart block, and the heart produces an ectopic beat after a previous pacer pacemaker pulse and the refractory period of the amplifier, but before the next pacer pacemaker pulse, the pulse generator will be reset. The pacer pacemaker will then pulse again at a time after the ectopic beat determined by the standby rate. if the heart continues natural beating at a rate greater than the standby rate, the pulse generator of the pacer pacemaker will be prevented from providing further pulses.
  • the pacer pacemaker will again provide a pulse at the end of this period. Then, if no further natural heartbeats are sensed, the unit will pulse again at the normal pulse generator frequency of 72 bpm, until another natural heartbeat is sensed.
  • the apparatus of this invention after sensing a natural heartbeat, waits for a period of time longer than the normal pacing frequency before it provides another heart stimulating pulse. If no more natural heartbeats are sensed, the pacer returns immediately, and during the next period of time between pulses, to the normal pacing rate.
  • capacitor 35 when transistor 30 is turned on to discharge capacitor 35, diode 38 will prevent the discharge of capacitor 39. Thus in normal operation only capacitor 35 has a substantial affect on the timing for the pulse generator. However, when transistor 40 is turned on to discharge capacitor 39, capacitor 35 will also discharge through diode 38 and transistor 40 and the pulse generator timing cycle will be completely reset. Further, current flowing through resistors 36 and 37 will now be divided between capacitors 35 and 39 until such time as diode 38 becomes reverse biased by the charge on capacitor 39. As the capacitance is increased by the addition of capacitor 39, and as the amount of current available through resistors 36 and 37 remains essentially the same, it will obviously take longer for capacitor 35 to charge to the potential where it will turn on transistor 20 of the pulse generator as described above.
  • the pacer pulse generator will operate at the standby frequency. If a standby frequency period is completed without the appearance of a natural heartbeat, the pacer will provide a stimulating pulse and immediately return to the normal pacing frequency, provided no further natural heartbeats appear.
  • the apparatus of this invention also includes circuitry for automatically reverting to asynchronous operation at a third frequency of the pulse generator different from either the first or second frequencies when it is subjected to interference from electrical signals of a repetitive nature.
  • circuitry for automatically reverting to asynchronous operation at a third frequency of the pulse generator different from either the first or second frequencies when it is subjected to interference from electrical signals of a repetitive nature To activate the reversion circuitry, such repetitive noise signals must have a repetition rate in excess of a designed minimum rate greater than the upper limit of normal heartbeat rates.
  • this circuitry comprises diode 41, resistor 42 and resistor 43 as combined with coupling capacitor 44. The refractory period of the amplifier contributes to determination of the pulse generator frequency in the presence of such interference.
  • capacitor 44 will charge with the plate connected to the collector of transistor 48 being positive and the other plate negative. This positive charge facing the source of the sine waves will eventually block out further positive portions of the sine wave and thereafter prevent the turnon of transistor 40.
  • capacitor 4 will have sufficient time to discharge through resistor 4-3, to avoid blocking the next incident pulse and subsequent normally spaced heartbeat pulses.
  • the pulse generator of this invention is immediately reset to the standby period and begins charging to fire as soon as capacitor 44 is substantially fully charged.
  • a pulse is fired by the pulse generator it is sensed by the amplifier but blocked by the inhibit circuit. Sensing of the pacemaker pulse makes the amplifier block other signals for its refractory period, during which capacitors 35 and 39 begin charging at the standby rate and capacitor 44 discharges.
  • the recovery pulse of the amplifier is superimposed on the recovery pulse of the amplifier and causes portions of the pulse to have a magnitude sufiicient to rapidly and repetitively turn on transistors 48 and 40 until capacitor 44 becomes fully charged.
  • the pulse firing and double reset repeat so long as interference is present.
  • the pacer runs at a rate slower than either the normal rate or the standby rate and is not synchronized with natural heartbeats.
  • the pacer pulse repetition period in the presence of repetitive noise signals is approximately the sum of the standby period and the amplifier refractory period. For example, if the standby period is 1,000 ms and the refractory period is ISO ms, the pacer period in the presence of repetitive interference is about l,l50 ms or a rate of about 52 bpm.
