CA2555441C - Method and apparatus for inflating and deflating balloon catheters - Google Patents
Method and apparatus for inflating and deflating balloon catheters Download PDFInfo
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- CA2555441C CA2555441C CA2555441A CA2555441A CA2555441C CA 2555441 C CA2555441 C CA 2555441C CA 2555441 A CA2555441 A CA 2555441A CA 2555441 A CA2555441 A CA 2555441A CA 2555441 C CA2555441 C CA 2555441C
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- catheter
- console
- expandable membrane
- volume
- balloon
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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
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/10—Balloon catheters
- A61M25/1011—Multiple balloon catheters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/10—Balloon catheters
- A61M25/1018—Balloon inflating or inflation-control devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/10—Balloon catheters
- A61M25/1018—Balloon inflating or inflation-control devices
- A61M25/10184—Means for controlling or monitoring inflation or deflation
- A61M25/10185—Valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
- A61B18/14—Probes or electrodes therefor
- A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
-
- 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
-
- 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
-
- 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
- A61B2018/0025—Multiple 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
- A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
- A61B2018/00577—Ablation
-
- 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
- A61B2018/00994—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body combining two or more different kinds of non-mechanical energy or combining one or more non-mechanical energies with ultrasound
-
- 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
Abstract
A system and method for controlling inflation, ablation, and deflation of a balloon catheter, including a catheter, a console having a pressurized gas or liquid inflation source, and an umbilical system to deliver coolant. A
pressure-sensing device monitors pressure and volume within the catheter.
During inflation, pressure and/or volume of fluid within the balloon is maintained to provide sufficient pressure against the target region. Inflation pressure is limited so a safe quantity of gas would be released should a leak occur. If the amount falls below a threshold, fluid egress is presumed, halting inflation. An intermediate console having a shut-off valve may be coupled between the console and catheter to interrupt coolant flow upon leak detection. The balloon can be re-inflated by a separate coolant source in the intermediate station or by a syringe. A second balloon may envelope the first balloon, providing a safety vacuum between the two balloons.
pressure-sensing device monitors pressure and volume within the catheter.
During inflation, pressure and/or volume of fluid within the balloon is maintained to provide sufficient pressure against the target region. Inflation pressure is limited so a safe quantity of gas would be released should a leak occur. If the amount falls below a threshold, fluid egress is presumed, halting inflation. An intermediate console having a shut-off valve may be coupled between the console and catheter to interrupt coolant flow upon leak detection. The balloon can be re-inflated by a separate coolant source in the intermediate station or by a syringe. A second balloon may envelope the first balloon, providing a safety vacuum between the two balloons.
Description
METHOD AND APPARATUS FOR INFLATING AND DEFLATING BALLOON
CATHETERS
FIELD OF THE INVENTION
The present invention relates to a method and system for inflating and deflating balloon catheters and more specifically to a method and system for controlling the inflation and deflation of balloon catheters in order to safely and effectively ablate a tissue region.
BACKGROUND OF THE INVENTION
The use of fluids with low operating temperatures, or cryogens, has begun to be explored in the medical and surgical field. Of particular interest are the potential use of catheter based devices, which employ the flow of cryogenic working fluids therein, to selectively freeze, or "cold-treat", targeted tissues within the body. Catheter based devices are desirable for various medical and surgical applications in that they axe relatively non-invasive and allow for precise treatment of localized discrete tissues that are otherwise inaccessible.
Catheters may be easily inserted and navigated through the blood vessels and arteries, allowing non-invasive access to areas of the body with relatively little trauma.
Catheter-based ablation systems axe well known in the art. A cryogenic device uses the energy transfer derived from thermodynamic changes occurring in the flow of a cryogen therethrough to create a net transfer of heat flow from the target tissue to the device, typically achieved by cooling a portion of the device to very low temperature through conductive and connective heat transfer between the cryogen and taxget tissue. The quality and magnitude of heat transfer is regulated by the device configuration and control of the cryogen flow regime within the device.
A cryogenic device uses the energy transfer derived from thermodynamic changes occurring in the flow of a refrigerant through the device. This energy transfer is then utilized to create a net transfer of heat flow from the target tissue to the device, typically achieved by cooling a portion of the device to very low temperature through conductive and connective heat transfer between the refrigerant and target tissue. The quality and magnitude of heat transfer is regulated by device configuration and control of the refrigerant flow regime within the device.
Structurally, cooling can be achieved through injection of high pressure refrigerant through am orifice. Upon injection from the orifice, the refrigerant undergoes two primary thermodynamic changes: (i) expanding to low pressure and temperature through positive Joule-Thomson throttling, and (ii) undergoing a phase change from liquid to vapor, thereby absorbing heat of vaporization. The resultant flow of low temperature refrigerant through the device acts to absorb heat from the target tissue and thereby cool the tissue to the desired temperature.
Once refrigerant is injected through an orifice, it may be expanded inside of a closed expansion chamber, which is positioned proximal to the target tissue. Devices with an expandable membrane, such as a balloon, are employed as expansion chambers. In such a device, refrigerant is supplied through a catheter tube into an expandable balloon coupled to such catheter, wherein the refrigerant acts to both: (i) expand the balloon near the target tissue for the purpose of positioning the balloon, and (ii) cool the target tissue proximal to the balloon to cold-treat adjacent tissue.
One of the principal drawbacks to such a technique is that during the inflation phase coolant may seep out of the balloon and get into the bloodstream to cause significant harm.
Therefore, if the balloon develops a crack, lealc, rupture,'or other critical structural integrity failure, coolant may quickly flow out of the catheter. Another situation that may occur during the balloon deflation phase is that the balloon may adhere to the ablated tissue causing severe damage. This may occur after ctyoablation or cryomapping. Cryomapping is a procedure that chills conducting target tissue to create a transient electrical effect. By temporarily chilling the target tissue, it allows for precise site confirmation in order to prevent inadvertent ablation.
Duxing ciyomapping, a procedure known as cryoadhesion takes place.
Cryoadhesion is a procedure that ensures the catheter tip remains at the target cite for a seamless transition to cryoablati~n. In a cryoadhesion procedure, the tip of the catheter firmly attaches to the tissue when it freezes thereby reducing the risk of accidental slippage of the catheter tip. Therefore, during unmonitored balloon deflation, i.e. if the balloon deflates too quickly, the balloon, adhering to the tissue walls, may cause severe damage.
Accordingly, it would be desirable to provide an apparatus and method of monitoring and controlling the inflation and deflation phases of a balloon catheter that is adaptable and compatible with all types of balloon ablation catheters, and with all types of ablation procedures, for example RF ablation or cryoablation.
SUMMARY OF THE INVENTION
The present invention advantageously provides a method and system for controllably inflating and deflating a balloon catheter. The method and system allows for the monitoring of the inflation and deflation phases of a catheter system in order to allow ablation to take place, while detecting unwanted leaks of refrigerant into the bloodstream. Balloon leaks are identified, safety evacuation routes are provided, and a controlled deflation mechanism is presented that prevents damage to the interior blood vessel and tissue region, which may occur during umonitored deflation due to the adherenace of the expandable membrane to the interior of the vessel.
In its preferred embodiment, a method of inflating and deflating a catheter during an ablation process, the catheter having an expandable membrane, is provided. The method comprises the steps of controllably inflating the expandable membrane to a target pressure or volume, ablating a desired tissue region while maintaining the target pressure or volume of the expandable membrane, and controllably deflating the expandable membrane so as not to damage desired tissue region.
In a~.iother aspect of the invention, a method for inflating and deflating a catheter having an expandable membrane during an ablation process is provided. The catheter is part of a catheter system including a console, the catheter, and an umbilical system coupling the console to the catheter. The method comprises the steps of evacuating air from the expandable membrane by creating a vacuum in the expandable membrane, controllably inflating the expandable membrane proximate a desired tissue region, wherein the expandable membrane is inflated to a target pressure or volume in order to provide sufficient mechanical force against the desired tissue region, ablating the desired tissue region while maintaining the expandable membrane at the target pressure or volume, and controllably deflating the expandable membrane such that the desired tissue region is not damaged.
. In still another aspect of the invention, an apparatus for inflating and deflating a catheter having an expandable membrane is provided. The apparatus comprises a console, the console including means for controlling the inflation and deflation of the expandable membrane and for determining if the expandable membrane maintains a target pressure or volume.
The console also includes a pressurized inflation source. The apparatus further inncludes a catheter, and an umbilical system coupling the console to the expandable membrane and delivering pressurized media to the expandable membrane.
BRIEF DESCRIPTION OF THE DRAWINGS
A more complete understanding of the present invention, and the attendant advantages amd features thereof, will be more readily understood by reference to the following detailed description when considered in conjunction with the accompanying drawings wherein:
FIG. lA illustrates a first embodiment of a double balloon catheter used in conjunction with the present invention;
FIG. 1B illustrates a catheter system used in conjunction with the present invention;
FIG. 1C illustrates the double balloon catheter of FIG. lA including a flow sensor located in the handle of the catheter;
FIG. 1D illustrates the double balloon catheter of FIG. lA including a pressure sensor located in the handle of the catheter;
FIGS. 2A-2E illustrate a cryoablation system incorporating various embodiments of the apparatus and method of the present invention;
FIG. 3 is a schematic representing the mechanical components of the control console of the present invention;
FIG. 4 is a schematic representing the mechanical components of the inflation circuit portion of the control console of the present invention;
FIG. 5 is a schematic representing the mechanical components of the deflation circuit and main vacuum path of the control console of the present invention; and FIG. 6 is a schematic representing the mechanical components of the safety vacuum path of the control console of the present invention;
FIG. 7 is a schematic representation of the embodiment illustrated in FIG. 2A;
FIG. 8 is a schematic representation of the embodiment illustrated in FIG. 2B;
FIG. 9 is a schematic representation of the embodiment illustrated in FIG. 2C;
FIG. 10 is a schematic representation of the embodiment illustrated in FIG.
2D; and FIG. 11 is a schematic representation of the embodiment illustrated in FIG.
2E.
CATHETERS
FIELD OF THE INVENTION
The present invention relates to a method and system for inflating and deflating balloon catheters and more specifically to a method and system for controlling the inflation and deflation of balloon catheters in order to safely and effectively ablate a tissue region.
BACKGROUND OF THE INVENTION
The use of fluids with low operating temperatures, or cryogens, has begun to be explored in the medical and surgical field. Of particular interest are the potential use of catheter based devices, which employ the flow of cryogenic working fluids therein, to selectively freeze, or "cold-treat", targeted tissues within the body. Catheter based devices are desirable for various medical and surgical applications in that they axe relatively non-invasive and allow for precise treatment of localized discrete tissues that are otherwise inaccessible.
Catheters may be easily inserted and navigated through the blood vessels and arteries, allowing non-invasive access to areas of the body with relatively little trauma.
Catheter-based ablation systems axe well known in the art. A cryogenic device uses the energy transfer derived from thermodynamic changes occurring in the flow of a cryogen therethrough to create a net transfer of heat flow from the target tissue to the device, typically achieved by cooling a portion of the device to very low temperature through conductive and connective heat transfer between the cryogen and taxget tissue. The quality and magnitude of heat transfer is regulated by the device configuration and control of the cryogen flow regime within the device.
A cryogenic device uses the energy transfer derived from thermodynamic changes occurring in the flow of a refrigerant through the device. This energy transfer is then utilized to create a net transfer of heat flow from the target tissue to the device, typically achieved by cooling a portion of the device to very low temperature through conductive and connective heat transfer between the refrigerant and target tissue. The quality and magnitude of heat transfer is regulated by device configuration and control of the refrigerant flow regime within the device.
Structurally, cooling can be achieved through injection of high pressure refrigerant through am orifice. Upon injection from the orifice, the refrigerant undergoes two primary thermodynamic changes: (i) expanding to low pressure and temperature through positive Joule-Thomson throttling, and (ii) undergoing a phase change from liquid to vapor, thereby absorbing heat of vaporization. The resultant flow of low temperature refrigerant through the device acts to absorb heat from the target tissue and thereby cool the tissue to the desired temperature.
Once refrigerant is injected through an orifice, it may be expanded inside of a closed expansion chamber, which is positioned proximal to the target tissue. Devices with an expandable membrane, such as a balloon, are employed as expansion chambers. In such a device, refrigerant is supplied through a catheter tube into an expandable balloon coupled to such catheter, wherein the refrigerant acts to both: (i) expand the balloon near the target tissue for the purpose of positioning the balloon, and (ii) cool the target tissue proximal to the balloon to cold-treat adjacent tissue.
One of the principal drawbacks to such a technique is that during the inflation phase coolant may seep out of the balloon and get into the bloodstream to cause significant harm.
Therefore, if the balloon develops a crack, lealc, rupture,'or other critical structural integrity failure, coolant may quickly flow out of the catheter. Another situation that may occur during the balloon deflation phase is that the balloon may adhere to the ablated tissue causing severe damage. This may occur after ctyoablation or cryomapping. Cryomapping is a procedure that chills conducting target tissue to create a transient electrical effect. By temporarily chilling the target tissue, it allows for precise site confirmation in order to prevent inadvertent ablation.
Duxing ciyomapping, a procedure known as cryoadhesion takes place.
Cryoadhesion is a procedure that ensures the catheter tip remains at the target cite for a seamless transition to cryoablati~n. In a cryoadhesion procedure, the tip of the catheter firmly attaches to the tissue when it freezes thereby reducing the risk of accidental slippage of the catheter tip. Therefore, during unmonitored balloon deflation, i.e. if the balloon deflates too quickly, the balloon, adhering to the tissue walls, may cause severe damage.
Accordingly, it would be desirable to provide an apparatus and method of monitoring and controlling the inflation and deflation phases of a balloon catheter that is adaptable and compatible with all types of balloon ablation catheters, and with all types of ablation procedures, for example RF ablation or cryoablation.
SUMMARY OF THE INVENTION
The present invention advantageously provides a method and system for controllably inflating and deflating a balloon catheter. The method and system allows for the monitoring of the inflation and deflation phases of a catheter system in order to allow ablation to take place, while detecting unwanted leaks of refrigerant into the bloodstream. Balloon leaks are identified, safety evacuation routes are provided, and a controlled deflation mechanism is presented that prevents damage to the interior blood vessel and tissue region, which may occur during umonitored deflation due to the adherenace of the expandable membrane to the interior of the vessel.
In its preferred embodiment, a method of inflating and deflating a catheter during an ablation process, the catheter having an expandable membrane, is provided. The method comprises the steps of controllably inflating the expandable membrane to a target pressure or volume, ablating a desired tissue region while maintaining the target pressure or volume of the expandable membrane, and controllably deflating the expandable membrane so as not to damage desired tissue region.
In a~.iother aspect of the invention, a method for inflating and deflating a catheter having an expandable membrane during an ablation process is provided. The catheter is part of a catheter system including a console, the catheter, and an umbilical system coupling the console to the catheter. The method comprises the steps of evacuating air from the expandable membrane by creating a vacuum in the expandable membrane, controllably inflating the expandable membrane proximate a desired tissue region, wherein the expandable membrane is inflated to a target pressure or volume in order to provide sufficient mechanical force against the desired tissue region, ablating the desired tissue region while maintaining the expandable membrane at the target pressure or volume, and controllably deflating the expandable membrane such that the desired tissue region is not damaged.
. In still another aspect of the invention, an apparatus for inflating and deflating a catheter having an expandable membrane is provided. The apparatus comprises a console, the console including means for controlling the inflation and deflation of the expandable membrane and for determining if the expandable membrane maintains a target pressure or volume.
The console also includes a pressurized inflation source. The apparatus further inncludes a catheter, and an umbilical system coupling the console to the expandable membrane and delivering pressurized media to the expandable membrane.
BRIEF DESCRIPTION OF THE DRAWINGS
A more complete understanding of the present invention, and the attendant advantages amd features thereof, will be more readily understood by reference to the following detailed description when considered in conjunction with the accompanying drawings wherein:
FIG. lA illustrates a first embodiment of a double balloon catheter used in conjunction with the present invention;
FIG. 1B illustrates a catheter system used in conjunction with the present invention;
FIG. 1C illustrates the double balloon catheter of FIG. lA including a flow sensor located in the handle of the catheter;
FIG. 1D illustrates the double balloon catheter of FIG. lA including a pressure sensor located in the handle of the catheter;
FIGS. 2A-2E illustrate a cryoablation system incorporating various embodiments of the apparatus and method of the present invention;
FIG. 3 is a schematic representing the mechanical components of the control console of the present invention;
FIG. 4 is a schematic representing the mechanical components of the inflation circuit portion of the control console of the present invention;
FIG. 5 is a schematic representing the mechanical components of the deflation circuit and main vacuum path of the control console of the present invention; and FIG. 6 is a schematic representing the mechanical components of the safety vacuum path of the control console of the present invention;
FIG. 7 is a schematic representation of the embodiment illustrated in FIG. 2A;
FIG. 8 is a schematic representation of the embodiment illustrated in FIG. 2B;
FIG. 9 is a schematic representation of the embodiment illustrated in FIG. 2C;
FIG. 10 is a schematic representation of the embodiment illustrated in FIG.
