WO2001064145A1 - Therapies de refroidissement/dispositif pour angioplastie avec restenose - Google Patents
Therapies de refroidissement/dispositif pour angioplastie avec restenose Download PDFInfo
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- WO2001064145A1 WO2001064145A1 PCT/US2001/006648 US0106648W WO0164145A1 WO 2001064145 A1 WO2001064145 A1 WO 2001064145A1 US 0106648 W US0106648 W US 0106648W WO 0164145 A1 WO0164145 A1 WO 0164145A1
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- balloon
- catheter
- fluid
- warm
- cold
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
- A61B2017/22001—Angioplasty, e.g. PCTA
- A61B2017/22002—Angioplasty, e.g. PCTA preventing restenosis
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
- A61B2017/22051—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation
- A61B2017/22054—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation with two balloons
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00005—Cooling or heating of the probe or tissue immediately surrounding the probe
- A61B2018/00011—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids
- A61B2018/00023—Cooling or heating of the probe or tissue immediately surrounding the probe with fluids closed, i.e. without wound contact by the fluid
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00214—Expandable means emitting energy, e.g. by elements carried thereon
- A61B2018/0022—Balloons
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
- A61B2018/0212—Surgical 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/02—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by cooling, e.g. cryogenic techniques
- A61B2018/0231—Characteristics of handpieces or probes
- A61B2018/0262—Characteristics of handpieces or probes using a circulating cryogenic fluid
Definitions
- Balloon angioplasty or the technology of reshaping of a blood vessel for the purpose of establishing vessel patency using a balloon tipped catheter, has been known since the late 1970' s.
- the procedure involves the use of a balloon catheter that is guided by means of a guidewire through a guiding catheter to the target lesion or vessel blockage.
- the balloon typically is equipped with one or more marker bands that allow the interventionalist to visualize the position of the balloon in reference to the lesion with the aid of fluoroscopy.
- the balloon is inflated with a biocompatible fluid, and pressurized to the appropriate pressure to allow the vessel to open.
- Typical procedures are completed with balloon inflation pressures between 8 and 12 atmospheres.
- the balloon inflation procedure is repeated several times before the lesion or blockage will yield.
- the placement of stents after angioplasty has become popular as it reduces the rate of restenosis.
- Restenosis refers to the renarrowing of the vascular lumen following vascular intervention such as a balloon angioplasty procedure or stent insertion. Restenosis is clinically defined as a greater than 50% loss of initial lumen diameter. The mechanism or root causes of restenosis are still not fully understood. The causes are multifactorial, and are partly the result of the injury caused by the balloon angioplasty procedure and stent placement. With the advent of stents, restenosis rates have dropped from over 30% to 10-20%. Recently, the use and effectiveness of low-dose radiation administered intravascularly following angioplasty is being evaluated as a method to alter the DNA or RNA of an affected vessel's cells in the hope of reducing cell proliferation.
- Atrial fibrillation refers to very rapid irregular contractions of the atria of the heart resulting in a lack of synchronization between the heartbeat and the pulse. The irregular contractions are due to irregular electrical activity that originates in the area of the pulmonary veins.
- a proposed device, currently under development, for treating atrial fibrillation is a balloon filled with saline that can be ultrasonically agitated and heated. This device is inserted in the femoral vein and snaked into the right atrium. The device is then poked through the interatrial septum and into the left atrium, where it is then angled into the volume adjoining the suspect pulmonary vein with the left atrium.
- the above technique is disadvantageous in that circumferential portions of the tissue, desired to be necrosed, are not in fact affected. Other techniques, including RF ablation, are similarly inefficient. Moreover, these techniques leave the necrosed portions with jagged edges, i.e., there is poor demarcation between the healthy and the necrosed tissue. These edges can then cause electrical short circuits, and associated electrical irregularities, due to the high electric fields associated with jagged edges of a conductive medium.
- the above technique is also disadvantageous in that heating is employed. Heating is associated with several problems, including increased coagulum and thrombus formation, leading to emboli. Heating also stimulates stenosis of the vein.
- tissues can only safely be heated to temperatures of less than or about 75°C - 85°C due to charring and tissue rupture secondary to steam formation.
- the thermal gradient thus induced is fairly minimal, leading to a limited heat transfer.
- heating causes tissues to become less adherent to the adjacent heat transfer element, the tissue contact with the heat transfer element is also reduced, further decreasing the heat transfer.
- the present invention provides an enhanced method and device to inhibit or reduce the rate of restenosis following angioplasty or stent placement.
- the invention is similar to placing an ice pack on a sore or overstrained muscle for a period of time to minimize or inhibit the bio-chemical events responsible for an associated inflammatory response.
- An embodiment of the invention generally involves placing a balloon-tipped catheter in the area treated or opened through balloon angioplasty immediately following angioplasty.
- a so- called "cryoplasty" balloon which can have a dual balloon structure, may be delivered through a guiding catheter and over a guidewire already in place from a balloon angioplasty.
- the dual balloon structure has benefits described below and also allows for a more robust design, providing significant safety advantages to the patient because two balloons must be broken if cooling fluid is to deleteriously infuse into the patient .
- the dual balloon may be centered in the recently opened vessel with the aid of radio opaque marker bands, indicating the "working length" of the balloon. In choosing a working length, it is important to note that typical lesions may have a size on the order of 2-3 cm.
- a biocompatible heat transfer fluid which may contain contrast media, may be infused through the space between the dual balloons. While this fluid does not circulate in this embodiment, once it is chilled or even frozen by thermal contact with a cooling fluid, it will stay sufficiently cold for therapeutic purposes.
- a biocompatible cooling fluid with a temperature between about, e.g., - 40°C and -60°C, may be injected into the interior of the inner balloon, and circulated through a supply lumen and a return lumen.
- the fluid exits the supply lumen through a skive in the lumen, and returns to the refrigeration unit via another skive and the return lumen.
