US20100114082A1

Movatterモバイル変換

Info

Publication number: US20100114082A1
Application number: US12/573,944
Authority: US
Inventors: Virender K. Sharma
Original assignee: Individual
Current assignee: Santa Anna Tech LLC
Priority date: 2008-10-06
Filing date: 2009-10-06
Publication date: 2010-05-06
Also published as: CN104739502A; US20150119869A1; US12310650B2; US9700365B2; EP2341859A1; EP2341859B1; US20100114083A1; WO2010042461A1; US20100094270A1; CN102238920B; US20160256214A9; US20210346088A1; CN102238920A; EP3175805A1; EP2341859A4; US20170231692A1; US11020175B2; CN104739502B

Abstract

The present invention is directed toward a device that performs ablation of tissue. The device has a catheter with a shaft through which an ablative agent can travel, a first positioning element attached to the catheter shaft at a first position and a second positioning element attached to the catheter shaft at a second position. The shaft also has ports through which the ablative agent can be released.

Description

CROSS-REFERENCE

The present invention relies on U.S. Provisional Application No. 61/102,885, filed on Oct. 6, 2008, for priority and is hereby incorporated herein by reference.

FIELD OF THE INVENTION

The present invention relates to medical apparatus and procedures. More particularly, the present invention relates to a device for ablation of tissue in a hollow organ comprising a centering or positioning attachment in order to position the device at a consistent distance from the tissue to be ablated.

BACKGROUND OF THE INVENTION

Colon polyps affect almost 25% of the population over the age of 50. While most polyps are detected on colonoscopy and easily removed using a snare, flat sessile polyps are hard to remove using the snare technique and carry a high risk of complications, such as bleeding and perforation. Recently, with improvement in imaging techniques, more flat polyps are being detected. Endoscopically unresectable polyps require surgical removal. Most colon cancer arises from colon polyps and, safe and complete resection of these polyps is imperative for the prevention of colon cancer.

Barrett esophagus is a precancerous condition effecting 10-14% of US population with gastro esophageal reflux disease (GERD) and is the proven precursor lesion of esophageal adenocarcinoma, the fastest rising cancer in the developed nations. The incidence of the cancer has risen over 6 fold in the last 2 decades and mortality has risen by 7 fold. The 5-year mortality from esophageal cancer is 85%. Ablation of Barrett epithelium has shown to prevent its progression to esophageal cancer.

Dysfunctional uterine bleeding (DUB), or menorrhagia, affects 30% of women in reproductive age. These symptoms have considerable impact on a woman's health and quality of life. The condition is typically treated with endometrial ablation or a hysterectomy. The rates of surgical intervention in these women are high. Almost 30% of women in US will undergo hysterectomy by theage 60, with menorrhagia or DUB being the cause for surgery in 50-70% of these women. Endometrial ablation techniques have been FDA approved for women with abnormal uterine bleeding and with intramural fibroids less than 2 cm. The presence of submucosal uterine fibroids and a large uterus size have been shown to decrease the efficacy of standard endometrial ablation. Of the five FDA approved global ablation devices (namely, Thermachoice, hydrothermal ablation, Novasure, Her Option, and microwave ablation) only microwave ablation (MEA) has been approved for use where the submucosal fibroids are less than 3 cm and are not occluding the endometrial cavity and, additionally, for large uteri up to 14 cm.

The known ablation treatments for Barrett esophagus include laser treatment (Ertan et al, Am. J. Gastro., 90:2201-2203 [1995]), ultrasonic ablation (Bremner et al, Gastro. Endo., 43:6 [1996]), photodynamic therapy (PDT) using photo-sensitizer drugs (Overholt et al, Semin. Surq. Oncol., 1:372-376 (1995), multipolar electrocoagulation such as by use of a bicap probe (Sampliner et al,), Argon Plasma Coagulation (APC;), Radiofrequency ablation (Sharma et al. Gastrointest Endosc) and cryoablation (Johnston et al. Gastrointest Endosc). The treatments are delivered with the aid of an endoscope and devices passed through the channel of endoscope or alongside the endoscope.

Conventional techniques have inherent limitations, however, and have not found widespread clinical applications. First, most of the hand held ablation devices (Bicap probe, APC, cryoablation) are point and shoot devices that create small foci of ablation. This ablation mechanism is operator dependent, cumbersome and time consuming. Second, because the target tissue is moving due to patient movement, respiration movement, normal peristalsis and vascular pulsations, the depth of ablation of the target tissue is inconsistent and results in a non-uniform ablation. Superficial ablation results in incomplete ablation with residual neoplastic tissue left behind. Deeper ablation results in complications such as bleeding, stricture formation and perforation. All of these limitations and complications have been reported with conventional devices.

