U.S. patent number 3,730,188 [Application Number 05/127,727] was granted by the patent office on 1973-05-01 for electrosurgical apparatus for dental use.
Invention is credited to Irving A. Ellman.
United States Patent |
3,730,188 |
Ellman |
May 1, 1973 |
ELECTROSURGICAL APPARATUS FOR DENTAL USE
Abstract
Electrosurgical apparatus for dental use employing an electronic
radio-frequency oscillator is described. The radio-frequency
oscillator or R.F. generator is powered by an electronic power
supply constructed to selectively deliver full-wave rectified
voltage and current for excellent cutting with minimal hemostasis,
half-wave rectified voltage and current providing moderate cutting
with maximum hemostasis, and voltage and current between the
full-wave rectified and half-wave rectified condition for combined
good cutting and good hemostasis. A further variation makes
selectively available filtered or unfiltered rectified voltage and
current for further control over cutting and hemostasis.
Inventors: |
Ellman; Irving A. (Cedarhurst,
NY) |
Family
ID: |
22431631 |
Appl.
No.: |
05/127,727 |
Filed: |
March 24, 1971 |
Current U.S.
Class: |
606/37 |
Current CPC
Class: |
A61B
18/12 (20130101); A61B 18/1206 (20130101); A61B
2018/0066 (20130101) |
Current International
Class: |
A61B
18/12 (20060101); A61b 017/38 (); A61n
003/02 () |
Field of
Search: |
;128/303.14,303.17,423 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Pace; Channing L.
Claims
What is claimed is:
1. Electrosurgical apparatus for dental use providing controlled
cutting and coagulation comprising a radio-frequency oscillator
circuit for generating at its output radio-frequency oscillating
currents when activated by voltage at its input, means coupled to
the output of said radio-frequency oscillator for applying said
radio-frequency oscillating currents to a dental patient, a voltage
supply circuit for receiving A.C. voltage and converting same to a
rectified D.C. output voltage capable of activating said
radio-frequency oscillator when applied to the oscillator input,
means for applying the said output voltage of the supply circuit to
the input of the radio-frequency oscillator, and means connected to
said voltage supply circuit for selectively changing the waveform
of its output voltage and thereby selectively modifying the
radio-frequency oscillating currents generated by the oscillator
when activated by said output voltage, said voltage supply circuit
comprising a single-phase full-wave rectifier circuit comprising
plural rectifiers capable of producing a fully-rectified output
voltage, and the selective changing means comprising means
connected to the rectifier circuit for producing a half-wave
rectified output voltage.
2. Electrosurgical apparatus as set forth in claim 1 wherein the
selective changing means comprises means for introducing resistance
in series with at least one of the rectifiers to produce a
rectified output voltage wherein the peak voltage is different for
alternate half cycles.
3. Electrosurgical apparatus as set forth in claim 1 wherein the
selective changing means comprises means for connecting one of the
rectifiers to the bridge circuit, means for disconnecting one of
the rectifiers from the bridge circuit, and means for connecting
one of the rectifiers in series with a fixed resistor in the bridge
circuit.
4. Electrosurgical apparatus as set forth in claim 1 wherein the
selective changing means includes a variable resistance, and means
for selectively connecting the variable resistance into the voltage
supply circuit.
5. Electrosurgical apparatus as set forth in claim 1 wherein the
voltage supply circuit comprises a single phase full-wave bridge
rectifier circuit and the selective changing means includes means
for disabling at least one of the rectifiers.
6. Electrosurgical apparatus as set forth in claim 1 wherein the
rectifier circuit comprises a center-tapped transformer and two
rectifiers, and the selective changing means comprises means for
disconnecting one of the two rectifiers.
7. Electrosurgical apparatus as set forth in claim 6 wherein the
selective changing means comprises means for introducing a
resistance in series with one of the two rectifiers.
8. Electrosurgical apparatus as set forth in claim 1 wherein the
voltage supply circuit comprises filtering means, and the selective
changing means comprises means for selectively connecting the
filtering means to the voltage supply circuit.
