US20070277550A1 - Refrigeration source for a cryoablation catheter - Google Patents

Refrigeration source for a cryoablation catheter Download PDF

Info

Publication number
US20070277550A1
US20070277550A1 US11098835 US9883505A US2007277550A1 US 20070277550 A1 US20070277550 A1 US 20070277550A1 US 11098835 US11098835 US 11098835 US 9883505 A US9883505 A US 9883505A US 2007277550 A1 US2007277550 A1 US 2007277550A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
system
coolant
catheter
medical device
primary cooling
Prior art date
Legal status (The legal status 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 status listed.)
Abandoned
Application number
US11098835
Inventor
Hong Li
Ravikumar Kudaravalli
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
AMERICAN MEDICAL SYSTEMS GYNECOLOGY Inc
CryoCor Inc
CooperSurgical Inc
Original Assignee
CryoCor Inc
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
Family has litigation

Links

Images

Classifications

    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F25REFRIGERATION OR COOLING; COMBINED HEATING AND REFRIGERATION SYSTEMS; HEAT PUMP SYSTEMS; MANUFACTURE OR STORAGE OF ICE; LIQUEFACTION SOLIDIFICATION OF GASES
    • F25DREFRIGERATORS; COLD ROOMS; ICE-BOXES; COOLING OR FREEZING APPARATUS NOT COVERED BY ANY OTHER SUBCLASS
    • F25D3/00Devices using other cold materials; Devices using cold-storage bodies
    • F25D3/10Devices using other cold materials; Devices using cold-storage bodies using liquefied gases, e.g. liquid air
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/02Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00017Electrical control of surgical instruments
    • A61B2017/00199Electrical control of surgical instruments with a console, e.g. a control panel with a display
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/02Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
    • A61B2018/0212Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques using an instrument inserted into a body lumen, e.g. catheter
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/02Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
    • A61B2018/0231Characteristics of handpieces or probes
    • A61B2018/0262Characteristics of handpieces or probes using a circulating cryogenic fluid
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/02Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
    • A61B2018/0231Characteristics of handpieces or probes
    • A61B2018/0262Characteristics of handpieces or probes using a circulating cryogenic fluid
    • A61B2018/0268Characteristics of handpieces or probes using a circulating cryogenic fluid with restriction of flow
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F25REFRIGERATION OR COOLING; COMBINED HEATING AND REFRIGERATION SYSTEMS; HEAT PUMP SYSTEMS; MANUFACTURE OR STORAGE OF ICE; LIQUEFACTION SOLIDIFICATION OF GASES
    • F25BREFRIGERATION MACHINES, PLANTS OR SYSTEMS; COMBINED HEATING AND REFRIGERATION SYSTEMS; HEAT-PUMP SYSTEMS
    • F25B2700/00Sensing or detecting of parameters; Sensors therefor
    • F25B2700/13Mass flow of refrigerants
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F25REFRIGERATION OR COOLING; COMBINED HEATING AND REFRIGERATION SYSTEMS; HEAT PUMP SYSTEMS; MANUFACTURE OR STORAGE OF ICE; LIQUEFACTION SOLIDIFICATION OF GASES
    • F25BREFRIGERATION MACHINES, PLANTS OR SYSTEMS; COMBINED HEATING AND REFRIGERATION SYSTEMS; HEAT-PUMP SYSTEMS
    • F25B9/00Compression machines, plant, or systems, in which the refrigerant is air or other gas of low boiling point
    • F25B9/02Compression machines, plant, or systems, in which the refrigerant is air or other gas of low boiling point using Joule-Thompson effect; using vortex effect
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F25REFRIGERATION OR COOLING; COMBINED HEATING AND REFRIGERATION SYSTEMS; HEAT PUMP SYSTEMS; MANUFACTURE OR STORAGE OF ICE; LIQUEFACTION SOLIDIFICATION OF GASES
    • F25DREFRIGERATORS; COLD ROOMS; ICE-BOXES; COOLING OR FREEZING APPARATUS NOT COVERED BY ANY OTHER SUBCLASS
    • F25D16/00Devices using a combination of a cooling mode associated with refrigerating machinery with a cooling mode not associated with refrigerating machinery
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F25REFRIGERATION OR COOLING; COMBINED HEATING AND REFRIGERATION SYSTEMS; HEAT PUMP SYSTEMS; MANUFACTURE OR STORAGE OF ICE; LIQUEFACTION SOLIDIFICATION OF GASES
    • F25DREFRIGERATORS; COLD ROOMS; ICE-BOXES; COOLING OR FREEZING APPARATUS NOT COVERED BY ANY OTHER SUBCLASS
    • F25D2400/00General features of, or devices for refrigerators, cold rooms, ice-boxes, or for cooling or freezing apparatus not covered by any other subclass
    • F25D2400/36Visual displays

Abstract

An apparatus and method for automatic operation of a refrigeration system to provide refrigeration power to a catheter for tissue ablation or mapping. The primary refrigeration system can be open loop or closed loop, and a precool loop will typically be closed loop. Equipment and procedures are disclosed for bringing the system to the desired operational state, for controlling the operation by controlling refrigerant flow rate, for performing safety checks, and for achieving safe shutdown. The catheter-based system for performing a cryoablation procedure uses a precooler to lower the temperature of a fluid refrigerant to a sub-cool temperature (−40° C.) at a working pressure (400 psi). The sub-cooled fluid is then introduced into a supply line of the catheter. Upon outflow of the primary fluid from the supply line, and into a tip section of the catheter, the fluid refrigerant boils at an outflow pressure of approximately one atmosphere, at a temperature of about −88° C. In operation, the working pressure is computer controlled to obtain an appropriate outflow pressure for the coldest possible temperature in the tip section.

