U.S. patent number 3,653,387 [Application Number 05/033,172] was granted by the patent office on 1972-04-04 for protector circuit for cardiac apparatus.
This patent grant is currently assigned to Cardiac Electronics, Inc.. Invention is credited to Richard R. Ceier.
United States Patent |
3,653,387 |
Ceier |
April 4, 1972 |
PROTECTOR CIRCUIT FOR CARDIAC APPARATUS
Abstract
A protector circuit having relay arrangement and gas discharge
tubes coupled between first electrodes attached to a patient and
the amplifier of an electrocardiograph, the relays comprising fast
acting reed relays which break the circuit when a defibrillator is
energized to apply a countershock voltage across second electrodes
mounted on said patient, to prevent the countershock voltage from
distorting the heartbeat waveform produced by the
electrocardiograph. The gas discharge tubes prevent voltages in
excess of a predetermined value from reaching the amplifier by
conducting such voltages to ground, whether the relays are opened
or closed.
Inventors: |
Ceier; Richard R. (East Aurora,
NY) |
Assignee: |
Cardiac Electronics, Inc.
(Clarence, NY)
|
Family
ID: |
21868924 |
Appl.
No.: |
05/033,172 |
Filed: |
May 8, 1970 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
Issue Date |
|
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653201 |
Jul 13, 1967 |
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Current U.S.
Class: |
600/525;
607/5 |
Current CPC
Class: |
A61B
5/304 (20210101); A61N 1/3931 (20130101); A61N
1/3912 (20130101) |
Current International
Class: |
A61B
5/0428 (20060101); A61B 5/0402 (20060101); A61N
1/39 (20060101); A61b 005/04 () |
Field of
Search: |
;128/2.5R,2.06,419D |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
Primary Examiner: Oechsle; Anton O.
Parent Case Text
The present application is a continuation of application, Ser. No.
653,201, filed July 13, 1967, and now abandoned.
Claims
I claim:
1. An electrocardiograph circuit comprising electrode means adapted
to be coupled to a patient for detecting a heartbeat, heartbeat
signal amplifier means, display means for providing a visual
indication of said patient's heartbeat, circuit means coupling said
electrode means and said heartbeat signal amplifier means and said
display means, circuit protector means in said circuit means
coupled between said electrode means and said heartbeat signal
amplifier means for effectively disconnecting said electrode means
from said heartbeat signal amplifier means for selectively
preventing distortion producing voltages from being conducted to
said heartbeat signal amplifier means and thereby preventing
distortions in said heartbeat signal amplifier means which can
result in a distorted representation on said display means, said
circuit protector means including relay means, defibrillator
circuit means, switch means in said defibrillator circuit means for
selectively energizing said defibrillator circuit means to apply a
countershock voltage to a patient, second circuit means coupling
said defibrillator circuit means to said circuit protector means
and energizable incidental to the energization of said
defibrillator circuit means for causing said circuit protector
means to prevent distortion producing voltages produced incidental
to defibrillation from being conducted to said heartbeat signal
amplifier means, and third circuit means having voltage discharge
means therein coupled between said electrode means and said relay
means for conducting voltages in excess of a predetermined value
applied to said electrode means away from said relay means and said
heartbeat signal amplifier means, said relay means comprising fast
acting reed relay means in said circuit means for opening said
circuit means between said electrode means and said heartbeat
signal amplifier means before said defibrillator circuit means
apply said countershock voltage to said patient.
