U.S. patent number 3,735,756 [Application Number 05/155,823] was granted by the patent office on 1973-05-29 for duplex ultrasound generator and combined electrical muscle stimulator.
This patent grant is currently assigned to Medco Products Co., Inc.. Invention is credited to Mark E. DeGroff, Joseph M. Richards.
United States Patent |
3,735,756 |
Richards , et al. |
May 29, 1973 |
DUPLEX ULTRASOUND GENERATOR AND COMBINED ELECTRICAL MUSCLE
STIMULATOR
Abstract
A duplex electro-ultrasonic medical therapy apparatus comprising
a pair of ultrasound generators connected to a common power source
and keyed by a duplex keyer circuit, the output of which is
connected to a transducer which converts the electrical
oscillations into mechanical vibrations for application to the
patient's body to administer the ultrasonic medical therapy
treatment. The apparatus also comprises an integrated electrical
pulse generator having outputs connected to a pair of conductive
pads to supply electrical muscle stimulation to the patient's body
simultaneously with the ultrasound treatment. The electrical pulse
generator further serves as a driving function for the ultrasound
duplex keyer circuit.
Inventors: |
Richards; Joseph M. (Tulsa,
OK), DeGroff; Mark E. (Tulsa, OK) |
Assignee: |
Medco Products Co., Inc.
(Tulsa, OK)
|
Family
ID: |
22556942 |
Appl.
No.: |
05/155,823 |
Filed: |
June 23, 1971 |
Current U.S.
Class: |
601/2; 607/3;
607/72; 607/71 |
Current CPC
Class: |
A61N
1/36034 (20170801); A61H 23/0245 (20130101); A61N
1/36003 (20130101); A61H 2201/10 (20130101) |
Current International
Class: |
A61H
23/02 (20060101); A61N 1/36 (20060101); A61N
1/00 (20060101); A61m 001/26 () |
Field of
Search: |
;128/24A,24.1-24.5,404,405,420,421,422,423 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Kamm; William E.
Claims
What is claimed is:
1. A duplex electro-ultrasonic medical therapy apparatus comprising
in combination a power supply, a pair of ultrasound generators
connected to the power supply for producing sound waves, keying
means connected to the ultrasound generators for activating said
ultrasound generators, a separate sound head applicator for each
ultrasound generator and operably connected therewith for
converting the sound waves into mechanical vibrations; a low
voltage electrical pulse generator connected to the power supply,
pulse rate means connected to the pulse generator for varying the
frequency of the output pulses from the pulse generator, a pair of
electrode pads operably connected to the pulse generator for
producing electrical stimulation for electro-therapy, and means
connecting said pulse generator and keying means for providing
mechanical stimulation alternately in one sound head applicator and
then the other sound head applicator simultaneously with the
electrical stimulations in each electrode pad.
2. A duplex electro-ultrasonic medical therapy apparatus as set
forth in claim 1 wherein each sound head applicator comprises a
ceramic transducer for converting the sound waves into the
mechanical vibrations, and an electrode operably connected to the
electrode pads whereby dual electrical and mechanical stimulation
will be produced through each sound head applicator.
3. A duplex electro-ultrasonic medical therapy apparatus as set
forth in claim 1 wherein each sound head applicator comprises a
crystal transducer for converting the sound waves into the
mechanical vibrations, and an electrode operably connected to the
electrode pads whereby dual electrical and mechanical stimulation
will be produced through each sound head applicator.
4. A duplex electro-ultrasonic medical therapy apparatus as set
forth in claim 3 wherein the means for connecting the pulse
generator and keying means comprises a bistable multivibrator means
whereby each output pulse from the bistable multivibrator means is
used to drive the keying means thereby alternately keying the first
ultrasound generator and then the second ultrasound generator.
5. A duplex electro-ultrasonic medical therapy apparatus for
comprising in combination a power supply, a pair of ultrasound
generators connected to the power supply for producing sound waves,
keying means connected to the ultrasound generators for activating
said ultrasound generators, a pair of sound head applicators
operably connected with the ultrasound generators, each of said
sound head applicators having a crystal transducer for converting
sound waves into mechanical vibrations, a low voltage electrical
surge generator connected to the power supply, surge rate means
connected to the surge generator for varying the duration of the
output surge, voltage control means connected to the surge
generator for varying the intensity level of each surge output, a
pair of electrode pads operably connected to the low voltage
generator for electrically producing stimulation for
electro-therapy, and means connecting the surge generator to the
ultrasound keying means for alternately keying the first ultrasound
generator and then the second ultrasound generator thereby
producing alternating surge outputs from the ultrasound generators
simultaneously with the electrical stimulation surges in each
electrode pad.