Description

  • This application is continuation of application Ser. No. 10/888,804 filed Jul. 9, 2004 which is a continuation of application Ser. No. 10/243,997, which is currently pending and which is a continuation-in-part of application Ser. No. 09/635,108 filed Aug. 9, 2000, now U.S. Pat. No. 6,471,694. The contents of application Ser. Nos. 10/243,997 and 09/635,108 are incorporated herein by reference.
  • FIELD OF THE INVENTION
  • The present invention pertains generally to systems and methods for implementing cryoablation procedures. More particularly, the present invention pertains to systems and methods that precool a primary fluid to a sub-cooled, fully saturated liquid state, for use in a cryoablation procedure. The present invention is particularly, but not exclusively, useful as a system and method for cooling the distal tip of a cryoablation catheter during cardiac cryoablation therapy to cure heart arrhythmias. The present invention also relates to the field of methods and apparatus used to generate and control the delivery of cryosurgical refrigeration power to a probe or catheter.
  • BACKGROUND OF THE INVENTION
  • As the word itself indicates, “cryoablation” involves the freezing of material. Of importance here, at least insofar as the present invention is concerned, is the fact that cryoablation has been successfully used in various medical procedures. In this context, it has been determined that cryoablation procedures can be particularly effective for curing heart arrhythmias, such as atrial fibrillation.
  • It is believed that at least one-third of all atrial fibrillations originate near the ostia of the pulmonary veins, and that the optimal treatment technique is to treat these focal areas through the creation of circumferential lesions around the ostia of these veins. Heretofore, the standard ablation platform has been radiofrequency energy. Radiofrequency energy, however, is not amenable to safely producing circumferential lesions without the potential for serious complications. Specifically, while ablating the myocardial cells, heating energy also alters the extracellular matrix proteins, causing the matrix to collapse. This may be the center of pulmonary vein stenosis. Moreover, radiofrequency energy is known to damage the lining of the heart, which may account for thromboembolic complications, including stroke. Cryoablation procedures, however, may avoid many of these problems.
  • In a medical procedure, cryoablation begins at temperatures below approximately minus twenty degrees Centigrade (−20° C.). For the effective cryoablation of tissue, however, much colder temperatures are preferable. With this goal in mind, various fluid refrigerants (e.g. nitrous oxide N2O), which have normal boiling point temperatures as low as around minus eighty eight degrees Centigrade (−88° C.), are worthy of consideration. For purposes of the present invention, the normal boiling point temperature of a fluid is taken to be the temperature at which the fluid boils under one atmosphere of pressure. Temperature alone, however, is not the goal. Specifically, it is also necessary there be a sufficient refrigeration potential for freezing the tissue. In order for a system to attain and maintain a temperature, while providing the necessary refrigeration potential to effect cryoablation of tissue, several physical factors need to be considered. Specifically, these factors involve the thermodynamics of heat transfer.
  • It is well known that when a fluid boils (i.e. changes from a liquid state to a gaseous state) a significant amount of heat is transferred to the fluid. With this in mind, consider a liquid that is not boiling, but which is under a condition of pressure and temperature wherein effective evaporation of the liquid ceases. A liquid in such condition is commonly referred to as being “fully saturated”. It will then happen, as the pressure on the saturated liquid is reduced, the liquid tends to boil and extract heat from its surroundings. Initially, the heat that is transferred to the fluid is generally referred to as latent heat. More specifically, this latent heat is the heat that is required to change a fluid from a liquid to a gas, without any change in temperature. For most fluids, this latent heat transfer can be considerable and is subsumed in the notion of wattage. In context, wattage is the refrigeration potential of a system. Stated differently, wattage is the capacity of a system to extract energy at a fixed temperature.
  • An important consideration for the design of any refrigeration system is the fact that heat transfer is proportional to the difference in temperatures (ΔT) between the refrigerant and the body that is being cooled. Importantly, heat transfer is also proportional to the amount of surface area of the body being cooled (A) that is in contact with the refrigerant. In addition to the above considerations (i.e. ΔT and A); when the refrigerant is a fluid, the refrigeration potential of the refrigerant fluid is also a function of its mass flow rate. Specifically, the faster a heat-exchanging fluid refrigerant can be replaced (i.e. the higher its mass flow rate), the higher will be the refrigeration potential. This notion, however, has it limits.
  • As is well known, the mass flow rate of a fluid results from a pressure differential on the fluid. More specifically, it can be shown that as a pressure differential starts to increase on a refrigerant fluid in a system, the resultant increase in the mass flow rate of the fluid will also increase the refrigeration potential of the system. This increased flow rate, however, creates additional increases in the return pressure that will result in a detrimental increase in temperature. As is also well understood by the skilled artisan, this effect is caused by a phenomenon commonly referred to as “back pressure.” Obviously, an optimal operation occurs with the highest mass flow rate at the lowest possible temperature.
  • In light of the above, it is an object of the present invention to provide an open-cycle, or closed-cycle, refrigeration system for cooling the tip of a cryoablation catheter that provides a pre-cooling stage in the system to maximize the refrigeration potential of the refrigerant fluid at the tip of the catheter. Another object of the present invention is to provide a refrigeration system for cooling the tip of a cryoablation catheter that substantially maintains a predetermined pressure at the tip of the catheter to maximize the refrigeration potential of the refrigerant fluid at the tip. Still another object of the present invention is to provide a refrigeration system for cooling the tip of a cryoablation catheter that provides the maximum practical surface area for the tip that will maximize the ablation potential of the refrigerant fluid. Also, it is an object of the present invention to provide a refrigeration system for cooling the tip of a cryoablation catheter that is relatively easy to manufacture, is simple to use, and is comparatively cost effective.
  • SUMMARY OF THE PREFERRED EMBODIMENTS
  • In a cryosurgical system, contaminants such as oil, moisture, and other impurities are often deposited in the impedance tubing or other restriction through which the refrigerant is pumped. In the impedance tubing, the temperature is very low, and the flow diameter is very small. Deposit of these impurities can significantly restrict the flow of the cooling medium, thereby significantly reducing the cooling power.
  • A cryosurgical catheter used in a cardiac tissue ablation process should be able to achieve and maintain a low, stable, temperature. Stability is even more preferable in a catheter used in a cardiac signal mapping process. When the working pressure in a cryosurgery system is fixed, the flow rate can vary significantly when contaminants are present, thereby varying the temperature to which the probe and its surrounding tissue can be cooled. For a given cryosurgery system, there is an optimum flow rate at which the lowest temperature can be achieved, with the highest possible cooling power. Therefore, maintaining the refrigerant flow rate at substantially this optimum level is beneficial.
  • In either the ablation process or the mapping process, it may be beneficial to monitor the flow rates, pressures, and temperatures, to achieve and maintain the optimum flow rate. Further, these parameters can be used to more safely control the operation of the system.
  • A cryosurgical system which is controlled based only upon monitoring of the refrigerant pressure and catheter temperature may be less effective at maintaining the optimum flow rate, especially when contaminants are present in the refrigerant. Further, a system in which only the refrigerant pressure is monitored may not have effective safety control, such as emergency shut down control.
  • It may also be more difficult to obtain the necessary performance in a cryosurgery catheter in which only a single compressor is used as a refrigeration source. This is because it can be difficult to control both the low and high side pressures at the most effective levels, with any known compressor. Therefore, it can be beneficial to have separate low side and high side pressure control in a cryosurgical system.
  • Finally, it is beneficial to have a system for monitoring various parameters of data in a cryosurgery system over a period of time. Such parameters would include catheter temperature, high side refrigerant pressure, low side refrigerant pressure, and refrigerant flow rate. Continuous historical and instantaneous display of these parameters, and display of their average values over a selected period of time, can be very helpful to the system operator.
  • The present invention provides methods and apparatus for controlling the operation of a cryosurical catheter refrigeration system by monitoring pressures, temperature, and/or flow rate, in order to automatically maintain a stable refrigerant flow rate at or near an optimum level for the performance of crysurgical tissue ablation or mapping. Different refrigerant flow rates can be selected as desired for ablation or mapping. Flow rate, pressures, and temperature can be used for automatic shut down control. Refrigerant sources which provide separate high side and low side pressure controls add to the performance of the system. Continuous displays of temperature, high side refrigerant pressure, low side refrigerant pressure, and refrigerant flow rate are provided to the operator on a single display, to enhance system efficiency and safety.
  • A refrigeration system (open-cycle, or closed-cycle) for cooling the tip of a cryoablation catheter includes a source for a primary fluid refrigerant, such as nitrous oxide (N2O). Initially, the primary fluid is held under pressure (e.g. 750 psia) at ambient temperature (e.g. room temperature). A pressure regulator is connected in fluid communication with the primary fluid source for reducing the pressure on the primary fluid down to a working pressure (e.g. approximately 400 psia). During this pressure reduction to the working pressure, the primary fluid remains at substantially the ambient temperature.
  • After pressure on the primary fluid has been reduced to the working pressure, a precooler is used to pre-cool the primary fluid from the ambient temperature. This is done while substantially maintaining the primary fluid at the working pressure. Importantly, at the precooler, the primary fluid is converted into a fully saturated liquid which has been pre-cooled to a sub-cool temperature. As used here, a sub-cool temperature is one that is below the temperature at which, for a given pressure, the fluid becomes fully saturated. For example, when nitrous oxide is to be used, the preferred sub-cool temperature will be equal to approximately minus forty degrees Centigrade (Tsc=−40° C.).
  • Structurally, the precooler is preferably a closed-cycle refrigeration unit that includes an enclosed secondary fluid (e.g. a freon gas). Additionally, the precooler includes a compressor for increasing the pressure on the secondary fluid to a point where the secondary fluid becomes a liquid. Importantly, for whatever secondary fluid is used, it should have a normal boiling point that is near to the preferred sub-cool temperature of the primary fluid (Tsc). The secondary fluid is then allowed to boil, and to thereby pre-cool the primary fluid in the system to its sub-cool temperature (Tsc). As a closed-cycle unit, the secondary fluid is recycled after it has pre-cooled the primary fluid.
  • The cryoablation catheter for the system of the present invention essentially includes a capillary tube that is connected with, and extends coaxially from a supply tube. Together, the connected supply and capillary tubes are positioned in the lumen of a catheter tube and are oriented coaxially with the catheter tube. More specifically, the supply tube and the capillary tube each have a distal end and a proximal end and, in combination, the proximal end of the capillary tube is connected to the distal end of the supply tube to establish a supply line for the catheter.
  • For the construction of the cryoablation catheter, the supply tube and the capillary tube are concentrically (coaxially) positioned inside the lumen of the catheter tube. Further, the distal end of the capillary tube (i.e. the distal end of the supply line) is positioned at a closed-in tip section at the distal end of the catheter tube. Thus, in addition to the supply line, this configuration also defines a return line in the lumen of the catheter tube that is located between the inside surface of that catheter tube and the supply line. In particular, the return line extends from the tip section at the distal end of the catheter tube, back to the proximal end of the catheter tube.
  • Insofar as the supply line is concerned, it is an important aspect of the present invention that the impedance to fluid flow of the primary refrigerant in the supply line be relatively low through the supply tube, as compared with the impedance presented by the capillary tube. Stated differently, it is desirable for the pressure drop, and consequently the temperature reduction, on the primary refrigerant be minimized as it traverses the supply tube. On the other hand, the pressure drop and temperature reduction on the primary refrigerant should be maximized as the refrigerant traverses the capillary tube. Importantly, the physical dimensions of the supply tube, of the capillary tube, and of the catheter tube can be engineered to satisfy these requirements. It is also desirable to engineer the length of the capillary tube so that gases passing from the tip section, back through the return line do not impermissibly warm the capillary tube. By balancing these considerations, the dimensions of the supply line, the tip section and the return line, can all be predetermined.
  • As the fluid refrigerant is transferred from its source to the catheter supply line, it passes through the precooler. During this transfer, a control valve(s) is used to establish a working pressure (pw) for the refrigerant. Also, a pressure sensor is provided to monitor the working pressure on the primary fluid refrigerant before the refrigerant enters the supply line at the proximal end of the catheter.
  • On the return side of the system, an exhaust unit is provided for removing the primary fluid from the tip section of the catheter. For the present invention, this exhaust unit consists of a vacuum pump that is attached in fluid communication with the return line at the proximal end of the catheter tube. A pressure sensor is also provided at this point to determine the pressure in the return line at the proximal end of the catheter tube (pr).
  • In accordance with well known thermodynamic principles, when pressures at specific points in a system are known, fluid pressures at various other points in the system can be determined. For the present invention, because the supply line and return line are contiguous and have known dimensions, because “pw” (working pressure) and “pr” (return line pressure) can be determined and, further, because the fluid refrigerant experiences a phase change during the transition from pw to pr, it is possible to calculate pressures on the fluid refrigerant at points between the proximal end of the supply tube (inlet) and the proximal end of the catheter tube (outlet). In particular, it is possible to calculate an outflow pressure (po) for the fluid refrigerant as it exits from the distal end of the capillary tube into the tip section of the catheter.
  • The outflow pressure (po) for the fluid refrigerant can be determined in ways other than as just mentioned above. For one, a pressure sensor can be positioned in the tip section of the catheter near the distal end of the capillary tube to measure the outflow pressure (po) directly. Additionally, the system of the present invention can include a temperature sensor that is positioned in the tip section of the catheter to monitor the temperature of the primary fluid refrigerant in the tip section (Tt). Specifically, when this temperature (Tt) is measured as the primary fluid refrigerant is boiling (i.e. as it enters the tip section from the capillary tube), it is possible to directly calculate the outflow pressure (po) using well known thermodynamic relationships.
  • A computer is used with the system of the present invention to monitor and control the operational conditions of the system. Specifically, the computer is connected to the appropriate sensors that monitor actual values for “pr” and “pw”. The values for “pr” and “pw” can then be used to determine the outflow pressure “po” in the tip section of the catheter (for one embodiment of the present invention, “po” is also measured directly). Further, the computer is connected to the control valve to manipulate the control valve and vary the working pressure (pw) on the primary fluid. At the same time, the computer can monitor the temperature in the tip section of the catheter (Tt) to ensure that changes in the working pressure “pw” result in appropriate changes in “Tt”. Stated differently, the computer can monitor conditions to ensure that an unwanted increase in “back pressure,” that would be caused by an inappropriate increase in “pw” does not result in an increase in “Tt”. The purpose here is to maintain the outflow pressure (po) in the tip section of the catheter at a desired value (e.g. 15 psia).