9. Electrosurgical apparatus as set forth in claim 8 wherein the
selective changing means comprises a three-position switch for
connecting the filtering means in one switch position and for
disabling part of the rectifying circuit in another switch
position.
Description
This invention relates to electrosurgical apparatus primarily for
dental use.
Electrosurgical apparatus has come into wide use in dentistry
because of its capability for making incisions in or cutting live
gum tissue while minimizing bleeding, i.e., hemostasis. In its
known form, the apparatus comprises a high-frequency oscillator or
radio-frequency (R.F.) generator in the range, generally, of 2-4
MHz, which is usually a conventional Hartley or Colpitts oscillator
employing a triode or tetrode electron tube capable of delivering
from 25-100 watts of R.F. power. Such R.F. generators have been
generally powered by single phase full-wave or half-wave rectifier
circuits operated directly from the commonly available A.C. house
supply and capable of supplying the high voltages and currents
necessary to operate the R.F. generator. However, the R.F. output
that is optimum for cutting is often not the optimum R.F. output
for controlling bleeding. Prior art efforts to overcome these
difficulties have followed generally along two different paths. In
the first, two different kinds of R.F. generators have bee provided
each to supply a different form of R.F. output for maximizing
cutting or maximizing hemostasis. For example, a spark-gap
generator is used for generating damped R.F. oscillations giving
excellent coagulation, and an electron tube generator is employed
for providing sustained undamped oscillations for excellent
cutting. Apparatus has been developed following the second path
employing special gating multivibrator or other pulsing circuits
for enabling controlled bursts of short duration of the R.F.
oscillations to be supplied to the tissue.
Both of these prior art paths have resulted in complicated,
expensive apparatus that have not fulfilled a real need in the
dental art for simple, inexpensive apparatus offering sufficient
control over the waveform of the generated R.F. power output
enabling the dentist to obtain optimum cutting, hemostasis, or
combined cutting and hemostasis for satisfying the wide variation
in operating conditions encountered in treating many dental
patients.
The main object of the invention is improved electro-surgical
apparatus capable of delivering controlled R.F. power to provide
excellent cutting, excellent hemostasis, or both with remarkably
simple and inexpensive circuitry.
These and other objects of the invention as will appear hereinafter
are achieved in accordance with the invention by constructing the
power supply that powers or activates the R.F. generator such that,
in a manner selected by the dentist, it will provide to the R.F.
generator fully-rectified D.C. power, half-wave rectified D.C.
power, and forms of rectified D.C. power lying between these
extremes. As a further feature of the invention, the power supply
can be selectively controlled to provide filtered or unfiltered
D.C. power to the R.F. generator providing still a further way of
optimizing the cutting and coagulating capabilities of
electrosurgery for dental use.
The foregoing and other objects of the invention will become more
apparent from the following detailed description of several
exemplary embodiments of the invention taken in conjunction with
the accompanying drawing wherein: FIG. 1 is a circuit diagram of
one form of electrosurgical apparatus in accordance with the
invention employing a bridge rectifier circuit; FIGS. 2a, 2b and 2c
illustrate the waveforms of the three D.C. output voltages
derivable from the bridge rectifier embodiment of FIG. 1; FIG. 3 is
a circuit diagram of just the power supply of a second embodiment
of the invention employing a center-tapped transformer; FIG. 4 is a
circuit diagram of just the power supply of a third embodiment of
the invention employing a filtered rectifier; FIGS. 5a, 5b and 5c
illustrate the waveforms of the three D.C. output voltages
derivable from the embodiment of FIG. 4.
FIG. 1 illustrates a typical R.F. electron tube generator employing
a Colpitts oscillator circuit. This is employed merely to
illustrate one form of known oscillator, it being understood that
other known forms of radio-frequency oscillators may also be used.
