U.S. patent number 3,903,897 [Application Number 05/339,537] was granted by the patent office on 1975-09-09 for cardiac pacer.
This patent grant is currently assigned to Kent Cambridge Medical Limited. Invention is credited to Michael John English, David John Woollons.
United States Patent |
3,903,897 |
Woollons , et al. |
September 9, 1975 |
Cardiac pacer
Abstract
In a cardiac pacer of the synchronous type and having both
atrial and ventricular electrode systems, the atrial electrode
senses atrial signals and the ventricular electrode is used to
sense the QRS complex and this is used to gate out the QRS complex
from the atrial signal and allow the atrial electrode to
discriminate against the QRS complex and sense only the P-wave.
Consequently the atrial electrode system can be within the heart,
and there can be a single catheter with both the atrial and the
ventricular electrodes spaced apart on it.
Inventors: |
Woollons; David John (Sussex,
EN), English; Michael John (Sussex, EN) |
Assignee: |
Kent Cambridge Medical Limited
(Cambridge, EN)
|
Family
ID: |
9987420 |
Appl.
No.: |
05/339,537 |
Filed: |
March 9, 1973 |
Foreign Application Priority Data
|
|
|
|
|
Mar 11, 1972 [GB] |
|
|
11501/72 |
|
Current U.S.
Class: |
607/9 |
Current CPC
Class: |
A61B
5/283 (20210101); A61N 1/368 (20130101); A61N
1/056 (20130101) |
Current International
Class: |
A61B
5/0408 (20060101); A61B 5/042 (20060101); A61N
1/368 (20060101); A61N 1/05 (20060101); A61n
001/36 () |
Field of
Search: |
;128/404,418,419P,419R,2.6A,2.6F,2.6R |
References Cited
[Referenced By]
U.S. Patent Documents
Other References
Rogel et al., "Journal of Thoracic & Cardiovascular Surgery,"
Vol. 61, No. 3, Mar. 1971, pp. 466-471. .
"U.S.C.I. Catalog," No. 5070021, Sept. 1972, 6 pp. .
Fischler et al., "IEEE Transactions on Bio-Medical Engineering,"
Vol. BME-16, No. 1, Jan. 1969, pp. 64-68. .
Castillo et al., "Chest," Vol. 59, No. 4, Apr. 1971, pp.
360-364..
|
Primary Examiner: Kamm; William E.
Attorney, Agent or Firm: Scrivener Parker Scrivener and
Clark
Claims
We claim:
1. A synchronous cardiac pacer comprising:
atrial electrode means which is adapted so that it can be arranged
in relation to an atrium of a heart in order to sense the naturally
occurring P-wave of said heart and produce a corresponding sensed
P-wave signal;
ventricular electrode means which is adapted so that it can be
arranged in relation to a ventricle of said heart in order to sense
the naturally occurring QRS complex of said heart and produce a
corresponding sensed QRS signal;
gating means which has an output connection to said ventricular
electrode means and respective input connections from said atrial
electrode means and ventricular electrode means so as to receive
said P-wave and QRS signals without disturbing the phase
relationship between them, and which responds to said P-wave and
QRS signals by blocking any similar signal variations which occur
simultaneously so that only a pure P-wave signal without any QRS
complex component passes to the output connection;
pulse generating means which is connected in the P-wave channel
comprising said atrial electrode means, said gating means, said
output connection and said ventricular electrode means to produce a
pulse signal corresponding to said P-wave signal, whereby a pure
P-wave pulse signal is applied to said ventricular electrode means
as a stimulating signal for said heart; and
delay means which is connected in said P-wave channel and
introduces an appropriate atrio-ventricular delay in said P-wave
signal.
2. A cardiac pacer as claimed in claim 1 in which said gating means
comprises a logic gate.
3. A cardiac pacer as claimed in claim 2 in which said P-wave and
QRS signals are converted to corresponding pulse signals by
respective means connected between said electrode means and said
inputs of the logic gate so that pulse signals are received at the
latter and pass to said output connection.
