WO2008077317A1 - Système d'ablation par radiofréquence avec refroidisseur joule-thomson - Google Patents

Système d'ablation par radiofréquence avec refroidisseur joule-thomson Download PDF

Info

Publication number
WO2008077317A1
WO2008077317A1 PCT/CN2007/003749 CN2007003749W WO2008077317A1 WO 2008077317 A1 WO2008077317 A1 WO 2008077317A1 CN 2007003749 W CN2007003749 W CN 2007003749W WO 2008077317 A1 WO2008077317 A1 WO 2008077317A1
Authority
WO
WIPO (PCT)
Prior art keywords
probe
ablation
tissue
temperature
joule
Prior art date
Application number
PCT/CN2007/003749
Other languages
English (en)
Inventor
Zhaohua Chang
Peng-Fei Yang
Original Assignee
Accutarget Medipharma (Shanghai) Corp. Ltd.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from CN200610147978A external-priority patent/CN100574719C/zh
Application filed by Accutarget Medipharma (Shanghai) Corp. Ltd. filed Critical Accutarget Medipharma (Shanghai) Corp. Ltd.
Publication of WO2008077317A1 publication Critical patent/WO2008077317A1/fr

Links

Classifications

    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F25—REFRIGERATION OR COOLING; COMBINED HEATING AND REFRIGERATION SYSTEMS; HEAT PUMP SYSTEMS; MANUFACTURE OR STORAGE OF ICE; LIQUEFACTION SOLIDIFICATION OF GASES
    • F25B—REFRIGERATION MACHINES, PLANTS OR SYSTEMS; COMBINED HEATING AND REFRIGERATION SYSTEMS; HEAT PUMP SYSTEMS
    • F25B9/00—Compression machines, plants or systems, in which the refrigerant is air or other gas of low boiling point
    • F25B9/02—Compression machines, plants or systems, in which the refrigerant is air or other gas of low boiling point using Joule-Thompson effect; using vortex effect
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
    • A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
    • A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
    • A61B2018/00017—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids with gas
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
    • A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
    • A61B2018/00023—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids closed, i.e. without wound contact by the fluid
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
    • A61B2018/00047—Cooling or heating of the probe or tissue immediately surrounding the probe using Peltier effect
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00642—Sensing and controlling the application of energy with feedback, i.e. closed loop control
    • A61B2018/00654—Sensing and controlling the application of energy with feedback, i.e. closed loop control with individual control of each of a plurality of energy emitting elements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00696—Controlled or regulated parameters
    • A61B2018/00702—Power or energy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00696—Controlled or regulated parameters
    • A61B2018/00744—Fluid flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00773—Sensed parameters
    • A61B2018/00791—Temperature
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00773—Sensed parameters
    • A61B2018/00791—Temperature
    • A61B2018/00797—Temperature measured by multiple temperature sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
    • A61B2018/0231—Characteristics of handpieces or probes
    • A61B2018/0262—Characteristics of handpieces or probes using a circulating cryogenic fluid

