U.S. patent number 3,885,569 [Application Number 05/308,488] was granted by the patent office on 1975-05-27 for electrosurgical unit.
This patent grant is currently assigned to The Birtcher Corporation. Invention is credited to Donald W. Judson.
United States Patent |
3,885,569 |
Judson |
May 27, 1975 |
Electrosurgical unit
Abstract
An electrosurgical unit for generating electrical signals
intended for application to the body of a patient via an
electrosurgical electrode, is disclosed. Cutting signals and
coagulation signals, as well as a blend of both signals, are
generated by the unit under the control of a mode control circuit
that is responsive to the operation of selector switches and/or
manually operated actuators. Selected patient and unit conditions
are monitored to have the electrosurgical unit disabled under
certain dangerous conditions.
Inventors: |
Judson; Donald W. (Simi Valley,
CA) |
Assignee: |
The Birtcher Corporation (Los
Angeles, CA)
|
Family
ID: |
23194174 |
Appl.
No.: |
05/308,488 |
Filed: |
November 21, 1972 |
Current U.S.
Class: |
606/37 |
Current CPC
Class: |
A61B
18/12 (20130101); A61B 18/1206 (20130101); H02H
3/33 (20130101); A61B 2018/0066 (20130101) |
Current International
Class: |
A61B
18/12 (20060101); A61N 1/08 (20060101); H02H
3/33 (20060101); H02H 3/32 (20060101); A61n
003/02 () |
Field of
Search: |
;128/303.13,303.14,303.17,303.18,421,422,423,2.1P |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Kamm; William E.
Claims
What is claimed is:
1. An electrosurgical unit for generating electrical signals to be
applied to the body of a patient by an electrosurgical electrode
for producing surgical cutting and coagulation as selected, said
electrosurgical unit comprising:
a pair of output terminals adapted to be coupled to the
electrosurgical electrode;
first means for providing a continuous alternating current cutting
signal having a selected freuency that produces surgical cutting
when applied to the body of a patient;
second means for cyclically disabling said first means to provide a
coagulating signal that is a succession of bursts of said
alternating current signal, said coagulating signal providing
coagulation when applied to the body of a patient;
third means for altering the disabling cycle of said second means
to extend the length of time said first means operates and to
provide a blended signal that alternately produces cutting and
coagulation when applied to the body of a patient; and
output means for applying the blended signal to the output
terminals.
2. The electrosurgical unit defined by claim 1, said first means
including:
drive means for providing drive pulses at a pulse rate
corresponding to the frequency of said alternating current signal;
and
wherein the output means is responsive to said drive pulses for
providing said alternating current signal at the output
terminals.
3. The electrosurgical unit defined by claim 2, said drive means
including:
a first multivibrator for providing pulses at a rate that is twice
said selected frequency;
a bistable means having two states and producing output signals
corresponding to each of two states thereof, said bistable device
being switched between said two states in response to said pulses
from said first multivibrator; and
gating means connected to be responsive to said first multivibrator
pulses and to the output signals of said bistable device for
providing said drive pulses.
4. The electrosurgical unit defined by claim 3, said gating means
including:
first and second NAND gates each receiving from said bistable
device an output signal corresponding to a different one of said
two states; and
a third NAND gate connected to be responsive to said first
multivibrator for simultaneously providing to said first and second
NAND gates an input signal corresponding to an inversion of said
pulses from said first multivibrator.
5. The electrosurgical unit defined by claim 3, said second means
including a second multivibrator connected to distable said
bistable device for predetermined time periods at predetermined
time intervals, said bistable device being prevented from providing
said drive pulses to said gating means when disabled.
6. The electrosurgical unit defined by claim 5, said third means
including means for alternately permitting and preventing, in
accordance with a predetermined timing sequence, said second
multivibrator from disabling said bistable device for said
predetermined time periods at said predetermined time
intervals.
7. The electrosurgical unit defined by claim 2, further including
inductive coupling means for providing said drive pulses to said
output means.
8. The electrosurgical unit defined by claim 2, said output means
including:
a transistorized push-pull amplifier responsive to said drive
pulses; and
a coupling transformer for inductively coupling the output of said
push-pull amplifier to said output terminals.
9. The electrosurgical unit defined by claim 8 further including
mode selection means for providing mode selection signals to
control the operation of said first, second, and third means to
provide cutting signals, coagulation signals, or blended
signals.