4. A cardiac pacer as claimed in claim 1 in which said pulse
generating means is connected in said output connection between
said gating means and said ventricular electrode means.
5. A cardiac pacer according to claim 1 in which said delay means
is connected in said output connection between said gating means
and said ventricular electrode means.
6. A cardiac pacer according to claim 5 in which second gating
means is connected in said output connection between said delay
means and said ventricular electrode means to control the passage
of said pure P-wave signal to the latter, said second gating means
having a control input, a blocking pulse generating means producing
a blocking pulse of fixed length in response to each QRS signal
connected to said control input for preventing the passage of said
pure P-wave signal through said gating means.
7. A cardiac pacer according to claim 1 in which a single catheter
designed for insertion in the heart carries both the atrial
electrode means and the ventricular electrode means.
8. A cardiac pacer according to claim 7 in which the catheter is
designed for pervenous insertion, the ventricular electrode means
being formed on the extreme end of the catheter and the atrial
electrode means being formed at a distance spaced from that
end.
9. A cardiac pacer according to claim 8 in which the distance
between the electrode means is substantially 12cm.
10. A cardiac pacer according to claim 8 in which each electrode
means comprises at least two poles, axially spaced apart along the
catheter.
11. A cardiac pacer according to claim 10 in which the spacing
between the poles of each electrode means is substantially 1cm.
12. A cardiac pacer according to claim 8 in which an end cap on the
catheter forms one pole and a second pole on the catheter is spaced
axially from said end cap, these two poles comprising ventricular
electrode means.
13. A cardiac pacer according to claim 1 in which said pulse
generating means includes means for generating said pure P-wave
pulse signal at a fixed minimum lower rate in the event of the
P-wave signal from the atrial electrode means falling below that
rate or vanishing.
14. A cardiac pacer according to claim 1 in which said pulse
generating means includes means for generating said pure P-wave
pulse signal at a normally fixed upper limiting rate in the event
of the P-wave signal from the atrial electrode means rising above
that rate.
15. A cardiac pacer according to claim 14 in which said pulse
generating means includes means for omitting a pulse of the pure
P-wave pulse signal at the upper limiting rate each time this
signal falls behind the sensed P-wave signal by an amount exceeding
a predetermined value.
Description
This invention relates to cardiac pacer. For an understanding of
the invention it is necessary first to discuss briefly the problems
involved in pacing and the various existing proposals that solve
these problems to a greater or lesser extent.
The normal human heart has two major pumping chambers, the left and
the right ventricles, which by their simultaneous contraction
(systole) expel blood into the aorta and the pulmonary artery.
Blood enters the ventricles from two thinner walled reservoir
chambers, respectively the left and right atrium. The atria also
contract in a separate action which precedes the ventricular
systole. Although this atrial contraction is not essential to life
it does boost the ventricular systole and help the performance of
the heart. The contraction of both atria and ventricles results
from a wave of electrical excitation which begins in the right
atrium and spreads to the left atrium. The excitation subsequently
enters the atrio-ventricular (A-V) node, which delays its passage
into the ventricles, to permit the correct temporal relationship
between atrial and ventricular contractions.
The spread of excitation in the atria can be recorded externally on
the electrocardiograph as a signal known as the P-wave. A larger
and more complex signal is caused by the spread of excitation in
the ventricles, which can be recorded externally as the QRS
complex. The interval from the beginning of the P wave to the
beginning of the QRS complex is approximately 150 milliseconds. The
repolarisation of the ventricles, i.e., the return to the resting
state, is signalled by a small deflection on the cardiograph known
as the T-wave. Signals corresponding to the P, QRS- and T-waves can
also be recorded from within thecavities of the heart chambers.
They are generally referred to as the electrograms.