  • In operation, the sub-cooled primary fluid is introduced into the proximal end of the capillary tube at substantially the working pressure (pw). The primary fluid then traverses the capillary tube for outflow from the distal end of the capillary tube at the outflow pressure (po). Importantly, in the capillary tube the fluid refrigerant is subjected to a pressure differential (Δp). In this case, “Δp” is substantially the difference between the working pressure (pw) on the primary fluid as it enters the proximal end of the capillary tube (e.g. 300 psi), and a substantially ambient pressure (i.e. po) as it outflows from the distal end of the capillary tube (e.g. one atmosphere, 15 psi)(Δp=pw−po). In particular, as the pre-cooled primary fluid passes through the capillary tube, it transitions from a sub-cool temperature that is equal to approximately minus forty degrees Centigrade (Tsc≅−40° C.), to approximately its normal boiling point temperature. As defined above, the normal boiling point temperature of a fluid is taken to be the temperature at which the fluid boils under one atmosphere of pressures. In the case of nitrous oxide, this will be a cryoablation temperature that is equal to approximately minus eighty-eight degrees Centigrade (Tca≅−88° C.). The heat that is absorbed by the primary fluid as it boils, cools the tip section of the catheter.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • The novel features of this invention, as well as the invention itself, both as to its structure and its operation, will be best understood from the accompanying drawings, taken in conjunction with the accompanying description, in which similar reference characters refer to similar parts, and in which:
  • FIG. 1 is a schematic of a first embodiment of the apparatus of the present invention, using a pressure bottle as the primary refrigerant source;
  • FIG. 2 is a schematic of a second embodiment of the apparatus of the present invention, using a compressor as the primary refrigerant source;
  • FIG. 3 is a schematic of a third embodiment of the apparatus of the present invention, using two compressors connected in series as the primary refrigerant source;
  • FIG. 4 is a schematic of a first embodiment of a control system apparatus according to the present invention, for use with the apparatus shown in FIG. 1;
  • FIG. 5 is a schematic of a second embodiment of a control system apparatus according to the present invention, for use with the apparatus shown in FIG. 2 or 3;
  • FIG. 6 is a schematic of a parameter display for use with the control equipment of the present invention; and
  • FIG. 7 is a flow diagram showing one control sequence for use with the control apparatus of the present invention.
  • FIG. 8 is a perspective view of the system of the present invention;
  • FIG. 9 is a cross-sectional view of the catheter of the present invention as seen along the line 2-2 in FIG. 8;
  • FIG. 10 is a schematic view of the computer and its interaction with system components and sensors for use in the control of a cryoablation procedure;
  • FIG. 11 is a schematic view of the interactive components in the console of the present invention;
  • FIG. 12 is a pressure-temperature diagram (not to scale) graphing an open-cycle operation for a refrigerant fluid in accordance with the present invention; and
  • FIG. 13 is a diagram (not to scale) showing the tendency for changes in temperature response to changes of fluid mass flow rate in a catheter environment as provided by the present invention.
  • DETAILED DESCRIPTION OF THE INVENTION
  • According to certain embodiments of the invention, the refrigeration system may be a two stage Joule-Thomson system with a closed loop precool circuit and either an open loop or a closed loop primary circuit. A typical refrigerant for the primary circuit would be R-508b, and a typical refrigerant for the precool circuit would be R-410a. In the ablation mode, the system may be capable of performing tissue ablation at or below minus 70.degree. C. while in contact with the tissue and circulating blood. In the mapping mode, the system may be capable of mapping by stunning the tissue at a temperature between minus 10.degree. C. and minus 18.degree. C. while in contact with the tissue and circulating blood. These performance levels may be achieved while maintaining the catheter tip pressure at or below a sub-diastolic pressure of 14 psia.
  • As shown in FIG. 1, one embodiment of the apparatus 10 of the present invention is an open loop system using a pressure bottle for the refrigerant source. Such a system can include a primary refrigerant supply bottle 200, a primary refrigerant fluid controller 208, a catheter 300, a primary refrigerant recovery bottle 512, a secondary refrigerant compressor 100, a precool heat exchanger 114, and various sensors. In certain embodiments, all but the catheter 300 and the precool heat exchanger 114 may be located in a cooling console housing. The precool heat exchanger 114 is connected to the console by flexible lines 121, 221. Pressure of the refrigerant in the primary refrigerant supply bottle 200 is monitored by a primary refrigerant supply pressure sensor 202. Output of primary refrigerant from the supply bottle 200 is regulated by a pressure regulator 204, which, in certain embodiments, can receive refrigerant from the bottle 200 at a pressure above 350 psia and regulate it to less than 350 psia. A primary refrigerant relief valve 206 is provided to prevent over pressurization of the primary system downstream of the pressure regulator 204, for example, above 400 psia. The flow rate of primary refrigerant is controlled by the fluid controller 208, which can be either a pressure controller or a flow controller. A feedback loop may be provided to control the operation of the fluid controller 208. The feedback signal for the fluid controller 208 can come from a pressure sensor 310 or a flow sensor 311, on the effluent side of the catheter 300, discussed below.
  • A primary refrigerant high pressure sensor 210 is provided downstream of the fluid controller 208, to monitor the primary refrigerant pressure applied to the precool heat exchanger 114. The high pressure side 212 of the primary loop passes through the primary side of the cooling coil of the precool heat exchanger 114, then connects to a quick connect fitting 304 on the precool heat exchanger 114. Similarly, the low side quick connect fitting 304 on the precool heat exchanger 114 is connected to the low pressure side 412 of the primary loop, which passes back through the housing of the precool heat exchanger 114, without passing through the cooling coil, and then through the flow sensor 311. The catheter tip pressure sensor 310 monitors catheter effluent pressure in the tip of the catheter 300. The control system maintains catheter tip pressure at a sub-diastolic level at all times.
  • The low pressure side 412 of the primary loop can be connected to the inlet 402 of a vacuum pump 400. A primary refrigerant low pressure sensor 410 monitors pressure in the low side 412 of the primary loop downstream of the precool heat exchanger 114. The outlet 404 of the vacuum pump 400 can be connected to the inlet 502 of a recovery pump 500. A 3 way, solenoid operated, recovery valve 506 is located between the vacuum pump 400 and the recovery pump 500. The outlet 504 of the recovery pump 500 is connected to the primary refrigerant recovery bottle 512 via a check valve 508. A primary refrigerant recovery pressure sensor 510 monitors the pressure in the recovery bottle 512. A 2 way, solenoid operated, bypass valve 406 is located in a bypass loop 407 between the low side 412 of the primary loop upstream of the vacuum pump 400 and the high side 212 of the primary loop downstream of the fluid controller 208. A solenoid operated bypass loop vent valve 408 is connected to the bypass loop 407.
  • In the catheter 300, the high pressure primary refrigerant flows through an impedance device such as a capillary tube 306, then expands into the distal portion of the catheter 300, where the resultant cooling is applied to surrounding tissues. A catheter tip temperature sensor 307, such as a thermocouple, monitors the temperature of the distal portion of the catheter 300. A catheter return line 308 returns the effluent refrigerant from the catheter 300 to the precool heat exchanger 114. The high and low pressure sides of the catheter 300 are connected to the heat exchanger quick connects 304 by a pair of catheter quick connects 302. As an alternative to pairs of quick connects 302, 304, coaxial quick connects can be used. In either case, the quick connects may carry both refrigerant flow and electrical signals.
  • In the precool loop, compressed secondary refrigerant is supplied by a precool compressor 100. An after cooler 106 can be connected to the outlet 104 of the precool compressor 100 to cool and condense the secondary refrigerant. An oil separator 108 can be connected in the high side 117 of the precool loop, with an oil return line 110 returning oil to the precool compressor 100. A high pressure precooler pressure sensor 112 senses pressure in the high side 117 of the precool loop. The high side 117 of the precool loop is connected to an impedance device such as a capillary tube 116 within the housing of the precool heat exchanger 114. High pressure secondary refrigerant flows through the capillary tube 116, then expands into the secondary side of the cooling coil of the precool heat exchanger 114, where it cools the high pressure primary refrigerant. The effluent of the secondary side of the precool heat exchanger 114 returns via the low side 118 of the precool loop to the inlet 102 of the precool compressor 100. A low pressure precooler pressure sensor 120 senses pressure in the low side 118 of the precool loop.
  • Instead of using primary refrigerant supply and return bottles, the apparatus can use one or more primary compressors in a closed loop system. FIG. 2 shows a second embodiment of the apparatus of the present invention, with a single compressor system. This embodiment would be appropriate in applications where the high side and low side pressures can be adequately controlled with a single compressor. In the apparatus 10′ of this type of system, the low side 622 of the primary loop conducts the effluent of the catheter 300 to the inlet 602 of a primary refrigerant compressor 600. The compressor 600 compresses the primary refrigerant, and returns it from the compressor outlet 604 via the high side 612 of the primary loop to the primary side of the precool heat exchanger 114. A primary refrigerant high pressure sensor 614 is provided in the high side 612 of the primary loop, to monitor the primary refrigerant pressure applied to the precool heat exchanger 114. A primary refrigerant high pressure flow sensor 312 can be provided in the high side 612 of the primary loop. A primary refrigerant low pressure sensor 610 monitors pressure in the low side 622 of the primary loop downstream of the precool heat exchanger 114. A primary loop filter 608 can be provided in the low side 622 of the primary loop. A 2 way, solenoid operated, primary refrigerant charge valve 626 and a primary refrigerant reservoir 628 can be provided in the low side 622 of the primary loop. A high pressure after-cooler 605 can be provided downstream of the primary refrigerant compressor 600.
  • As further shown in FIG. 2, a 2 way, solenoid operated, primary loop bypass valve 606 is located in a bypass loop 607 between the low side 622 of the primary loop upstream of the compressor 600 and the high side 612 of the primary loop downstream of the compressor 600. Opening of the primary loop bypass valve 606 can facilitate startup of the primary compressor 600. A precool loop filter 101 can be provided in the low side 118 of the precool loop. Further, a 2 way, solenoid operated, precool loop bypass valve 111 is located in a bypass loop 119 between the low side 118 of the precool loop upstream of the compressor 100 and the high side 117 of the precool loop downstream of the compressor 100. Opening of the precool loop bypass valve 111 can facilitate startup of the precool compressor 100.
  • A purification system 900 can be provided for removing contaminants from the primary refrigerant and the secondary refrigerant. Solenoid operated 3 way purification valves 609, 611 are provided in the high side and low side, respectively, of the primary loop, for selectively directing the primary refrigerant through the purification system 900. Similarly, solenoid operated 3 way purification valves 115, 113 are provided in the high side and low side, respectively, of the precool loop, for selectively directing the secondary refrigerant through the purification system 900.
  • The remainder of the precool loop, the precool heat exchanger 114, and the catheter 300 are the same as discussed above for the first embodiment.
  • In applications where separate low side and high side pressure control is required, but where a closed loop system is desired, a two compressor primary system may be used. FIG. 3 shows a third embodiment of the apparatus of the present invention, with a dual compressor system. In the apparatus 10″ of this type of system, the low side 622 of the primary loop conducts the effluent of the catheter 300 to the inlet 616 of a low side primary refrigerant compressor 618. The low side compressor 618 compresses the primary refrigerant, and provides it via its outlet 620 to the inlet 602 of a high side primary refrigerant compressor 600. A low pressure after-cooler 623 can be provided downstream of the low side compressor 618. The high side compressor 600 further compresses the primary refrigerant to a higher pressure and returns it via its outlet 604 and via the high side 612 of the primary loop to the primary side of the precool heat exchanger 114. A primary refrigerant high pressure sensor 614 is provided in the high side 612 of the primary loop, to monitor the high side primary refrigerant pressure upstream of the precool heat exchanger 114. A primary refrigerant low pressure sensor 610 monitors pressure in the low side 622 of the primary loop downstream of the precool heat exchanger 114. A primary refrigerant intermediate pressure sensor 624 monitors pressure between the outlet 620 of the low side compressor 618 and the inlet 602 of the high side compressor 600. The high side compressor 600 and the low side compressor 618 are separately controlled, using feedback from the catheter tip pressure sensor 310 and/or the flow sensors 311, 312.
  • As further shown in FIG. 3, a 3 way, solenoid operated, bypass valve 606′ is located in a bypass loop 607 between the low side 622 of the primary loop upstream of the low side compressor 618 and the high side 612 of the primary loop downstream of the high side compressor 600. A third port is connected between the high side and low side compressors. The precool loop, the precool heat exchanger 114, and the catheter 300 are the same as discussed above for the first and second embodiments.
  • FIG. 4 shows a control diagram which would be suitable for use with the apparatus shown in FIG. 1. A computerized automatic control system 700 is connected to the various sensors and control devices to sense and control the operation of the system, and to provide safety measures, such as shut down schemes. More specifically, on the sensing side, the low pressure precool sensor 120 inputs low side precool pressure PA, the high pressure precool sensor 112 inputs high side precool pressure PB, the primary supply pressure sensor 202 inputs supply bottle pressure P1, the primary recovery pressure sensor 510 inputs recovery bottle pressure P2, the high pressure primary sensor 210 inputs high side primary pressure P3, the low pressure primary sensor 410 inputs low side primary pressure P4, the catheter tip pressure sensor 310 inputs catheter tip pressure P5, the temperature sensor 307 inputs catheter tip temperature T, and the flow sensor 311 inputs primary refrigerant flow rate F. Further, on the control side, the control system 700 energizes the normally closed bypass valve 406 to open it, energizes the normally open vent valve 408 to close it, and energizes the recovery valve 506 to connect the vacuum pump outlet 404 to the recovery pump inlet 502. Finally, the control system 700 provides a pressure set point SPP or flow rate set point SPF to the fluid controller 208, depending upon whether it is a pressure controller or a flow controller.
  • FIG. 5 shows a control diagram which would be suitable for use with the apparatus shown in FIG. 2 or FIG. 3. A computerized automatic control system 700 is connected to the various sensors and control devices to sense and control the operation of the system, and to provide safety measures, such as shut down schemes. More specifically, on the sensing side, the low pressure precool sensor 120 inputs low side precool pressure PA, the high pressure precool sensor 112 inputs high side precool pressure PB, the high pressure primary sensor 614 inputs high side primary pressure P3, the low pressure primary sensor 610 inputs low side primary pressure P4, the catheter tip pressure sensor 310 inputs catheter tip pressure P5, the temperature sensor 307 inputs catheter tip temperature T, and the flow sensors 311, 312 input primary refrigerant flow rate F. Further, on the control side, the control system 700 energizes the normally closed primary loop bypass valve 606, 606′ to open it, and the control system 700 energizes the normally closed precool loop bypass valve 111 to open it. The control system 700 also energizes the primary loop purification valves 609, 611 to selectively purify the primary refrigerant, and the control system 700 energizes the precool loop purification valves 113, 115 to selectively purify the secondary refrigerant. Finally, the control system 700 provides a minimum high side pressure set point PL2 to the controller 601 of the primary compressor 600 in the system shown in FIG. 2. Alternatively, in the system shown in FIG. 3, the control system 700 provides a minimum high side pressure set point PL2B to the controller 601 of the high side primary compressor 600, and the control system 700 provides a maximum low side pressure set point PL2A to the controller 619 of the low side primary compressor 618.
  • A numeric digital display, or a graphical display similar to that shown in FIG. 6, is provided on the cooling console to assist the operator in monitoring and operating the system. For example, on a single graphical display, graphs can be shown of catheter tip temperature T, high side primary pressure P3, low side primary pressure P4, and primary flow rate F, all versus time. Further, on the same display, the operator can position a vertical cursor at a selected time, resulting in the tabular display of the instantaneous values of T, P3, P4, and F, as well as the average, maximum, and minimum values of these parameters.
  • The present invention will now be further illustrated by describing a typical operational sequence of the open loop embodiment, showing how the control system 700 operates the remainder of the components to start up the system, to provide the desired refrigeration power, and to provide system safety. The system can be operated in the Mapping Mode, where the cold tip temperature might be maintained at minus 10 C., or in the Ablation Mode, where the cold tip temperature might be maintained at minus 65 C. Paragraphs are keyed to the corresponding blocks in the flow diagram shown in FIG. 7. Suggested exemplary Pressure Limits used below could be PL1=160 psia; PL2=400 psia; PL3=500 psia; PL4=700 psia; PL5=600 psia; PL6=5 psia; PL7=diastolic pressure; PL8=375 psia; and PL9=5 psia. Temperature limits, flow limits, procedure times, and procedure types are set by the operator according to the procedure being performed.