2D; and FIG. 11 is a schematic representation of the embodiment illustrated in FIG.
2E.
DETAILED DESCRIPTION OF THE INVENTION
The present invention is an apparatus and method for controlling the inflation and deflation of balloon catheters. In its preferred embodiment, the invention requires four steps to properly control the inflation and deflation of the balloon catheter. However, the invention allows for a variety of different implementations in order to accomplish this task. An intermediary control station containing a shut off valve and/or a coolant source may be implemented to assist in properly monitoring, controlling and maintaining the target balloon pressure and/or volume.
Referring now to the drawing figures in which lilce reference designations refer to lilce elements, a first embodiment of a double balloon catheter used in conjunction with the present invention is shown in FIG. lA. The catheter 1 includes a handle 2 having a number of proximal connector ports 3a-3d. Port 3a may be a first vacuum connector, having a first,vacuum lumen therein, such as a 10 French lumen. Port 3b may be a coaxial connector having both a vacuum lumen and injection therein, the vacuum lumen being a second vacuum lumen, such as a 8 French lumen. Port 3c may be an electrical connector. Port 3d may be a guidewire luer hub.
The handle 2 further includes a blood detection board 4 and pressure relief valve 5. The distal end portion of the catheter 1 includes two balloons: an inner balloon 6a and an outer balloon 6b surrounding inner balloon 6a. A soft distal tip 7 is loacted just distal to the two balloons 6a and 6b. When refrigerant is injected into the balloons along lines R as showm, vacuum applied through the ports 3a and 3b will serve to draw any fluid within balloons 6a and 6b along arrows V out of the balloons and the catheter. Radiopaque marker bands M are located proximate the exit point of the refrigerant injected into balloon 6a to aid in the positioning and tracking of the device.
Catheter 1 includes an elongate shaft having a guidewire 8 and an inner shaft 9a and outer shaft 9b. Exemplary embodiments of the inner shaft 9a include an 8 French shaft, while exemplary embodiments of the outer shaft 9b include a 10 French shaft.
A typical catheter system 10 is shown in FIG. 1B. The system includes a console 20 coupled to one end of an umbilical system 12. The opposing end of umbilical system 12 is coupled to an energy treatment device 22. Energy treatment device 22 may be a medical probe, ~0 a catheter, a balloon-catheter, as well as other devices commonly known in the axt that are smooth enough to pass easily through blood vessels and heart valves. As shown in FIG. lA, the energy treatment device 22 includes a balloon structure 23 that can be a single wall or a double wall configuration, wherein the double wall configuration places the space between balloon walls in communication with a vacuum source.
Umbilical system 12 is comprised of three separate umbilicals: a coaxial cable umbilical 14, an electrical umbilical 16 and a vacuum umbilical 18. An outer vacuum umbilical is used in the case of a double balloon system; it is not necessary for a single balloon system having only one vacuum lumen. If the user wishes to perform an RF ablation procedure, radiofrequency energy can be provided to electrodes on device 22 via electrical umbilical 16 to perform an RF
ablation technique as is common in the art. Electrical umbilical 16 can include an ECG box 82 to facilitate a connection from electrodes on catheter 22 (not shown) to an ECG monitor.
Coaxial umbilical 14 includes both a cooling injection umbilical and a vacuum umbilical that provide respective inlet and return paths for a refrigerant or coolant used to cool a tissue-treating end of device 22. The vacuum umbilical 18 is used as safety conduit to allow excess coolant or gas to escape from device 22 if the pressure within the balloon on device 22 exceeds a predefined limit. The vacuum umbilical 18 can also be used to capture air through a leak of the outer vacuum system where it is outside the patient and as a lumen to ingress blood when in the patient.
Referring once again to FIG. 1B; catheter system 10 may include one or more sensors #, which are used to monitox the amount of fluid or gas refrigerant injected through the umbilical system and into the balloons. It is contempaltd that the sensors may be located in one of several locations throughout catheter system 10. For example, sensor 11 may be located in console 20, ECG Box 82, and/or handle 2.
Two different types of sensors are contemplated for use with the present invention in order to monitor how much coolant is flowing into the balloons. A flow sensor 13 shown in FIG.
1 C, measures the rate or speed of fluid or gas at a certain location. An examplaxy embodiment of flow sensor 13 is the Microbridge Mass Air Flow Sensor by Honeywell" .
Alternately, one or more sensors 11 may be a pressure sensor 15 as shown in FIG. 1D.
Pressure sensor 15 in FIG. 1D is a differential pressure sensor that can determine the amount of pressure in the balloons by determining the differnecne in pressure between points pl and p2 and 0 the velocity through the restriction point d. An exemplary embodiment of pressure sensor 15 is the 26PC SMT Pressure Sensor by Honeywell".
FIGS. 2A-2E illustrate different embodiments of the catheter system 10 of the present invention. In general, the inflation/deflation system described herein can be used with both single and double balloon systems. For a single balloon system, the refrigerant is sprayed into the baloon and creates a circumferential region of cooling arough the balloon's perimeter. The refrigerant expands and the vapor is drawn baclc into the console via the return vacuum lumen.
With respect to a double ballon system, a second balloon and second vacuum lumen envelop the single balloon system and are always maintained under vacuum for safety reasons. The vacuum of the outer balloon will capture refrigerant escaping through any breach of the inner balloon system. A flow switch mounted on the outer vacuum system is used to monitor any flow activity. Under normal operation, no fluid should pass through the outer vacuum.system. Any discussion of a "flow switch" herein implies a double balloon system.
Otherwise, all inflation/deflation methods also apply to a single balloon catheter.
Each embodiment includes a console 20 or console 21, an umbilical system 'comprised of varying combinations of separate umbilicals, and an ablation device 22.
Each of the embodiments shown in FIGS. 2A-2E is represented by more detailed corresponding schematics in FIGS. 7-1 l, respectively, and are discussed in greater detail below.
FIG. 2A represents a typical catheter ablation system 10. Console 20 is coupled to a catheter 22 via an umbilical system 12, comprised of coaxial umbilical 14, which transfers coolant from console 20 to catheter 22 and provides a return conduit for the coolant, electrical umbilical 16, which transfers RF energy from console 20 to catheter 22 during an RF ablation procedure or electrical signals during a cryoablation procedure, and safety vacuum umbilical 18, to allow for quick evactuation of coolant if needed.
Coolant is provided by a coolant source within console 20. Coolant, typically N20, passes through the internal piping of console 20 before being transferred to catheter 22 via the coaxial umbilical 14. At the distal end of the umbilical, inside catheter 22, the coolant is released inside the catheter tip cavity, which is under vacuum. Both the phase change from liquid to gas and the sudden expansion of the coolant are endothermic reactions, causing a temperature differential which results in the catheter tip or balloon freezing. The coolant vapor is then returned through the vacuum path via umbilical 14 and into console 20, where it is evacuated 0 through a scavenging line.
FIG. 2B represents another catheter ablation system. However, in this embodiment, an intermediary station 74 is inserted into the catheter system. As explained in greater detail below, station 74 contains detection valves to detect a drop in balloon pressure which might indicate a leak, amd shut off valves to terminate balloon inflation if necessary. Station 74 is coupled to console 21 and catheter 22 via electrical umbilical 16 and coaxial umbilical 14. Vaccuum umbilical 18 provides an emergency evacuation path for coolant from the catheter.
FIG. 2C represents the catheter ablation system of FIG. 2A including a secondary coolant source 78 used to re-inflate the expandable membrane, or balloon 23 of catheter 22 via syringe 76.
FIG. 2D illustrates two possible configurations for the ablation system. In a first configuration, a secondary coolant source' includes a small tank or canister 80 located within an intermediary station 74. In a second configuration, the secondary coolant source.includes a small tank or canister 60 located inside the console 21. In both configurations, the secondary coolant source is independent from the source of cooling provided by other components within the console 21 (the primary coolant source), and it does not require the same type of refrigerant that is provided by the primary coolant source.
FIG. 2E illustrates a configuration where the secondary cooling source and the primary cooling source are unified and thus share the same source of refrigerant.
FIG. 3 refers to a schematic representing the console 20 portrayed in FIGS. 2A
and 2C.
The schematic shov~m is designed specially for balloon catheters and contains a series of two and three-way solenoid valves and regulators that assist in monitoring the pressure of the balloon catheter 23, which may drop quickly if a leak of fluid occurs. Device 22 (shown in FIGS. 2A-2E) is a catheter with an expandable membrane 23 at its distal end. Console 20 is represented by the schematic in FIG. 3 that shows the layout of the internal mechanical components of console 20.
In an exemplary embodiment, the system is operated in four phases. The first phase is the evacuation/flushing phase. When the catheter 22 is inserted inside the patient it is first necessary to evacuate air molecules from within the catheter, air contained inside the umbilical connecting the catheter 22 to the console 20, as well as from the catheter shaft itself. Although it 0 is not theoretically possible to evacuate 100% of the air molecules, by minimizing the amount of air within the umbilical and catheter shaft, the catheter is prepared for inflation and then ablation, while minimizing the dangers associated with fluid egress.
During the evacuation/flushing phase, a 3-way solenoid valve 24 is open toward vacuum pump 26, which ensures that there is a vacuum in catheter 22. The 3-way solenoid valve 24 can be replaced by a PID-driven proportional valve. In either configuration, the 2-way solenoid 28 that supports high pressure is closed to prevent any high-pressure gas from reservoir 30 from entering the inner vacuum system/balloon catheter during the refilling process. Reservoir 30 could be a tube or reservoir containing enough fluid volume to fill the umbilical tubes and catheter 22 to a predefined pressure. If the pressure within reservoir 30 exceeds a predetermined pressure setpoint, a check valve 32 will open to evacuate the exceeded amount of coolant such as, for example, nitrous oxide (N20) in the system in order to keep a fixed amount of nitrous oxide in reservoir 30. During this phase, reservoir 30 is filled with N20 received from N20 source 60. The N20 is received from a high pressure line after leaves tank 60 and passes through a series of regulators, namely, a first regulator 34, a second regulator 36 and then into either a third regulator 38 or a proportional valve, that are adjusted to the predetermined pressure. The reservoir pressure can be controlled through a pressure regulator 38 or through a proportional valve that would refill the tank with different pressure setpoints for different balloon sizes or different inflation pressures. The pressure setpoint can be programmed into a circuit, chip or other memory device that can be located in the handle.
Refilling valve 40 opens for a period of time and fills reservoir 30. During this phase, the 2-way solenoid valve 28 remains closed. Also, during this phase, the system is under vacuum and provides verification for any leaks that occur.
Thus when the the catheter is outside the patient, any breach of the inner or outer vacuum systems will be detected by a high baseline flow through the console flow meter. In addition, a flow switch located in the console or in the catheter handle and mounted on the outer vacuum system will also detect a leak of air through a breach of the outer balloon or vacuum lumen. The flow switch is capable of detecting volumes of gas as little as 1 cc of vapor, and flow rates as little as 20 sccm. When the catheter is inserted into the patient, blood ingress through either the imler or outer vacuum lumens or both will be detected by the leak and blood detection systems. In the case of a constant pressure inflation with circulating flow, the balloon pressure can also be controlled with a PID-driven proportional valve located on the return vacuum lumen or a three-way solenoid valve in series with a pressure switch or pressure transducer.
Referring to FIG. 4, the inflation phase of the invention will now be discussed. Prior to positioning catheter 22 on the ablation site, the physician must first inflate the expandable membrane 23 inside the heart chamber and then position the balloon 23 proximate the ablation site. During this phase, the system is under vacuum and provides verification for leaks between balloon 23 and the blood. In one embodiment, balloon 23 is inflated by injecting fluid or gas through the umbilical under a fixed flow pressure. This insures a defined and constant pressure inside the balloon in order to provide a mechanical force for inflation. An alternate way to inflate balloon 23 is to use a fixed volume of inflation. This volume would be minimized in order to meet the constraints related to gas egress within the blood stream (maximum of 20cc within 10 minutes) and meet the requirement for pressure needed to inflate the balloon under the harshest room conditions.
FIG. 3 illustrates the inflation portion of the console mechanics of FIG. 2.
During the inflation phase, valve 24 is open toward reservoir 30 and valve 28 opens, while refilling valve 40 remains closed. A fixed amount of Na0 is injected to inflate balloon 23 in order to provide sufficient mechanical force for inflation. If a leak occurs in the balloon, the released volume of N20 would be no more than 20 cc. The solenoid valve 44 (shown in FIG. 33) remains open during this phase in order to ensure a vacuum in the safety line. If a lealc occurs in the inner balloon of the catheter, the flow switch 42 (FIG. 3), detects leaks as small as 1 cc of vapor. .
Flow switch 42 is active during all phases to prevent any leak of the inner balloon system in catheter 22. The leak and blood detection systems are still active and monitoring any blood ingress through the outer bacuum lumen. After air has been flushed from catheter 22 and the umbilicals connecting catheter 22 to console 20, and balloon 23 has been inflated, ablation may now take place.
A transition mode follows inflation but precedes ablation. In the case of cyrogenic ablation systems, a transition method is needed to transition from closed pressurized volume to an open circuit, which allows the flow of refrigerant to enter and exit the catheter tip while at the same time contrilling the balloon pressure in order to keep. the balloon inflated and in place.
During the transition , a pressure switch, which is adjusted to a pressure higher than atmospheric pressure but preferably lower than 20 Asia, monitors the pressure inside the balloon catheter 22.
The solenoid valve 24 remains closed until the pressure in the catheter is higher than the preset switch value after which the solenoid valve opens to allow evacuation of excess refrigerant.
When the pressure falls below the reset switch value, the solenoid valve 24 closes to keep the balloon inflated and above atmospheric pressure. During the transition, ablation is already initiated but the pressure switch controls the balloon pressure until refrigerant flow alone maintains the balloon open and above atmospheric pressure. The transition phase is considered complete when certain conditions are met: 1) when the pressure switch commands the solenoid valve 24 to open to vacuum and the balloon pressure remains above the present switch value; 2) the duration of the transition phase exceeds a predetermined time; and 3) the injection pressure reaches a predetermined value that is adequate to generate enough flow to maintain the balloon open. Check valve 56 is used to prevent any abnormal rise in the pressure in the catheter tip.
Another check valve 58, shown also in FIG. 6, prevents any excessive pressure in the safety vacuum line and in in the event the soloenoid valve 44 is blocked.
During the ablation phase, refrigerant is injected through the umbilical system into the ablation device 22. When injection of refrigerant is desired, N2Q gas is released from source 60 and provides high pressure liquid through a check valve 62 and a series of pressure regulators 34 and 36. Regulators 34 and 36 are primary and secondary pressure regulators respectively, which serve to bring the gas pressure down to between 810 and approximately 840 psig. The liquid nitrous oxide goes through a proportional valve 64 driven by a Proportional Integral Derivative (PID) controller 66 so that the refrigerant pressure can be varied from 0 psig to approximately 760 psig, and through an injection solenoid valve 68 which remains open. The N20 then passes through a sub-cooler 70 with various refrigeration components such as a compressor, a condenser, a capillary tube and a heat exchanger, which insures its liquid state through the umbilical and into the small diameter catheter injection tubing. During injection, solenoid vent valve 46 is closed. To detect a failure of this valve, the pressure switch 72 will close when detecting a pressure higher than 15 psig, creating a failure signal.
During the injection phase, proportional valve 64 is used to vary the pressure inside the injection line. This in turn will vary the flow rate of refrigerant to the catheter tip. An increase in the flow rate (less restriction by the regulator) lowers the temperature of the catheter tip.
Conversely, decreasing the flow rate allows the catheter tip to be waxmed by its suiTOUndings.
FIG. 5 illustrates the deflation and main path circuitry of the present invention. At the end of the ablation phase, the system provides a method to insure a controlled/slow deflation in order to prevent damaging the ablated tissue during balloon deflation. This can be a hazard due to cryoadhesion, which may occur when the catheter attaches to the tissue during freezing.
Referring to both FIGS. 3 and 5, during deflation, the solenoid valve 24 (FIG.
3) remains closed until the temperature in the balloon is higher than a predetermined temperature (usually above freezing to ensure that surrounding tissue has thawed). When the temperature increases to greater than the predetermined temperature, the solenoid valve 24 opens to vacuum and collapses the balloon. On both vacuum paths, liquid sensors and insulated liquid sparators 48 and 50 (FIG.
3) are installed to prevent any liquid from entering the vacuum pump 26. If this occurs, injection and /or inflation will be stopped and both valves 52 (FIG. 3) and 44 (FIG. 3) will switch to atmosphere.
FIG. 6 illustrates the safety vacuum portion of the console circuitry of FIG.