  • This slowdown of the pacer accompanying its reversion to asynchronous operation in the presence of repetitive noise signals is very useful in testing the functioning of the unit after implantation. It can also be seen that the slowdown accompanying a reversion to asynchronous operation can be achieved in a demand pacer without the standby rate feature in a similar manner by double reset of the simpler timing circuit used in such devices.
  • FIG. 2 there is shown a portion of the schematic of FIG. 1 with necessary changes pertaining to a second embodiment of the invention.
  • those circuit elements which are the same as in FIG. 1 bear the same number.
  • FIG. 2 there is again shown the pulse generator generally described as including transistors 19, 20, 26 and 30, along with their associated components.
  • Transistor again comprises the output transistor.
  • junction 10 is connected to the base of transistor through a capacitor 100, and to the base ofa transistor 110. It is thus apparent that the on time of the pulse generator will be determined by the charge time of capacitor 100 of FIG. 2, as opposed to capacitor 28 of FIG. I.
  • Transistor 110 has its collector connected directly to bus 12, while its emitter is connected to a capacitor 111 to bus 13.
  • a bypass capacitor 112 is connected across capacitor 111.
  • the collector of transistor 30 is connected through a resistor M4 to bus l2, and through a resistor 113 to the emitter of transistor 110.
  • he collector of transistor 30 is also connected through a resistor 102 to the base of transistor 20, and through a capacitor 103 to bus 13.
  • a bypass capacitor 104 is connected across capacitor 103.
  • the base oftransistor 30 is connected (not shown) to receive an input signal from the sensing amplifier whenever a natural heartbeat occurs, for example with circuitry similar to that shown in FIG. 1.
  • the charge on capacitor 103 has built to a sufficiently positive level to turn on transistor 20.
  • the turn-on of transistor 20 will cause the turn-on of transistor 26 causing a positive voltage rise at junction 10.
  • This positive voltage rise will be felt at the base of transistor 15 to turn it on and cause capacitor 74 to discharge through the heart through terminals 75 and 80.
  • the positive pulse at junction 10 will also be felt through capacitor to keep transistor 20 and thus transistor 26 turned on. This voltage will be affective for the charge time of capacitor 100, which thus determines the output pulse width.
  • the positive pulse at junction 10 will also be felt through diode 32 and resistor 33 on the base of transistor 30 to turn it on and thus discharge capacitor 103 to prepare it for the next timing sequence.
  • the positive pulse at junction 10 will be felt on the base of transistor to turn it on causing capacitor 111 to charge.
  • Capacitor 103 will have been generally completely discharged by the turn-on of transistor 30, and will commence its normal charge through the path comprising positive bus 12, resistor 114, through capacitor 103 to negative bus 13.
  • transistor 110 was on during the generated output pulse
  • capacitor 111 will have received a charge.
  • the charge on capacitor 111 will discharge through the path comprising resistor 113, capacitor 103 and bus 13.
  • capacitor 103 received an additional charge from capacitor 111. This results in a faster charge time for capacitor 103 with a resulting increase in the frequency of the pulse generator. It is thus apparent that when there is a generated or stimulating output from the pulse generator, transistor 110 and capacitor 111 will operate to cause an increased generating frequency.
  • FIG. 2 operates to provide the same function as the apparatus of FIG. 1.
  • FIG. 1 provides a decrease in the pulse generator frequency in the presence of a natural heartbeat
  • FIG. 2 provides an increase in the pulse generator frequency when there is no natural heartbeat, both embodiments thus providing a stimulating pulse at a first frequency, and a standby rate of a lower frequency, as well as a minimum frequency.
  • Electrodes 75 and 80 are adapted to be connected directly to the heart muscle in one of several manners well known in the art, and are made of an electrically conductive material which is also substantially inert to body fluids and tissue.
  • resistor 36 is shown to be a variable resistor which may be used to vary the normal frequency of the pulse generator.
  • capacitor 39 may be a variable capacitor or comprises a plurality of capacitors which are selectively connected in the circuit by a manual switch or the like, to thus provide means for selecting the standby or sentinel frequency of the pacer.
  • the novel apparatus of this invention provides a demand type pacer having circuitry for providing heart stimulating pulses at first rate and a lower pulse generating or standby rate in the presence of a natural heartbeat, and having further circuitry to cause asynchronous operation at a third rate in the presence of external electrical noise of a periodic nature.
