US3865116A - Method of controlling tissue hypothermia - Google Patents

Method of controlling tissue hypothermia Download PDF

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US3865116A
US3865116A US349442A US34944273A US3865116A US 3865116 A US3865116 A US 3865116A US 349442 A US349442 A US 349442A US 34944273 A US34944273 A US 34944273A US 3865116 A US3865116 A US 3865116A
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thermoelectric device
flap
temperature
pedicle flap
pedicle
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Harold W Brooks
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F7/00Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F7/10Cooling bags, e.g. ice-bags
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F7/00Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F2007/0001Body part
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F7/00Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F7/007Heating or cooling appliances for medical or therapeutic treatment of the human body characterised by electric heating
    • A61F2007/0075Heating or cooling appliances for medical or therapeutic treatment of the human body characterised by electric heating using a Peltier element, e.g. near the spot to be heated or cooled
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F7/00Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F2007/0086Heating or cooling appliances for medical or therapeutic treatment of the human body with a thermostat

Definitions

  • ABSTRACT A pedicle flap is covered with a water-filled, latex rubher bag having a surface in contact with and substantially the same size, shape and outline as the pedicle flap, The cooling face of a thermoelectric device is placed in contact with the exposed surface of the bag.
  • a thermostatic control system including a temperature sensitive probe which is placed between the pedicle flap and the bag maintains the predetermined temperature in the range of l520C. Heat generated by the thermoelectric device is carried off by a coolant which flows through a coolant system including a heat exchanger and a pump in series with the thermoelectric device.
  • This invention relates to methods for inducing hypothermia in pedicle flaps and other types of tissue transplants.
  • a thermistor is utilized as a temperature sensitive probe in the vicinity of the copper disc but not in contact with the pedicle flap to operate a circuit-breaker which interrupts the power to a refrigerator unit associated with a coolant reservoir.
  • the other system involves the use of a dry ice reservoir which is placed in thermal communication with the pedicle flap to be cooled by a cool air column.
  • a thermistor which is placed a considerable distance from the pedicle flap is again utilized to actuate a circuit-breaker associated with a heating element in the cold air column.
  • the article fails to disclose the relative sizes, shapes and outlines of the pedicle flap and the copper disc on the one hand or the pedicle flap and the size of the cold air column on the other hand.
  • Thermoelectric devices were suggested for use in inducing local tissue hypothermia in an article entitled A Thermoelectric Device for Inducing Local Tissue Hypothermia and Hyperthermia, Nature, Vol. 203, pp. 6l3-6l4, Aug. 8, 1964, D. M. Makow and H. C. Grice.
  • the Makow and Grice system comprises a thermally conductive tissue holder which is placed in thermal communication with a thermoelectric device. However, the temperature is maintained by placing a thermister in thermal communication with the tissue holder but spaced from the tissue being cooled. The system is not adapted to cool transplanted tissue in situ.
  • a thermal transmission medium having one surface of substantially the same size and shape as the transplanted tissue to be cooled is placed in substantial contact with the entirety of the transplanted tissue without any substantial contact with the surrounding tissue.
  • the cooling face of a thermoelectric device is then placed in contact with an exposed surface of the thermal transmission medium to cool the transplanted tissue.
  • a temperature sensing device such as a thermistor is placed between the transplanted tissue and the thermal transmission medium and a signal representing the sensed temperature is applied to the input to the thermostatic control which maintains the temperature of the transplanted tissue within the selected l5-20 C. temperature range.
  • the thermal transmission. medium may comprise a flexible, liquid-filled bag.
  • the bag itself may be formed so as to have one surface of the proper size.
  • the bag may be formed from sheets of latex rubber which are adhesively sealed together over a substantial portion of the periphery thereof, filled with a liquid such as water, and then sealed shut.
  • the heat generated by the thermoelectric device is car ried off by a coolant circulating system.
  • the circulating system comprises a heat exchanger, a pump and a pres sure sensitive switch which is adapted to interrupt the supply of power to the thermoelectric device when a pressure drop in the collant circulating system is encountered, as when the pump fails or the coolant otherwise fails to circulate.
  • FIG. 1 illustrates an embodiment of the invention being utilized to cool a pedicle flap in a laboratory animal
  • FIG. 2 is an enlarged perspective view of the pedicle flap being cooled in FIG. 1 and the cooling mechanism in contact therewith;
  • FIGS. 3 (a-f) are simplified perspective views illustrating various steps in the formation of a water-filled bag which serves as the thermal transmission medium between the pedicle flap of FIG. 2 and a thermoelectric cooling device;
  • FIG. 4 is a schematic diagram of the electrical circuitry in a preferred embodiment of the invention.
  • FIG. 5 is a schematic diagram of the hydraulic system in a preferred embodiment of the invention.
  • thermoelectric cooling device 10 is being uti-' lized to cool the pedicle flap of a laboratory rabbit 12 through a thermal transmission medium comprising a water-filled, latex rubber bag 14. Since the pedicle flap must be cooled over an extended period of time, the rabbit 12 is held in a substantially stationary position by a restraining box 16. Electrical lead lines 18 from temperature sensing and control devices, e.g., thermisters, and electrical-hydraulic umbilical lines 20 from the thermoelectric device 10 extend through an opening 21 in the restraining box 16. As shown in FIG. 2, the thermisters 2282 a-c are connected to the electrical leads 18.
  • the water-filled rubber bag 14 has a cooling surface 23 in contact with the pedicle flap 24 which is of substantially the same size, shape and outline as the pedicle flap 24.
  • a cooling face 26 of the thermoelectric device 12 which is in contact with exposed surface 27v of the bag 14 is able to cool the pedicle flap 24 alone without any substantial cooling of the surrounding tissue. This has been found to be critical if high flap viability is to be obtained.
  • the temperature ofthe pedicle flap 24 is precisely controlled to maximize the viability of the pedicle flap.
  • the thermister 22a is located between and in contact with the flap 24 as well as the bag 14.
  • the temperature of the pedicle flap 24 may be maintained with a good deal of precision at a preset temperature level in the range of l-20 C. Temperature at the distal end of the flap stayed, for the most part, within l2 C. of the pre-set temperature. Temperatures taken at the sides of the flap (anteriorly and posteriorly) were at times warmer than the pre-set temperature but all peripheral parts of the flap were always at least 5-l5 C. (generally C.) cooler than the surrounding normal skin temperatures. Temperatures of the surrounding tissue, as monitored by the thermistor 22c, remained within 5 of normal skin temperature. The precision in temperature control is attributed to the configuration of the bag 14 as well as the precise temperature control afforded by the thermoelectric device. In addition, it is believed that the thermal inertia provided by the liquid medium in the water-filled bag which is separate and apart from any circulating coolant is of great assistance in maintaining the proper pedicle flap temperature.