6. A duplex electro-ultrasonic medical therapy apparatus as set
forth in claim 5 wherein each sound head applicator also comprises
an electrode operably connected to the electrode pads whereby dual
electrical and mechanical stimulation will be produced through each
sound head applicator.
7. A duplex electro-ultrasonic medical therapy apparatus comprising
in combination a power supply, a pair of ultrasound generators
connected to the power supply for producing sound waves, a pair of
sound head applicators operably connected with the ultrasound
generators, each of said sound head applicators having a crystal
transducer for converting sound waves into mechanical vibrations,
separate keying means for each ultrasound generator and operably
connected thereto, separate keyer monostable multivibrators
operably connected to each keying means for operating each keying
means, a bistable multivibrator operably connected to both keyer
monostable multivibrators for providing alternating inputs for each
keyer monostable multivibrator, a triggering monostable
multivibrator operably connected to the bistable multivibrator to
provide triggering inputs to the bistable multivibrator; a low
voltage electrical generator connected to the power supply having a
pulse mode of operation and a surge mode of operation, mode
selector switching means connected to the electrical generator for
selecting either the pulse or surge mode of operation, pulse rate
means connected to the electrical generator for varying the
frequency of the output pulses, surge rate means connected to the
electrical generator for varying the duration of the output pulses,
voltage control means connected to the electrical generator for
varying the intensity in either the pulse or surge mode of
operation, a pair of electrode pads operably connected to the low
voltage electrical generator for producing electrical stimulation
for electro-therapy and means for connecting the low voltage
electrical generator to the triggering monostable multivibrator
whereby each pulse or surge from the electrical generator will
operate the triggering multivibrator which in turn will trigger the
bistable multivibrator causing it to change states with each
triggering input thereby alternately keying the first ultrasound
generator and then the second ultrasound generator simultaneously
with the electrical stimulations in each electrode pad.
8. A duplex electro-ultrasonic medical therapy apparatus as set
forth in claim 7 wherein the electrical generator and mode selector
switching means provide, in addition, a continuous mode whereby the
electrical generator and the first ultrasound generator are
simultaneously turned off and the second ultrasound generator
produces a continuous ultrasound output.
9. A duplex electro-ultrasonic medical therapy apparatus as set
forth in claim 8 wherein a manually set timer is operably connected
to the power supply such that the electrical and mechanical
stimulations may be automatically turned off after a predetermined
treatment dosage.
10. A duplex electro-ultrasonic medical therapy apparatus as set
forth in claim 8 wherein a safety switch and positive latching
relay means are provided to preclude accidental switching to the
"continuous" mode of operation without manually closing the said
safety switch.
11. A duplex electro-ultrasonic medical therapy apparatus as set
forth in claim 10 wherein calibration switching means is provided
whereby the ultrasound intensity level may be preset prior to
application to the patient to be treated.
12. A duplex electro-ultrasonic medical therapy apparatus
comprising in combination a power supply, an ultrasound generator
connected to the power supply for producing sound waves, a pair of
sound head applicators operably connected to the ultrasound
generator, each of said sound head applicators having a transducer
for converting sound waves into mechanical vibrations; a low
voltage electrical pulse generator connected to the power supply
frequency adjustment means for varying the pulse rate, a pair of
electrode pads operably connected to the low voltage generator for
producing electrical stimulation for electrical therapy and means
connecting said low voltage generator and ultrasound generator
whereby mechanical vibrations will be provided alternately in one
sound head applicator and then in the other simultaneously with the
electrical stimulation in each electrode pad.
13. A duplex electro-ultrasonic medical therapy apparatus as set
forth in claim 12 wherein the means connecting the low voltage
generator and the ultrasound generator comprises a monostable
multivibrator for conditioning the output pulses from the low
voltage generator, a bistable multivibrator connected to the output
of said monostable multivibrator, two high power capacity "and"
gates operably connected to the dual outputs of the bistable
multivibrator and to the output of the ultrasound generator such
that the ultrasound signal is allowed to pass through the first
"and" gate only when the bistable multivibrator is in a first state
and said ultrasound signal is allowed to pass through the second
"and" gate only when the bistable multivibrator is in its second
state, the output of the first "and" gate being operably connected
to one sound head applicator and the output of the second "and"
gate being operably connected to the other sound head applicator.