10. The electrosurgical unit defined by claim 9, further including
manually operable actuator means for controlling the selection and
generation of desired signals by said unit.
11. The electrosurgical unit defined by claim 8, wherein the
push-pull amplifier includes a pair of inputs and an output and
wherein the output means includes feedback means coupled between
the output and inputs of the amplifier for altering the voltage
level at the inputs of said amplifier in accordance with the
voltage level at the output thereof to prevent said amplifier from
attaining a saturated mode.
12. The electrosurgical unit defined by claim 8, wherein the output
means includes a cut level control means and a coagulation level
control means for individually controlling the gain of the
push-pull amplifier to thereby control the amplitude of the output
signal, said cut level control means and said coagulation control
means being respectively operated in response to the application
thereto of mode selection signals corresponding to cutting and
coagulating signals, respectively.
13. The electrosurgical unit defined by claim 12, further including
monitoring means for disabling said electrosurgical unit in
response to the detection of unequal amounts of current flowing to
and from a patient with respect to said unit.
14. The electrosurgical unit defined by claim 12, further including
means for monitoring the temperature of said electrosurgical unit
to disable said unit in response to said temperature thereof
exceeding a selected temperature.
15. The electrosurgical unit defined by claim 14, said drive means
including:
a first multivibrator for providing pulses at a rate that is twice
said selected frequency;
a bistable means having two states and producing output signals
corresponding to each of two states thereof said bistable device
being switched between said two states in response to said pulses
from said first multivibrator; and
gating means connected to be responsive to said first multivibrator
pulses and to the output signals of said bistable device for
providing said drive pulses.
16. The electrosurgical unit defined by claim 15, said second means
including a second multivibrator connected to disable said bistable
device for predetermined time periods at predetermined time
intervals, said bistable device being prevented from providing said
drive pulses to said gating means when disabled.
17. The electrosurgical unit defined by claim 16, said third means
including means for alternately permitting and preventing, in
accordance with a predetermined timing sequence, said second
multivibrator from disabling said bistable device for said
predetermined time periods at said predetermined time
intervals.
18. The electrosurgical unit defined by claim 17, further including
inductive coupling means for providing said drive pulses to said
output means.
19. The electrosurgical unit defined by claim 1 further including
actuator means for controlling the selection and generation of said
cutting signals, coagulating signals, and blended signals in
response to manual manipulation of said actuator means.
20. The electrosurgical unit defined by claim 19, further including
mode selection means for generating mode selection signals in
response to operation of said actuator means, said mode selection
signals being applied to control the operation of said first,
second and third means to have selectively provided said cutting
signals, coagulating signals, and said blended signals.
21. The electrosurgical unit defined by claim 1, further including
monitoring means for disabling said electrosurgical unit in
response to the detection of unequal amounts of current flowing to
and from a patient with respect to said unit.
22. The electrosurgical unit defined by claim 1, further including
means for controlling the output amplitude of said cutting signals
and said coagulating signals.
23. The electrosurgical unit defined by claim 1 wherein the output
means includes level control means for providing the independent
adjustment of the amplitude level of the cutting and coagulating
components of the blended signal.
24. The electrosurgical unit defined by claim 23 wherein the level
control means includes means for manually adjusting said level
control means.
25. The electrosurgical unit defined by claim 24 wherein said third
means includes means to provide a blended signal in which the
cutting component has a time duration of approximately three times
the time duration of the coagulating component.
26. An electrosurgical unit for generating electrical signals to be
applied to the body of a patient by an electrosurgical electrode
for producing surgical cutting and coagulation, the electrosurgical
unit comprising:
first means for generating a high frequency cutting signal for
producing surgical cutting when applied to the body of a
patient;
second means for generating a succession of bursts of a high
frequency signal for providing a coagulating signal which produces
coagulation when applied to the body of a patient;
a pair of output terminals adapted to be coupled to the
electrosurgical electrode;
output means coupled between the first and second means and the
output terminals for applying a blended signal to the output
terminals, the blended signal consisting of successive intervals of
the cutting signal and coagulating signal to alternately produce
cutting and coagulation when applied to the body of a patient;
and
level control means coupled to the output means for providing an
independent adjustment of the amplitude level of the cutting and
coagulating components of the blended signal.