  • the heat generated at the hot side 30 of the thermoelectric device 10 is carried away from the pedicle flap 24 by a coolant such as water which is circulated to and from the hot side 30 of the thermoelectric device 10 by means of the umbilical lines 20.
  • a coolant such as water which is circulated to and from the hot side 30 of the thermoelectric device 10 by means of the umbilical lines 20.
  • FIGS. 3af a preferred method of forming a water-filled bag having a cooling surface of the appropriate size, shape and outline will now be described.
  • a sheet 40 of latex rubber or other water impervious material is being cut to form two circular segments 42.
  • the segments 42 which may be first traced on to the sheet 40 using a template are of the same shape and slightly larger size than the pedicle flap to be cooled where the dotted circular lines correspond to the size of the pedicle flap.
  • a scalpel 44 or other suitable cutting means may be utilized to cut the segments 42 from the sheet 40.
  • a rubber or dermatome cement is being applied from a tube 46 to a substantial portion of the peripheries 48 of the segments 42. Note however that a portion 50 of the periphery of each of the segments 42 does not receive the cement.
  • the peripheries 48 of the segments 42 are being secured to one another by sandwiching the segments 42 between a surface 52 and a weight 54.
  • water may be applied through a hose 56 or other suitable means, to an opening formed at peripheral portions 50 of the segments 42 as shown in FIG. 3d.
  • the peripheral portions may be sealed shut utilizing cement from the tube 46 as shown in FIG. 3e and then brought into bonding relation by a clamp 58 shown in FIG. 3f to incapsulate the-water in the bag 14.
  • thermoelectric device 10 is supplied by a power pack 60 (This is a simple, open chasis, center tap transformer-choke-l2 automotive-type diode package with approximately l5 percent ripple at design output) which is supplied by a 110 volt AC force 62 in series with a variable transformer 64.
  • a power switch 66 controls the application of the l 10 volts to the power pack 60.
  • a thermostatic control 68 such as the Yellow Springs Instrument Temperature Controller, Model 73 or similar controlling unit is connected in series with the thermoelectric device 10 in response to the temperature being sensed by the thermister probe 22a.
  • thermoelectric device 10 In order to circulate the coolant through the thermoelectric device 10, a pump is also connected across the 110 volt source 62.
  • a pressure switch 72 which is responsive to the pressure of the coolant being pumped by the pump 70 is connected to relay 74 having a coil 76.
  • relay 74 having a coil 76.
  • a movable contact bar 78 is in contact with contact points 80 to provide power from the power pack 60 to the temperature controller 68 and the thermoelectric device 10.
  • the contact between the bar 78 and the point 80 is broken and contact between a coolant bar 82 and contact points 84 is established so as to apply power from the source 62 to an indicating light 86 or other suitable alarm means while interrupting power to the thermoelectric device 10.
  • the light 86 When the light 86 is on, it may indicate a pump failure which would result in an increase in the temperature at the cooling face 26 of the thermoelectric device 10 and a resulting, potentially harmful rise in the temperature of the pedicle flap 24.
  • a fan 88 is also connected across the source 62.
  • the fan circulates the air across the vanes of the heat exchanger. It also assures proper cooling of the electrical components in the system.
  • An on/off light 89 is also provided across the source 62 so as to indicate when the power switch 66 is closed. Fuses 90 are provided in series with the power switch 66, the pump 70, the fan 88 and the power pack 60.
  • a volt meter 91 is provided across the output terminals of the power pack 60 to permit the monitoring of the input voltage to the thermoelectric device 10.
  • the coolant is circulated through the thermoelectric device 10 to carry away the heat from the hot face thereof. As shown in FIG. 5, the coolant is circulated by the pump 70 through the pressure switch 72 and into and out of the thermoelectric device 10. Coolant then flows to a heat exchanger 92 and into a coolant reservoir 94.
  • the coolant may comprise water or other suitable liquid coolants.
  • thermoelectric device embraces any and all devices which utilize the Peltier Effect involving the generation of or obstruction of heat (depending upon the direction of current) at a rate Q, at the junction between two different semiconductors when a current I flows through the semiconductors.
  • the rate Q equals ll X l where II is the Peltier coefficient which is a function of semiconductor conductivities.
  • thermoelectric device is the model no. CP 1.4-71-06 manufactured by the Melcor Corporation, 990 Spruce Street, Trenton, N..]. This device has a cooling face of 1.17 square inches which is capable of-i02 BTUs per hour with a maximum current of 6 amps.
  • the device includes a coolant circulating path associated with the warm face of the device.
  • This particular size thermoelectric device is particularly suitable for use with a pedicle flap of 3+ square inches.
  • a method of cooling a pedicle flap or graft in situ comprising:
  • thermal transmission medium having one surface of substantially the same size, shape and outline as the pedicle flap or graft to be cooled; placing said one surface of said thermal transmission medium in substantial contact with the entirety of i the pedicle flap or graft;
  • thermoelectric device holding the cooling face of a thermoelectric device in contact with an exposed surface of the thermal transmission medium; maintaining a temperature sensing device in position between the pedicle flap or graft and said one surface of said thermal transmission medium;
  • thermoelectric device thermostatically controlling the temperature of the cooling face of the thermoelectric device between the pedicle flap or graft and said thermal transmission medium so as to maintain the temperature of a substantial portion of the pedicle flap or graft at l5-20 C.
  • thermoelectric device cooling face is equal to at least 10 percent of the pedicle flap or graft to be cooled.
  • thermoelectric device 4. The method of claim 1 including the step of circulating coolant to and from said thermoelectric device so as to carry away heat generated thereby.

Abstract

A pedicle flap is covered with a water-filled, latex rubber bag having a surface in contact with and substantially the same size, shape and outline as the pedicle flap. The cooling face of a thermoelectric device is placed in contact with the exposed surface of the bag. A thermostatic control system including a temperature sensitive probe which is placed between the pedicle flap and the bag maintains the predetermined temperature in the range of 15*-20*C. Heat generated by the thermoelectric device is carried off by a coolant which flows through a coolant system including a heat exchanger and a pump in series with the thermoelectric device.