3. If a leak occurs in the catheter during inflation or ablation, flow switch 42 can detect such a leak in amounts as small as 1 cc of vapor. Upon detection of the leak, inflation of the balloon catheter is stopped. Prior to inflation, the flow switch can detect leaks of the outer balloon or guide wire lumen when the Gather is in the air. In case of pressurization of the safety vacuum line 1/3 psi above atmospheirc, a pressure relief valve 58 located distal to the flow switch will vent excess pressure.
Referring now to FIG. 7, one embodiment of the present invention is shown. The schematic in FIG. 7 illustrates the mechanical connection of the console 20, umbilical system 12 and catheter 22. The representation in FIG. 7 corresponds to the embodiment shown in FIG. 2A.
The internal components of console 20 are similar and correspond to those shown in greater detail in FIG. 3 explained above. In this embodiment, the balloon 23 is inflated by receiving gas or fluid from source 60 via coaxial umbilical 14. PID controller 66 controls the flow of pressurized fluid/gas from console 20 through umbilical system 12 to balloon 23.
FIG. 8 shows an alternate embodiment of the invention in which an intermediary station 74 containing all components and circuts to operate the balloon catheter is coupled to console 10, between the console and balloon catheter 23. Station 74 includes a series of shut-off valves and detection switches. Detection circuitry within station 74 can detect if the volume of gas within balloon catheter 23 has exceeded a certain predetermined amount (i.e. 20cc within the catheter and the umbilical system), and shut-off valves within station 74 are activated, preventing any further inflation. Station 74 advantageously provides a quicker and more effective way of detecting leakage of gas or liquid into the blood stream. If the pressure within balloon catheter 23 drops, this could be an indication that fluid within the balloon has escaped. By inserting station 74 within system 10, a quicker and more efficient way of detecting leaks and preventing unwanted balloon inflation is provided.
FIG. 9 shows yet another embodiment of the invention. Here, balloon inflation can be performed by a syringe 76 coupled to a saline water source 78 or any other fluid media including gasses or liquids. This embodiment becomes practical when manual balloon inflation is required.
In FIG. 10, intermediary station 74 includes a second inflation source 80. As in the embodiment depicted in FIG. 8, leak detection circuitry and shut-off valves located in station 74 provide an efficient way of detecting leaks and quickly prohibiting the further inflation of balloon catheter 23. Should further inflation be required, a separate pressurized N20 source 80 is provided in station 74, which is at a closer and more convenient location, i.e. ne'arer the catheter and not in a remote location such as console 20.
In FIG. 10, the refilling source 80 is located in the intermediate box 74 and inflation occurs through the outer vacuum umbilical. In FIG. 1 l, the refilling source is the coolant tank 60 located in the cryoablation console and inflation occurs through the inner vacuum umbilical.
It will be appreciated by persons skilled in the art that the present invention is not limited to what has been particularly shown and described herein above. In addition, unless mention was made above to the contrary, it should be noted that all of the accompanying drawings are not to scale. A variety of modifications and variations are possible in light of the above teachings without departing from the scope and spirit of the invention, which is limited only by the following claims.
The present invention is an apparatus and method for controlling the inflation and deflation of balloon catheters. In its preferred embodiment, the invention requires four steps to properly control the inflation and deflation of the balloon catheter. However, the invention allows for a variety of different implementations in order to accomplish this task. An intermediary control station containing a shut off valve and/or a coolant source may be implemented to assist in properly monitoring, controlling and maintaining the target balloon pressure and/or volume.
Referring now to the drawing figures in which lilce reference designations refer to lilce elements, a first embodiment of a double balloon catheter used in conjunction with the present invention is shown in FIG. lA. The catheter 1 includes a handle 2 having a number of proximal connector ports 3a-3d. Port 3a may be a first vacuum connector, having a first,vacuum lumen therein, such as a 10 French lumen. Port 3b may be a coaxial connector having both a vacuum lumen and injection therein, the vacuum lumen being a second vacuum lumen, such as a 8 French lumen. Port 3c may be an electrical connector. Port 3d may be a guidewire luer hub.
The handle 2 further includes a blood detection board 4 and pressure relief valve 5. The distal end portion of the catheter 1 includes two balloons: an inner balloon 6a and an outer balloon 6b surrounding inner balloon 6a. A soft distal tip 7 is loacted just distal to the two balloons 6a and 6b. When refrigerant is injected into the balloons along lines R as showm, vacuum applied through the ports 3a and 3b will serve to draw any fluid within balloons 6a and 6b along arrows V out of the balloons and the catheter. Radiopaque marker bands M are located proximate the exit point of the refrigerant injected into balloon 6a to aid in the positioning and tracking of the device.
Catheter 1 includes an elongate shaft having a guidewire 8 and an inner shaft 9a and outer shaft 9b. Exemplary embodiments of the inner shaft 9a include an 8 French shaft, while exemplary embodiments of the outer shaft 9b include a 10 French shaft.
A typical catheter system 10 is shown in FIG. 1B. The system includes a console 20 coupled to one end of an umbilical system 12. The opposing end of umbilical system 12 is coupled to an energy treatment device 22. Energy treatment device 22 may be a medical probe, ~0 a catheter, a balloon-catheter, as well as other devices commonly known in the axt that are smooth enough to pass easily through blood vessels and heart valves. As shown in FIG. lA, the energy treatment device 22 includes a balloon structure 23 that can be a single wall or a double wall configuration, wherein the double wall configuration places the space between balloon walls in communication with a vacuum source.
Umbilical system 12 is comprised of three separate umbilicals: a coaxial cable umbilical 14, an electrical umbilical 16 and a vacuum umbilical 18. An outer vacuum umbilical is used in the case of a double balloon system; it is not necessary for a single balloon system having only one vacuum lumen. If the user wishes to perform an RF ablation procedure, radiofrequency energy can be provided to electrodes on device 22 via electrical umbilical 16 to perform an RF
ablation technique as is common in the art. Electrical umbilical 16 can include an ECG box 82 to facilitate a connection from electrodes on catheter 22 (not shown) to an ECG monitor.
Coaxial umbilical 14 includes both a cooling injection umbilical and a vacuum umbilical that provide respective inlet and return paths for a refrigerant or coolant used to cool a tissue-treating end of device 22. The vacuum umbilical 18 is used as safety conduit to allow excess coolant or gas to escape from device 22 if the pressure within the balloon on device 22 exceeds a predefined limit. The vacuum umbilical 18 can also be used to capture air through a leak of the outer vacuum system where it is outside the patient and as a lumen to ingress blood when in the patient.
Referring once again to FIG. 1B; catheter system 10 may include one or more sensors #, which are used to monitox the amount of fluid or gas refrigerant injected through the umbilical system and into the balloons. It is contempaltd that the sensors may be located in one of several locations throughout catheter system 10. For example, sensor 11 may be located in console 20, ECG Box 82, and/or handle 2.
Two different types of sensors are contemplated for use with the present invention in order to monitor how much coolant is flowing into the balloons. A flow sensor 13 shown in FIG.
1 C, measures the rate or speed of fluid or gas at a certain location. An examplaxy embodiment of flow sensor 13 is the Microbridge Mass Air Flow Sensor by Honeywell" .
Alternately, one or more sensors 11 may be a pressure sensor 15 as shown in FIG. 1D.
Pressure sensor 15 in FIG. 1D is a differential pressure sensor that can determine the amount of pressure in the balloons by determining the differnecne in pressure between points pl and p2 and 0 the velocity through the restriction point d. An exemplary embodiment of pressure sensor 15 is the 26PC SMT Pressure Sensor by Honeywell".
FIGS. 2A-2E illustrate different embodiments of the catheter system 10 of the present invention. In general, the inflation/deflation system described herein can be used with both single and double balloon systems. For a single balloon system, the refrigerant is sprayed into the baloon and creates a circumferential region of cooling arough the balloon's perimeter. The refrigerant expands and the vapor is drawn baclc into the console via the return vacuum lumen.
With respect to a double ballon system, a second balloon and second vacuum lumen envelop the single balloon system and are always maintained under vacuum for safety reasons. The vacuum of the outer balloon will capture refrigerant escaping through any breach of the inner balloon system. A flow switch mounted on the outer vacuum system is used to monitor any flow activity. Under normal operation, no fluid should pass through the outer vacuum.system. Any discussion of a "flow switch" herein implies a double balloon system.
Otherwise, all inflation/deflation methods also apply to a single balloon catheter.
Each embodiment includes a console 20 or console 21, an umbilical system 'comprised of varying combinations of separate umbilicals, and an ablation device 22.
Each of the embodiments shown in FIGS. 2A-2E is represented by more detailed corresponding schematics in FIGS. 7-1 l, respectively, and are discussed in greater detail below.
FIG. 2A represents a typical catheter ablation system 10. Console 20 is coupled to a catheter 22 via an umbilical system 12, comprised of coaxial umbilical 14, which transfers coolant from console 20 to catheter 22 and provides a return conduit for the coolant, electrical umbilical 16, which transfers RF energy from console 20 to catheter 22 during an RF ablation procedure or electrical signals during a cryoablation procedure, and safety vacuum umbilical 18, to allow for quick evactuation of coolant if needed.
Coolant is provided by a coolant source within console 20. Coolant, typically N20, passes through the internal piping of console 20 before being transferred to catheter 22 via the coaxial umbilical 14. At the distal end of the umbilical, inside catheter 22, the coolant is released inside the catheter tip cavity, which is under vacuum. Both the phase change from liquid to gas and the sudden expansion of the coolant are endothermic reactions, causing a temperature differential which results in the catheter tip or balloon freezing. The coolant vapor is then returned through the vacuum path via umbilical 14 and into console 20, where it is evacuated 0 through a scavenging line.
FIG. 2B represents another catheter ablation system. However, in this embodiment, an intermediary station 74 is inserted into the catheter system. As explained in greater detail below, station 74 contains detection valves to detect a drop in balloon pressure which might indicate a leak, amd shut off valves to terminate balloon inflation if necessary. Station 74 is coupled to console 21 and catheter 22 via electrical umbilical 16 and coaxial umbilical 14. Vaccuum umbilical 18 provides an emergency evacuation path for coolant from the catheter.
FIG. 2C represents the catheter ablation system of FIG. 2A including a secondary coolant source 78 used to re-inflate the expandable membrane, or balloon 23 of catheter 22 via syringe 76.
FIG. 2D illustrates two possible configurations for the ablation system. In a first configuration, a secondary coolant source' includes a small tank or canister 80 located within an intermediary station 74. In a second configuration, the secondary coolant source.includes a small tank or canister 60 located inside the console 21. In both configurations, the secondary coolant source is independent from the source of cooling provided by other components within the console 21 (the primary coolant source), and it does not require the same type of refrigerant that is provided by the primary coolant source.
FIG. 2E illustrates a configuration where the secondary cooling source and the primary cooling source are unified and thus share the same source of refrigerant.
FIG. 3 refers to a schematic representing the console 20 portrayed in FIGS. 2A
and 2C.
The schematic shov~m is designed specially for balloon catheters and contains a series of two and three-way solenoid valves and regulators that assist in monitoring the pressure of the balloon catheter 23, which may drop quickly if a leak of fluid occurs. Device 22 (shown in FIGS. 2A-2E) is a catheter with an expandable membrane 23 at its distal end. Console 20 is represented by the schematic in FIG. 3 that shows the layout of the internal mechanical components of console 20.
In an exemplary embodiment, the system is operated in four phases. The first phase is the evacuation/flushing phase. When the catheter 22 is inserted inside the patient it is first necessary to evacuate air molecules from within the catheter, air contained inside the umbilical connecting the catheter 22 to the console 20, as well as from the catheter shaft itself. Although it 0 is not theoretically possible to evacuate 100% of the air molecules, by minimizing the amount of air within the umbilical and catheter shaft, the catheter is prepared for inflation and then ablation, while minimizing the dangers associated with fluid egress.
During the evacuation/flushing phase, a 3-way solenoid valve 24 is open toward vacuum pump 26, which ensures that there is a vacuum in catheter 22. The 3-way solenoid valve 24 can be replaced by a PID-driven proportional valve. In either configuration, the 2-way solenoid 28 that supports high pressure is closed to prevent any high-pressure gas from reservoir 30 from entering the inner vacuum system/balloon catheter during the refilling process. Reservoir 30 could be a tube or reservoir containing enough fluid volume to fill the umbilical tubes and catheter 22 to a predefined pressure. If the pressure within reservoir 30 exceeds a predetermined pressure setpoint, a check valve 32 will open to evacuate the exceeded amount of coolant such as, for example, nitrous oxide (N20) in the system in order to keep a fixed amount of nitrous oxide in reservoir 30. During this phase, reservoir 30 is filled with N20 received from N20 source 60. The N20 is received from a high pressure line after leaves tank 60 and passes through a series of regulators, namely, a first regulator 34, a second regulator 36 and then into either a third regulator 38 or a proportional valve, that are adjusted to the predetermined pressure. The reservoir pressure can be controlled through a pressure regulator 38 or through a proportional valve that would refill the tank with different pressure setpoints for different balloon sizes or different inflation pressures. The pressure setpoint can be programmed into a circuit, chip or other memory device that can be located in the handle.
Refilling valve 40 opens for a period of time and fills reservoir 30. During this phase, the 2-way solenoid valve 28 remains closed. Also, during this phase, the system is under vacuum and provides verification for any leaks that occur.
Thus when the the catheter is outside the patient, any breach of the inner or outer vacuum systems will be detected by a high baseline flow through the console flow meter. In addition, a flow switch located in the console or in the catheter handle and mounted on the outer vacuum system will also detect a leak of air through a breach of the outer balloon or vacuum lumen. The flow switch is capable of detecting volumes of gas as little as 1 cc of vapor, and flow rates as little as 20 sccm. When the catheter is inserted into the patient, blood ingress through either the imler or outer vacuum lumens or both will be detected by the leak and blood detection systems. In the case of a constant pressure inflation with circulating flow, the balloon pressure can also be controlled with a PID-driven proportional valve located on the return vacuum lumen or a three-way solenoid valve in series with a pressure switch or pressure transducer.
Referring to FIG. 4, the inflation phase of the invention will now be discussed. Prior to positioning catheter 22 on the ablation site, the physician must first inflate the expandable membrane 23 inside the heart chamber and then position the balloon 23 proximate the ablation site. During this phase, the system is under vacuum and provides verification for leaks between balloon 23 and the blood. In one embodiment, balloon 23 is inflated by injecting fluid or gas through the umbilical under a fixed flow pressure. This insures a defined and constant pressure inside the balloon in order to provide a mechanical force for inflation. An alternate way to inflate balloon 23 is to use a fixed volume of inflation. This volume would be minimized in order to meet the constraints related to gas egress within the blood stream (maximum of 20cc within 10 minutes) and meet the requirement for pressure needed to inflate the balloon under the harshest room conditions.
FIG. 3 illustrates the inflation portion of the console mechanics of FIG. 2.
During the inflation phase, valve 24 is open toward reservoir 30 and valve 28 opens, while refilling valve 40 remains closed. A fixed amount of Na0 is injected to inflate balloon 23 in order to provide sufficient mechanical force for inflation. If a leak occurs in the balloon, the released volume of N20 would be no more than 20 cc. The solenoid valve 44 (shown in FIG. 33) remains open during this phase in order to ensure a vacuum in the safety line. If a lealc occurs in the inner balloon of the catheter, the flow switch 42 (FIG. 3), detects leaks as small as 1 cc of vapor. .
Flow switch 42 is active during all phases to prevent any leak of the inner balloon system in catheter 22. The leak and blood detection systems are still active and monitoring any blood ingress through the outer bacuum lumen. After air has been flushed from catheter 22 and the umbilicals connecting catheter 22 to console 20, and balloon 23 has been inflated, ablation may now take place.
A transition mode follows inflation but precedes ablation. In the case of cyrogenic ablation systems, a transition method is needed to transition from closed pressurized volume to an open circuit, which allows the flow of refrigerant to enter and exit the catheter tip while at the same time contrilling the balloon pressure in order to keep. the balloon inflated and in place.
During the transition , a pressure switch, which is adjusted to a pressure higher than atmospheric pressure but preferably lower than 20 Asia, monitors the pressure inside the balloon catheter 22.
The solenoid valve 24 remains closed until the pressure in the catheter is higher than the preset switch value after which the solenoid valve opens to allow evacuation of excess refrigerant.
When the pressure falls below the reset switch value, the solenoid valve 24 closes to keep the balloon inflated and above atmospheric pressure. During the transition, ablation is already initiated but the pressure switch controls the balloon pressure until refrigerant flow alone maintains the balloon open and above atmospheric pressure. The transition phase is considered complete when certain conditions are met: 1) when the pressure switch commands the solenoid valve 24 to open to vacuum and the balloon pressure remains above the present switch value; 2) the duration of the transition phase exceeds a predetermined time; and 3) the injection pressure reaches a predetermined value that is adequate to generate enough flow to maintain the balloon open. Check valve 56 is used to prevent any abnormal rise in the pressure in the catheter tip.