  • a demand type heart pacer including input and output means adapted to be connected to a heart, the input means connected to means for sensing natural heartbeats
  • the improvement comprising: pulse generator means connected to the output means and including timing circuit means operable to control output pulses from said generator means at a selected frequency; means connecting the means for sensing natural heartbeats to said pulse generator means for resetting said timing circuit means on the occurrence of a natural heartbeat; and further timing circuit means connected to said timing circuit means for changing the frequency of output pulses from said generator means for one pulse cycle following a pulse cycle in which a natural heartbeat occurs.
  • a demand heart pacemaker including power supply means, sensing means for detecting a natural heartbeat, pulse generator means for supplying pulses to stimulate a heartbeat and means for connecting the sensing means and generator means to a heart
  • the improvement comprising: resistor means and first capacitor means serially connected across the power supply means; said first capacitor means connected to the pulse generator means for controlling the frequency of pulses therefrom according to the charging time of said first capacitor means; and circuit means including second capacitor means connected to said first capacitor means for selectively changing the charge time of said first capacitor means for one pulse cycle following a pulse cycle in which the natural heartbeat occurs.
  • a demand type heart pacer including input and output means adapted to be connected to a heart, the input means connected to means for sensing natural heartbeats, the improvement comprising: pulse generator means connected to the output means and including timing circuit means operable to control output pulses from said generator means at a selected frequency; and further means connecting the means for sensing natural heartbeats to said pulse generator means for resetting said timing circuit means on the occurrence of a natural heartbeat and including further timing circuit means operably connected to said timing circuit means on the occurrence of a natural heartbeat for decreasing the frequency of output pulses from said generator means for one pulse cycle following a pulse cycle in which a natural heartbeat occurs.
  • said timing circuit means includes resistor means and capacitor means connected in an RC timing circuit; and said further timing circuit means includes further capacitor means and switch means for conmeeting said further capacitor means into said RC timing circuit.
  • said timing circuit means includes serially connected resistance means and capacitance means; and said further timing circuit means includes further capacitance means, means including diode means connecting said further capacitance means across said capacitance means, said diode means poled to prevent said further capacitance means from discharging into said capacitance means, and switch means connected across said further capacitance means and connected to said further means for discharging all said capacitance means on the occurrence of a natural heartbeat.
  • a demand heart pacer including power supply means, sensing means for detecting a natural heartbeat, pulse generator means for supplying pulses to stimulate a heartbeat and means for connecting the sensing means and generator means to a heart
  • the improvement comprising: resistor means and first capacitor means serially connected across the power supply means; said first capacitor means connected to the pulse generator means for controlling the frequency of pulses therefrom according to the charging time of said first capacitor means; and circuit means connected to the sensing means and to said first capacitor means and operable in response to the occurrence of a natural heartbeat for changing the charge time of said first capacitor means for one pulse cycle following a pulse cycle in which the natural heartbeat occurs.
  • circuit means comprises; second capacitor means; switch means connected between the sensing means and said first and second capacitor means for connecting said first and second capacitor means in parallel charging paths in response to the occurrence of a natural heartbeat for increasing the charging time of said first capacitor means.
  • noise responsive means for blocking repetitive noise signals from said circuit means comprising: capacitor means having an input plate connected to the sensing means and an output plate connected to said circuit means; a first discharge path for said capacitor means connected to said output plate and including serially connected diode means and resistor means, said diode means poled to pass current of a first polarity, said resistor means having a resistance value selected for generally fast discharge of said capacitor means; and a second discharge path for said capacitor means connected to said output plate and including further resistor means having a resistance value selected for generally slow discharge of said capacitor means for charging said capacitor means with repeated noise pulses of a second polarity at a frequency above that of the normal heartbeat range to block further of said noise pulses of the second polarity.
