U.S. patent number 3,566,876 [Application Number 04/690,586] was granted by the patent office on 1971-03-02 for defibrillator.
This patent grant is currently assigned to SAID Stoft assignor to Hewlett-Packard Company. Invention is credited to Robert F. Shaw, Paul E. Stoft.
United States Patent |
3,566,876 |
Stoft , et al. |
March 2, 1971 |
DEFIBRILLATOR
Abstract
A monopolar cardiac defibrillator obviates the need for bulky
storage capacitors by operating directly from line signal to supply
a high power-defibrillating pulse substantially as a half-wave
portion of the line signal the defibrillating pulse is generated in
timed relationship to a patient's electrocardiogram by activating a
signal-controlled switch to apply a half wave of line signal to the
defibrillator circuitry.
Inventors: |
Stoft; Paul E. (Menlo Park,
CA), Shaw; Robert F. (San Francisco, CA) |
Assignee: |
SAID Stoft assignor to
Hewlett-Packard Company (Palo Alto, CA)
|
Family
ID: |
24773075 |
Appl.
No.: |
04/690,586 |
Filed: |
December 14, 1967 |
Current U.S.
Class: |
607/5;
607/72 |
Current CPC
Class: |
A61N
1/3904 (20170801); A61B 5/352 (20210101) |
Current International
Class: |
A61B
5/0452 (20060101); A61B 5/0456 (20060101); A61N
1/39 (20060101); A61n 001/36 () |
Field of
Search: |
;128/419--424,419
(D)(digest)/ |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
Other References
Leeds, "Journal of American Medical Association," Vol. 152, No. 15,
Aug. 8, 1953, pp. 1411--1413 (128-419D).
|
Primary Examiner: Kamm; William E.
Claims
We claim:
1. Monopolar defibrillator apparatus for applying an electrical
signal to a mammalian subject, the apparatus comprising:
an input for receiving alternating signal from a source;
output means for applying an electrical signal to a subject;
a transformer having primary and secondary windings;
signal controllable switch means connecting the primary winding of
said transformer to said input for applying a selected portion of a
half cycle of alternating signal appearing at said input to said
transformer in response to a control signal applied to said switch
means;
circuit means connecting said secondary winding to said output
means and including a first diode connected to conduct current in
one direction to said output means from said secondary winding for
signal therefrom of one polarity, and including a second diode and
impedance means in series therewith for conducting current through
said second diode and impedance means from said secondary winding
for signal therefrom of the opposite polarity; and
control means connected to said switch means to apply a control
signal thereto at a selected time for applying said selected
portion of alternating signal to said transformer.
Description
BACKGROUND OF THE INVENTION
Conventional cardiac defibrillators commonly include a storage
capacitor for storing a sufficient quantity of charge to supply to
a patient a defibrillating pulse of about 2000 volts and 20 amperes
for about 5 milliseconds. The physical size and weight of the
storage capacitor is typically of the order of 1 cubic foot and
several pounds and thus is not readily conductive to miniaturized
packaging and convenient portability. Defibrillator apparatus of
this type is described in the literature (See U.S. Pat. No.
3,236,239 issued on Feb. 22, 1966 to B. V. Berkovits). Also, the
time required between defibrillating pulses to charge the storage
capacitor of such conventional defibrillator apparatus prevents the
delivery of several defibrillating pulses in rapid succession.
SUMMARY OF THE INVENTION
The present invention obviates the need for a storage capacitor to
supply a high voltage, high current-defibrillating pulse by
operating directly from a half-wave portion of applied line signal.
Synchronization of the defibrillating pulse with the heart beat of
a patient may be accomplished using conventional means coupled to a
signal-controlled switch in the line signal circuit.
DESCRIPTION OF THE DRAWING
The drawing shows a schematic diagram and selected signal waveforms
present in the defibrillator circuit of the present invention.
DESCRIPTION OF THE PREFERRED EMBODIMENT
Referring now to the drawing, there is shown a line input 9 which
may be connected to receive an alternating signal 11 from the power
lines. The power line signal at input 9 is applied to the primary
winding 13 of a step-up transformer 15 through a controlled
rectifier 17 or other suitable signal-controlled switch. The
voltage step-up ratio from the primary 13 to the secondary winding
19 of the transformer 15 may be as high as 30 to provide a
secondary voltage as high as 2000 volts, even under conditions
where the voltage applied to the primary may be as low as 60 volts
at the peak of the half sine wave supplied to the primary winding
13. The pulse 20 of voltage produced on the secondary winding 19
when controlled rectifier 17 is conductive is applied to the
patient 23 through diode 21, connecting cables 24 and the contact
electrodes 25 suitably positioned on the chest of the patient 23.
