U.S. patent number 3,835,845 [Application Number 05/300,290] was granted by the patent office on 1974-09-17 for cardiac synchronization system and method.
This patent grant is currently assigned to Medical Innovations, Inc.. Invention is credited to Charles E. Maher.
United States Patent |
3,835,845 |
Maher |
September 17, 1974 |
CARDIAC SYNCHRONIZATION SYSTEM AND METHOD
Abstract
Improved internal circulatory assist apparatus comprising
control means whereby the optimum synchronization of the assist
apparatus with the beat of the heart can be effectively achieved
while using any of a plurality of parts of the body as monitor
sites for obtaining an arterial signal representative of the
patient's heartbeat. The control means consists of a marker means,
such as a pip on an oscilloscope, which is adjustable by
variable-delay circuitry throughout a range equal to the time
difference between the sensing of a selected cardiac event at an
earliest-reacting monitoring site and the sensing of a selected
cardiac event at a later-reacting monitoring site.
Inventors: |
Maher; Charles E. (Brockton,
MA) |
Assignee: |
Medical Innovations, Inc.
(Waltham, MA)
|
Family
ID: |
23158488 |
Appl.
No.: |
05/300,290 |
Filed: |
October 24, 1972 |
Current U.S.
Class: |
601/150 |
Current CPC
Class: |
A61H
9/0078 (20130101); A61B 5/0285 (20130101); A61H
2230/04 (20130101) |
Current International
Class: |
A61H
23/04 (20060101); A61B 5/0285 (20060101); A61B
5/026 (20060101); A61h 009/00 () |
Field of
Search: |
;128/1D,2.5P,2.5R,2.6R,30,64 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Kamm; William E.
Attorney, Agent or Firm: Cesari; Robert A. McKenna; John F.
Kehoe; Andrew F.
Claims
What is claimed is:
1. In an external circulatory assist apparatus comprising means to
pressurize a portion of a patients body, means to synchronize
actuation of said pressurization means on a portion of the body
with the heart cycle of a patient being treated, means for creating
an arterial waveforms signal representative of said heart cycle,
and display means for monitoring a said waveform signal exhibiting
a dicrotic notch portion representative of said heart cycle in the
form of visible traces on said display means the improvement
wherein said synchronizing means includes:
A. means to provide first and second intensified marker pips on
said display means displaying a marker trace representative of said
arterial waveform derived from a patient,
B. a first means to adjust the position of said first marker pip
relative to and along said waveform to a characteristic and
identifiable position of arterial waveforms, said adjusting means
also forming,
C. means to, concurrently with the adjustment of said first marker
pip, move a second intensified pip along said waveform at a
constant distance from said first marker, and
D. a second independent adjusting means to bring said intensified
trace into register with the dicrotic notch of said waveform, said
first and second adjusting means for moving said trace pips further
forming variable-time adjusting means and synchronization means
between a patients heart cycle and the start of said pressurization
of his body.
2. Apparatus as defined in claim 1 wherein said means to provide
said second said intensified marker pip comprises means to form an
ECG-derived signal, a signal generator, means for triggering said
signal generator by said ECG-derived signal, a variable delay
means, a marker pip generator, and a pulse mixer for integrating
said second marker pip signal with a signal representative of a
pressure wave exerted by said external assist apparatus on said
patient.
3. Apparatus as described in claim 2 wherein said variable delay
means provides a delay variable over a time difference at least
equal to the time elapsing from diastole in a patient's heart cycle
to the time such diastole is registered in said patient's digital
extremities.
4. Apparatus as defined in claim 1 wherein said position adjusting
means provide means to adjust said marker pip over a portion of the
waveform equivalent in length to time elapsing from diastole in a
patient's heart cycle to the time such diastole is registered in
said patient's digital extremities.