- the biocompatible cooling fluid chills the biocompatible heat transfer fluid between the dual balloons to a therapeutic temperature between about, e.g., 0°C and -50°C.
- the chilled heat transfer fluid between the dual balloons transfers thermal energy through the balloon wall and into the adjacent intimal vascular tissue for the appropriate therapeutic length of time.
- the circulation of the biocompatible cooling fluid is stopped, and the heat transfer fluid between the dual balloons withdrawn through the annular space. Both balloons may be collapsed by means of causing a soft vacuum in the lumens. Once collapsed, the cryoplasty catheter may be withdrawn from the treated site and patient through the guiding catheter.
- the invention is directed to a device to treat tissue, including an outer tube, an an inner tube disposed at least partially within the outer tube, and a dual balloon including an inner balloon and an outer balloon, the inner balloon coupled to the inner tube at a proximal and at a distal end, the outer balloon coupled to the inner tube at a distal end and to the outer tube at a proximal end.
- a first interior volume is defined between the outer balloon and the inner balloon in fluid communication with an inlet in the volume between the outer tube and the inner tube .
- Variations of the invention may include one or more of the following.
- the inner tube may further define a guidewire lumen, a supply lumen, and return lumen.
- the supply lumen may define a hole or skive such that a fluid flowing in the supply lumen may be caused to flow into a volume defined by the inner balloon
- the return lumen may define a hole or skive such that a fluid flowing in a volume defined by the inner balloon may be caused to flow into the return lumen.
- the guidewire lumen may extend from a proximal end of the inner tube to a distal end of the inner tube.
- the device may further comprise at least two radially extending tabs disposed around a circumference of the inner tube to substantially center the inner tube within the dual balloon.
- the device may further comprise at least one marker band disposed on the inner tube to locate a working region of the device at a desired location.
- the device may further comprise a source of chilled fluid having a supply tube and a return tube, the supply tube coupled in fluid communication to the supply lumen and the return tube coupled in fluid communication to the return lumen.
- a source of fluid may also be included, the source of fluid coupled in fluid communication to a volume between the inner balloon and the outer balloon.
- the fluid may be a perfluorocarbon such as Galden fluid.
- the fluid may also include contrast media.
- the invention is directed to a method of reducing restenosis after angioplasty in a blood vessel .
- the method includes inserting a catheter into a blood vessel, the catheter having a balloon.
- the balloon is then inflated with a perfluorocarbon such that an exterior surface of the balloon is in contact with at least a partial inner perimeter of the blood vessel, the perfluorocarbon having a temperature in the range of about -10°C to -50°C.
- Variations of the method may include one or more of the following.
- the method may include disposing the catheter at a desired location using at least one radio opaque marker band.
- the method may include flowing the perfluorocarbon into the balloon using a supply lumen and exhausting the perfluorocarbon from the balloon using a return lumen.
- the balloon may be a dual balloon, and the method may further include providing a heat transfer fluid in the volume between the dual balloons.
- the heat transfer fluid may include a contrast media fluid.
- the method may include disposing the catheter such that at least a portion of the balloon is in a coronary artery or in a carotid artery.
- the invention is directed to a method of reducing atrial fibrillation.
- the method includes inserting a catheter at least partially into the heart, the catheter having a balloon, a portion of the balloon located in the left atrium and a portion of the balloon located in a pulmonary vein.
- the balloon is then inflated with a perfluorocarbon such that an exterior surface of the balloon is in contact with at least a partial circumference of the portion of the pulmonary vein adjacent the left atrium, the perfluorocarbon having a temperature in the range of about -10°C to -50°C.
- Variations of the method may include one or more of the following.
- the balloon may have a working region having a length of between about 5 mm and 10 mm.
- the method may further include inserting a wire having a needle point from the femoral vein into the right atrium and forming a hole using the needle point in the interatrial septum between the right atrium and the left atrium.
- a guide catheter may then be inserted into the right atrium.
- a guide wire may further be inserted through the guide catheter into the right atrium and further into a pulmonary vein.
- the catheter may then be disposed over the guidewire into a volume defined by the joint of the right atrium and the pulmonary vein.
- the invention inhibits or reduces the rate of restenosis following a balloon angioplasty or any other type of vascular intervention. At least the following portions of the vascular anatomy can benefit from such a procedure: the abdominal aorta (following a stent or graft placement) , the coronary arteries (following PTCA or rotational artherectomy) , the carotid arteries (following an angioplasty or stent placement) , as well as the larger peripheral arteries.
- FIG. 1A shows a side schematic view of a catheter according to a first embodiment of the invention.
- FIG. IB shows a cross- sectional view of the catheter of FIG. 1A, as indicated by lines IB- IB in FIG. 1A.
- FIG. 1C shows an alternate cross-sectional view of the catheter of FIG. 1A, as indicated by lines IB-IB in FIG. 1A.
- FIG. 2A shows a side schematic view of a catheter according to a second embodiment of the invention.
- FIG. 2B shows a cross-sectional view of the catheter of FIG. 2A, as indicated by lines 2B-2B in FIG. 2A.
- FIG. 3 shows a schematic view of a catheter in use according to a third embodiment of the invention.
- FIG. 4 shows a cross-sectional view of the catheter of FIG. 3.
- FIG. 5 shows an alternative cross -sectional view of the catheter of FIG. 3.
- FIG. 6 shows an alternative cross-sectional view of the catheter of FIG. 3.
- FIG. 7 shows a schematic view of the warm balloon of the catheter of FIG. 3.
- a catheter 100 is shown according to a first embodiment of the invention.
- the catheter 100 has a proximal end 130 and a distal end 114.
- this figure is not necessarily to scale and in general use the proximal end 130 is far upstream of the features shown in FIG. 1A.
- the catheter 100 may be used within a guide catheter 102, and generally includes an outer tube 103, a dual balloon 134, and an inner tube 122. These parts will be discussed in turn.
