U.S. patent number 3,630,203 [Application Number 04/884,071] was granted by the patent office on 1971-12-28 for cryogenic biological apparatus.
This patent grant is currently assigned to Air Products and Chemicals, Inc.. Invention is credited to Robert B. Currie, Martin S. Sellinger, Henry F. Villaume.
United States Patent |
3,630,203 |
Sellinger , et al. |
December 28, 1971 |
CRYOGENIC BIOLOGICAL APPARATUS
Abstract
A spray-type cryogenic probe including a dual stream, cryogenic
liquifier for converting stored gas into an ultracold liquid which
is ejected from the probe in a fine, controlled stream to freeze
tissue.
Inventors: |
Sellinger; Martin S.
(Livingston, NJ), Currie; Robert B. (Bethlehem, PA),
Villaume; Henry F. (Intervale, NH) |
Assignee: |
Air Products and Chemicals,
Inc. (Allentown, PA)
|
Family
ID: |
25383890 |
Appl.
No.: |
04/884,071 |
Filed: |
December 11, 1969 |
Current U.S.
Class: |
606/24;
606/25 |
Current CPC
Class: |
A61B
18/0218 (20130101) |
Current International
Class: |
A61B
18/00 (20060101); A61B 18/02 (20060101); A61b
017/36 () |
Field of
Search: |
;128/303.1,400,401
;62/293,514 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Trapp; L. W.
Claims
Having described the invention in one preferred embodiment, what is
claimed is:
1. A cryogenic system for use in cryobiological applications
including, a source of high-pressure gas, a probe including a
nozzle for ejecting a stream of cryogenic fluid against tissue to
be frozen, and cooling means including a cryogenic heat exchanger
having a Joule Thompson expansion orifice intermediate said gas
source and said nozzle for cooling said gas to a cryogenic
temperature before ejection from said nozzle as said stream of
cryogenic fluid.
2. A cryogenic system for use in cryobiological applications
including, a source of high-pressure gas, a probe including a
nozzle for ejecting a stream of cryogenic fluid against tissue to
be frozen, cooling means intermediate said gas source and said
nozzle for cooling at least a portion of said gas to a cryogenic
temperature before ejection thereof from said nozzle as said stream
of cryogenic fluid, said cooling means including means for dividing
said high-pressure gas into first and second streams, means for
cooling said first stream, means for cooling said second stream in
heat exchange with said first stream, means for venting said first
stream after warming said first stream in heat exchange with said
second stream, and means connecting said second stream to said
nozzle for ejection therefrom as said stream of cryogenic
fluid.
3. The system as claimed in claim 2 wherein said means for cooling
said first stream comprises a first heat exchanger and a Joule
Thompson expansion orifice, and said means for cooling said second
stream comprises a second heat exchanger connected to said
nozzle.
4. The system as claimed in claim 3 wherein said first and second
heat exchangers comprise wound tubular coils in heat exchange
relationship with each other, and at least one of said coils is
composed of finned tubing.
5. A cryobiological probe for use in generating and directing a
cryogenic fluid against tissue comprising:
a. a hollow, elongated casing forming a handle having forward and
rearward portions,
b. a gas supply tube extending into said rearward portion,
c. means within said casing and connected to said supply tube for
dividing said gas into first and second streams,
d. means within said casing forming a first heat exchanger and a
Joule Thompson orifice for cooling said first stream,
e. means within said casing forming a second heat exchanger for
cooling said second stream in heat exchange with said first cooled
stream whereby said first stream is warmed and said second stream
is cooled to form a cryogenic fluid,
f. a nozzle located in the forward portion of said casing and
connected to said second heat exchanger for ejecting said second
stream as a jet of cryogenic fluid, and
g. means for exhausting said warmed first stream from said probe
after heat exchange with said second stream.
6. The cryobiological probe as claimed in claim 5 including means
forming a liquid chamber for collecting cryogenic liquid produced
by said Joule Thompson orifice, and means for passing said second
stream in heat exchange relationship with said cryogenic liquid so
as to at least partially liquefy the gas in said second stream.
7. The cryobiological probe as claimed in claim 6 wherein said
first heat exchanger comprises finned tubing helically wound about
a first mandrel, and a sleeve surrounding said finned tubing
forming said liquid chamber.
8. A method of freezing tissue comprising:
a. storing a gas at ambient temperature and at high pressure,
b. withdrawing a portion of said stored gas,
c. dividing said withdrawn gas into first and second streams,
d. cooling said first stream by Joule Thompson expansion and heat
exchange with itself to produce a first cryogenic fluid,
e. cooling said second stream to a cryogenic temperature in
exchange with said first stream so as to warm said first
stream,
f. exhausting said warmed first stream, and
g. ejecting a jet of said second stream at a cryogenic temperature
against said tissue to freeze said tissue.
9. The method as claimed in claim 8 wherein step (d) includes
cooling said first stream to its liquefaction temperature so as to
form a cryogenic liquid, and step (e) includes cooling said second
stream to its liquefaction temperature so as to liquefy
substantially all of said second stream to form a jet of cryogenic
liquid as it is ejected from said nozzle.