Description

atet 1 llttite States roolts [4 1 Feb. 1t, 1975 1 1 METHOD OF CONTROLLING TISSUE HYPOTHERMM [76] Inventor: Harold W. Brooks, RD. 4, Danville,
[22] Filed: Apr. 9, 1973 [21] Appl. No.1 349,442
[52} U.S. C1. 128/400 [51] int. Cl. A6lf 7/00 [58] Field of Search 128/399, 400, 303.1, 401, 128/402 VI 56] References Cited UNITED STATES PATENTS 2,260,134 10/1941 Ballman 128/400 2,726,658 12/1955 Chessey 3,738,372 6/1973 Shioshvili 128/400 Primary Examiner-Lawrence W. Trapp Attorney, Agent, or Firm-Woodcock, Washburn, Kurtz & Mackiewicz [57] ABSTRACT A pedicle flap is covered with a water-filled, latex rubher bag having a surface in contact with and substantially the same size, shape and outline as the pedicle flap, The cooling face of a thermoelectric device is placed in contact with the exposed surface of the bag. A thermostatic control system including a temperature sensitive probe which is placed between the pedicle flap and the bag maintains the predetermined temperature in the range of l520C. Heat generated by the thermoelectric device is carried off by a coolant which flows through a coolant system including a heat exchanger and a pump in series with the thermoelectric device.
4 Claims, 10 Drawing Figures PATENTED FEB] 1 I975 SHEET 2 BF 3 HEAT EXCHANGER PR URE S CH THERMO- ELECTRIC v UNIT PATENTEBFEBT 1 I915 3.865.116
SHEET 3 0F 3 L1 HOV L2 PRESSURE /72 TEMPERATURE 2 SWITCH CONTROLLER THERMO- ELECTRIC UNIT POWER PACK /60 INPUT 3 VARIABLE 2* TRANSFORMER 9o Fig. 4
METHOD OF CONTROLLING TISSUE HYPOTHERMIA BACKGROUND OF THE INVENTION This invention relates to methods for inducing hypothermia in pedicle flaps and other types of tissue transplants.
The effect of moderate cold on living tissues and the healing of wounds has been studied and chronicled for centuries. C. L. Kiehn and J. D. Desprez, in an article entitled Effects of Local Hypothermia on Pedicle Flap Tissue, Journal of Plastic and Reconstructive Surgery, Vol. 4, 1960, described studies involving the cooling of experimental animal pedicle flaps to a temperature of l-20 C. Two different systems for achieving pedicle flap cooling are disclosed in the article. One of the systems relies upon the circulation of a coolant through a copper disc which is maintained in contact with the pedicle being cooled. A thermistor is utilized as a temperature sensitive probe in the vicinity of the copper disc but not in contact with the pedicle flap to operate a circuit-breaker which interrupts the power to a refrigerator unit associated with a coolant reservoir. The other system involves the use of a dry ice reservoir which is placed in thermal communication with the pedicle flap to be cooled by a cool air column. In order to control the temperature, a thermistor which is placed a considerable distance from the pedicle flap is again utilized to actuate a circuit-breaker associated with a heating element in the cold air column. The article fails to disclose the relative sizes, shapes and outlines of the pedicle flap and the copper disc on the one hand or the pedicle flap and the size of the cold air column on the other hand. Although beneficial effects of the hypothermia created by the systems in this article are beyond question, the systems themselves are too cumbersome, impractical and inexact for clinical use.
Thermoelectric devices were suggested for use in inducing local tissue hypothermia in an article entitled A Thermoelectric Device for Inducing Local Tissue Hypothermia and Hyperthermia, Nature, Vol. 203, pp. 6l3-6l4, Aug. 8, 1964, D. M. Makow and H. C. Grice. The Makow and Grice system comprises a thermally conductive tissue holder which is placed in thermal communication with a thermoelectric device. However, the temperature is maintained by placing a thermister in thermal communication with the tissue holder but spaced from the tissue being cooled. The system is not adapted to cool transplanted tissue in situ.
SUMMARY OF THE INVENTION It is an object of this invention to provide a practical clinical method for inducing transplanted tissue hypothermia in situ.
It is also an object of this invention to provide a method which is capable of precisely maintaining the optimum temperature at the tissue.
It is a further specific object of this invention to maximize the benefits to be derived from tissue hypothermia.
In accordance with these and other objects of the invention, a thermal transmission medium having one surface of substantially the same size and shape as the transplanted tissue to be cooled is placed in substantial contact with the entirety of the transplanted tissue without any substantial contact with the surrounding tissue. The cooling face of a thermoelectric device is then placed in contact with an exposed surface of the thermal transmission medium to cool the transplanted tissue. A temperature sensing device such as a thermistor is placed between the transplanted tissue and the thermal transmission medium and a signal representing the sensed temperature is applied to the input to the thermostatic control which maintains the temperature of the transplanted tissue within the selected l5-20 C. temperature range.
In accordance with one important aspect of the invention, the thermal transmission. medium may comprise a flexible, liquid-filled bag. The bag itself may be formed so as to have one surface of the proper size.
'shape and outline so as to conform with the trans planted tissue to be cooled. In this connection, the bag may be formed from sheets of latex rubber which are adhesively sealed together over a substantial portion of the periphery thereof, filled with a liquid such as water, and then sealed shut.
In accordance with another object of the invention, the heat generated by the thermoelectric device is car ried off by a coolant circulating system. The circulating system comprises a heat exchanger, a pump and a pres sure sensitive switch which is adapted to interrupt the supply of power to the thermoelectric device when a pressure drop in the collant circulating system is encountered, as when the pump fails or the coolant otherwise fails to circulate.
BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 illustrates an embodiment of the invention being utilized to cool a pedicle flap in a laboratory animal;
FIG. 2 is an enlarged perspective view of the pedicle flap being cooled in FIG. 1 and the cooling mechanism in contact therewith;
FIGS. 3 (a-f) are simplified perspective views illustrating various steps in the formation of a water-filled bag which serves as the thermal transmission medium between the pedicle flap of FIG. 2 and a thermoelectric cooling device;
FIG. 4 is a schematic diagram of the electrical circuitry in a preferred embodiment of the invention; and
FIG. 5 is a schematic diagram of the hydraulic system in a preferred embodiment of the invention.
DETAILED DESCRIPTION OF A PREFERRED EMBODIMENT In accordance with this invention and as depicted in FIG. 1, a thermoelectric cooling device 10 is being uti-' lized to cool the pedicle flap of a laboratory rabbit 12 through a thermal transmission medium comprising a water-filled, latex rubber bag 14. Since the pedicle flap must be cooled over an extended period of time, the rabbit 12 is held in a substantially stationary position by a restraining box 16. Electrical lead lines 18 from temperature sensing and control devices, e.g., thermisters, and electrical-hydraulic umbilical lines 20 from the thermoelectric device 10 extend through an opening 21 in the restraining box 16. As shown in FIG. 2, the thermisters 2282 a-c are connected to the electrical leads 18.