Definitions

  • the inventions described below relate the field of RF ablation.
  • Radio frequency (RF) ablation and cryoablation are widely used for treating many kinds of diseases, including liver tumor, mastadenoma, prostate tumor and cerebroma, etc.
  • the RF electrode is inserted into the pathological tissue, and a large reference or ground electrode for contracting a large surface of the body is placed on the skin.
  • the high-frequency current passed through the probe tip to the ground electrode heats body tissue in the vicinity of the probe tip, resulting in ablation of the tissue.
  • Cryoablation of diseased tissues is also widely used, accomplished through the application of a cryoprobe to a designated area, which is operated to freeze and thereby ablate a target tissue area.
  • the effect of direct thermal ablation is correlated with the temperature achieved within the target tissue, and the temperature is determined by the total thermal energy applied, rate of removal of heat, and the specific thermal sensitivity of the tissue.
  • heating tissue to a temperature of 42 1 C to 45 1 C can cause the irreversible cellular damage needed for thermal ablation.
  • the inactivation of vital enzymes within this range of temperature is the most dominant factor in resulting tissue damage.
  • tissue temperature rises to 60 1 C the time of producing irreversible cellular damage is greatly shortened.
  • the temperature is above 60 1 C, protein denaturation occurs. An area of coagulation and necrosis block appear.
  • water within the tissue is boiled.
  • the current density is the highest around the electrode, so the temperature in the target tissue is highest immediately proximate the RF electrode. As the distance from the electrode tip increases, the temperature gradually decreases. If the RF ablation energy is improved to increase the temperature, tissue close to the electrode is easy to be charred, making it difficult to create deep lesions.
  • RF ablation lesion depth is expanded by the following methods:
  • One is to utilize multiple electrodes to increase the diameter of ablation, such as multiple antenna ablation apparatus from Rita Medical Systems, Inc.
  • multiple electrodes to increase the diameter of ablation, such as multiple antenna ablation apparatus from Rita Medical Systems, Inc.
  • Such systems require multiple tissue punctures, and therefore result in additional tissue trauma, and increased danger of damaging adjacent important tissue.
  • the use and operation of the electrodes are complicated, so it is difficult to insert the electrode correctly into the target tissue.
  • the ablation area of multiple antenna ablation electrode is irregular, so hemorrhage and infection are inevitable .
  • a cooling element Another technique for enhancing lesion depth in RF ablation systems is the addition of a cooling element.
  • Ablation electrodes with cooling elements can reduce the probability of carbonization, make more electromagnetic energy applied to the pathological tissue, lengthen ablation time, and finally increase the lesion depth of ablation.
  • the cool- tip electrode of Sherwood Services AG injects fluid coolant, such as water or saline, to reduce tip temperature through heat convection. This system can reduce the excessive temperature of the ablation process adjacent to the tip and increase the heat energy effectively.
  • the cooling element adopted at present is mainly liquid fluid, for instance water, saline, etc. These cooling solutions are pumped into the RF probe to cool the RF electrode.
  • the warming to melt the bulk of the frozen tissue can damage the tissue by the mechanisms of solution effects and recrystallization.
  • RF energy provided through an RF electrode in a cryoprobe can be used to thaw the bulk of the frozen tissue and damage the tissue by post-cryoablation warming and by thermal ablation.
  • the RF ablation probe described is combined with a Joule- Thomson cooling system which is operable to cool the RF electrode of the probe in order to prevent overheating of body tissue proximate the probe and enable the creation of larger and deeper lesions.
  • the system can also be operated as Joule- Thomson cryoprobe, wherein the RF electrode can be used to thaw body tissue after cryoablation.
  • This system can control the temperature at the tip of the probe. When operated to accomplish RF ablation, the temperature of tip can be controlled through the modes of RF ablation and cooling, and in this way it can not only create a deep lesion and avoid denaturing tissue adjacent to the RF tip.
  • the gas used for Joule Thomson can be supplied at different pressures to generate different cooling effects, and cooperate with radio frequency energy of different power to change the thermal distribution of the tissue around the probe, in order to control the ablation range.
  • the system includes the probe, handle, transporting tube, control unit and gas container.
  • the control unit can display, control, monitor the parameters of ablation.
  • Figure 1 shows a first embodiment of a hybrid ablation system with RF ablation and cryogenic cooling modalities.
  • Figure 2 shows a cross section of one form of the probe tip.
  • Figure 3 is a graph illustrating temperature history with and without the cooling method in the process of radio frequency ablation.
  • Figure 4 is a graph illustrating the change of tissue temperature when cooling method is adopted after a certain stage of radio frequency ablation.
  • Figure 5 is a graph illustrating temperature distribution associated with the probe in the process of radio frequency ablation.
  • Figure 6 is a block diagram illustrating operating methods of the control unit.
  • Fig. 1 illustrates a hybrid ablation system 100 with RF ablation and Joule-Thomson cooling modalities and the illustrative elements thereof.