- the guide catheter 102 provides a tool to dispose the catheter 100 adjacent the desired location for, e.g., angioplasty or reduction of atrial fibrillation.
- Typical guide catheter diameters may be about 6 french to 9 french, and the same may be made of polyether blockamide, polyamides, polyurethanes, and other similar materials.
- the distal end of the guide catheter is generally adjacent the proximal end of the dual balloon 134, and further is generally adjacent the distal end of the outer tube 103.
- the ability to place the guide catheter is a significant factor in the size of the device.
- a suitably sized guide catheter must be used. This restricts the size of the catheter 100 that may be disposed within the guide catheter. A typical diameter of the catheter 100 may then be about 7 french or less or about 65 to 91 mils.
- a catheter for use in the coronary arteries is described. Of course, which catheter is used in which artery is a matter to be determined by the physician, taking into account such factors as the size of the individual patient's affected arteries, etc.
- the outer tube 103 houses the catheter 100 while the latter traverses the length of the guide catheter 102.
- the outer tube 103 may have a diameter of about 4 french to 7 french, and the same may be made of polyether blockamide, poly-butylene terephtalate, polyurethane, polyamide, polyacetal polysulfone, polyethylene, ethylene tetrafluoroethylene, and other similar materials.
- the distal end of the outer tube 103 adjoins the proximal end of the dual balloon 134.
- the outer tube 103 provides a convenient location for mounting a proximal end of an outer balloon 104 within the dual balloon 134, and further may provide an inlet 128 for providing a fluid such as a liquid to a first interior volume 106 between the dual balloons.
- a fluid such as a liquid to a first interior volume 106 between the dual balloons.
- an inlet 128 per se may not be necessary: the fluid, which may also be a sub-atmospheric level of gas or air, may be provided during manufacture in the first interior volume 106.
- the proximal and distal ends of the first interior volume may be sealed during manufacture.
- the inlet 128 may be at least partially defined by the annular volume between the interior of the outer tube 103 and the exterior of the inner tube 122.
- the dual balloon 134 includes an outer balloon 104 and an inner balloon 108. Between the two is the first interior volume 106.
- the outer balloon 104 may be inflated by inflating the interior volume 106.
- the inner balloon 108 has a second interior volume 110 associated with the same.
- the inner balloon 108 may be inflated by inflating the second interior volume 110.
- both the inner balloon 108 and the outer balloon 104 may be inflated using biocompatible liquids, such as Galden ® fluid, perfluorocarbon-based liquids, or various contrast agents. There is no need that the fluid inflating one of the interior volumes be the same fluid as that inflating the other. Additional details on these fluids are described below.
- this fluid may be, e.g., stationary or static: in other words, it need not be circulated.
- this fluid would in general be circulated by an external chiller (not shown) .
- the chiller may be, e.g., a gear pump, peristaltic pump, etc. It may be preferable to use a gear pump over a peristaltic pump as the attainable pressure of the former is generally greater than that of the latter.
- gear pumps have the advantageous property of being linear, i.e., their output varies in direction proportion with their revolutions per minute. Two types of gear pumps which may be employed include radial spur gear pumps and helical tooth gear pumps.
- the helical tooth gear pump may be more preferable as the same has been associated with higher pressures and a more constant output.
- the ability to achieve high pressures may be important as the cooling fluid is required to pass through a fairly narrow, e.g., five to seven french, catheter at a certain rate.
- the viscosity of the fluid, at the low temperatures should be appropriately low. In this way, e.g., the flow may be increased.
- an appropriate type of fluid may be Galden ® fluid, and in particular Galden ® fluid item number "HT-55", available from Ausimont Inc. of Thorofare, NJ. At -55°C, this fluid has a viscosity of 2.1 centiStokes. At -70°C, this fluid has a viscosity of 3.8 centiStokes. It is believed that fluids with such viscosities at these temperatures would be appropriate for use.
- the so-called “cones” of the balloons 108 and 104 may be made somewhat thicker than the remainder of the balloon sections. In this way, the heat transfer efficiency in these sections is significantly less than over the remainder of the balloon sections, this "remainder” effectively defining a "working region” of the balloon. In this way, the cooling or "cryoplasty" may be efficiently localized to the affected area rather than spread over the length of the balloon.
- the inner tube 122 is disposed within the interior of the dual balloon 134 and within the interior of the guide catheter 102.
- the inner tube 122 includes a supply lumen 120, a return lumen 118, and a guidewire lumen 116.
- the guidewire lumen 116 may have sizes of, e.g., 17 or 21 mils inner diameter, in order to accommodate current standard sized guidewires, such as those having an outer diameter of 14 mils. This structure may be preferable, as the pressure drop encountered may be substantially less.
- the supply lumen 120 may be used to supply a circulating liquid to the second interior volume 110.
- the return lumen 118 may be used to exhaust the circulating liquid from the second interior volume to the external chiller. As may be seen from FIG.
- both lumens 118 and 120 may terminate prior to the distal end 114 of the catheter 100.
- the lumen arrangement may be seen more clearly in Fig. IB.
- Fig. 1C shows an alternate such arrangement, and one that may provide an even better design for minimal pressure drop.
- lumens 118' and 120' are asymmetric about guidewire lumen 116'.
- a set of radio opaque marker bands 112 may be disposed on the inner tube 122 at locations substantially adjacent the cones 132 to define a central portion of the "working region" of the balloons 104 and 108. This working region is where the "cryoplasty" procedures described below may substantially occur.
- the proximal portion of the outer balloon 104 is mounted on the outer tube 103 at its distal end.
- the distal end of the outer balloon 104 is secured to the distal end of the catheter 100 and along the inner tube 122.
- both the proximal and distal ends of the inner balloon 108 may be secured to the inner tube 122 to create a sealed second interior volume 110.
