This application is a continuation-in-part of application Ser. No. 09/635,108 filed Aug. 9, 2000, now U.S. Pat. No. 6,471,694, which is a continuation-in-part of application Ser. No. 09/344,423, filed Jun. 25, 1999, now U.S. Pat. No. 6,237,355 . The contents of application Ser. No. 09/635,108 are incorporated herein by reference.

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.

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 refrigerant 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 the 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 top 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.

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 (T_sc=−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 (T_sc). The secondary fluid is then allowed to boil, and to thereby pre-cool the primary fluid in the system to its sub-cool temperature (T_sc). 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 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 connected, 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 (p_w) 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 (p_r).

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 “p_w” (working pressure) and “p_r” (return line pressure) can be determined and, further, because the fluid refrigerant experiences a phase change during the transition from p_w to p_r, 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 (p_o) 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 (p_o) 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 (p_o) 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 (T_t). Specifically, when this temperature (T_t) 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 (p_o) 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 “p_r” and “p_w”. The values for “p_r” and “p_w” can be used to determine the outflow pressure “p_o” in the tip section of the catheter (for one embodiment of the present invention, “p_o” is also measured directly). Further, the computer is connected to the control valve to manipulate the control valve and vary the working pressure (p_w) on the primary fluid. At the same time, the computer can monitor the temperature in the tip section of the catheter (T_t) to ensure that changes in the working pressure “p_w” result in appropriate changes in “T_t”. 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 “p_w” does not result in an increase in “T_i”. The purpose here is to maintain the outflow pressure (p_o) 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 (p_w). The primary fluid then traverses the capillary tube for outflow from the distal end of the capillary tube at the outflow pressure (p_o). 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 (p_w) 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. p_o) as it outflows from the distal end of the capillary tube (e.g. one atmosphere, 15 psi) (Δp=p_w−p_o). 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 (T_sc≅−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 (T_ca≅−88° C.). The heat that is absorbed by the primary fluid as it boils, cools the tip section of the catheter.

Referring initially to FIG. 1, a system for a performing cryoablation procedures is shown and generally designated 10. As shown, the system 10 includes a cryoablation catheter 12 and a primary fluid source 14. Preferably, the primary fluid is nitrous oxide (N₂O) and is held in source 14 at a pressure of around 750 psig. FIG. 1 also shows that the system 10 includes a console 16 and that the console 16 is connected in fluid communication with the primary fluid source 14 via a fluid line 18. Console 16 is also connected in fluid communication with the catheter 12 via a fluid line 20. Further, the console 16 is shown to include a precooler 22, an exhaust unit 24, and a computer 26.

In detail, the components of the catheter 12 will be best appreciated with reference to FIG. 2. There, it will be seen that the catheter 12 includes a catheter tube 28 that has a closed distal end 30 and an open proximal end 32. Also included as part of the catheter 12, are a supply tube 34 that has a distal end 36 and a proximal end 38, and a capillary tube 40 that has a distal end 42 and a proximal end 44. As shown, the distal end 36 of supply tube 34 is connected with the proximal end 44 of the capillary tube 40 to establish a supply line 46. Specifically, supply line 46 is defined by the lumen 48 of supply tube 34 and the lumen 50 of capillary tube 40. It is an important aspect of the system 10 that the diameter (i.e. cross section) of the supply tube 34 is greater than the diameter (i.e. cross section) of the capillary tube 40. The consequence of this difference is that the supply tube 34 presents much less importance to fluid flow than does the capillary tube 40. In turn, this causes a much greater pressure drop for fluid flow through the capillary tube 40. As will be seen, this pressure differential is used to advantage for the system 10.

Still referring to FIG. 2, it is seen that the supply line 46 established by the supply tube 34 and capillary tube 40, is positioned coaxially in the lumen 52 of the capillary tube 28. Further, the distal end 42 of the capillary tube 40 (i.e. also the distal end of the supply line 46) is displaced from the distal end 30 of catheter tube 28 to create an expansion chamber 54 in the tip section 56 of the catheter 12. Additionally, the placement of the supply line 46 in the lumen 52 establishes a return line 58 in the catheter 12 that is located between the supply line 46 and the wall of the catheter tube 28.