  • Perform self tests (block 802) of the control system circuitry and connecting circuitry to the sensors and controllers to insure circuit integrity.
  • Read and store supply cylinder pressure P1, primary low pressure P4, and catheter tip pressure P5 (block 804). At this time, P4 and P5 are at atmospheric pressure. If P1 is less than Pressure Limit PL2 (block 808), display a message to replace the supply cylinder (block 810), and prevent further operation. If P1 is greater than PL2, but less than Pressure Limit PL3, display a message to replace the supply cylinder soon, but allow operation to continue.
  • Read precool charge pressure PB and recovery cylinder pressure P2 (block 806). If PB is less than Pressure Limit PL1 (block 808), display a message to service the precool loop (block 810), and prevent further operation. If P2 is greater than Pressure Limit PL4 (block 808), display a message to replace the recovery cylinder (block 810), and prevent further operation. If P2 is less than PL4, but greater than Pressure Limit PL5, display a message to replace the recovery cylinder soon, but allow operation to continue.
  • Energize the bypass loop vent valve 408 (block 812). The vent valve 408 is a normally open two way solenoid valve open to the atmosphere. When energized, the vent valve 408 is closed.
  • Start the precool compressor 100 (block 814). Display a message to attach the catheter 300 to the console quick connects 304 (block 816). Wait for the physician to attach the catheter 300, press either the Ablation Mode key or the Mapping Mode key, and press the Start key (block 818). Read the catheter tip temperature T and the catheter tip pressure P5. At this time, T is the patient's body temperature and P5 is atmospheric pressure.
  • Energize the bypass loop valve 406, while leaving the recovery valve 506 deenergized (block 820). The bypass valve 406 is a normally closed 2 way solenoid valve. Energizing the bypass valve 406 opens the bypass loop. The recovery valve 506 is a three way solenoid valve that, when not energized, opens the outlet of the vacuum pump 400 to atmosphere. Start the vacuum pump 400 (block 822). These actions will pull a vacuum in the piping between the outlet of the fluid controller 208 and the inlet of the vacuum pump 400, including the high and low pressure sides of the catheter 300. Monitor P3, P4, and P5 (block 824), until all three are less than Pressure Limit PL6 (block 826).
  • Energize the recovery valve 506 and the recovery pump 500 (block 828). When energized, the recovery valve 506 connects the outlet of the vacuum pump 400 to the inlet of the recovery pump 500. De-energize the bypass valve 406, allowing it to close (block 830). Send either a pressure set point SPP (if a pressure controller is used) or a flow rate set point SPF (if a flow controller is used) to the fluid controller 208 (block 832). Where a pressure controller is used, the pressure set point SPP is at a pressure which will achieve the desired refrigerant flow rate, in the absence of plugs or leaks. The value of the set point is determined according to whether the physician has selected the mapping mode or the ablation mode. These actions start the flow of primary refrigerant through the catheter 300 and maintain the refrigerant flow rate at the desired level.
  • Continuously monitor and display procedure time and catheter tip temperature T (block 834). Continuously monitor and display all pressures and flow rates F (block 836). If catheter tip pressure P5 exceeds Pressure Limit PL7, start the shutdown sequence (block 840). Pressure Limit PL7 is a pressure above which the low pressure side of the catheter 300 is not considered safe.
  • If F falls below Flow Limit FL1, and catheter tip temperature T is less than Temperature Limit TL1, start the shutdown sequence (block 840). Flow Limit FL1 is a minimum flow rate below which it is determined that a leak or a plug has occurred in the catheter 300. FL1 can be expressed as a percentage of the flow rate set point SPF. Temperature Limit TL1 is a temperature limit factored into this decision step to prevent premature shutdowns before the catheter 300 reaches a steady state at the designed level of refrigeration power. So, if catheter tip temperature T has not yet gone below TL1, a low flow rate will not cause a shutdown.
  • If P3 exceeds Pressure Limit PL8, and F is less than Flow Limit FL2, start the shutdown sequence (block 840). PL8 is a maximum safe pressure for the high side of the primary system. Flow Limit FL2 is a minimum flow rate below which it is determined that a plug has occurred in the catheter 300, when PL8 is exceeded. FL2 can be expressed as a percentage of the flow rate set point SPF.
  • If P4 is less than Pressure Limit PL9, and F is less than Flow Limit FL3, start the shutdown sequence (block 840). PL9 is a pressure below which it is determined that a plug has occurred in the catheter 300, when flow is below FL3. FL3 can be expressed as a percentage of the flow rate set point SPF.
  • An exemplary shutdown sequence will now be described. Send a signal to the fluid controller 208 to stop the primary refrigerant flow (block 840). Energize the bypass valve 406 to open the bypass loop (block 842). Shut off the precool compressor 100 (block 844). Continue running the vacuum pump 400 to pull a vacuum between the outlet of the fluid controller 208 and the inlet of the vacuum pump 400 (block 846). Monitor primary high side pressure P3, primary low side pressure P4, and catheter tip pressure P5 (block 848) until all three are less than the original primary low side pressure which was read in block 804 at the beginning of the procedure (block 850). Then, de-energize the recovery pump 500, recovery valve 506, vent valve 408, bypass valve 406, and vacuum pump 400 (block 852). Display a message suggesting the removal of the catheter 300, and update a log of all system data (block 854).
  • Similar operational procedures, safety checks, and shutdown procedures would be used for the closed loop primary system shown in FIG. 2 or FIG. 3, except that the primary compressor 600 or compressors 600, 618 would provide the necessary primary refrigerant flow rate in place of the supply and recovery cylinders, the fluid controller, and the vacuum and recovery pumps. As with the open loop system, the closed loop system can be operated in the Mapping Mode, where the cold tip temperature might be maintained at minus 10 C., or in the Ablation Mode, where the cold tip temperature might be maintained at minus 65 C. As a first option to achieve the desired cold tip temperature, the precool bypass valve 111 can be adjusted to control the liquid fraction resulting after expansion of the secondary refrigerant, thereby adjusting the refrigeration capacity. Under this option, primary refrigerant high and low pressures are kept constant. As a second option, or in combination with the first option, primary refrigerant flow rate can be by means of operating controllers 601, 619 on the primary compressors 600, 618 to maintain a high pressure set point SPP which will achieve the desired flow rate, resulting in the desired cold tip temperature.
  • A Service Mode is possible, for purification of the primary and secondary refrigerants. In the Service Mode, the normally open bypass valves 111, 606 are energized to close. The primary loop purification valves 609, 611 are selectively aligned with the purification system 900 to purify the primary refrigerant, or the precool loop purification valves 113, 115 are selectively aligned with the purification system 900 to purify the secondary refrigerant.
  • In either the Mapping Mode or the Ablation Mode, the desired cold tip temperature control option is input into the control system 700. Further, the type of catheter is input into the control system 700. The normally closed charge valve 626 is energized as necessary to build up the primary loop charge pressure. If excessive charging is required, the operator is advised. Further, if precool loop charge pressure is below a desired level, the operator is advised.
  • When shutdown is required, the primary loop high side purification valve 609 is closed, and the primary loop compressors 600, 618 continue to run, to draw a vacuum in the catheter 300. When the desired vacuum is achieved, the primary loop low side purification valve 611 is closed. This isolates the primary loop from the catheter 300, and the disposable catheter 300 can be removed.
  • Referring to FIG. 8, a system for performing cryoablation procedures is shown and generally designated 910. As shown, the system 910 includes a cryoablation catheter 912 and a primary fluid source 914. Preferably, the primary fluid is nitrous oxide (N2O) and is held in source 914 at a pressure of around 750 psig. FIG. 8 also shows that the system 910 includes a console 916 and that the console 916 is connected in fluid communication with the primary fluid source 914 via a fluid line 918. Console 916 is also connected in fluid communication with the catheter 912 via a fluid line 920. Further, the console 916 is shown to include a precooler 922, an exhaust unit 924, and a computer 926.
  • In detail, the components of the catheter 912 will be best appreciated with reference to FIG. 9. There, it will be seen that the catheter 912 includes a catheter tube 928 that has a closed distal end 930 and an open proximal end 932. Also included as part of the catheter 912, are a supply tube 934 that has a distal end 936 and a proximal end 938, and a capillary tube 940 that has a distal end 942 and a proximal end 944. As shown, the distal end 936 of supply tube 934 is connected with the proximal end 944 of the capillary tube 940 to establish a supply line 946. Specifically, supply line 946 is defined by the lumen 948 of supply tube 934 and the lumen 950 of capillary tube 940. It is an important aspect of the system 910 that the diameter (i.e. cross section) of the supply tube 934 is greater than the diameter (i.e. cross section) of the capillary tube 940. The consequence of this difference is that the supply tube 934 presents much less impedance to fluid flow than does the capillary tube 940. In turn, this causes a much greater pressure drop for fluid flow through the capillary tube 940. As will be seen, this pressure differential is used to advantage for the system 910.
  • Still referring to FIG. 9, it is seen that the supply line 946 established by the supply tube 934 and capillary tube 940, is positioned coaxially in the lumen 952 of the catheter tube 928. Further, the distal end 942 of the capillary tube 940 (i.e. also the distal end of the supply line 946) is displaced from the distal end 930 of catheter tube 928 to create an expansion chamber 954 in the tip section 956 of the catheter 912. Additionally, the placement of the supply line 946 in the lumen 952 establishes a return line 958 in the catheter 912 that is located between the supply line 946 and the wall of the catheter tube 928.
  • Optionally, a sensor 960 can be mounted in expansion chamber 954 (tip section 956). This sensor 960 may be either a temperature sensor or a pressure sensor, or it may include both a temperature and pressure sensor. In any event, if used, the sensor 960 can be of a type well known in the art for detecting the desired measurement. Although FIG. 9 shows both a pressure sensor 962 and a valve 964 positioned at the proximal end 938 of the supply tube 934, this is only exemplary as the sensor 962 and valve 964 may actually be positioned elsewhere. The import here is that a pressure sensor 962 is provided to monitor a working fluid pressure, “pw,” on a fluid refrigerant (e.g. N2O). In turn, this pressure “pw” is controlled by a valve 964 as it enters the inlet 966 of the supply line 946. Further, FIG. 9 shows that a pressure sensor 968 is provided to monitor a return pressure “pr” on the fluid refrigerant as it exits from the outlet 970 of the return line 958.
  • FIG. 10 indicates that the various sensors mentioned above are somehow electronically connected to the computer 926 in console 916. More specifically, the sensors 960, 962 and 968 can be connected to computer 926 in any of several ways, all known in the pertinent art. Further, FIG. 10 indicates that the computer 926 is operationally connected with the valve 964. The consequence of this is that the computer 926 can be used to control operation of the valve 964, and thus the working pressure “pw”, in accordance with preprogrammed instructions, using measurements obtained by the sensors 960, 962 and 968 (individually or collectively).
  • A schematic of various components for system 910 is presented in FIG. 11 which indicates that a compressor 972 is incorporated as an integral part of the precooler 922. More specifically, the compressor 972 is used to compress a secondary fluid refrigerant (e.g. Freon) into its liquid phase for subsequent cooling of the primary refrigerant in the precooler 922. For purposes of the present invention, the secondary fluid refrigerant will have a normal boiling point that is at a temperature sufficiently low to take the primary fluid refrigerant to a sub-cool condition (i.e. below a temperature where the primary fluid refrigerant will be fully saturated). For the present invention, wherein the primary fluid refrigerant is nitrous oxide, the temperature is preferably around minus forty degrees Centigrade (Tsc=−40° C.).
  • The operation of system 910 will be best appreciated by cross referencing FIG. 11 with FIG. 12. During this cross referencing, recognize that the alphabetical points (A, B, C, D and E), shown relative to the curve 974 in FIG. 12, are correspondingly shown on the schematic for system 910 in FIG. 11. Further, appreciate that curve 974, which is plotted for variations of pressure (P) and temperature (T), represents the fully saturated condition for the primary fluid refrigerant (e.g. nitrous oxide). Accordingly, the area 976 represents the liquid phase of the refrigerant, and area 978 represents the gaseous phase of the refrigerant.
  • Point A (FIG. 11 and FIG. 12) represents the primary fluid refrigerant as it is drawn from the fluid source 914, or its back up source 914″. Preferably, point A corresponds to ambient temperature (i.e. room temperature) and a pressure greater than around 700 psig. After leaving the fluid source 914, the pressure on the refrigerant is lowered to a working pressure “pw” that is around 400 psig. This change is controlled by the regulator valve 964, is monitored by the sensor 962, and is represented in FIG. 12 as the change from point A to point B. The condition at point B corresponds to the condition of the primary refrigerant as it enters the precooler 922.
  • In the precooler 922, the primary refrigerant is cooled to a sub-cool temperature “Tsc” (e.g. −40° C.) that is determined by the boiling point of the secondary refrigerant in the precooler 922. In FIG. 12 this cooling is represented by the transition from point B to point C. Note that in this transition, as the primary fluid refrigerant passes through the precooler 922, it changes from a gaseous state (area 978) into a liquid state (area 976). Point C in FIG. 12 represents the condition of the primary fluid refrigerant as it enters the supply line 946 of cryocatheter 12 at the proximal end 938 of supply tube 934. Specifically, the pressure on the primary fluid refrigerant at this point C is the working pressure “pw”, and the temperature is the sub-cool temperature “Tsc”.
  • As the primary fluid refrigerant passes through the supply line 946 of catheter 12, its condition changes from the indications of point C, to those of point D. Specifically, for the present invention, point D is identified by a temperature of around minus eighty eight degrees Centigrade (−88° C.) and an outlet pressure “po” that is close to 15 psia. Further, as indicated in FIG. 11, point D identifies the conditions of the primary fluid refrigerant after it has boiled in the tip section 956 as it is leaving the supply line 946 and entering the return line 958 of the catheter 12.
  • The exhaust unit 924 of the catheter 912 is used to evacuate the primary fluid refrigerant from the expansion chamber 954 of tip section 956 after the primary refrigerant has boiled. During this evacuation, the conditions of the primary refrigerant change from point D to point E. Specifically, the conditions at point E are such that the temperature of the refrigerant is an ambient temperature (i.e. room temperature) and it has a return pressure “pr”, measured by the sensor 968, that is slightly less than “po”. For the transition from point D to point E, the main purpose of the exhaust unit 924 is to help maintain the outlet pressure “po” in the tip section 956 as near to one atmosphere pressure as possible.
  • Earlier it was mentioned that the mass flow rate of the primary fluid refrigerant as it passes through the catheter 912 has an effect on the operation of the catheter 912. Essentially this effect is shown in FIG. 13. There it will be seen that for relatively low mass flow rates (e.g. below point F on curve 980 shown in FIG. 13), increases in the mass flow rate of the refrigerant will cause lower temperatures. Refrigerant flow in this range is said to be “refrigeration limited.” On the other hand, for relatively high mass flow rates (i.e. above point F), increases in the mass flow rate actually cause the temperature of the refrigerant to rise. Flow in this range is said to be “surface area limited.” Because the system 910 is most efficient at the lowest temperature for the refrigerant, operation at point F is preferred. Accordingly, by monitoring the temperature of the refrigerant in the tip section 956, “Tt”, variations of Tt can be used to control the mass flow rate of the refrigerant, to thereby control the refrigeration potential of the catheter 912.
  • In operation, the variables mentioned above (pw, po, pr, and Tt) can be determined as needed. System 910 then manipulates the regulator valve 964, in response to whatever variables are being used, to vary the working pressure “pw” of the primary fluid refrigerant as it enters the supply line 946. In this way, variations in “pw” can be used to control “po” and, consequently, the refrigeration potential of the catheter 912.
  • While the particular invention as herein shown and disclosed in detail is fully capable of obtaining the objects and providing the advantages herein before stated, it is to be understood that it is merely illustrative of the presently preferred embodiments of the invention and that no limitations are intended to the details of construction or design herein shown other than as described in the appended claims.