- At least two skives 124 and 126 may be defined by the inner tube 122 and employed to allow the working fluid to exit into the second interior volume 110 and to exhaust the same from the second interior volume 10.
- the skive 124 is in fluid communication with the lumen 120 and the skive 126 is in fluid communication with the lumen 118.
- fluid communication refers to a relationship between two vessels where a fluid pressure may cause a net amount of fluid to flow from one vessel to the other.
- the skives may be formed by known techniques .
- a suitable size for the skives may be from about 50 mils to 125 mils.
- a plurality of tabs 119 may be employed to roughly or substantially center the inner tube 122 within the catheter 100. These tabs may have the shape shown, the shape of rectangular or triangular solids, or other such shapes so long as the flow of working fluid is not unduly impeded. In this specification, the phrase "the flow of working fluid is not unduly impeded” is essentially equated to the phrase “substantially center” .
- the tabs 119 may be made of polyether blockamide, poly-butylene terephtalate, polyurethane, polyamide, polyacetal polysulfone, polyethylene, ethylene tetrafluoroethylene, and other similar materials, and may have general dimensions of from about 3 mils to 10 mils in height, and by about 10 mils to 20 mils in width.
- the guide catheter 102 may be inserted into an affected artery or vein such that the distal tip of the guide catheter is just proximal to an affected area such as a calcified area or lesion.
- an affected area such as a calcified area or lesion.
- typical lesions do not occur in the venous system, but only in the arterial .
- the guide catheter may be placed using a guide wire (not shown) . Both the guide catheter and guide wire may already be in place as it may be presumed a balloon angioplasty or stent placement has previously been performed.
- the catheter 100 may then be inserted over the guide wire via the lumen 116 and through the guide catheter 102. In general, both a guide wire and a guide catheter are not strictly necessary - one or the other may often suffice.
- the dual balloon 134 may be uninflated to maintain a minimum profile. In fact, a slight vacuum may be drawn to further decrease the size of the dual balloon 134 so long as the structural integrity of the dual balloon 134 is not thereby compromised.
- a fine positioning step may occur by way of the radio opaque marker bands 112.
- the location of the radio opaque marker bands 112 can be identified in relation to the location of the lesion.
- the catheter may be advantageously placed at the location of the lesion and further such that the lesion is between the two marker bands. In this way, the working region of the balloon 134 will substantially overlap the affected area, i.e., the area of the lesion.
- a biocompatible heat transfer fluid which may also contain contrast media, may be infused into the first interior volume 106 through the inlet 128. While the use of contrast media is not required, its use may allow early detection of a break in the balloon 104 because the contrast media may be seen via fluoroscopy to flow throughout the patient's vasculature.
- a biocompatible cooling fluid may be circulated through the supply lumen 120 and the return lumen 118. Before or during the procedure, the temperature of the biocompatible cooling fluid may be lowered to a therapeutic temperature, e.g., between -40°C and -60°C, although the exact temperature required depends on the nature of the affected area.
- the fluid exits the supply lumen 120 through the skive 124 and returns to the chiller through the skive 126 and via the return lumen 118. It is understood that the respective skive functions may also be reversed without departing from the scope of the invention.
- the biocompatible cooling fluid in the second interior volume 110 chills the biocompatible heat transfer fluid within the first interior volume 106 to a therapeutic temperature of, e.g., between about -25°C and -50°C.
- the chilled heat transfer fluid transfers thermal energy through the wall of the balloon 104 and into the adjacent intimal vascular tissue for an appropriate therapeutic length of time. This time may be, e.g., about Vz to 4 minutes .
- the circulation of the biocompatible cooling fluid may cease.
- the heat transfer fluid within the first interior volume 106 may be withdrawn though the inlet 128.
- the balloons 104 and 108 may be collapsed by pulling a soft vacuum through any or all of the lumens 124, 126, and 128. Following collapse, the catheter 100 may be withdrawn from the treatment site and from the patient through the guide catheter 102. To inhibit restenosis, the following therapeutic guidelines may be suggested:
- Substantially the same catheter may be used to treat atrial fibrillation.
- the catheter is inflated as above once it is in location.
- the location chosen for treatment of atrial fibrillation is such that the working region spans a portion of the left atrium and a portion of the affected pulmonary vein.
- the working region of the catheter may have a length of about 5 mm to 30 mm.
- the affected pulmonary vein, of the four possible pulmonary veins, which enter the left atrium, may be determined by electrophysiology studies .
- a catheter with a needle point may first be inserted at the femoral vein and routed up to the right atrium.
- the needle of the catheter may then be poked through the interatrial septum and into the left atrium.
- the catheter may then be removed if desired and a guide catheter disposed in the same location.
- a guide wire may be used through the guide catheter and may be maneuvered at least partially into the pulmonary vein.
- a catheter such as the catheter 100 may be placed in the volume defining the intersection of the pulmonary vein and the left atrium.
- a method of use similar to that disclosed above is then employed to cool at least a portion of, and preferably all of, the circumferential tissue.
- the coldness of the balloon assists in the adherence of the circumferential tissue to the balloon, this feature serving to increase the overall heat transfer rate.
- the catheter 100 above may be particularly useful for procedures in the carotid arteries by virtue of its size.
- an even smaller catheter may be desired. For example, one with an outer diameter less than 5 french may be desired.
- a catheter 200 is shown according to a second embodiment of the invention.
- the catheter 200 may be particularly useful for use in the coronary arteries because the dimensions of the catheter 200 may be considerably smaller than the dimensions of the catheter 100.
- the catheter 200 is similar to the above-described catheter 100.
- the catheter 200 has a proximal end 230 and a distal end 214 and may be used within a guide catheter 202.
- the catheter 200 includes an outer tube 203, a dual balloon 234, and an inner tube 222.
- the ability to place the guide catheter is a significant factor in the size of the device.
- a suitably sized guide catheter may be used to perform angioplasty in the coronary arteries. This then restricts the size of the catheter 200 which may be disposed within the guide catheter.