5. In apparatus for applying external pressure assist action to the
limbs of a patient in cyclic synchronization with the heartbeat of
said patient, wherein said assist is achieved with means for
transmitting pressure to said limbs through a fluid-filled bladder
pressurizing means surrounding said limbs, means for creating an
arterial waveform signal representative of said heartbeat and
display means for monitoring a said waveform signal representative
of said hearbeat in the form of visible traces on said display
means, wherein the apparatus also includes a visual cycle-phasing
monitor comprising:
A. a multi-channel display means for displaying
1. an ECG trace, and
2. a trace derived from an arterial pressure sensor,
B. means for visually displaying for the relative time duration of
a pressure command signal on said traces, and
C. manual means to adjust the relative timing and duration of said
pressure command signal, while simultaneously achieving a visual
adjustment of said signal to bring it into the desired relationship
to said ECG trace or arterial trace; and means to initiate said
pressure command signal; and wherein said apparatus comprises:
A. means to provide a first marker pip on display apparatus
displaying a marker trace representative of a radial arterial
waveform derived from a patient,
B. means to adjust the position of said marker pip relative to said
waveform to a characteristic and identifiable configuration of
arterial waveforms, said adjusting means also forming,
C. means to, form an intensified trace on said waveform,
D. means to move, concurrently with said adjusting, an intensified
trace along said waveform at a constant distance from said first
marker, and
E. means to bring said intensified trace into register with the
dicrotic notch of said waveform, thereby adjusting the
synchronization for activating said pressure command signal.
6. In apparatus for applying external pressure assist action to the
limbs of a patient in cyclic synchronization with the heartbeat of
said patient, wherein said apparatus comprises means for producing
a pressure command signal, means for transmitting pressure through
a hydraulic cylinder to said limbs through a fluid-filled bladder
pressurizing means surrounding said limbs in response to means for
activating said pressure command signal, and means for creating an
arterial waveform signal representative of said heartbeat and
display means for monitoring a said waveform signal representative
of said heartbeat in the form of visible traces on said display
means, and wherein the apparatus includes
A. an ideal pressure waveform generator means,
B. actual limb pressure waveform sensing means,
C. said display means forming means for continually comparing said
ideal and actual waveforms, and
D. variable valve means, responsible to a signal from said
comparing means, to modify fluid flow to said hydraulic cylinder
and thereby to transmit pressure to said limbs through said
fluid-filled bladder more nearly achieve said ideal-pressure
waveform at said limbs the improvement wherein said apparatus
comprises:
A. means to provide a first marker pip on display apparatus
displaying a marker trace representative of said arterial waveform
derived from a patient,
B. means to adjust the position of said marker pip relative to said
waveform to a characteristic and identifiable configuration of
arterial waveforms, said adjusting means also forming,
C. means to, form an intensified trace on said waveform,
D. means to move, concurrently with said adjusting, an intensified
trace along said waveform at a constant distance from said first
marker, and
E. means to bring said intensified trace into register with the
dicrotic notch of said waveform, thereby adjusting the
synchronization for activating said pressure command signal.
7. Apparatus as defined in claim 6 comprising:
A. a multi-channel oscillosopce adapted to display
1. an ECG trace, and
2. a trace derived from an arterial pressure sensor,
B. means for visually displaying of the relative time duration of a
pressure command signal on said traces, and
C. manual means to adjust the relative timing and duration of said
pressure command signal, while simultaneously achieving a visual
adjustment of said signal to bring it into the desired relationship
to said ECG trace.
8. In a process for synchronizing a pulsed pressurizing action of
an external pressure circulatory assist apparatus with the
heartbeat cycle of a patient being treated with said apparatus,
said process including the steps of using a display means
exhibiting a trace derived from an arterial pressure sensor as a
means to judge when said pressurizing action is to be initiated,
the improvement comprising the steps of
1. adjusting a reference pip on said arterial trace display means
to that portion of said arterial trace which is indicative of the
start of the systole rise,
2. simultaneously positioning a second marker pip representative of
the time and duration of said pressurization action on said
arterial trace proximate and dicrotic notch portion of said trace
so that said second pip coincides with the dicrotic notch of said
arterial trace, and simultaneously adjusting, through setting a
variable time delay means, the synchronization of a patient's
heartbeat with said pulsed pressurizing action, and
3. adjusting the pulse time of said pressurization action by
operating a duration control means which simultaneously expands the
second marker pip to form a visual representation of the pulse time
on said arterial trace.