Description
This invention relates to improvements in electro-therapy apparatus
and more particularly, but not by way of limitation, to a
combination dual low voltage electrical generator co-acting with
dual ultrasonic generators to provide simultaneous synchronized
dual electrical pulse stimulation and dual ultrasonic medical
therapy treatment.
The use of a combination of electrical muscle stimulation and
ultrasonic therapy is well known in medical science as disclosed in
the Mark E. DeGroff U.S. Pat. No. 2,830,578, issued Apr. 15, 1958.
However, heretofore the apparatus used in this application has
comprised a single ultrasound head thereby limiting the treatment
to only one area of the patient's body at a given time. Most
muscles of the human body, to effect a given movement, have
opposing muscles to effect an opposite movement. While the first
mentioned set of muscles are being treated by a single ultrasound
unit, the opposing muscles thereto are "antagonistic" to the muscle
being treated, and hence the treatment loses effectiveness by the
adverse reaction of the opposing muscles to the ones being treated.
The nerve controlling the painful area of the patient to be treated
is often remotely located with respect to the actual pain and hence
the simultaneous use of the conductive electrode pads of the
electrical muscle stimulator should be applied at that remote
location and can not be used effectively to provide relief to the
opposing or "antagonistic" muscles to those being treated directly
by the ultrasound unit.
The present invention contemplates a dual electro-ultrasonic
apparatus designed and constructed to overcome the above
disadvantages. The ultrasound portion of the present invention
comprises two ultrasonic oscillators, having built-in amplifiers or
keyed power oscillators. The output of these amplifiers or
oscillators drive two ultrasonic transducers which are used to
convert the electrical oscillations into mechanical vibrations to
effect the ultrasound treatment. The two ultrasound oscillators are
connected to a common power supply and to dual keyer circuits to
provide inter-dependent operation whereby the pulses emitted are
alternately produced by each respective oscillator and are spaced
by equal rest periods between the pulses. The two units may thus be
simultaneously utilized to effectively treat opposing muscles
without interference between said units. The present invention also
combines the ultrasound application with the low voltage electrical
muscle stimulator to produce simultaneously, superimposed
synergistic action of the ultrasound and electro-therapy combined.
Further, when there is no problem in the ultrasonic treatment of
opposing "antagonistic" muscles, the two ultrasound units may be
used simultaneously to cover a greater treatment area thereby
greatly reducing treatment time.
It is an important object of this invention to provide a novel
duplex electro-ultrasound apparatus for producing simultaneously,
dual superimposed synergistic action of combined ultrasonic and
electro-therapy.
It is another object of this invention to transmit through each of
two single ultrasound applicators both a low voltage current and an
ultrasound radio frequency for producing improved therapeutic
action.
It is still another object of this invention to provide a duplex
electro-therapy and dual ultrasound medical therapy apparatus in
one compact and portable unit.
Another object of this invention is to provide a medical therapy
unit wherein a plurality of electrode pad members and a pair of
sound head applicators are electrically grounded to a common ground
for producing dual, co-acting electrical stimulation and mechanical
vibrations for patient treatment.
And a still further object of this invention is to provide a novel
medical therapy apparatus wherein the dual, co-acting electrical
and mechanical stimulations may be automatically timed and
controlled to provide predetermined treatment dosage for patient
treatment.
Other and further objects and advantageous features of the present
invention will hereinafter more fully appear in connection with a
detailed description of the drawings in which:
FIG. 1 is a schematic diagram of the elements embodied in the
invention depicting the functional relationship of said
elements.
FIG. 2 is a schematic diagram of the electrical pulse generator
device depicting the keying function of the dual ultrasonic unit
and the generation of the electrical muscle stimulation pulses.
FIG. 3 is a schematic diagram depicting the functional relationship
between the dual ultrasonic treatment heads and the electrical
muscle stimulator pads.
FIG. 4 is an electrical circuit diagram of the electrical pulse
generator circuitry.
FIG. 5 is an electrical circuit diagram of the alternate pulse
controller network and keyer circuits for the ultrasound units.
FIG. 6 is an electrical circuit diagram of an ultrasound generator
network.
FIG. 7 is an electrical circuit diagram of the common power control
network for the ultrasound generator and the keyers.
FIG. 8 is an electrical circuit diagram of the power supply and
central control circuitry.
FIG. 9 is a schematic diagram depicting the gating of the
ultrasound generator output.
