U.S. patent number 3,747,604 [Application Number 05/205,195] was granted by the patent office on 1973-07-24 for atrial and ventricular demand pacer with separate atrial and ventricular beat detectors.
This patent grant is currently assigned to American Optical Corporation. Invention is credited to Barouh V. Berkovits.
United States Patent |
3,747,604 |
Berkovits |
July 24, 1973 |
ATRIAL AND VENTRICULAR DEMAND PACER WITH SEPARATE ATRIAL AND
VENTRICULAR BEAT DETECTORS
Abstract
An atrial and ventricular pacer in which competition between
spontaneous atrial activity and atrial stimulation is prevented. In
the conventional type atrial and ventricular pacer, the detection
of a QRS wave re-starts both the atrial and ventricular timing
circuits, but spontaneous atrial activity does not inhibit the
generation of an atrial stimulating pulse. In the description of an
illustrative embodiment contained herein, by preventing the
generation of such a pulse when a spontaneous atrial beat is
detected the batteries have a longer life.
Inventors: |
Berkovits; Barouh V. (Newton
Highlands, MA) |
Assignee: |
American Optical Corporation
(Southbridge, MA)
|
Family
ID: |
26900202 |
Appl.
No.: |
05/205,195 |
Filed: |
December 6, 1971 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
Issue Date |
|
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884825 |
Dec 15, 1969 |
3661158 |
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Current U.S.
Class: |
607/9 |
Current CPC
Class: |
A61N
1/368 (20130101) |
Current International
Class: |
A61N
1/368 (20060101); A61n 001/38 () |
Field of
Search: |
;128/419P,421,422 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Kamm; William E.
Parent Case Text
This application is a continuation-in-part of my co-pending
application, Ser. No. 884,825, filed on Dec. 15, 1969 and which has
matured into U.S. Pat. No. 3,661,158.
Claims
What I claim is:
1. A pacer comprising terminal means for connection to a patient's
heart for atrial stimulation, terminal means for connection to said
patient's heart for ventricular stimulation, means for detecting an
atrial beat of said patient's heart, means for detecting a
ventricular beat of said patient's heart, means responsive to the
operation of said ventricular detecting means for generating an
electrical stimulus on said ventricular terminal means following a
first predetermined time interval after the last detected
ventricular beat only of said patient's heart, means for generating
an electrical stimulus on said atrial terminal means following a
second predetermined time interval after the last ventricular beat
only of said patient's heart, and means for preventing the
generation of an electrical stimulus on said atrail terminal means
responsive to the detection of an atrial beat of said patient's
heart during said second predetermined time interval.
2. A pacer in accordance with claim 1 wherein said first
predetermined time interval is longer than said second
predetermined time interval.
3. A pacer in accordance with claim 2 wherein said second
predetermined time interval is shorter than a probable minimum
interval between successive ventricular beats of said patient's
heart and is longer than a probable maximum interval between a
ventricular beat and the next atrail beat of said patient's
heart.
4. A pacer in accordance with claim 3 wherein said first
predetermined time interval is longer than the usually-occurring
interval between successive ventricular beats of said patient's
heart.
5. A pacer comprising terminal means for connection to a patient's
heart for ventricular stimulation, terminal means for connection to
said patient's heart for atrial stimulation, a first timing circuit
means for generating an electrical impulse on said ventricular
terminal means, a second timing circuit means for generating an
electrical impulse on said atrial terminal means, means for
detecting a ventricular beat of said patient's heart and responsive
thereto for resetting both of said first and second timing circuit
means, and means for detecting an atrial beat of said patient's
heart and responsive thereto for resetting said second timing
circuit.
6. A pacer in accordance with claim 5 wherein the period of said
first timing circuit means is longer than a probable maximum
interval between two successive ventricular beats of said patient's
heart.
7. A pacer in accordance with claim 6 wherein the period of said
second timing circuit means is longer than a probable maximum
interval between a ventricular beat and the next atrail beat of
said patient's heart.
Description
This invention relates to atrial and ventricular pacers, and more
particularly to such pacers in which competition between
spontaneous atrial activity and atrial stimulation is
prevented.
There are many patients who require an atrial and ventricular
pacer, as opposed to the more usual ventricular pacer. In demand
pacers of the latter type, a detector monitors the spontaneous
ventricular beating of the heart; if too long a time interval has
elapsed since the last beat, a stimulating pulse is generated to
trigger the ventricular beat. In pacers of the former type, an
additional circuit is provided for generating atrial stimulating
pulses to compensate for irregular atrial activity. To maintain
synchronism between the two pulsing circuits, as disclosed in my
above-identified application, every ventricular beat -- whether
natural or stimulated -- causes the atrial timing period to
re-start together with the (longer) ventricular timing period.
