U.S. patent number 3,782,389 [Application Number 05/219,455] was granted by the patent office on 1974-01-01 for computer controlled defibrillator.
This patent grant is currently assigned to Health Technology Labs, Inc.. Invention is credited to David Bell.
United States Patent |
3,782,389 |
Bell |
January 1, 1974 |
COMPUTER CONTROLLED DEFIBRILLATOR
Abstract
A computer controlled defibrillator comprising a set of
electrodes which are engageable with a patient and which are
connected to a source of electrical energy by a circuit means. The
circuit means comprises storage capacitors, energy selector,
computer, manual and reset switches, voltage monitor, current
monitor, and output meter. The computer responds to certain
external inputs, automatic and manual, and controls the output
delivered to the patient. The energy selector permits the selection
of the energy which is desired to be delivered to the patient. The
sequence is started by closing the manual reset switch which zeroes
the output meter and activates the power supply (electric energy)
at a voltage which is dependent on the energy selector. The energy
drived from the power supply is stored in the storage capacitors.
The energy selector, which is manually set to the energy desired,
also feeds an input to the computer. When the manual switch is
activated, the computer causes the stored energy source to be
connected to the patient through the electrodes. The current
monitor and voltage monitor feed instantaneous signals to the
computer which computes the energy as a continuous integration
process. When the computer energy equals the selected energy, the
computer causes the energy source to be disconnected from the
patient. The total energy delivered to the patient is indicated as
a steady reading on the output meter.
Inventors: |
Bell; David (Omaha, NB) |
Assignee: |
Health Technology Labs, Inc.
(Omaha, NB)
|
Family
ID: |
25765974 |
Appl.
No.: |
05/219,455 |
Filed: |
January 20, 1972 |
Current U.S.
Class: |
607/27; 324/111;
607/8 |
Current CPC
Class: |
A61N
1/3937 (20130101) |
Current International
Class: |
A61N
1/39 (20060101); A61n 001/36 () |
Field of
Search: |
;128/419D,419P,419R,420,421,422,423 ;324/111 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
Primary Examiner: Kamm; William E.
Attorney, Agent or Firm: Zarley, McKee & Thomte
Claims
I claim:
1. A defibrillator comprising in combination,
an electrical power source,
a set of electrodes engageable with a patient,
circuit means connecting said power source to said set of
electrodes comprising, a computer means, a storage capacitor means
for storing energy derived from said power source, an energy
selector means for selecting the energy to be delivered to the
patient, said energy selector also feeding an input to said
computer means, a switch means for causing the stored energy to be
connected to the patient, said switch means being operatively
electrically connected to said computer means, a power monitor
means for feeding signals to said computer means when said stored
energy is delivered to the patient, said computer means computing
the energy delivered to the patient and causing the delivery of
energy to the patient to be discontinued when the computed energy
substantially equals the selected energy.
2. The combination of claim 1 wherein said power monitor means
comprises a voltage monitor means and a current monitor means.
3. The combination of claim 1 wherein said circuit means has a
visual output meter which indicates the energy delivered to the
patient.
4. A defibrillator comprising in combination,
an electrical power source,
a set of electrodes engageable with a patient,
circuit means connecting said power source to said set of
electrodes comprising, a computer means, a storage capacitor means
for storing energy derived from said power source, an energy
selector means for selecting the energy desired to be delivered to
the patient, a switch means for causing the stored energy to be
connected to the patient, said switch means being operatively
electrically connected to said computer means, a power monitor
means for feeding signals to said computer means when said stored
energy is delivered to the patient, said circuit means having a
visual output means for indicating the energy delievered to the
patient, said computer means computing the energy actually
delivered to the patient and causing said visual output means to
indicate the energy actually delivered to the patient.
Description
The use of DC defibrillators in emergency resuscitation has become
well established. Limitations due to weight have prevented more
widespread use of the defibrillators. Most clinical defibrillators
depend on the storage and discharge of energy through a stable RLC
combination, thus requiring accurate capacitance, inductance and
resistance. The conventional defibrillators employ a pair of
electrodes or paddles which are placed in contact with the
patient's chest. A defibrillation or electrical pulse is then
applied to the patient, through the electrodes, to momentarily stop
the heart so that fibrillation of the heart is stopped. Since time
is critical in defibrillation techniques, it is extremely important
that a sufficiently large impulse be applied to the patient during
the first attempt. A majority of the prior art devices employ some
means for selecting the energy to be delivered to the patient.
However, it has been found that these devices generally deliver a
smaller or lower output to the patient than that which was
selected. A further complication is that the resistance of the
patients vary greatly. Thus, the operator could possibly determine
that it was necessary to apply an impulse of 200 joules to the
patient. Quite often, the variances in the defibrillator and the
variable resistance of the patient will result in considerably less
than 200 joules being applied to the patient. If the pulse is
insufficient to momentarily stop the patient's heart, the patient
could possibly die.
Therefore, it is a principal object of this invention to provide an
improved defibrillator.
