U.S. patent number 3,795,247 [Application Number 05/301,395] was granted by the patent office on 1974-03-05 for passive pacer refractory circuit.
This patent grant is currently assigned to American Optical Corporation. Invention is credited to Sherwood S. Thaler.
United States Patent |
3,795,247 |
Thaler |
March 5, 1974 |
PASSIVE PACER REFRACTORY CIRCUIT
Abstract
There is disclosed an implantable pacer having a one-shot
multivibrator refractory circuit which does not require the use of
any active elements other than those normally found in an
implantable pacer. The last stage of the heartbeat detector and
amplifier is capacitively coupled to the base of the discharging
transistor which is in parallel with the conventional timing
capacitor. Positive resistive feedback is provided between the
collector of the discharging transistor and the input terminal of
the last stage of the amplifier. While the last stage of the
amplifier and the discharging transistor both perform their usual
functions, together they also function as a one-shot multivibrator
refractory circuit.
Inventors: |
Thaler; Sherwood S. (Lexington,
MA) |
Assignee: |
American Optical Corporation
(Southbridge, MA)
|
Family
ID: |
23163157 |
Appl.
No.: |
05/301,395 |
Filed: |
October 27, 1972 |
Current U.S.
Class: |
607/9;
327/227 |
Current CPC
Class: |
A61N
1/365 (20130101) |
Current International
Class: |
A61N
1/365 (20060101); A61n 001/36 () |
Field of
Search: |
;128/419P,421,422
;307/260,267,268,273,274 ;328/191,192,207 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Kamm; William E.
Attorney, Agent or Firm: Wall; Joel Nealon; William C.
Claims
What I claim is:
1. In a pacer having a pair of ventricular electrodes, a timing
capacitor, means for charging said capacitor, means responsive to
the voltage across said capacitor reaching a predetermined value
for discharging said capacitor and for supplying a stimulating
pulse on said ventricular electrodes, means coupled to said
ventricular electrodes for detecting and amplifying a heartbeat
signal, said detecting and amplifying means including a transistor
in the last stage thereof, transistor means for selectively
discharging said timing capacitor, said last stage transistor and
said discharging transistor means each having a base terminal and a
collector terminal, means for capacitively coupling the collector
terminal of said last stage transistor to said base terminal of
said discharging transistor means for controlling the conduction
thereof responsive to the detection of a heartbeat signal, the
improvement comprising diode means connected between said timing
capacitor and the collector terminal of said discharging transistor
means poled in a direction to permit easy current flow from said
timing capacitor to the collector terminal of said discharging
transistor means, and regenerative resistive feedback means
connected between the collector terminal of said discharging
transistor means and the base terminal of said last stage
transistor for controlling said last stage transistor and said
discharging transistor to function as a one-shot multivibrator
refractory circuit.
Description
This invention relates to refractory circuits for heart pacers, and
more particularly to a passive refractory circuit for an
implantable pacer.
During a short refractory period following a heartbeat, the human
heart cannot be stimulated once again. Even if a stimulus is
provided, the heart does not respond. When a patient is provided
with a heart pacer, the pacer is often designed to exhibit a
refractory period. For approximately 200 milliseconds following
each heartbeat, the heart activity is not sensed, or if it is
sensed no action is taken in response to the detection of a beat.
The reason for this is that any heart activity during the
refractory period is a reflection of the previous beat; there
should be no heart signals (ventricular beat) which can be detected
during the refractory period.
In a demand pacer, a timing circuit is usually provided. The timing
circuit includes a capacitor which is discharged whenever a
heartbeat takes place. The capacitor then starts to charge toward a
firing level, and when this level is reached a stimulating pulse is
generated. In the case of a natural heartbeat which occurs prior to
the capacitor reaching the firing level, the detection of the
heartbeat results in the discharge of the capacitor and the start
of a new timing cycle.
There are two reasons for providing a refractory circuit in a
pacer. First, if a reflection signal were to be detected and to
result in the discharge of the capacitor, it is apparent that in
the absence of a natural heartbeat, the next stimulating pulse
would occur after the lapse of too long a time interval. This is
because upon the occurrence of the previous heartbeat the capacitor
started to charge toward the firing level, but the charging was
interrupted and the capacitor was discharged upon the detection of
the reflection signal. Since the capacitor must start to charge all
over again, an extra time interval elapses between the previous
heartbeat and the next stimulating pulse.
The second reason for providing a refractory circuit in a pacer
relates to the particular refractory circuit which is usually
provided. The circuit is usually a one-shot multivibrator. In the
absence of the multivibrator, marginal heartbeats which are
detected might control only the partial discharging of the timing
capacitor. In such a case, the capacitor would start to charge from
an intermediate level rather than from a minimum level, and the
next stimulating pulse would be generated too early. In fact, the
next stimulating pulse might even be generated during the natural T
wave, and this can be dangerous to the patient. For this reason, a
one-shot multivibrator is used because once it is triggered, even
following the detection of a marginal heartbeat, it can be designed
to fully discharge the timing capacitor. The output pulse of the
multivibrator controls the discharge of the capacitor to the
minimum level following the detection of even a marginal heartbeat.