  • the whole system 100 is mainly composed of probe 20 and handle 29, an RF generator 62, high pressure gas reservoir 70, combined RF supply cable and high pressure gas supply line 50, and the control unit 60.
  • Handle 29 and the control unit 60 are connected together through combined RF supply cable and high pressure gas supply line 50.
  • the combined RF supply cable and high pressure gas supply line 50 comprises gas inlet tube 51, gas outlet cavity 52, and RF supply cable 26.
  • There is a microprocessor 64 in the control unit 60 which controls electromagnetic control equipment 61, temperature monitoring equipment 63, RF generator 62 and display equipment 67.
  • the gas inlet tube 51 is linked with gas container 70 through electromechanical control valves 61.
  • Thermo-sensor 27 is linked through cable 53 with temperature monitoring equipment 63, wherein RF line 26 is linked with RF generator 62.
  • gas flows in high- pressure tube 21 and spiral finned tube 22 to Joule-Thomson nozzle 23.
  • high pressure gas such as Argon
  • Joule-Thomson effect leads to cooling of the gas upon exit from the nozzle.
  • the lumen on the tip of the probe is filled with the cooling gas, and the gas cools the probe wall, and upon exhaust also cools the spiral finned tube 22 and probe wall, then discharges through the lumen between heat insulation tube 24 and high-pressure tube 21, and vents to atmosphere at the bottom of the control unit 60 through gas supply line 50.
  • the tip 25 of probe 24 is adapted for easy insertion into pathological tissue. It comprises an outer sheath with a closed distal end. The length and diameter of the sheath is selected depending on the size of pathological tissue to be ablated, and is inserted into the tissue to a depth such that the RF electrode is located within the pathological tissue.
  • the outer sheath may comprise stainless steel, nickel titanium alloy or titanium, etc.
  • the inner surface of the tip 25 may be fitted with internal screw fins for a length of about 2 cm to 3 cm. This facilitates heat exchange between the cooling gas and the probe tip and cooling of the external wall of the probe.
  • RF line 26 is connected with the tip by junction (a weld, braze, or other secure electrical connection).
  • RF power supplied by the RF generator 62 is transmitted through the pathological tissue, between the tip and a reference ground or indifferent electrode, to heat the pathological tissue to temperature sufficient to cause ablation.
  • the heating of the tissue can be controlled through controlling the power of RF generator 62.
  • the elongated tissue-penetrating probe includes an insulating coating 28 in order to prevent the flow of electric current from the shaft of the probe into the health tissue surrounding proximal portions of the probe. Therefore, except the tip of probe, surrounding tissue contacting with the shaft of probe is not heated up.
  • the length of insulating coating can be changed to alter the effective length of the probe from which ablative energy will pass into body tissue.
  • the ablation temperature of the tip of probe 25 can be adjusted through the cooling effect generated by gas passing through Joule-Thomson nozzle 23, thus the temperature of the tissue in contact with probe can be controlled.
  • gas flows into spiral finned tube 22 and then exits the Joule-Thomson nozzle 23.
  • the pressure sharply drops after the gas flows through Joule-Thomson nozzle 23, and this results in cooling of the gas to cryogenic temperatures.
  • Lumen on the tip of the probe is filled with the cooling gas, and the cooled gas exhausts over spiral finned tube 22 and pre-cools incoming gas through heat exchange with spiral finned tube 22, to enhance the cooling effect.
  • This classic fin-tube helical coil heat exchanger is preferred, but other heat exchange arrangements may be used, including a straight fin-tube counterflow heat exchanger, or a spiral-finned counterflow heat exchanger.
  • the gas used in system 100 is the gas having a positive Joule-Thomson effect, such as nitrogen, argon and most other gases.
  • the gas is stored in gas reservoir 70.
  • Gas container 70 has a certain initial pressure, such as 1800 psi.
  • the pressure of gas can be controlled by electromagnetic control equipment 61.
  • the different cooling capacities can be produced under different pressures of supplied gas.
  • the control system is operable to alter the supplied gas pressure, through pressure control valves in the electromagnetic control equipment, to effect different levels of cooling. Therefore, temperature probe tip and of the surrounding tissue can be controlled or changed through changing and balancing the gas pressure supplied to the probe tip and RF power supplied to the RF electrode in the tip.
  • the cooling can reduce the temperature of tissue in contact with the tip of the probe 25 to avoid necrosis and/or charring of the tissue, so that RF energy supplied through the tip can be applied without regard to the high electrical resistance of necrosed and charred tissue.
  • Thermo-sensor 27 in the probe 20 may be thermocouple, thermal resistance or sensors of other forms.
  • the signal gathered by the sensor indicates the temperature of surrounding tissue or the degree of ablation.
  • the temperature monitoring equipment 63 and microprocessor 64 process the temperature signal provided by the thermo-sensor and control the RF generator 62 and electromagnetic control equipment 61 to achieve a desired ablation profile.
  • heat insulation tube 24 is disposed coaxially between the outer sheath and the gas inlet tube 21. It extends through the probe 20 and both ends of it are fixed to the inner wall of probe by soldering or other means, to create an air insulated or vacuum insulated chamber proximal to the distal tip of the probe.