Description
BACKGROUND OF THE INVENTION
The present invention relates to the field of cryogenic biology
(cryobiology) and, more particularly, to a cryogenic system for
generating cryogenic liquid specifically for application in the
freezing of tissue such as, for example, skin tissue in
cryodermatology operations.
Prior methods of freezing tissue have included the direct
application of cryogenic liquids such as liquid argon and liquid
nitrogen to tissue. However, storage and transfer of cryogenic
liquids at temperatures in the order of minus 300.degree. F. have
presented many disadvantages. For example, the ultracold liquid
must be stored in relatively expensive cryogenic dewars, and a
significant portion of the liquid may vaporize during prolonged
storage. Even more importantly, the transfer line from the dewar to
the probe may become frosted and stiff at low temperatures such
that heat must be applied to the transfer line during the operation
in order to keep it flexible and frost-free Alternatively, some
prior devices have been designed wherein a gas is liquefied and
circulated entirely within a closed tip or "cold-finger." Such
systems require that the liquid be vaporized within the tip, and
the vapor is returned in countercurrent heat exchange with the
incoming gas to cool and condense it. While such closed cycle,
cold-tip probes solve the liquid problem, they are medically
disadvantageous in that the cold tip quickly accumulates frost
which substantially reduces the heat transfer rate between the tip
and the tissue. On the other hand, if the tip is kept frost-free,
the tissue tends to freeze to the tip such that free movement of
the tip is hindered, in addition to causing considerable discomfort
to the patient.
SUMMARY OF THE INVENTION
The present invention solves all of the above-indicated problems by
utilization of a unique, dual stream liquefier wherein gas from the
source is divided into first and second streams. The first stream
is passed through a heat exchanger and a Joule Thompson expansion
orifice whereby it is reduced in temperature to its liquefaction
point and liquefied. This first stream is passed in heat exchange
relationship with the second stream so as to liquefy the second
stream which is then ejected against the tissue in a fine,
controlled jet. The first stream is vaporized in liquefying the
second stream and is returned in countercurrent heat exchange with
the incoming first and second streams before being vented to
atmosphere at a relatively warm temperature.
Accordingly, it is a primary object of the present invention to
provide a cryogenic system for use in biological applications
wherein the refrigerant can be stored as an ambient temperature
gas, liquefied, and ejected as a controlled jet of ultracold
liquid.
It is a further object of the present invention to provide a
cryobiological probe including a dual stream liquefier whereby a
first portion of the stored gas refrigerant is liquefied and heat
exchanged against a second portion, such that, the first portion is
vented as a gas at relatively warm temperature, while the second
portion is ejected as a controlled jet of ultracold liquid or
gas.
BRIEF DESCRIPTION OF DRAWINGS
FIG. 1 is a schematic flow diagram of the complete cryobiological
system including the gas storage cylinder, the control unit, and
the probe; and
FIG. 2 is a cross-sectional view of the probe illustrating the
details of the dual-stream liquefier.
DETAILED DESCRIPTION
Referring first to FIG. 1, numeral 10 indicates a standard,
high-pressure cylinder in which a gas such as argon or nitrogen may
be stored in a compressed state such as a pressure of 3,000
p.s.i.a. The cylinder includes a standard cylinder valve 12 which
is manually opened and which is connected to a flexible line or
hose 14 for conducting the high-pressure gas into a control cabinet
16. Of course, it will be understood that the size of cabinet 16
has been greatly enlarged relative to the size of cylinder 10 so as
to facilitate the illustration of the control components contained
within the cabinet. In practice, the cabinet is sufficiently small
so as to be placed on a desk or table in close proximity to the
probe 18, whereas, the cabinet may be located at any distance from
the cylinder 10. Alternatively, line 14 may be provided with a
connector so as to be connected to a high-pressure gas piping
system.
Within cabinet 16, line 14 is connected to a pressure gauge 18
which indicates the operating pressure of the cylinder 10, or other
source of compressed gas. This gauge indicates that a sufficient
source pressure is available for operating the system. Line 14 is
also connected to a pressure reduction valve 20 which may be
manually variable, or may be set to operate at a predetermined
pressure reduction. By way of example, the cylinder 10 may be at a
pressure in the order of 3,000 p.s.i.a., whereas, the pressure
downstream of valve 20 may be in the order of 1,500 p.s.i.a.
The output side of valve 20 is connected to an adsorber 22 which is
provided to remove any impurities in the gas which may solidify and
thereby plug the very fine heat exchanger tubing which will be
subsequently described. Adsorber 22 may be filled with any
conventional adsorbent material such as charcoal, silica gel or
other material.
The output side of adsorber 22 is connected through a solenoid
valve 24 to a flexible line 26 leading to the probe 18. Solenoid
valve 24 is connected via electrical lines 27 to a plug 28 which
may be plugged into any standard electrical outlet. Lines 27
include an ON/OFF switch 29 closure of which actuates the solenoid
and opens the valve 24. An indicator light 30 is also connected in
parallel with the valve so as to indicate the open position of
valve 24, and hence, the operating condition of the system.