2. An electrocardiograph circuit comprising electrode means adapted
to be coupled to a patient for detecting a heartbeat, heartbeat
signal amplifier means in said electrocardiograph circuit for
amplifying a heartbeat signal picked up by said electrode means,
display means for providing a visual indication of said patient's
heartbeat, first circuit means coupling said electrode means and
said heartbeat signal amplifier means, second circuit means
coupling said amplifier means and said display means, circuit
protector means in said first circuit means coupled between said
electrode means and said heartbeat signal amplifier means with said
electrode means being in immediate preceding relationship to said
circuit protector means which in turn are in immediate preceding
relationship to said heartbeat amplifier means, said circuit
protector means effectively disconnecting said electrode means from
said heartbeat signal amplifier means for preventing distortion
producing voltages from being conducted to any portion of said
heartbeat signal amplifier means and thereby preventing distortions
in said heartbeat signal amplifier means which can result in a
distorted representation on said display means, said circuit
protector means including relay means for disconnecting said
electrode means from said heartbeat signal amplifier means,
defibrillator circuit means, switch means in said defibrillator
circuit means for selectively energizing said defibrillator circuit
means to apply a countershock voltage to a patient, third circuit
means coupling said defibrillator circuit means to said circuit
protector means and energizable incidental to the energization of
said defibrillator circuit means for causing said circuit protector
means to prevent distortion producing voltages produced incidental
to defibrillation from being conducted to said heartbeat signal
amplifier means, means for causing said circuit protector means to
automatically reconnect said electrode means to said heartbeat
signal amplifier means after said switch means is released after
the termination of said countershock voltage to cause said display
means to provide said visual indication of said patient's heartbeat
immediately after the termination of said countershock voltage,
said relay means comprising fast acting reed relay means in said
first circuit means for opening said first circuit means between
said electrode means and said heartbeat signal amplifier means
before said defibrillator circuit means apply said countershock
voltage to said patient.
3. An electrocardiograph circuit comprising electrode means adapted
to be coupled to a patient for detecting a heartbeat, heartbeat
signal amplifier means in said electrocardiograph circuit for
amplifying a heartbeat signal picked up by said electrode means,
display means for providing a visual indication of said patient's
heartbeat, first circuit means coupling said electrode means and
said heartbeat signal amplifier means, second circuit means
coupling said amplifier means and said display means, circuit
protector means in said first circuit means coupled between said
electrode means and said heartbeat signal amplifier means with said
electrode means being in immediate preceding relationship to said
circuit protector means which in turn are in immediate preceding
relationship to said heartbeat amplifier means, said circuit
protector means effectively disconnecting said electrode means from
said heartbeat signal amplifier means for preventing distortion
producing voltages from being conducted to any portion of said
heartbeat signal amplifier means and thereby preventing distortions
in said heartbeat signal amplifier means which can result in a
distorted representation on said display means, said circuit
protector means including relay means for disconnecting said
electrode means from said heartbeat signal amplifier means,
defibrillator circuit means, switch means in said defibrillator
circuit means for selectively energizing said defibrillator circuit
means to apply a countershock voltage to a patient, third circuit
means coupling said defibrillator circuit means to said circuit
protector means and energizable incidental to the energization of
said defibrillator circuit means for causing said circuit protector
means to prevent distortion producing voltages produced incidental
to defibrillation from being conducted to said heartbeat signal
amplifier means, and a fourth circuit means having voltage
discharge means therein coupled between said electrode means and
said relay means for conducting voltages in excess of a
predetermined value applied to said electrode means away from said
relay means and said heartbeat signal amplifier means, means for
causing said circuit protector means to automatically reconnect
said electrode means to said heartbeat signal amplifier means after
said switch means is released after the termination of said
countershock voltage to cause said display means to provide said
visual indication of said patient's heartbeat immediately after the
termination of said countershock voltage, said relay means
comprising fast acting reed relay means in said first circuit means
for opening said circuit means between said electrode means and
said heartbeat signal amplifier means before said defibrillator
circuit means apply said countershock voltage to said patient.
Description
BACKGROUND OF THE INVENTION
The present invention may be used in conjunction with the
defibrillating apparatus disclosed in application, Ser. No.
529,410, filed Feb. 23, 1966, in the name of Joseph H. McLaughlin,
now U.S. Pat. No. 3,527,228.
The present invention relates to improved apparatus for treating a
cardiac patient and more particularly to an improved protector
circuit for preventing stray voltages from affecting the accuracy
of the visual representation of the heartbeat produced by an
electrocardiograph.
By way of background, multi-purpose electrocardiac apparatus is
capable of performing a plurality of functions. One of the
functions is to monitor the heartbeat of a patient and display this
heartbeat in visual form on an oscilloscope, graph or the like.
This is the conventional electrocardiograph apparatus, which
obtains its intelligence through electrodes applied to the patient.
Another function of the improved electrocardiac apparatus is to
selectively apply defibrillating countershock voltage to a patient
experiencing fibrillation, which is an irregular heartbeat.