Referring to the figures in detail, reference character 10
generally indicates a duplex ultrasound generator and combined
electrical muscle stimulator for administering ultrasonic and
electro-medical therapy treatment. The medical therapy apparatus 10
specifically comprises a first and second sound head applicator 12
and 14, each of which are operably connected to a pair of radio
frequency ultrasound generators 16 and 18, respectively, to provide
sound waves for producing mechanical vibration in the sound head
applicators 12 and 14 in a manner as will be hereinafter set forth.
The medical therapy apparatus 10 also comprises a first and a
second of electrode pad means 20 and 22 which are operably
connected to a low voltage electrical muscle stimulator generator
generally indicated by reference character 24 which produces
interrupted modulated current in either a "pulse" mode of operation
or a "surge" mode of operation, in a manner as will be hereinafter
set forth.
Reference character 26 generally indicates a common power supply
for the medical therapy apparatus 10. The electrical input power
for the apparatus 10 is supplied by connection of the power supply
26 to any suitable common alternating current line (not shown) with
voltage preferably ranging from 110 to 125 volts AC with frequency
between 50 and 60 cycles. The power supply unit 26 may be connected
with the line voltage by means of a suitable plug member 28 (FIG.
8) and the input power is supplied to the power supply 26 through a
suitable line filter 30 to prevent any radio frequency interference
back into the power line.
The input power line is protected by suitable current limiting
devices 31 and 33 connected in series with the input windings of
the power transformers T4 and T5, respectively. A timer device 35
is also connected in series with the input power to provide for
predetermined application dosages of the ultrasound and
electro-therapy treatment.
Referring particularly to FIG. 4, which is an electrical circuit
diagram of the electrical pulse generator 24, the transistor Q1 and
its associated components represents a blocking oscillator 32 which
generates electrical impulses which are used to provide the
electrical muscle stimulation voltages in a manner as will be
hereinafter set forth. The frequency of these electrical impulses
is controllable by the variable resistor R1 (FIGS. 2 and 8) for
varying the RC time constant in the base of the transistor Q1. The
output of this blocking oscillator 32 is connected to a blocking
oscillator transformer T3 (FIG. 8) which is used to couple the
output voltages from the pulse generator 24 to a first electrode
pad jack 21 and a second pad jack 23 for connecting the electrical
pads 20 and 22 respectively thereto, and simultaneously to the
alternate pulse control network, depicted in FIG. 5, through the
secondary output windings S1 and S2, respectively, of the
transformer T3. The amplitude of the blocking oscillator impulses
is controllable by a variable resistor R2 (FIG. 8) which is
operably connected across the output winding S1 of the transformer
T3. It is readily apparent that by means of the two output windings
S1 and S2, electrical pulses identical in frequency to the
stimulation voltages are supplied to the alternate pulse control
network (FIG. 5) through a coupling transformer T2. The blocking
oscillator 32 also comprises a voltage supply circuit and two
control transistors Q2 and Q3 and their associated components (FIG.
4). As hereinbefore set forth, the electrical pulse generator 24
may be operated in a pulse mode or in a surge mode. The mode
selection is accomplished by a switching means SW1 (FIG. 8). The
switch SW1 is a six-pole triple-throw switch which may be set in a
first position for a pulse mode of operation, hereinbefore set
forth, or a second position for a surge mode of operation wherein a
standard astable multivibrator 34 (FIG. 4) is coupled to the
blocking oscillator power control transistors Q2 and Q3 which in
turn supply voltage to the blocking oscillator transistor Q1. The
blocking oscillator 32 thus produces a series of output surges each
being followed by an equal rest period. The repetition rate of
these output surges for this particular application is variable
from approximately one second on and one second off to six seconds
on and six seconds off, by means of a rheostat R3 (FIG. 8). The
astable multivibrator 34 is comprised generally of transistors Q4,
Q5, the unijunction transistor Q6 and their associated components
(FIG. 4). The third position of the switch SW1 is for operation of
the ultrasound generator in a continuous mode in a manner as will
be hereinafter set forth.