- a typical diameter of the catheter 200 may then be about 3 french or less or about 35-39 mils. The same may be placed in the femoral artery in order to be able to track to the coronary arteries in a known manner.
- the outer tube 203 houses the catheter 200 and may have an outside diameter of about 5 french to 7 french, and the same may be made of similar materials.
- the distal end of the outer tube 203 adjoins the proximal end of the dual balloon 234.
- the outer tube 203 provides a mounting location for an outer balloon 204, and further provides an inlet 228 for providing a fluid such as a liquid to a first interior volume 206 between the dual balloons.
- an inlet 228 per se may not be necessary: the fluid, which may also be a sub-atmospheric level of air, may be provided in the first interior volume 206.
- the proximal and distal ends of the volume may be sealed during manufacture.
- the inlet 228 may be at least partially defined by the annular volume between the interior of the outer tube 203 and the exterior of the inner tube 222.
- the dual balloon 234 includes an outer balloon 204 and an inner balloon 208. These balloons are basically similar to balloons 104 and 108 described above, but may be made even smaller for use in the smaller coronary arteries.
- the same types of fluids may be used as in the catheter 100.
- the inner tube 222 is disposed within the interior of the dual balloon 234 and within the interior of the guide catheter 202.
- the inner tube 222 includes a supply lumen 220 and a return lumen 218.
- a set of radio opaque marker bands 212 may be disposed on the inner tube 222 for the same reasons disclosed above in connection with the marker bands 112.
- the proximal portion of the outer balloon 204 is mounted on the outer tube 203 at its distal end.
- the distal end of the outer balloon 204 is secured to the distal end of the catheter 200 and along the inner tube 222.
- both the proximal and distal ends of the inner balloon 208 may be secured to the inner tube 222 to create a sealed second interior volume 210.
- At least two skives 224 and 226 may be defined by the inner tube 222 and employed to allow the working fluid to exit into the second interior volume 210 and to exhaust the same from the second interior volume 210.
- a plurality of tabs 219 may be employed to roughly or substantially center the inner tube 222 within the catheter 200 as in catheter 100. These tabs may have the same general geometry and design as tabs 119. Of course, they may also be appropriately smaller to accommodate the smaller dimensions of this coronary artery design.
- the tabs 119 and 219 are particularly important in the catheters 100 and 200, as contact by the inner tube of the outer tube may also be associated with an undesired conductive heat transfer prior to the working fluid reaching the working region, thereby deleteriously increasing the temperature of the working fluid at the working region.
- the method of use of the catheter 200 is generally the same as for the catheter 100.
- Known techniques may be employed to place the catheter 200 into an affected coronary artery.
- an external guidewire may be used with appropriate attachments to the catheter.
- a catheter 300 which may be employed in PV ablation is detailed.
- a dual balloon system 301 is shown; however, the balloons are not one within the other as in Fig. 1.
- a warm balloon 302 is distal of a cold balloon 304.
- Warm balloon 302 may be used to anchor the system 301 against movements, which may be particularly useful within a beating heart.
- Cold balloon 304 may then be employed to cryo-ablate a circumferential lesion at the point where a pulmonary vein 306 enters the left atrium 308.
- a working fluid may be introduced via an outlet port 308 and may be retrieved via an inlet port 310.
- Ports 308 and 310 may be skived in known fashion into the catheter shaft lumens whose design is exemplified below.
- the warm balloon 302 serves to anchor the system 301 in the pulmonary vein and left atrium.
- the warm balloon 302 also serves to stop blood, which is traveling in the direction indicated by arrow 312, from freezing upon contact with the cold balloon 304. In this way, the warm balloon 302 acts as an insulator to cold balloon 304.
- the warm balloon 302 may be served by only one skived port, or by two ports, such as an inlet port 314 and an outlet port 316, as shown in Fig. 3.
- a separate lumen or lumens may be used to fill the warm balloon.
- a valve mechanism may be used to fill the warm balloon using fluid from the cold balloon. In the case where only one port is used to fill the warm balloon, draining the same requires a slight vacuum or negative pressure to be placed on the lumen servicing the inlet/outlet port.
- a benefit to the two lumen design is that the warm balloon may be inflated and deflated in a more expeditious manner.
- Typical pressures within the warm balloon may be about 1-2 atm (10-30 psi) , and thus maintains a fairly low pressure.
- An appropriate fluid will be biocompatible, and may be Galden fluid, D5W, and so on.
- Typical pressures within the cold balloon may be about 5-7 atm, for example about 6 atm (e.g., at about 100 psi), and thus maintains a higher pressure.
- An appropriate fluid may be Galden fluid, e.g., HT-55, D5W, and so on.
- the volume of fluid required to fill the cold balloon may vary, but may be about 4-8 cc .
- the cold balloon may be about 2 to 2 Vz cm long, and have a diameter of 1 to 2 Vz cm.
- the warm balloon may be glued or otherwise attached to the cold balloon.
- draining both balloons may simply entail closing either the return lumen or the supply lumen, and drawing a vacuum on the other. In this way, both the cold and warm balloons may be evacuated.
- a standard medical "indeflator" may be used to pressurize and de- pressurize the various lumens and balloons.
- Fig. 4 shows an embodiment of the arrangement of lumens within the catheter.
- supply and return lumens for the cold balloon 304 are shown by lumens 318 and 320, respectively.
- Supply and return lumens for the warm balloon 302 are shown by lumens 322 and 324, respectively, although as noted only one may be used as required by the dictates of the user.
- a guidewire lumen 326 is also shown.
- An alternative arrangement is shown in Fig. 5, where the corresponding lumens are shown by primes .
- FIG. 6 an alternative lumen design is shown in which the cold fluid supply lumen 328 is exposed to only the cold fluid return lumen 330.
- An insulation space 332 may also be employed. In this way, the heat flux from the exterior flow is minimized and the cold fluid may reach the cold balloon at a lower temperature.