Claims (30)

  1. 1. A cryogenic medical system comprising:
    a medical device;
    a refrigeration system for cooling the medical device including
    a primary cooling system circulating a coolant through the medical device; and
    a precooling system cooling the coolant before the coolant reaches the medical device;
    wherein the primary cooling system includes a recovery system which recovers the coolant after it passes through the medical device and wherein the primary cooling system is substantially an open loop.
  2. 2. The cryogenic medical system of claim 1 wherein the primary cooling system includes:
    a pressure bottle supplying the coolant to the primary cooling system; and
    a compressor interposed between the medical device and a recovery bottle.
  3. 3. The cryogenic medical system of claim 1
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger enveloping a portion of the primary cooling system; and
    wherein the precooling system is a substantially closed loop further comprising a compressor and an aftercooler.
  4. 4. The cryogenic medical system of claim 1
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger defining a coolant flow path and enveloping a portion of the primary cooling system; and
    further comprising a compressor in fluid communication with an aftercooler outputting coolant to the inlet of the heat exchanger and receiving coolant from the outlet of the heat exchanger.
  5. 5. A cryogenic medical system comprising:
    a medical device;
    a console;
    a primary cooling system directing a coolant to the medical device; and,
    a precooling system cooling the coolant before the coolant reaches the medical device;
    wherein the primary cooling system includes a recovery system which recovers the coolant after it passes through the medical device and wherein the primary cooling system is substantially an open loop.
  6. 6. The cryogenic medical system of claim 5 wherein the primary cooling system includes:
    a pressure bottle supplying the coolant to the primary cooling system; and
    a compressor interposed between the medical device and a recovery bottle.
  7. 7. The cryogenic medical system of claim 5
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger enveloping a portion of the primary cooling system; and
    wherein the precooling system is a substantially closed loop further comprising a compressor and an aftercooler.
  8. 8. The cryogenic medical system of claim 5
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger defining a coolant flow path and enveloping a portion of the primary cooling system; and
    further comprising a compressor in fluid communication with an aftercooler outputting coolant to the inlet of the heat exchanger and receiving coolant from the outlet of the heat exchanger.
  9. 9. A cryogenic medical system comprising:
    a medical device having a connection point;
    a console;
    a primary cooling system directing a coolant to the medical device; and
    a precooling system cooling the coolant before the coolant reaches the connection point;
    wherein the primary cooling system includes a recovery system which recovers the coolant after it passes through the medical device and wherein the primary cooling system is substantially an open loop.
  10. 10. The cryogenic medical system of claim 9 wherein the primary cooling system includes:
    a pressure bottle supplying the coolant to the primary cooling system; and
    a compressor interposed between the medical device and a recovery bottle.
  11. 11. The cryogenic medical system of claim 9
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger enveloping a portion of the primary cooling system; and
    wherein the precooling system is a substantially closed loop further comprising a compressor and an aftercooler.
  12. 12. The cryogenic medical system of claim 9
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger defining a coolant flow path and enveloping a portion of the primary cooling system; and
    further comprising a compressor in fluid communication with an aftercooler outputting coolant to the inlet of the heat exchanger and receiving coolant from the outlet of the heat exchanger.
  13. 13. A cryogenic medical system comprising:
    a medical device having a connection point;
    a console, the console being used to cool the medical device and being connectable to the medical device at the connection point, the console including
    a primary cooling system directing a coolant to the medical device along a supply conduit; and
    a precooling system cooling the coolant within the supply conduit before the coolant reaches the connection point;
    wherein the primary cooling system includes a return conduit leading from the medical device to a recovery system which recovers the coolant after it passes through the medical device and wherein the primary cooling system is substantially an open loop.
  14. 14. The cryogenic medical system of claim 13 wherein the primary cooling system includes:
    a pressure bottle in fluid communication with the supply conduit; and
    a compressor interposed between the medical device a recovery bottle.
  15. 15. The cryogenic medical system of claim 13
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger enveloping a portion of the supply conduit; and
    wherein the precooling system is a substantially closed loop further comprising a compressor and an aftercooler.
  16. 16. The cryogenic medical system of claim 13
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger defining a coolant flow path and enveloping a portion of the supply conduit; and
    further comprising a compressor in fluid communication with an aftercooler outputting coolant to the inlet of the heat exchanger and receiving coolant from the outlet of the heat exchanger.
  17. 17. A cryogenic medical system comprising:
    a medical device;
    a console, the console being connectable to the medical device at a connection point, the console controlling temperature of the medical device, and the console including
    a first cooling circuit directing coolant to the medical device at a first temperature along a coolant supply line; and
    a second cooling circuit chilling the coolant within the coolant supply line to a temperature below the first temperature before the coolant reaches the connection point;
    wherein the first cooling circuit includes a coolant return line leading from the catheter to a coolant scavenging system, and wherein the first cooling circuit and the catheter comprise a substantially open-loop.
  18. 18. The cryogenic medical system of claim 17 wherein the first cooling circuit includes:
    a coolant reservoir in fluid communication with the fluid supply line; and
    a vacuum pump interposed between the catheter and the coolant collection tank.
  19. 19. The cryogenic medical system of claim 17
    wherein the second cooling circuit includes an enclosure having an inlet and an outlet; the enclosure defining a fluid path from the inlet to the outlet, and the enclosure enveloping a portion of the coolant supply line; and
    further comprising a compressor in fluid communication with a condenser outputting coolant to the inlet of the enclosure and receiving coolant from the outlet of the enclosure.
  20. 20. A cryogenic medical system comprising:
    a medical device, wherein the medical device includes a catheter;
    a refrigeration system for cooling the medical device including
    a primary cooling system circulating a coolant through the medical device; and
    a precooling system cooling the coolant before the coolant reaches the catheter;
    wherein the primary cooling system includes a recovery system which recovers the coolant after it passes through the catheter and wherein the primary cooling system is substantially an open loop; and
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger enveloping a portion of the primary cooling system.
  21. 21. The cryogenic medical system of claim 20
    wherein the coolant is supplied to the primary cooling system in a substantially gaseous state; and
    wherein the precooling system cools the coolant within the primary cooling system from a substantially gaseous state to a substantially liquid state.
  22. 22. A cryogenic medical system comprising:
    a medical device, wherein the medical device includes a catheter;
    a console;
    a primary cooling system directing a coolant to the catheter;
    a precooling system cooling the coolant before the coolant reaches the catheter;
    wherein the primary cooling system includes a recovery system which recovers the coolant after it passes through the catheter and wherein the primary cooling system is substantially an open loop; and
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger enveloping a portion of the primary cooling system.
  23. 23. The cryogenic medical system of claim 22
    wherein the coolant is supplied to the primary cooling system in a substantially gaseous state; and
    wherein the precooling system cools the coolant within the primary cooling system from a substantially gaseous state to a substantially liquid state.
  24. 24. A cryogenic medical system comprising:
    a medical device having a connection point, wherein the medical device includes a catheter;
    a console;
    a primary cooling system directing a coolant to the catheter;
    a precooling system cooling the coolant before the coolant reaches the connection point;
    wherein the primary cooling system includes a recovery system which recovers the coolant after it passes through the catheter and wherein the primary cooling system is substantially an open loop; and
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger enveloping a portion of the primary cooling system.
  25. 25. The cryogenic medical system of claim 24
    wherein the coolant is supplied to the primary cooling system in a substantially gaseous state; and
    wherein the precooling system cools the coolant within the primary cooling system from a substantially gaseous state to a substantially liquid state.
  26. 26. A cryogenic medical system comprising:
    a medical device having a connection point, wherein the medical device includes a catheter;
    a console, the console being used to cool the catheter and being connectable to the medical device at the connection point, the console including
    a primary cooling system directing a coolant to the catheter along a supply conduit; and
    a precooling system cooling the coolant within the supply conduit before the coolant reaches the connection point;
    wherein the primary cooling system includes a return conduit leading from the catheter to a recovery system which recovers the coolant after it passes through the catheter and wherein the primary cooling system is substantially an open loop; and
    wherein the precooling system includes a heat exchanger having an inlet and an outlet, the heat exchanger enveloping a portion of the supply conduit.
  27. 27. The cryogenic medical system of claim 26
    wherein the coolant is supplied to the primary cooling system in a substantially gaseous state; and
    wherein the precooling system cools the coolant within the primary cooling system from a substantially gaseous state to a substantially liquid state.
  28. 28. A cryogenic medical system comprising:
    a medical device, wherein the medical device includes a catheter;
    a system component, the system component being connectable to the medical device at a connection point, the system component controlling temperature of the medical device, and the system component including
    a first cooling circuit directing coolant to the medical device at a first temperature along a coolant supply line; and
    a second cooling circuit chilling the coolant within the coolant supply line to a temperature below the first temperature before the coolant reaches the connection point,
    wherein the first cooling circuit includes a coolant return line leading from the catheter to a coolant scavenging system, and wherein the first cooling circuit and the catheter comprise a substantially open-loop, and
    wherein the second cooling circuit includes an enclosure having a fluid inlet and a fluid outlet; the enclosure defining a fluid path from the inlet to the outlet, and the enclosure enveloping a portion of the coolant supply line, and
    wherein the inlet is provided inside the enclosure.
  29. 29. The cryogenic medical system of claim 28
    wherein coolant is supplied to the first cooling circuit in a substantially gaseous state; and,
    wherein the second cooling circuit chills the coolant within the first cooling circuit and coolant supply line from a substantially gaseous state to a substantially liquid state.
  30. 30-39. (canceled)
US11098835 2000-08-09 2005-04-05 Refrigeration source for a cryoablation catheter Abandoned US20070277550A1 (en)

Priority Applications (4)

Application Number Priority Date Filing Date Title
US09635108 US6471694B1 (en) 2000-08-09 2000-08-09 Control system for cryosurgery
US10243997 US7004936B2 (en) 2000-08-09 2002-09-12 Refrigeration source for a cryoablation catheter
US10888804 US20050159735A1 (en) 2000-08-09 2004-07-09 Refrigeration source for a cryoablation catheter
US11098835 US20070277550A1 (en) 2000-08-09 2005-04-05 Refrigeration source for a cryoablation catheter

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US11098835 US20070277550A1 (en) 2000-08-09 2005-04-05 Refrigeration source for a cryoablation catheter
US12353962 US20090318913A1 (en) 2000-08-09 2009-01-14 Refrigeration source for a cryoablation catheter

Related Parent Applications (2)

Application Number Title Priority Date Filing Date
US10243997 Continuation US7004936B2 (en) 2000-08-09 2002-09-12 Refrigeration source for a cryoablation catheter
US10888804 Continuation US20050159735A1 (en) 2000-08-09 2004-07-09 Refrigeration source for a cryoablation catheter

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US12353962 Continuation US20090318913A1 (en) 2000-08-09 2009-01-14 Refrigeration source for a cryoablation catheter

Publications (1)

Publication Number Publication Date
US20070277550A1 true true US20070277550A1 (en) 2007-12-06

Family

ID=31887815

Family Applications (5)

Application Number Title Priority Date Filing Date
US10243997 Active US7004936B2 (en) 2000-08-09 2002-09-12 Refrigeration source for a cryoablation catheter
US10888804 Abandoned US20050159735A1 (en) 2000-08-09 2004-07-09 Refrigeration source for a cryoablation catheter
US11098835 Abandoned US20070277550A1 (en) 2000-08-09 2005-04-05 Refrigeration source for a cryoablation catheter
US11865686 Expired - Fee Related USRE40868E1 (en) 1999-06-25 2007-10-01 Refrigeration source for a cryoblation catheter
US12353962 Abandoned US20090318913A1 (en) 2000-08-09 2009-01-14 Refrigeration source for a cryoablation catheter

Family Applications Before (2)

Application Number Title Priority Date Filing Date
US10243997 Active US7004936B2 (en) 2000-08-09 2002-09-12 Refrigeration source for a cryoablation catheter
US10888804 Abandoned US20050159735A1 (en) 2000-08-09 2004-07-09 Refrigeration source for a cryoablation catheter

Family Applications After (2)

Application Number Title Priority Date Filing Date
US11865686 Expired - Fee Related USRE40868E1 (en) 1999-06-25 2007-10-01 Refrigeration source for a cryoblation catheter
US12353962 Abandoned US20090318913A1 (en) 2000-08-09 2009-01-14 Refrigeration source for a cryoablation catheter

Country Status (5)

Country Link
US (5) US7004936B2 (en)
EP (1) EP1398002B1 (en)
JP (1) JP4412965B2 (en)
CA (1) CA2440777C (en)
DE (2) DE60306281D1 (en)

Cited By (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080119837A1 (en) * 2006-11-17 2008-05-22 Devens Douglas A Cryoprobe with Coaxial Chambers
US20080119838A1 (en) * 2006-11-17 2008-05-22 Vancelette David W Disposable Sheath with Replaceable Console Probes for Cryosurgery
US20090270851A1 (en) * 2008-04-24 2009-10-29 Babkin Alexei V Method and System for Cryoablation Treatment
US20100057064A1 (en) * 2008-09-03 2010-03-04 Baust John M Medical Device for the Transport of Subcooled Cryogenic Fluid through a Linear Heat Exchanger
US20100057067A1 (en) * 2008-09-03 2010-03-04 Baust John M Modular pulsed pressure device for the transport of liquid cryogen to a cryoprobe
US20100076421A1 (en) * 2008-09-19 2010-03-25 Baust John M Nucleation Enhanced Surface Modification to Support Physical Vapor Deposition to Create a Vacuum
US20100147006A1 (en) * 2007-06-04 2010-06-17 Taras Michael F Refrigerant system with cascaded circuits and performance enhancement features
US20100256621A1 (en) * 2009-04-06 2010-10-07 Cryomedix Llc Single phase liquid refrigerant cryoablation system with multitubular distal section and related method
US20100280507A1 (en) * 2009-04-30 2010-11-04 Cryomedix Llc Cryoablation system having docking station for charging cryogen containers and related method
US20110152849A1 (en) * 2008-09-03 2011-06-23 Baust John M Cryogenic System and Method of Use
US8475441B2 (en) 2008-12-23 2013-07-02 Cryomedix, Llc Isotherm-based tissue ablation control system
DE102013101104A1 (en) * 2013-02-05 2014-08-07 Bürkert Werke GmbH A cooling arrangement for cooling an object with a control device and method for monitoring such a cooling arrangement
US9089316B2 (en) 2009-11-02 2015-07-28 Endocare, Inc. Cryogenic medical system
US9101343B2 (en) 2012-08-03 2015-08-11 Thach Buu Duong Therapeutic cryoablation system
US9402676B2 (en) 2010-08-26 2016-08-02 Cryomedix, Llc Cryoablation balloon catheter and related method
US9408655B2 (en) 2010-10-27 2016-08-09 Cryomedix, Llc Cryoablation apparatus with enhanced heat exchange area and related method
US20170219261A1 (en) * 2016-02-01 2017-08-03 Medtronic Cryocath Lp Recovery system for n20