When the switch SW1 is positioned in with the pulse or the surge
mode the output impulses or surges from the blocking oscillator 32
are supplied to the alternating pulse control network depicted in
FIG. 5 by way of the output winding S2 of the transformer T3, then
through the coupling transformer T2. Power to operate the
alternating pulse control network is provided from the output
winding S4 of the power transformer T4 and is converted to direct
current by the half-way rectifier circuit 36 (FIG. 5). Each pulse
or surge from the blocking oscillator 32 is then provided from the
transformer T2 as an input to a standard monostable multivibrator
38. The one-shot monostable multivibrator 38 is comprised of two
N-P-N transistors Q6 and Q7, a unijunction transistor Q8 and
associated components. As depicted in FIG. 5, the transistor Q6 is
"on" in the quiescent state. Therefore, a negative pulse at the
base of Q6 will trigger the one-shot. At the end of the timing
interval, the unijunction will be triggered and cause the circuit
to revert to its quiescent state. The monostable multivibrator 38
has the advantage of a fast recovery time thereby permitting
operation at a high duty ratio without any loss of accuracy. This
multivibrator 38 generates pulses of uniform width; one standard
pulse is generated for each input pulse provided by the oscillator
32. The width of the output pulse of the multivibrator 38 is
approximately 16.6 milliseconds for this application, due to the
time constant of the resistor R5 and capacitor C1 and the action of
the unijunction transistor Q8. These standard 16.6 millisecond
pulses are then coupled to a standard bistable multivibrator 40.
Since the multivibrator 38 only puts out standard pulses of 16.6
milliseconds duration, the maximum number of pulses that can be
produced will be 60 per second which will maintain a low duty cycle
level in each ultrasound generator as will be hereinafter set
forth. The bistable multivibrator 40 is comprised of a pair of
N-P-N transistors Q9 and Q10, and their associated components. Each
input pulse from the multivibrator 38 then operates to trigger the
bistable multivibrator 40 (flip-flop) which in turn automatically
generates narrow pulses for each of its two outputs. The first
output of this bistable multivibrator 40 is coupled to a monostable
multivibrator 42 and the second output thereof is coupled to a
second monostable multivibrator 44. The monostable multivibrator 42
comprises a pair of N-P-N transistors Q11 and Q12, a unijunction
transistor Q13, and associated components. Referring to FIG. 5, Q11
is "on" in the quiescent state. Therefore, a negative pulse at the
base of Q11 will trigger the one-shot. At the end of the timing
interval, the unijunction transistor Q13 will be triggered and
cause the circuit to revert to the quiescent state. The timing
interval for this application is approximately 6.6 milliseconds,
due to the time constant of the resistor R6 and the capacitor C and
the action of the unijunction transistor Q13. The monostable
multivibrator 42, like that of 38, has the advantage of a fast
recovery time. The monostable multivibrator 44, which is
substantially identical to that of 42, is comprised of a pair of
N-P-N transistors Q14 and Q15, a unijunction transistor Q16, and
associated components. Referring to FIG. 5 again, the transistor
Q14 is "on" in the quiescent state, therefore a negative pulse at
the base of Q14 will trigger the one-shot. At the end of the timing
interval, which is set by the time constant of the resistor R7 and
the capacitor C3, the unijunction transistor Q16 will be triggered
and cause the circuit to revert to its quiescent state. Each of the
multivibrators 42 and 44 generate a standard width output pulse in
response to each input pulse as provided by the multivibrator 40.
It is readily seen that these output pulses alternate in response
to each input pulse provided by the blocking oscillator circuit 32.
The standard output pulse from the multivibrator 42 is provided as
an input to a first ultrasound keyer circuit 46 which comprises two
P-N-P transistors Q17 and Q18 and their associated components (FIG.
5). The multivibrator 44 likewise provides an automatic standard
pulse output to a second ultrasonic keyer circuit 48 which
comprises two P-N-P transistors Q19 and Q20, and their associated
components (FIG. 5). Each of the keyer circuits 46 and 48 provide
positive voltage output pulses for each keying pulse from the
monostable multivibrators 42 and 44, respectively. For this
particular application, each keyer output pulse is approximately
6.6 milliseconds in duration and 32 volts in amplitude.