For example, radiofrequency ablation uses a rigid bipolar balloon based electrode and radiofrequency thermal energy. The thermal energy is delivered by direct contact of the electrode with the diseased Barrett epithelium allowing for a relatively uniform, large area ablation. However, the rigid electrode does not accommodate for variations in esophageal size and is ineffective in ablating tortuous esophagus, proximal esophageal lesions as an esophagus narrows towards the top, and esophagus at the gastroesophageal junction due to changes in the esophagus diameter. Nodular disease in Barrett esophagus also cannot be treated using the rigid bipolar RF electrode. Due to its size and rigidity, the electrode cannot be passed through the scope. In addition sticking of sloughed tissue to the electrode impedes with delivery of radiofrequency energy resulting in incomplete ablation. The electrode size is limited to 3 cm, thus requiring repeat applications to treat larger lengths of Barrett esophagus.

Photodynamic therapy (PDT) is a two part procedure that involves injecting a photo-sensitizer that is absorbed and retained by the neoplastic and pre-neoplastic tissue. The tissue is then exposed to a selected wavelength of light which activates the photo-sensitizer and results in tissue destruction. PDT is associated with complications such as stricture formation and photo-sensitivity which has limited its use to the most-advanced stages of the disease. In addition, patchy uptake of the photosensitizer results in incomplete ablation and residual neoplastic tissue. Cryoablation of the esophageal tissues via direct contact with a liquid nitrogen has been studied in both animal models and humans (Rodgers et al, Cryobiology, 22:86-92 (1985); Rodgers et al, Ann. Thorac. Surq. 55:52-7 [1983]) and has been used to treat Barrett esophagus and (Johnston et al. Gastrointest Endosc) early esophageal cancer (Grana et al, Int. Surg., 66:295 [1981]). A spray catheter that directly sprays liquid N₂or CO₂(cryoablation) or argon (APC) to ablate Barrett tissue in the esophagus has been described. These techniques suffer the shortcoming of the traditional hand-held devices. Treatment using this probe is cumbersome and requires operator control under direct endoscopic visualization. Continuous movement in the esophagus due to respiration or cardiac or aortic pulsations or movement causes an uneven distribution of the ablative agent and results in non-uniform and/or incomplete ablation. Close or direct contact of the catheter to the surface epithelium may cause deeper tissue injury, resulting in perforation, bleeding or stricture formation. Too distant a placement of the catheter due to esophageal movement will result in incomplete Barrett ablation, requiring multiple treatment sessions or buried lesions with a continued risk of esophageal cancer. Expansion of cryogenic gas in the esophagus results in uncontrolled retching which may result in esophageal tear or perforation requiring continued suctioning of cryogen.

Colon polyps are usually resected using snare resection with or without the use of monopolar cautery. Flat polyps or residual polyps after snare resection have been treated with argon plasma coagulation or laser treatment. Both these treatments, have the previously mentioned limitations. Hence, most large flat polyps undergo surgical resection due to high risk of bleeding, perforation and residual disease using traditional endoscopic resection or ablation techniques.

Most of the conventional balloon catheters traditionally used for tissue ablation either heat or cool the balloon itself or a heating element such as a radio frequency (RF) coils mounted on the balloon. This requires direct contact of the balloon catheter with the ablated surface. When the balloon catheter is deflated, the epithelium sticks to the catheter and sloughs off, thereby causing bleeding. Blood can interfere with delivery of energy i.e. energy sink. In addition reapplication of energy will result in deeper bur in the area where superficial lining has sloughed. Further, balloon catheters cannot be employed for treatment in non cylindrical organs, like the uterus or sinuses, and also do not provide non-circumferential or focal ablation in a hollow organ. Additionally, if used with cryogens as ablative agents, which expand exponentially upon being heated, balloon catheters may result in a closed cavity and trap the escape of cryogen, resulting in complications such as perforations and tears.

Accordingly, there is a need in the art for an improved method and system for delivering ablative agents to a tissue surface, for providing a consistent, controlled, and uniform ablation of the target tissue, and for minimizing the adverse side effects of introducing ablative agents into a patient.