Also, while a tetrode tube is shown, triodes or semiconductor
devices can be used in place of the tetrode. The filament circuitry
for the tube is not shown as it is well known, and similarly many
of the known safety features of the circuit have been omitted as
unnecessary to an understanding of the present invention.
The tetrode 10 contains the usual cathode 11, control grid 12,
screen grid 13 and plate 14. The usual tank circuit 15, consisting
of paralled connected coil 16 and capacitors 17 is coupled via
capacitors 18 and grid resistor 19 between the control grid 12 and
plate 14. The connection between the tank capacitors 17 is
grounded. The control grid 12 is also connected via an R.F. choke
21 and resistor 22 to ground. The cathode 12 is grounded via an
on-off switch 23, which can be a foot switch operable by the
dentist for turning the R.F. generator on and off as desired. The
R.F. power output is taken from the plate via several blocking
capacitors 25, one of which 26 is variable to control the output
R.F. power. The power can be applied to the patient via terminals
27, which is the hot or active terminal, and 28, which is ground.
As is well known, the patient is connected to the ground terminal
28, and the usual cutting implement or electrode is connected to
the active terminal 27 and then applied by the dentist to the
patients tissue where cutting or coagulation is desired.
The high voltage for operating the R.F. generator is obtained from
a power supply designated 30. The power supply 30 comprises the
usual high voltage transformer 31 having a primary winding 32
connected to the A.C. supply, usually 110 volts, 60 Hz, and a high
voltage secondary winding 33 connected to opposite sides of a
bridge rectifier 34 at points designated 35 and 36. The remaining
two points of the bridge designated 37 and 38, are connected
respectively to the tetrode plate 14 via an R.F. choke 39 and to
ground. Three of the rectifiers, designated 40, of the bridge are
connected in the usual way as shown. However, in accordance with
the invention, the fourth rectifier 41, instead of being connected
directly to point 38 as is usual, is connected to the movable arm
42 of a three-position rotary switch 43 having positions A, B, and
C. Position A is directly grounded. Position B is grounded via a
series resistor 44, and Position C is unconnected or open.
FIG. 2 illustrates the voltage output waveforms from the point 37
to ground of the power supply 30 with switch 43 in the three
positions as selected by the dentist upon operating the switch 43.
With switch 43 in position A, a normal bridge rectifier is obtained
producing unfiltered full-wave rectification, as illustrated by the
solid line curve in FIG. 2a. With switch 43 in position C, one leg
of the bridge is disabled producing unfiltered half-wave
rectification, as illustrated in FIG. 2C. With switch 43 in
position B, one leg of the bridge has an additional resistance 44
in series causing a voltage drop across it with the result that
while full-wave rectification is obtained, the output voltage level
during the half cycle when the rectifier 41 is conducting is
reduced, producing a full voltage half sine wave 44, as illustrated
in FIG. 2b, and a partial voltage half sine wave 45.
Application of the voltages depicted in FIG. 2 to the R.F.
generator will cause it to break into oscillation each time the
rising voltage of each half sine wave reaches a level causing the
tetrode to conduct, and the R.F. oscillations will terminate as the
voltage reapproaches zero. Thus, the FIG. 2 solid line waveforms
illustrate the top half of the modulation envelope of the R.F.
power output which can be applied to the patient, the bottom half
being a mirror image of the top half. This is illustrated by the
dashed curves shown.
The R.F. power generated by the waveform depicted in FIG. 2a
provides the hottest current and thus maximum cutting but with
minimum hemostasis. The R.F. power corresponding to the waveform of
FIG. 2c provides poorer cutting but excellent hemostasis because
the R.F. energy is interrupted for a time substantially equal to
the time of its application, thus allowing the tissue to cool
between the R.F. pulses. The waveform of FIG. 2b provides an
operating condition roughly halfway between that of FIGS. 2a and
2c, that is, the cutting is better than with the waveform of FIG.
2c, and the hemostasis is more effective than with the waveform of
FIG. 2a because of the smaller power pulses 45, allowing some
tissue cooling, alternating with the larger power pulses 44.