Broadly, this consists of applying a very high countershock voltage
to the heart of the patient through electrodes placed in opposition
to each other on the patient's back and chest to cause a current
flow through the chest cavity. When the countershock voltage is
applied, the patient acts as a conductor and this countershock
voltage, which may be of extremely high magnitude, on the order of
7,500 volts, may be transmitted to the electrodes of the
electrocardiograph apparatus and set up stray voltages which may
completely distort the visual representation of the heartbeat for a
period of as much as 20 to 30 seconds. It is extremely important
that an accurate visual representation of the patient's heartbeat
be obtained immediately after application of the countershock
voltage, so that the effect of the countershock voltage can be
readily observed. The reason for this is that many times additional
countershock voltage must be applied immediately after the initial
countershock application of voltage if the application of the first
countershock voltage is ineffective. However, as can readily be
seen, if the electrocardiograph is producing an inaccurate signal,
or one which is objectionally distorted, there is no clear
intelligence upon which to base the decision as to whether
additional countershock voltage should be applied. It is with
improved electrocardiac apparatus which overcomes the foregoing
shortcoming that the present invention is concerned.
SUMMARY OF THE INVENTION
It is accordingly one object of the present invention to provide a
protector circuit for electrocardiograph apparatus which prevents
stray voltages above a predetermined magnitude from affecting the
visual representation of the heartbeat on the electrocardiograph,
thereby assuring that such representation remains undistorted and
true.
Another object of the present invention is to provide improved
electrocardiac apparatus for providing a visual representation of a
patient's heartbeat and for providing countershock voltage to the
patient's heart, with a protector circuit for preventing the
countershock voltage which is applied to the patient from adversely
affecting the visual representation on the electrocardiograph,
thereby providing an accurate picture of the patient's heartbeat at
all times regardless of the voltages to which a patient may be
subjected.
A further object of the present invention is to provide improved
electrocardiograph apparatus including a protector circuit having a
first circuit which causes the display portion of the
electrocardiograph apparatus to be disconnected from the patient
during the application of a countershock voltage and in addition
includes a second circuit which prevents any countershock voltage
applied to the patient from being transmitted to the
electrocardiograph apparatus in the event disconnecting is not
fully completed by said first circuit or in the event the
distorting voltage comes from any other source. Other objects and
attendant advantages of the present invention will readily be
perceived hereafter.
The improved electrocardiac apparatus of the present invention
includes an electrocardiograph for providing a visual
representation of the patient's heartbeat and a defibrillator for
providing countershock voltage to the patient for treatment of
either ventricular fibrillation or other arrhythmias. The
electrocardiograph has electrodes coupled to the patient in the
conventional manner. The defibrillator has electrodes coupled to
the chest and back of the patient. A protector circuit
interconnects the defibrillator and the leads leading to the
electrocardiograph display device. When the defibrillator is
actuated, the leads to the electrocardiograph are automatically
disconnected prior to the application of the countershock voltage
and automatically reconnected after the countershock voltage has
been applied. Thus, during the period of applying the countershock
voltage, which is only approximately 21/2 milliseconds, stray
voltages produced incidental to the application of defibrillating
voltage cannot affect the picture of the patient's heartbeat on the
display device. After this brief period of disconnection, the
picture reappears with complete accuracy. In addition, in the event
that disconnecting should not be effected as required, or in the
event the patient is subjected to a stray voltage from any source
other than the defibrillator, the protector circuit includes
circuit means for preventing such voltages from reaching the
apparatus, thereby insuring an accurate picture thereon. By the use
of the foregoing protector circuit an accurate representation of
the patient's heartbeat on the electrocardiograph apparatus is
always assured. The present invention will be more fully understood
when the following portions of the specification are read in
conjunction with the accompanying drawing.
DESCRIPTION OF THE PREFERRED EMBODIMENT
In the drawing the improved apparatus is shown which includes an
electrocardiograph 10, a defibrillator circuit 11, and a protector
circuit 12 coupling the electrocardiograph and the defibrillator.
The electrocardiograph apparatus 10 includes three sensor
electrodes 13, 14 and 15, the latter being coupled to ground.
