U.S. patent number 3,557,371 [Application Number 04/735,901] was granted by the patent office on 1971-01-19 for method and apparatus for calibrating a cardiac x-ray synchronizer.
This patent grant is currently assigned to X-Scope Corporation. Invention is credited to Hal Clarence Becker.
United States Patent |
3,557,371 |
|
January 19, 1971 |
METHOD AND APPARATUS FOR CALIBRATING A CARDIAC X-RAY
SYNCHRONIZER
Abstract
Method and Apparatus for calibrating a cardiac X-ray
synchronizer which causes an X-ray machine to produce an X-ray
burst at a given adjustable point in the cardiac cycle of a person
disposed in the burst path by detecting each R-wave peak and
producing a signal actuating the machine at a given adjustable time
after the peak and which displays the cardiac waveform and a pulse
having a duration equal to the inherent time delay between
actuation and burst production so that the operator can set the
trailing edge of the pulse on the point. Calibration is
accomplished by placing an X-ray detector in the burst path and
utilizing a simulated R-wave signal to actuate the synchronizer so
that the X-ray burst signal, the simulated R-wave and the pulse are
displayed. The pulse width is then adjusted so that the trailing
edge coincides with the X-ray burst signal.
Inventors: |
Hal Clarence Becker (New
Orleans, LA) |
Assignee: |
X-Scope Corporation
(Philadelphia, PA)
|
Family
ID: |
24957697 |
Appl.
No.: |
04/735,901 |
Filed: |
June 10, 1968 |
Current U.S.
Class: |
378/95;
250/363.01; 378/207 |
Current CPC
Class: |
H05G
1/62 (20130101); A61B 6/541 (20130101) |
Current International
Class: |
A61B
6/00 (20060101); H05G 1/62 (20060101); H05G
1/00 (20060101); H05g 001/26 () |
Field of
Search: |
;250/93,102,65
;128/2.05,(Inquired) |
References Cited
[Referenced By]
U.S. Patent Documents
Other References
"Cardiopulmonary X-Ray Synchronizer," NASA technical Brief No.
65--10203, .
July, 1965 class 250--93 .
"Cardiac Phase Correlator," Elema-Schonander Stockholm, Sweden,
February, .
1966 class 250--93.
|
Primary Examiner: Archie R. Borchelt
Assistant Examiner: C. E. Church
Attorney, Agent or Firm: Cushman, Darby and Cushman
Claims
1. Apparatus for calibrating an X-ray cardiac synchronizer for use
with an X-ray machine for causing an X-ray burst to be produced at
a given point in the cardiac cycle of a person disposed in the path
of said burst having means for receiving the electrical waveform
representing said cardiac cycle of said person, means for actuating
an X-ray machine an adjustable time after a given portion of said
waveform is received, means for producing a pulse beginning when
said machine is actuated and having a duration equal to the time
between when said machine is actuated and when said burst is
produced, so that the time of occurrence of the trailing edge of
said pulse coincides with the time of production of said burst, and
means for displaying said pulse and said waveform as a function of
time, comprising: an X-ray detector disposable in the path of said
burst for producing an electrical signal characteristic of said
burst when said burst is produced; means for connecting said
electrical signal to said displaying means so that said electrical
signal is displayed with said pulse and said waveform as a function
of time; means for adjusting said duration of said pulse so that
the trailing edge of said pulse coincides with said electrical
signal on said display means so that the duration of said pulse is
equal to the time between when said X-ray machine is actuated and
when said burst is produced; and means for producing a simulated
cardiac waveform, and means for connecting said simulated waveform
to said synchronizer in the same manner as said waveform of said
person so that said simulated waveform is displayed on said
displaying means as a function of time and said actuating means
actuates said X-ray machine an adjustable time after a given
portion of
2. Apparatus as in claim 1 wherein said given portion of said
waveform of said person is the R-wave peak and said simulated
signal is sufficiently similar to said R-wave peak to cause said
actuating means to actuate said
3. Apparatus for causing an X-ray burst from an X-ray machine to be
produced at a chosen point in the cardiac cycle of a person
disposed in the path of said burst comprising: means for detecting
said cardiac cycle and for producing the electrical waveform
representing said cycle; means connected to said detecting means
