U.S. patent number 3,800,552 [Application Number 05/239,088] was granted by the patent office on 1974-04-02 for cryogenic surgical instrument.
This patent grant is currently assigned to The Bendix Corporation. Invention is credited to Thomas J. Bulat, Walter L. Dray, Blase J. Sollami.
United States Patent |
3,800,552 |
Sollami , et al. |
April 2, 1974 |
CRYOGENIC SURGICAL INSTRUMENT
Abstract
An apparatus for directly converting a gas into a liquid to
lower the temperature of a cryogenic surgical instrument. A tube
with a linear entrance and exit section is helically wound around a
core. A thermal conductive member surrounds the tube between the
entrance and exit sections. A gas under pressure is connected to
the entrance section of the tube. A sleeve with a closed end
frictionally engages and surrounds the thermal conductive member to
form a closed chamber adjacent the exit section of the tube. The
pressurized gas is throttled upon leaving the exit section causing
the temperature in the chamber to be lowered to between -80.degree.
to -250.degree. C causing the gas to liquefy. A path through the
thermal conductive member from the chamber to the atmosphere will
permit thermal energy in the throttled gas to be dissipated to the
pressurized gas in the tube. The liquefied gas in the chamber will
correspondingly cool the closed end of the sleeve allowing the
external surface thereof to be used as a cryogenic surgical
probe.
Inventors: |
Sollami; Blase J. (Davenport,
IA), Bulat; Thomas J. (Davenport, IA), Dray; Walter
L. (Davenport, IA) |
Assignee: |
The Bendix Corporation (South
Bend, IN)
|
Family
ID: |
22900552 |
Appl.
No.: |
05/239,088 |
Filed: |
March 29, 1972 |
Current U.S.
Class: |
62/293; 606/23;
62/51.1 |
Current CPC
Class: |
B22F
1/025 (20130101); A61B 18/02 (20130101); F25B
9/02 (20130101); F25J 1/0276 (20130101); A61B
2018/0287 (20130101) |
Current International
Class: |
A61B
18/00 (20060101); A61B 18/02 (20060101); F25B
9/02 (20060101); F25J 1/00 (20060101); F25b
019/00 () |
Field of
Search: |
;128/303.1
;62/293,514 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Perlin; Meyer
Attorney, Agent or Firm: McCormick, Jr.; Leo H. Antonis;
William N.
Claims
We claim:
1. An apparatus for directly converting a gas into a liquid for use
in cryosurgery, said apparatus comprising:
a cylindrical core having a front end and a rear end, said rear end
having a series of radial stops extending therefrom;
a tube helically wound around said core having an entrance section
which extends past said rear end and an exit section which extends
past said front end;
screen means secured to the front and rear ends of the cylindrical
core;
thermal conductive means surrounding said tube from said entrance
section to said exit section, said thermal conductive means
including granular particle means retained between said screen
means, said particle means contacting each other and said tube, a
source of gas under pressure connected to said entrance section of
said tube; and
sleeve means having a closed end and an open end frictionally
engaging and surrounding said thermal conductive means, said open
end abutting said radial stops to form a fixed volume chamber
between the exit section of the tube and the closed end, said gas
under pressure being throttled by passing through said exit section
into said fixed volume chamber, said throttled gas lowering the
temperature in said fixed volume chamber to between -80.degree. to
-250.degree.C by liquefying, said thermal conductive means
providing a flow path from said fixed volume chamber around said
tube and out said rear end, said flow path providing an escape
route for pressurized gas during said throttling, said flow path
from the fixed volume chamber being intercepted by the granular
particle means causing numerous deflections permitting the granular
particle means to absorb thermal energy from the pressurized gas
flowing along the path and to transfer this thermal energy to the
gas under pressure in the tube by conductions, said liquefied gas
conducting a corresponding temperature to said closed end for
permitting the external surface thereof to be used as a cryogenic
surgical instrument.
2. The apparatus, as recited in claim 1, wherein said exit section
of said tube includes:
regulator means responsive to the temperature of the liquefied gas
in fixed volume chamber for restricting the flow of the pressurized
gas.
3. The apparatus, as recited in claim 2, wherein said regulator
means includes:
a base attached to said exit section; and
a series of bimetal strips attached to said base, said bimetal
strips reacting to the temperature in the fixed volume chamber to
form an orifice through which the pressurized gas flows into the
fixed volume chamber.