Electrodes 13, 14 and 15 are attached to patient 18, as on his
opposite wrists, and suitable electrical contact is made by the use
of electrode jelly. Electrode 15 is attached to the leg of the
patient. Electrodes 13 and 14 are coupled to protector circuit 12
through leads 16 and 17, respectively. Leads 19 and 20, leading
from circuit 12, are coupled to amplifier 21 which effects suitable
amplification of the heartbeat waveform. The amplified heartbeat is
visually indicated on cathode ray oscilloscope 22 by feeding the
amplified signal from amplifier 21 to vertical amplifier 23 through
leads 24 and 25, the output of vertical amplifier 23 being applied
to plates 24' and 25' through leads 26 and 27, respectively. This
signal is used to modify the trace provided by horizontal free
running sweep amplifier 28 which is coupled to plates 29 and 30 by
leads 31 and 32, respectively. In lieu of oscilloscope 22 any other
type of visual indicating device, such as a graph or an elongated
paper tape or the like, may be used.
The heartbeat waveform comprises a QRS complex including the Q
portion, R portion and S portion as shown on the scope in FIG. 1.
The countershock voltage is applied across the chest cavity of the
patient by electrodes 33 and 34 which are coupled to leads 35 and
36, respectively, leading from the defibrillator circuit 11. One of
these electrodes is mounted on the chest and the other on the back
of the patient 18.
Summarizing the following portion of the specification briefly at
this point, it can be seen that the electrodes 33 and 34 leading
from the defibrillating circuit 11 and the electrodes 13, 14 and 15
leading to the electrocardiograph 10 are both mounted on patient
18. The countershock voltage, which may be as high as 7,500 volts,
or translated into energy, in excess of 400 joules, when applied to
the patient 18, may also be transmitted through the patient, who
thus acts as a conductor, to the electrocardiograph apparatus 10 in
the absence of a protector circuit 12. This direct application to
the electrocardiograph apparatus will set up stray voltages therein
which will completely distort the picture of the heart waveform on
oscilloscope 22 for as long as 20 to 30 seconds. During this period
the oscilloscope 22 will be incapable of providing accurate
information as to the heartbeat of the patient. It is during this
period that accurate information is critical to determine whether
additional countershock should be applied. The instant protector
circuit 12 contains switch means which disconnect the
electrocardiograph 10 from the defibrillator circuit 11 when the
countershock voltage is being applied and automatically reconnects
the electrocardiograph 10 to the patient 18 after the countershock
voltage is no longer being applied, to thereby protect the
electrocardiograph and insure accuracy of the pictorial
representation of the heartbeat thereon. The mode of operation of
the defibrillator circuit 11 and the interrelationship between the
electrocardiograph 10 and the protector circuit 12 will be more
fully understood from the ensuing portions of the description.
The instant defibrillator circuit 11 provides a synchronized
countershock to a patient, that is, in timed relationship to the
patient's heartbeat. This is explained in detail in the above noted
copending application. However, a certain repetition will be made
here for the purpose of completeness. It will be appreciated that
the protector circuit 12 of the present invention can be used with
any type of defibrillator circuit and any type of
electrocardiograph.
The amplified heartbeat signal at lead 24 is also fed to Schmitt
trigger 37 by lead 38 to produce waveform 39 which in turn is fed
to single shot multivibrator 40 by lead 41. It is the multivibrator
40 which produces a usable signal 42 in synchronized relationship
to the heartbeat. The lead portion 43 of signal 42 is initiated
when the R portion of the heartbeat 17 reaches a predetermined
magnitude. Lead 45 conducts waveform 42 from multivibrator 40 to
the indicating device 44, which indicates whether multivibrator 40
is operating satisfactorily. The indicating device 44 may include a
pulse form inverter (not shown) for inverting waveform 42, an
amplifier (not shown) and an integrator (not shown) in series, with
the integrator being coupled to a meter. As is well understood, the
foregoing components level out the pulse 42 to provide a constant
output which can be read on the meter forming a part of indicating
device 44. The foregoing elements are shown in detail in the above
mentioned copending application but are omitted from the instant
drawing in the interest of brevity. The magnitude of the reading on
the meter associated with device 44 is proportional to the
heartbeat rate.
When a heart pattern is shown on scope 22 which indicates that
countershock is necessary, the attending physician will close
defibrillator switch 46 to establish contact between leads 47 and
48. Preferably, however, switch 46 should be in lead 53. The output
of multivibrator 40 is fed to silicon control rectifier 49 by lead
50, which is connected to lead 45. The silicon control rectifier 49
will be energized whenever the lead portion 43 of square wave 42
reaches a predetermined magnitude to cause current to flow from B+
to ground through lead 51, slow acting relay coil 52, lead 53,
silicon control rectifier 49, lead 47, defibrillation switch 46,
and lead 48 to ground. Whenever the silicon control rectifier 49 is
energized to complete the above circuit, relay coil 52 will be
energized. At this point it is only necessary to understand the
energization of coil 52 is synchronized with the patient's
heartbeat and that the relay 55 of which coil 52 forms a part
actuates the remainder of the circuit which supplies the
countershock voltage.