Families Citing this family (36)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050228367A1 (en) * 1999-01-25 2005-10-13 Marwan Abboud Leak detection system for catheter based medical device
US7004936B2 (en) * 2000-08-09 2006-02-28 Cryocor, Inc. Refrigeration source for a cryoablation catheter
US20040034344A1 (en) * 2002-08-16 2004-02-19 Eric Ryba Tip pressure monitoring for cryoablation catheters
US6981382B2 (en) * 2003-07-24 2006-01-03 Cryocor, Inc. Distal end for cryoablation catheters
US7580507B2 (en) * 2004-01-13 2009-08-25 Koninklijke Philips Electronics N.V. Liquid flow sensor fox x-ray tubes
CN102664661A (en) 2004-08-12 2012-09-12 美商内数位科技公司 Base station, wireless transmit/receive unit and method
US20060178662A1 (en) * 2005-02-04 2006-08-10 Ripley Kenneth L Warming gradient control for a cryoablation applicator
CA2634683C (en) 2005-12-22 2016-02-02 The Trustees Of Columbia University In The City Of New York Systems and methods for intravascular cooling
EP2010084A2 (en) * 2006-04-24 2009-01-07 Thomas Jefferson University Cryoneedle and cryotherapy system
US20080125764A1 (en) * 2006-11-17 2008-05-29 Vancelette David W Cryoprobe thermal control for a closed-loop cryosurgical system
WO2009085666A1 (en) * 2007-12-27 2009-07-09 Boston Scientific Scimed, Inc. System for controllably delivering liquid coolant to a cryo-ablation device
EP2104116B1 (en) * 2008-03-12 2017-05-10 ALSTOM Transport Technologies Oil cooling system, particularly for transformers feeding traction electric motors, transformer with said system and method for determining the cooling fluid flow in a cooling system
US9050069B2 (en) 2008-05-16 2015-06-09 Medtronic Cryocath Lp Thermocouple-controlled catheter cooling system
JP2010008487A (en) * 2008-06-24 2010-01-14 Fujitsu Ltd Optical module and dispersion compensator
DE102008045563B9 (en) * 2008-07-02 2012-01-26 Erbe Elektromedizin Gmbh Temperature control for a cryoprobe cryosurgical device with temperature controller and method of controlling the temperature of a cryoprobe
JP5233031B2 (en) * 2008-07-15 2013-07-10 株式会社デージーエス・コンピュータ Frozen treatment planning system and freeze-treatment device
WO2010083281A1 (en) * 2009-01-15 2010-07-22 Boston Scientific Scimed, Inc. Controlling depth of cryoablation
US20100241113A1 (en) * 2009-03-20 2010-09-23 Boston Scientific Scimed, Inc. Protecting the phrenic nerve while ablating cardiac tissue
EP2485638B1 (en) 2009-10-07 2016-11-30 Endophys Holdings, LLC Pressure-sensing medical device
EP2575657B1 (en) 2010-06-01 2017-07-26 AFreeze GmbH Leakage protection system, pressure balancing system, and precipitator with valve function for ablation applications
US9687386B2 (en) 2010-09-10 2017-06-27 Medivance Incorporated Cooling medical pad
US9622907B2 (en) 2010-09-10 2017-04-18 Medivance Incorporated Cooling medical pad
US9011420B2 (en) 2010-10-27 2015-04-21 Medtronic Cryocath Lp Compatible cryogenic cooling system
RU2483691C2 (en) * 2011-03-11 2013-06-10 Валентин Николаевич Павлов Cryosyrgical apparatus
US20120265452A1 (en) * 2011-04-14 2012-10-18 Galil Medical Inc. Method of monitoring gas supply during a cryosurgical procedure
US20130018368A1 (en) * 2011-07-13 2013-01-17 Galil Medical Inc. User interface for operating and monitoring a cryosurgical system
CN102488550B (en) * 2011-11-29 2013-04-17 浙江大学 Low-temperature therapeutic apparatus for tumour
CA2861116A1 (en) * 2012-01-13 2013-07-18 Myoscience, Inc. Cryogenic probe filtration system
US20140031804A1 (en) * 2012-07-26 2014-01-30 Medtronic Cryocath Lp Device and method for ablating tissue
USD685916S1 (en) 2012-11-26 2013-07-09 Medivance Incorporated Medical cooling pad
US10054262B2 (en) 2014-04-16 2018-08-21 Cpsi Holdings Llc Pressurized sub-cooled cryogenic system
US9956024B2 (en) 2014-07-11 2018-05-01 Medtronic Cryocath Lp Cryoablation method and system
US9861422B2 (en) 2015-06-17 2018-01-09 Medtronic, Inc. Catheter breach loop feedback fault detection with active and inactive driver system
US9993280B2 (en) 2015-07-02 2018-06-12 Medtronic Cryocath Lp N2O thermal pressurization system by cooling
US20170000544A1 (en) * 2015-07-02 2017-01-05 Medtronic Cryocath Lp N2o liquefaction system with subcooling heat exchanger for medical device
CN105852960B (en) * 2016-04-11 2018-07-06 天津美电医疗科技有限公司 Gases throttling type cryosurgical device and control method

Citations (91)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3299646A (en) * 1964-06-17 1967-01-24 Little Inc A Cryogenic joule-thomson helium liquefier with cascade helium and nitrogen refrigeration circuits
US3300991A (en) * 1964-07-07 1967-01-31 Union Carbide Corp Thermal reset liquid level control system for the liquefaction of low boiling gases
US3392541A (en) * 1967-02-06 1968-07-16 Larkin Coils Inc Plural compressor reverse cycle refrigeration or heat pump system
US3552384A (en) * 1967-07-03 1971-01-05 American Hospital Supply Corp Controllable tip guide body and catheter
US3733845A (en) * 1972-01-19 1973-05-22 D Lieberman Cascaded multicircuit,multirefrigerant refrigeration system
US3823575A (en) * 1971-06-07 1974-07-16 Univ Melbourne Cryogenic apparatus
US3852974A (en) * 1971-12-03 1974-12-10 T Brown Refrigeration system with subcooler
US4000626A (en) * 1975-02-27 1977-01-04 Webber Robert C Liquid convection fluid heat exchanger for refrigeration circuit
US4072152A (en) * 1976-02-23 1978-02-07 Linehan John H Orthopedic cryosurgical apparatus
US4118934A (en) * 1975-03-21 1978-10-10 Enterprise Industrielle De Chaudronnerie Process and apparatus for transforming heat at a relatively low temperature into power or energy
US4228660A (en) * 1977-03-16 1980-10-21 L'air Liquide, Societe Anonyme Pour L'etude Et L'exploitation Des Procedes Georges Claude Heat exchangers
US4339253A (en) * 1979-12-12 1982-07-13 Compagnie Francaise D'etudes Et De Construction "Technip" Method of and system for liquefying a gas with low boiling temperature
US4539028A (en) * 1983-05-06 1985-09-03 Compagnie Francaise D'etudes Et De Construction "Technip" Method and apparatus for cooling and liquefying at least one gas with a low boiling point, such as for example natural gas
US4597268A (en) * 1984-02-14 1986-07-01 Andersson Bengt O K Method and apparatus for gas-cooling
US4777805A (en) * 1984-09-19 1988-10-18 Kabushiki Kaisha Toshiba Heat pump system
US4829785A (en) * 1987-12-04 1989-05-16 The Boeing Company Cryogenic cooling system with precooling stage
US4850199A (en) * 1988-03-21 1989-07-25 Guild Associates, Inc. Cryo-refrigeration system
US4899741A (en) * 1987-01-14 1990-02-13 Hgm Medical Laser Systems, Inc. Laser heated probe and control system
US4911148A (en) * 1989-03-14 1990-03-27 Intramed Laboratories, Inc. Deflectable-end endoscope with detachable flexible shaft assembly
US4917667A (en) * 1988-02-11 1990-04-17 Retroperfusion Systems, Inc. Retroperfusion balloon catheter and method
US4951474A (en) * 1988-03-21 1990-08-28 Guild Associates, Inc. Cryo-refrigeration system
US5114399A (en) * 1990-10-01 1992-05-19 Intramed Laboratories Surgical device
US5170639A (en) * 1991-12-10 1992-12-15 Chander Datta Cascade refrigeration system
US5254116A (en) * 1991-09-06 1993-10-19 Cryomedical Sciences, Inc. Cryosurgical instrument with vent holes and method using same
US5275595A (en) * 1992-07-06 1994-01-04 Dobak Iii John D Cryosurgical instrument
US5277199A (en) * 1990-09-17 1994-01-11 C. R. Bard, Inc. Core wire steerable catheters
US5281215A (en) * 1992-04-16 1994-01-25 Implemed, Inc. Cryogenic catheter
US5281213A (en) * 1992-04-16 1994-01-25 Implemed, Inc. Catheter for ice mapping and ablation
US5348554A (en) * 1992-12-01 1994-09-20 Cardiac Pathways Corporation Catheter for RF ablation with cooled electrode
US5386709A (en) * 1992-12-10 1995-02-07 Baltimore Aircoil Company, Inc. Subcooling and proportional control of subcooling of liquid refrigerant circuits with thermal storage or low temperature reservoirs
US5395327A (en) * 1990-02-02 1995-03-07 Ep Technologies, Inc. Catheter steering mechanism
US5423807A (en) * 1992-04-16 1995-06-13 Implemed, Inc. Cryogenic mapping and ablation catheter
US5431168A (en) * 1993-08-23 1995-07-11 Cordis-Webster, Inc. Steerable open-lumen catheter
US5472017A (en) * 1992-11-17 1995-12-05 Life Medical Technologies, Inc. Deflectable catheter
US5513498A (en) * 1995-04-06 1996-05-07 General Electric Company Cryogenic cooling system
US5540062A (en) * 1993-11-01 1996-07-30 State Of Israel, Ministry Of Defence, Rafael Armaments Development Authority Controlled cryogenic contact system
US5549542A (en) * 1992-11-17 1996-08-27 Life Medical Technologies, Inc. Deflectable endoscope
US5603221A (en) * 1994-06-30 1997-02-18 State Of Israel, Ministry Of Defense, Rafael-Armaments Development Authority Multiprobe surgical cryogenic apparatus
US5656029A (en) * 1992-12-01 1997-08-12 Cardiac Pathways Corporation Steerable catheter with adjustable bend location and/or radius and method
US5662606A (en) * 1993-03-12 1997-09-02 Heart Rhythm Technologies, Inc. Catheter for electrophysiological procedures
US5667505A (en) * 1992-03-24 1997-09-16 Smt Spol. S.R.O. Method of carrying out cryosurgical interventions and device for this method
US5674218A (en) * 1990-09-26 1997-10-07 Cryomedical Sciences, Inc. Cryosurgical instrument and system and method of cryosurgery
US5676653A (en) * 1995-06-27 1997-10-14 Arrow International Investment Corp. Kink-resistant steerable catheter assembly
US5687579A (en) * 1994-09-12 1997-11-18 Vaynberg; Mikhail M. Double circuited refrigeration system with chiller
US5728144A (en) * 1992-04-13 1998-03-17 Ep Technologies, Inc. Steerable coaxial cable systems for cardiac ablation
US5733319A (en) * 1996-04-25 1998-03-31 Urologix, Inc. Liquid coolant supply system
US5733280A (en) * 1995-11-15 1998-03-31 Avitall; Boaz Cryogenic epicardial mapping and ablation
US5752385A (en) * 1995-11-29 1998-05-19 Litton Systems, Inc. Electronic controller for linear cryogenic coolers
US5758505A (en) * 1995-10-12 1998-06-02 Cryogen, Inc. Precooling system for joule-thomson probe
US5759182A (en) * 1993-11-09 1998-06-02 Spembly Medical Limited Cryosurgical probe with pre-cooling feature
US5795332A (en) * 1996-04-15 1998-08-18 Lucas; Daniel R. Silicone catheter
US5800493A (en) * 1995-04-26 1998-09-01 Gynecare, Inc. Intrauterine ablation system
US5807391A (en) * 1993-10-26 1998-09-15 Cordis Corporation Cryo-ablation catheter
US5820626A (en) * 1996-07-30 1998-10-13 Laser Aesthetics, Inc. Cooling laser handpiece with refillable coolant reservoir
US5860970A (en) * 1994-05-10 1999-01-19 Spembly Medical Limited Cryosurgical instrument
US5865800A (en) * 1993-08-19 1999-02-02 Boston Scientific Corporation Deflectable catheter
US5868735A (en) * 1997-03-06 1999-02-09 Scimed Life Systems, Inc. Cryoplasty device and method
US5876373A (en) * 1997-04-04 1999-03-02 Eclipse Surgical Technologies, Inc. Steerable catheter
US5899898A (en) * 1997-02-27 1999-05-04 Cryocath Technologies Inc. Cryosurgical linear ablation
US5902299A (en) * 1997-07-29 1999-05-11 Jayaraman; Swaminathan Cryotherapy method for reducing tissue injury after balloon angioplasty or stent implantation
US5910104A (en) * 1996-12-26 1999-06-08 Cryogen, Inc. Cryosurgical probe with disposable sheath
US5916212A (en) * 1998-01-23 1999-06-29 Cryomedical Sciences, Inc. Hand held cyrosurgical probe system
US5992158A (en) * 1994-05-10 1999-11-30 Spembly Medical Limited Cryosurgical instrument
US6019783A (en) * 1999-03-02 2000-02-01 Alsius Corporation Cooling system for therapeutic catheter
US6027499A (en) * 1997-05-23 2000-02-22 Fiber-Tech Medical, Inc. (Assignee Of Jennifer B. Cartledge) Method and apparatus for cryogenic spray ablation of gastrointestinal mucosa
US6039730A (en) * 1996-06-24 2000-03-21 Allegheny-Singer Research Institute Method and apparatus for cryosurgery
US6106518A (en) * 1998-04-09 2000-08-22 Cryocath Technologies, Inc. Variable geometry tip for a cryosurgical ablation device
US6120476A (en) * 1997-12-01 2000-09-19 Cordis Webster, Inc. Irrigated tip catheter
US6151901A (en) * 1995-10-12 2000-11-28 Cryogen, Inc. Miniature mixed gas refrigeration system
US6197045B1 (en) * 1999-01-04 2001-03-06 Medivance Incorporated Cooling/heating pad and system
US6235019B1 (en) * 1997-02-27 2001-05-22 Cryocath Technologies, Inc. Cryosurgical catheter
US6237355B1 (en) * 1999-06-25 2001-05-29 Cryogen, Inc. Precooled cryogenic ablation system
US6241722B1 (en) * 1998-06-17 2001-06-05 Cryogen, Inc. Cryogenic device, system and method of using same
US6270494B1 (en) * 1996-12-26 2001-08-07 Cryogen, Inc. Stretchable cryoprobe sheath
US6270476B1 (en) * 1999-04-23 2001-08-07 Cryocath Technologies, Inc. Catheter
US6270493B1 (en) * 1999-07-19 2001-08-07 Cryocath Technologies, Inc. Cryoablation structure
US6283959B1 (en) * 1999-08-23 2001-09-04 Cyrocath Technologies, Inc. Endovascular cryotreatment catheter
US6355029B1 (en) * 1997-12-02 2002-03-12 Cryovascular Systems, Inc. Apparatus and method for cryogenic inhibition of hyperplasia
US6383180B1 (en) * 1999-01-25 2002-05-07 Cryocath Technologies Inc. Closed loop catheter coolant system
US6428534B1 (en) * 1999-02-24 2002-08-06 Cryovascular Systems, Inc. Cryogenic angioplasty catheter
US6432102B2 (en) * 1999-03-15 2002-08-13 Cryovascular Systems, Inc. Cryosurgical fluid supply
US6440126B1 (en) * 1999-04-21 2002-08-27 Cryocath Technologies Cryoblation catheter handle
US6471694B1 (en) * 2000-08-09 2002-10-29 Cryogen, Inc. Control system for cryosurgery
US6485455B1 (en) * 1990-02-02 2002-11-26 Ep Technologies, Inc. Catheter steering assembly providing asymmetric left and right curve configurations
US6485440B1 (en) * 1999-04-23 2002-11-26 Medtronic, Inc. Apparatus for deflecting a catheter or lead
US6530914B1 (en) * 2000-10-24 2003-03-11 Scimed Life Systems, Inc. Deflectable tip guide in guide system
US6530234B1 (en) * 1995-10-12 2003-03-11 Cryogen, Inc. Precooling system for Joule-Thomson probe
US6540740B2 (en) * 1997-02-27 2003-04-01 Cryocath Technologies Inc. Cryosurgical catheter
US6551302B1 (en) * 1997-09-24 2003-04-22 Michael J. Rosinko Steerable catheter with tip alignment and surface contact detector
US6554794B1 (en) * 1997-09-24 2003-04-29 Richard L. Mueller Non-deforming deflectable multi-lumen catheter
US6572610B2 (en) * 2001-08-21 2003-06-03 Cryogen, Inc. Cryogenic catheter with deflectable tip