for amplifying said waveform; means for detecting the R-wave peak
of the amplified waveform; means for actuating said X-ray machine
at a given adjustable time after said R-wave is detected; pulse
generating means for producing a pulse with its leading edge
occurring at the time said X-ray machine is actuated and its
trailing edge at the time said burst is produced; display means for
displaying said pulse and said waveform as a function of time so
that the trailing edge of said pulse coincides with the point in
said waveform at which said burst is produced; means for altering
said given adjustable time to alter said chosen point; manual
operated means for causing said actuating means to activate said
X-ray machine; X-ray detecting means disposable in the path of said
burst for producing an electrical signal representing said burst;
means for connecting said electrical signal to said displaying
means so that said electrical signal is displayed as a function of
time; means for producing a simulated R-wave signal for causing
said actuating mans to actuate said X-ray machine; switch means for
connecting said producing means to said amplifying means and
disconnecting said detecting means from said amplifying means so
that said simulated signal causes said actuating means to actuate
said machine and is displayed on said displaying means as a
function of time; and means for adjusting the width of said pulse
so that when said simulated signal, said electrical signal; and
said pulse are displayed on said displaying means the trailing edge
of said pulse coincides with said
Description
The invention relates to a method and apparatus for compensating
for the time delays inherent in activating an X-ray machine and for
calibrating an X-ray synchronizer so that it can be used with any
given X-ray machine.
A cardiac synchronizer is a device for causing an X-ray picture to
be taken at any predetermined point in the cardiac cycle thereby
enabling the clinician to follow changes in the size of the heart
of a given patient from time to time in an exact manner and to
examine the size of the heart at different points during the cycle.
The conventional procedure for taking X-ray pictures is simply to
manually activate the X-ray machine wherever the subject is in the
desired physical position without reference to the cardiac cycle.
Since the heart size may vary as much as 2 to 3 centimeters in
width between maximum contraction and maximum dilation, it is
impossible, with the conventional procedure to extract any
meaningful information relating to changes in heart size over a
period of time or during a given cycle by comparing X-ray
photographs taken at different times. However, using a cardiac
synchronizer allows these changes to be detected and evaluated.
Several techniques have been developed for detecting heart disease
from such changes or lack of them in the heart size. One such
technique is described in an article entitled "Roentgenographic
Exercise Test" in the Oct. 23, 1967 issue of the Journal of the
American Medical Association and utilizes the two step Master test
or a walk of a given distance such as 100 yards. In a normal heart,
a decrease in heart diameter after such exercise can be detected by
comparing X-ray pictures taken at any given point in the cardiac
cycle before and after the exercise, but the heart in most patients
with certain types of coronary disease shows either no change at
all in heart size or an actual increase in size. Furthermore, this
technique is apparently capable of detecting abnormal conditions
which no other test can. Therefore, photographing the heart at any
given point in the cardiac cycle before exercise and then after
exercise can then serve as an effective test to determine the
presence of certain abnormal cardiac conditions which might
otherwise be undetectable.
One method of photographing the heart at a given point in the cycle
used in cardiac synchronizers is to produce an electrical signal
delayed for an adjustable time with respect to some prominent
characteristic of the electrical waveform produced by the heart,
such as the R-wave peak, and use this delayed signal to activate
the X-ray machine. However, since a certain amount of time is
required between the activating of the X-ray machine and the actual
burst of X-rays, the total time between the R-wave peak and the
actual photographing is the sum of the adjustable delay and the
inherent delay in the X-ray machine itself.