An AC source 56 is coupled across leads 57 and 58 with sine wave 59
depicting the waveform at this point. The normally centered
armature 60 of switch 61 is selectively movable from a normally
open position to either contact 62 or 63. As can be seen, when
armature 60 contacts contact 63, a circuit will be completed
through the primary 64 of transformer 65, which in turn will induce
a voltage in the secondary winding 66. As will become more apparent
hereafter, a charge will be placed on capacitor 67. The magnitude
of the charge depends on the length of time that armature 60 is
held on contact 63. After armature 60 is released it will return to
a normally open position and capacitor 67 will retain a charge
thereon. If it is desired to cause a lower voltage to be induced on
the secondary winding 66, it is merely necessary to move armature
60 into engagement with contact 62 to complete a circuit to primary
winding 64 through resistor 69.
The charge is placed on capacitor 67 through the following circuit.
The output of secondary winding 66 is rectified by diodes 70 which
are coupled to one side of secondary 66 by lead 71. Diodes 70 are
coupled in series to prevent a reverse discharge thereacross after
a charge is placed on capacitor 67, which is coupled in series with
diodes 70 and secondary 66 through lead 72, armature 73 of slow
acting relay 55, lead 74, choke coil 75, lead 76 and lead 77. At
this point it is to be noted that lead 77 is grounded at 82' to the
chassis of the apparatus through resistor 78, armatures 79 and 80
of fast-acting relay and lead 82.
Relay 81 is of the normally open type. Armatures 79 and 80 of
fast-acting relay 81 are in engagement whenever there is a B+
voltage applied at terminal 83. The foregoing engagement is
effected because coil 88 is energized through the path consisting
of lead 51, winding 52, lead 53, lead 84, voltage drop resistor 85,
lead 86, lead 87, winding 88 of relay 81, lead 89 and lead 90 to
ground. This energization of relay 81 occurs whenever the apparatus
is turned on through its master switch (not shown). Otherwise,
armatures 79 and 80 are not in engagement and line 77 is not
grounded. Because of the parameters of the circuit, armatures 79
and 80 will move into contact to couple the circuit to chassis
ground 82'. However, there will be an insufficient flow of current
through slow-acting relay coil 52 to energize slow-acting relay 55
and therefore armature 73 thereof will occupy the position shown in
the drawing. There is also a small current flow from lead 86
through lead 91, diode 92, lead 93, resistor 94 and lead 95 to
ground. However, there will be a delay before there is a build-up
of voltage across capacitor 96, which is coupled across leads 93
and 95 and it is only after voltage builds up of capacitor 96 that
coil 88 will be energized.
The above described voltage which is applied to capacitor 67 is
selectively discharged across the chest cavity of a patient to
effect defibrillation. Quantitatively, this voltage may be as high
as 7,500 volts, or translated into energy, in excess of 400 joules.
The magnitude of this voltage depends upon the charging time
through armature 60 and it can be read on meter 97 which is coupled
across capacitor 67 through resistor 98. If for any reason it is
desired to harmlessly discharge the voltage built up on capacitor
67, it is merely necessary to close switch 99 to thereby discharge
capacitor 67 through resistor 100.
To apply the countershock voltage to the patient 18, electrodes 33
and 34, which are in the form of paddles, are coupled onto the
opposite of the chest cavity of patient 18 by means of a suitable
electrode jelly to establish good electrical contact. One paddle is
mounted on the chest and the other paddle is mounted in opposition
thereto on the back of the patient, with the heart essentially
being located therebetween. Paddles 33 and 34 each include a
conducting plate (not shown) which are electrically connected to
leads 35 and 36. The remainder of paddles 33 and 34 are made out of
a suitable non-conductive plastic material to confine the
electrical countershock. Paddles 33 and 34 are conveniently
provided with insulating handles 101 and 102.
As noted above, the capacitor 67, which provides the countershock
voltage, is in charged condition while relay armature 73 is in the
position shown in the drawing. In order to cause capacitor 67 to
discharge across paddles or electrodes 33 and 34, armature 73 of
slow-acting relay 55 must move from contact 103 to contact 104.