Description
BACKGROUND OF THE INVENTION
1. Field of the Invention
This invention generally relates to electrosurgical units. More
specifically, the present invention concerns an improved
electrosurgical unit that operates to generate high power
electrical signals for use in performing electrosurgery.
2. Description of the Prior Art
A variety of electrosurgical units are available in the prior art.
These units function to permit surgical cutting and/or coagulation
electrically. Three different signals are characteristically
generated and used. These signals may be referred to as cutting
signals, coagulation signals, or blended signals formed by
combining both the cutting and coagulation signals. Such signals
are applied to a patient, conducted through the patient's body, and
returned to the unit via a ground path provided by an "indifferent"
pad that is maintained in contact with the patient.
Generally described, the cutting signal is a high frequency signal
that serves to cut when applied to a patient. An electrosurgical
electrode is used to apply the electrical energy to definitely
defined and concentrated points of a patient's body. As is well
known, cutting is accomplished by the concentrated application of
high frequency electrical energy which effectively destroys the
body cells directly beneath the electrosurgical electrode.
Coagulation signals are intended to produce coagulation by
shrinking vessel walls. Typically such coagulation signals are
pulses of energy having a damped sinusoidal waveform. Generally,
coagulation signals may be viewed as causing cell dehydration to
produce coagulation rather than destroying cells in the fashion of
cutting signals.
Blended signals formed by combining cutting and coagulation signals
are useful for accomplishing cutting and coagulation at the same
time. Alternating periods of each signal may be used to form the
blended signals.
As may be readily appreciated, the application of large amounts of
electrical power to a human body presents the potential for serious
burning. Consequently, the power level of electrosurgical signals
must be accurately controlled.
Prior art units are generally not as stable and readily
controllable as is desirable to promote maximum safety. The reason
is that "tube" type circuits have been necessarily used to produce
the cutting and coagulation signals due to the high power levels
involved, i.e., 450 watts output, and the inability to generate the
earlier mentioned damped sinusoidal pulses with solid-state
circuits.
As is well known, such tube-type circuits vary in output power as a
function of the condition and age of the tubes, i.e., as the tubes
age and deteriorate the output power changes.
Such aging of electronic tubes is continuous and consequently the
power generated by such circuits also is continually changing to
effectively frustrate stability and accurate control. As a result,
a not uncommon result is over or under coagulation with the
attendant medical complications.
It is thus the intention of the subject invention to provide an
improved electrosurgical unit that overcomes the disadvantages of
prior art units by providing a greater amount of electrical power
for electrosurgical use than heretofore possible, being stable and
accurately controllable, being compatible with solid state
technology, and being of reduced size and weight to more readily
permit repositioning of the unit by medical personnel.
SUMMARY OF THE INVENTION
Briefly described, the present invention involves an
electrosurgical unit for providing cutting, coagulation and blended
signals suitable for use in performing surgical cutting or
coagulation or a combination of both.
More particularly, the subject electrosurgical unit includes
circuitry for providing high frequency, high power electrical
signals for cutting, pulses of said high frequency signals for
coagulation, and a blend of the two signals when desired.
Generation of each of the signals is controlled by mode control and
selection circuitry that is in turn responsive to hand or foot
operated actuators. Output level control circuits are used to
permit control of the amplitude level of the cutting and
coagulation signals individually. Circuits for continually
monitoring certain patient and unit conditions may be connected to
disable the electrosurgical unit in response to the detection of
undesired conditions.
The objects and many attendant advantages of the present invention
will be more readily appreciated as the same becomes better
understood by reference to the following detailed description which
is to be considered in conjunction with the accompanying drawings
wherein like reference symbols designate like parts throughout the
figures thereof.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a schematic block diagram generally illustrating an
electrosurgical unit in accordance with the present invention.
FIG. 2 is a schematic block diagram illustrating exemplary drive
and mode control circuitry that may be used in conjunction with the
present invention.
FIG. 3 is a schematic block diagram illustrating exemplary
circuitry that may be used to provide mode control signals in
accordance with the present invention.
FIG. 4 is a schematic diagram illustrating an exemplary electrode
monitoring arrangement that may be used in conjunction with the
present invention.
FIG. 5 illustrates exemplary level control and output amplifier
circuits that may be used in conjunction with the present
invention.
FIG. 6 is a graphic diagram illustrating a number of waveforms that
are useful in describing the operation of the subject
invention.