In accordance with one very important aspect of the invention shown in FIG. 2, the water-filled rubber bag 14 has a cooling surface 23 in contact with the pedicle flap 24 which is of substantially the same size, shape and outline as the pedicle flap 24. By providing such a cooling surface 23 on the rubber bag 14, a cooling face 26 of the thermoelectric device 12 which is in contact with exposed surface 27v of the bag 14 is able to cool the pedicle flap 24 alone without any substantial cooling of the surrounding tissue. This has been found to be critical if high flap viability is to be obtained.
In accordance with another important aspect of the invention, the temperature ofthe pedicle flap 24 is precisely controlled to maximize the viability of the pedicle flap. In this connection, the thermister 22a is located between and in contact with the flap 24 as well as the bag 14.
It has been found that the temperature of the pedicle flap 24 may be maintained with a good deal of precision at a preset temperature level in the range of l-20 C. Temperature at the distal end of the flap stayed, for the most part, within l2 C. of the pre-set temperature. Temperatures taken at the sides of the flap (anteriorly and posteriorly) were at times warmer than the pre-set temperature but all peripheral parts of the flap were always at least 5-l5 C. (generally C.) cooler than the surrounding normal skin temperatures. Temperatures of the surrounding tissue, as monitored by the thermistor 22c, remained within 5 of normal skin temperature. The precision in temperature control is attributed to the configuration of the bag 14 as well as the precise temperature control afforded by the thermoelectric device. In addition, it is believed that the thermal inertia provided by the liquid medium in the water-filled bag which is separate and apart from any circulating coolant is of great assistance in maintaining the proper pedicle flap temperature.
In accordance with another important aspect of the invention, the heat generated at the hot side 30 of the thermoelectric device 10 is carried away from the pedicle flap 24 by a coolant such as water which is circulated to and from the hot side 30 of the thermoelectric device 10 by means of the umbilical lines 20. This removal of heat from the thermoelectric 26 which is in close proximity to the patient permits the necessary cool temperatures at the pedicle flap 24 to be maintained as well as eliminating any discomfort to the patient due to the heating at the hot side 30. The nature of the coolant circulating system including the umbilical lines will be described in somewhat further detail with reference to FIG. 5.
Referring now to FIGS. 3af, a preferred method of forming a water-filled bag having a cooling surface of the appropriate size, shape and outline will now be described. As shown in FIG. 3a, a sheet 40 of latex rubber or other water impervious material is being cut to form two circular segments 42. Note that the segments 42 which may be first traced on to the sheet 40 using a template are of the same shape and slightly larger size than the pedicle flap to be cooled where the dotted circular lines correspond to the size of the pedicle flap. A scalpel 44 or other suitable cutting means may be utilized to cut the segments 42 from the sheet 40.
In FIG. 3b, a rubber or dermatome cement is being applied from a tube 46 to a substantial portion of the peripheries 48 of the segments 42. Note however that a portion 50 of the periphery of each of the segments 42 does not receive the cement. In FIG. 30, the peripheries 48 of the segments 42 are being secured to one another by sandwiching the segments 42 between a surface 52 and a weight 54. After a suitable length of time to assure a good bond along the peripheries 48 of the segments 42, water may be applied through a hose 56 or other suitable means, to an opening formed at peripheral portions 50 of the segments 42 as shown in FIG. 3d. Once the segments 42 are filled with water, the peripheral portions may be sealed shut utilizing cement from the tube 46 as shown in FIG. 3e and then brought into bonding relation by a clamp 58 shown in FIG. 3f to incapsulate the-water in the bag 14.
In the electrical schematic diagram of FIG. 4, the thermoelectric device 10 is supplied by a power pack 60 (This is a simple, open chasis, center tap transformer-choke-l2 automotive-type diode package with approximately l5 percent ripple at design output) which is supplied by a 110 volt AC force 62 in series with a variable transformer 64. A power switch 66 controls the application of the l 10 volts to the power pack 60.
A thermostatic control 68 such as the Yellow Springs Instrument Temperature Controller, Model 73 or similar controlling unit is connected in series with the thermoelectric device 10 in response to the temperature being sensed by the thermister probe 22a.
In order to circulate the coolant through the thermoelectric device 10, a pump is also connected across the 110 volt source 62. A pressure switch 72, which is responsive to the pressure of the coolant being pumped by the pump 70 is connected to relay 74 having a coil 76. When the pressure sensed by the switch 72 is at or above a predetermined leve, a movable contact bar 78 is in contact with contact points 80 to provide power from the power pack 60 to the temperature controller 68 and the thermoelectric device 10. However, when the pressure sensed by the switch 72 drops below a predetermined level, the contact between the bar 78 and the point 80 is broken and contact between a coolant bar 82 and contact points 84 is established so as to apply power from the source 62 to an indicating light 86 or other suitable alarm means while interrupting power to the thermoelectric device 10. When the light 86 is on, it may indicate a pump failure which would result in an increase in the temperature at the cooling face 26 of the thermoelectric device 10 and a resulting, potentially harmful rise in the temperature of the pedicle flap 24.
A fan 88 is also connected across the source 62. The fan circulates the air across the vanes of the heat exchanger. It also assures proper cooling of the electrical components in the system. An on/off light 89 is also provided across the source 62 so as to indicate when the power switch 66 is closed. Fuses 90 are provided in series with the power switch 66, the pump 70, the fan 88 and the power pack 60. A volt meter 91 is provided across the output terminals of the power pack 60 to permit the monitoring of the input voltage to the thermoelectric device 10.
As mentioned previously, the coolant is circulated through the thermoelectric device 10 to carry away the heat from the hot face thereof. As shown in FIG. 5, the coolant is circulated by the pump 70 through the pressure switch 72 and into and out of the thermoelectric device 10. Coolant then flows to a heat exchanger 92 and into a coolant reservoir 94. The coolant may comprise water or other suitable liquid coolants.
Various thermoelectric devices may be utilized in this system. As utilized herein, the term thermoelectric device" embraces any and all devices which utilize the Peltier Effect involving the generation of or obstruction of heat (depending upon the direction of current) at a rate Q, at the junction between two different semiconductors when a current I flows through the semiconductors. The rate Q equals ll X l where II is the Peltier coefficient which is a function of semiconductor conductivities.