The whole cycle repeats itself at a frequency ranging in health
from about 50 to 190 times per minute depending upon many factors
but principally the metabolic requirements of the body (e.g., the
rate is fastest during hard exercise). The timing of the heart beat
is set by the region high in the right atrium, called the
sinoatrial node. In the absence of any external control this gives
rise to electrical signals (which cause the spread of excitation
referred to above) at the rate of about 105, but the central
nervous system acts on the node by way of nerves capable of slowing
or accelerating the spontaneous rate of discharge, thus providing a
wide range of frequency of heartbeat.
The electrical control of the heart can break down in a variety of
ways. One of the most important concerns the propagation of the
electrical impulses that activate the heart, usually referred to as
heart block. In this conditions the electrical signals may fail to
penetrate into the right atrial (sino-atrial block), fail to
traverse the region of the A-V node, or fail to activate the
ventricles due to disturbances in conduction below the A-V node
(two varieties of A-V block). These disorders may cause serious
slowing of the heartbeat. The ventricles do have subsidiary
(natural) pacers of their own, capable of monitoring the slow rate
of electrical activation in the event of heart block but with
disease of the conducting system these can also fail. Heart block
can then cause temporary or even permanent cessation of the
heartbeat.
Artificial pacers are used to restore a satisfactory heartbeat in
patients with heart block. An electrode is inserted into the heart,
usually by way of a vein, to lie with the tip in the right
ventricle. Electrical impulses are generated in to the pacer, which
may be outside the patient (external unit) or implanted under the
skin and travel by way of the electrode to stimulate the heart. The
pacer system can be operated in several different modes which will
be discussed briefly.
So-called fixed rate ventricular pacing refers to a system in which
the ventricle is stimulated at a preset rate which continues in an
uninterrupted fashion. If the heart block is only intermittent,
there will be times when the normal electrical signals and the
artificial stimuli compete for control of the heart. The heartbeat
will therefore be irregular. Moreover an artificial stimulus will
fail, from time to time, on a position, on the T-wave, known as the
vulnerable period. Under certain adverse conditions such an event
can trigger a complete disorganisation of the heart's electrical
activity and cause immediate death.
So-called `demand` ventricular pacing is designed to obviate this
risk. Naturally occuring heartbeats are detected by the electrode
in the ventricle which thus serves both for the sensing and for the
delivery of electrical impulses. A spontaneous heartbeat
deactivates the pacer for a period determined by its rate setting.
The deactivation is always long enough to prevent the pacer impulse
coinciding with the T-wave of any previous complex. `Demand`
ventricular pacing is in some circumstances safer than fixed rate
pacing but important disadvantages remain. First the ventricles
beat independently of the atria so that the effect of the atrial
boost on the heart is lost. Secondly the ventricular rate depends
on the setting of the pacer and cannot accelerate in the normal
manner to meet varying metabolic demands.
So-called sequential atrio-ventricular pacing has been used to
restore normal A-V relationships. In this technique an atrium and a
ventricle are paced by twin stimuli separated by an appropriate
interval. However the heart rate is again controlled by the pacer
setting and does not vary according to physiological needs.
Moreover the pacer rate must be set to exceed the spontaneous rate
of the sino-atrial node for otherwise the naturally occuring
sino-atrial impulse and the pacer compete for control of the atrium
in a manner which precludes satisfactory pacing. TWo electrodes are
usually necessary, one to lie with its tip in the right atrium and
the other with its tip in the right ventricle. The placing of the
two electrodes prolongs the procedure in a patient who may be
critically ill.
So-called synchronous pacing approximates most closely to the
normal physiological mechanism. The spontaneous atrial electrogram
(P-wave) is sensed by an electrode usually in contact with the
atrial wall and this is used to trigger the ventricle after an
appropriate preset delay. In this way the spontaneous atrial rate
(subject to normal nervous control) determines the ventricle rate
and normal A-V relationships are maintained. Present techniques
have been limited by the need for two electrode systems (atrial and
ventricular) and more seriously because an electrograph recorded
from within the atrium may show not only P-waves but also QRS
complexes, resulting in false triggering. Synchronous pacing has
been used satisfactorily with implanted units utilising atrial
electrodes sewn onto the atrial surface (which requires exposure of
the heart by surgery). It has not previously been developed
successfully for pervenous use.