- One drawback to such a system is that the operational pressure may be higher.
- the overall catheter outer diameter may be about .130", e.g. about 10 french, including an insulation sleeve and guide discussed below.
- the catheter shaft 303 itself may be about .110" and may be made of, e.g., polyethylene (PE) , and preferably a combination of a low density PE and a high density PE .
- the inlet and outlet ports or inlet/outlet port of the warm balloon may be skived from the lumens 322 and 324.
- the warm balloon 302 itself may be made of a sleeve 332 of silicone tubing of, e.g., 35 durometer on the "D" scale, and held in place by two pieces of PET heat shrink tubing 334.
- Alternative methods of securing the warm balloon during inflation may include metal bands or an adhesive.
- marker bands 336 may be employed within either or both of the cold balloon and warm balloon to assist the physician is disposing the same in an appropriate location.
- the marker bands typically denote the working areas of the balloons, and may be made of Pt, Iridium, Au, etc.
- the working cold fluid may exit the circulation system or chiller at, e.g., about -85°C.
- the circulation system or chiller may be, e.g., a two-stage heat exchanger.
- the fluid may then enter the catheter at about -70°C to about -75°C, and may strike the balloon at about -55°C to about -65°C.
- the overall procedure may take less than a minute to circumferentially ablate the desired tissue up to several minutes.
- these numbers are only exemplary and the same depend on the design of the system and fluids used.
- Mapping electrodes 338 may be employed at the distal end of the warm balloon. These mapping electrodes may each have a wire attached, the wires extending down, e.g., the supply and return lumens for the warm fluid or the cold fluid. The mapping electrodes 338 may be used to detect stray electrical fields to determine where ablation may be needed and/or whether the ablation procedure was successful . The mapping electrodes may typically be about 2-3 mm apart from each other.
- Construction of the warm balloon typically involves adhering the same to the shaft 303 and skiving the inlet and outlet ports.
- the silicone sleeve 340 may then serve to further insulate the non-working sections of the balloons from blood that would otherwise potentially freeze during a procedure.
- the silicone sleeve would typically be attached only at a portion of its length, such as that indicated by circle 342, so that the same may slide along the balloon as the balloon is inflated. In addition to insulation effects, the silicone sleeve also serves to assist in collapsing the balloon during deflation.
- the entire catheter shaft 303 may be surrounded by an insulation catheter sleeve 344 (see Fig. 4) .
- Sleeve 344 may have a thickness of, e.g., 0.01 inches, and may be made of a foamed extrusion, e.g., that with voids of air disposed within. The voids further assist the insulating effect since their heat transfer is extremely low. A void to polymer ratio of, e.g., 20% to 30% may be particularly appropriate.
- foamed extrusions are available from, e.g., Applied Medical Resources in Website, CA, or Extrusioneering, Inc., in Temecula, CA.
- an insulation sleeve may be used as noted above .
- the invention has been described above with respect to particular embodiments. It will be clear to one of skill in the art that numerous variations may be made from the above embodiments with departing from the spirit and scope of the invention.
- the invention may be combined with stent therapies or other such procedures.
- the dual balloon disclosed may be used after angioplasty or may be an angioplasty balloon itself.
- Fluids that may be used as heat transfer fluids include perfluorocarbon-based liquids, i.e., halogenated hydrocarbons with an ether bond, such as FC 72.
- Other materials that may be used include CFCs, Freon ® , or chemicals that when placed together cause an endothermic reaction.
- low viscosity materials are used as these result generally in a lessened pressure drop.
- the balloons may be made, e.g., of Pebax, PET/PEN, PE, PA 11/12, PU, or other such materials .
- Either or both of the dual balloons may be doped to improve their thermal conductivities.
- the shaft of inner tube 122 may be made of Pebax, PBT, Pl/PEI, PU, PA 11/12, SI, or other such materials.
- the precise shapes and dimensions of the inner and outer lumens, while indicated in, e.g., Figs. IB, 1C, and 2B, may vary.
- the lumen design shown in Figs. 1B-1C may be employed in the catheter of Fig. 2A and vice-versa.
- Embodiments of the invention may be employed in the field of cold mapping, where a circle of tissue is cooled to see if the affected part has been reached. If the affected tissue is that which is being cooled, a more vigorous cooling may be instituted.
- Other variations will be clear to one of skill in the art, thus the invention is limited only by the claims appended hereto.