One particularly satisfactory thermoelectric device is the model no. CP 1.4-71-06 manufactured by the Melcor Corporation, 990 Spruce Street, Trenton, N..]. This device has a cooling face of 1.17 square inches which is capable of-i02 BTUs per hour with a maximum current of 6 amps. The device includes a coolant circulating path associated with the warm face of the device. This particular size thermoelectric device is particularly suitable for use with a pedicle flap of 3+ square inches. In general, it is desirable and preferred to utilize a thermoelectric device having a cooling face with area which is equal to at least 10 percent of the pedicle flap area and preferably 33 percent or more. This of course means that the thermoelectric device cooling face is equal to at least 10 percent and preferably 33 percent or more of the cooling surface of the rubber, wateriilled bag in contact with the pedicle flap.
Experiments conducted on pedicle flaps which were not cooled and those which were cooled with the previously described system of this invention indicate that the latter have greatly improved chances of survival as compared with the former. Without cooling, slough of the uncooled flaps was evident by the end of the first day and well-established by the end of the third day. In contrast, the flaps which were cooled with the system of this invention were for the most part healthy afer 7 days. Without cooling, the estimated survival of viability of the flaps was percent as compared with 643 percent for the flaps cooled in accordance with this invention. The survival or viability of the flaps cooled with the invention would have been higher except for the loss of one flap. If it were not for the loss of this one flap, final estimates of viability would have increased 75 percent in the cooled flaps. It has also been found that the viability of the flaps is dramatically reduced if the surrounding tissue is cooled or the temperature of the tissue is allowed to fluctuate as by spacing the control thermister from the tissue to be cooled.
Although the system has been described in conjunction with the cooling of pedicle flaps, it is understood that it is equally applicable to the cooling of grafts and other tissue transplants in situ also. Even though a particular embodiment of the invention has been shown and described in detail, it will be understood that various modifications will occur to those of ordinary skill in the art which fall within the true spirit and scope of the invention as set forth in the appended claims.
What is claimed is:
l. A method of cooling a pedicle flap or graft in situ comprising:
forming a thermal transmission medium having one surface of substantially the same size, shape and outline as the pedicle flap or graft to be cooled; placing said one surface of said thermal transmission medium in substantial contact with the entirety of i the pedicle flap or graft;
holding the cooling face ofa thermoelectric device in contact with an exposed surface of the thermal transmission medium; maintaining a temperature sensing device in position between the pedicle flap or graft and said one surface of said thermal transmission medium; and
thermostatically controlling the temperature of the cooling face of the thermoelectric device between the pedicle flap or graft and said thermal transmission medium so as to maintain the temperature of a substantial portion of the pedicle flap or graft at l5-20 C.
2. The method of claim 1 wherein the temperature of the pedicle flap or graft is maintained within 2 C. of a preset temperature in the range of l5-20 C. over a substantial portion thereof.
3. The method of claim 1 wherein the area of the thermoelectric device cooling face: is equal to at least 10 percent of the pedicle flap or graft to be cooled.
4. The method of claim 1 including the step of circulating coolant to and from said thermoelectric device so as to carry away heat generated thereby.

Claims (4)

1. A method of cooling a pedicle flap or graft in situ comprising: forming a thermal transmission medium having one surface of substantially the same size, shape and outline as the pedicle flap or graft to be cooled; placing said one surface of said thermal transmission medium in substantial contact with the entirety of the pedicle flap or graft; holding the cooling face of a thermoelectric device in contact with an exposed surface of the thermal transmission medium; maintaining a temperature sensing device in position between the pedicle flap or graft and said one surface of said thermal transmission medium; and thermostatically controlling the temperature of the cooling face of the thermoelectric device between the pedicle flap or graft and said thermal transmission medium so as to maintain the temperature of a substantial portion of the pedicle flap or graft at 15*-20* C.
2. The method of claim 1 wherein the temperature of the pedicle flap or graft is maintained within 2* C. of a preset temperature in the range of 15*-20* C. over a substantial portion thereof.
3. The method of claim 1 wherein the area of the thermoelectric device cooling face is equal to at least 10 percent of the pedicle flap or graft to be cooled.
4. The method of claim 1 including the step of circulating coolant to and from said thermoelectric device so as to carry away heat generated thereby.
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Cited By (47)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3122617A1 (en) * 1980-06-16 1982-04-08 The Kendall Co., Walpole, Mass. DEVICE FOR THERAPEUTIC COLD TREATMENT OF A PATIENT
US4335726A (en) * 1980-07-11 1982-06-22 The Kendall Company Therapeutic device with temperature and pressure control
US4846176A (en) * 1987-02-24 1989-07-11 Golden Theodore A Thermal bandage
EP0342676A2 (en) * 1988-05-20 1989-11-23 Temperature Research Corporation Apparatus for localized heat and cold therapy
WO1994000086A1 (en) * 1992-06-26 1994-01-06 Horn Stuart B Temperature controlled body pads
US6096068A (en) * 1998-01-23 2000-08-01 Innercool Therapies, Inc. Selective organ cooling catheter and method of using the same
US6149677A (en) * 1998-03-31 2000-11-21 Innercool Therapies, Inc. Circulating fluid hypothermia method
US6224624B1 (en) 1998-03-24 2001-05-01 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US6235048B1 (en) 1998-01-23 2001-05-22 Innercool Therapies, Inc. Selective organ hypothermia method and apparatus
US6238428B1 (en) 1998-01-23 2001-05-29 Innercool Therapies, Inc. Selective organ cooling apparatus and method employing turbulence-inducing element with curved terminations