Another check valve 58, shown also in FIG. 6, prevents any excessive pressure in the safety vacuum line and in in the event the soloenoid valve 44 is blocked.
During the ablation phase, refrigerant is injected through the umbilical system into the ablation device 22. When injection of refrigerant is desired, N2Q gas is released from source 60 and provides high pressure liquid through a check valve 62 and a series of pressure regulators 34 and 36. Regulators 34 and 36 are primary and secondary pressure regulators respectively, which serve to bring the gas pressure down to between 810 and approximately 840 psig. The liquid nitrous oxide goes through a proportional valve 64 driven by a Proportional Integral Derivative (PID) controller 66 so that the refrigerant pressure can be varied from 0 psig to approximately 760 psig, and through an injection solenoid valve 68 which remains open. The N20 then passes through a sub-cooler 70 with various refrigeration components such as a compressor, a condenser, a capillary tube and a heat exchanger, which insures its liquid state through the umbilical and into the small diameter catheter injection tubing. During injection, solenoid vent valve 46 is closed. To detect a failure of this valve, the pressure switch 72 will close when detecting a pressure higher than 15 psig, creating a failure signal.
During the injection phase, proportional valve 64 is used to vary the pressure inside the injection line. This in turn will vary the flow rate of refrigerant to the catheter tip. An increase in the flow rate (less restriction by the regulator) lowers the temperature of the catheter tip.
Conversely, decreasing the flow rate allows the catheter tip to be waxmed by its suiTOUndings.
FIG. 5 illustrates the deflation and main path circuitry of the present invention. At the end of the ablation phase, the system provides a method to insure a controlled/slow deflation in order to prevent damaging the ablated tissue during balloon deflation. This can be a hazard due to cryoadhesion, which may occur when the catheter attaches to the tissue during freezing.
Referring to both FIGS. 3 and 5, during deflation, the solenoid valve 24 (FIG.
3) remains closed until the temperature in the balloon is higher than a predetermined temperature (usually above freezing to ensure that surrounding tissue has thawed). When the temperature increases to greater than the predetermined temperature, the solenoid valve 24 opens to vacuum and collapses the balloon. On both vacuum paths, liquid sensors and insulated liquid sparators 48 and 50 (FIG.
3) are installed to prevent any liquid from entering the vacuum pump 26. If this occurs, injection and /or inflation will be stopped and both valves 52 (FIG. 3) and 44 (FIG. 3) will switch to atmosphere.
FIG. 6 illustrates the safety vacuum portion of the console circuitry of FIG.
3. If a leak occurs in the catheter during inflation or ablation, flow switch 42 can detect such a leak in amounts as small as 1 cc of vapor. Upon detection of the leak, inflation of the balloon catheter is stopped. Prior to inflation, the flow switch can detect leaks of the outer balloon or guide wire lumen when the Gather is in the air. In case of pressurization of the safety vacuum line 1/3 psi above atmospheirc, a pressure relief valve 58 located distal to the flow switch will vent excess pressure.
Referring now to FIG. 7, one embodiment of the present invention is shown. The schematic in FIG. 7 illustrates the mechanical connection of the console 20, umbilical system 12 and catheter 22. The representation in FIG. 7 corresponds to the embodiment shown in FIG. 2A.
The internal components of console 20 are similar and correspond to those shown in greater detail in FIG. 3 explained above. In this embodiment, the balloon 23 is inflated by receiving gas or fluid from source 60 via coaxial umbilical 14. PID controller 66 controls the flow of pressurized fluid/gas from console 20 through umbilical system 12 to balloon 23.
FIG. 8 shows an alternate embodiment of the invention in which an intermediary station 74 containing all components and circuts to operate the balloon catheter is coupled to console 10, between the console and balloon catheter 23. Station 74 includes a series of shut-off valves and detection switches. Detection circuitry within station 74 can detect if the volume of gas within balloon catheter 23 has exceeded a certain predetermined amount (i.e. 20cc within the catheter and the umbilical system), and shut-off valves within station 74 are activated, preventing any further inflation. Station 74 advantageously provides a quicker and more effective way of detecting leakage of gas or liquid into the blood stream. If the pressure within balloon catheter 23 drops, this could be an indication that fluid within the balloon has escaped. By inserting station 74 within system 10, a quicker and more efficient way of detecting leaks and preventing unwanted balloon inflation is provided.
FIG. 9 shows yet another embodiment of the invention. Here, balloon inflation can be performed by a syringe 76 coupled to a saline water source 78 or any other fluid media including gasses or liquids. This embodiment becomes practical when manual balloon inflation is required.
In FIG. 10, intermediary station 74 includes a second inflation source 80. As in the embodiment depicted in FIG. 8, leak detection circuitry and shut-off valves located in station 74 provide an efficient way of detecting leaks and quickly prohibiting the further inflation of balloon catheter 23. Should further inflation be required, a separate pressurized N20 source 80 is provided in station 74, which is at a closer and more convenient location, i.e. ne'arer the catheter and not in a remote location such as console 20.
In FIG. 10, the refilling source 80 is located in the intermediate box 74 and inflation occurs through the outer vacuum umbilical. In FIG. 1 l, the refilling source is the coolant tank 60 located in the cryoablation console and inflation occurs through the inner vacuum umbilical.
It will be appreciated by persons skilled in the art that the present invention is not limited to what has been particularly shown and described herein above. In addition, unless mention was made above to the contrary, it should be noted that all of the accompanying drawings are not to scale. A variety of modifications and variations are possible in light of the above teachings without departing from the scope and spirit of the invention, which is limited only by the following claims.
Claims (31)
1. (Amended) A method of inflating and deflating a catheter having an expandable membrane, the method comprising the steps of:
controllably inflating the expandable membrane to a target pressure or volume;
injecting coolant through an umbilical under a fixed flow pressure;
maintaining the target pressure or volume of the expandable membrane; and controllably deflating the expandable membrane.
controllably inflating the expandable membrane to a target pressure or volume;
injecting coolant through an umbilical under a fixed flow pressure;
maintaining the target pressure or volume of the expandable membrane; and controllably deflating the expandable membrane.
2. (Cancelled)
3. (Original)The method of claim 1, wherein the steps of controllably inflating the expandable membrane to a target pressure or volume is performed by inflation/deflation control means located within a first console.
4. (Original)The method of claim 3, wherein the inflation/deflation control means is a Proportional Integral Derivative controller.
5. (Original)The method of claim 4, wherein the inflation/deflation control means further includes a pressure switch that controls an on/off valve.
6. (Original)The method of claim 1, wherein, if the target pressure or volume is not reached, further comprising the step of re-inflating the expandable membrane in order to reach the target pressure or volume.
7. (Original)The method of claim 6, wherein the step of re-inflating the expandable membrane is performed by a pressurized coolant source within an intermediary console located between the first console and the catheter.
8. (Original)The method of claim 7, wherein the pressurized coolant source is a fixed volume reservoir located within the first console.
9. (Cancelled)
10. (Cancelled)
11. (Amended)A method for inflating and deflating a catheter having an expandable membrane, the catheter being part of a catheter system including a first console, a catheter, and an umbilical system coupling the first console to the catheter, the method comprising the steps of:
evacuating air from the expandable membrane by creating a vacuum in the expandable membrane;
controllably inflating the expandable membrane to a target pressure or volume;
maintaining the expandable membrane at the target pressure or volume; and controllably deflating the expandable membrane.
evacuating air from the expandable membrane by creating a vacuum in the expandable membrane;
controllably inflating the expandable membrane to a target pressure or volume;
maintaining the expandable membrane at the target pressure or volume; and controllably deflating the expandable membrane.
12. (Amended)An apparatus for inflating and deflating a catheter having a first expandable membrane, the apparatus comprising:
a first console including means for controlling the inflation and deflation of the first expandable membrane in order to reach a target pressure or volume;
a catheter;
an umbilical system coupling the console to the catheter and delivering pressurized coolant to the first expandable membrane; and, an intermediary console coupled between the first console and the catheter.
a first console including means for controlling the inflation and deflation of the first expandable membrane in order to reach a target pressure or volume;
a catheter;
an umbilical system coupling the console to the catheter and delivering pressurized coolant to the first expandable membrane; and, an intermediary console coupled between the first console and the catheter.
13. (Original)The apparatus of claim 12, wherein the first console includes means for determining if the first expandable membrane has reached its target pressure or volume.
14. (Original)The apparatus of claim 13, wherein the means for determining if the first expandable membrane has reached its target pressure or volume is a Proportional Integral Derivative controller.
15. (Cancelled)
16. (Amended)The apparatus of claim 12, wherein the intermediary console includes means for interrupting the flow of pressurized coolant from the first console to the catheter if the target pressure or volume has been exceeded.
17. (Original)The apparatus of claim 16, wherein the means for interrupting the flow of pressurized coolant from the first console to the catheter is a shut-off valve located within the intermediary console.
18. (Amended)The apparatus of claim 12, wherein the intermediary console includes means for re-inflating the first expandable membrane.
19. The apparatus of claim 18, wherein the means for re-inflating the first expandable membrane is a source of pressurized coolant within the intermediary console.
20. An apparatus for inflating and deflating a catheter having a first expandable membrane; the apparatus comprising:
a first console including means for controlling the inflation and deflation of the first expandable membrane in order to reach a target pressure or volume;
a catheter;
an umbilical system coupling the console to the catheter and delivering pressurized coolant to the first expandable membrane;
wherein the catheter further comprises a second expandable membrane, the first and second expandable membranes defining a safety vacuum space disposed between the first and second expandable membranes; and a flow switch for detecting volumes of gas.
a first console including means for controlling the inflation and deflation of the first expandable membrane in order to reach a target pressure or volume;
a catheter;
an umbilical system coupling the console to the catheter and delivering pressurized coolant to the first expandable membrane;
wherein the catheter further comprises a second expandable membrane, the first and second expandable membranes defining a safety vacuum space disposed between the first and second expandable membranes; and a flow switch for detecting volumes of gas.
21. The apparatus of claim 20, further comprising a vacuum umbilical in communication with the safety vacuum space.
22. (Cancelled)
23. The apparatus of claim 20, further comprising a flow detector, the flow switch and flow detector being in fluid communication with the safety vacuum space.
24. The apparatus of claim 20, further comprising a pressure sensing element in communication with the safety vacuum space.
25. The apparatus of claim 20, further comprising a leak detection element in communication with the safety vacuum space.
26. The apparatus of claim 20, further comprising a blood detection element in communication with the safety vacuum space.
27. The apparatus of claim 20, further comprising a fluid detection element in communication with the safety vacuum space.
28. The apparatus of claim 12, further comprising a pressure sensing element in communication with a volume within the first expandable membrane.
29. The apparatus of claim 12, further comprising a leak detection element in communication with a volume within the first expandable membrane.
30. The apparatus of claim 12, further comprising a blood detection element in communication with a volume within the first expandable membrane.
31. The apparatus of claim 12, further comprising a fluid detection element in communication with a volume within the first expandable membrane.
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA2652097A CA2652097C (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
| CA2652112A CA2652112C (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US10/806,995 US7727228B2 (en) | 2004-03-23 | 2004-03-23 | Method and apparatus for inflating and deflating balloon catheters |
| US10/806,995 | 2004-03-23 | ||
| PCT/CA2005/000437 WO2005089853A1 (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
Related Child Applications (2)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2652112A Division CA2652112C (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
| CA2652097A Division CA2652097C (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2555441A1 CA2555441A1 (en) | 2005-09-29 |
| CA2555441C true CA2555441C (en) | 2010-09-07 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2652097A Expired - Fee Related CA2652097C (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
| CA2555441A Expired - Fee Related CA2555441C (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
| CA2652112A Expired - Fee Related CA2652112C (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
Family Applications Before (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2652097A Expired - Fee Related CA2652097C (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