However, in the absence of opening the connection to chassis ground
82' through lead 82 before armature 73 engages contact 104, there
is the possibility that a person in contact with the patient 18 may
form a leg of the circuit and thus receive an electrical shock.
This would occur if he were grounded and touching either the
patient or anything in electrical contact with him while the shock
was being administered.
At this point it is to be noted that slow-acting relay 55 is a high
voltage vacuum relay wherein armature 73 and contacts 103 and 104
are encased in a vacuum envelope (not shown) and coil 52 is mounted
in encircling relationship to the envelope. This type of relay must
be used to prevent arcing during the switching action. Fast-acting
relay 81 is also a high voltage vacuum relay of the type having
armatures 79 and 80 within a vacuum envelope 105 and a relay coil
88 surrounding the envelope.
In operation, the person administering the countershock closes
switch 46 when he determines that countershock is necessary, as
indicated by the picture of the heartbeat on oscilloscope 22. Upon
the closing of switch 46, both sides of fast-acting relay coil 88
will be grounded, one side through leads 89 and 90, and the other
side through leads 87 and 86, resistor 85, lead 84, silicon control
rectifier 49, lead 47, switch 46 and lead 48. This grounding will
occur only when silicon control rectifier 49 is conducting and it
does so only when the proper voltage is supplied thereto from the
single shot multivibrator 40 through lead 50. In other words, the
silicon control rectifier 49 will conduct at portion 43 of waveform
42 produced by multivibrator 40. This occurs at the R portion of
the heartbeat. It is approximately 2 milliseconds after this that
armatures 79 and 80 of relay 81 will separate and this will
disconnect the circuit from chassis ground. The foregoing is
explained in greater detail in the above mentioned copending
application.
Contact between armatures 79 and 80 must be broken to disconnect
the circuit from chassis ground 82' before armature 73 of
slow-acting relay 55 reaches contact 104 to thereby insure that the
attendant cannot be subjected to the countershock voltage.
Slow-acting relay 55 requires approximately 20 milliseconds for
armature 73 to reach contact 104 after leaving contact 103. When
armature 73 reaches contact 104, capacitor 67, which has
countershock voltage stored thereon, will discharge through choke
coil 75, armature 73 and leads 36 and 35, across paddles or
electrodes 33 and 34, thereby establishing an electric discharge
through the chest of the patient. The choke coil 75 causes the
discharge to extend over a period of approximately 21/2
milliseconds (0.0025 seconds). The countershock voltage will be
synchronized with the heartbeat and fall between the R and S
waves.
The armature 73 will remain in engagement with contact 104 for as
long as defibrillation switch 46 is held closed after contact is
once made because once the silicon control rectifier 49 has been
triggered by waveform 42, it will continue to conduct. Capacitor 67
provides only a single discharge each time switch 46 is closed. In
other words, the attendant may maintain the defibrillation switch
50 closed for as long as he desires but he will get only a single
shot of countershock voltage. Another shot can be obtained only
after the capacitor 67 is again charged up in the manner described
in detail above, and after switch 46 is again closed. After switch
46 has been released, it returns to a normally open position. The
armature 73 of slow-acting relay 52 will move from contact 104 to
contact 103 in a time period dependent on the inherent delay in the
relay 55. This occurs because the opening of switch 46 terminates
the flow of current through slow-acting relay coil 52.
However, armatures 79 and 80 of fast-acting relay 81 do not return
into contact with each other before armature 73 leaves contact 104,
to insure that an undesired countershock cannot be applied to
either the patient or the attendant through ground. The circuit
containing capacitor 96 achieves this function. More specifically,
after both sides of fast-acting relay coil 88 were grounded by
switch 46 incidental to initiating countershock, capacitor 96 is
also discharged across resistor 94. However, after switch 46 is
opened, relay coil 88 will not be energized until after capacitor
96 becomes energized and this takes a period of time depending on
the time constant of the circuit consisting of capacitor 96 and
resistor 94. The armature 73 of slow-acting relay 55 returns to
contact 103 and it takes a period of time which is dependent on the
inherent delay in the relay for this switching action to be
completed. However, the switching action effected by fast-acting
relay 81 is not completed until a time greater than 20 milliseconds
because of the action of capacitor 96. This insures that the
fast-acting relay 81 will not close until after the armature 73 of
slow-acting relay 55 is no longer in contact with contact 104.