4. The apparatus, as recited in claim 3, wherein said thermal
conductive means includes:
fin means attached to said tube to form a finned section thereon,
said finned section cooperating with the granular particle means to
said flow path.
5. The apparatus, as recited in claim 4, wherein the length of the
finned section as compared to the length of the helical tube is
adequate to dissipate sufficient thermal energy from said
pressurized gas to eliminate discomfort to an operator in contact
with the entrance section of said tube.
6. The apparatus, as recited in claim 5, wherein the external
surface of said sleeve means is covered with a thermal
non-conductive material to prevent outside thermal energy from
affecting dissipation of the internal thermal energy of said gas by
the conductive fins.
7. The apparatus, as recited in claim 1, wherein said source of
pressurized gas passes through a dryer to remove any moisture
therefrom which would adversely affect said throttling.
8. The apparatus, as recited in claim 2, wherein said source of gas
passes through a regulator to stabilize the pressure and flow of
said gas.
9. The apparatus, as recited in claim 8, wherein said apparatus
further includes:
a liquid absorption material located in said fixed volume chamber
to retain the liquefied gas in said fixed volume chamber and allow
unrestricted movement of said closed end without loss of said
liquefied gas through said path.
10. The apparatus, as recited in claim 9, wherein the size of the
fixed volume chamber and the exit section of the tube are mated to
provide effective throttling for the source of gas under pressure.
Description
BACKGROUND OF THE INVENTION
Cryogenic surgical instruments have been developed for use in
treating diseases wherein other methods would be detrimental to the
patient. These cryosurgical instruments usually have a tip or probe
which is cooled by a low boiling liquid. However, the storage
required for low boiling presents a problem to the mobility of the
surgical instrument.
Later a cryogenic device was developed wherein cooling of the probe
was achieved utilizing the Joule-Thomson effect wherein high
pressure gases cool upon expansion. With this device the probe
could be cooled to about -80.degree.C. At -80.degree.C upon
touching tissue with the probe, the moisture in the tissue is
turned into ice which adheres to the probe. In order to prevent the
probe from sticking to tissue, a heating means for instantaneously
raising the probe temperature evolved from necessity. Thus, the
operator could remove the probe without injury to the healthy
tissue. In experimentation where the probe had inadvertently
touched healthy tissue, cell destruction has been prevented by
immediately warming the end of the probe. However, the surface
cells still would be destroyed but in the body's internal repair
process of the damaged cells little or no scar tissue could be
observed. This was attributed in part to the dead cells which were
disposed of through the function of the body.
SUMMARY OF THE INVENTION
It was observed that if the temperature of the probe could be
maintained below -80.degree.C adherence of the tissue cells to the
probe could be averted. However, to achieve a mobile cryogenic
surgical unit without the problems associated with liquefied gases,
it was considered a necessity that the easily stored gas be
converted into a liquid upon demand. To directly convert a gas into
a liquid between -80.degree. to -250.degree.C we have devised an
appropriate cryogenic apparatus. In our apparatus a pressurized gas
is connected to a tube which is coiled around a cylindrical core. A
thermal conductive material in turn surrounds the tube and a sleeve
with a closed end frictionally secured to the conductive material.
The closed end of the sleeve and the end of the cylindrical core
form a chamber into which the end of the tube extends. Gas under
pressure is throttled into the chamber causing the temperature
therein to be lowered. A path through the thermal conductive
material will permit the throttled gas to escape to the atmosphere.
As the throttled gas goes through the thermal conductive material,
thermal energy is absorbed and transferred to the pressurized gas
in the tube to initially cool this gas before it is throttled in
the chamber. In this manner if nitrogen is used as the pressurized
gas, the initial throttling systematically reduces the temperature
of the pressurized nitrogen to the point where liquefication occurs
upon throttling. Once the liquefication has begun, the thermal
transfer by the conductive material maintains the overall
efficiency at an effective level.
It is therefore the object of this invention to provide a cryogenic
surgical apparatus with means to directly convert a gas to a liquid
between -80.degree. to -250.degree.C.
It is another object of this invention to provide a means of
initially cooling a gas under pressure by transferring thermal
energy produced by throttling to maintain a portion of the gas in
the chamber as a liquid.
It is another object of this invention to provide a cryogenic
surgical instrument with the means of liquefying different gases
corresponding to the required temperature needed to provide medical
treatment.