Family Applications After (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2652112A Expired - Fee Related CA2652112C (en) | 2004-03-23 | 2005-03-23 | Method and apparatus for inflating and deflating balloon catheters |
Country Status (4)
| Country | Link |
|---|---|
| US (7) | US7727228B2 (en) |
| EP (2) | EP1980287B1 (en) |
| CA (3) | CA2652097C (en) |
| WO (1) | WO2005089853A1 (en) |
Families Citing this family (193)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7527622B2 (en) * | 1999-08-23 | 2009-05-05 | Cryocath Technologies Inc. | Endovascular cryotreatment catheter |
| US7455666B2 (en) | 2001-07-13 | 2008-11-25 | Board Of Regents, The University Of Texas System | Methods and apparatuses for navigating the subarachnoid space |
| AU2003272682C1 (en) | 2002-09-20 | 2009-07-16 | Nellix, Inc. | Stent-graft with positioning anchor |
| US8491636B2 (en) | 2004-03-23 | 2013-07-23 | Medtronic Cryopath LP | Method and apparatus for inflating and deflating balloon catheters |
| US7727228B2 (en) | 2004-03-23 | 2010-06-01 | Medtronic Cryocath Lp | Method and apparatus for inflating and deflating balloon catheters |
| US9555223B2 (en) | 2004-03-23 | 2017-01-31 | Medtronic Cryocath Lp | Method and apparatus for inflating and deflating balloon catheters |
| JP3962999B2 (en) * | 2004-03-29 | 2007-08-22 | 有限会社エスアールジェイ | Endoscope device |
| US7156840B2 (en) * | 2004-06-29 | 2007-01-02 | Cryocor, Inc. | Pressure monitor for cryoablation catheter |
| US7163535B2 (en) * | 2004-06-30 | 2007-01-16 | Cryocor, Inc. | System for detecting leaks and occlusions in a cryoablation catheter |
| US8048145B2 (en) | 2004-07-22 | 2011-11-01 | Endologix, Inc. | Graft systems having filling structures supported by scaffolds and methods for their use |
| US7544260B2 (en) * | 2004-10-20 | 2009-06-09 | Mark Banister | Micro thruster, micro thruster array and polymer gas generator |
| US7604631B2 (en) * | 2004-12-15 | 2009-10-20 | Boston Scientific Scimed, Inc. | Efficient controlled cryogenic fluid delivery into a balloon catheter and other treatment devices |
| US8858495B2 (en) * | 2004-12-28 | 2014-10-14 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Five degree of freedom ultrasound catheter and catheter control handle |
| US7691095B2 (en) * | 2004-12-28 | 2010-04-06 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Bi-directional steerable catheter control handle |
| US8206345B2 (en) * | 2005-03-07 | 2012-06-26 | Medtronic Cryocath Lp | Fluid control system for a medical device |
| US7740627B2 (en) | 2005-04-29 | 2010-06-22 | Medtronic Cryocath Lp | Surgical method and apparatus for treating atrial fibrillation |
| US7794455B2 (en) * | 2005-04-29 | 2010-09-14 | Medtronic Cryocath Lp | Wide area ablation of myocardial tissue |
| AU2006269419A1 (en) | 2005-07-07 | 2007-01-18 | Nellix, Inc. | Systems and methods for endovascular aneurysm treatment |
| US20070239082A1 (en) * | 2006-01-27 | 2007-10-11 | General Patent, Llc | Shock Wave Treatment Device |
| US9814511B2 (en) * | 2006-06-28 | 2017-11-14 | Medtronic Cryocath Lp | Variable geometry cooling chamber |
| US10208158B2 (en) | 2006-07-10 | 2019-02-19 | Medipacs, Inc. | Super elastic epoxy hydrogel |
| EP2227635A2 (en) | 2007-12-03 | 2010-09-15 | Medipacs, Inc. | Fluid metering device |
| EP2245678A1 (en) * | 2008-02-19 | 2010-11-03 | Medipacs, Inc. | Therapeutic pressure system |
| US8579890B2 (en) * | 2008-03-13 | 2013-11-12 | Boston Scientific Scimed, Inc. | Cryo-ablation refrigerant distribution catheter |
| DE112009000700T5 (en) * | 2008-03-20 | 2011-02-10 | Medrad, Inc. | Hydrodynamic direct current catheter system |
| JP5663471B2 (en) | 2008-04-25 | 2015-02-04 | ネリックス・インコーポレーテッド | Stent / graft delivery system |
| WO2009140066A1 (en) | 2008-05-12 | 2009-11-19 | Boston Scientific Scimed, Inc. | Apparatus for chilling cryo-ablation coolant |
| US8480663B2 (en) * | 2008-05-15 | 2013-07-09 | Boston Scientific Scimed, Inc. | Apparatus and methods for cryogenically ablating tissue and adjusting cryogenic ablation regions |
| US8187261B2 (en) | 2008-05-29 | 2012-05-29 | Boston Scientific Scimed, Inc. | Regulating internal pressure of a cryotherapy balloon catheter |
| JP2011522615A (en) | 2008-06-04 | 2011-08-04 | ネリックス・インコーポレーテッド | Sealing device and method of use |
| JP5233031B2 (en) * | 2008-07-15 | 2013-07-10 | 株式会社デージーエス・コンピュータ | Cryotherapy planning device and cryotherapy device |
| EP2341859B1 (en) | 2008-10-06 | 2017-04-05 | Virender K. Sharma | Apparatus for tissue ablation |
| US9561068B2 (en) | 2008-10-06 | 2017-02-07 | Virender K. Sharma | Method and apparatus for tissue ablation |
| US10064697B2 (en) | 2008-10-06 | 2018-09-04 | Santa Anna Tech Llc | Vapor based ablation system for treating various indications |
| US9561066B2 (en) | 2008-10-06 | 2017-02-07 | Virender K. Sharma | Method and apparatus for tissue ablation |
| US10695126B2 (en) * | 2008-10-06 | 2020-06-30 | Santa Anna Tech Llc | Catheter with a double balloon structure to generate and apply a heated ablative zone to tissue |
| US9123614B2 (en) | 2008-10-07 | 2015-09-01 | Mc10, Inc. | Methods and applications of non-planar imaging arrays |
| US9289132B2 (en) | 2008-10-07 | 2016-03-22 | Mc10, Inc. | Catheter balloon having stretchable integrated circuitry and sensor array |
| US8097926B2 (en) | 2008-10-07 | 2012-01-17 | Mc10, Inc. | Systems, methods, and devices having stretchable integrated circuitry for sensing and delivering therapy |
| US9545216B2 (en) | 2011-08-05 | 2017-01-17 | Mc10, Inc. | Catheter balloon methods and apparatus employing sensing elements |
| US8389862B2 (en) | 2008-10-07 | 2013-03-05 | Mc10, Inc. | Extremely stretchable electronics |
| WO2010061379A1 (en) * | 2008-11-03 | 2010-06-03 | G.I. View Ltd | Remote pressure sensing system and method thereof |
| US8226601B2 (en) | 2008-11-12 | 2012-07-24 | Sanovas, Inc. | Resector balloon system |
| US8540667B2 (en) * | 2008-11-12 | 2013-09-24 | Sanovas, Inc. | Multi-balloon catheter for extravasated drug delivery |
| US8382746B2 (en) | 2008-11-21 | 2013-02-26 | C2 Therapeutics, Inc. | Cryogenic ablation system and method |
| US10772717B2 (en) | 2009-05-01 | 2020-09-15 | Endologix, Inc. | Percutaneous method and device to treat dissections |
| US9579103B2 (en) | 2009-05-01 | 2017-02-28 | Endologix, Inc. | Percutaneous method and device to treat dissections |
| WO2010141500A1 (en) | 2009-06-01 | 2010-12-09 | Theranova, Llc | Methods and apparatus for treatment of a body cavity or lumen |
| US8205779B2 (en) * | 2009-07-23 | 2012-06-26 | Tyco Healthcare Group Lp | Surgical stapler with tactile feedback system |
| WO2011017123A2 (en) | 2009-07-27 | 2011-02-10 | Endologix, Inc. | Stent graft |
| WO2011019947A1 (en) * | 2009-08-14 | 2011-02-17 | Boston Scientific Scimed, Inc. | Medical device comprising a catheter coupled to a conduct ive -fluid detector |
| WO2011032011A1 (en) | 2009-09-10 | 2011-03-17 | Medipacs, Inc. | Low profile actuator and improved method of caregiver controlled administration of therapeutics |
| US9723122B2 (en) | 2009-10-01 | 2017-08-01 | Mc10, Inc. | Protective cases with integrated electronics |
| WO2011044387A2 (en) | 2009-10-07 | 2011-04-14 | The Board Of Regents Of The University Of Texas System | Pressure-sensing medical devices, systems and methods, and methods of forming medical devices |
| US20110092967A1 (en) * | 2009-10-21 | 2011-04-21 | Medtronic Cryocath Lp | Deflation mechanism for a medical device |
| US8529562B2 (en) * | 2009-11-13 | 2013-09-10 | Minerva Surgical, Inc | Systems and methods for endometrial ablation |
| US20110144637A1 (en) * | 2009-12-11 | 2011-06-16 | Medtronic Cryocath Lp | Vein Occlusion Devices and Methods for Catheter-Based Ablation |
| US20110276078A1 (en) | 2009-12-30 | 2011-11-10 | Nellix, Inc. | Filling structure for a graft system and methods of use |
| US10743854B2 (en) | 2010-01-20 | 2020-08-18 | Micro Interventional Devices, Inc. | Tissue closure device and method |
| US10058314B2 (en) | 2010-01-20 | 2018-08-28 | Micro Interventional Devices, Inc. | Tissue closure device and method |
| US10959840B2 (en) | 2010-01-20 | 2021-03-30 | Micro Interventional Devices, Inc. | Systems and methods for affixing a prosthesis to tissue |
| US9980708B2 (en) | 2010-01-20 | 2018-05-29 | Micro Interventional Devices, Inc. | Tissue closure device and method |
| US8926602B2 (en) | 2010-01-28 | 2015-01-06 | Medtronic Cryocath Lp | Triple balloon catheter |
| US9500186B2 (en) | 2010-02-01 | 2016-11-22 | Medipacs, Inc. | High surface area polymer actuator with gas mitigating components |
| EP2613748B1 (en) | 2010-09-10 | 2018-09-05 | Medivance Incorporated | Cooling medical pad |
| US9622907B2 (en) | 2010-09-10 | 2017-04-18 | Medivance Incorporated | Cooling medical pad |
| US9028417B2 (en) | 2010-10-18 | 2015-05-12 | CardioSonic Ltd. | Ultrasound emission element |
| EP2661304A1 (en) | 2010-10-18 | 2013-11-13 | Cardiosonic Ltd. | Therapeutics reservoir |
| US9566456B2 (en) * | 2010-10-18 | 2017-02-14 | CardioSonic Ltd. | Ultrasound transceiver and cooling thereof |
| US8585601B2 (en) | 2010-10-18 | 2013-11-19 | CardioSonic Ltd. | Ultrasound transducer |
| US9655666B2 (en) * | 2010-10-29 | 2017-05-23 | Medtronic Ablatio Frontiers LLC | Catheter with coronary sinus ostium anchor |
| WO2012068298A1 (en) | 2010-11-17 | 2012-05-24 | Endologix, Inc. | Devices and methods to treat vascular dissections |
| US8801768B2 (en) | 2011-01-21 | 2014-08-12 | Endologix, Inc. | Graft systems having semi-permeable filling structures and methods for their use |
| MX341823B (en) | 2011-02-01 | 2016-09-05 | Channel Medsystems Inc | Methods and apparatus for cyrogenic treatment of a body cavity or lumen. |
| US8597239B2 (en) * | 2011-03-01 | 2013-12-03 | Sanovas, Inc. | Abrading balloon catheter for extravasated drug delivery |
| US8348890B2 (en) | 2011-03-01 | 2013-01-08 | Sanovas, Inc. | Nested balloon catheter for localized drug delivery |
| US20160074581A1 (en) | 2014-09-17 | 2016-03-17 | Lawrence J. Gerrans | Modulated Drug Delivery |
| US10898693B2 (en) | 2011-03-01 | 2021-01-26 | Sanovas Intellectual Property, Llc | Nasal delivery of agents with nested balloon catheter |
| US9415195B2 (en) | 2011-04-06 | 2016-08-16 | Engologix, Inc. | Method and system for treating aneurysms |
| US20120265452A1 (en) * | 2011-04-14 | 2012-10-18 | Galil Medical Inc. | Method of monitoring gas supply during a cryosurgical procedure |
| KR102000302B1 (en) | 2011-05-27 | 2019-07-15 | 엠씨10, 인크 | Electronic, optical and/or mechanical apparatus and systems and methods for fabricating same |
| US20130018369A1 (en) * | 2011-07-13 | 2013-01-17 | Medtronic Cryocath Lp | Systems and methods for treatment in proximity to sensitive tissue structures |
| US9387031B2 (en) | 2011-07-29 | 2016-07-12 | Medtronic Ablation Frontiers Llc | Mesh-overlayed ablation and mapping device |
| JP6441679B2 (en) | 2011-12-09 | 2018-12-19 | メタベンション インコーポレイテッド | Therapeutic neuromodulation of the liver system |
| CN104302689A (en) | 2012-03-14 | 2015-01-21 | 麦德医像公司 | Smart polymer materials with excess reactive molecules |
| WO2013157011A2 (en) | 2012-04-18 | 2013-10-24 | CardioSonic Ltd. | Tissue treatment |
| US11357447B2 (en) | 2012-05-31 | 2022-06-14 | Sonivie Ltd. | Method and/or apparatus for measuring renal denervation effectiveness |
| US9226402B2 (en) | 2012-06-11 | 2015-12-29 | Mc10, Inc. | Strain isolation structures for stretchable electronics |
| US9168094B2 (en) | 2012-07-05 | 2015-10-27 | Mc10, Inc. | Catheter device including flow sensing |
| US9295842B2 (en) | 2012-07-05 | 2016-03-29 | Mc10, Inc. | Catheter or guidewire device including flow sensing and use thereof |
| US9113911B2 (en) | 2012-09-06 | 2015-08-25 | Medtronic Ablation Frontiers Llc | Ablation device and method for electroporating tissue cells |
| US9082025B2 (en) | 2012-10-09 | 2015-07-14 | Mc10, Inc. | Conformal electronics integrated with apparel |
| US9171794B2 (en) | 2012-10-09 | 2015-10-27 | Mc10, Inc. | Embedding thin chips in polymer |
| US10342608B2 (en) | 2012-10-18 | 2019-07-09 | The Board Of Trustees Of The Leland Stanford Junior University | Ablation catheter system and method for deploying same |
| USD685916S1 (en) | 2012-11-26 | 2013-07-09 | Medivance Incorporated | Medical cooling pad |
| WO2014113724A2 (en) | 2013-01-17 | 2014-07-24 | Sharma Virender K | Method and apparatus for tissue ablation |
| US10076384B2 (en) | 2013-03-08 | 2018-09-18 | Symple Surgical, Inc. | Balloon catheter apparatus with microwave emitter |
| US9358042B2 (en) | 2013-03-13 | 2016-06-07 | The Spectranetics Corporation | Expandable member for perforation occlusion |
| US10201638B2 (en) | 2013-03-14 | 2019-02-12 | Endologix, Inc. | Systems and methods for forming materials in situ within a medical device |
| US9351783B2 (en) * | 2013-05-01 | 2016-05-31 | Medtronic Cryocath Lp | Diagnostic guidewire for cryoablation sensing and pressure monitoring |
| US9706647B2 (en) | 2013-05-14 | 2017-07-11 | Mc10, Inc. | Conformal electronics including nested serpentine interconnects |
| MX346726B (en) * | 2013-05-23 | 2017-03-30 | Channel Medsystems Inc | Cyrogenic treatment systems. |
| WO2014188430A2 (en) | 2013-05-23 | 2014-11-27 | CardioSonic Ltd. | Devices and methods for renal denervation and assessment thereof |
| US9636172B2 (en) | 2013-05-31 | 2017-05-02 | Medtronic Cryocath Lp | Compliant balloon with liquid injection |
| CA2920485A1 (en) | 2013-08-05 | 2015-02-12 | Mc10, Inc. | Flexible temperature sensor including conformable electronics |
| US9895183B2 (en) | 2013-09-17 | 2018-02-20 | Channel Medsystems, Inc. | Liner for cryogenic treatment systems |
| US9687288B2 (en) | 2013-09-30 | 2017-06-27 | Arrinex, Inc. | Apparatus and methods for treating rhinitis |
| KR20160065948A (en) | 2013-10-07 | 2016-06-09 | 엠씨10, 인크 | Conformal sensor systems for sensing and analysis |
| CN107669332B (en) | 2013-11-01 | 2020-09-18 | 美国宾得公司 | Cryogenic ablation catheter, handle assembly and cryogenic balloon ablation system |
| JP6413131B2 (en) * | 2013-11-06 | 2018-10-31 | クライオセラピューティクス ゲーエムベーハー | Catheter for plaque stabilization |
| EP3071096A4 (en) | 2013-11-22 | 2017-08-09 | Mc10, Inc. | Conformal sensor systems for sensing and analysis of cardiac activity |
| KR20160106582A (en) * | 2014-01-03 | 2016-09-12 | 엠씨10, 인크 | Catheter or guidewire device including flow sensing and use thereof |
| WO2015103580A2 (en) | 2014-01-06 | 2015-07-09 | Mc10, Inc. | Encapsulated conformal electronic systems and devices, and methods of making and using the same |
| KR20160129007A (en) | 2014-03-04 | 2016-11-08 | 엠씨10, 인크 | Multi-part flexible encapsulation housing for electronic devices |
| US11419656B2 (en) * | 2014-04-04 | 2022-08-23 | Cpsi Holdings Llc | Thermal regulation catheter system |
| US10610279B2 (en) | 2014-04-10 | 2020-04-07 | Channel Medsystems, Inc. | Apparatus and methods for regulating cryogenic treatment |
| US10054262B2 (en) * | 2014-04-16 | 2018-08-21 | Cpsi Holdings Llc | Pressurized sub-cooled cryogenic system |
| US9763743B2 (en) | 2014-07-25 | 2017-09-19 | Arrinex, Inc. | Apparatus and method for treating rhinitis |