A further object of this invention is to provide a defibrillator
wherein the energy delivered to the patient substantially equals
the selected energy.
A further object of this invention is to provide a defibrillator
including a circuit means having an energy computer and control
which computes the energy delivered to the patient and causes the
energy source to be disconnected from the patient when the computed
energy substantially equals the selected energy.
A further object of this invention is to provide a defibrillator
which delivers the selected energy to the patient regardless of the
resistance of the patient.
A further object of this invention is to provide a defibrillator
which is light weight and portable.
A further object of this invention is to provide a defibrillator
which is economical of manufacture, durable in use and refined in
appearance.
These and other objects will be apparent to those skilled in the
art.
This invention consists in the construction, arrangements, and
combination of the various parts of the device, whereby the objects
contemplated are attained as hereinafter more fully set forth,
specifically pointed out in the claims, and illustrated in the
accompanying drawings, in which:
FIG. 1 is a perspective view of the defibrillator of this
invention.
FIG. 2 is a block diagram of the electrical circuitry of the
defibrillator.
FIG. 3 is a block diagram illustrating the components of the energy
computer and control and its relationship with other components of
the device.
FIG. 4 is a schematic view of a portion of the circuitry of the
invention.
FIG. 5 is a schematic view of more of the circuitry of the
invention; and
FIG. 6 is a schematic view of more of the electrical circuitry of
the invention.
The defibrillator of this invention is referred to generally by the
reference numeral 10 and comprises a portable housing 12 having a
pair of electrodes or paddles 14 and 16 connected to the circuitry
therein as will be described in more detail hereinafter. The
electrodes or paddles 14 and 16 are engageable with the patient to
deliver a predetermined energy output to the patient to momentarily
stop the patient's heart so that fibrillation of the heart is
stopped.
The circuitry of the defibrillator is depicted in schematic form in
FIG. 2 wherein the numeral 18 refers to a 110 VAC power supply
having a switch 20 associated therewith. The power supply 18 is
electrically connected to the storage capacitors 22 which are
adapted to store energy derived from the power supply 18. A
"switch" mechanism 24 is connected to the storage capacitors 22.
Mechanism 24 is connected to the electrodes 14 and 16 as seen in
FIG. 2 and to a voltage monitor means 26 and current monitor means
28. Manual switch 30 and reset switch 32 are connected to the
energy computer and control means 34. Energy selector 36 is also
connected to the computer and control means 34 as is the output
meter 38. Energy selector 36 may be comprised of a conventional
rotatable dial or the like for setting the energy to be delivered
to the patient.
The energy computer and control means 34 is illustrated in
schematic form in FIG. 3. In FIG. 3, it can be seen that the
current monitor 28 and voltage monitor 26 are electrically
connected to the Multiplier 40 and that the Multiplier 40 is
connected to an Integrator 42. Integrator 42 is connected to an
Analog Memory 44 which is connected to the meter 38. The current
monitor 28 and the voltage monitor 26 are also connected to a Time
Out Comparator which is connected to the OR gate 48. The energy
selector 36 is connected to the Time Out Comparator 46, Integral
Comparator 50 and Voltage Comparator 52. The Integral Comparator 50
is connected to the OR gate 48 and to the Integrator 42 as depicted
in FIG. 3. Voltage Comparator 52 is connected to the Voltage
Reference 54 and to the Charge Logic 56. The Multiplier 40 is also
connected to the Voltage Comparator 52.
The reset switch 32 is electrically connected to the Analog Memory
44 and to the Charge Logic 56 while the manual switch 30 is
connected to the Delay-Start 58 and to the Charge Logic 56.
The heart of the control mechanism in the defibrillator is the
energy computer and control 34 which responds to certain external
inputs, manual and automatic, and controls the output delivered to
the patient. In operation, the manual reset 32 starts the sequence
by zeroing the output meter 38 and activating the power supply 18
at a voltage which is dependent on the energy selector 36. Thus, if
it were desired to deliver an impulse of 200 joules to the patient,
the energy selector 36 would be set at 200 joules. The energy
derived from the power supply 18 is stored in the storage
capacitors 22. The energy selector 36, which is manually set to the
energy desired, also feeds an input to the energy computer and
control 34. The electrodes or paddles 14 and 16 are then placed
into contact with the patient and the manual switch 30, located on
either or both of the paddles 14 and 16, is activated.
When the manual switch 30 is activated, the energy computer and
control 34 causes the stored energy source to be connected to the
patient. The current monitor 28 and voltage monitor 26 feed
instantaneous signals to the energy computer and control 34 which
computes the energy as a continuous integration process. When the
computed energy equals the selected energy, the energy computer and
control 34 causes the energy source to be disconnected from the
patient. The total energy delivered to the patient is indicated as
a steady reading on the output meter 38.