US6245095B1 (en) 1998-03-24 2001-06-12 Innercool Therapies, Inc. Method and apparatus for location and temperature specific drug action such as thrombolysis
US6251129B1 (en) 1998-03-24 2001-06-26 Innercool Therapies, Inc. Method for low temperature thrombolysis and low temperature thrombolytic agent with selective organ temperature control
US6251130B1 (en) 1998-03-24 2001-06-26 Innercool Therapies, Inc. Device for applications of selective organ cooling
US6254626B1 (en) 1998-03-24 2001-07-03 Innercool Therapies, Inc. Articulation device for selective organ cooling apparatus
US6261312B1 (en) 1998-06-23 2001-07-17 Innercool Therapies, Inc. Inflatable catheter for selective organ heating and cooling and method of using the same
US6312452B1 (en) 1998-01-23 2001-11-06 Innercool Therapies, Inc. Selective organ cooling catheter with guidewire apparatus and temperature-monitoring device
US6325818B1 (en) 1999-10-07 2001-12-04 Innercool Therapies, Inc. Inflatable cooling apparatus for selective organ hypothermia
US6379378B1 (en) 2000-03-03 2002-04-30 Innercool Therapies, Inc. Lumen design for catheter
US6464716B1 (en) 1998-01-23 2002-10-15 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US6471717B1 (en) 1998-03-24 2002-10-29 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US6491039B1 (en) 1998-01-23 2002-12-10 Innercool Therapies, Inc. Medical procedure
US6491716B2 (en) 1998-03-24 2002-12-10 Innercool Therapies, Inc. Method and device for applications of selective organ cooling
US20030023288A1 (en) * 1999-02-09 2003-01-30 Michael Magers Method and device for patient temperature control employing optimized rewarming
US20030060863A1 (en) * 1999-02-09 2003-03-27 Dobak John D. Method and apparatus for patient temperature control employing administration of anti-shivering agents
US6551349B2 (en) 1998-03-24 2003-04-22 Innercool Therapies, Inc. Selective organ cooling apparatus
US20030078641A1 (en) * 1998-01-23 2003-04-24 Innercool Therapies, Inc. Selective organ hypothermia method and apparatus
US6576002B2 (en) 1998-03-24 2003-06-10 Innercool Therapies, Inc. Isolated selective organ cooling method and apparatus
US6585752B2 (en) 1998-06-23 2003-07-01 Innercool Therapies, Inc. Fever regulation method and apparatus
US6599312B2 (en) 1998-03-24 2003-07-29 Innercool Therapies, Inc. Isolated selective organ cooling apparatus
US6602276B2 (en) 1998-03-31 2003-08-05 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation
US6660028B2 (en) 2000-06-02 2003-12-09 Innercool Therapies, Inc. Method for determining the effective thermal mass of a body or organ using a cooling catheter
US6685732B2 (en) 1998-03-31 2004-02-03 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing microporous balloon
US6719779B2 (en) 2000-11-07 2004-04-13 Innercool Therapies, Inc. Circulation set for temperature-controlled catheter and method of using the same
US6726708B2 (en) 2000-06-14 2004-04-27 Innercool Therapies, Inc. Therapeutic heating and cooling via temperature management of a colon-inserted balloon
US20040199230A1 (en) * 2003-02-24 2004-10-07 Yon Steve A. System and method for inducing hypothermia with control and determination of catheter pressure
US20040267250A1 (en) * 1998-03-31 2004-12-30 Yon Steven A. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection
US6840955B2 (en) * 2000-01-27 2005-01-11 Robert J. Ein Therapeutic apparatus
US6843800B1 (en) 1998-01-23 2005-01-18 Innercool Therapies, Inc. Patient temperature regulation method and apparatus
US20050076924A1 (en) * 1998-01-23 2005-04-14 Dobak John D. Medical procedure
US6905494B2 (en) 1998-03-31 2005-06-14 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection
US20050157774A1 (en) * 2003-11-12 2005-07-21 Sensitech, Inc. Probeless dry ice sensor
US20050171586A1 (en) * 1999-02-09 2005-08-04 Dobak John D.Iii Method and apparatus for patient temperature control employing administration of anti-shivering agents
US20050222653A1 (en) * 1998-04-21 2005-10-06 Alsius Corporation Indwelling heat exchange catheter and method of using same
US6991645B2 (en) 1998-01-23 2006-01-31 Innercool Therapies, Inc. Patient temperature regulation method and apparatus
US20060136023A1 (en) * 2004-08-26 2006-06-22 Dobak John D Iii Method and apparatus for patient temperature control employing administration of anti-shivering agents
US20060241535A1 (en) * 2005-04-25 2006-10-26 Chan Yung C Arthritic hand or foot treatment apparatus
US7291144B2 (en) 1998-03-31 2007-11-06 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2260134A (en) * 1939-10-27 1941-10-21 William H Ballman Body pad
US2726658A (en) * 1953-04-27 1955-12-13 Donald E Chessey Therapeutic cooling devices for domestic and hospital use
US3738372A (en) * 1972-01-13 1973-06-12 T Shioshvili Apparatus for application of local hypothermy to the kidney

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2260134A (en) * 1939-10-27 1941-10-21 William H Ballman Body pad
US2726658A (en) * 1953-04-27 1955-12-13 Donald E Chessey Therapeutic cooling devices for domestic and hospital use
US3738372A (en) * 1972-01-13 1973-06-12 T Shioshvili Apparatus for application of local hypothermy to the kidney

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* Cited by examiner, † Cited by third party
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US4338944A (en) * 1980-06-16 1982-07-13 The Kendall Company Therapeutic device
DE3122617A1 (en) * 1980-06-16 1982-04-08 The Kendall Co., Walpole, Mass. DEVICE FOR THERAPEUTIC COLD TREATMENT OF A PATIENT
US4335726A (en) * 1980-07-11 1982-06-22 The Kendall Company Therapeutic device with temperature and pressure control
US4846176A (en) * 1987-02-24 1989-07-11 Golden Theodore A Thermal bandage
EP0342676A2 (en) * 1988-05-20 1989-11-23 Temperature Research Corporation Apparatus for localized heat and cold therapy
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WO1994000086A1 (en) * 1992-06-26 1994-01-06 Horn Stuart B Temperature controlled body pads
US6702842B2 (en) 1998-01-23 2004-03-09 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US6096068A (en) * 1998-01-23 2000-08-01 Innercool Therapies, Inc. Selective organ cooling catheter and method of using the same
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US7998182B2 (en) 1998-01-23 2011-08-16 Innercool Therapies, Inc. Selective organ cooling apparatus
US7951183B2 (en) 1998-01-23 2011-05-31 Innercool Therapies, Inc. Medical procedure
US6235048B1 (en) 1998-01-23 2001-05-22 Innercool Therapies, Inc. Selective organ hypothermia method and apparatus
US6238428B1 (en) 1998-01-23 2001-05-29 Innercool Therapies, Inc. Selective organ cooling apparatus and method employing turbulence-inducing element with curved terminations