Family Cites Families (45)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US659158A (en) * 1900-05-16 1900-10-02 William Schlabach Fertilizer-distributing attachment.
US3696813A (en) 1971-10-06 1972-10-10 Cryomedics Cryosurgical instrument
GB1438759A (en) 1972-06-02 1976-06-09 Spembly Ltd Cryo-surgical apparatus
US4018227A (en) 1975-10-09 1977-04-19 Cryomedics, Inc. Cryosurgical instrument
US5147355A (en) 1988-09-23 1992-09-15 Brigham And Womens Hospital Cryoablation catheter and method of performing cryoablation
GB2226497B (en) 1988-12-01 1992-07-01 Spembly Medical Ltd Cryosurgical probe
JP3232308B2 (en) * 1990-02-02 2001-11-26 ボストン サイエンティフィック リミテッド Catheter steering mechanism
US5063747A (en) 1990-06-28 1991-11-12 United States Of America As Represented By The United States National Aeronautics And Space Administration Multicomponent gas sorption Joule-Thomson refrigeration
US5139496A (en) 1990-12-20 1992-08-18 Hed Aharon Z Ultrasonic freeze ablation catheters and probes
GB2269107B (en) 1992-07-31 1996-05-08 Spembly Medical Ltd Cryosurgical ablation
US5724832A (en) 1995-03-29 1998-03-10 Mmr Technologies, Inc. Self-cleaning cryogenic refrigeration system
US5617739A (en) 1995-03-29 1997-04-08 Mmr Technologies, Inc. Self-cleaning low-temperature refrigeration system
US6669689B2 (en) 1997-02-27 2003-12-30 Cryocath Technologies Inc. Cryosurgical catheter
US6602247B2 (en) 1997-02-27 2003-08-05 Cryocath Technologies Inc. Apparatus and method for performing a treatment on a selected tissue region
US5876399A (en) 1997-05-28 1999-03-02 Irvine Biomedical, Inc. Catheter system and methods thereof
US6245064B1 (en) 1997-07-08 2001-06-12 Atrionix, Inc. Circumferential ablation device assembly
US6024740A (en) 1997-07-08 2000-02-15 The Regents Of The University Of California Circumferential ablation device assembly
US6117101A (en) 1997-07-08 2000-09-12 The Regents Of The University Of California Circumferential ablation device assembly
US6080151A (en) 1997-07-21 2000-06-27 Daig Corporation Ablation catheter
EP1014873A4 (en) 1997-09-22 2003-07-09 Ethicon Inc Cryosurgical system and method
US6051019A (en) * 1998-01-23 2000-04-18 Del Mar Medical Technologies, Inc. Selective organ hypothermia method and apparatus
CA2321671C (en) 1998-03-02 2009-07-14 Atrionix, Inc. Tissue ablation system and method for forming long linear lesion
US6251105B1 (en) 1998-03-31 2001-06-26 Endocare, Inc. Cryoprobe system
GB2337000B (en) * 1998-04-30 2000-08-09 Spembly Medical Ltd Improvements relating to cooled probes
US6575933B1 (en) 1998-11-30 2003-06-10 Cryocath Technologies Inc. Mechanical support for an expandable membrane
US6635053B1 (en) 1999-01-25 2003-10-21 Cryocath Technologies Inc. Cooling system
US6592577B2 (en) * 1999-01-25 2003-07-15 Cryocath Technologies Inc. Cooling system
US6048919A (en) 1999-01-29 2000-04-11 Chip Coolers, Inc. Thermally conductive composite material
US6562030B1 (en) 1999-04-06 2003-05-13 Cryocath Technologies Inc. Heater control of cryocatheter tip temperature
US6139544A (en) 1999-05-26 2000-10-31 Endocare, Inc. Computer guided cryosurgery
CA2377430A1 (en) 1999-06-15 2000-12-21 Cryocath Technologies Inc. Deflection structure
US6280439B1 (en) 1999-07-12 2001-08-28 Cryocath Technologies, Inc. Adjustable position injection tubing
US6575966B2 (en) 1999-08-23 2003-06-10 Cryocath Technologies Inc. Endovascular cryotreatment catheter
US6471693B1 (en) 1999-09-10 2002-10-29 Cryocath Technologies Inc. Catheter and system for monitoring tissue contact
WO2002034304A9 (en) 2000-10-23 2003-10-16 Tissuemed Ltd Self-adhesive hydratable matrix for topical therapeutic use
US6407149B1 (en) 1999-12-06 2002-06-18 Cool Options, Inc. Method of manufacturing an evenly colored thermally conductive composite
US6503964B2 (en) 2000-01-11 2003-01-07 Cool Options, Inc. Polymer composition with metal coated carbon flakes
CA2413529C (en) 2000-06-23 2008-12-02 Cryocath Technologies Inc. Cryotreatment device and method
US6710109B2 (en) 2000-07-13 2004-03-23 Cool Options, Inc. A New Hampshire Corp. Thermally conductive and high strength injection moldable composition
US7004936B2 (en) * 2000-08-09 2006-02-28 Cryocor, Inc. Refrigeration source for a cryoablation catheter
US6755823B2 (en) 2001-02-28 2004-06-29 Cryocath Technologies Inc. Medical device with enhanced cooling power
US6585728B2 (en) 2001-05-25 2003-07-01 Biosense Webster, Inc. Cryoablation catheter with an improved gas expansion chamber
US6589234B2 (en) 2001-09-27 2003-07-08 Cryocath Technologies Inc. Cryogenic medical device with high pressure resistance tip
US6579287B2 (en) 2001-10-09 2003-06-17 Cryocath Technologies Inc. Cryosurgical ablation device having sequential injection and method therefor
US20070043342A1 (en) * 2005-08-16 2007-02-22 Galil Medical Ltd. Cryoprobe with reduced adhesion to frozen tissue, and cryosurgical methods utilizing same

Patent Citations (97)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3299646A (en) * 1964-06-17 1967-01-24 Little Inc A Cryogenic joule-thomson helium liquefier with cascade helium and nitrogen refrigeration circuits
US3300991A (en) * 1964-07-07 1967-01-31 Union Carbide Corp Thermal reset liquid level control system for the liquefaction of low boiling gases
US3392541A (en) * 1967-02-06 1968-07-16 Larkin Coils Inc Plural compressor reverse cycle refrigeration or heat pump system
US3552384A (en) * 1967-07-03 1971-01-05 American Hospital Supply Corp Controllable tip guide body and catheter
US3823575A (en) * 1971-06-07 1974-07-16 Univ Melbourne Cryogenic apparatus
US3852974A (en) * 1971-12-03 1974-12-10 T Brown Refrigeration system with subcooler
US3733845A (en) * 1972-01-19 1973-05-22 D Lieberman Cascaded multicircuit,multirefrigerant refrigeration system
US4000626A (en) * 1975-02-27 1977-01-04 Webber Robert C Liquid convection fluid heat exchanger for refrigeration circuit
US4118934A (en) * 1975-03-21 1978-10-10 Enterprise Industrielle De Chaudronnerie Process and apparatus for transforming heat at a relatively low temperature into power or energy
US4072152A (en) * 1976-02-23 1978-02-07 Linehan John H Orthopedic cryosurgical apparatus
US4228660A (en) * 1977-03-16 1980-10-21 L'air Liquide, Societe Anonyme Pour L'etude Et L'exploitation Des Procedes Georges Claude Heat exchangers
US4339253A (en) * 1979-12-12 1982-07-13 Compagnie Francaise D'etudes Et De Construction "Technip" Method of and system for liquefying a gas with low boiling temperature
US4539028A (en) * 1983-05-06 1985-09-03 Compagnie Francaise D'etudes Et De Construction "Technip" Method and apparatus for cooling and liquefying at least one gas with a low boiling point, such as for example natural gas
US4597268A (en) * 1984-02-14 1986-07-01 Andersson Bengt O K Method and apparatus for gas-cooling
US4777805A (en) * 1984-09-19 1988-10-18 Kabushiki Kaisha Toshiba Heat pump system
US4899741A (en) * 1987-01-14 1990-02-13 Hgm Medical Laser Systems, Inc. Laser heated probe and control system
US4829785A (en) * 1987-12-04 1989-05-16 The Boeing Company Cryogenic cooling system with precooling stage
US4917667A (en) * 1988-02-11 1990-04-17 Retroperfusion Systems, Inc. Retroperfusion balloon catheter and method
US4951474A (en) * 1988-03-21 1990-08-28 Guild Associates, Inc. Cryo-refrigeration system
US4850199A (en) * 1988-03-21 1989-07-25 Guild Associates, Inc. Cryo-refrigeration system
US4911148A (en) * 1989-03-14 1990-03-27 Intramed Laboratories, Inc. Deflectable-end endoscope with detachable flexible shaft assembly
US6485455B1 (en) * 1990-02-02 2002-11-26 Ep Technologies, Inc. Catheter steering assembly providing asymmetric left and right curve configurations
US5395327A (en) * 1990-02-02 1995-03-07 Ep Technologies, Inc. Catheter steering mechanism
US5277199A (en) * 1990-09-17 1994-01-11 C. R. Bard, Inc. Core wire steerable catheters
US5318041A (en) * 1990-09-17 1994-06-07 C. R. Bard, Inc. Core wire steerable electrode catheter
US5674218A (en) * 1990-09-26 1997-10-07 Cryomedical Sciences, Inc. Cryosurgical instrument and system and method of cryosurgery
US5114399A (en) * 1990-10-01 1992-05-19 Intramed Laboratories Surgical device
US5254116A (en) * 1991-09-06 1993-10-19 Cryomedical Sciences, Inc. Cryosurgical instrument with vent holes and method using same
US5170639A (en) * 1991-12-10 1992-12-15 Chander Datta Cascade refrigeration system
US5667505A (en) * 1992-03-24 1997-09-16 Smt Spol. S.R.O. Method of carrying out cryosurgical interventions and device for this method
US5728144A (en) * 1992-04-13 1998-03-17 Ep Technologies, Inc. Steerable coaxial cable systems for cardiac ablation
US5281215A (en) * 1992-04-16 1994-01-25 Implemed, Inc. Cryogenic catheter
US5423807A (en) * 1992-04-16 1995-06-13 Implemed, Inc. Cryogenic mapping and ablation catheter
US5281213A (en) * 1992-04-16 1994-01-25 Implemed, Inc. Catheter for ice mapping and ablation
US5275595A (en) * 1992-07-06 1994-01-04 Dobak Iii John D Cryosurgical instrument
US5549542A (en) * 1992-11-17 1996-08-27 Life Medical Technologies, Inc. Deflectable endoscope
US5472017A (en) * 1992-11-17 1995-12-05 Life Medical Technologies, Inc. Deflectable catheter
US5656029A (en) * 1992-12-01 1997-08-12 Cardiac Pathways Corporation Steerable catheter with adjustable bend location and/or radius and method
US5348554A (en) * 1992-12-01 1994-09-20 Cardiac Pathways Corporation Catheter for RF ablation with cooled electrode
US5386709A (en) * 1992-12-10 1995-02-07 Baltimore Aircoil Company, Inc. Subcooling and proportional control of subcooling of liquid refrigerant circuits with thermal storage or low temperature reservoirs
US5662606A (en) * 1993-03-12 1997-09-02 Heart Rhythm Technologies, Inc. Catheter for electrophysiological procedures
US5865800A (en) * 1993-08-19 1999-02-02 Boston Scientific Corporation Deflectable catheter
US5431168A (en) * 1993-08-23 1995-07-11 Cordis-Webster, Inc. Steerable open-lumen catheter
US5807391A (en) * 1993-10-26 1998-09-15 Cordis Corporation Cryo-ablation catheter
US5540062A (en) * 1993-11-01 1996-07-30 State Of Israel, Ministry Of Defence, Rafael Armaments Development Authority Controlled cryogenic contact system
US5759182A (en) * 1993-11-09 1998-06-02 Spembly Medical Limited Cryosurgical probe with pre-cooling feature
US5860970A (en) * 1994-05-10 1999-01-19 Spembly Medical Limited Cryosurgical instrument
US5992158A (en) * 1994-05-10 1999-11-30 Spembly Medical Limited Cryosurgical instrument
US5603221A (en) * 1994-06-30 1997-02-18 State Of Israel, Ministry Of Defense, Rafael-Armaments Development Authority Multiprobe surgical cryogenic apparatus
US5687579A (en) * 1994-09-12 1997-11-18 Vaynberg; Mikhail M. Double circuited refrigeration system with chiller
US5513498A (en) * 1995-04-06 1996-05-07 General Electric Company Cryogenic cooling system
US5800493A (en) * 1995-04-26 1998-09-01 Gynecare, Inc. Intrauterine ablation system
US5676653A (en) * 1995-06-27 1997-10-14 Arrow International Investment Corp. Kink-resistant steerable catheter assembly
US5758505A (en) * 1995-10-12 1998-06-02 Cryogen, Inc. Precooling system for joule-thomson probe
US5758505C1 (en) * 1995-10-12 2001-10-30 Cryogen Inc Precooling system for joule-thomson probe
US6151901A (en) * 1995-10-12 2000-11-28 Cryogen, Inc. Miniature mixed gas refrigeration system
US6530234B1 (en) * 1995-10-12 2003-03-11 Cryogen, Inc. Precooling system for Joule-Thomson probe
US5733280A (en) * 1995-11-15 1998-03-31 Avitall; Boaz Cryogenic epicardial mapping and ablation
US5752385A (en) * 1995-11-29 1998-05-19 Litton Systems, Inc. Electronic controller for linear cryogenic coolers
US5795332A (en) * 1996-04-15 1998-08-18 Lucas; Daniel R. Silicone catheter
US5733319A (en) * 1996-04-25 1998-03-31 Urologix, Inc. Liquid coolant supply system
US6007571A (en) * 1996-04-25 1999-12-28 Urologix, Inc. Liquid coolant supply system
US6039730A (en) * 1996-06-24 2000-03-21 Allegheny-Singer Research Institute Method and apparatus for cryosurgery
US5820626A (en) * 1996-07-30 1998-10-13 Laser Aesthetics, Inc. Cooling laser handpiece with refillable coolant reservoir
US6270494B1 (en) * 1996-12-26 2001-08-07 Cryogen, Inc. Stretchable cryoprobe sheath
US5910104A (en) * 1996-12-26 1999-06-08 Cryogen, Inc. Cryosurgical probe with disposable sheath
US5899898A (en) * 1997-02-27 1999-05-04 Cryocath Technologies Inc. Cryosurgical linear ablation
US6235019B1 (en) * 1997-02-27 2001-05-22 Cryocath Technologies, Inc. Cryosurgical catheter
US6540740B2 (en) * 1997-02-27 2003-04-01 Cryocath Technologies Inc. Cryosurgical catheter
US5868735A (en) * 1997-03-06 1999-02-09 Scimed Life Systems, Inc. Cryoplasty device and method
US5876373A (en) * 1997-04-04 1999-03-02 Eclipse Surgical Technologies, Inc. Steerable catheter
US6530913B1 (en) * 1997-04-04 2003-03-11 Jeffrey Giba Steerable catheter
US6027499A (en) * 1997-05-23 2000-02-22 Fiber-Tech Medical, Inc. (Assignee Of Jennifer B. Cartledge) Method and apparatus for cryogenic spray ablation of gastrointestinal mucosa
US5902299A (en) * 1997-07-29 1999-05-11 Jayaraman; Swaminathan Cryotherapy method for reducing tissue injury after balloon angioplasty or stent implantation
US6554794B1 (en) * 1997-09-24 2003-04-29 Richard L. Mueller Non-deforming deflectable multi-lumen catheter
US6551302B1 (en) * 1997-09-24 2003-04-22 Michael J. Rosinko Steerable catheter with tip alignment and surface contact detector
US6120476A (en) * 1997-12-01 2000-09-19 Cordis Webster, Inc. Irrigated tip catheter
US6355029B1 (en) * 1997-12-02 2002-03-12 Cryovascular Systems, Inc. Apparatus and method for cryogenic inhibition of hyperplasia
US5916212A (en) * 1998-01-23 1999-06-29 Cryomedical Sciences, Inc. Hand held cyrosurgical probe system
US6106518A (en) * 1998-04-09 2000-08-22 Cryocath Technologies, Inc. Variable geometry tip for a cryosurgical ablation device
US6241722B1 (en) * 1998-06-17 2001-06-05 Cryogen, Inc. Cryogenic device, system and method of using same
US6197045B1 (en) * 1999-01-04 2001-03-06 Medivance Incorporated Cooling/heating pad and system
US6383180B1 (en) * 1999-01-25 2002-05-07 Cryocath Technologies Inc. Closed loop catheter coolant system
US6468268B1 (en) * 1999-01-25 2002-10-22 Cryocath Technologies Inc. Cryogenic catheter system
US6428534B1 (en) * 1999-02-24 2002-08-06 Cryovascular Systems, Inc. Cryogenic angioplasty catheter
US6019783A (en) * 1999-03-02 2000-02-01 Alsius Corporation Cooling system for therapeutic catheter
US6432102B2 (en) * 1999-03-15 2002-08-13 Cryovascular Systems, Inc. Cryosurgical fluid supply
US6440126B1 (en) * 1999-04-21 2002-08-27 Cryocath Technologies Cryoblation catheter handle
US6485440B1 (en) * 1999-04-23 2002-11-26 Medtronic, Inc. Apparatus for deflecting a catheter or lead
US6270476B1 (en) * 1999-04-23 2001-08-07 Cryocath Technologies, Inc. Catheter
US6237355B1 (en) * 1999-06-25 2001-05-29 Cryogen, Inc. Precooled cryogenic ablation system
USRE40049E1 (en) * 1999-06-25 2008-02-12 Ams Research Corporation Precooled cryogenic ablation system
US6270493B1 (en) * 1999-07-19 2001-08-07 Cryocath Technologies, Inc. Cryoablation structure
US6283959B1 (en) * 1999-08-23 2001-09-04 Cyrocath Technologies, Inc. Endovascular cryotreatment catheter
US6471694B1 (en) * 2000-08-09 2002-10-29 Cryogen, Inc. Control system for cryosurgery
US6530914B1 (en) * 2000-10-24 2003-03-11 Scimed Life Systems, Inc. Deflectable tip guide in guide system
US6572610B2 (en) * 2001-08-21 2003-06-03 Cryogen, Inc. Cryogenic catheter with deflectable tip