As noted above, when the countershock voltage is applied to the
patient 18, he can act as a conductor to transmit this voltage to
the electrocardiograph apparatus 10 and this would normally distort
the picture on the scope 22 for a period of as much as 20 or 30
seconds, during which time it is important that the physician be
able to monitor the patient's heartbeat accurately. In certain
cases the foregoing voltage can permanently damage apparatus 10. In
accordance with the present invention, a protector circuit 12 is
supplied for preventing the foregoing by producing a selective
switching action. More specifically, a reed relay 106 is provided
having a glass envelope 107 containing armatures 108 and 109, and a
coil 110. Envelope 107 is evacuated to prevent arcing between leads
108 and 109 as they open and close. Coil 110 is energized from a B+
source through lead 111, voltage drop resistor 112, lead 113 and
lead 114, which is coupled to ground. In addition, a reed relay 115
is provided having armatures 116 and 117 in glass envelope 118 and
a coil 119 wound around envelope 118. Coil 119 is coupled to the B+
source also through leads 111, 112, 113, 120 and 121 to ground. It
is to be noted that whenever the B+ source connected to lead 111 is
energized, that is, when the machine is connected to an electrical
source and its master switch (not shown) is on, relay coils 110 and
119 will be energized to cause the respective armatures in the
envelopes associated therewith to be in contact to thereby permit
the amplifier 21 to be connected to electrodes 13 and 14. It will
be appreciated that a single coil can be used around envelopes 107
and 111 instead of two coils 110 and 119.
Whenever defibrillator switch 46 is closed, transistor 122 will
couple lead 113 to ground through leads 123 and 124. Both sides of
relay coils 110 and 119 will thus be grounded when transistor 122
conducts, and it conducts only when defibrillator switch 46 is
closed and there is a current flow from lead 48 to transistor 122
through lead 125. Reed relays 106 and 115 are of the fast-acting
type which will open substantially simultaneously with the
energization of fast-acting relay 81 to thereby insure that the
leads to amplifier 21 are open before the countershock voltage is
applied, that is, before armature 73 of slow-acting relay 55
engages contact 104. Relays 106 and 115 will close only after
defibrillator switch 46 is released and returns to an open position
shown in the drawing whereupon transistor 122 will cease to
conduct. At this time the countershock voltage has already been
applied to the patient and there is no danger of such voltage being
applied to amplifier 21.
A neon lamp is associated with each of leads 16 and 17. More
specifically, neon lamp 126 is coupled to lead 16 by lead 127 and
said lamp in turn is coupled to ground by lead 128. In addition, a
neon lamp 129 is connected between lead 17 and ground through leads
130 and 131. In the event that the voltage applied across leads 16
and 17 exceeds a predetermined value, for example, 50 volts, neon
lamps 126 and 129 will conduct this voltage to ground while relays
106 and 115 are open. This prevents any residual voltage across
leads 16 and 17 from being applied to electrocardiograph 10 after
relays 106 and 115 are reclosed.
There may also be times when leads 16 and 17 are subjected to stray
voltages when defibrillation is not being effected. Under these
circumstances, relays 106 and 115 will be closed. If these stray
voltages exceed a predetermined voltage, neon lamps 126 and 129
will conduct to ground, thereby preventing distortion of the
picture on oscilloscope 22 or danger to amplifier 21. Lamps 126 and
129 will continue to conduct until such time as the voltage applied
to leads 16 and 17 is below a certain value, at which time they
will cease to conduct and leads 16 and 17, relays 106 and 115, and
leads 19 and 20 will thereafter conduct normally to the amplifier
21.
It can thus be seen that an extremely simple protector circuit has
been applied to electrocardiac apparatus, consisting of an
electrocardiograph and a defibrillator circuit, for preventing
countershock voltages applied to the patient from adversely
affecting the electrocardiograph by either damaging the amplifier
or distorting the visual representation of the heartbeat on the
oscilloscope. In addition, the protector circuit includes an
arrangement for preventing stray voltages which are not necessarily
originated by the defibrillator from adversely affecting the
electrocardiograph in the same manner. It will be appreciated that
protector circuit 12 may be used with any type of
electrocardiograph and any type of defibrillator or other
electronic apparatus used in the treatment of a cardiac
patient.
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