  • a demand pacer having input and output means adapted to be connected to a heart, pulse generator means connected to the output means and sensing means for detecting natural heartbeats connected to the input means, the improvement comprising: resistor means and first capacitor means connected in an RC timing circuit and to the pulse generator means for controlling the frequency of the pulse generator means according to the charge time of said first capacitor means; first switch means connected to said first capacitor means and to the pulse generator means, and actuated by an output pulse from the pulse generator means to discharge said first capacitor means; second capacitor means; means including diode means connecting said second capacitor to said first capacitor means, said diode means poled to permit said first and second capacitor means to charge in parallel and to prevent the discharge of said second capacitor means by said first switch means; and second switch means connected to said second capacitor means and the sensing means, and actuated by a natural heartbeat to discharge said first and second capacitor means.
  • noise responsive means comprising: third capacitor means connected between the sensing means and said second switch means; second resistor means; further diode means; third resistor means; means for connecting said second resistor means across said third capacitor means to provide a first discharge path, and for connecting said further diode means and said third resistor means across said third capacitor means to provide a second discharge path for one electrical polarity; and said second and third resistor means having resistances selected to make the time constant of said first discharge path substantially greater than the time constant of said second discharge path.
  • a demand type heart pacer including input and output means adapted to be connected to a heart, the input means connected to means for sensing natural heartbeats, the improvement comprising: pulse generator means connected to the output means and including timing circuit means operable to control output pulses from said generator means at a selected frequency; further means connecting the means for sensing natural heartbeats to said pulse generator means for resetting said timing circuit means on the occurrence of a natural heartbeat; and further timing circuit means operably connected to said timing circuit means on the occurrence of an output pulse from said pulse generator for increasing the frequency of output pulses from said generator means for one pulse cycle following the absence of a natural heartbeat.
  • said timing circuit means includes resistor means and capacitor means connected in an RC timing circuit; and said further timing circuit means includes further capacitor means connected to said RC timing circuit and switch means operable on the occurrence of an output pulse from said pulse generator for charging said further capacitor means.
  • said timing circuit means includes serially connected resistance means and capacitance means; and said further timing circuit means includes further capacitance means, means connecting said further capacitance means across said capacitance means, switch means adapted to connect said further capacitance means across a source of energy, and means connecting said switch means to said pulse generator for receiving pulses therefrom.
  • a demand heart pacer including power supply means, pulse generator means for supplying stimulating pulses to a heart and means for connecting the generator means to a heart, the improvement comprising: resistor means and first capacitor means serially connected across the power supply means; said first capacitor means connected to the pulse generator means for controlling the frequency of pulses therefrom according to the charging time of said first capacitor means; and circuit means connected to the pulse generator and to said first capacitor means and operable in response to the occurrence of a generated stimulating pulse for changing the charge time of said first capacitor means.
  • circuit means comprises: second capacitor means; switch means connecting said second capacitor means across the power supply; said switch means connected to and controllable by the pulse generator for charging said second capacitor means on the occurrence of a generated stimulating pulse; and means connecting said first and second capacitor means in parallel for decreasing the charging time ofsaid first capacitor means.
  • noise responsive means for blocking repetitive noise signals from said circuit means comprising: capacitor means having an input plate connected to the sensing means and an output plate connected to said circuit means; a first discharge path for said capacitor means connected to said output plate and including serially connected diode means and resistor means, said diode means poled to pass current of a first polarity, said resistor means having a resistance value selected for generally fast discharge of said capacitor means; and a second discharge path for said capacitor means connected to said output plate and including further resistor means having a resistance value selected for generally slow discharge of said capacitor means for charging said capacitor means with repeated noise pulses of a second polarity at a frequency above that of the normal heartbeat range to block further of said noise pulses of the second polarity.
  • a demand pacer having input and output means adapted to be connected to a heart, pulse generator means connected to the output means and sensing means for detecting natural heartbeats connected to the input means, the improvement comprising: resistor means and first capacitor means connected in an RC timirgg circuit and to the pulse generator means for controlling e frequency of the pulse generator means according to the charge time of said first capacitor means; first switch means connected to said first capacitor means and to the sensing means, and actuated by a pulse from the sensing means to discharge said first capacitor means; second capacitor means; means connecting said second capacitor to said first capacitor means for discharging said second capacitor into said first capacitor; and second switch means connected to said second capacitor means and the pulse generator means and actuated by a generated pulse to charge said second capacitor means.