Description
BACKGROUND OF THE INVENTION
1. Field of the Invention
This invention relates to a novel apparatus for assisting blood
flow in the circulatory system by synchronizing the pulsing of an
external-assist means with the heartbeat and particularly relates
to a novel synchronization-control system for use with the
aforesaid apparatus.
2. Background of the Invention
Methods for atraumatically assisting blood circulation of patients
have been described in the art. In U.S. Pat. No. 3,303,841 to
Dennis, a process is described whereby an external compressing of
the lower part of the body expresses a volume of blood larger than
the volume of blood pumped in a single stroke of the heart. The
blood so expressed is forced back into the aorta and greater
arterial vessels and thereby allows a reduction in ventricular
workload while maintaining a satisfactory perfusion of blood during
ventricular diastole. This general type of process has been
elaborated upon in an article entitled "Synchronous Assisted
Circulation" by Birtwell et al., appearing in The Canadian Medical
Association Journal (Vol. 95, pages 652-664) on Sept. 24, 1966. In
general, synchronous external pressure assist processes are
distinguishable and advantageous over pre-existing
counter-pulsation processes because the latter kind of procedure
involves the cannulation of a major artery, use of an
extra-corporeal blood handling device, the use of stringently
sterile techniques and the necessity of administering
anti-coagulants to the patient. Moreover, the blood trauma or
hemolysis produced by extra-corporeal pumping devices limits
permissible duration of the assist procedure and compromises the
condition of the patient. Finally, these trauma-requiring
procedures are not only time consuming, they can present a very
significant hazard to many patients, and they increase the risk
factor in treating all patients.
In U.S. Pat. No. 3,654,919 to Birtwell, an improved external assist
apparatus was described wherein the effective pressure on
circulatory passages of the legs could be cycled to valves at or
below ambient pressure. This apparatus is a major advance in the
art and has been extensively used as a vehicle for evaluating the
therapeutic potential of externally assisted circulation. Some
results of this work are reported in a paper entitled "The
Hemodynamic Evaluation of External Counterpulsation in Man" by T.
J. Ryan et al., and presented at the American Heart Association
Scientific Sessions held in Atlatntic City, N.J., during November
1970.
At the present time the external counterpulsation method is the
only controlled method of assist which requires no surgical
intervention or sterile procedures, no use of anticoagulants or
anesthesia, and produces no significant trauma. These factors are
most important because they usually allow a much earlier use of the
apparatus on a patient in, say, a state of circulatory shock than
could be justified if another type of assist apparatus had to be
used.
The selective application of positive and negative pressures to the
portion of the vascular bed in the legs serves to control directly
the volume of blood within that portion of the vascular bed and,
hence, the pressures within the arterial system, particularly the
pressures of the aorta. It is these controlled changes in aortic
pressure that lead directly to a reduction in cardiac work, to
increased perfusion of the systemic circulation, and to
preferential perfusion of the myocardium.
An improved system for providing the desired synchronization of the
heartbeat and the external assist apparatus has been developed more
recently. That system utilized a feedback signal from the external
pressurization of the legs, directly compared this signal to a
control signal representative of the desired waveform for treatment
of the patient and used an error signal derived from the difference
between the aforesaid feedback signal and the control signal to
achieve an adjustment of the pressurization to the desired
waveform. This pressurization, if not properly timed with respect
to the heartbeat, could cause a deleterious, physiological effect
on the patient. Therefore, a simple, accurate, automatic phasing
means was disclosed, whereby an arterial waveform from the patient
is displayed on a multi-channel oscilloscope (or other suitable
display device) in conjunction with an elecrocardiographic
waveform. The arterial pressure waveform would be obtained at a
pre-selected site, for example, at the wrist, and the
electrocardiographic waveform is obtained by placement of sensors
directly on the torso of the patient proximate the heart.