  • the heat insulation tube can comprise stainless steel or other materials.
  • Handle 29 is a hollow tube which provides an ergonomic handle structure and serves as a support structure for joining the several components of the probe.
  • the end of the probe 20 fits tightly into the distal end of the handle.
  • the proximal end of the handle fits tightly into outer tube 55 of high pressure gas supply tube.
  • the handle can be made of any material, an is preferably made of an thermally and electrically insulative material.
  • This graph illustrates temperature history during RF ablation, both with and without application of cooling gas. It shows the curves of tissue temperature changing with time.
  • the horizontal axis corresponds to ablation time, while the vertical axis corresponds to tissue temperature.
  • Body temperature of 37°C is indicated by the horizontal solid line.
  • a temperature level of 100 0 C is marked. It has mentioned in the above, 100 °C is the boiling point of water and is very important in the course of ablation of tissue, and body temperature is easily charred when the temperature exceeds 100 0 C.
  • a temperature level of 0 0 C (the freezing point of water) is also marked in the graph.
  • Curves 81 and 82 in Figure 3 show that when traditional RF ablation probe is used, the temperature history of tissue close to the ablation probe (Curve 81) and tissue farther from the ablation probe, for example about 2 cm from the probe (Curve 82).
  • the RF ablation begins, it can be seen from curve 81 that the temperature of tissue close to the ablation probe rises rapidly and exceeds the ablation temperature in a short time, and can quickly reach 100 ⁇ C.
  • Curve 82 shows that within this period of time, the temperature of tissue farther from the ablation probe rises slowly and does not reach the ablation temperature, so the effect of ablation in this place is limited. If RF heating proceeds, curve 81 will extend to curve 90.
  • Temperature curves represented by curves 83 and 85 illustrate the characteristic temperatures in tissue near and distant from the probe of Figure 1 when operated to provide RF ablation with JT cooling.
  • electromagnetic control equipment 61 make the gas flow into the probe 20, and Joule-Thomson effect occurs at the tip of the probe to cool the tissue close to the electrode probe.
  • Curve 83 shows that the temperature drops to a certain temperature, which depends on the time and the gas pressure. Tissue farther removed from the ablation probe is not affected and remains at 37 0 C, as curve 85 shows. Subsequently, RF ablation starts and the temperature rises gradually. The change can be seen in curve 84.
  • Figure 4 shows the change of tissue temperature when cooling method is initiated after a period of radio frequency ablation.
  • the course of curve 81 and 82 has already been described in Figure 3.
  • the radio frequency heating temperature is close to 100 0 C, such as 80 °C
  • gas flow is initiated to cool the probe tip and immediately adjacent tissue to prevent the charring of tissue.
  • curve 87 temperature at or near the probe may drop upon initiation of cooling flow.
  • the relative amounts of RF power and cooling gas supplied to the probe can be adjusted to provide heating power greater than the cooling power, so that the temperature of the tissue close to the probe remains above the ablation temperature and begins to rise after dropping, s illustrated by curve 88.
  • the temperature of the tissue farther from the probe slowly rises and eventually exceeds the ablation temperature.
  • Figure 3 and 4 show the different methods, in which cooling carried on at different times relative to the start of the RF ablation process effects the temperature profile of the tissue surrounding the probe.
  • the cooling gas flow can be started and stopped for many times according to the actual conditions of the body tissue, as indicated by the temperature sensor in the probe, and the gas pressure can be changed to adjust the course of ablation.
  • Figure 5 shows the curve of the tissue temperature changing with the distance of tissue from the probe.
  • the nominal radial distance TISSUE DEPTH from the central axis of a probe tip is plotted against temperature T.
  • the ablation temperature is marked in the figure, namely ABLATION TEMPERATURE indicated by the dashed line.
  • the corresponding distance of ABLATION TEMPERATURE is the ablation radius or tissue depth.
  • the curve 91 represents the operation of a traditional ablation probe. It can be seen that the temperature rapidly falls off and approaches body temperature a short distance from the probe.
  • the temperature of the tissue close to the probe surface is illustrated by point 92 and this temperature is higher than the ablation temperature.
  • FIG 6 is a block diagram of the control unit of this hybrid ablation system with RF ablation and cryogenic modalities. It can be seen from the Figure 8 that the RF generator 62 applies the electromagnetic energy to the tissue to be ablated through the probe 20. Temperature monitoring equipment 63 monitors the temperatures of the probe 20, and provides signals indicative of the temperature to microprocessor 64. If the temperature of the probe is high, microprocessor 64 will send a signal to electromechanical control system, electromechanical control system 61 will function, as directed by the microprocessor, to provide cooling gas at suitable pressure to the probe, and then the temperature of the probe comes down. If the temperature of the probe is low, the temperature of the probe tip will be controlled by increasing the generating power of RF generator 62 to realize ablation. In this way, the temperature can be regulated and controlled to carry on different treatment schemes.