  • noise responsive means comprising: third capacitor means connected between the sensing means and said first switch means; second resistor means; diode means; third resistor means; means for connecting said second resistor means across said third capacitor means to provide a first discharge path, and for connecting said diode means and said third resistor means across said third capacitor means to provide a second discharge path for one electrical polarity; and said second and third resistor means having resistances selected to make the time constant of said first discharge path substantially greater than the time constant of said second discharge path.
  • noise responsive means for preventing repetitive noise signals sensed by the sensing means from disabling the pulse generator means comprising: capacitor means having an input plate connected to the sensing means and an output plate connected to the pulse generator means; a first discharge path for said capacitor means connected to said output plate and including serially connected diode means and resistor means, said diode means poled to pass current of a first polarity, said resistor means having a resistance value selected for generally fast discharge of said capacitor means; and a second discharge path for said capacitor means connected to said output plate and including further resistor means having a resistance value selected for generally slow discharge of said capacitor means for charging said capacitor means with repeated noise pulses of a second polarity at a frequency above that of the normal heartbeat range to block further of said noise pulses of the second polarity.
  • a demand type heart pacer having pulse generator means including timing means operable to control output pulses from the generator means at a selected frequency, having sensing means for sensing natural heartbeats including means refractory to applied signals for a predetermined refractory period following each pacer pulse, having reset means, operatively connected to the pulse generator means, for resetting the timing means upon occurrence of each output pulse and having means connected to the pulse generator means and the sensing means and adapted to be connected to a heart; the improvement comprising: further means, operatively connecting the sensing means to the pulse generator means, for resetting the timing means for a predetermined limited time upon termination of the refractory period in response to repetitive signals, sensed by the sensing means, which exceed a predetermined rate greater than a natural heart rate and including means for preventing the timing means from continuous resetting in response to such repetitive signals, thereby decreasing the frequency of output pulses from the pulse generator means and causing the pacer to operate asynchronously.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Cardiology (AREA)
  • Engineering & Computer Science (AREA)
  • Physiology (AREA)
  • Biophysics (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
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US1178A 1969-06-12 1970-01-07 Electronic demand heart pacemaker with different pacing and standby rates Expired - Lifetime US3656487A (en)

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US117870A 1970-01-07 1970-01-07

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US (1) US3656487A (enrdf_load_stackoverflow)
JP (1) JPS518275B1 (enrdf_load_stackoverflow)
CA (1) CA986589A (enrdf_load_stackoverflow)
DE (1) DE2065013C3 (enrdf_load_stackoverflow)
FR (1) FR2051135A5 (enrdf_load_stackoverflow)
GB (2) GB1316291A (enrdf_load_stackoverflow)
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Cited By (21)

* Cited by examiner, † Cited by third party
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US3857399A (en) * 1970-03-24 1974-12-31 F Zacouto Heart pacer
US3881493A (en) * 1974-02-07 1975-05-06 American Optical Corp Synchronously reinforcing pacer
US3888260A (en) * 1972-06-28 1975-06-10 Univ Johns Hopkins Rechargeable demand inhibited cardiac pacer and tissue stimulator