| US9899330B2 (en) | 2014-10-03 | 2018-02-20 | Mc10, Inc. | Flexible electronic circuits with embedded integrated circuit die |
| US10297572B2 (en) | 2014-10-06 | 2019-05-21 | Mc10, Inc. | Discrete flexible interconnects for modules of integrated circuits |
| USD781270S1 (en) | 2014-10-15 | 2017-03-14 | Mc10, Inc. | Electronic device having antenna |
| CA2973748C (en) | 2015-01-27 | 2020-04-14 | Medivance Incorporated | Improved medical pad and system for thermotherapy |
| US10477354B2 (en) | 2015-02-20 | 2019-11-12 | Mc10, Inc. | Automated detection and configuration of wearable devices based on on-body status, location, and/or orientation |
| WO2016140961A1 (en) | 2015-03-02 | 2016-09-09 | Mc10, Inc. | Perspiration sensor |
| US9414878B1 (en) | 2015-05-15 | 2016-08-16 | C2 Therapeutics, Inc. | Cryogenic balloon ablation 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 |
| US10433894B2 (en) | 2015-07-02 | 2019-10-08 | Medtronic Cryocath Lp | N2O liquefaction system with subcooling heat exchanger for medical device |
| WO2017015000A1 (en) | 2015-07-17 | 2017-01-26 | Mc10, Inc. | Conductive stiffener, method of making a conductive stiffener, and conductive adhesive and encapsulation layers |
| EP3328331A4 (en) | 2015-07-27 | 2019-04-10 | University of Maryland, Baltimore | Body temperature management devices and methods |
| US10499892B2 (en) | 2015-08-11 | 2019-12-10 | The Spectranetics Corporation | Temporary occlusion balloon devices and methods for preventing blood flow through a vascular perforation |
| US10449336B2 (en) | 2015-08-11 | 2019-10-22 | The Spectranetics Corporation | Temporary occlusions balloon devices and methods for preventing blood flow through a vascular perforation |
| US10709384B2 (en) | 2015-08-19 | 2020-07-14 | Mc10, Inc. | Wearable heat flux devices and methods of use |
| US9568918B1 (en) * | 2015-08-27 | 2017-02-14 | Southwest Research Institute | Balloon system |
| US11219351B2 (en) | 2015-09-03 | 2022-01-11 | Neptune Medical Inc. | Device for endoscopic advancement through the small intestine |
| EP3356003A4 (en) | 2015-10-01 | 2019-04-03 | Mc10, Inc. | Method and system for interacting with a virtual environment |
| CN108289630A (en) | 2015-10-05 | 2018-07-17 | Mc10股份有限公司 | Method and system for nerve modulation and stimulation |
| ES2874028T3 (en) | 2015-10-08 | 2021-11-04 | Channel Medsystems Inc | Exhaust gas collection bag for cryoablation treatment |
| WO2017095756A1 (en) | 2015-11-30 | 2017-06-08 | Adagio Medical, Inc. | Ablation method for creating elongate continuous lesions enclosing multiple vessel entries |
| EP3386437A4 (en) * | 2015-12-07 | 2020-03-25 | Micro Interventional Devices, Inc. | Affixing a prosthesis to tissue |
| GB2546082B (en) * | 2016-01-06 | 2018-05-16 | Airway Medix S A | Closed suction system |
| US11602260B2 (en) | 2016-02-11 | 2023-03-14 | Arrinex, Inc. | Method and device for image guided post-nasal nerve ablation |
| US10277386B2 (en) | 2016-02-22 | 2019-04-30 | Mc10, Inc. | System, devices, and method for on-body data and power transmission |
| US10673280B2 (en) | 2016-02-22 | 2020-06-02 | Mc10, Inc. | System, device, and method for coupled hub and sensor node on-body acquisition of sensor information |
| CN109310340A (en) | 2016-04-19 | 2019-02-05 | Mc10股份有限公司 | For measuring the method and system of sweat |
| US11331140B2 (en) | 2016-05-19 | 2022-05-17 | Aqua Heart, Inc. | Heated vapor ablation systems and methods for treating cardiac conditions |
| CN109414284B (en) | 2016-05-20 | 2021-08-10 | 美国宾得公司 | Cryogenic ablation system with rotatable and translatable catheter |
| US10524859B2 (en) | 2016-06-07 | 2020-01-07 | Metavention, Inc. | Therapeutic tissue modulation devices and methods |
| CN109600988B (en) | 2016-06-15 | 2021-08-31 | 阿里内克斯股份有限公司 | Device and method for treating the outer surface of the nasal cavity |
| WO2018013329A1 (en) * | 2016-07-15 | 2018-01-18 | University Of Florida Research Foundation, Inc. | Epicardial cryoablation |
| US10939965B1 (en) | 2016-07-20 | 2021-03-09 | Arrinex, Inc. | Devices and methods for treating a nerve of the nasal cavity using image guidance |
| US10447347B2 (en) | 2016-08-12 | 2019-10-15 | Mc10, Inc. | Wireless charger and high speed data off-loader |
| WO2018035452A1 (en) | 2016-08-18 | 2018-02-22 | Neptune Medical | Device and method for enhanced visualization of the small intestine |
| US11253312B2 (en) | 2016-10-17 | 2022-02-22 | Arrinex, Inc. | Integrated nasal nerve detector ablation-apparatus, nasal nerve locator, and methods of use |
| US11400205B2 (en) | 2016-11-23 | 2022-08-02 | Biosense Webster (Israel) Ltd. | Balloon-in-balloon irrigation balloon catheter |
| US10821272B2 (en) | 2016-11-23 | 2020-11-03 | Biosense Webster (Israel) Ltd. | Double balloon catheter having a lobed inner balloon |
| US10874307B2 (en) * | 2017-01-24 | 2020-12-29 | Verily Life Sciences Llc | Digital artery blood pressure monitor |
| US20200129328A1 (en) * | 2017-03-15 | 2020-04-30 | Bingren Hu | Body temperature management devices and methods |
| US20200094080A1 (en) | 2017-03-20 | 2020-03-26 | Sonivie Ltd. | Method for treating heart failure by improving ejection fraction of a patient |
| WO2018191013A1 (en) * | 2017-04-11 | 2018-10-18 | Cryterion Medical, Inc. | Pressure control assembly for cryogenic balloon catheter system |
| JP7300999B2 (en) | 2017-04-28 | 2023-06-30 | アリネックス， インコーポレイテッド | Systems and methods for locating blood vessels in the treatment of rhinitis |
| US10492844B2 (en) | 2017-05-25 | 2019-12-03 | Channel Medsystems, Inc. | Tethered system for cryogenic treatment |
| US11185245B2 (en) * | 2017-06-03 | 2021-11-30 | Sentinel Medical Technologies, Llc. | Catheter for monitoring pressure for muscle compartment syndrome |
| US11045143B2 (en) | 2017-06-03 | 2021-06-29 | Sentinel Medical Technologies, LLC | Catheter with connectable hub for monitoring pressure |
| US11045128B2 (en) | 2017-06-03 | 2021-06-29 | Sentinel Medical Technologies, LLC | Catheter for monitoring intra-abdominal pressure |
| CN107307901B (en) * | 2017-06-22 | 2021-05-11 | 心诺普医疗技术（北京）有限公司 | Cryoablation system |
| EP3459469A1 (en) | 2017-09-23 | 2019-03-27 | Universität Zürich | Medical occluder device |
| WO2019083765A1 (en) * | 2017-10-27 | 2019-05-02 | St. Jude Medical, Cardiology Division, Inc. | Pulmonary vein isolation balloon catheter |
| US10595918B2 (en) | 2018-01-08 | 2020-03-24 | Medtronic Holding Company Sàrl | High-pressure balloon catheter with pressure regulating valve |
| JP2021525598A (en) | 2018-06-01 | 2021-09-27 | サンタ アナ テック エルエルシーＳａｎｔａ Ａｎｎａ Ｔｅｃｈ Ｌｌｃ | Multi-stage steam-based ablation processing method and steam generation and delivery system |
| JP7066850B2 (en) * | 2018-07-10 | 2022-05-13 | オリンパス株式会社 | Phototherapy support device, phototherapy system and phototherapy support method |
| JP2021531111A (en) | 2018-07-19 | 2021-11-18 | ネプチューン メディカル インク． | Dynamic hardening medical composite structure |
| CN108969088A (en) * | 2018-08-08 | 2018-12-11 | 兖矿集团有限公司总医院 | A kind of clinical freezing freezing foley's tube with treatment atrial fibrillation |
| CN113015495A (en) | 2018-09-11 | 2021-06-22 | 阿卡赫特有限公司 | Heating steam ablation system and method for treating heart disease |
| US11672457B2 (en) | 2018-11-24 | 2023-06-13 | Sentinel Medical Technologies, Llc. | Catheter for monitoring pressure |
| WO2020132379A1 (en) * | 2018-12-20 | 2020-06-25 | The Regents Of The University Of Michigan | Anastomosis testing device and method |
| US11779263B2 (en) * | 2019-02-08 | 2023-10-10 | Sentinel Medical Technologies, Llc. | Catheter for monitoring intra-abdominal pressure for assessing preeclampsia |
| US11793392B2 (en) | 2019-04-17 | 2023-10-24 | Neptune Medical Inc. | External working channels |
| US11730385B2 (en) | 2019-08-08 | 2023-08-22 | Sentinel Medical Technologies, LLC | Cable for use with pressure monitoring catheters |
| CN110623724B (en) * | 2019-09-05 | 2020-07-24 | 南京桑迪医疗科技有限公司 | Radio frequency plasma needle knife external water-cooling anti-inflammation device and use method thereof |
| WO2021059273A2 (en) | 2019-09-26 | 2021-04-01 | Universitat Zurich | Left atrial appendage occlusion devices |
| US11617543B2 (en) | 2019-12-30 | 2023-04-04 | Sentinel Medical Technologies, Llc. | Catheter for monitoring pressure |
| CN111329575B (en) * | 2020-03-04 | 2021-10-26 | 上海微创电生理医疗科技股份有限公司 | Freezing sacculus pipe system |
| CN115666676A (en) | 2020-03-30 | 2023-01-31 | 海王星医疗公司 | Laminar wall for rigidifying device |
| US20210307804A1 (en) * | 2020-04-02 | 2021-10-07 | Medtronic Cryocath Lp | Control method for a one balloon fits all in automated mode |
| KR20220015460A (en) | 2020-06-09 | 2022-02-08 | 에이시시유 타겟 메디파르마 (상하이) 컴퍼니 리미티드 | Double Frozen Inflation Balloons |
| US20220047303A1 (en) * | 2020-08-17 | 2022-02-17 | Ebr Systems, Inc. | Systems and methods for delivering stimulation electrodes to endocardial or other tissue |
| CN112402005B (en) * | 2020-10-21 | 2022-06-14 | 宁波胜杰康生物科技有限公司 | Cavity channel cryotherapy system |
| KR20230133374A (en) * | 2021-01-29 | 2023-09-19 | 넵튠 메디컬 인코포레이티드 | Device and method for preventing inadvertent movement of a dynamic stiffening device |
| US20230053149A1 (en) * | 2021-08-10 | 2023-02-16 | Medtronic Cryocath Lp | Contact pressure assessment for cryoballoon ablation catheters |
| WO2023039310A1 (en) * | 2021-09-10 | 2023-03-16 | Cardiovascular Systems, Inc. | Drug coated balloon for angioplasty systems with programmed inflation sequences and adaptive monitoring control of inflation sequences |
| US20230346204A1 (en) | 2022-04-27 | 2023-11-02 | Neptune Medical Inc. | Endoscope sheath apparatuses |
| US20230389976A1 (en) * | 2022-06-06 | 2023-12-07 | Medtronic Cryocath Lp | Delivering refrigerant to catheters for cryotherapy |
Family Cites Families (294)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3125096A (en) * | 1964-03-17 | Compressor | ||
| 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 |
| US3398738A (en) | 1964-09-24 | 1968-08-27 | Aerojet General Co | Refrigerated surgical probe |
| US3425417A (en) * | 1965-02-24 | 1969-02-04 | Maurice S Kanbar | Refillable cryogenic probe for surgical use |
| 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 |
| US3924628A (en) * | 1972-12-01 | 1975-12-09 | William Droegemueller | Cyrogenic bladder for necrosing tissue cells |
| US3903871A (en) | 1974-05-01 | 1975-09-09 | Us Navy | Ophthalmodynamometer |
| US3938514A (en) | 1974-07-18 | 1976-02-17 | Boucher Lionel J | Bladder wash method and apparatus |
| US4000626A (en) | 1975-02-27 | 1977-01-04 | Webber Robert C | Liquid convection fluid heat exchanger for refrigeration circuit |
| FR2304771A1 (en) | 1975-03-21 | 1976-10-15 | Chaudronnerie Entr Indle | METHOD AND APPARATUS FOR TRANSFORMATION OF RELATIVELY LOW TEMPERATURE HEAT INTO DRIVING FORCE OR ENERGY |
| US4029099A (en) | 1975-12-04 | 1977-06-14 | Loretta Alice Fifield | Urine drainage apparatus |
| US4043341A (en) | 1975-12-09 | 1977-08-23 | Tromovitch Theodore A | Portable cryosurgical instrument |
| US4072152A (en) | 1976-02-23 | 1978-02-07 | Linehan John H | Orthopedic cryosurgical apparatus |
| FR2384221A1 (en) | 1977-03-16 | 1978-10-13 | Air Liquide | PLATE EXCHANGER TYPE HEAT EXCHANGE ASSEMBLY |
| US4176662A (en) | 1977-06-17 | 1979-12-04 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Apparatus for endoscopic examination |
| DE2831199C3 (en) * | 1978-07-15 | 1981-01-08 | Erbe Elektromedizin Gmbh & Co Kg, 7400 Tuebingen | Cryosurgical device |
| FR2471566B1 (en) | 1979-12-12 | 1986-09-05 | Technip Cie | METHOD AND SYSTEM FOR LIQUEFACTION OF A LOW-BOILING GAS |
| US4411656A (en) | 1982-01-29 | 1983-10-25 | Urologic & Enteric Research Associates | Compressible syringe |
| US4509370A (en) | 1982-09-30 | 1985-04-09 | Regents Of The University Of California | Pressure-sensitive optrode |
| JPS59124312A (en) | 1982-12-29 | 1984-07-18 | Sumitomo Electric Ind Ltd | Image observing device |
| FR2545589B1 (en) | 1983-05-06 | 1985-08-30 | Technip Cie | METHOD AND APPARATUS FOR COOLING AND LIQUEFACTING AT LEAST ONE GAS WITH LOW BOILING POINT, SUCH AS NATURAL GAS |
| US4534339A (en) | 1983-10-17 | 1985-08-13 | Warner-Lambert Technologies, Inc. | Endoscope |
| SE459883B (en) | 1984-02-14 | 1989-08-14 | Andersson Bengt O K | SEAT AND DEVICE FOR PRESSURE AIR COOLING |
| GB2163655B (en) | 1984-08-20 | 1988-04-07 | Fischell Robert | Stiffener cylinder for an inflatable penile erection device |
| DE3565718D1 (en) | 1984-09-19 | 1988-11-24 | Toshiba Kk | Heat pump system |
| US4686996A (en) | 1985-12-24 | 1987-08-18 | Paul Ulbrich | Electrode assembly for sensing heart activity |
| SE449053B (en) | 1986-01-16 | 1987-04-06 | Gambro Cardio Ab | Hjert CATHETER |
| US4704104A (en) | 1986-03-20 | 1987-11-03 | Christensen John F | Disposable tube for rectal injection of drugs |
| US4899741A (en) | 1987-01-14 | 1990-02-13 | Hgm Medical Laser Systems, Inc. | Laser heated probe and control system |
| US4725267A (en) | 1987-05-06 | 1988-02-16 | Vaillancourt Vincent L | Post-injection needle sheath |
| US4813425A (en) | 1987-08-26 | 1989-03-21 | American Home Products Corporation | Fetal electrode product |
| 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 |
| US4949718B1 (en) * | 1988-09-09 | 1998-11-10 | Gynelab Products | Intrauterine cauterizing apparatus |
| US5159925A (en) * | 1988-09-09 | 1992-11-03 | Gynelab, Inc. | Cauterizing apparatus and method for laparoscopic cholecystostomy, gallbladder ablation and treatment of benign prostate hypertrophy |
| JPH0295364A (en) | 1988-10-02 | 1990-04-06 | Yuichiro Takayama | Urine taking device |
| US4946440A (en) | 1988-10-05 | 1990-08-07 | Hall John E | Evertible membrane catheter and method of use |
| US4955377A (en) * | 1988-10-28 | 1990-09-11 | Lennox Charles D | Device and method for heating tissue in a patient's body |
| US5151100A (en) | 1988-10-28 | 1992-09-29 | Boston Scientific Corporation | Heating catheters |
| US5108390A (en) * | 1988-11-14 | 1992-04-28 | Frigitronics, Inc. | Flexible cryoprobe |
| GB2226497B (en) | 1988-12-01 | 1992-07-01 | Spembly Medical Ltd | Cryosurgical probe |
| DE8916283U1 (en) | 1989-01-30 | 1997-05-15 | Bard Inc C R | Quickly replaceable coronary catheter |
| US4911148A (en) | 1989-03-14 | 1990-03-27 | Intramed Laboratories, Inc. | Deflectable-end endoscope with detachable flexible shaft assembly |
| US4919112B1 (en) | 1989-04-07 | 1993-12-28 | Low-cost semi-disposable endoscope | |
| US4946460A (en) * | 1989-04-26 | 1990-08-07 | Cryo Instruments, Inc. | Apparatus for cryosurgery |
| JPH0316664U (en) * | 1989-06-30 | 1991-02-19 | ||
| CA2067110C (en) | 1989-09-08 | 2001-07-31 | John E. Abele | Physiologic low stress angioplasty |
| EP0613650A3 (en) | 1989-10-13 | 1995-01-18 | Machida Endoscope Co Ltd | Bending device. |
| US5254088A (en) | 1990-02-02 | 1993-10-19 | Ep Technologies, Inc. | Catheter steering mechanism |
| US5891088A (en) | 1990-02-02 | 1999-04-06 | Ep Technologies, Inc. | Catheter steering assembly providing asymmetric left and right curve configurations |
| EP0450181B1 (en) | 1990-03-30 | 1995-05-17 | Pacesetter AB | Device for positioning an electrode |