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US7651518B2 (en) 1998-01-23 2010-01-26 Innercool Therapies, Inc. Inflatable catheter for selective organ heating and cooling and method of using the same
US20080221651A1 (en) * 1998-01-23 2008-09-11 Innercool Therapies, Inc. Medical procedure
US20080200970A1 (en) * 1998-01-23 2008-08-21 Innercool Therapies, Inc. Patient temperature regulation method and apparatus
US7371254B2 (en) 1998-01-23 2008-05-13 Innercool Therapies, Inc. Medical procedure
US7311725B2 (en) 1998-01-23 2007-12-25 Innercool Therapies, Inc. Patient temperature regulation method and apparatus
US6312452B1 (en) 1998-01-23 2001-11-06 Innercool Therapies, Inc. Selective organ cooling catheter with guidewire apparatus and temperature-monitoring device
US20060276865A1 (en) * 1998-01-23 2006-12-07 Dobak John D Iii Fever regulation method and apparatus
US7101386B2 (en) 1998-01-23 2006-09-05 Innercool Therapies, Inc. Patient temperature regulation method and apparatus
US6464716B1 (en) 1998-01-23 2002-10-15 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US6468296B1 (en) * 1998-01-23 2002-10-22 Innercool Therapies, Inc. Method for low temperature thrombolysis and low temperature thrombolytic agent with selective organ temperature control
US7094253B2 (en) 1998-01-23 2006-08-22 Innercool Therapies, Inc. Fever regulation method and apparatus
US7066948B2 (en) 1998-01-23 2006-06-27 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US7063718B2 (en) 1998-01-23 2006-06-20 Innercool Therapies, Inc. Selective organ hypothermia method and apparatus
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US6482226B1 (en) 1998-01-23 2002-11-19 Innercool Therapies, Inc. Selective organ hypothermia method and apparatus
US6491039B1 (en) 1998-01-23 2002-12-10 Innercool Therapies, Inc. Medical procedure
US20030018375A1 (en) * 1998-01-23 2003-01-23 Dobak John D. Selective organ cooling apparatus and method
US20060124141A1 (en) * 1998-01-23 2006-06-15 Innercool Therapies, Inc. Patient temperature regulation method and apparatus
US6533804B2 (en) 1998-01-23 2003-03-18 Innercool Therapies, Inc. Inflatable catheter for selective organ heating and cooling and method of using the same
US6991645B2 (en) 1998-01-23 2006-01-31 Innercool Therapies, Inc. Patient temperature regulation method and apparatus
US6540771B2 (en) 1998-01-23 2003-04-01 Innercool Therapies, Inc. Inflatable catheter for selective organ heating and cooling and method of using the same
US20050240250A1 (en) * 1998-01-23 2005-10-27 Dobak John D Iii Selective organ hypothermia method and apparatus
US20030078641A1 (en) * 1998-01-23 2003-04-24 Innercool Therapies, Inc. Selective organ hypothermia method and apparatus
US6558412B2 (en) 1998-01-23 2003-05-06 Innercool Therapies, Inc. Selective organ hypothermia method and apparatus
US6905509B2 (en) 1998-01-23 2005-06-14 Innercool Therapies, Inc. Selective organ cooling catheter with guidewire apparatus and temperature-monitoring device
US6887262B2 (en) 1998-01-23 2005-05-03 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US20050076924A1 (en) * 1998-01-23 2005-04-14 Dobak John D. Medical procedure
US6843800B1 (en) 1998-01-23 2005-01-18 Innercool Therapies, Inc. Patient temperature regulation method and apparatus
US20040230265A1 (en) * 1998-01-23 2004-11-18 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US20030144714A1 (en) * 1998-01-23 2003-07-31 Innercool Therapies, Inc. Selective organ hypothermia method and apparatus
US6786218B2 (en) 1998-01-23 2004-09-07 Innercool Therapies, Inc. Medical procedure
US6648908B2 (en) 1998-01-23 2003-11-18 Innercool Therapies, Inc. Inflatable catheter for selective organ heating and cooling and method of using the same
US20040153133A1 (en) * 1998-01-23 2004-08-05 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US6676689B2 (en) 1998-01-23 2004-01-13 Innercool Therapies, Inc. Inflatable catheter for selective organ heating and cooling and method of using the same
US6755850B2 (en) 1998-01-23 2004-06-29 Innercool Therapies, Inc. Selective organ hypothermia method and apparatus
US6676688B2 (en) 1998-01-23 2004-01-13 Innercool Therapies, Inc. Method of making selective organ cooling catheter
US20040106969A1 (en) * 1998-01-23 2004-06-03 Innercool Therapies, Inc. Inflatable catheter for selective organ heating and cooling and method of using the same
US6692488B2 (en) 1998-01-23 2004-02-17 Innercool Therapies, Inc. Apparatus for cell necrosis
US6695873B2 (en) 1998-01-23 2004-02-24 Innercool Therapies, Inc. Inflatable catheter for selective organ heating and cooling and method of using the same
US6491716B2 (en) 1998-03-24 2002-12-10 Innercool Therapies, Inc. Method and device for applications of selective organ cooling
US6251129B1 (en) 1998-03-24 2001-06-26 Innercool Therapies, Inc. Method for low temperature thrombolysis and low temperature thrombolytic agent with selective organ temperature control
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US6471717B1 (en) 1998-03-24 2002-10-29 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US6740109B2 (en) 1998-03-24 2004-05-25 Innercool Therapies, Inc. Isolated selective organ cooling method
US6551349B2 (en) 1998-03-24 2003-04-22 Innercool Therapies, Inc. Selective organ cooling apparatus
US6254626B1 (en) 1998-03-24 2001-07-03 Innercool Therapies, Inc. Articulation device for selective organ cooling apparatus
US6251130B1 (en) 1998-03-24 2001-06-26 Innercool Therapies, Inc. Device for applications of selective organ cooling
US6576002B2 (en) 1998-03-24 2003-06-10 Innercool Therapies, Inc. Isolated selective organ cooling method and apparatus
US6582455B1 (en) 1998-03-24 2003-06-24 Innercool Therapies, Inc. Method and device for applications of selective organ cooling
US6224624B1 (en) 1998-03-24 2001-05-01 Innercool Therapies, Inc. Selective organ cooling apparatus and method
US6475231B2 (en) 1998-03-24 2002-11-05 Innercool Therapies, Inc. Method and device for applications of selective organ cooling
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US20040267250A1 (en) * 1998-03-31 2004-12-30 Yon Steven A. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection
US7288089B2 (en) 1998-03-31 2007-10-30 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection
US8043351B2 (en) 1998-03-31 2011-10-25 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection
US6905494B2 (en) 1998-03-31 2005-06-14 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection
US6602276B2 (en) 1998-03-31 2003-08-05 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation
US6818011B2 (en) 1998-03-31 2004-11-16 Innercool Therapies, Inc. Circulating fluid hypothermia method and apparatus