US3921642A (en) * 1974-07-01 1975-11-25 Thomas A Preston Automatic rate adjustment pacer with natural rate searching means and method of operation
US3972334A (en) * 1975-02-10 1976-08-03 Telectronics Pty. Limited Demand heart pacer with dual time bases
US3983880A (en) * 1973-03-05 1976-10-05 Arco Medical Products Company Apparatus for generating heart stimulation pulses upon demand
US4030510A (en) * 1970-03-10 1977-06-21 General Electric Company Standby heart pacer
US4043347A (en) * 1975-08-28 1977-08-23 Vitatron Medical B.V. Multiple-function demand pacer with low current drain
EP0000983A1 (en) * 1977-08-19 1979-03-07 BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin Programmably variable voltage multiplier for implantable stimulator
US4397316A (en) * 1979-03-30 1983-08-09 Medtronic, Inc. Rate and A-V delay generator for heart pacemaker
EP0096464A1 (en) * 1982-05-19 1983-12-21 Purdue Research Foundation Exercise responsive cardiac pacemaker
US4448197A (en) * 1982-07-22 1984-05-15 Telectronics Pty. Ltd. Heart pacer end-of-life detector
US4467813A (en) * 1982-05-04 1984-08-28 Cardiac Resuscitator Corporation Biological signal source amplifier
USRE32378E (en) * 1980-04-07 1987-03-24 Medtronic, Inc. Output pulse artifact rejection in demand pacemakers and sensing circuits employed in conjunction therewith
WO1992004076A1 (en) * 1990-08-30 1992-03-19 Vitatron Medical B.V. Rate controlled pacemaker system using ar internal for rate control
EP0539258A1 (fr) * 1991-10-25 1993-04-28 ELA MEDICAL (Société anonyme) Procédé de réglage automatique de l'hystérésis dans un stimulateur cardiaque
US5782886A (en) * 1997-02-28 1998-07-21 Vitatron Medical, B.V. Pacemaker with improved hysteresis
US5891175A (en) * 1996-12-26 1999-04-06 Cardiac Pacemakers Method and apparatus for rate-responsive cardiac pacing
US20050113886A1 (en) * 2003-11-24 2005-05-26 Fischell David R. Implantable medical system with long range telemetry
US6915169B2 (en) 1998-07-22 2005-07-05 Cardiac Pacemakers, Inc. Extendable and retractable lead having a snap-fit terminal connector
US6983185B2 (en) 1998-07-22 2006-01-03 Cardiac Pacemakers, Inc. Lead with terminal connector assembly

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FR2082703A5 (enrdf_load_stackoverflow) * 1970-03-24 1971-12-10 Zacouto Fred
US3757791A (en) * 1971-12-30 1973-09-11 American Optical Corp Synchronized atrial and ventricular pacer and timing circuitry therefor
JPS5645626B2 (enrdf_load_stackoverflow) * 1972-01-10 1981-10-27
FR2175638B1 (enrdf_load_stackoverflow) * 1972-03-16 1974-08-02 Lejeune Seitz A Eline
DE2331499A1 (de) * 1972-06-28 1974-01-17 Univ Johns Hopkins Aufladbarer herzschrittmacher mit automatisch einsetzenden pausen
FR2218082B1 (enrdf_load_stackoverflow) * 1973-02-21 1979-01-26 American Offical Corp
US3999557A (en) * 1975-07-11 1976-12-28 Medtronic, Inc. Prophylactic pacemaker
JPS54136061U (enrdf_load_stackoverflow) * 1978-03-13 1979-09-20
US4250883A (en) * 1978-11-06 1981-02-17 Medtronic, Inc. Digital cardiac pacemaker with refractory, reversion and sense reset means
FR2440197A1 (fr) * 1978-11-06 1980-05-30 Medtronic Inc Amplificateur de detection de stimulateur cardiaque a la demande
FR2440200A1 (fr) * 1978-11-06 1980-05-30 Medtronic Inc Stimulateur cardiaque

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US3050695A (en) * 1959-09-10 1962-08-21 W W Henry Co Inc Pulse generator for human treatment
US3345990A (en) * 1964-06-19 1967-10-10 American Optical Corp Heart-beat pacing apparatus
US3431912A (en) * 1966-05-06 1969-03-11 Cordis Corp Standby cardiac pacer
US3528428A (en) * 1968-04-11 1970-09-15 American Optical Corp Demand pacer

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US3050695A (en) * 1959-09-10 1962-08-21 W W Henry Co Inc Pulse generator for human treatment
US3345990A (en) * 1964-06-19 1967-10-10 American Optical Corp Heart-beat pacing apparatus
US3431912A (en) * 1966-05-06 1969-03-11 Cordis Corp Standby cardiac pacer
US3528428A (en) * 1968-04-11 1970-09-15 American Optical Corp Demand pacer