It takes about 80 milliseconds (ms) for a pressure wave, introduced
in the femoral arteries with the apparatus of the invention, to
reach the root of the aorta. The subsequent transmission from the
root of the aorta to the wrist, where the arterial waveform was
typically obtained, takes another 90 ms. It is important that the
artificially-induced positive pressure waves be produced in the
legs sufficiently before diastole (80 ms) and that the pressure
wave reaches the root of the aorta at the beginning of diastole.
Therefore the control system of the aforesaid improved apparatus
comprises a built-in 80-second delay factor adapting it for use on
the pre-selected wrist sensing site.
The start of the augmented diastolic waveform, as seen at the
wrist, which results from use of the applicants' apparatus,
therefore will take place about 170 ms after the pressure is
applied to the legs of the patient. In such a situation, it is
desirable to have the induced pressure wave initiated by a command
signal timed to start 170 ms before the arterial wave, as seen at
the wrist indicates the beginning of diastole and 80 ms before the
ECG signal indicates the beginning of diastole. The beginning of
diastole is indicated in the arterial wave by the so-called
dicrotic notch in good approximation by the end of the so-called
"T-wave" which is known to be positive indication of the relaxation
of the left ventricle and the end of systole.
In the signal phasing system, the leg pressurization signal was
used to intensify the ECG and arterial trace on the oscilloscope
after this pressurization signal has been delayed for 80 and 170 ms
respectively. The duration of intensification is the duration of
each positive pressurization cycle of the leg. With the system, an
operator could adjust the delay time until the intensified signal
on the ECG or arterial wave form is located at the beginning of a
diastole. At that point, leg pressurization can be triggered in
correct synchronization with the cardiac cycle.
Although the above-described system is generally useful and has
been used successfully in some situations, it had the drawback of
depending on a predicted constant delay between the aortic event
and the selected sensing site. It has now been discovered to be
desirable to provide a more versatile means of synchronizing the
heartbeat and the apparatus.
SUMMARY OF THE INVENTION
Therefore, it is an object of the invention to provide an improved
external circulatory assist apparatus.
Another object of the invention is to provide an external
circulatory assist device having a synchronizationcontrol means of
greater versatility.
Another object of the invention is to provide an apparatus easily
synchronized by personnel of moderate skill and training.
A further object of the invention is to provide an improved control
means and method which allows the operator of the apparatus to
accurately synchronize the apparatus without (1) the necessity of
precise prediction of the time delay between the heart action and
its effect on the arterial wave sensing site and (2) without
predicting the sensing site to be selected.
Other objects of the invention will be obvious to those skilled in
the art on their reading this application.
The above objects have been substantially achieved by controlling
the synchronization of the external circulatory assist apparatus
with a control means whereby the optimum time period between a
certain cardiac event (typically the "R" wave of an ECG curve) and
the triggering of the circulatory assist pressure is precisely
achieved by a visual and movable indicator means which can be moved
during the setting of a time variable, throughout a time range
which allows compensation for the time differences between the
cardiac event and its manifestation at any arterial-wave sensing
site which may be selected at the time of treatment.
The visual marker is advantageously electronic and moved along a
channel of an oscilloscope as a trace intensification of a finger
plethysmograph, or some like manifestation of a cardiac event,
until the marker is positioned at an easily-recognized point on the
curve (e.g., at a point indicative of the start of systole).
ILLUSTRATIVE EXAMPLE OF THE INVENTION
In this application and accompanying drawings there is shown and
described a preferred embodiment of the invention and suggested
various alternatives and modifications thereof, but it is to be
understood that these are not intended to be exhaustive and that
other changes and modifications can be made within the scope of the
invention. These suggestions are selected and included for purposes
of illustration in order that others skilled in the art will more
fully understand the invention and the principles thereof and will
be able to modify it in a variety of forms, each as may be best
suited in the condition of a particular case.
IN THE DRAWINGS
FIGS. 1 and 2, taken together, are a schematic diagram of an
external circulatory assist apparatus, including the control means
which forms the particular improvement of this invention.
FIG. 3 is a graph illustrating, in real time, the relationship of
an electrocardiographic curve and external circulatory assist
pressurization.