Optionally, a sensor 60 can be mounted in expansion chamber 54 (tip section 56). This sensor 60 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 60 can be of a type well known in the art for detecting the desired measurement. Although FIG. 2 shows both a pressure sensor 62 and a valve 64 positioned at the proximal end 38 of the supply tube 34, this is only exemplary as the sensor 62 and valve 64 may actually be positioned elsewhere. The import here is that a pressure sensor 62 is provided to monitor a working fluid pressure, “p_w,” on a fluid refrigerant (e.g. N₂O). In turn, this pressure “p_w” is controlled by a valve 64 as it enters the inlet 66 of the supply line 46. Further, FIG. 2 shows that a pressure sensor 68 is provided to monitor a return pressure “p_r” on the fluid refrigerant as it exits from the outlet 70 of the return line 58.

FIG. 3 indicates that the various sensors mentioned above are somehow electronically connected to the computer 26 in console 16. More specifically, the sensors 60, 62 and 68 can be connected to computer 26 in any of several ways, all known in the pertinent art. Further, FIG. 3 indicates that the computer 26 is operationally connected with the valve 64. The consequence of this is that the computer 26 can be used to control operation of the valve 64, and thus the working pressure “p_w”, in accordance with preprogrammed instructions, using measurements obtained by the sensors 60, 62 and 68 (individually or collectively).

A schematic of various components for system 10 is presented in FIG. 4 which indicates that a compressor 72 is incorporated as an integral part of the precooler 22. More specifically, the compressor 72 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 22. 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 (T_sc=−40° C.).

The operation of system 10 will be best appreciated by cross referencing FIG. 4 with FIG. 5. During this cross referencing, recognize that the alphabetical points (A, B, C, D and E), shown relative to the curve 74 in FIG. 5, are correspondingly shown on the schematic for system 10 in FIG. 4. Further, appreciate that curve 74, 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 76 represents the liquid phase of the refrigerant, and area 78 represents the gaseous phase of the refrigerant.

Point A (FIG. 4 and FIG. 5) represents the primary fluid refrigerant as it is drawn from the fluid source 14, or its back up source 14′. Preferably, point A corresponds to ambient temperature (i.e. room temperature) and a pressure greater than around 700 psig. After leaving the fluid source 14, the pressure on the refrigerant is lowered to a working pressure “p_w” that is around 400 psig. This change is controlled by the regulator valve 64, is monitored by the sensor 62, and is represented in FIG. 5 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 22.

In the precooler 22, the primary refrigerant is cooled to a sub-cool temperature “T_sc” (e.g. −40° C.) that is determined by the boiling point of the secondary refrigerant in the precooler 22. In FIG. 5 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 22, it changes from a gaseous state (area 78) into a liquid state (area 76). Point C in FIG. 5 represents the condition of the primary fluid refrigerant as it enters the supply line 46 of cryocather 12 at the proximal end 38 of supply tube 34. Specifically, the pressure on the primary fluid refrigerant at this point C is the working pressure “p_w”, and the temperature is the sub-cool temperature “T_sc”.

As the primary fluid refrigerant passes through the supply line 46 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 “p_o” that is close to 15 psia. Further, as indicated in FIG. 4, point D identifies the conditions of the primary fluid refrigerant after it has boiled to the tip section 56 as it is leaving the supply line 46 and entering the return line 58 of the catheter 12.

The exhaust unit 24 of the catheter 12 is used to evacuate the primary fluid refrigerant from the expansion chamber 54 of tip section 56 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 “p_r”, measured by the sensor 68, that is slightly less than “p_o”. For the transition from point D to point E, the main purpose of the exhaust unit 24 is to help maintain the outlet pressure “p_o” in the tip section 56 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 12 has an effect on the operation of the catheter 12. Essentially this effect is shown in FIG. 6. There it will be seen that for relatively low mass flow rates (e.g. below point F on curve 80 shown in FIG. 6), 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 10 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 56, “T_t”, variations of T_t can be used to control the mass flow rate of the refrigerant, to thereby control the refrigeration potential of the catheter 12.

In operation, the variables mentioned above (p_w, p_o, p_r, and T_t) can be determined as needed. System 10 then manipulates the regulator valve 64, in response to whatever variables are being used, to vary the working pressure “p_w” of the primary fluid refrigerant as it enters the supply line 46. In this way, variations in “p_w” can be used to control “p_o” and, consequently, the refrigeration potential of the catheter 12.

While the particular Refrigeration Source for a Cryoablation Catheter 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.