Cited By (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4030510A (en) * 1970-03-10 1977-06-21 General Electric Company Standby heart pacer
US3857399A (en) * 1970-03-24 1974-12-31 F Zacouto Heart pacer
US3888260A (en) * 1972-06-28 1975-06-10 Univ Johns Hopkins Rechargeable demand inhibited cardiac pacer and tissue stimulator
US3983880A (en) * 1973-03-05 1976-10-05 Arco Medical Products Company Apparatus for generating heart stimulation pulses upon demand
US3881493A (en) * 1974-02-07 1975-05-06 American Optical Corp Synchronously reinforcing pacer
US3921642A (en) * 1974-07-01 1975-11-25 Thomas A Preston Automatic rate adjustment pacer with natural rate searching means and method of operation
US3972334A (en) * 1975-02-10 1976-08-03 Telectronics Pty. Limited Demand heart pacer with dual time bases
US4043347A (en) * 1975-08-28 1977-08-23 Vitatron Medical B.V. Multiple-function demand pacer with low current drain
EP0000983A1 (en) * 1977-08-19 1979-03-07 BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin Programmably variable voltage multiplier for implantable stimulator
US4397316A (en) * 1979-03-30 1983-08-09 Medtronic, Inc. Rate and A-V delay generator for heart pacemaker
USRE32378E (en) * 1980-04-07 1987-03-24 Medtronic, Inc. Output pulse artifact rejection in demand pacemakers and sensing circuits employed in conjunction therewith
US4467813A (en) * 1982-05-04 1984-08-28 Cardiac Resuscitator Corporation Biological signal source amplifier
US4436092A (en) 1982-05-19 1984-03-13 Purdue Research Foundation Exercise responsive cardiac pacemaker
EP0096464A1 (en) * 1982-05-19 1983-12-21 Purdue Research Foundation Exercise responsive cardiac pacemaker
US4448197A (en) * 1982-07-22 1984-05-15 Telectronics Pty. Ltd. Heart pacer end-of-life detector
WO1992004076A1 (en) * 1990-08-30 1992-03-19 Vitatron Medical B.V. Rate controlled pacemaker system using ar internal for rate control
EP0539258A1 (fr) * 1991-10-25 1993-04-28 ELA MEDICAL (Société anonyme) Procédé de réglage automatique de l'hystérésis dans un stimulateur cardiaque
FR2682878A1 (fr) * 1991-10-25 1993-04-30 Ela Medical Sa Procede de reglage automatique de l'hysteresis dans un stimulateur cardiaque.
US5891175A (en) * 1996-12-26 1999-04-06 Cardiac Pacemakers Method and apparatus for rate-responsive cardiac pacing
US5782886A (en) * 1997-02-28 1998-07-21 Vitatron Medical, B.V. Pacemaker with improved hysteresis
US6915169B2 (en) 1998-07-22 2005-07-05 Cardiac Pacemakers, Inc. Extendable and retractable lead having a snap-fit terminal connector
US6983185B2 (en) 1998-07-22 2006-01-03 Cardiac Pacemakers, Inc. Lead with terminal connector assembly
US7392095B2 (en) 1998-07-22 2008-06-24 Cardiac Pacemakers, Inc. Extendable and retractable lead having a snap-fit terminal connector
US20080262587A1 (en) * 1998-07-22 2008-10-23 Cardiac Pacemakers, Inc Extendable and retractable lead having a snap-fit terminal connector
US7774934B2 (en) 1998-07-22 2010-08-17 Cardiac Pacemakers, Inc. Method for making a terminal connector
US8209035B2 (en) 1998-07-22 2012-06-26 Cardiac Pacemakers, Inc. Extendable and retractable lead having a snap-fit terminal connector
US8285398B2 (en) 1998-07-22 2012-10-09 Cardiac Pacemakers, Inc. Lead with terminal connector assembly
US20050113886A1 (en) * 2003-11-24 2005-05-26 Fischell David R. Implantable medical system with long range telemetry
US20070100384A1 (en) * 2003-11-24 2007-05-03 Fischell David R Implantable medical system with long range telemetry

Also Published As

Publication number Publication date
DE2025499B2 (de) 1976-03-25
NL164478C (nl) 1981-01-15
SE384138B (sv) 1976-04-26
DE2065013B2 (de) 1980-12-11
NL164478B (nl) 1980-08-15
NL7008591A (enrdf_load_stackoverflow) 1970-12-15
DE2025499A1 (de) 1970-12-17
FR2051135A5 (enrdf_load_stackoverflow) 1971-04-02
DE2065013A1 (de) 1972-04-13
JPS518275B1 (enrdf_load_stackoverflow) 1976-03-15
GB1316291A (en) 1973-05-09
DE2065013C3 (de) 1985-03-21
CA986589A (en) 1976-03-30
GB1316292A (en) 1973-05-09

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