FIG. 4 is a graph showing curves similar to those which would
appear on a two-channel oscilloscope, displaying (1) an
electrocardiographic curve and (2) any of several alternative
curves manifesting the heartbeat as it is manifested by pressure at
the central aorta, a radial artery or a finger.
Referring now to FIGS. 1 and 2, it is seen that a transducer-type
pressure sensor 34 including a sensing bladder 35 is utilized to
sense hydraulic pressure in bladder 22. If the pressure so sensed
is less than 20 millimeters of mercury (mm of Hg), then a
pressure-level amplifier 46 will provide an output to the
"and-type" gate 48. If during this low-pressure signal situation,
the operator closes a water fill switch 50, he will cause the "and
gate" 48 to transmit a signal which will activate a fill pump 52
through pump control circuit 54 and simultaneously cause a
multiposition, solenoid valve 56 to shift to its fill position,
i.e., the position allowing water to flow from conduit 58 to
conduit 60. Thereupon water will flow into the bladder 22 until a
pressure of 20 mm Hg is sensed by pressure sensor 34. The signal
from amplifier 46 will then drop consequently closing "and-gate"
48. Thereupon, fill pump 52 is deactivated and solenoid valve 56 is
shifted to its off position.
Water is emptied from bladder 22 by using an analogous system
whereby pressure is sensed by sensor 62. In a typical mode of
operation, if the pressure sensed is above a minus 15 mm Hg value,
a signal is sent to "and-gate" 64. If "empty switch" 66 is closed,
the gate 64 will allow a signal command to actuate pump control 68
and "empty pump" 69 and cause solenoid valve 56 to shift to its
empty position, i.e., the position allowing water to flow from
conduit 60 to conduit 70 and thence back to water reservoir 72
through 74. The pump 69 will empty until a pressure of less than
the illustrative minus 15 mm Hg is sensed. At that time the
"and-gate" 64 will no longer sense the required signal from sensor
62, and the pump 69 will be turned off and valve 56 will return to
its off position.
It is noted that the above-described filling and emptying
operations are generally used at the beginning and ending of use
and not as continuous control means. Nevertheless it is emphasized
that the ability to fill the bladder to a particular pre-determined
pressure by automatic means rather than judgement means is highly
advantageous.
During operation of the apparatus, the pressure within bladder 34
is maintained at its desired level by adding or removing water from
the bladder system as follows:
A displacement sensing type transducer 76 is mounted on
hydraulically-actuated rod 78. Transducer 76 is adapted to provide
an electrical signal output proportional to the linear advance of
rod 78 at any given moment.
A normalized value of the position of rod 78 is provided by feeding
the signal from transducer 76 into a displacement level sensor 80.
Thence the normalized signal is provided to a level comparator
82.
A second input to comparator 82 is derived as follows: An ECG
signal from a patient being treated is fed into a trigger generator
84. The trigger generator is so selected that it recognizes and
responds to the so-called "R" wave of the ECG signal. (This wave is
identified by numeral 415 in FIGS. 3 and 4.) Thus when the R wave
periodically occurs with each heartbeat, an output is triggered
which is fed to a manually controlled delay 86. The purpose of
delay 86 is to convert the original signal from first trigger
generator 84 to a second time-delayed signal corresponding in real
time with the beginning of cardiac diastole. This second signal
enters a duration signal generator 88. Generator 88 is so selected
that the signal therefrom continues for the length of time that leg
pressurization (as caused by pressure in bladder 34) is desired.
This signal from generator 88 is fed to level comparator 82 through
a level strobe signal generator 89.
The signal from generator 88 is also fed to a waveform generator 90
which produces a wave whose amplitude and shape is analogous to
that desired for the leg pressurization sequence. A typical such
wave will be trapazoidal-like in shape with a rise of 60 ms, a
plateau of 250 ms, and a fall of 60 ms. This wave from generator 90
is fed to a wave form comparator 92 wherein it is continually
compared to a signal derived from the actual bladder pressure wave
as experienced by sensor 34. The output of comparator 92 is a
so-called "error signal", i.e., a signal which is indicative of the
quality and strength of the difference between the desired wave
signal from generator 90 and the actual wave signal from sensor
34.