The output pulses provided by the keyer circuit 46 is coupled to an
oscillator and buffer circuit 51 of the first ultrasonic generator
16 (FIG. 6). The oscillator and buffer circuit 51 comprises two
N-P-N transistors Q21 and Q22 and associated components. Likewise,
the alternate output pulse provided by the keyer circuit 48 is
coupled to a substantially identical oscillator and buffer circuit
(not shown) of the second ultrasound generator 18. Each ultrasound
generator 16 and 18 produces an output pulse equal in duration (6.6
milliseconds) to the input pulse from the keyer circuits 46 and 48
and of a frequency of approximately 1 megaHertz, for this
application. As pointed out, these output pulses alternate between
the ultrasound generators 16 and 18 so that they do not produce
outputs simultaneously. The amplitude of the ultrasound generator
output pulses are simultaneously adjustable by means of a
potentiometer R4 (FIG. 8) which adjusts the voltage supplied by an
output collector circuit 52 of the ultrasound generator 16; and a
second substantially identical output collector circuit (not shown)
of the ultrasound generator 18. The output collector circuit 52
comprises an N-P-N transistor Q23 and its associated components
which provides the 1 megaHertz output through the output coupling
transformer T6. It is again noted that the ultrasound generator 16
circuitry depicted in FIG. 6 is duplicated for the ultrasound
generator 18. The output from the ultrasound generator 16 is
provided to a first ultrasound applicator jack 54 (FIG. 8) and the
output from the ultrasound generator 18 is provided to a second
ultrasound applicator jack 56 (FIG. 8) for use with the ultrasound
applicators 12 and 14, respectively. Referring to FIG. 1, each
sound head applicator is provided with a crystal or ceramic type
transducer 53 and 55, respectively, when provided with the
ultrasound radio frequencies from the ultrasound generators 16 and
18, are resonated at their natural frequencies. In this
application, the transducers 53 and 55 are constructed to vibrate
only at the frequency of approximately 1 megaHertz. Although it is
readily seen that the outputs of the ultrasound generators 16 and
18 are equal since equal voltages are applied to each collector
circuit 52, two separate ultrasound intensity meters 57 and 59 are
provided so that the output of each ultrasound generator may be
monitered separately. When the ultrasound is operated at low duty
cycle levels, the ultrasound intensity meters 57 and 59 do not
indicate the peak ultrasound power (the meter circuit being a
R.M.S. type measuring device). The dosage preset switch SW6 and a
dummy load consisting of an adjustable resistor R6 and a capacitor
C4 have been provided to permit the therapist to set the treatment
dosage to a desired level without the necessity of artificially
loading the vibrating transducers 53 and 55. By actuating the push
button switch SW6, the dummy load resistor R6 (which has been
previously calibrated) is substituted for the transducer 55 and
simultaneously switches the blocking oscillator to the rapid or
"tetanizing" pulse mode of operation. Further, the blocking
oscillator voltage is removed from the electrode pads to prevent
any unpleasantness to the patient due to unexpected changes in
stimulation level. By this means, and by the use of the ultrasound
intensity control R4, the treatment dosage may be set at any
desired peak power level. This present peak power will then be
produced in each ultrasound impulse even through the duty cycle is
quite low.
A two-pole single-throw switch SW4 (FIG. 8) is provided whereby the
first-mentioned ultrasound generator 16 may be switched off
independently of the second ultrasound generator 18 by interrupting
the keyer circuit 48 output to the oscillator buffer circuit 51 of
the ultrasound generator 16. It should be noted that when the
selector switch SW1 is in the "continuous" position (as shown) the
ultrasound generator 16 is automatically switched off and the
ultrasound generator 18 is keyed to produce continuous ultrasonic
energy of 1 megacycle frequency as distinguished from the pulse and
surge modes of operation described above.
Referring to FIGS. 1 and 8, the circuitry is so arranged to provide
stimulation voltage from the blocking oscillator circuit 32
directly to the two ultrasound applicators 12 and 14 through the
connector jacks 54 and 56, respectively. As stated above, the
amplitude of the blocking oscillator voltage is adjustable by means
of the potentiometer R2 and the frequency thereof is controllable
by the potentiometer R1.
Since pulsed ultrasound at a low duty cycle rate and high peak
power may be applied to a patient with the ultrasound transducers
strapped in place, without danger of tissue damage or periosteal
pain, it may readily be seen that inadvertent switching to
continuous, by means of SW1, or 100 percent duty cycle ultrasound
would be very undesirable inasmuch as serious discomfort and even
injury to the person under treatment could result.
To prevent this type of accident, a safety circuit, as generally
indicated by reference character 61, has been devised. This circuit
61 is comprised of a portion of six-pole three position selector
switch SW1, the relay RY1 and the push button switch SW5. It may be
seen that when the selector switch SW1 is rotated to the
"continuous" position that even though the ultrasound power switch
SW3 is in the "on" position, no power will be supplied to the
primary of the ultrasound power transformer T5, unless the push
button switch SW5 is momentarily depressed to actuate the relay
RY1. RY1 will not remain closed unless the ultrasound power switch
SW3 is in the "on" position. Further, de-energizing the relay due
to any cause necessitates resetting by means of SW5, thus obviating
the possibility of inadvertently leaving the unit operating in the
continuous mode.