DESCRIPTION OF THE PREFERRED EMBODIMENT
Referring to FIG. 1 of the drawings, an electrosurgical unit in
accordance with the present invention essentially includes a
push-pull amplifier 10 that is connected to be driven by pulses
provided by a drive circuit 12. Output signals provided by the
amplifier circuit 10 are applied through a coupling transformer 14
to a pair of output terminals 16. Any conventional electrosurgical
electrode (not shown) may be connected to the terminals 16 for
applying electrical energy to a patient. The level of the output
signals provided by the amplifier 10 are controlled by an output
level control circuit 18 that is selectively operated in response
to mode selection signals provided from a mode selection circuit
20. Such mode selection signals are also applied to a mode control
circuit 22 to have appropriate drive pulses developed by the drive
circuit 12. manually operated actuators 24 may be connected to the
mode selection circuit 20 for controlling the output of such mode
selection signals. Selected monitoring circuits 26 may be connected
to provide alarm signals which disable the electrosurgical
unit.
Referring briefly to the waveforms of FIG. 6, cutting signals
provided by an electrosurgical unit in accordance with the
invention involve high frequency, high power signals. As an
example, the cutting signals illustrated by waveforms A may have a
frequency of 250kHz. The output power may be controlled to be as
high as is necessary to perform the desired cutting. For example,
an electrosurgical unit has been designed to provide up to 600
watts of cutting power.
Coagulation signals, as illustrated by waveform B, involve short
pulses, or bursts, of the high frequency signals used for cutting.
The power level of coagulation signals is usually decreased
considerably from the level that is used for cutting. As an
example, it has been empirically found that 25 microsecond pulses
of high frequency energy occurring at 75 microsecond intervals will
efficiently produce coagulation.
Blended signals, as illustrated by waveform C, are formed by
including alternate periods of cutting signals and coagulation
signals. As shown, a 10 millisecond duty cycle may be used wherein
coagulation signals are provided for 2.5 milliseconds and cutting
signals are provided for 7.5 milliseconds. The blended signals
would be used to produce coagulation as cutting progresses.
Referring again to FIG. 1, the 250kHz high frequency signals are
provided by the amplifier circuit 10 in response to drive pulses
that are provided by the drive circuit 12. The coagulation signals
are provided by allowing the drive circuit 12 to operate for 25
microsecond periods and be disabled for 75 microsecond intervals
following each operation period of 25 microseconds. The blended
signals would be produced by alternately operating the drive
circuit 12 between the cut mode and the coagulation mode. The
different amplitude levels to be used for the cutting and
coagulation signals are independently controlled by the output
level control circuit 18 in a manner described in greater detail
hereinafter.
An exemplary drive circuit 12 and mode control circuit 22 is
illustrated by FIG. 2. As shown, a 500kHz multivibrator circuit is
connected to provide pulses to clock a flip-flop circuit 30. The
pulses provided by the multivibrator 28 are illustrated by waveform
H of FIG. 6 wherein 0.5 microsecond pulses occur every 2
microseconds. The output signals at the Q and Q output terminals 32
and 34, respectively, of the flip-flop 30 alternately change
between high and low levels with each succeeding pulse from the
multivibrator as shown by waveforms J and K of FIG. 6.
For the purposes of this application, a NAND gate as hereinafter
referred to is understood to provide a high output signal whenever
any of its inputs is a low signal and provide a low output signal
only when all input signals are high.
The output terminals 32 and 34 of the flip-flop 30 are connected as
one of two inputs to a pair of NAND gates 36 and 38, respectively.
The pulses from the multivibrator 28 are applied as a second input
signal to the NAND gates 36 and 38 via a NAND gate 40 which
effectively serves as an inverter as may be observed from the
waveforms H and I of FIG. 6.
Assuming that the enabling input signal applied to the J input
terminal of the flip-flop 30, and to the NAND gate 40 is
continually high, the output of the NAND gate 40 will be high for
the time interval between successive pulses from the multivibrator
28 and low for the duration of each of the multivibrator pulses as
shown by waveform I. Consequently, the NAND gates 36 and 38 will
alternately provide low signals for the periods between successive
pulses from the multivibrator 28 as shown by waveforms L and M,
respectively. Otherwise considered, each of the NAND gates 36 and
38 will produce negative pulses at a 250kHz rate which, when
applied to drie the push-pull amplifier circuit 10 as described in
greater detail in conjunction with FIG. 5, will produce the desired
250 kHz high frequency signals.