The aim of the present invention is to provide a pacer which will,
in normal operation, act in a synchronous mode and maintain
sequential A-V operation, yet without the need for extensive heart
surgery to implant an external electrode on the atrium.
According to the invention this is achieved in that electrodes are
applied both to the atrium and the ventricle and in addition to the
atrial electrode acting as a sensing element, with the ventricular
electrode acting as a stimulating element (as in known synchronous
pacing), the ventricular electrode acts also as a sensing element
for QRS complexes and the resulting signals are caused to act on
the circuit receiving the signals from the atrial electrode so as
to prevent that circuit passing on signals from the atrium which in
fact originate from the QRS complex.
In this way the sensing circuit connected to the atrial electrode
is able to discriminate against the QRS complex and to identify
clearly the atrial P-wave even in the presence of QRS complexes of
equal or greater amplitude. The most important consequence of this
is that it is no longer essential to apply the atrial electrode
intimately to the atrial wall. On the contrary it is possible to
achieve synchronous pacing with the atrial electrode simply
immersed in the blood in the atrium. This leads to a further
important feature of the invention, according to which both the
atrial electrode and the ventricular electrode are incorporated in
a single catheter. In a preferred arrangement the catheter is
designed to be inserted, as in known ventricular pacing, through a
vein and the superior vena cava and the right atrium so that its
tip lodges in the apex of the right ventricle. The atrial electrode
is then formed by a pole or poles exposed at the surface of the
catheter at a distance (for example 12cm in a catheter for a normal
adult heart) from the tip such as to lie within the atrium.
There may be single active poles in the ventricle and atrium, with
a return path formed by an `indifferent` electrode placed elsewhere
in or on the body, but preferably each electrode system comprises
two respective axially spaced poles on the catheter itself.
The invention will now be further described by way of example with
reference to the accompanying drawings, in which:
FIG. 1 is a simplified block circuit diagram of the pacer;
FIG. 2 illustrates the location of the catheter in the heart;
FIGS. 3a and 3b show a more detailed circuit diagram of a preferred
version;
FIG. 4 shows a possible modification to the circuit of FIG. 3;
and
FIG. 5 is an electrocardiogram picture of the waveform of a
heartbeat measured by external electrodes, and serving to identify
the various parts referred to above.
Referring first to FIGS. 1 and 2, a catheter 1 of flexible inert
material forms effectively a double electrode system and contains
four wires. It is designed to be inserted into the body through a
vein, for example through a vein in the right arm or in the region
of the collar-bone, and then passed by known techniques into the
heart by way of the superior vena cava 2, passing through the
tricuspid valve 3, into the right ventricle 4 until its tip lodges
in the apex of the right ventricle. At its tip it has an
electrically conducting cap 5 forming one pole, and then spaced
about 1 cm from this is a sleeve 6, flush with the material of the
catheter, forming a second pole so that the two together form the
ventricular electrode. About 12 cm from the tip is a pair of
sleeves 7 about 1cm apart, forming the atrial electrode. This is
immersed in the blood in the atrium and may or may not be close to
the atrial wall. It therefore receives electrical signals present
in the region of the atrium and these include not only the P-wave
originating in the atrial wall but also the QRS complex from the
ventricle. The QRS complex is generally of much greater inherent
amplitude than the P-wave, and so even in the interior of the
atrium it can have at least a comparable amplitude. That is why
hitherto in synchronous pacing it has been considered essential for
the atrial electrode to be placed on the outside of the atrial wall
by major cardiac surgery.