Further, in the continuous position the stimulator is
simultaneously turned off by means of RY1. This is to serve as an
indicator to the therapist that no ultrasound is being produced
(ultrasound being sensationaless at therapeutic dosage levels)
because there will be no electrical muscle stimulation either. The
electrical muscle stimulation is felt quite plainly by the patient
and may also be observed by the therapist. Therefore, inadvertent
failure to energize the ultrasound would be apparent immediately to
both the patient and the therapist.
A single-pole single-throw switch SW2 (FIG. 8) is provided whereby
the electrical power may be interrupted between the power
transformer T4 and the timer 35 thereby cutting off the power to
the electrical muscle stimulation generator 24. A two-pole
single-throw switch SW3 is also provided whereby the electrical
power may be interrupted between the power transformer T5 and the
line input power thereby cutting off power to the ultrasound
generators 16 and 18. It is readily seen that the electrical muscle
stimulation generator 24 may be operated independently of the
ultrasound generators 16 and 18 by positioning the switch SW2 in
the closed position and the switch SW3 in the open position.
A single ultrasound generator power supply 50 is provided to supply
electrical power for the ultrasound generators 16 and 18. The power
supply 50 utilizes two silicone controlled rectifiers (SCR), SCR1
and SCR2, in a typical single phase center-tip phase-controlled
rectifier. By varying the rheostat R4 the DC voltage across the
load can be continuously adjusted from its maximum resistance value
down to zero. As in the AC phase-controlled switch a single
unijunction transistor Q24 is used to develop a gate signal to fire
both SCR's on alternate half-cycles. Whichever of the two SCR's has
positive anode voltage at the time the gate pulse occurs will fire,
thus applying voltage to the load for the remainder of the
half-cycle. The firing angle can be adjusted by means of the
rheostat R4. In this application, at 60 Hertz, the firing angle of
this circuit can be varied from approximately 10.degree. to
180.degree. (fully off).
It should be noted that the electrical circuitry depicted in FIGS.
4 through 8 may be constructed as one complete integrated circuit
or as separate disconnectable modules as shown. As shown in the
drawings, each of the circuit modules, FIGS. 4 through 7, are
connected to the power supply and control circuitry depicted in
FIG. 8, in a manner as follows:
The electrical pulse generator circuitry (FIG. 4) is connected to
the circuitry of FIG. 8 by means of a common connector J4 having
pin connections 1 through 7. The circuitry of FIG. 5 is connected
to the circuitry of FIG. 8 by means of a common connector J5 having
pin connections 1 through 7. The circuitry of FIG. 6 is connected
to that of FIG. 8 by a common connector J6 having pin connections 1
through 7. The second ultrasound generator 18 circuitry (not shown)
which is substantially identical to that of FIG. 6 is connected to
the circuitry of FIG. 8 by a common connector J6a having pin
connections 1 through 7. The circuitry of FIG. 7 is also connected
to the circuitry of FIG. 8 by means of a common connector J7 having
pin connections 1 through 11.
It is readily apparent that the dual alternating ultrasound
treatment could be effected by the utilization of only one
ultrasound generator 16a by suitable gating in conjunction with the
bistable multivibrator 40. This could be accomplished by the use of
two high power capacity "and" gates 67 and 69 (FIG. 9). The output
of the single ultrasound generator 16a would be present
simultaneously as an input to each "and" gate. The other input to
the first "and" gate 67 would be provided by the first output from
the bistable multivibrator 40 such that the ultrasound signal would
be allowed to pass through the first "and" gate 67 only when the
bistable multivibrator 40 is in its first state. The second input
to the second "and" gate 69 would be provided by the second output
from the bistable multivibrator 40 such that the ultrasound signal
would be allowed to pass through said second "and" gate 69 only
when the bistable multivibrator 40 is in its second state. Since
the bistable multivibrator 40 (flip-flop) can be only in one state
at a single instant in time, the ultrasound signal would
necessarily alternate between the output of the first "and" gate 67
and the second "and" gate 69. The problem with this arrangement at
the present time is the inability to obtain commercially available
reliable components for the "and" gates which have the power
capacity required to handle the ultrasound generator output.