US20080300585A1 (en) * 1998-03-31 2008-12-04 Innercool Therapies, Inc. Method and device for performing cooling-or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation
US20040147914A1 (en) * 1998-03-31 2004-07-29 Kramer Hans W. Method and device for performing cooling- or cryo-therapies for, E.G., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing microporous balloon
US8043283B2 (en) 1998-03-31 2011-10-25 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation
US7291144B2 (en) 1998-03-31 2007-11-06 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation
US6149677A (en) * 1998-03-31 2000-11-21 Innercool Therapies, Inc. Circulating fluid hypothermia method
US6231595B1 (en) 1998-03-31 2001-05-15 Innercool Therapies, Inc. Circulating fluid hypothermia method and apparatus
US6685732B2 (en) 1998-03-31 2004-02-03 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing microporous balloon
US20010007951A1 (en) * 1998-03-31 2001-07-12 Innercool Therapies, Inc Circulating fluid hypothermia method and apparatus
US7001378B2 (en) 1998-03-31 2006-02-21 Innercool Therapies, Inc. Method and device for performing cooling or cryo-therapies, for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection
US20050228368A1 (en) * 1998-03-31 2005-10-13 Yon Steven A Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection
US8157794B2 (en) 1998-03-31 2012-04-17 Innercool Therapies, Inc. Method and device for performing cooling-or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation
US20040087934A1 (en) * 1998-03-31 2004-05-06 Innercool Therapies, Inc. Method and device for performing cooling- or cryo-therapies for, E.G., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation
US20050222653A1 (en) * 1998-04-21 2005-10-06 Alsius Corporation Indwelling heat exchange catheter and method of using same
US7857781B2 (en) 1998-04-21 2010-12-28 Zoll Circulation, Inc. Indwelling heat exchange catheter and method of using same
US6585752B2 (en) 1998-06-23 2003-07-01 Innercool Therapies, Inc. Fever regulation method and apparatus
US7018399B2 (en) 1998-06-23 2006-03-28 Innercool Therapies, Inc. Method of making selective organ cooling catheter
US6261312B1 (en) 1998-06-23 2001-07-17 Innercool Therapies, Inc. Inflatable catheter for selective organ heating and cooling and method of using the same
US20040230264A1 (en) * 1998-06-23 2004-11-18 Dobak John D. Method of making selective organ cooling catheter
US7351254B2 (en) 1999-02-09 2008-04-01 Innercool Therapies, Inc. Method and device for patient temperature control employing optimized rewarming
US20030060863A1 (en) * 1999-02-09 2003-03-27 Dobak John D. Method and apparatus for patient temperature control employing administration of anti-shivering agents
US20030023288A1 (en) * 1999-02-09 2003-01-30 Michael Magers Method and device for patient temperature control employing optimized rewarming
US6830581B2 (en) 1999-02-09 2004-12-14 Innercool Therspies, Inc. Method and device for patient temperature control employing optimized rewarming
US6869440B2 (en) 1999-02-09 2005-03-22 Innercool Therapies, Inc. Method and apparatus for patient temperature control employing administration of anti-shivering agents
US7189254B2 (en) 1999-02-09 2007-03-13 Innercool Therapies, Inc. Method and device for patient temperature control employing optimized rewarming
US20050096715A1 (en) * 1999-02-09 2005-05-05 Innercool Therapies, Inc. Method and device for patient temperature control employing optimized rewarming
US7422600B2 (en) 1999-02-09 2008-09-09 Innercool Therapies, Inc. Method and apparatus for patient temperature control employing administration of anti-shivering agents
US20050171586A1 (en) * 1999-02-09 2005-08-04 Dobak John D.Iii Method and apparatus for patient temperature control employing administration of anti-shivering agents
US6676690B2 (en) 1999-10-07 2004-01-13 Innercool Therapies, Inc. Inflatable heat transfer apparatus
US6325818B1 (en) 1999-10-07 2001-12-04 Innercool Therapies, Inc. Inflatable cooling apparatus for selective organ hypothermia
US7052508B2 (en) 1999-10-07 2006-05-30 Innercool Therapies, Inc. Inflatable heat transfer apparatus
US6840955B2 (en) * 2000-01-27 2005-01-11 Robert J. Ein Therapeutic apparatus
US6576001B2 (en) 2000-03-03 2003-06-10 Innercool Therapies, Inc. Lumen design for catheter
US6379378B1 (en) 2000-03-03 2002-04-30 Innercool Therapies, Inc. Lumen design for catheter
US20040116987A1 (en) * 2000-06-02 2004-06-17 Innercool Therapies, Inc. Method for determining the effective thermal mass of a body or organ using a cooling catheter
US6660028B2 (en) 2000-06-02 2003-12-09 Innercool Therapies, Inc. Method for determining the effective thermal mass of a body or organ using a cooling catheter
US7211105B2 (en) 2000-06-02 2007-05-01 Innercool Therapias, Inc. Method for determining the effective thermal mass of a body or organ using a cooling catheter
US7491223B2 (en) 2000-06-14 2009-02-17 Innercool Therapies, Inc. Therapeutic heating and cooling via temperature management of a colon-inserted balloon
US20040199229A1 (en) * 2000-06-14 2004-10-07 Innercool Therapies, Inc. Therapeutic heating and cooling via temperature management of a colon-inserted balloon
US6726708B2 (en) 2000-06-14 2004-04-27 Innercool Therapies, Inc. Therapeutic heating and cooling via temperature management of a colon-inserted balloon
US7004960B2 (en) 2000-11-07 2006-02-28 Innercool Therapies, Inc. Circulation set for temperature-controlled catheter and method of using the same
US6719779B2 (en) 2000-11-07 2004-04-13 Innercool Therapies, Inc. Circulation set for temperature-controlled catheter and method of using the same
US20040102825A1 (en) * 2000-11-07 2004-05-27 Innercool Therapies, Inc. Circulation set for temperature-controlled catheter and method of using the same
US7300453B2 (en) 2003-02-24 2007-11-27 Innercool Therapies, Inc. System and method for inducing hypothermia with control and determination of catheter pressure
US20040199230A1 (en) * 2003-02-24 2004-10-07 Yon Steve A. System and method for inducing hypothermia with control and determination of catheter pressure
US20050157774A1 (en) * 2003-11-12 2005-07-21 Sensitech, Inc. Probeless dry ice sensor
US20060136023A1 (en) * 2004-08-26 2006-06-22 Dobak John D Iii Method and apparatus for patient temperature control employing administration of anti-shivering agents
US20070093730A1 (en) * 2005-04-25 2007-04-26 Chan Yung C Arthritic hand or foot treatment apparatus
US7169119B2 (en) * 2005-04-25 2007-01-30 Chan Yung C Arthritic hand or foot treatment apparatus
US20060241535A1 (en) * 2005-04-25 2006-10-26 Chan Yung C Arthritic hand or foot treatment apparatus

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