The signals from the atrial electrode 7 are passed through a
variable gain amplifier 8 and used in circuit 9 to produce a
corresponding train of pulses of clear and uniform shape and
amplitude. Likewise signals are picked up from the ventricular
electrode system 5,6; these will only be QRS complexes, either
naturally occurring or stimulated, as the P-wave will be barely
detectable, if at all, at the apex of the ventricle. These signals
are likewise amplified in amplifier 10 and formed in circuit 11
into a train of pulses. These pulses are passed to a circuit 12 in
which, while they are present, they block the passage of pulses
from the atrial signal amplifier 9. Therefore they eliminate those
signals from the atrial electrode 7 that originate in QRS complexes
and allow through only those signals originating from the naturally
occurring P-wave. The resulting train of pulses is passed through a
circuit 13, which sets an upper limit on the pulse repetition rate.
If the natural rate rises above this value, indicating very rapid
heartbeats or possible interference from external sources, the
circuit 13 blocks some of the pulses so as to pass pulses at this
fixed maximum rate. The pulses then pass through a circuit 14 which
sets a lower limit on the rate. If the rate is below this lower
limit or if the atrial pulses are absent altogether the circuit 14
will block the train of pulses and the generator 16, described
below, produces a train of pulses at a minimum rate.
The atrio-ventricular delay is introduced in a circuit 15 and will
be of the order of 120 milliseconds, but is preferably variable
over a range, for example from 18 to 220 milliseconds. This circuit
produces a train of pulses which are used to trigger a pulse
generator 16 in which the ventricular stimulating pulses are
generated. As in known pacer, it is important that the artificially
generated pulses should not be applied to the heart in a period,
following a natural QRS complex, that might coincide with the
subsequent natural T-wave. Therefore, from the circuit 11 that
produces pulses when a QRS complex is detected, a further circuit
17 produces pulses of longer duration (about 360 milliseconds) that
block the output of the pulse generator 16 in a gate 18 and prevent
the transmission of artificial ventricular stimulating pulses for
this preset period following any detected signals. Subject to this
restriction, the pulses from the generator 16 are fed from an
output amplifier 19 to the ventricle through the electrode poles 5
and 6.
Thus the pacer according to the invention, in its normal mode of
operation, achieves synchronous pacing, timed from the spontaneous
atrial P-wave associated with atrial contraction, yet without
requiring an accurately placed external atrial electrode, and in
fact requiring only a single catheter, inserted in the manner of
known fixed-rate or demand pacer catheters.
FIGS. 3a and 3b show the preferred circuit in sufficient detail to
enable the invention to be put into practice. Each of the boxes
represents a commercially available integrated circuit and the
letters alongside them identify the external connections that
enable them to act in the required manner. Mostly they act as
monostable multivibrators, i.e., so that an incoming trigger pulse
causes the circuit to change its state and it then reverts to its
original state automatically after a preset period determined by
the values of capacitors and/or resistors (which may be variable)
connected externally in accordance with the maker's instructions.
This results in a square-wave pulse of length equal to that preset
period. Inside each of the boxes in FIGS. 3a and 3b is indicated
the length of the pulses it produces. For example it will be seen
that the atrial signal, after amplification in amplifier 8,
produces pulses in circuit 9 of a duration of 150 milliseconds
which in their turn are used to produce very short pulses of only
0.5 milliseconds duration. These pass through a NAND gate (forming
the circuit 12 of FIG. 1) to the upper rate limit circuit 13.
It is believed that it will not be necessary to describe the
circuit of FIGS. 3a and 3b in great detail as the legends
accompanying the boxes identify the characteristics and the
components sufficiently for those skilled in the field of modern
electronics to put the invention into practice. Where appropriate
the reference numerals correspond to those of FIG. 1. The
monostable integrated circuits are all of the type 74121 or 74123
marketed by Texas Instruments. In the case of the 74123 unit two of
the boxes shown form one such unit.
As stated above the function of circuit 13 is to block the P-wave
pulses which have been gated by the circuit 12 and which have a
repetition rate above a preset upper limit.