These and other objects will be apparent from reading this
specification and viewing the drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a diagrammatic view of a medical cryogenic system with an
enlarged sectional view showing a proposed surgical instrument
constructed in accordance with our invention.
FIG. 2 is a sectional view substantially along lines 2--2 of FIG. 1
showing the fluid supply tube surrounded by a thermal conductive
member.
FIG. 3 is a sectional view along lines 3--3 of FIG. 1 showing a top
view of the surgical instrument.
FIG. 4 is a sectional view of another surgical probe for use in the
medical cryogenic system of FIG. 1.
FIG. 5 is an enlarged sectional view of a bimetal strip regulator
for controlling cryogenic fluid flow through the surgical
instrument taken along lines 5--5 of FIG. 1.
FIG. 6 is a sectional view of a secondary embodiment of a finned
cryogenic supply conduit for the surgical instrument of FIG. 1.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT
The medical cryogenic system in FIG. 1 has a supply vessel 10
containing a suitable pressurized gas. The type of gas is chosen
for its liquefication temperature, which should be between
-80.degree. to -250.degree.C, for an example nitrogen gas, whose
liquefication temperature is -196.degree.C. A control valve 12 is
located in the outlet 14 of the supply vessel 10 to regulate flow
of the pressurized gas therefrom. A supply line 16 is connected to
gage 18 which will register the level of pressurized gas flowing
from the supply vessel 10 when the regulator is opened. The gage 18
in turn is connected to container 20 by conduit 22. The container
20 is filled with a chemical dryer, such as lithium oxide or a
molecular sieve where excessive moisture is removed from the
pressurized gas. The container 20 is connected to a surgical
instrument means 26 by a delivery line 24.
The surgical instrument means 26 consists of a cylindrical core 28
which has a front end 30 and a rear end 32. The front end 30 has a
shoulder 33 which extends from the cylindrical core 28. The rear
end 32 has a stepped shoulder 34 which extends from the cylindrical
core 28 with a first ledge 36 and a second ledge 38. A series of
radial fingers 40 extend from the second ledge 38. A central bore
42 in the rear end 32 is connected by a passageway 44 which
terminates between the first and second ledges 36 and 38,
respectively. A tube 46 has a linear entrance section 48 which
extends through passageway 44 into the central bore 42. The
entrance section 48 is sealed in the passageway 44 and the end 50
thereof centrally located in bore 42. A jacket member 52 having a
central passageway 56 with a slot 54 is placed around the end 50 of
tube 48 and between a rearward projection 58 surrounding the
central bore 42. A slight taper can be present in the external
surface of the jacket member 52 adjacent the end 60 of the jacket
member 52 so that a tight interference fit will be achieved between
the end 50 of the tube and the central passage when the end 60
contacts the bottom 62 of the central bore 42. An additional seal
57 located between jacket 52 and the rearward projection 58
provides a unitary structure capable of withstanding fluid
pressures delivered by the storage vessel 10 to the tube 46. The
other end 64 of the jacket member 52 retains a male connector 66
which engages a female connector 68 on the flexible delivery line
24.
Where the tube 46 emerges from the passageway 44 individually
attached fins such as discs or plates 102, see FIG. 6, or a
continuous helically wound fin 70 shown in FIG. 2 is secured to the
tube 46, until reaching a predetermined length. This finned tube 46
is now wound in a coil series around the cylindrical core 28. The
fin 70 extends to the shoulder 33 and an exit section 72 extends
past the end 30 of the cylindrical core 28. After the coil series
tube 46 is located around the cylindrical core 28, a resilient
barrier means 74 is alternately wound on the cylindrical core 28.
Sleeve means 76 having an opened end 78 and a closed end 80
surrounds the resilient barrier means 74. The resilient barrier
means being compressed between the cylindrical core 28 and the
internal surface 82 to frictionally retain the surface 84 of the
opened end 78 against the radial fingers 40. The radial fingers 40
provide a stop for establishing a fixed volume chamber 86 between
the front end of the cylindrical core 28 and the closed end 80.