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- Life Sciences & Earth Sciences (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Medical Informatics (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Otolaryngology (AREA)
- Molecular Biology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
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- Media Introduction/Drainage Providing Device (AREA)
- Thermotherapy And Cooling Therapy Devices (AREA)
Abstract
Priority Applications (6)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP01916337A EP1261304A4 (fr) | 2000-03-01 | 2001-03-01 | Therapies de refroidissement/dispositif pour angioplastie avec restenose |
CA002400753A CA2400753A1 (fr) | 2000-03-01 | 2001-03-01 | Therapies de refroidissement/dispositif pour angioplastie avec restenose |
JP2001563045A JP2003524506A (ja) | 2000-03-01 | 2001-03-01 | 再狭窄を伴う血管形成術のための冷却療法及び装置 |
AU4337401A AU4337401A (en) | 2000-03-01 | 2001-03-01 | Cooling therapies/device for angioplasty with restenosis |
AU2001243374A AU2001243374B2 (en) | 2000-03-01 | 2001-03-01 | Cooling therapies/device for angioplasty with restenosis |
US09/787,599 US6602276B2 (en) | 1998-03-31 | 2001-03-01 | Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US51631900A | 2000-03-01 | 2000-03-01 | |
US09/516,319 | 2000-03-01 |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US51631900A Continuation-In-Part | 1998-03-31 | 2000-03-01 |
Related Child Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/787,599 A-371-Of-International US6602276B2 (en) | 1998-03-31 | 2001-03-01 | Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation |
US10/608,978 Division US20040087934A1 (en) | 1998-03-31 | 2003-06-26 | Method and device for performing cooling- or cryo-therapies for, E.G., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2001064145A1 true WO2001064145A1 (fr) | 2001-09-07 |
Family
ID=24055036
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2001/006648 WO2001064145A1 (fr) | 1998-03-31 | 2001-03-01 | Therapies de refroidissement/dispositif pour angioplastie avec restenose |
Country Status (5)
Country | Link |
---|---|
EP (1) | EP1261304A4 (fr) |
JP (1) | JP2003524506A (fr) |
AU (2) | AU4337401A (fr) |
CA (1) | CA2400753A1 (fr) |
WO (1) | WO2001064145A1 (fr) |
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Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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 |
US6602246B1 (en) | 2000-08-18 | 2003-08-05 | Cryovascular Systems, Inc. | Cryotherapy method for detecting and treating vulnerable plaque |
US6786900B2 (en) | 2001-08-13 | 2004-09-07 | Cryovascular Systems, Inc. | Cryotherapy methods for treating vessel dissections and side branch occlusion |
US6908462B2 (en) | 1997-12-02 | 2005-06-21 | Cryovascular Systems, Inc. | Apparatus and method for cryogenic inhibition of hyperplasia |
US6955174B2 (en) | 2000-08-18 | 2005-10-18 | Uryovascular Systems, Inc. | Cryotherapy method for detecting and treating vulnerable plaque |
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US8016740B2 (en) | 2000-04-14 | 2011-09-13 | Attenuex Technologies, Inc. | Pressure attenuation device |
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Families Citing this family (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7374532B2 (en) | 2000-04-14 | 2008-05-20 | Attenuex Technologies, Inc. | High vapor pressure attenuation device |
US7758572B2 (en) * | 2004-05-20 | 2010-07-20 | Boston Scientific Scimed, Inc. | Medical devices and methods including cooling balloons having nanotubes |
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US9931153B2 (en) * | 2013-03-15 | 2018-04-03 | Spiration, Inc. | Thermochemical reaction ablation catheter |
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Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5630837A (en) * | 1993-07-01 | 1997-05-20 | Boston Scientific Corporation | Acoustic ablation |
US5971979A (en) * | 1997-12-02 | 1999-10-26 | Odyssey Technologies, Inc. | Method for cryogenic inhibition of hyperplasia |
Family Cites Families (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5868735A (en) * | 1997-03-06 | 1999-02-09 | Scimed Life Systems, Inc. | Cryoplasty device and method |
-
2001
- 2001-03-01 JP JP2001563045A patent/JP2003524506A/ja active Pending
- 2001-03-01 EP EP01916337A patent/EP1261304A4/fr not_active Withdrawn
- 2001-03-01 AU AU4337401A patent/AU4337401A/xx active Pending
- 2001-03-01 WO PCT/US2001/006648 patent/WO2001064145A1/fr not_active Application Discontinuation
- 2001-03-01 CA CA002400753A patent/CA2400753A1/fr not_active Abandoned
- 2001-03-01 AU AU2001243374A patent/AU2001243374B2/en not_active Ceased
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5630837A (en) * | 1993-07-01 | 1997-05-20 | Boston Scientific Corporation | Acoustic ablation |
US5971979A (en) * | 1997-12-02 | 1999-10-26 | Odyssey Technologies, Inc. | Method for cryogenic inhibition of hyperplasia |
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US9089340B2 (en) | 2010-12-30 | 2015-07-28 | Boston Scientific Scimed, Inc. | Ultrasound guided tissue ablation |
US9283021B2 (en) | 2011-04-13 | 2016-03-15 | Cryotherapeutics Gmbh | Plaque stabilization using cryoenergy |
US8968282B2 (en) | 2011-04-13 | 2015-03-03 | Cryotherapeutics Gmbh | Plaque stabilisation using cryoenergy |
US10588682B2 (en) | 2011-04-25 | 2020-03-17 | Medtronic Ardian Luxembourg S.A.R.L. | Apparatus and methods related to constrained deployment of cryogenic balloons for limited cryogenic ablation of vessel walls |
US9241687B2 (en) | 2011-06-01 | 2016-01-26 | Boston Scientific Scimed Inc. | Ablation probe with ultrasonic imaging capabilities |
US9603659B2 (en) | 2011-09-14 | 2017-03-28 | Boston Scientific Scimed Inc. | Ablation device with ionically conductive balloon |
US9463064B2 (en) | 2011-09-14 | 2016-10-11 | Boston Scientific Scimed Inc. | Ablation device with multiple ablation modes |