Typical peak values of the wave 20 applied to the patient 23 are
about 2000 volts and 20 amps for about 5 to 10 milliseconds. The
secondary winding 19 may include a plurality of taps to alter the
turns ratio and provide selected values of secondary voltages and
currents.
For power line frequency of 60 cycles, the pulse width of a
half-wave is about 8 milliseconds. The portion of the line signal
applied to the primary winding through the controlled rectifier 17
may be regulated simply by adjusting the electrical angle 22 at
which the controlled rectifier 17 is rendered conductive. The
inductance and resistance in the circuitry which supplies the
defibrillating pulse 20 to the electrodes 25 smooths out transients
upon turn-on of controlled rectifier 17 and causes a small amount
of undershoot 26 in the defibrillating pulse 20. This undershoot
portion of the waveform produces a reversal of pulse polarity which
causes diode 21 to become nonconductive and which renders diode 27
conductive. The undershoot portion 26 is not applied to the patient
but rather is dissipated in the resistor 29 which is serially
connected with diode 27 across the secondary winding 19 of
transformer 15.
It should be noted that the peak secondary current of about 20
amperes requires a peak primary current of several hundred amperes
which must be supplied from the applied power line signal. However,
since the primary current of such high value flows from the power
lines only during a portion of a half-wave period, and since the
response time of fuses is typically equal to the period of a few
cycles of line signal, the average power supplied to the circuit of
the present invention during such response time is sufficiently low
so that fuses in the supply lines are not blown. Thus, the
transformer 15 may be relatively small in size with typically core
dimensions of about 21 .times. 21 centimeters with a 7 .times. 7
centimeter cross section. The primary winding comprises wire of
sufficiently large cross section to carry the high peak current and
the number of primary turns with reference to the number of
secondary turns is selected with due consideration for the fact
that such high primary currents produce high line drops and thus
that only about 60--70 volts may be available across the inputs 9
at the time peak current flows in the primary winding 13.
Conventional electrocardiographic apparatus 28 may be attached to
the patient 23 using pickup electrodes 30, 32 suitably positioned
on the patient to receive the electrocardial signals 34. The
apparatus 28 may include a monitor 36 such as an oscilloscope or
strip chart recorder which is connected to provide a continuous
display of the patient's electrocardial signals 34.
In operation, it is desirable that defibrillating pulses be applied
to the patients with nonfibrillating hearts during the period of
the electrocardial signal waveform designated t.sub.a to t.sub.b
and avoided during the period t.sub.b to t.sub.c. During the period
t.sub.a to t.sub.b several cycles of the line signal occur and thus
the controlled rectifier 17 may be rendered conductive during any
one of these cycles occurring during this desirable period t.sub.a
to t .sub.b. A synchronized pulser 39 responsive to the predominant
QRS portion of the electrocardial signal may thus include a
conventional monostable multivibrator or other suitable circuit for
generating the conduction-initiating gate pulse 41 and may include
transformer coupling to the gate electrode of controlled rectifier
17 so that true isolation of the patient 23 from line signal is
preserved. The synchronized pulser 39 may also include conventional
lockout circuitry for preventing gate pulses 41 from being
generated during the undesirable period t.sub.b to t.sub.c.
It should be apparent that the present circuit may also be operated
with a controlled rectifier in place of diode 21 where it is
desirable to switch lower currents. However, the high secondary
voltage presents some problems in biasing and insulating a trigger
circuit for a controlled rectifier so connected, and also may
require that another controlled rectifier connected in place of
diode 27 be rendered conductive in the following half cycle to
dissipate the undershoot portion 26 of the defibrillating pulse
20.
Therefore, the defibrillator circuit of the present invention
obviates the need for a large and heavy storage capacitor by
supplying to a patient a high power-defibrillating pulse derived
directly from the power lines. The present circuit thus eliminates
the requirement of charging time between defibrillating pulses and
therefore permits several such pulses to be supplied to a patient
in rapid succession.
* * * * *