It is to be noted in reference to waveform generator 90 that a
typical generated wave will normally have a total positive pressure
period of from about 250 to about 300 milliseconds. The rise and
fall in pressure will take about 60 ms each and rise will start
about 80 ms before diastole. In general, it is desirable to select
a period-determining device which can maintain positive-pressure
periods of up to about 500 ms.
The error signal is used to control servo valve 94 through a
servo-amplifier 93 and thereby controls the supply of fluid to, and
consequently the movement of, hydraulic cylinder 78.
As has been described above, level comparator 82 receives two
signals: one, a periodic signal from a duration signal generator
88, via strobe signal generator 89 and the other from displacement
level sensor 80. lever comparator 82 compares these two signals,
one indicative of the actual position of hydraulic cylinder 78 at a
given time. It is the periodic, or "strobe" signal from duration
signal generator 88, as modified by a level strobe signal generator
89, which determines when this comparison is to be made. The
comparison is most usefully made at the time platen 30 is in the
upper-most portion of its stroke and pressing firmly against
bladder 22.
If level comparator 82 senses that the uppermost position of platen
30 is too high, output signal is provided to a "one shot"
(monostable multivibrator) 96. This "one shot" 96 will then turn on
fill pump 52 and also position solenoid valve 56 for a 0.5-second
fill period. The 0.5-second fill periods will continue during each
cardiac period, (i.e., each heartbeat) until the water volume in
bladder 22 is sufficient so that the uppermost position of platen
30 is within an acceptable displacement range at the top of its
stroke.
If, on the other hand, the level comparator 82 receives a signal
that the uppermost position of platen 30 is too low in its stroke,
the uppermost position of empty pump is turned on for one-half
second on each cardiac cycle by activation of the "one shot" device
98 and the empty pump 69. Water is then pumped out of the bladder
until the platen achieves a desired rise during its stroke.
The general operation of the system described above is known in the
art but is believed to be desirably set forth herein to fully
describe the nature of the improved apparatus subject of the
invention and the manner in which the operation is phased into
correct synchronization with the heartbeat as described below:
A signal from any given arterial pressure-sensing device 99 is fed
into a dual trace oscilloscope 101 along with a signal from ECG
device 102. These signals appear only as width intensifications 103
of ECG trace 104 and the arterial trace 106.
Before discussing the processing of the ECG and arterial wave
signals with respect to the oscilloscope, attention is called to
FIG. 3 which shows the relative real timing of the cardiac cycle as
represented by electrocardiogram 402, radial arterial pressure
waveform 407, and the curve 404, representing the leg pressure rise
405 exerted by the external circulatory assist device on legs of a
patient.
The electrocardiograph is characterized by R wave 415, sometimes
called a "QRS" complex, and a T wave 420 see FIG. 4. The beginning
of systole is manifested at 399 or about 40 ms after the R wave
peak 415. A radial arterial sensing of this heart action will
provide a waveform representative of the heart cycle; however, the
precise time at which the arterial waveform is sensed, as shown in
FIG. 4, will be out of phase with the ECG signal itself by a time
dependent on the particular site at which the arterial waveform is
sensed. Moreover, a modified waveform, and not the arterial
waveform itself, will be sensed at the radial arterial sites. These
modified arterial waveforms are characterized by a so-called
dicrotic notch 409 which is a manifestation of the beginning of
diastole in the cardiac cycle.
In the apparatus described above and known in the prior art, the
external assist pressurization, for example at the legs, was to
occur at a time (D.sub.1) after the triggering signal; 80
milliseconds later the pressure wave reached the heart and after 90
more milliseconds it was sensed at the wrist, the pre-selected
sensing site. Thus, the external pressure wave became effective at
the heart at the start of diastole as desired. This time
corresponds, with reference to an arterial waveform, to the
appearance of dicrotic notch 409 on the arterial waveform at the
wrist and the apparatus was designed to initiate the pressure pulse
at the legs at a time equal to 170 seconds before the manifestation
of diastole at the wrist.