Following any ventricular beat, an atrial stimulating pulse is
generated a short time after the next atrial beat should occur. The
atrial stimulating pulse is generated even if a natural atrial beat
occurs. Thereafter, a ventricular stimulating pulse is generated,
but only if a natural ventricular beat does not occur within a
predetermined time interval subsequent to the previous ventricular
beat.
As explained in my co-pending application, if an atrial stimulating
pulse is generated following an atrial contraction, that is, during
the refractory interval of the atria, it has no effect on the
beating action of the patient's heart. It is only the generation of
a ventricular stimulating pulse during the refractory interval of
the ventricles that can be dangerous. For this reason, the
detection of a spontaneous ventricular beat inhibits the generation
of the ventricular stimulating pulse which would otherwise soon
occur. But atrial stimulating pulses are not inhibited. In fact,
even if the heart beats perfectly, in the conventional type atrial
and ventricular pacer, an atrial stimulating pulse is generated
during every heartbeat cycle. Of course, the timing of the atrial
pulse generator is keyed to the ventricular beats so that at all
times both pulsers and the natural heart activity remain in
synchronism.
In my co-pending application, I described the possibility of
detecting an atrial contraction and in response thereto re-starting
the atrial timing period. However, it was believed to be difficult
to detect an atrial contraction (or, more accurately, the atrial
depolarization signal), and for that reason an atrial beat detector
was not provided in my earlier pacer.
It is a general object of my invention to provide an atrial and
ventricular pacer of the prior art type but in which the detection
of an atrial beat inhibits the generation of the atrial stimulating
pulse which otherwise would be generated soon thereafter.
In accordance with the principles of my invention, a conventional
type ECG wave detector is provided to detect atrial depolarization
signals in the prior art type atrial and ventricular pacer. The
detection of a ventricular beat still re-starts the timing of the
atrial pulse generating circuit (along with that of the ventricular
pulse generating circuit), but now the atrial pulse generator is
also inhibited from producing an atrial simulating pulse whenever a
spontaneous atrial beat is detected. The major advantage of this
design is that atrial stimulating pulses are not generated when
they are not needed; the drain on the battery is reduced and the
pacer has to be replaced less frequently. (Although some atrial
contractions may not be detected, that simply results in the type
of operation described in my co-pending application. It is for each
atrial beat which is detected that the drain on the battery is
reduced.)
It is a feature of my invention to provide an atrial beat detector
in an atrial and ventricular pacer, the detection of an atrial beat
resulting in the re-starting of the atrial timing period and the
inhibition of the generation of the atrial stimulating pulse which
otherwise would be generated.
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 schematically the atrial and ventricular pacer
disclosed in my co-pending application;
FIG. 2 consists of timing waveforms which will be helpful in
understanding the operation of the circuit of FIG. 1;
FIG. 3 depicts schematically the illustrative embodiment of the
invention; and
FIG. 4 consits of timing waveforms which will be helpful in
understanding the operation of the circuit of FIG. 3.
FIG. 1 depicts three circuit blocks, the details of which are
disclosed in my co-pending application. Ventricular demand
stimulator 10 applies a ventricular stimulating pulse, on
ventricular electrodes E1 and E2, 800 milliseconds after the
previous ventricular beat, whether spontaneous or stimulated. A
ventricular beat also results in the appearance of a pulse on the
electrodes which is extended to ventricular beat (VB) detector 20.
The VB detector extends a signal over conductor 40 to the
ventricular demand stimulator, in response to the detection of a
ventricular beat, to inhibit the generation of the next ventricular
pulse which otherwise would be generated and to control the start
of a new 800-millisecond timing interval. Atrial demand stimulator
30 is provided to extend an atrial stimulating pulse to electrodes
E3 and E4. The atrial stimulator timing period starts together with
the ventircular stimulator timing period, the VB detector output
being extended to both pulse generators. However, the timing period
of the atrial stimulator is 600 milliseconds rather than 800
milliseconds.
FIG. 2 depicts the operation of the pacer during seven heartbeat
cycles. The letters R and P indicate respectively spontaneous
ventricular and atrial contractions which occur during the seven
cycles. The letters VS and AS identify respectively the generations
of ventricular and atrial stimulating pulses. Since the detection
of a ventricular beat re-starts the atrial timing period, and the
atrial timing period is 600 milliseconds, the time interval between
each spontaneous ventricular beat and the next atrial stimulating
(AS) pulse is 600 milliseconds as shown. The notation 600(F) is
used to indicate that the interval separating any spontaneous
ventricular contraction and the next atrial stimulating pulse is
fixed. Similarly, since each stimulating ventricular beat (VS)
results in VB detector 20 energizing its output 40 to re-start both
timing periods, the interval between each VS pulse and the next AS
pulse is similarly 600 milliseconds and is shown by the notation
600(F).