MODE OF OPERATION OF THE PREFERRED EMBODIMENT
When a surgeon determines cryogenic surgery is necessary to relieve
an unwanted tissue condition, he turns the control valve 12 to an
open position. The pressure of the fluid (nitrogen for example)
flowing from the storage vessel 10 is registered on gage 18. The
fluid passes through the chemical drier 20 where any moisture
therein is removed. This fluid under pressure is transmitted
through the supply line 24 into the entrance section 48 of the tube
46. The fluid flows around the coil series and emerges from the
tube 46 through the orifice 98 of the exit section 72 into the
fixed volume chamber 86. The fluid which passes through the orifice
98 which has a smaller cross sectional area than the entrance
section 48, goes from a high pressure to a lower pressure. This
change in pressure is directly proportional to the area of orifice
98 as compared to the area of the fixed volume chamber 82. When the
pressurized gas passes from a high pressure area to a low pressure
area throttling occurs with a corresponding drop in the
temperature. The cooled gas can now travel around the tube 46 over
by the fins 70 in a path to the rear 32 of cylindrical core 28. The
fins being thermally conductive will absorb thermal energy from the
cooled gas and dissipate this thermal energy to the gas flowing
inside the tube 46. Thus, the gas in tube 46 is systematically and
sequentially reduced in temperature to a point where the
temperature in the fixed volume chamber 82 approaches -196.degree.C
if nitrogen is used. When -196.degree.C is reached, a portion of
the throttled gas is converted into a liquid. The liquid in turn
will uniformly distribute its temperature to the closed end 80 of
the sleeve means 76. The external surface 88 of the closed end 80
can now probe the damaged tissue and surgically destroy the
diseased part.
To maintain the liquid in the fixed volume chamber 86 in any
orientation, a liquid absorbing material 90 is placed in the fixed
volume chamber 86. With the liquid in the chamber being inhibited
from escaping by following the flow path around the tube 46, the
surgical instrument 26 can be used in any position the surgeon may
need. Since this instrument is designed to be hand held in order
that the temperature from the body does not affect the thermal
transfer between the throttled gas and the pressurized gas in the
tube 46, a non-thermal conductive material 92 is placed around the
opened end 78. Further, in order to protect the surgeon, the number
of fins around the tube as compared to the helically wound tube 46
around the cylindrical core are selected such that the dissipation
of thermal energy between the fixed volume chamber 86 and the gas
which passes between the finger 40 and surface 84 will not cause
discomfort to the hand of a surgeon if exposed to it over a period
of time.
In the embodiment shown in FIG. 4 like parts are numbered the same
as in FIG. 1. The tube 46 upon emerging from the passageway 44 is
helically wound around the cylindrical core 28. A screen 94 is
placed on shoulder 33 and granular particle means 98 poured into
the space 100 between surface 82 and the cylindrical core 28. The
conductive granular particles could be bronze coated with a brazing
alloy having a melting point below that of bronze, said conductive
granular particles being coated with a flux before placing in the
instrument.
When the cavity 100 is filled with this bronze coated flux, the
temperature is raised causing the flux to flow and securely bind
the particles together in a desired configuration. As the gas flows
from chamber 86, the flow paths available will be many since the
individual particles will block any direct flow to the exit 78. The
granular particles 98 will absorb the thermal energy developed by
throttling and dissipate the same to the gas flowing in tube 46 as
described with reference to FIG. 1.
The size of the fixed volume chamber 86 and the area of the exit
section 72 construction will vary with the particular gas used in
the supply chamber. However, as is apparent when nitrogen gas is
used, the possibility of fire or damage from breathing a pollutant
is greatly reduced. Moreover, in order to conserve the nitrogen
supply, a regulator 94 which is responsive to the liquefication
temperature in chamber 86 is attached to the opening on the exit
section 72. The regulator 94, see FIG. 5, has a series of bimetal
strips 96 attached to a base 98. The bimetal strips 96 form an
orifice 98 through which the pressurized gas flows into the fixed
volume chamber 86. As the pressurized gas is throttled, the bimetal
strips will contract to form an orifice as illustrated by numeral
100 when the liquefication of the gas has occurred. The bimetal
strips being sensitive to temperature change can contract and
expand as needed to maintain the temperature on the external
surface 88 within a preselected temperature range. Equally
appropriate regulators such as described in U. S. Pat. Nos.
3,517,525, 3,590,597, 3,630,047 and incorporated herein by
reference could be adapted to control the flow of the pressurized
gas. However, we have found that the bimetal strip regulator 94
adequately controls the flow of pressurized gas to maintain the
cryogenic surgical instrument 26 within the desired operating
range.
* * * * *