In order to illustrate the time at which the actual burst occurs,
superimposed upon the cardiac waveform, for example on an
oscilloscope, so that the operator can choose the point in the
cycle when firing is to occur without actually taking an X-ray, a
pulse having a time width equal to the inherent delay can be
produced and displayed. The leading edge of this pulse then
represents the instant at which the X-ray machine is activated and
the trailing edge then when the actual burst is produced.
However, the delays inherent in activating the X-ray machine vary
greatly among the different types of machines and particularly
between those devices actuated by a mechanical relay and those
operated by solid state electronic circuits. Even different
machines of a given model display some time variation which is
sufficient to disturb the results of delicate tests. Furthermore,
this inherent time delay may change as the machine ages or after
repair.
The present invention sets forth an apparatus and method whereby
the width of this pulse representing the inherent time delay within
the X-ray machine itself between actuation and firing can be easily
calibrated to exactly equal that inherent time delay which varies
from machine to machine, after the cardiac synchronizer has been
completely installed.
First, an X-ray detector, which produces an electrical signal when
X-rays impinge upon it, is placed in the line of fire of the X-ray
machine and connected into the same electronic circuit which
receives the EKG. signals from the heart. Another electrical
circuit which produces a signal simulating the R-wave peak is also
so connected so that both the simulated R-wave and the X-ray bursts
are displayed on the oscilloscope.
The cardiac synchronizer can then be adjusted to fire at any point
in the cycle and then reacts to the simulated R-wave in the same
manner as it reacts to an actual R-wave peak, by activating the
X-ray machine at the proper time after operation of a manual
control and displaying the pulse imitating the inherent delays on
the oscilloscope. To calibrate the synchronizer then it is only
necessary to operate the manual control and then to adjust the
width of the pulse imitating the inherent delay so that the
trailing edge of the pulse coincides with the displayed burst of
X-rays. After this calibration the R-wave simulator and the X-ray
detector can be removed, the actual EKG. waveform connected to the
synchronizer, and an X-ray photograph taken at any point in the
cycle by adjusting the time between the R-wave peak and the
actuation of the machine until the trailing edge of the pulse
coincides with that point and then simply operating the manual
control.
Other objects and purposes of the invention will become apparent
from the following detailed description of the drawings.
FIG. 1 shows the electrical signals produced by the act of the
heart pumping the blood and detected by attaching electrodes to the
body.
FIG. 2 shows a cardiac X-ray synchronizer with calibrating
apparatus.
FIG. 3 shows the CRT screen of the cardiac X-ray synchronizer while
the synchronizer is being calibrated.
DETAILED DESCRIPTION OF THE DRAWINGS
Reference is now made to FIG. 1 which shows the waveform of the
electrical signals produced by the heart during a complete cycle,
along with the conventional letter representations of the prominent
characteristics. Diastole normally occurs upon the trailing edge of
the R-wave peak, and systole upon the trailing edge of the T-wave.
Since the R-wave peak represents the maximum amplitude of the
signal produced it is convenient to utilize it as a reference point
from which the time to any other point in the cycle can be
measured, and this arrangement is preferred for this embodiment.
However, any of the other characteristics of the cycle can
alternately be used as such a reference is desired.
Reference is now made to FIG. 2 which shows an X-ray synchronizer
10, including calibrating apparatus, and made up of a preamplifier
unit 12 and a control unit 14 which are each disposed in a separate
cabinet. The EKG. electrodes 26, 28 and 30 can be placed on the
patient as desired but preferably they are affixed to the thorax at
the auxiliary regions since there is little muscular activity in
these areas and therefore practically all muscular displacement
artifacts and action potential artifact interference are
eliminated. These electrodes can be quickly and easily affixed by
applying electrode jelly (or pad) and using adhesive tape over the
electrodes to hold them in place. Although only two are normally
used, the third can be attached to a leg, or other suitable
location, if severe external electrical interference is
present.
The three electric leads 26, 28 and 30 lead into the preamplifier
unit 12 where they are connected to a conventional amplifier 32 via
a fuse 34 and a three position switch 36. During normal operation,
the switch 36 connects line 37 to the amplifier 32 as shown.