In the absence of a spontaneous ventricular beat, a ventricular
stimulating pulse is generated 800 milliseconds after the previous
ventricular beat under control of ventricular demand stimulator 10.
Since the interval is always 800 milliseconds, the notation 800 (F)
is used to indicate the time between a spontaneous ventricular beat
(R) and the next ventricular stimulating (VS) pulse if such a pulse
is generated, and the time interval between one ventricular
stimulating pulse and the next ventricular stimulating pulse in the
absence of an intervening spontaneous ventricular beat. Finally, in
the example shown in the drawing, it is assumed that a spontaneous
ventricular beat (R) occurs 700 milliseconds after a previous
ventricular beat, whether spontaneous (R) or stimulated (VS).
Consequently, 700 milliseconds separate each R--R pair or VS-R
pair. Since each of these time intervals is not fixed, and instead
is a function of the condition of the patient, the letter F is not
used together with the 700 -millisecond designations.
In the circuit of FIG. 1, as shown in FIG. 4 of my copending
application, two capacitors are provided to control the
600-millisecond atrial timing period and the 800-millisecond
ventricular timing period. Each capacitor charges from an initial
value toward a respective firing level. It takes 600 milliseconds
for the atrial capacitor (57') in my co-pending application to
reach the atrail firing level, at which time an atrial stimulating
pulse is generated, the capacitor is discharged and a new timing
interval begins; it requires 800 milliseconds for the ventricular
timing capacitor (57) in my co-pending application to reach the
ventricular firing level, at which time a ventricular stimulating
pulse is generated, the capacitor is discharged and a new
ventricular timing period begins. Both capacitors are discharged
and new timing periods begin when either a spontaneous ventricular
beat (R) is detected or a ventricular stimilating (VS) pulse is
generated. The two sawtooth waveforms depict the respective
capacitor voltage waveforms. The little arrows directly above the
peaks of the waveforms indicate when, for the seven illustrative
cycles, atrial and ventricular stimulating pulses are generated as
a result of the voltages of the respective capacitors rising to the
respective firing levels.
With respect to the ventricular capacitor voltage waveform, the
voltage across the capacitor has sufficient time to rise to the
ventricular firing level only in the absence of a spontaneous
ventricular beat. Consequently, it is only at the end of each of
cycles 3 and 4 that a ventricular stimulating pulse is generated.
In the case of the atrial capacitor, however, the voltage across it
always reaches the atrial firing level 600 milliseconds after the
detection of a spontaneous ventricular beat (R) or the generation
of a ventricular stimulating (VS) pulse. Consequently, an atrial
stimulating pulse is shown as occuring during every cycle.
Immediately after the generation of an AS pulse, the atrial
capacitor voltage starts to rise. But the QRS detector causes the
capacitor to be discharged at the end of each cycle when a
spontaneous ventricular beat (R) is detected, or a ventricular
stimulating (VS) pulse is generated. The capacitor then starts to
charge again and the atrial firing level is reached 600
milliseconds later.
The circuit of FIG. 3 is similar to that of FIG. 1 except that
atrial beat (AB) detector 50 is provided. The atrial electrodes E3
and E4 are connected to inputs of the AB detector. The AB detector
is similar to the VB detector 20, and may in fact be identical.
Although it was believed to be difficult to detect atrial beats
(that is, the atrial depolarization signal), this is no longer
always true. The problem in the past was that the atrial electrodes
would shift slightly after implantation. But newer atrial
electrodes which have become available commercially permit far more
reliable detection of atrial depolarization signals.
The output of AB detector 50 and the output of VB detector 20 are
both extended to respective inputs or OR gate 60, the output of
which is extended to atrial demand stimulator 30. The only
difference between the pacers of FIGS. 1 and 3 is that in the
latter circuit the timing period of the atrial demand stimulator is
re-started whenever a spontaneous atrial beat is detected, as well
as when a spontaneous ventricular beat is detected or a ventricular
stimulating pulse is generated.
FIG. 4 shows the capacitor waveforms for the same seven heartbeat
cycles depicted in FIG. 2. The major difference between the two
timing sequences is that with the circuit of FIG. 3 each
spontaneous atrial beat (P) re-starts the atrial timing period. It
is only in the absence of a spontaneous atrial beat, during
heartbeat cycles 4, 5 and 7, that atrial simulating (AS) pulses are
generated. While the ventricular sawtooth waveforms are thus the
same in FIGS. 2 and 4, the atrial sawtooth waveforms are
considerably different. In FIG. 4, the atrial firing level is
reached during only three of the seven heartbeat cycles. In
general, because an atrial stimulating pulse is not generated by
the pacer of FIG. 3 when a spontaneous atrial beat is detected,
there is reduced battery dissipation. This contributes to extended
life of the pacer.
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.
* * * * *