Thus, by simple switching of one of the legs of the bridge
rectifier in and out of the circuit, or in series with a resistor,
a very simple circuit results for controlling the output R.F. power
waveforms in a stepped manner for optimizing, at the will of the
operating dentist, the apparatus for cutting, for hemostasis, and
for combined cutting and hemostasis.
FIG. 3 is a circuit of a modified power supply providing an even
greater flexibility of operation. A full-wave rectifier circuit is
illustrated, this time with a center-tapped transformer 50, of
which only the secondary is shown. The usual two rectifiers 51 and
52 are shown. In the usual full-wave rectified circuit, the anode
of the rectifier 52 would be connected directly to the point 53,
with the result that the output wave-form would appear as depicted
in FIG. 2a. In accordance with the invention however, the rectifier
anode is connected to the movable arm 54 of a rheostat 55 one end
56 of whose resistor is connected to the point 53, and the other
end 57 of which is unconnected or open. With the arm 54 full
counterclockwise at point 56, then the full-wave output of FIG. 2a
is obtained. With the arm 54 full clockwise at point 57, then, with
a sufficiently high resistance, say 50,000 ohms, the rectifier 52
is effectively open-circuited producing the half-wave voltage
depicted in FIG. 2c. With arm 54 in intermediate positions, then
waveforms similar to that of FIG. 2b are obtained, with the
amplitude of the smaller voltage 45 being controllable in a
continuous manner between the full level shown in FIG. 2a and the
zero level shown in FIG. 2c. This provides the practicing dentist
with a greater degree of control over the output power for most
efficient cutting, hemostasis or both. It is understood that the
rheostat 55 of FIG. 3 can be employed as a substitute for the
three-position switch 43 to provide the same advantages in a bridge
rectifier.
FIG. 4 shows a further modified power supply affording still
greater control of the output R.F. power. As in FIG. 1, a bridge
rectifier is depicted, the same numbers referencing the same
elements, except in this modification a three-ganged three-position
switch 60, 61, 62 is employed. The movable arm 63 of switch 60
connects the rectifier 41 to ground in two positions D and E, and
leaves it unconnected in the third position F. The switch 61 of the
three-ganged switch connects the power supply output lead 64 to a
filter capacitor in switch position D, and remains unconnected in
positions E and F. The switch 62, similarly to switch 61, connects
a lower voltage point from a voltage divider 65 via lead 66 to a
filter capacitor 67 in position D, and remains unconnected in
positions E and F.
The results on the D.C. output from the supply rectifier circuit is
depicted in FIG. 5. In position D, FIG. 5a, a normal full-wave
condensor filter rectification is obtained that is applied to the
tetrode plate 14, while similarly the voltage applied to the screen
13 of the tetrode is additionally filtered by capacitor 67,
providing a high degree of cutting action due to the continuous
R.F. power generation, as illustrated by the dashed waveforms. In
position E, FIG. 5b, a full-wave unfiltered rectified output is
obtained, similar to that of FIG. 2a. In position F, FIG. 5c,
half-wave unfiltered rectified output is obtained, similar to that
of FIG. 2c. Of course, this combination with filtering can also be
combined with the resistor 44 or rheostat 55 of FIGS. 1 and 3
respectively, providing additional possibilities of control over
the R.F. power output as desired by the dentist.
As before, the filtered fully rectified supply voltage will afford
the hottest current and cleanest cutting with minimal hemostasis
whereas the unfiltered half-wave rectified supply voltage will
afford poorer cutting but maximum coagulation, and the unfiltered
full-wave rectified supply voltage an inbetween condition.
In a typical example for the FIG. 1 embodiment, the plate voltage
will be, for example, 600 volts, the screen voltage about 300
volts, and the resistor 44 may be about 7,500 ohms.
While my invention has been described and illustrated in several
specific embodiments, it will be understood they are merely
exemplary, and that various changes and modifications may be made
in the circuitry disclosed without departing from the principles of
the invention herein described.
* * * * *