Reference is now made to FIG. 2 which illustrates the internal
details of probe 18. The probe includes a cylindrical casing 30
closed at the rearward end by a cap 32 and including casing
portions 34 and 36 which are disposed at an angle relative to the
longitudinal axis of cylinder 30. Axially disposed within the
casing 30 is an elongated, metallic sleeve 38 which is closed at
the rearward end by cap 32 and closed at the forward end by a plug
40. A second metallic sleeve or mandrel 42 is concentrically
positioned within sleeve 38 and is closed at opposite ends by plugs
44 and 46. Finned tubing 48 is helically wound on mandrel 42 so as
to form a heat exchanger coil 49 in direct engagement with both
mandrel 42 and the interior surface of sleeve 38. The forward end
of tubing 48 terminates in a reduced diameter tip portion 50
forming a Joule Thompson expansion orifice disposed within a
chamber 52. The opposite end of tubing 48 is secured in a fitting
54 which extends through cap 32.
Fitting 54 also includes a lateral port which receives the end of a
length of tubing 56 which is helically wound about the external
surface of cylinder 38 and forms a second heat exchanger coil 57.
Coil 57 terminates in an elongated nozzle portion 58 extending
slightly outwardly of casing portion 36 and is supported by a rod
60 having one end rigidly secured in plug 40. Fitting 54 further
includes a counterbored portion 62 which receives a plug of filter
material 64 and which receives the end of a stem 66 to which
flexible line 26 is connected by a suitable coupling 68.
A short length of tubing 70 is provided through cap 32 so as to
provide a vent from the interior of sleeve 38 to atmosphere.
Lastly, the space between sleeve 38 and casing 30 is filled with a
suitable thermal insulation 72 such as, for example, expanded
polyurethane foam.
OPERATION
The operation of the cryogenic biological system is as follows.
Assuming that cylinder valve 12 is open, the operator closes switch
29 which opens solenoid valve 24 and permits the passage of ambient
temperature gas through valve 20, adsorber 22, valve 24 and
flexible line 26 to probe 18. The gas passes through stem 66 and
filter plug 64 in fitting 54 wherein it is divided into a first
stream which flows through tubing 48, coil 49 and tip portion 50
forming a Joule Thompson expansion orifice whereby the gas is
rapidly expanded and cooled. As this first stream continues to flow
through coil 49 and the expansion orifice formed by the end of tip
50, the gas is precooled by the colder gas flowing countercurrently
from chamber 52 around coil 49 and through vent 70 to atmosphere.
Thus, the first gas stream is quickly cooled to its liquefaction
temperature and cryogenic liquid is formed in chamber 52. Since the
liquid in chamber 52, and the cold gas flowing countercurrently
around coil 49, are in heat exchange relationship with the second
gas stream passing through coil 57 around sleeve 38, the second gas
stream is also cooled and liquefied. Thus, as soon as the brief
cool-down period is completed, the second stream is ejected from
nozzle 58 as a fine, controlled jet of cryogenic liquid having a
temperature in the order of minus 320.degree. F., while the first
stream of gas is vented at a temperature of in the order of
60.degree. F.
From the foregoing description it will be apparent that by gripping
the handle provided by cylinder 30, the operator may direct the
fine stream or jet of ultracold liquid against the precise portion
of tissue which is to be frozen. In addition to having precise
control over the area which is to be treated by the fine jet, the
volume or rate of heat transfer may also be varied by presetting or
manually varying the pressure reduction occurring in valve 20. For
example, valve 20 may be set such as to produce a substantially
pure liquid jet or, if desired, the second stream may be ejected
from the nozzle 58 as a gas at a cryogenic temperature in the order
of minus 300.degree. F. which is slightly above the normal
liquefaction temperature of nitrogen, argon, air, etc. It will
therefore be apparent that the particular tissue area may be
selectively frozen without the disadvantages of maintaining a
continuous liquid reservoir, and without the problems incident to
the use of closed tip systems previously disclosed. That is, the
gas in the cylinder may be stored for extended periods of time with
no loss of refrigerant gas and the lines 14 and 26 present no
problems of frost accumulation or loss of flexibility since they
operate at ambient temperatures.
From the foregoing description of one preferred embodiment of the
invention, it will be readily apparent that numerous changes may be
made without departing from the scope of the invention. For
example, the tubing 56 forming coil 57 may be wound around mandrel
42 along with tubing 48 instead of being separately wound on the
outside of cylinder 38. In addition, it will be apparent that an
additional flow control valve may be utilized in line 26 in order
to control the volume of flow if desired. Lastly, the term
"cryogenic" as used hereinabove and in the following claims is
intended to denote temperatures lower than minus 200.degree. F.,
and the term "fluid" is intended to denote gas, liquid and mixed
gas-liquid streams at cryogenic temperatures.
* * * * *