Landscapes

  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Surgery (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Animal Behavior & Ethology (AREA)
  • Physics & Mathematics (AREA)
  • Veterinary Medicine (AREA)
  • Otolaryngology (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Plasma & Fusion (AREA)
  • Mechanical Engineering (AREA)
  • Thermal Sciences (AREA)
  • General Engineering & Computer Science (AREA)
  • Surgical Instruments (AREA)

Abstract

L'invention concerne un système d'ablation de tissus par radiofréquence (100) avec un refroidisseur Joule-Thomson. Ce refroidisseur Joule-Thomson est utilisé pour limiter la température des électrodes RF. Un générateur RF (62) génère une énergie électromagnétique destinée à l'ablation de tissus, et cette énergie électromagnétique peut aussi être utilisée pour réchauffer la sonde (20) lorsque cette sonde (20) est utilisée comme cryosonde.
PCT/CN2007/003749 2006-12-26 2007-12-24 Système d'ablation par radiofréquence avec refroidisseur joule-thomson WO2008077317A1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
CN200610147978.6 2006-12-26
CN200610147978A CN100574719C (zh) 2006-12-26 2006-12-26 气体节流冷却式射频消融电极
US11/935,331 2007-11-05
US11/935,331 US20080154258A1 (en) 2006-12-26 2007-11-05 Radio Frequency Ablation System with Joule-Thomson Cooler

Publications (1)

Publication Number Publication Date
WO2008077317A1 true WO2008077317A1 (fr) 2008-07-03

Family

ID=39562097

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2007/003749 WO2008077317A1 (fr) 2006-12-26 2007-12-24 Système d'ablation par radiofréquence avec refroidisseur joule-thomson

Country Status (1)