More specifically, the circuitry of FIGS. 4, 5 and 6 operates as
follows. The circuit of FIG. 4 is basically the power supply for
the device. TP3 transformer feeds a full wave bridge rectifier to
generate plus and minus DC voltage. The transistor and zener diodes
regulate the DC to .+-.15 v. and are of conventional design. The
second set of diodes leading to the coils of K1 and K2 supply power
to operate these relays. Contacts K3 operates coil K2. K2 operates
the contacts on FIG. 5. K3 is operated off of control circuit FIG.
6. These devices, K2 and K3, control the main discharge from the
firing circuit to the patient.
K1 which is controlled by the voltage comparator 52 and charge
logic 56 switches 110 VAC to transformers T1 and T2. This circuit
supplies power to the capacitor bank 22 in FIG. 5 as required to
maintain 1,400 VDC.
The four rectifiers between T1 and T2 in FIG. 4 and the four
capacitors 22 in FIG. 5 form two full wave voltage double circuits
in cascade to generate 1,400 v. About 500 joules of energy are then
stored in the capacitor bank. Initially all four silicone
controlled rectifiers SCR are not conducting. The 150 K resistors
around the SCRs are used to balance the off leakage current. The
0.05 mfd - 50 ohm networks around each SCR are to suppress
switching transcients.
Terminals 1, 2 and 3 are the monitor points. The voltage between 1
and 2 is proportional to the stored voltage and the voltage to the
load. The voltage between 1 and 3 is proportional to the current in
the load. The 5 ohm, 100 watt resistor serves the dual function of
current shunt and crowbar protection.
The remainder of this circuit can be best explained by a typical
operating sequence. Initially the capacitors are charged and all
SCRs are off. The cycle starts with the start input going to a
positive 15 v. This starts the 0.030 sec. timer 58. At the same
time K2 relay begins to close. The timer delay is to allow K2 to
close completely. When the unijunction transistor in the timer
fires, a large current pulse is fed to trigger transformers T1 and
T2. These pulses turn on SCR 1 and 2 applying power to the load.
The LED is turned on by the applied voltage and is optically
coupled to the photo transistor in FIG. 6. This transistor starts
timeout comparator Z9. When the comparator circuit determines the
required energy has been delivered, a positive voltage is applied
to the stop terminal. This fires the small 2N5062 SCR generating a
high current pulse in T3 and T4. This pulse fires SCR 3 and 4 which
crow-bars the remaining energy in the capacitor bank.
With respect to FIG. 6, amplifiers Z1, Z2 and Z3 form two DC
differential amplifiers. These amplifiers convert the essentially
floating inputs 1, 2 and 3 to ground referenced signals. The two
outputs are v(t) from Z2 and i (t) from Z3. These signals are fed
to 40 which together with Z4 form an analog multiplier. The output
of Z3 in mathematical terms is v(t) x i(t)/K.
This signal is proportional to the power being delivered to the
load at any instant of time. Z5 is an integrator which integrates
power with time to give energy. The AC coupling network on the
output of Z3 removes the long term DC drift. The output at this
point is approximately an increasing ramp voltage. This ramp is
compared to the setting of the pot 36, by comparator 50. When these
are equal the comparator sends the stop output high. The peak value
of the ramp is stored on the 0.22 mfd capacitor in analog storage
circuit 44. The four transistor amplifier has a gain of +1. This
allows the energy delivered to be displayed on the meter.
Comparator Z9 (46) performs a similar function to 50 except it
compares the pot 36 setting with time. In this way the output pulse
width is limited to a maximum value for any given setting. This
circuit does not affect operation for loads of less than 150
ohms.
Comparator Z6, controls the charging of the capacitor bank. Z6
compares the output of amplifier Z2 which is proportional to the
bank voltage to a zener diode. A certain amount of positive
feedback is used as controlled hysteresis to prevent chatter of
relay K1.
The remaining transistors are used as switches to turn on or off
certain functions when the manual switch 30 is closed. For example,
the voltage comparator Z6 is turned off and comparator 56 and 50
and analog memory 44 are turned on.
The operation described causes the selected energy to be delivered
regardless of the variable patient load resistance. The limits are
zero resistance at the patient (which will occur if the paddles are
touched together) or an open or high (over 100 ohm) patient
resistance. In case of the low limit, all of the energy stored in
the capacitors would be dissipated within the defibrillator. In the
case of the high limit, the defibrillator would attempt to deliver
the selected energy but would take too long and the time out input
will terminate the discharge before the selected value is reached.
The meter 38 will indicate to the operator that the energy that was
selected was not delivered and the load was abnormal.
Thus it can be seen that a novel defibrillator has been provided
which insures that the energy delivered to the patient will be
substantially equal to the selected energy regardless of the
variable patient load resistance. The circuitry of the
defibrillator permits a light weight and portable defibrillator to
be provided so that the defibrillator can be easily transported to
the patient. In summary, it can be seen that the defibrillator
provides the following:
1. Pre-selection of the energy to be delivered;
2. Automatic Energy Control to deliver the energy selected
independently of load; and
3. Verification by computation of energy delivered and indication
on an output meter.
Thus it can be seen that the defibrillator accomplishes at least
all of its stated objectives.
* * * * *