This same one-shot multivibrator functions as a refractory circuit
because any reflection signals which are detected during the
refractory period (the multivibrator pulse period) have no effect
on the multivibrator and are effectively ignored.
Thus it is known to be desirable to utilize a one-shot
multivibrator to insure the full discharge of the timing capacitor
upon the detection of a heartbeat, and to provide for a pacer
refractory period. Nevertheless, such refractory one-shot
multivibrators, while used in external pacers, are not usually
incorporated in implantable pacers. The reason for this is that
they add to the volume of the unit, they draw current and thus
reduce the life of the batteries, and they represent two additional
active devices which may fail. In general, only absolutely
necessary active devices are included in implantable pacers.
It is a general object of my invention to provide a one-shot
multivibrator refractory circuit for an implantable pacer which
does not require any additional active elements.
Briefly, in accordance with the principles of my invention, I
interconnect two transistors which are already included in an
existing implantable pacer in such a way that in addition to
performing their usual functions, they further function as a
one-shot multivibrator refractory circuit. In some pacers, a
discharge transistor is placed across a timing capacitor.
Ordinarily, the capacitor charges from a potential source, and when
it reaches a firing level it discharges through a stimulating pulse
forming circuit. The discharging transistor which is placed in
parallel across the timing capcitor is normally non-conductive, and
thus allows the timing capacitor to charge and then discharge
through the stimulating pulse forming circuit. However, whenever a
natural heartbeat is detected, the discharging transistor is turned
on to provide an alternate discharge path for the timing capacitor.
The pulse for turning on the discharging transistor is usually
derived from the last transistor stage in the heartbeat detecting
circuit. This circuit responds to the appearance of an electrical
signal on the ventricular electrodes --which signal indicates the
occurrence of a heartbeat-- amplifies the signal, and then applies
the pulse to trigger the discharging transistor.
In some prior art implantable pacers, there is provided a capacitor
for coupling the pulse from the output stage of the amplifier to
the trigger terminal of the discharging transistor. But there is
generally no feedback from the discharging transistor back to the
last stage of the amplifier. In accordance with the principles of
my invention, I provide regenerative resistive feedback. This
feedback, together with the coupling capacitor, converts the last
stage of the amplifier and the discharging transistor to a one-shot
multivibrator. Even though the last stage of the amplifier still
performs its amplification function, and the discharging transistor
still performs its discharging function, the two of them together
further function as a refractory circuit. In effect, a refractory
circuit for the pacer is achieved without requiring any additional
active elements other than those usually found in an implantable
pacer; the additional elements required for the refractory circuit
are passive only.
Further objects, features and advantages of my invention will
become apparent upon consideration of the following detailed
description in conjunction with the drawing, in which:
FIG. 1 depicts a prior art implantable pacer; and
FIG. 2 depicts the modifications required thereto in accordance
with the principles of my invention to provide a one-shot
multivibrator refractory circuit without requiring the use of
additional active elements.
FIG. 1 is the same as the drawing in U.S. Pat. application Ser. No.
214,218, filed Dec. 30, 1971, of Barouh V. Berkovits entitled
"Synchronized Atrial and Ventricular Pacer," which application is
hereby incorporated by reference. Although the pacer of FIG. 1
provides stimulating pulses for a paient's atria as well as his
ventricles, it will be apparent that the principles of the present
invention are applicable to pacers without an atrial stimulating
capability. The atrial stimulating circuit of FIG. 1 includes those
elements in the bottom half of the drawing, and if they are omitted
from the circuit, tgether with resistors 89 and 38, capacitor 54
and diodes 36 and 40 (with diode 40 being replaced by a short
circuit), there results a prior art type ventricular pacer. It is
this ventricular pacer which will now be described briefly.
Capacitor 57 is the timing capacitor. It is bridged by transistor
T6 which is normally off. The capacitor charges from batteries 1-5
through potentiometers 35 and 37, and when the voltage across it
reaches the firing level, the capacitor discharges tnrough
transistors T7 and T8, and a stimulating pulse is applied to
ventricular electrodes E1 and E2.
THe electrodes are coupled to the base and emitter terminals of
transistor T1, this transistor being the first in a 3-stage
amplifier for detecting and amplifying heartbeat signals which
appear on the electrodes. Whenever a heartbeat is detected, a
negative pulse is applied at the base of transistor T4 to turn this
transistor on. As a result of current flowing through transistor
T4, the junction of resistors 34, 45 and 32 rises in potential. The
positive pulse is extended through capacitor 53 to the base of
transistor T6 to turn the latter on. When the transistor turns on,
capacitor 57 discharges through it; the capacitor is not allowed to
charge to the firing level because a natural heartbeat has been
detected. Instead, the capacitor is discharged and a new timing
cycle begins. The capacitor must charge from a minimum level up to
the firing level before a stimulating pulse is next generated.