OPERATION
In using the duplex electro-ultrasonic medical therapy apparatus 10
in the "pulse" mode of operation, to simultaneously produce a
super-imposed synergistic action in patient treatment, the unit is
activated by closing the switch SW2. The switch SW3 is then closed
to provide electrical power to the ultrasound generators. The
switch SW1 is then set in the "pulse" position and the switch SW4
is closed to provide impulses from the keyer circuit 48 of FIG. 5
to the ultrasound generator 16. Before application to the patient,
and especially when intending to operate at a low duty cycle level,
the switch SW6 should be closed in order to calibrate the
ultrasound power level. This feature is provided since the dosage
reading meters 57 and 59 (FIG. 8) are R.M.S. type measuring devices
and as such do not indicate the peak ultrasound power when operated
at a low duty cycle. In closing the switch SW6, the dummy load
resistor R6 (FIG. 8) is substituted for the transducer 55 and the
stimulator is automatically switched to the rapid pulse (or
"tetanizing") mode of operation. At this point, the desired
ultrasound intensity level may be adjusted by the rheostat R4.
After setting the ultrasound power level to the desired intensity,
adjusting to the desired pulse rate by the rheostat R1 and the
stimulation voltage level by means of the potentiometer R2, the
switch SW6 is opened and the apparatus 10 is ready for patient
treatment.
As hereinbefore set forth, the ultrasonic pulses are being produced
alternately by each ultrasound unit 16 and 18 and converted to
mechanical vibrations by the transducers 53 and 55, respectively.
In addition to the ultrasonic vibrations, the circuit is so
arranged to simultaneously supply electrical muscle stimulation to
the treatment area either through the conductive electrode pads 20
and 22 or in combination with the transducers 53 and 55. As
previously mentioned, in addition to supplying ultrasonic energy
for treatment, the two ultrasound applicator heads 12 and 14 may be
used to simultaneously apply electrical muscle stimulation which
effects massage of the musculature for reducing pain, increasing
circulation and other therapeutic actions. By using the dual
ultrasound heads 12 and 14 simultaneously, one of the heads may be
placed on the primary area of the patient to be treated while the
other head is placed on the so-called "antagonistic" muscle as
hereinbefore set forth.
The use of the duplex ultrasound circuitry to produce
interdependent operation of the two ultrasound units allowing only
one of the two units 16 and 18 to produce output at a given instant
in time, permits effective treatment of twice the normal treatment
area while substantially reducing treatment time. Where the use of
only one ultrasound head applicator is desired, the switch SW4 may
be opened, thereby removing the keying impulses and high voltage
from the ultrasound generator 16.
When it is desired to utilize the unit 10 in a surge mode of
operation, the selector switch SW1 is set in the "surge" position,
and the switch SW6 is temporarily closed for purposes of
calibration as set forth in the pulse mode of operation above. As
hereinbefore set forth, the surge mode of operation is effected by
the astable multivibrator 34 which is coupled to the power
controlled transistor Q2 and Q3 which in turn supply voltage to the
blocking oscillator 32. The blocking oscillator 32 thus produces
output surges followed by equal rest periods. The rheostat R3 is
then utilized to set the desired repetition rate of the surges. The
use of the unit 10 in the surge mode of operation is similar to
that of the pulse mode and it will be apparent that when it is
desired to use only one of the ultrasound units in the surge mode,
the ultrasound unit 16 may be turned off by using the switch
SW4.
It is well known that if large amounts of continuous ultrasonic
energy is administered, the patient will suffer not only periosteal
pain, but tissue damage as well. Hence, the use of pulsed
ultrasound to reduce pain and the possibility of tissue damage is
well known. When it is desired to utilize the apparatus 10 in an
ultrasound continuous mode of operation, the switch SW1 is set in
the "continuous" position and the safety switch SW5 is closed
momentarily to actuate the relay RY1. RY1 will not remain closed
unless the ultrasound power switch SW3 is in the closed position.
Further, de-energizing the relay RY1 due to any cause necessitates
resetting by means of the switch SW5, thus obviating the
possibility of inadvertently leaving the unit operating in the
"continuous" mode. When the relay RY1 is actuated, it is readily
seen (FIG. 8) that the blocking oscillator 32 is simultaneously
turned off.
From the foregoing it will be apparent that the present invention
provides a duplex electro-ultrasonic medical apparatus particularly
designed and constructed for producing simultaneously, dual
superimposed synergistic action of combined ultrasonic and
electrical muscle stimulation therapy by transmission through each
of two ultrasound applicators both in low voltage current and
ultrasonic mechanical vibrations. The novel duplex
electro-ultrasonic medical therapy apparatus is economical and
durable in construction and simple and efficient in operation.
Whereas the present invention has been described in particular
relation to the drawings attached hereto, it should be understood
that other and further modifications, apart from those shown or
suggested herein, may be made within the spirit and scope of this
invention.
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