As earlier discussed, the coagulation signals may be simply viewed
as pulses, or bursts, of the 250kHz high frequency signal that is
used as a cutting signal wherein the bursts last for 30
microseconds and occur every 100 microseconds. Referring to FIG. 2,
this is accomplished by effectively cyclically disabling the
flip-flop 30 for periods of 75 microseconds every 100 microseconds.
This would require that the J input terminal of the flip-flop 30
alternately rerceive a low signal for a period of 75 microseconds
followed by a high signal for a period of 25 microseconds. To this
end, a multivibrator 42 is connected to provide 25 microsecond
pulses at 100 microsecond intervals as shown by waveform N of FIG.
6. Such pulses from the multivibrator 42 are applied through a pair
of serially connected NAND gates 44 and 46, and a flip-flop 48, to
the J input terminal of the flip-flop 30. The NAND gates 44 and 46
serve to permit controlled application of the pulses from the
multivibrator 42 to the flip-flop 30 as is hereinafter explained.
Synchronism of cutting and coagulation signals is provided by
having the flip-flops 30 and 48 both clocked by the multivibrator
28.
Assuming that a high signal is provided to the respective NAND
gates 44 and 46 at the respective input leads 52 and 54 thereof,
the pulses from the multivibrator 42 will pass through both the
gates 44 and 46. However, if a low input signal is applied to the
NAND gate 44 via the lead 52, the pulses from the multivibrator 42
will be effectively blocked since the output of the NAND gate 44
will be maintained high regardless of the level of the signal
applied thereto from the multivibrator 42. Accordingly, high
signals are applied to the gates 44 and 46 via the leads 52 and 54,
respectively, whenever coagulation signals are to be provided while
a low signal is applied to the gate 44 whenever a coagulation
signal is not desired. Similarly, a low signal is applied to the
gate 46 when cutting signals are desired to have the flip-flop 30
and 48 set and reset by the pulses from the multivibrator 28.
The above-described signals applied to the gates 44 and 46 via the
leads 52 and 54, respectively, are provided in response to
coagulation and cutting mode selection signals appearing at the
leads 56 and 58, respectively. The coagulation mode selection
signal applied to the lead 56 will be low as will be the cut mode
selection signal when applied to the lead 58. The leads 56 and 58
will receive high signals at all other times when no mode selection
signals are present.
The coagulation mode selection signal appearing at the lead 56 is
applied as an input to a NAND gate 60 to have the desired high
input signal applied to the NAND gate 44 via the lead 52 during the
coagulation mode. Similarly, a cut mode selection signal is applied
to a NAND gate 62, and an inverter 64 connected in series
therewith, to have the desired low signal applied to the NAND gate
46 via the lead 54 during a cutting mode.
Desired blended signals are generated by alternately applying low
signals to the NAND gates 60 and 62 from a pair of NAND gates 66
and 68, respectively. This is accomplished in accordance with the
earlier described timing sequence (see waveform C) by having the
NAND gate 66 provide a low signal to the gate 60 for a period of
2.5 milliseconds for the coagulation period followed by having the
NAND gate 68 provide a low signal to the gate 62 for a period of
7.5 milliseconds for the cutting period. The gates 66 and 68 are
connected to receive a high input signal via an inverter 70 when a
blend mode selection signal is applied to the inverter via the lead
72. The desired timing sequence is controlled by input signals
applied to the NAND gates 66 and 68 from a timing circuit including
a multivibrator 74. Pulses occurring at a rate of 400Hz are
provided by the multivibrator 74. A pair of dividers 76 and 78 may
be used to provide pulsed signals having reduced rates of 200Hz and
100Hz at the respective output terminals 77 and 79, thereof. Such
200Hz and 100Hz signals are illustrated by waveforms O and P.