A signal from an arterial pressure-sensing device 99 was fed into a
dual trace oscilloscope 101 along with a signal from ECG device
102. The duration of an intensification of these signals was the
duration of a pressure command signal as received from duration
signal generator 88 and appeared as intensifications of ECG trace
104 and arterial trace 106. Delay devices of 90 milliseconds and 80
milliseconds respectively, caused the pressure command signal to
appear on both waveforms in approximately correct time relationship
referenced to the actual ECG and arterial pressure. D.sub.1 i.e.,
variable delay 86 was used to bring the intensification signal into
register with the diastolic period as viewed on either the ECG or
arterial traces, thereby simultaneously phasing the pressurization
wave to the cardiac cycle.
The operator of the apparatus also has variable control means for
changing the characteristics of the duration signal generator 88 to
provide the intensified signal duration which is required for a
particular patient. On the oscilloscope 100, this duration showed
up as intensifications 103 of the oscilloscope traces.
This prior control system depended for optimum operation on the
pre-selection of a particular arterial-sensing site, such as the
wrist, which would typically be about 90 milliseconds out of phase
with the ECG cycle.
In order to make it possible to avoid pre-selection of a given
delay such as the aforesaid 90 milliseconds between the ECG event
and the sensing thereof at the wrist, the following system is
utilized:
A signal from an ECG device 102 is fed through a trigger generator
84, delay 86, and duration signal generator 88, into an 80 ms delay
device 110 as before. The output from device 110, a pulse equal in
duration to D.sub.4, is delayed from the R wave by a time D.sub.1
(imparted by delay 86) plus 80 milliseconds. This pulse is used to
provide the ECG (Channel 1) intensification.
The pulse is also fed into variable delay device 112, from which a
signal is obtained which is delayed from the R wave by a time
equalling D.sub.1 plus 80 milliseconds plus D.sub.2, wherein
D.sub.2 is the variable delay imparted by adjustable delay device
112.
The trigger signal from trigger generator 84, meanwhile, is being
fed to a 40-millisecond delay device 114, and thence to a variable
delay device 116. The output from device 116 is fed to a marker
generator 118, which generates a marker pulse delayed from the R
wave by D.sub.2 plus 40 milliseconds wherein D.sub.2 is the
variable delay imparted by adjustable delay device 116. The signals
from marker generator 118 and delay device 112 are fed into pulse
mixer 120 and the resulting signal is fed to the channel 2 trace of
the oscilloscope, i.e., that channel showing the arterial
waveform.
In operation, a marker pip from generator 118, and illustrated
alternatively as 414, 415 or 416 on FIG. 4, depending on the
placement of the arterial sensor 99, is moved along arterial trace
106 to a position which is at the start of systole, e.g., as shown
at 414. This position is characterized by the start of a fast rise
403 in the arterial trace.
The marker pip can be moved by use of marker position control 122
throughout a range equivalent to the D.sub.2 variable time delay
simultaneously achievable with delay devices 112 and 116. As the
marker pip is so moved, the intensified trace provided by duration
generator 86 and representative of the external assist pressure
stroke follows the marker pip but is delayed by an amount D.sub.1
less 40 milliseconds from the marker pip.
In use, the operator of the apparatus will first look at the
arterial trace and adjust marker position control 122 and move the
marker pip to its desired position, indicative of the start of
systole. This time is equal to 40 milliseconds plus the delay
imparted by variable delay device 116. Next variable delay device
86, i.e., D.sub.1 will be set by adjusting delay control 124 to
bring the intensification signal into register with the dicrotic
notch, thereby adjusting the time between notch and the
intensification signal to a time represented in FIG. 4 by D.sub.3.
Finally duration generator 88 is set by adjusting duration control
126 to give the proper pulse length, i.e., as shown by numerals
410, 411, 412 and 413 for ECG, Central Aorta, radial artery and
finger plethysmograph, respectively, thereby phasing the
pressurization wave to the cardiac cycle.
It is also to be understood that the following claims are intended
to cover all of the generic and specific features of the invention
herein described and all statements of the scope of the invention
which might be said to fall therebetween.
* * * * *