However, for those occasional persons whose axis is inverted so
that their EKG. Waveform is the negative of the waveform shown in
FIG. 1, an inverted signal is made available on line 38 and switch
36 can be connected to this line in a second position. The third
position of switch 36 connecting line 40 to the amplifier 32 is
used to calibrate the X-ray synchronizer 10 as described below.
A cable 42 connects the preamplifier unit 12 with the main control
unit 14, which may be mounted on or near the control console of the
X-ray machine 61 for easy viewing by the X-ray machine operator.
The preamplifier unit 12 may be located on or near the chest film
rack so that a cable length of 35 to 50 feet may be necessary.
The signal received in the control unit 14 from the cable 42 is
first carried to another amplifier 46 via line 48. The amplifier 46
is equipped with an amplitude control 50 which can be used to
adjust the output signal level on line 52 so that the R-wave peak
is sufficient to operate the detector 54 and not enough to result
in blocking in amplifier 46. This adjustment may be made for each
individual subject, preferably during maximum inspiration. The
output of amplifier 46 on line 52 is then applied to frequency and
amplifier detector 54 which produces a short electrical triggering
pulse or other appropriate signal coinciding with the leading edge
of the R-wave and eliminates the remainder of the waveform shown in
FIG. 1 representing the cardiac cycle.
This short pulse is then passed to an event selector device 56
which delays it for a given and variable amount of time, or
produces a similar short triggering pulse a given time after the
pulse from detector 54 is received. At the end of this given time,
the triggering pulse is conveyed to a driver 58 on line 59, which
actuates the X-ray machine 61 by imposing a suitable electrical
signal on cable 60 whenever the manual control 62 is operated.
This manual control 60 may be simply a hand held unit with a button
which the operator presses when he wishes to take an X-ray
exposure. The cardiac synchronizer 10 will then trigger the machine
61 at the next chosen and appropriate point in the cardiac
cycle.
In every X-ray machine a definite time will elapse between the time
that the machine is activated and when an actual burst occurs. With
conventional methods, this delay is inconsequential but if the
photograph is to be taken at a definite point in the cardiac cycle
the burst itself must coincide with that point and not simply the
activation of the machine. This requires that the X-ray machine be
activated at a time before the given point equal to this inherent
time delay.
The proper time for activating the X-ray machine 61 can be simply
determined by displaying on a CRT or oscilloscope screen in
conjunction with the cardiac wave a pulse having a width equal to
this inherent delay and produced by the signal actuating the
machine 61 so that the leading edge represents the time at which
the X-ray machine 61 is actuated and the trailing edge the time at
which the X-ray burst is actually produced. Therefore, the operator
of the machine 61 can visually select and ascertain at what point
in the cycle the actual photograph will be taken by setting the
trailing edge of this pulse, hereforth called the d pulse, on the
event.
In this embodiment, the d pulse is produced by pulse generator 66
and has a given adjustable width which is varied as described below
to calibrate the synchronizer 10. The generator 66 is activated by
the production of the triggering pulse by the event selector 56
which serves to activate the X-ray machine 61 via driver 58. The
generator 66 is connected to the CRT screen 64 which may be of the
long persistence type so that both the d pulse and the cardiac wave
will appear on the screen 64 continuously before, during and after
actuation of the X-ray machine 61.
To take an exposure, the operator merely attaches the electrodes
26, 28 and 30 to the subject and applies a suitable source of
electrical energy (not shown) to the synchronizer 10. The cardiac
waveform shown in FIG. 1 and the d pulse produced by each R-wave
peak then appear on the CRT screen 64. Then the trailing edge of
the d pulse can be merely adjusted without altering the width of
the d pulse, which merely represents the inherent and unchanging
delay in the X-ray machine 61, to coincide with the event at which
the X-ray burst is chosen to occur by adjusting the event selector
56. Finally, the manual control 62 is operated so that an X-ray
burst results from the signal produced by the driver 58 at the time
of the event selected.