It is thus apparent that in the pacer of FIG. 1 the last stage T4
of the heartbeat detector and amplifier extends a pulse directly to
the base of discharging transistor T6. There are two problems with
this configuration. First, reflection signals which occur during
the heart's refractory period can cause transistors T4 and T6 to
conduct and to thus discharge capacitor 57, with the result that
the next stimulating pulse, if one is required, may be delayed
unnecessarily. Second, a marginal heartbeat which is detected may
not result in the full discharge of capacitor 57 and thus it is
possible for the next stimulating pulse to be generated
prematurely.
FIG. 2 depicts the changes required in the prior art circuit of
FIG. 1 to provide a one-shot multivibrator refractory circuit
without the inclusion of any addtional active elements in the
circuit. In the circuit of FIG. 2, two elemenets have been added --
resistor 91 connected between the collector of transistor T6 and
the base of transistor T4, and diode 93 connected between the upper
end of capacitor 57 and the collector of transistor T6. (In the
event that a prior art pacer does not include capacitor 53, such a
capacitor should be added to the circuit.)
The function of resistor 91 is to provide regenerative feedback
from the collector of transistor T6 to the base of transistor T4.
When a natural heartbeat is detected, the detecting circuit applies
a negative pulse to the base of transistor T4. This causes a
positive pulse to be extended to the base of transistor T6 and this
transistor to turn on for discharging capacitor 57. When transistor
T6 turns on, its collector drops in potential, and this drop in
potential is extended through resistor 91 to the base of transistor
T4. Consequently, transistor T4 is held on even after termination
of the negative pulse which is extended through resistor 30 to its
base terminal. Both transistors remain on and capacitor 53 charges
from current flowing through resistor 32 and the capacitor. After
the capacitor has charged to an extent such that a sufficiently
positive potential is no longer extended to the base of transistor
T6, this transistor turns off. The increased potential which is now
extended through resistor 91 to the base of transistor T4 turns the
latter transistor off. Capacitor 53 then discharges through the
various resistors connected across it preparatory to the next cycle
of operation.
In effect, the combination of resistor 32 and capacitor 53 between
the collector of transistor T4 and the base of transistor T6, and
the regenerative feedback provided by resistor 91, convert
transistors T4 and T6 to a one-shot multivibrator. Even though
transistor T4 still functions as the last stage of the input
amplifier, and even though transistor T6 still functions to
discharge capacitor 57 when a natural heartbeat is detected, the
two transistors together also function as a one-shot multivibrator.
As such, they provide the known advantages of a one-shot
multivibrator refractory circuit, without however requiring any
additional active elements. Even marginal R waves which are
detected result in the complete discharge of capacitor 57 because
once the multivibrator is triggered, both of transistors T4 and T6
remain on until the termination of the multivibrator pulse period.
Even though the input pulse to the base of transistor T4 may be
only marginal, transistor T6 remains fully on for the multivibrator
pulse period (typically, 50-500 milliseconds, depending upon the
magnitudes of resistor 32 and capacitor 53). As for reflection
signals which are applied to the base of transistor T4 during the
refractory period, they have no effect because the one-shot
multivibrator remains on for the entire refractory period, during
which time the voltage across capacitor 57 remains at the minimum
level. Charging of the capacitor begins only after termination of
the multivibrator pulse, that is, at the end of the refractory
period, and any reflection signals which are detected during this
refractory period have no effect on the circuit.
It should be noted that without the refractory circuit, capacitor
57 is discharged only so long as a pulse is extended through
resistor 30 to the base of transistor T4. The capacitor then starts
to charge immediately. With the refractory circuit, however, the
capacitor does not start to charge once again until after the
refractory period is over. For this reason, the potentiometers in
the charging circuit of capacitor 57 should be decreased in
magnitude when the refractory circuit is used so that the
capacitor, once it starts to charge, can reach the firing level by
the time that the next stimulating pulse is required.
It should also be noted that with the addition of feedback resistor
91 in the circuit, and if diode 93 is not included, the charging
current for capacitor 57 which flows through potentiometer 37 could
be diverted through resistor 91. This would necessarily interfere
with the charging of the capacitor. It is for this reason that
diode 93 is provided. When transistor T6 is off, its collector is
at a higher potential (as a result of the potential extended
through resistor 91) than the upper end of capacitor 57. Thus,
diode 93 is reverse biased and current through potentiometer 37
flows only into capacitor 57. It is only when transistor T6 is
turned on that its collector potential drops and the diode is
forward biased; at this time, capacitor 57 discharges through the
diode and transistor T6.
Although the invention has been described with reference to a
particular embodiment, it is to be understood that this embodiment
is merely illustrative of the application of the principles of the
invention. Numerous modifications may be made therein and other
arrangements may be devised without departing from the spirit and
scope of the invention.
* * * * *