As shown by waveform O, the 200Hz pulsed signals provided by the
divider 76 include 2.5 millisecond pulses occurring at 5
microsecond intervals while the 100Hz signal includes 5 millisecond
pulses occurring at 10 millisecond intervals. When such 200Hz and
100Hz signals are applied as inputs to a NAND gate 80 via the leads
77 and 79, the output of the gate 80 will be cyclically maintained
high for 7.5 milliseconds and low for 2.5 microseconds as shown by
waveform Q of FIG. 6. An inverted waveform is provided by an
inverter circuit 82 as shown by FIG. 6, waveform R. The respective
outputs of the NAND gate 80 and the inverter 82 are applied as
inputs to the NAND gates 68 and 66 via leads 81 and 83. The gate 68
thus applies a low signal to the gate 62 to have cutting signals
generated for a period of 7.5 milliseconds followed by the NAND
gate 66 applying a low signal to the gate 60 to have coagulation
signals generated for a period of 2.5 milliseconds.
The three mode selection signals necessarily applied to the leads
56, 58 and 72, to operate the mode control circuit 22 to have
desired cutting, coagulation or blended signals generated, are
provided from the mode selection circuit 20 in response to
operation of the actuators 24.
An exemplary foot operated actuator may involve an arrangment of
three individual pedals, or the like, which ultimately cause a
desired mode selection signal to be provided at the appropriate one
of the leads 56, 58 and 72 when a pedal is depressed or otherwise
operated. Such foot operated actuators are well known and a
detailed discussion of such actuators is not deemed necessary for
the purpose of this description. A hand operated actuator may be
used to perform the same functions.
As shown by FIG. 3, the mode selection circuit 20 includes a bank
of mechanical switches 84 that are manually operable and which
serve to pass or stop signals provided by operation of the foot
actuators 24. For example, four switch positions may be provided
for CUT ONLY, COAGULATION ONLY, BLEND ONLY, and
CUT-COAGULATE-BLEND. In the first three positions, only operation
of the mode pedal corresponding to the position of the switch 84
will be effective. In the last position any pedal may be
effectively operated.
The selection switch 84 may simply involve opening the conductive
path for non-selected modes and closing the conductive path for the
selected mode. For example, where only the cut mode is desired, the
switches 84 would be placed in the CUT ONLY position. The circuit
for the cut mode would be closed while all other switches would be
open.
The signals provided by the actuators 24 via the mode selection
switches 84 are applied to an array of NAND gates that are
essentially connected to form a decoder. As shown in FIG. 3, a cut
mode selection signal would appear at the lead 58 at the output of
a NAND gate 86 whenever certain input signals summarized by the
equations appearing in FIG. 3 are applied. For Example, the
equation CUT = CT.sup.. CG.sup.. ALARM indicates that the desired
low level cut mode selection signal will be provided by gate 86 in
response to the simultaneous application of input signals
representing a cut signal, a lack of a coagulation signal, and a
lack of an alarm signal. The cut signal would be high and would be
provided via an inverter 88. The signal indicating the lack of a
coagulation signal and the lack of an alarm signal is provided at
the output of an inverter 90 which is connected to receive the
output of a NAND gate 92 connected to receive as inputs a high
signal via a lead 94 representing CG and a high signal via a lead
96 representing the lack of an alarm condition (ALARM).
Similarly, a blend mode selection signal is provided at the lead 72
at the output of a NAND gate 98 and a coagulation mode selection
signal is provided at the lead 56 at the output of a NAND gate 100
in accordance with the equations shown in FIG. 3.
As may be noted, the ALARM signal may be directly applied to each
of the NAND gates 86, 98 and 100 as a high level signal under
normal non-alarm conditions. This high level signal permits the
respective NAND gates 86, 98 and 100 to respond in a routine
fashion to any low level signals applied thereto. However, should
an alarm condition occur, the ALARM signal is replaced by a low
ALARM signal which would be applied to each of the NAND gates 86,
98 and 100. The result is that each of these gates 86, 98 and 100
will provide a high output signal regadless of the presence or
absence of any mode selection signals. The result is that the
electrosurgical unit is effectively disabled until the ALARM signal
is removed by the detected dangerous condition being remedied.
Any number of inherently dangerous conditions may be monitored and
used to generate an ALARM signal which disables the electrosurgical
unit. Exemplary of such monitoring schemes would be a heat
transducer situated within the unit itself to monitor the
temperature of certain component elements of the unit to detect
when the temperature is at a level dangerous to to components and
to the unit. For example, the temperature of a power transformer
may be monitored to prevent overheating and consequent damage to
circuit components.