The pulses from gate 12 are negative going pulses (from +5v to 0v
hereinafter called negative pulses) and set the bistable formed by
gates 21 and 22 to the state where the output of 21 is positive (+5
volts) and the output of 22 is zero (0 volts). Thus, if the
monostable 23 is in its state with its output Q positive, the A
inputs to monostable 23 receive a negative pulse via gate 24
whenever a negative pulse is delivered from gate 12. As a result
monostable 23 is triggered and delivers a positive pulse of 2ms
duration at its Q output which passes to the next circuit 14. A
complementary negative pulse of 2ms duration appears at the output
Q of monostable 23 and this pulse resets bistable 21,22 so that the
output of 22 is positive and the output of 21 is zero. The bistable
is, thereby, placed in a state where it is ready to receive the
next pulse from gate 12.
The trailing edge of the negative pulse from the output Q of
monostable 23 also triggers monostable pulses which then produces a
negative pulse at its output Q which is applied to the one input of
gate 24. If a negative pulse is produced by gate 12 after
monostable 25 has reset (i.e., after its output Q has again become
positive), it produces a positive pulse from the output Q of
monostable 23 in the manner already described above. If, however, a
pulse is produced by gate 12 while monostable 25 is triggered
(i.e., while its output Q is zero), it is prevented from triggering
monostable 23. Instead, it is stored in the bistable 21,22, and, as
soon as monostable 25 resets, the pulse then produces a positive
pulse at Q from monostable 23. In other words, a pulse from gate 12
cannot trigger monostable 23 until a fixed period, determined by
the pulse length of monostable 25, has elapsed following a previous
pulse from gate 12. Monostable 25 thus determines the minimum
period between output pulses from monostable 23 to circuit 14, that
is it determines an upper limit to the repetition rate of pulse
which it passes.
Considering now circuit 14, this receives positive pulses from
circuit 13 as described above. Each such input pulse is delayed
slightly by the C-R network 26 and applied to the input of
monostable 27. The trailing edge of the positive input pulse
triggers monostable 27 which then produces a positive pulse at its
output Q, thereby opening gate 28. The input pulse, if it is the
first one to be received, cannot pass through gate 28 as it
terminates before monostable 27 opens gate 28. However, if another
input pulse is received before monostable 27 resets, it will pass
straight through gate 28 to circuit 15 (FIG. 3b) and will also
re-trigger monostable 27. Thus, in general, if the input pulses
from circuit 13 appear at interval spacings less than the pulse
length of monostable 27, the gate 28 is held permanently open by
monostable 27 and the pulses will pass straight to circuit 15.
However, if the pulses from circuit 13 appear at interval spacings
greater than the pulse length of monostable 27 they will all be
blocked by gate 28 and none will pass to circuit 15.
Circuit 15 (FIG. 3b) produces the A-V delay. Monostable 29 is
triggered by the reading edge of the negative pulses from circuit
14 and after a preset delay resets, triggering the monostable 30
which in turn passes a negative pulse to the circuit 16.
Circuit 16 is a triggered astable. Negative input pulses from
circuit 15 pass through gate 31 and trigger the monostable 32 which
in turn produces a positive stimulating pulse at output Q to the
gate 18. The output Q of monostable 32 delivers a corresponding
negative pulse through gate 33 to trigger the monostable 34.
Monostable 34 then produces a negative pulse at its output Q, and
the trailing edge of this pulse triggers monostable 32. That is,
monostable 32 is triggered by either an input pulse from the A-V
delay circuit 15 if one arrives before monostable 34 has reset, or
by the pulse at Q from monostable 34. In the absence of input
pulses the circuit therefore free-runs generating pulses at a fixed
minimum rate determined by the pulse length of monostable 34.
However, if input pulses are received the circuit follows them in
producing output pulses to gate 18.
If a QRS wave is sensed in the ventricle, monostable 11 produces a
positive pulse at Q which triggers the monostable 35 and this in
turn produces a negative pulse at Q which passes through gate 33 to
monostable 34. Monostable 34, which is retriggerable, is thus reset
and will not trigger monostable 32 until its full period has
elapsed from the advent of the QRS signal. This arrangement
provides the demand facility of the pacer. It should be noted that
the triggering of monostable 34 by monostable 35 does not produce
any output stimulating pulse to gate 18, it merely extends the
period for which monostable 34 remains triggered.