The synchronizer 10 can be associated with other devices to perform
different functions and this capability is represented in FIG. 2 as
an input terminal 68 with two arrows carrying electrical signals
outward and one carrying signals inward. One of the outwardly
directed arrows represents a connection to a strip chart recorder
which can produce a permanent record for later study of the cardiac
waveform and the d pulse. Furthermore, the strip chart recorder can
also be used to record the X-ray burst on the strip chart recorder
by disposing an X-ray detector in the path of the X-ray bursts. The
other of the outward directed arrows represents the connection to
another remote display such as another oscilloscope or CRT
screen.
The inwardly directed arrow represents a possible connection to a
pulmonary synchronization unit which can be used to ensure that
triggering of the X-ray machine occurs only at some level of
inspiration, normally maximum inspiration or exhaustion. For
example, the U.S. Pat. No. 2,967,944, to Lusted, describes one such
system for triggering upon some level of inspiration. Of course,
many other exterior devices can be attached and these three are
only exemplary.
Reference is now made to FIG. 3 which shows the signals which are
displayed on CRT screen 64 during calibration, and the calibrating
operation will now be described in detail. To calibrate the cardiac
synchronizer 10, so that the width of the d pulse is exactly equal
to the inherent delay in the X-ray machine 61, the switch 36 is
first shifted so as to contact line 40. Connected to line 40 is an
R-wave peak simulator 74 which produces an electrical signal which
is similar to the R-wave peak of the normal cardiac cycle and an
X-ray detector 72. It is in this embodiment not necessary to
attempt to imitate the entire cardiac waveform since only the
R-wave is used as a reference. Of course, if another portion of the
cycle such as the Q or S valleys where utilized as the reference
then that portion would be limited during calibration.
This simulated R-wave signal is then amplified by amplifier 32,
conveyed to the control unit 14 on the cable 46 and properly
amplified by the amplifier 42 in the same manner as the ordinary
cardiac waveform. The simulated R-wave then passes the frequency
and amplitude detector 54, and operates on the event selector 56 to
trigger the driver 58 after a given time has elapsed, which in turn
activates the X-ray machine 61 in the same manner as a genuine
R-wave peak, whenever the manual control 62 is operated. Since for
the purpose of calibration of the d pulse it makes no difference
which event is selected, the event selector 56 can be arbitrarily
set to produce an X-ray burst at any arbitrary time during the
cardiac cycle. The passage of a simulated R-wave through the
control unit 14 then operates to trigger the X-ray machine 61,
producing a burst of X-rays.
The X-ray detector 72 is disposed so as to intercept a portion of
this burst and to produce an electrical signal characteristic of it
which can be passed through amplifiers 32 and 46 and displayed on
the CRT screen 64. The detector may be simply a fluorescent screen
optically coupled to a solid-state photocell encased in epoxy resin
disc and may be taped to the X-ray tube cone to intercept the beam,
providing an electrical signal proportional to, and in phase with,
the emitted X-ray intensity. This signal is shown in FIG. 3 and
labeled "Burst from X-ray Detector." Alternatively, any other
suitable device for producing an electrical signal indicating a
burst can be employed.
The d pulse, the simulated R-wave, and the X-ray bursts will then
appear on the CRT screen 64 as shown in FIG. 3 and to calibrate the
synchronizer, it is only necessary to alter the width of the d
pulse so that its trailing edge coincides with the initiation of
the pulse of the X-ray as shown. When this adjustment is completed
the width of the d pulse will then be exactly equal to the inherent
time delay between the actuation of the X-ray machine 61 and the
actual production of an X-ray burst. Since this time may change
slightly over a period of time, this simple calibration can be made
as often as desired to ensure accurate results.
The above embodiment merely represents one example of the invention
and any changes and modifications are possible without departing
from the spirit of the invention. Consequently, the scope of the
invention is limited only by the scope of the appended claims.
* * * * *