Country Link
WO (1) WO2008077317A1 (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2160990A1 (fr) * 2008-07-02 2010-03-10 Erbe Elektromedizin GmbH Appareil d'alimentation doté d'une commande destinée au fonctionnement d'une cryosonde, appareil cryochirurgical
WO2010040431A1 (fr) * 2008-10-07 2010-04-15 Erbe Elektromedizin Gmbh Procédé et dispositif de dévitalisation de tissu biologique
CN102309364A (zh) * 2010-07-01 2012-01-11 上海导向医疗系统有限公司 辅助射频消融用的气体流量控制装置及其实施冷却的方法

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5275595A (en) * 1992-07-06 1994-01-04 Dobak Iii John D Cryosurgical instrument
US5452582A (en) * 1994-07-06 1995-09-26 Apd Cryogenics, Inc. Cryo-probe
US20020022832A1 (en) * 1998-06-19 2002-02-21 Mikus Paul W. Cryoprobe assembly with detachable sheath
CN2579358Y (zh) * 2002-11-25 2003-10-15 罗昌渠 可控射频冷热极
CN1812748A (zh) * 2003-06-25 2006-08-02 恩道凯尔公司 一种可拆卸的冷冻外科探针

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5275595A (en) * 1992-07-06 1994-01-04 Dobak Iii John D Cryosurgical instrument
US5452582A (en) * 1994-07-06 1995-09-26 Apd Cryogenics, Inc. Cryo-probe
US20020022832A1 (en) * 1998-06-19 2002-02-21 Mikus Paul W. Cryoprobe assembly with detachable sheath
CN2579358Y (zh) * 2002-11-25 2003-10-15 罗昌渠 可控射频冷热极
CN1812748A (zh) * 2003-06-25 2006-08-02 恩道凯尔公司 一种可拆卸的冷冻外科探针

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2160990A1 (fr) * 2008-07-02 2010-03-10 Erbe Elektromedizin GmbH Appareil d'alimentation doté d'une commande destinée au fonctionnement d'une cryosonde, appareil cryochirurgical
WO2010040431A1 (fr) * 2008-10-07 2010-04-15 Erbe Elektromedizin Gmbh Procédé et dispositif de dévitalisation de tissu biologique
CN102164555A (zh) * 2008-10-07 2011-08-24 爱尔伯电子医疗设备公司 用于使生物组织失活的方法和装置
JP2012504979A (ja) * 2008-10-07 2012-03-01 エルベ エレクトロメディジン ゲーエムベーハー 生物組織を失活させる方法及び装置
CN102309364A (zh) * 2010-07-01 2012-01-11 上海导向医疗系统有限公司 辅助射频消融用的气体流量控制装置及其实施冷却的方法

Similar Documents

Publication Publication Date Title
US20080154258A1 (en) Radio Frequency Ablation System with Joule-Thomson Cooler
US8287526B2 (en) Method of simultaneously freezing and heating tissue for ablation
JP4365786B2 (ja) 冷凍外科療法用装置および使用方法
US9554842B2 (en) Cryoprobe for low pressure systems
US7393350B2 (en) Cryo-surgical apparatus and methods
Brace Thermal tumor ablation in clinical use
EP1265543B1 (fr) Instrument electrochirurgical-cryochirurgical combine
US20050182393A1 (en) Multi-energy ablation station
WO1999015092A9 (fr) Procede et appareil de chauffage a utiliser pendant une operation de cryochirurgie
WO2008142686A2 (fr) Sonde d'ablation
EP1804703B1 (fr) Appareil cryo-chirurgical
Tungjitkusolmun Ablation
WO2008077317A1 (fr) Système d'ablation par radiofréquence avec refroidisseur joule-thomson
Morrison et al. Minimally Invasive Therapies for Hepatocellular Cancer: Ablation Technologies
Brace A Minimally Invasive Treatment Option for Cancers

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 07855757

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 07855757

Country of ref document: EP

Kind code of ref document: A1