A heat transducer circuit 102 is illustrated in FIG. 3 and is
intended to provide a high signal at an output lead 104 under
normal ambient conditions and a low signal whenever the temperature
is detected to be at a predetermined dangerous level. Any
conventional heat transducer circuit may be used. When the low
signal is applied via the lead 104 as an input to a NAND gate 106,
a corresponding low output signal is provided at the output of an
inverter 108 as an ALARM signal.
Another dangerous condition that may cause serious injury to a
patient is an imbalance in the amount of current flowing from the
electrosurgical unit through an active conductor to the
electrosurgical electrode and the current flowing from the
indifferent pad through ground conductor to a ground terminal of
the unit. Under normal conditions the amount of current flowing
through these two conductors is equal. An imbalance may indicate
that current applied to the patient is exiting through a path other
than the desired path provided by the indifferent pad. An example
would be where the indifferent pad is not in proper contact with
the patient and/or the patient is improperly grounded by having
some part of the body in contact with an item such as the operating
table at ground potential.
To detect such a dangerous condition, a current monitor 110 may be
provided to generate an ALARM signal which is also applied to the
NAND gate 106 as a low level signal to disable the electrosurgical
unit in the manner previously described.
An exemplary current monitoring circuit is illustrated by FIG. 4.
As shown, an active conductor 112 connected to an electrosurgical
electrode and a ground conductor 114 connected to an indifferent
pad may be wound about a toroidal core 16. A sensing winding 118 is
also wound about the toroidal core. Unequal amounts of current flow
through the conductors 112 and 114 will result in current flow
through the sensing windings 118. A current detector 120 of
conventional design is connected to the windings 118 to detect the
current flow therein and respond by providing a low output signal
to a latching circuit 124 via an output lead 122. In the exemplary
circuit of FIG. 4, the current detector 120 may be of the type that
will provide an output signal whenever the current flow through the
windings 118 exceeds a selected threshold current level.
The latching circuit 124 is of a conventional type including a pair
of NAND gates 126 and 128. The application of a low signal to the
NAND gate 126 via the lead 122 causes the output of the gate 126 to
be high. This high output of the gate 126 when applied as an input
to the gate 128, along with a high reset signal at the lead 129,
will cause the output of the latching circuit 124 at the terminal
130 to be low. As is typical of the illustrated latching circuit
124, the output appearing at the terminal 130 will remain low until
a low reset signal is applied to the gate 128 to reset the latching
circuit. If the reset signal used is a momentarily low signal (a
negative pulse), the output signal at the terminal 130 will remain
high (return to normal) only if the alarm condition has been
removed and the signal at the lead 122 is high. If a low signal
continues to bbe applied as an input to the NAND gate 126 via the
lead 122, the output of the latching circuit will revert to a low
signal after removal of the reset signal. As such, the
electrosurgical unit may not be artificially reset to be made
operative, without correction of the dangerous condition.
From the foregoing discussion, it is now apparent that operation of
the foot actuators 24 will cause mode selection signals to be
provided by the mode selection circuit 20 for controlling the mode
control circuit 22, and the level control circuit 18, such that the
driving pulses illustrated by waveforms L and M of FIG. 6 will be
applied from the NAND gates 36 and 38 at the output leads 136 and
138, respectively, to drive the push-pull amplifier circuit 10.
Referring now to FIG. 5, the push-pull amplifier circuit 10 may be
observed to basically include a conventional transistorized
push-pull amplifier circuit including complementary circuit halves
formed by serially connected transistors Q1, Q2, Q3, and Q1', Q2',
Q3'. The series connected amplifying transistors Q1 and Q2 are
driven by the transistor Q3 which is in turn driven by an output
transistor Q4. Similarly, the transistors Q1' and Q2' are driven by
the transistor Q3' which receives drive signals at the base thereof
from an output transistor Q4'. The drive transistors Q3 and Q3' are
alternately driven in unison with the output transistors Q4 and
Q4', respectively, in response to the application of the pulses
from the respective NAND gates 36 and 38 to the output gates 132
and 134 via leads 136 and 138, respectively.
The gates 132 and 134 as well as the gates 140 and 142 to be later
discussed, are of a conventional type wherein the application of
prescribed low signals thereto enable the gates.