The positive output pulses from monostable 11 corresponding to the
QRS wave also pass via a gate 36 and trigger a monostable 17 which
produces a negative pulse at Q which closes the gate 18 to prevent
the passage of the stimulating pulses from circuit 16.
It will be seen that the practical circuit of FIG. 3, includes a
light-emitting diode LED1, which is connected via a monostable 37
to the output of the gate 12 and therefore flashes every time a
pulse derived from the P-wave is received. It could, if desired, be
connected to the atrial pulse circuit ahead of the gate 12, in
which case it would flash every time a signal is received in this
circuit, i.e., both P-wave and QRS pulses.
Another diode LED2 is connected to the monostable 17 and flashes
every time a pulse is received from the ventricular electrode, and
a third one LED3, is connected via a monostable 38 to the output of
the pulse generator 16 to show the stimulating pulses which the
pacer is producing.
The output current amplifier 19 includes at its input an isolating
circuit comprising a non-electric link in the form of a
light-emitting diode LED4 acting on a phototransistor PT. This
provides complete electrical isolation of the input and output. The
output amplifier includes a potentiometer P allowing adjustment of
the amplitude of the pulse, to a maximum of 20 milliamperes,
negative-going.
All of the logic gates used are also formed by commercially
available integrated circuits.
As described above, the circuit 13 limits the output pulse rate to
a predetermined maximum value. However, when this occurs the output
pulses from the pacer are not synchronously related to the input P
waves. That is atrio-ventricular synchronism is lost.
The circuit of FIG. 4 is an alternative embodiment which maintains
this synchronism even when the input pulse rate is above the upper
limit setting. When the switch S is in the right hand position, the
circuit operation is as has already been described. When it is in
the left hand position, however, the circuit action is modified as
follows.
Circuit C is a monostable type 74121 and each input pulse from gate
12 triggers the bistable 21,22 as before and also triggers
monostable C. The output Q of the triggered monostable C produces a
positive output pulse which opens gate D. Hence, if the input pulse
passing through the bistable 21,22, gate 24 and monostable 23
arrives at gate D before monostable C has reset it passes through
gate D to circuit 14. However, if it arrives after monostable C has
reset it is blocked by gate D. In this latter case monostable 25 is
not triggered and no output pulse appears. Since monostable 25 is
not triggered it will be in the reset state when the next input
pulse arrives from gate 12 and this pulse therefore passes straight
through gate 24, monostable 23 and gate D. Hence the action of C is
to measure the time interval elapsing between an input pulse from
gate 12 and an output pulse to circuit 14. That is, it measures the
time for which a pulse is stored in the bistable 21,22. If this
time is less than the pulse length of monostable C the pulse passes
from gate 12 through gate D to circuit 14. If, however, it is
greater than the pulse length of monostable C a pulse is dropped
i.e. blocked by gate D. In this situation the next input from gate
12 passes straight to the circuit 14.
To summarize, if input pulses are above the upper rate they are
allowed through, at this upper rate, until their delay from the P
wave which produces them exceeds a preset value determined by the
pulse length of monostable C. When this occurs one output pulse is
omitted and the output is resynchronized to the input.
It will be understood that, although the version illustrated
employs timing of the various pulse lengths and spacings by the use
of monostable multivibrator circuit and capacitors, with variable
resistors to alter the values of the timings, it would be within
the scope of the invention to achieve the same result employing
digital circuits with clock counters for doing the timing.
In a modification of the catheter 1 there could be more than two
poles for each electrode system, to allow the same catheter to be
used in hearts of different sizes. For example the atrial electrode
system could comprise three poles, spaced apart, and one uses the
upper pair or the lower pair, whichever is placed best in the
atrium in the heart in question.
* * * * *