| US5015240A (en) | 1990-05-01 | 1991-05-14 | Ian Campbell Cree | Hypodermic needle shield |
| US5624392A (en) * | 1990-05-11 | 1997-04-29 | Saab; Mark A. | Heat transfer catheters and methods of making and using same |
| US5190540A (en) * | 1990-06-08 | 1993-03-02 | Cardiovascular & Interventional Research Consultants, Inc. | Thermal balloon angioplasty |
| US5217482A (en) | 1990-08-28 | 1993-06-08 | Scimed Life Systems, Inc. | Balloon catheter with distal guide wire lumen |
| EP0476807A1 (en) | 1990-09-17 | 1992-03-25 | C.R. Bard, Inc. | Core wire steerable catheters |
| ZA917281B (en) | 1990-09-26 | 1992-08-26 | Cryomedical Sciences Inc | Cryosurgical instrument and system and method of cryosurgery |
| US5114399A (en) | 1990-10-01 | 1992-05-19 | Intramed Laboratories | Surgical device |
| US5139496A (en) | 1990-12-20 | 1992-08-18 | Hed Aharon Z | Ultrasonic freeze ablation catheters and probes |
| DK32091D0 (en) | 1991-02-25 | 1991-02-25 | Mogens Thyge Corfitsen | Apparatus for feeding an object through a body channel |
| US5098428A (en) | 1991-03-14 | 1992-03-24 | Sandlin Felix M | Cryosurgical spraying apparatus |
| JP3091253B2 (en) * | 1991-04-25 | 2000-09-25 | オリンパス光学工業株式会社 | Thermal treatment equipment |
| WO1992020290A1 (en) * | 1991-05-17 | 1992-11-26 | Innerdyne Medical, Inc. | Method and device for thermal ablation |
| US5766151A (en) | 1991-07-16 | 1998-06-16 | Heartport, Inc. | Endovascular system for arresting the heart |
| US5584803A (en) | 1991-07-16 | 1996-12-17 | Heartport, Inc. | System for cardiac procedures |
| US5735290A (en) | 1993-02-22 | 1998-04-07 | Heartport, Inc. | Methods and systems for performing thoracoscopic coronary bypass and other procedures |
| US5879499A (en) | 1996-06-17 | 1999-03-09 | Heartport, Inc. | Method of manufacture of a multi-lumen catheter |
| US5795325A (en) | 1991-07-16 | 1998-08-18 | Heartport, Inc. | Methods and apparatus for anchoring an occluding member |
| US5452733A (en) | 1993-02-22 | 1995-09-26 | Stanford Surgical Technologies, Inc. | Methods for performing thoracoscopic coronary artery bypass |
| US5769812A (en) | 1991-07-16 | 1998-06-23 | Heartport, Inc. | System for cardiac procedures |
| US5906776A (en) * | 1991-10-18 | 1999-05-25 | Texas Instruments Incorporated | Method of degating molded parts |
| US5860971A (en) | 1991-11-05 | 1999-01-19 | Spembly Cryosurgery Limited | Thawing of cryosurgical apparatus |
| US5205298A (en) | 1991-11-26 | 1993-04-27 | Carroll Hurst | Method and apparatus for use in applying elastomeric coverings to body |
| US5170639A (en) | 1991-12-10 | 1992-12-15 | Chander Datta | Cascade refrigeration system |
| US5300099A (en) * | 1992-03-06 | 1994-04-05 | Urologix, Inc. | Gamma matched, helical dipole microwave antenna |
| SK279802B6 (en) | 1992-03-24 | 1999-04-13 | Jaroslav �Traus | Apparatus for executing cryogenic destruction of pathological tissue |
| WO1993020768A1 (en) | 1992-04-13 | 1993-10-28 | Ep Technologies, Inc. | Steerable microwave antenna systems for cardiac ablation |
| 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 |
| US5281215A (en) | 1992-04-16 | 1994-01-25 | Implemed, Inc. | Cryogenic catheter |
| JPH05293077A (en) | 1992-04-20 | 1993-11-09 | Olympus Optical Co Ltd | Intraluminal inserting apparatus |
| US5443470A (en) * | 1992-05-01 | 1995-08-22 | Vesta Medical, Inc. | Method and apparatus for endometrial ablation |
| US5275595A (en) | 1992-07-06 | 1994-01-04 | Dobak Iii John D | Cryosurgical instrument |
| US5342298A (en) | 1992-07-31 | 1994-08-30 | Advanced Cardiovascular Systems, Inc. | Automated fluid pressure control system |
| WO1994007446A1 (en) * | 1992-10-05 | 1994-04-14 | Boston Scientific Corporation | Device and method for heating tissue |
| US5569161A (en) | 1992-10-08 | 1996-10-29 | Wendell V. Ebling | Endoscope with sterile sleeve |
| US5314408A (en) | 1992-11-13 | 1994-05-24 | Cardiovascular Imaging Systems, Inc. | Expandable member for a catheter system |
| US5472017A (en) | 1992-11-17 | 1995-12-05 | Life Medical Technologies, Inc. | Deflectable catheter |
| US5549542A (en) | 1992-11-17 | 1996-08-27 | Life Medical Technologies, Inc. | Deflectable endoscope |
| CA2109980A1 (en) | 1992-12-01 | 1994-06-02 | Mir A. Imran | 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 |
| US5718725A (en) | 1992-12-03 | 1998-02-17 | Heartport, Inc. | Devices and methods for intracardiac procedures |
| US6325067B1 (en) | 1992-12-03 | 2001-12-04 | Wesley D. Sterman | Methods and systems for performing thoracoscopic coronary bypass and other procedures |
| US6283127B1 (en) | 1992-12-03 | 2001-09-04 | Wesley D. Sterman | Devices and methods for intracardiac procedures |
| US5814097A (en) | 1992-12-03 | 1998-09-29 | Heartport, Inc. | Devices and methods for intracardiac procedures |
| 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 |
| US5324286A (en) | 1993-01-21 | 1994-06-28 | Arthur A. Fowle, Inc. | Entrained cryogenic droplet transfer method and cryosurgical instrument |
| US5437673A (en) * | 1993-02-04 | 1995-08-01 | Cryomedical Sciences, Inc. | Closed circulation tissue warming apparatus and method of using the same in prostate surgery |
| US6161543A (en) | 1993-02-22 | 2000-12-19 | Epicor, Inc. | Methods of epicardial ablation for creating a lesion around the pulmonary veins |
| US5728151A (en) | 1993-02-22 | 1998-03-17 | Heartport, Inc. | Intercostal access devices for less-invasive cardiovascular surgery |
| US5327881A (en) | 1993-02-26 | 1994-07-12 | Beth Israel Hospital Association | Fiberoptic intubating stylet |
| US5364352A (en) | 1993-03-12 | 1994-11-15 | Heart Rhythm Technologies, Inc. | Catheter for electrophysiological procedures |
| US6233491B1 (en) | 1993-03-16 | 2001-05-15 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
| US5405346A (en) * | 1993-05-14 | 1995-04-11 | Fidus Medical Technology Corporation | Tunable microwave ablation catheter |
| KR960015616B1 (en) | 1993-05-27 | 1996-11-18 | 송경진 | Vein neddle set |
| US5715817A (en) | 1993-06-29 | 1998-02-10 | C.R. Bard, Inc. | Bidirectional steering catheter |
| CA2165829A1 (en) * | 1993-07-01 | 1995-01-19 | John E. Abele | Imaging, electrical potential sensing, and ablation catheters |
| US5431168A (en) | 1993-08-23 | 1995-07-11 | Cordis-Webster, Inc. | Steerable open-lumen catheter |
| US5673695A (en) | 1995-08-02 | 1997-10-07 | Ep Technologies, Inc. | Methods for locating and ablating accessory pathways in the heart |
| US5575810A (en) | 1993-10-15 | 1996-11-19 | Ep Technologies, Inc. | Composite structures and methods for ablating tissue to form complex lesion patterns in the treatment of cardiac conditions and the like |
| NL9301851A (en) | 1993-10-26 | 1995-05-16 | Cordis Europ | Cryo-ablation catheter. |
| IL107460A (en) | 1993-11-01 | 1999-06-20 | Israel State | Controlled cryogenic contact system |
| US5575766A (en) | 1993-11-03 | 1996-11-19 | Daig Corporation | Process for the nonsurgical mapping and treatment of atrial arrhythmia using catheters guided by shaped guiding introducers |
| US5409469A (en) | 1993-11-04 | 1995-04-25 | Medtronic, Inc. | Introducer system having kink resistant splittable sheath |
| GB2283678B (en) | 1993-11-09 | 1998-06-03 | Spembly Medical Ltd | Cryosurgical catheter probe |
| US5487385A (en) | 1993-12-03 | 1996-01-30 | Avitall; Boaz | Atrial mapping and ablation catheter system |
| US5466222A (en) | 1994-03-30 | 1995-11-14 | Scimed Life Systems, Inc. | Longitudinally collapsible and exchangeable catheter |
| US5472424A (en) | 1994-04-05 | 1995-12-05 | Merit Medical Systems, Inc. | Syringe with volume displacement apparatus |
| GB2289510A (en) | 1994-05-10 | 1995-11-22 | Spembly Medical Ltd | Connector |
| GB2289414B (en) | 1994-05-10 | 1998-05-13 | Spembly Medical Ltd | Cryosurgical instrument |
| US5672172A (en) * | 1994-06-23 | 1997-09-30 | Vros Corporation | Surgical instrument with ultrasound pulse generator |
| IL110176A (en) | 1994-06-30 | 1999-12-31 | Israel State | Multiprobe surgical cryogenic apparatus |
| US5452582A (en) | 1994-07-06 | 1995-09-26 | Apd Cryogenics, Inc. | Cryo-probe |
| US5687579A (en) | 1994-09-12 | 1997-11-18 | Vaynberg; Mikhail M. | Double circuited refrigeration system with chiller |
| US5885278A (en) | 1994-10-07 | 1999-03-23 | E.P. Technologies, Inc. | Structures for deploying movable electrode elements |
| SE9403433D0 (en) | 1994-10-10 | 1994-10-10 | Pharmacia Ab | Injection device |
| SE508792C2 (en) * | 1994-11-21 | 1998-11-09 | Wallsten Medical Sa | Balloon catheter for performing heat treatment in a body cavity or duct |
| 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 |
| WO1996034571A1 (en) * | 1995-05-04 | 1996-11-07 | Cosman Eric R | Cool-tip electrode thermosurgery system |
| AU6889896A (en) | 1995-09-08 | 1997-03-27 | Baker, Michiko | Syringe serving also as an ampule and syringe for collecting blood |
| US6151901A (en) | 1995-10-12 | 2000-11-28 | Cryogen, Inc. | Miniature mixed gas refrigeration system |
| US5758505C1 (en) | 1995-10-12 | 2001-10-30 | Cryogen Inc | Precooling system for joule-thomson probe |
| JPH11514269A (en) | 1995-10-13 | 1999-12-07 | トランスバスキュラー インコーポレイテッド | Methods and apparatus for bypassing arterial occlusion and / or performing other transvascular approaches |
| US5685878A (en) | 1995-11-13 | 1997-11-11 | C.R. Bard, Inc. | Snap fit distal assembly for an ablation catheter |
| US5733280A (en) | 1995-11-15 | 1998-03-31 | Avitall; Boaz | Cryogenic epicardial mapping and ablation |
| US5860953A (en) | 1995-11-21 | 1999-01-19 | Catheter Imaging Systems, Inc. | Steerable catheter having disposable module and sterilizable handle and method of connecting same |
| US5752385A (en) | 1995-11-29 | 1998-05-19 | Litton Systems, Inc. | Electronic controller for linear cryogenic coolers |
| US5769702A (en) | 1996-02-01 | 1998-06-23 | Sorenson Critical Care, Inc. | Variable positioning gaseous conduit orifice and method of use |
| US6190348B1 (en) | 1996-04-10 | 2001-02-20 | Harris A. Tiemann | Disposable applicator |
| US5762996A (en) | 1996-04-15 | 1998-06-09 | Lucas; Daniel R. | Silicone balloon catheter |
| TW359023B (en) * | 1996-04-20 | 1999-05-21 | Winbond Electronics Corp | Device for improvement of static discharge protection in ICs |
| US5733319A (en) | 1996-04-25 | 1998-03-31 | Urologix, Inc. | Liquid coolant supply system |
| GB2312856A (en) | 1996-05-09 | 1997-11-12 | Pall Corp | Filter with a slidable end cap for subterranean use |
| US5669870A (en) | 1996-06-13 | 1997-09-23 | Elist; James J. | Penile implant for improved appearance |
| US6059757A (en) | 1996-06-18 | 2000-05-09 | Cardeon | Single lumen catheter with controlled antegrade and retrograde flow |
| US5833671A (en) | 1996-06-17 | 1998-11-10 | Cardeon Corporation | Triple lumen catheter with controllable antegrade and retrograde fluid flow |
| US5827237A (en) | 1996-06-17 | 1998-10-27 | Cardeon Corporation | Dual lumen catheter with controlled antegrade and retrograde fluid flow |
| US6039730A (en) | 1996-06-24 | 2000-03-21 | Allegheny-Singer Research Institute | Method and apparatus for cryosurgery |
| US5755682A (en) | 1996-08-13 | 1998-05-26 | Heartstent Corporation | Method and apparatus for performing coronary artery bypass surgery |
| US5904147A (en) | 1996-08-16 | 1999-05-18 | University Of Massachusetts | Intravascular catheter and method of controlling hemorrhage during minimally invasive surgery |
| CA2186671C (en) | 1996-09-27 | 2000-08-01 | Eugene Trouchine | Penile stimulator device using turbulent water flow and method of use |
| US6221070B1 (en) | 1996-10-18 | 2001-04-24 | Irvine Biomedical, Inc. | Steerable ablation catheter system having disposable shaft |
| US6237605B1 (en) | 1996-10-22 | 2001-05-29 | Epicor, Inc. | Methods of epicardial ablation |
| US6719755B2 (en) | 1996-10-22 | 2004-04-13 | Epicor Medical, Inc. | Methods and devices for ablation |
| US6311692B1 (en) | 1996-10-22 | 2001-11-06 | Epicor, Inc. | Apparatus and method for diagnosis and therapy of electrophysiological disease |
| US5827235A (en) | 1996-12-23 | 1998-10-27 | Beaver; George M. | Method and apparatus used to apply topical medication |
| 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 |
| US6235019B1 (en) | 1997-02-27 | 2001-05-22 | Cryocath Technologies, Inc. | Cryosurgical catheter |
| WO2000032126A1 (en) | 1997-02-27 | 2000-06-08 | Cryocath Technologies Inc. | Cryosurgical catheter |
| US5899898A (en) | 1997-02-27 | 1999-05-04 | Cryocath Technologies Inc. | Cryosurgical linear ablation |
| 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 |
| US6012457A (en) | 1997-07-08 | 2000-01-11 | The Regents Of The University Of California | Device and method for forming a circumferential conduction block in a pulmonary vein |
| US6024740A (en) | 1997-07-08 | 2000-02-15 | The Regents Of The University Of California | Circumferential ablation device assembly |
| US5885244A (en) | 1997-05-14 | 1999-03-23 | Cordis Corporation & University Of Miami | Synchronous, pulsatile angioplasty system |
| 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 |
| US5938660A (en) | 1997-06-27 | 1999-08-17 | Daig Corporation | Process and device for the treatment of atrial arrhythmia |
| US6164283A (en) | 1997-07-08 | 2000-12-26 | The Regents Of The University Of California | Device and method for forming a circumferential conduction block in a pulmonary vein |
| US6117101A (en) | 1997-07-08 | 2000-09-12 | The Regents Of The University Of California | Circumferential ablation device assembly |
| US6514249B1 (en) | 1997-07-08 | 2003-02-04 | Atrionix, Inc. | Positioning system and method for orienting an ablation element within a pulmonary vein ostium |
| US6245064B1 (en) | 1997-07-08 | 2001-06-12 | Atrionix, Inc. | Circumferential ablation device assembly |
| US6652515B1 (en) | 1997-07-08 | 2003-11-25 | Atrionix, Inc. | Tissue ablation device assembly and method for electrically isolating a pulmonary vein ostium from an atrial wall |
| US5902299A (en) | 1997-07-29 | 1999-05-11 | Jayaraman; Swaminathan | Cryotherapy method for reducing tissue injury after balloon angioplasty or stent implantation |
| JPH1199156A (en) | 1997-07-29 | 1999-04-13 | Olympus Optical Co Ltd | Access device for surgical treatment |
| WO1999007354A2 (en) | 1997-08-08 | 1999-02-18 | Duke University | Compositions, apparatus and methods for facilitating surgical procedures |
| US6592552B1 (en) | 1997-09-19 | 2003-07-15 | Cecil C. Schmidt | Direct pericardial access device and method |
| US5972013A (en) | 1997-09-19 | 1999-10-26 | Comedicus Incorporated | Direct pericardial access device with deflecting mechanism and method |
| JPH11221229A (en) | 1997-09-24 | 1999-08-17 | Eclipse Surgical Technol Inc | Catheter |
| US6554794B1 (en) | 1997-09-24 | 2003-04-29 | Richard L. Mueller | Non-deforming deflectable multi-lumen catheter |
| ATE386562T1 (en) | 1997-11-07 | 2008-03-15 | Acist Medical Sys Inc | ANGIOGRAPHY SYRINGE WITH MULTIPLE REDUNDANT PROCESSORS |
| US6120476A (en) | 1997-12-01 | 2000-09-19 | Cordis Webster, Inc. | Irrigated tip catheter |
| US5971979A (en) | 1997-12-02 | 1999-10-26 | Odyssey Technologies, Inc. | Method for cryogenic inhibition of hyperplasia |