Cited By (30)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080119837A1 (en) * 2006-11-17 2008-05-22 Devens Douglas A Cryoprobe with Coaxial Chambers
US20080119838A1 (en) * 2006-11-17 2008-05-22 Vancelette David W Disposable Sheath with Replaceable Console Probes for Cryosurgery
US8298221B2 (en) 2006-11-17 2012-10-30 Coopersurgical, Inc. Disposable sheath with replaceable console probes for cryosurgery
US8298220B2 (en) 2006-11-17 2012-10-30 Coopersurgical, Inc. Cryoprobe with coaxial chambers
US20100147006A1 (en) * 2007-06-04 2010-06-17 Taras Michael F Refrigerant system with cascaded circuits and performance enhancement features
US20090270851A1 (en) * 2008-04-24 2009-10-29 Babkin Alexei V Method and System for Cryoablation Treatment
US8814850B2 (en) 2008-04-24 2014-08-26 Cryomedix, Llc Method and system for cryoablation treatment
US8998888B2 (en) 2008-09-03 2015-04-07 Endocare, Inc. Modular pulsed pressure device for the transport of liquid cryogen to a cryoprobe
US20100256622A1 (en) * 2008-09-03 2010-10-07 Baust John M Modular pulsed pressure device for the transport of liquid cryogen to a cryoprobe
US9408654B2 (en) 2008-09-03 2016-08-09 Endocare, Inc. Modular pulsed pressure device for the transport of liquid cryogen to a cryoprobe
US20110152849A1 (en) * 2008-09-03 2011-06-23 Baust John M Cryogenic System and Method of Use
US20100057067A1 (en) * 2008-09-03 2010-03-04 Baust John M Modular pulsed pressure device for the transport of liquid cryogen to a cryoprobe
US20100057064A1 (en) * 2008-09-03 2010-03-04 Baust John M Medical Device for the Transport of Subcooled Cryogenic Fluid through a Linear Heat Exchanger
US8784409B2 (en) 2008-09-03 2014-07-22 Endocare, Inc. Cryogenic system and method of use
US9974592B2 (en) 2008-09-03 2018-05-22 Endocare, Inc. Cryogenic medical system
US8439905B2 (en) 2008-09-19 2013-05-14 Endocare, Inc. Nucleation enhanced surface modification to support physical vapor deposition to create a vacuum
US20100076421A1 (en) * 2008-09-19 2010-03-25 Baust John M Nucleation Enhanced Surface Modification to Support Physical Vapor Deposition to Create a Vacuum
US8475441B2 (en) 2008-12-23 2013-07-02 Cryomedix, Llc Isotherm-based tissue ablation control system
US8685014B2 (en) 2008-12-23 2014-04-01 Cryomedix, Llc Isotherm-based tissue ablation control method
US20100256621A1 (en) * 2009-04-06 2010-10-07 Cryomedix Llc Single phase liquid refrigerant cryoablation system with multitubular distal section and related method
US8845628B2 (en) 2009-04-30 2014-09-30 Cryomedix, Llc Cryoablation system having docking station for charging cryogen containers and related method
US8888768B2 (en) 2009-04-30 2014-11-18 Cryomedix, Llc Cryoablation system having docking station for charging cryogen containers and related method
US20100280507A1 (en) * 2009-04-30 2010-11-04 Cryomedix Llc Cryoablation system having docking station for charging cryogen containers and related method
US9089316B2 (en) 2009-11-02 2015-07-28 Endocare, Inc. Cryogenic medical system
US9402676B2 (en) 2010-08-26 2016-08-02 Cryomedix, Llc Cryoablation balloon catheter and related method
US9408655B2 (en) 2010-10-27 2016-08-09 Cryomedix, Llc Cryoablation apparatus with enhanced heat exchange area and related method
US9101343B2 (en) 2012-08-03 2015-08-11 Thach Buu Duong Therapeutic cryoablation system
DE102013101104A1 (en) * 2013-02-05 2014-08-07 Bürkert Werke GmbH A cooling arrangement for cooling an object with a control device and method for monitoring such a cooling arrangement
US20170219261A1 (en) * 2016-02-01 2017-08-03 Medtronic Cryocath Lp Recovery system for n20
WO2017132753A1 (en) * 2016-02-01 2017-08-10 Medtronic Cryocath Lp Recovery system for n20

Also Published As

Publication number Publication date Type
US20050159735A1 (en) 2005-07-21 application
EP1398002B1 (en) 2006-06-21 grant
EP1398002A1 (en) 2004-03-17 application
DE60306281D1 (en) 2006-08-03 grant
US7004936B2 (en) 2006-02-28 grant
US20030220634A1 (en) 2003-11-27 application
US20090318913A1 (en) 2009-12-24 application
DE60306281T2 (en) 2007-04-26 grant
JP4412965B2 (en) 2010-02-10 grant
CA2440777C (en) 2009-09-29 grant
CA2440777A1 (en) 2004-03-12 application
USRE40868E1 (en) 2009-08-11 grant
JP2004275732A (en) 2004-10-07 application

Similar Documents

Publication Publication Date Title
US6595988B2 (en) Cryotreatment device and method
US5224943A (en) Cryosurgical apparatus
US5979440A (en) Methods and apparatus to generate liquid ambulatory oxygen from an oxygen concentrator
US6251105B1 (en) Cryoprobe system
US6432102B2 (en) Cryosurgical fluid supply
US5243821A (en) Method and apparatus for delivering a continuous quantity of gas over a wide range of flow rates
US5570585A (en) Universal cooling system automatically configured to operate in compound or single compressor mode
US20030018326A1 (en) Cryogenic catheter system
US6151901A (en) Miniature mixed gas refrigeration system
US20030060762A1 (en) Cryoplasty apparatus and method
US6306129B1 (en) Cryosurgical system and method
US3800552A (en) Cryogenic surgical instrument
US20040215295A1 (en) Cryotherapy system
US6789545B2 (en) Method and system for cryoablating fibroadenomas
US5522870A (en) Fast changing heating-cooling device and method
US20020068929A1 (en) Apparatus and method for compressing a gas, and cryosurgery system and method utilizing same
US5860971A (en) Thawing of cryosurgical apparatus
US5540062A (en) Controlled cryogenic contact system
US4018227A (en) Cryosurgical instrument
US6589234B2 (en) Cryogenic medical device with high pressure resistance tip
US5674218A (en) Cryosurgical instrument and system and method of cryosurgery
US7156840B2 (en) Pressure monitor for cryoablation catheter
US20080119834A1 (en) Cryosurgical System with Disposable Cryoprobe Portion
US20080306475A1 (en) Cryo-applicator cross-section configuration
US5254116A (en) Cryosurgical instrument with vent holes and method using same

Legal Events

Date Code Title Description
AS Assignment

Owner name: AMS RESEARCH CORPORATION, MINNESOTA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:LASERSCOPE, SUCCESSOR IN INTEREST TO AMERICAN MEDICAL SYSTEMS GYNECOLOGY, INC.;REEL/FRAME:019678/0633

Effective date: 20070810

AS Assignment

Owner name: AMERICAN MEDICAL SYSTEMS GYNECOLOGY, INC., MINNESO

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:LI, HONG;REEL/FRAME:019693/0355

Effective date: 20070122

Owner name: LASERSCOPE, CALIFORNIA

Free format text: MERGER;ASSIGNOR:AMERICAN MEDICAL SYSTEMS GYNECOLOGY, INC.;REEL/FRAME:019688/0769

Effective date: 20061229

AS Assignment

Owner name: COOPERSURGICAL, INC.,CONNECTICUT

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:AMS RESEARCH CORPORATION;REEL/FRAME:023937/0314

Effective date: 20100216

Owner name: COOPERSURGICAL, INC., CONNECTICUT

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:AMS RESEARCH CORPORATION;REEL/FRAME:023937/0314

Effective date: 20100216