US9241761B2 (en) | 2011-12-28 | 2016-01-26 | Koninklijke Philips N.V. | Ablation probe with ultrasonic imaging capability |
US9757191B2 (en) | 2012-01-10 | 2017-09-12 | Boston Scientific Scimed, Inc. | Electrophysiology system and methods |
US8945015B2 (en) | 2012-01-31 | 2015-02-03 | Koninklijke Philips N.V. | Ablation probe with fluid-based acoustic coupling for ultrasonic tissue imaging and treatment |
US10420605B2 (en) | 2012-01-31 | 2019-09-24 | Koninklijke Philips N.V. | Ablation probe with fluid-based acoustic coupling for ultrasonic tissue imaging |
US9241752B2 (en) | 2012-04-27 | 2016-01-26 | Medtronic Ardian Luxembourg S.A.R.L. | Shafts with pressure relief in cryotherapeutic catheters and associated devices, systems, and methods |
US9872718B2 (en) | 2012-04-27 | 2018-01-23 | Medtronic Adrian Luxembourg S.a.r.l. | Shafts with pressure relief in cryotherapeutic catheters and associated devices, systems, and methods |
US11751931B2 (en) | 2012-04-27 | 2023-09-12 | Medtronic Ardian Luxembourg S.A.R.L. | Cryotherapeutic devices for renal neuromodulation and associated systems and methods |
US10905490B2 (en) | 2012-04-27 | 2021-02-02 | Medtronic Ardian Luxembourg S.A.R.L. | Cryotherapeutic devices for renal neuromodulation and associated systems and methods |
US8894563B2 (en) | 2012-08-10 | 2014-11-25 | Attenuex Technologies, Inc. | Methods and systems for performing a medical procedure |
US9801658B2 (en) | 2012-08-10 | 2017-10-31 | Attenuex Technologies, Inc. | Removal device |
US10531894B2 (en) | 2012-08-10 | 2020-01-14 | Solace Therapeutics, Inc. | Methods and systems for performing a medical procedure |
US8864649B2 (en) | 2012-08-10 | 2014-10-21 | Attenuex Technologies, Inc. | Methods and systems for performing a medical procedure |
US10543071B2 (en) | 2012-08-10 | 2020-01-28 | Solace Therapeutics, Inc. | Methods and systems for performing a medical procedure |
US8882653B2 (en) | 2012-08-10 | 2014-11-11 | Attenuex Technologies, Inc. | Methods and systems for performing a medical procedure |
US10799268B2 (en) | 2012-08-10 | 2020-10-13 | Solace Therapeutics, Inc. | Methods and systems for performing a medical procedure |
US8992412B2 (en) | 2012-08-10 | 2015-03-31 | Attenuex Technologies, Inc. | Removal device |
US9370329B2 (en) | 2012-09-18 | 2016-06-21 | Boston Scientific Scimed, Inc. | Map and ablate closed-loop cooled ablation catheter |
US9211156B2 (en) | 2012-09-18 | 2015-12-15 | Boston Scientific Scimed, Inc. | Map and ablate closed-loop cooled ablation catheter with flat tip |
US9095321B2 (en) | 2012-11-21 | 2015-08-04 | Medtronic Ardian Luxembourg S.A.R.L. | Cryotherapeutic devices having integral multi-helical balloons and methods of making the same |
US9017317B2 (en) | 2012-12-06 | 2015-04-28 | Medtronic Ardian Luxembourg S.A.R.L. | Refrigerant supply system for cryotherapy including refrigerant recompression and associated devices, systems, and methods |
US10448985B2 (en) | 2013-09-30 | 2019-10-22 | Arrinex, Inc. | Apparatus and methods for treating rhinitis |
US10512498B2 (en) | 2013-09-30 | 2019-12-24 | Arrinex, Inc. | Apparatus and methods for treating rhinitis |
US10028781B2 (en) | 2013-09-30 | 2018-07-24 | Arrinex, Inc. | Apparatus and methods for treating rhinitis |
US10307200B2 (en) | 2013-09-30 | 2019-06-04 | Arrinex, Inc. | Apparatus and methods for treating rhinitis |
US11406437B2 (en) | 2014-03-07 | 2022-08-09 | Medtronic Ardian Luxembourg S.A.R.L. | Monitoring and controlling internally administered cryotherapy |
US10492842B2 (en) | 2014-03-07 | 2019-12-03 | Medtronic Ardian Luxembourg S.A.R.L. | Monitoring and controlling internally administered cryotherapy |
US10470837B2 (en) | 2014-07-25 | 2019-11-12 | Arrinex, Inc. | Apparatus and method for treating rhinitis |
US10159538B2 (en) | 2014-07-25 | 2018-12-25 | Arrinex, Inc. | Apparatus and method for treating rhinitis |
US10524684B2 (en) | 2014-10-13 | 2020-01-07 | Boston Scientific Scimed Inc | Tissue diagnosis and treatment using mini-electrodes |
US11589768B2 (en) | 2014-10-13 | 2023-02-28 | Boston Scientific Scimed Inc. | Tissue diagnosis and treatment using mini-electrodes |
US10603105B2 (en) | 2014-10-24 | 2020-03-31 | Boston Scientific Scimed Inc | Medical devices with a flexible electrode assembly coupled to an ablation tip |
US9743854B2 (en) | 2014-12-18 | 2017-08-29 | Boston Scientific Scimed, Inc. | Real-time morphology analysis for lesion assessment |
US11602260B2 (en) | 2016-02-11 | 2023-03-14 | Arrinex, Inc. | Method and device for image guided post-nasal nerve ablation |
US11026738B2 (en) | 2016-06-15 | 2021-06-08 | Arrinex, Inc. | Devices and methods for treating a lateral surface of a nasal cavity |
US10939965B1 (en) | 2016-07-20 | 2021-03-09 | Arrinex, Inc. | Devices and methods for treating a nerve of the nasal cavity using image guidance |
US11253312B2 (en) | 2016-10-17 | 2022-02-22 | Arrinex, Inc. | Integrated nasal nerve detector ablation-apparatus, nasal nerve locator, and methods of use |
US11786292B2 (en) | 2016-10-17 | 2023-10-17 | Arrinex, Inc. | Integrated nasal nerve detector ablation-apparatus, nasal nerve locator, and methods of use |
US11278356B2 (en) | 2017-04-28 | 2022-03-22 | Arrinex, Inc. | Systems and methods for locating blood vessels in the treatment of rhinitis |
US11806484B2 (en) | 2018-01-19 | 2023-11-07 | Focalcool, Llc | Catheter with heat transfer minimizing annular space |
US11197981B2 (en) | 2019-02-07 | 2021-12-14 | Solace Therapeutics, Inc. | Pressure attenuation device |
Also Published As
Publication number | Publication date |
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AU4337401A (en) | 2001-09-12 |
CA2400753A1 (fr) | 2001-09-07 |
AU2001243374B2 (en) | 2005-02-03 |
JP2003524506A (ja) | 2003-08-19 |
EP1261304A1 (fr) | 2002-12-04 |
EP1261304A4 (fr) | 2005-06-08 |
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