Referring again to the waveforms of FIG. 6, the negative output
pulse applied from the gate 36 (waveform L) will enable the gate
132 and thereby permit current flow through the primary coil of a
coupling transformer 133. The transistor Q4 will be rendered
conductive by the resulting voltage across the secondary coil of
the transformer 133 to have a positive drive voltage (shown by
waveform F) applied to the base of the transistor Q3 from an
accurately controlled voltage source including a transistor Q5. The
transistors Q3, Q2 and Q1 will thus be rendered conductive as is
illustrated by waveform D of FIG. 6. Similarly, the negative pulses
from the NAND gate 38 (see waveform M) will enable the gate 134 to
permit current flow through the primary coil of a coupling
transformer 135. The transistor Q4' will thus be rendered
conductive and positive drive signals will be applied to the base
of the transistor Q3'. The transistors Q3', Q2' and Q1' will thus
be rendered conductive and non-conductive (as shown by waveform E)
at alternte time intervals with the transistors Q3, Q2 and Q1. An
essentially sinusoidal waveform is provided at the output terminals
16 via the output transformer 14 in that harmonics are for the most
part eliminated in the operation of the amplifier 10.
The push-pull amplifier 10 may be provided with an appropriate
number of capacitors 144 to provide filtering of any high frequency
ripple from the power supply connected thereto. It is to be
understood that although only series of two amplifying transistors
Q1 and Q2 and Q1' and Q2' have been illustrated, that each half of
the push-pull amplifier 10 may include a series of as many
transistors as is required to satisfy desired output power
requirements of a unit. For example, it has been found that as many
as eight transistors may be readily connected in parallel in the
manner exemplified by the transistors Q1 and Q2 or Q1' and Q2' to
provide an output power level of 600 watts.
The amplitude level of the signals provided at the output terminals
16 are controlled by a cut level control circuit including a
transistor Q6 for cut signals and a coagulation level control
circuit including a transistor Q7 for coagulation signals. The
level control circuits also include variable resistors 146 and 148
which are respectively connected to control the base voltage of the
transistors Q6 and Q7. Each of these resistors 146 and 148 is of
the type that may be manually adjusted by a user of an
electrosurgical unit. As shown, the gates 140 and 142 are connected
to be enabled by the application of mode selection signals from the
NAND gate 64 and the interver 60, respectively. Accordingly, the
cut and coagulation level control circuits will be operative only
during the periods of time during which cutting or coagulating
signals to be controlled are being provided at the output terminal
16.
As earlier mentioned, the transistor Q5 is connected to function as
an accurate voltage source that provides bias voltage to the
collectors of the output transistors Q4 and Q4'. The bias voltage
provided by the transistor Q5 is controlled by the operative one of
the two level control circuits including the transistors Q6 and
Q7.
The amplifier 10 is operated in a non-saturated mode by a pair of
feedback leads 150 and 152 that are respectively connected between
the nodes 154 and 156, at the ends of the primary coil 158 of the
output transformer 14, and the cathode of a zener diode 160. As the
voltage at the nodes 154 and 156 approaches a voltage level set by
the zener diode 160, i.e., 3 volts, a transistor Q8 having its base
connected to the zener diode 160 is rendered conductive. The
transistor Q5 is hence rendered non-conductive and the transistors
Q4 and Q4' cease providing additional drive voltage to the base of
the transistors Q3 and Q3', respectively. The transistor Q9 is
briefly rendered conductive and acts to drain any residual voltage
stored on the energized one of the secondary coils of the coupling
transformers 133 and 135.
Any suitable power supply circuit may be used with the subject
invention to provide the required biasing and other indicated
voltges. Needless to state, the multivibrator circuits 28, 42 and
74 may be of any conventional type wherein the duration and
frequency of pulses provided may be adjusted as desired.
A capacitor 162 is illustrated as being connected in one of the
leads to the output terminals 16. Such a capacitor 162 provides
D.C. isoltion to prevent the application of direct current to a
patient and thereby preclude unexpected muscular reactions by a
patient undergoing electrosurgery.
From the foregoing description, it is now clear that the present
invention provides an improved electrosurgical unit that provides
output signals for which the voltage levels are consistent,
accurately controllable, and not subject to degradation and
fluctuaton resulting from deterioration of included electronic
tubes.
While a preferred embodiment of the present invention has been
described hereinabove, it is intended that all matter contained in
the above description and shown in the accompanying drawings be
interpreted as illustrative and not in a limiting sense and that
all modifications, constructions and arrangements which fall within
the scope and spirit of the invention may be made.
* * * * *