| US6231595B1 (en) | 1998-03-31 | 2001-05-15 | Innercool Therapies, Inc. | Circulating fluid hypothermia method and apparatus |
| US5916212A (en) | 1998-01-23 | 1999-06-29 | Cryomedical Sciences, Inc. | Hand held cyrosurgical probe system |
| US6843800B1 (en) | 1998-01-23 | 2005-01-18 | Innercool Therapies, Inc. | Patient temperature regulation method and apparatus |
| US6051019A (en) | 1998-01-23 | 2000-04-18 | Del Mar Medical Technologies, Inc. | Selective organ hypothermia method and apparatus |
| US6238428B1 (en) | 1998-01-23 | 2001-05-29 | Innercool Therapies, Inc. | Selective organ cooling apparatus and method employing turbulence-inducing element with curved terminations |
| US6096068A (en) | 1998-01-23 | 2000-08-01 | Innercool Therapies, Inc. | Selective organ cooling catheter and method of using the same |
| US6245095B1 (en) | 1998-03-24 | 2001-06-12 | Innercool Therapies, Inc. | Method and apparatus for location and temperature specific drug action such as thrombolysis |
| US6251130B1 (en) | 1998-03-24 | 2001-06-26 | Innercool Therapies, Inc. | Device for applications of selective organ cooling |
| US20010029394A1 (en) | 1998-03-24 | 2001-10-11 | Dobak John D. | Selective organ cooling catheter with guidewire apparatus and temperature-monitoring device |
| US6312452B1 (en) | 1998-01-23 | 2001-11-06 | Innercool Therapies, Inc. | Selective organ cooling catheter with guidewire apparatus and temperature-monitoring device |
| US6254626B1 (en) | 1998-03-24 | 2001-07-03 | Innercool Therapies, Inc. | Articulation device for selective organ cooling apparatus |
| US6258087B1 (en) * | 1998-02-19 | 2001-07-10 | Curon Medical, Inc. | Expandable electrode assemblies for forming lesions to treat dysfunction in sphincters and adjoining tissue regions |
| US6179827B1 (en) | 1998-03-16 | 2001-01-30 | Chase Medical | Catheter having integral expandable/collapsible lumen |
| US5964778A (en) | 1998-03-17 | 1999-10-12 | Medtronic, Inc. | Balloon attachment at catheter tip |
| US6001117A (en) | 1998-03-19 | 1999-12-14 | Indigo Medical, Inc. | Bellows medical construct and apparatus and method for using same |
| US6223491B1 (en) * | 1998-03-23 | 2001-05-01 | Ted C. Dial, Jr. | Block system |
| US6576002B2 (en) | 1998-03-24 | 2003-06-10 | Innercool Therapies, Inc. | Isolated selective organ cooling method and apparatus |
| US6551349B2 (en) | 1998-03-24 | 2003-04-22 | Innercool Therapies, Inc. | Selective organ cooling apparatus |
| US6224624B1 (en) | 1998-03-24 | 2001-05-01 | Innercool Therapies, Inc. | Selective organ cooling apparatus and method |
| JP2002507716A (en) * | 1998-03-25 | 2002-03-12 | オプション セイフティ リミテッド ライアビリティ カンパニー | Non-lethal fluid launcher |
| US6685732B2 (en) | 1998-03-31 | 2004-02-03 | Innercool Therapies, Inc. | Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing microporous balloon |
| US6602276B2 (en) | 1998-03-31 | 2003-08-05 | Innercool Therapies, Inc. | Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation |
| US6905494B2 (en) | 1998-03-31 | 2005-06-14 | Innercool Therapies, Inc. | Method and device for performing cooling- or cryo-therapies for, e.g., angioplasty with reduced restenosis or pulmonary vein cell necrosis to inhibit atrial fibrillation employing tissue protection |
| US6106518A (en) | 1998-04-09 | 2000-08-22 | Cryocath Technologies, Inc. | Variable geometry tip for a cryosurgical ablation device |
| US6645234B2 (en) | 1998-04-21 | 2003-11-11 | Alsius Corporation | Cardiovascular guiding catheter with heat exchange properties and methods of use |
| US6740104B1 (en) | 1998-05-15 | 2004-05-25 | Advanced Cardiovascular Systems, Inc. | Enhanced catheter with alignment means |
| US6231518B1 (en) | 1998-05-26 | 2001-05-15 | Comedicus Incorporated | Intrapericardial electrophysiological procedures |
| US6241722B1 (en) | 1998-06-17 | 2001-06-05 | Cryogen, Inc. | Cryogenic device, system and method of using same |
| US6036697A (en) | 1998-07-09 | 2000-03-14 | Scimed Life Systems, Inc. | Balloon catheter with balloon inflation at distal end of balloon |
| US6319248B1 (en) | 1998-07-29 | 2001-11-20 | Cryocath Technologies, Inc. | Spray catheter |
| US6168586B1 (en) | 1998-08-07 | 2001-01-02 | Embol-X, Inc. | Inflatable cannula and method of using same |
| IL126111A0 (en) | 1998-09-07 | 1999-05-09 | Medivice Systems Ltd | Tampon applicator |
| WO2000029060A2 (en) | 1998-11-19 | 2000-05-25 | Percusurge, Inc. | Low volume syringe and method for inflating surgical balloons |
| US6575933B1 (en) | 1998-11-30 | 2003-06-10 | Cryocath Technologies Inc. | Mechanical support for an expandable membrane |
| US6162171A (en) | 1998-12-07 | 2000-12-19 | Wan Sing Ng | Robotic endoscope and an autonomous pipe robot for performing endoscopic procedures |
| US6197045B1 (en) | 1999-01-04 | 2001-03-06 | Medivance Incorporated | Cooling/heating pad and system |
| CA2547953C (en) | 1999-01-25 | 2010-11-09 | Cryocath Technologies Inc. | Cryogenic catheter system |
| US6592577B2 (en) | 1999-01-25 | 2003-07-15 | Cryocath Technologies Inc. | Cooling 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 |
| US6648879B2 (en) * | 1999-02-24 | 2003-11-18 | Cryovascular Systems, Inc. | Safety cryotherapy catheter |
| US6514245B1 (en) | 1999-03-15 | 2003-02-04 | Cryovascular Systems, Inc. | Safety cryotherapy catheter |
| US6432102B2 (en) | 1999-03-15 | 2002-08-13 | Cryovascular Systems, Inc. | Cryosurgical fluid supply |
| US6019783A (en) | 1999-03-02 | 2000-02-01 | Alsius Corporation | Cooling system for therapeutic catheter |
| US6248096B1 (en) | 1999-03-04 | 2001-06-19 | Paul Dwork | Male urinary incontinence device having expandable flutes |
| KR100322135B1 (en) * | 1999-03-11 | 2002-02-04 | 윤종용 | Optical Fiber in which residual mechanical stress is maximized and method for fabricating fiber gratings using the same |
| US6702811B2 (en) | 1999-04-05 | 2004-03-09 | Medtronic, Inc. | Ablation catheter assembly with radially decreasing helix and method of use |
| US6325797B1 (en) | 1999-04-05 | 2001-12-04 | Medtronic, Inc. | Ablation catheter and method for isolating a pulmonary vein |
| US6248117B1 (en) | 1999-04-16 | 2001-06-19 | Vital Access Corp | Anastomosis apparatus for use in intraluminally directed vascular anastomosis |
| US6440126B1 (en) | 1999-04-21 | 2002-08-27 | Cryocath Technologies | Cryoblation catheter handle |
| US20030028182A1 (en) * | 1999-04-21 | 2003-02-06 | Cryocath Technologies Inc. | Cryoablation catheter handle |
| US6270476B1 (en) | 1999-04-23 | 2001-08-07 | Cryocath Technologies, Inc. | Catheter |
| US6146338A (en) | 1999-04-23 | 2000-11-14 | Medtronic, Inc. | Apparatus for deflecting a catheter or lead |
| US6287302B1 (en) | 1999-06-14 | 2001-09-11 | Fidus Medical Technology Corporation | End-firing microwave ablation instrument with horn reflection device |
| US6471694B1 (en) | 2000-08-09 | 2002-10-29 | Cryogen, Inc. | Control system for cryosurgery |
| US6270493B1 (en) | 1999-07-19 | 2001-08-07 | Cryocath Technologies, Inc. | Cryoablation structure |
| EP1207788A4 (en) | 1999-07-19 | 2009-12-09 | St Jude Medical Atrial Fibrill | Apparatus and method for ablating tissue |
| US6569082B1 (en) | 1999-08-10 | 2003-05-27 | Origin Medsystems, Inc. | Apparatus and methods for cardiac restraint |
| US6179810B1 (en) | 1999-08-17 | 2001-01-30 | Advanced Cardiovascular Systems, Inc. | Catheter with a flexible and pushable shaft |
| US6264679B1 (en) | 1999-08-20 | 2001-07-24 | Radiant Medical, Inc. | Heat exchange catheter with discrete heat exchange elements |
| US6575966B2 (en) | 1999-08-23 | 2003-06-10 | Cryocath Technologies Inc. | Endovascular cryotreatment catheter |
| US6283959B1 (en) * | 1999-08-23 | 2001-09-04 | Cyrocath Technologies, Inc. | Endovascular cryotreatment catheter |
| US6283294B1 (en) | 1999-09-01 | 2001-09-04 | Biogaia Biologics Ab | Enclosed living cell dispensing tube |
| US6237604B1 (en) | 1999-09-07 | 2001-05-29 | Scimed Life Systems, Inc. | Systems and methods for preventing automatic identification of re-used single use devices |
| US6387092B1 (en) | 1999-09-07 | 2002-05-14 | Scimed Life Systems, Inc. | Systems and methods to identify and disable re-used single use devices based on time elapsed from first therapeutic use |
| US6270482B1 (en) | 1999-09-09 | 2001-08-07 | Tri-Med International, Llc | Multiple-dose syringe |
| US6315761B1 (en) | 1999-09-29 | 2001-11-13 | Alexis Shcherbina | Injection device with bellowed reservoir |
| US6270488B1 (en) | 2000-01-24 | 2001-08-07 | Allegiance Corporation | Large volume medical fluid vacuum collection canister |
| US6551274B2 (en) | 2000-02-29 | 2003-04-22 | Biosense Webster, Inc. | Cryoablation catheter with an expandable cooling chamber |
| US6579243B2 (en) | 2000-03-02 | 2003-06-17 | Scimed Life Systems, Inc. | Catheter with thermal sensor for detection of vulnerable plaque |
| US6546935B2 (en) | 2000-04-27 | 2003-04-15 | Atricure, Inc. | Method for transmural ablation |
| JP2001321368A (en) | 2000-05-16 | 2001-11-20 | Fuji Photo Film Co Ltd | Plasma taking tool |
| CA2413529C (en) | 2000-06-23 | 2008-12-02 | Cryocath Technologies, Inc. | Cryotreatment device and method |
| US6641511B2 (en) | 2000-08-31 | 2003-11-04 | Hurco Companies, Inc. | Movable arm activated tool changer for machine tool system |
| US6530914B1 (en) | 2000-10-24 | 2003-03-11 | Scimed Life Systems, Inc. | Deflectable tip guide in guide system |
| US20030149368A1 (en) * | 2000-10-24 | 2003-08-07 | Hennemann Willard W. | Method and apparatus for locating and detecting vascular plaque via impedence and conductivity measurements, and for cryogenically passivating vascular plaque and inhibiting vascular plaque progression and rupture |
| US6659981B2 (en) | 2000-12-08 | 2003-12-09 | Medtronic, Inc. | Medical device delivery catheter with distal locator |
| GB2371754B (en) | 2001-02-02 | 2005-09-21 | Biocompatibles Ltd | Balloon catheter inflation |
| AU2002240386A1 (en) * | 2001-02-14 | 2002-08-28 | Acist Medical Systems, Inc. | Catheter fluid control system |
| WO2002064194A1 (en) | 2001-02-14 | 2002-08-22 | Acist Medical Systems, Inc. | Fluid injector system |
| US6666858B2 (en) | 2001-04-12 | 2003-12-23 | Scimed Life Systems, Inc. | Cryo balloon for atrial ablation |
| US6648883B2 (en) | 2001-04-26 | 2003-11-18 | Medtronic, Inc. | Ablation system and method of use |
| US6786900B2 (en) | 2001-08-13 | 2004-09-07 | Cryovascular Systems, Inc. | Cryotherapy methods for treating vessel dissections and side branch occlusion |
| US6776784B2 (en) | 2001-09-06 | 2004-08-17 | Core Medical, Inc. | Clip apparatus for closing septal defects and methods of use |
| US6695769B2 (en) | 2001-09-25 | 2004-02-24 | The Foundry, Inc. | Passive ventricular support devices and methods of using them |
| AU2002337596A1 (en) * | 2001-09-27 | 2003-04-07 | Galil Medical Ltd. | Cryoplasty apparatus and method |
| US6579287B2 (en) * | 2001-10-09 | 2003-06-17 | Cryocath Technologies Inc. | Cryosurgical ablation device having sequential injection and method therefor |
| US6989009B2 (en) | 2002-04-19 | 2006-01-24 | Scimed Life Systems, Inc. | Cryo balloon |
| US6881213B2 (en) * | 2002-06-28 | 2005-04-19 | Ethicon, Inc. | Device and method to expand treatment array |
| US20040024392A1 (en) | 2002-08-05 | 2004-02-05 | Lewis James D. | Apparatus and method for cryosurgery |
| US20040034344A1 (en) | 2002-08-16 | 2004-02-19 | Eric Ryba | Tip pressure monitoring for cryoablation catheters |
| IL151486A0 (en) | 2002-08-26 | 2003-04-10 | Levin Alexander | Cryosurgical instrument and its accessory system |
| US6893433B2 (en) * | 2002-12-11 | 2005-05-17 | Cryocor, Inc. | System and method for performing a single step cryoablation |
| US6796979B2 (en) * | 2002-12-11 | 2004-09-28 | Cryocor, Inc. | Coaxial catheter system for performing a single step cryoablation |
| US7273479B2 (en) | 2003-01-15 | 2007-09-25 | Cryodynamics, Llc | Methods and systems for cryogenic cooling |
| US7060062B2 (en) | 2003-06-04 | 2006-06-13 | Cryo Vascular Systems, Inc. | Controllable pressure cryogenic balloon treatment system and method |
| US7727228B2 (en) | 2004-03-23 | 2010-06-01 | Medtronic Cryocath Lp | Method and apparatus for inflating and deflating balloon catheters |
| US8491636B2 (en) | 2004-03-23 | 2013-07-23 | Medtronic Cryopath LP | Method and apparatus for inflating and deflating balloon catheters |
| US7310955B2 (en) | 2004-09-03 | 2007-12-25 | Nitrocision Llc | System and method for delivering cryogenic fluid |
| US7604631B2 (en) * | 2004-12-15 | 2009-10-20 | Boston Scientific Scimed, Inc. | Efficient controlled cryogenic fluid delivery into a balloon catheter and other treatment devices |
| US7674256B2 (en) * | 2005-03-17 | 2010-03-09 | Boston Scientific Scimed, Inc. | Treating internal body tissue |
| US20080125764A1 (en) | 2006-11-17 | 2008-05-29 | Vancelette David W | Cryoprobe thermal control for a closed-loop cryosurgical system |
| JP5293077B2 (en) | 2007-10-30 | 2013-09-18 | 株式会社デンソー | Heat exchanger |
-
2004
- 2004-03-23 US US10/806,995 patent/US7727228B2/en not_active Expired - Lifetime
-
2005
- 2005-03-23 CA CA2652097A patent/CA2652097C/en not_active Expired - Fee Related
- 2005-03-23 WO PCT/CA2005/000437 patent/WO2005089853A1/en active Application Filing
- 2005-03-23 CA CA2555441A patent/CA2555441C/en not_active Expired - Fee Related
- 2005-03-23 CA CA2652112A patent/CA2652112C/en not_active Expired - Fee Related
- 2005-03-23 EP EP08010700.6A patent/EP1980287B1/en active Active
- 2005-03-23 EP EP05714668.0A patent/EP1735041B1/en active Active
- 2005-12-13 US US11/301,768 patent/US8545491B2/en active Active
-
2007
- 2007-09-24 US US11/767,774 patent/US20080009925A1/en not_active Abandoned
- 2007-10-18 US US11/839,785 patent/US8382747B2/en active Active
-
2013
- 2013-01-25 US US13/749,795 patent/US8900222B2/en not_active Expired - Lifetime
-
2014
- 2014-10-23 US US14/522,045 patent/US9808301B2/en active Active
-
2017
- 2017-10-16 US US15/784,853 patent/US11357563B2/en active Active
Also Published As
| Publication number | Publication date |
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| US20050215989A1 (en) | 2005-09-29 |
| CA2652112C (en) | 2013-07-16 |
| US20080009925A1 (en) | 2008-01-10 |
| US20180036057A1 (en) | 2018-02-08 |
| EP1980287B1 (en) | 2021-01-20 |
| EP1735041A1 (en) | 2006-12-27 |
| US20060122589A1 (en) | 2006-06-08 |
| WO2005089853B1 (en) | 2005-11-17 |
| US8900222B2 (en) | 2014-12-02 |
| CA2555441A1 (en) | 2005-09-29 |
| US9808301B2 (en) | 2017-11-07 |
| US20130172866A1 (en) | 2013-07-04 |
| EP1735041A4 (en) | 2008-04-09 |
| US20080039791A1 (en) | 2008-02-14 |
| US8382747B2 (en) | 2013-02-26 |
| US20150045781A1 (en) | 2015-02-12 |
| US8545491B2 (en) | 2013-10-01 |
| CA2652112A1 (en) | 2005-09-29 |
| WO2005089853A1 (en) | 2005-09-29 |
| US7727228B2 (en) | 2010-06-01 |
| EP1735041B1 (en) | 2014-01-22 |
| CA2652097A1 (en) | 2005-09-29 |
| US11357563B2 (en) | 2022-06-14 |
| CA2652097C (en) | 2013-12-24 |
| EP1980287A3 (en) | 2008-10-29 |
| EP1980287A2 (en) | 2008-10-15 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKLA | Lapsed |
Effective date: 20200831 |