SUMMARY OF THE INVENTION

The present invention is directed toward a device to perform ablation of endometrial tissue, comprising a catheter having a shaft through which an ablative agent can travel, a first positioning element attached to said catheter shaft at a first position, wherein said first positioning element is configured to center said catheter in a center of a cervix, and a second positioning element attached to said catheter shaft at a second position, wherein the shaft comprises a plurality of ports through which said ablative agent can be released out of said shaft and wherein said ports are located between said first position and second position.

Optionally, the first positioning element is conical. The first positioning element comprises an insulated membrane which can be configured to prevent an escape of thermal energy through the cervix. The second positioning element is disc shaped. The second positioning element has a dimension which can be used to determine a uterine cavity size. The second positioning element has a dimension which can be used to calculate an amount of thermal energy needed to ablate the endometrial tissue. The device also includes at least one temperature sensor, which can be used to control delivery of the ablative agent, such as steam.

Optionally, the second positioning element is separated from endometrial tissue to be ablated by a distance of greater than 0.1 mm. The first positioning element is a covered wire mesh. The first positioning element is comprises a circular body with a diameter between 0.1 mm and 10 cm. The second positioning element is oval and wherein said oval has a long axis between 0.1 mm and 10 cm and a short axis between 0.1 mm and 5 cm.

In another embodiment, the present invention is directed toward a device to perform ablation of endometrial tissue, comprising a catheter having a hollow shaft through which steam can be delivered, a first positioning element attached to said catheter shaft at a first position, wherein said first positioning element is conical and configured to center said catheter in a center of a cervix, a second positioning element attached to said catheter shaft at a second position, wherein the second positioning element is disc shaped, a plurality of ports integrally formed in said catheter shaft, wherein steam can be released out of said ports and directed toward endometrial tissue and wherein said ports are located between said first position and second position; and at least one temperature sensor.

Optionally, the second positioning element has a dimension, which can be used to determine a uterine cavity size. The second positioning element has a dimension, which can be used to calculate an amount of thermal energy needed to ablate the endometrial tissue. The temperature sensors are used to control delivery of said ablative agent. The first positioning element comprises wire mesh. The second positioning element has a disc shape that is oval and wherein said oval has a long axis between 0.1 mm and 10 cm and a short axis between 0.1 mm and 5 cm.

A device to perform ablation of tissue in a hollow organ, comprising a catheter having a shaft through which an ablative agent can travel; a first positioning element attached to said catheter shaft at a first position, wherein said first positioning element is configured to position said catheter at a predefined distance from the tissue to be ablated; and wherein the shaft comprises one or more port through which said ablative agent can be released out of said shaft.

In another embodiment, the present invention is directed to a device to perform ablation of tissue in a hollow organ, comprising a catheter having a hollow shaft through which steam can be delivered; a first positioning element attached to said catheter shaft at a first position, wherein said first positioning element is configured to position said catheter at a predefined distance from the surface of the hollow organ; a second positioning element attached to said catheter shaft at a second position, wherein the second positioning element is shaped to position said catheter at a predefined distance from the surface of the hollow organ; a plurality of ports integrally formed in said catheter shaft, wherein steam can be released out of said ports and directed toward tissue to be ablated and wherein said ports are located between said first position and second position; and at least one temperature sensor.

Optionally, the first positioning element has a predefined dimension and wherein said dimension is used to determine the size of the hollow organ. The second positioning element has a predefined dimension and wherein said dimension is used to calculate an amount of thermal energy needed to ablate the tissue. The temperature sensor is used to control delivery of said ablative agent. The first positioning element comprises wire mesh. The second positioning element has a disc shape that is oval and wherein said oval has a long axis between 0.01 mm and 10 cm and a short axis between 0.01 mm and 9 cm.

In another embodiment, the present invention is directed to a device to perform ablation of the gastrointestinal tissue, comprising a catheter having a shaft through which an ablative agent can travel; a first positioning element attached to said catheter shaft at a first position, wherein said first positioning element is configured to position the catheter at a fixed distance from the gastrointestinal tissue to be ablated, and wherein said first positioning element is separated from an ablation region by a distance of between 0 mm and 5 cm, and an input port at a second position and in fluid communication with said catheter shaft in order to receive said ablative agent wherein the shaft comprises one or more ports through which said ablative agent can be released out of said shaft.

Optionally, the first positioning element is at least one of an inflatable balloon, wire mesh disc or cone. By introducing said ablative agent into said ablation region, the device creates an gastrointestinal pressure equal to or less than 5 atm. The ablative agent has a temperature between −100 degrees Celsius and 200 degrees Celsius. The catheter further comprises a temperature sensor. The catheter further comprises a pressure sensor. The first positioning element is configured to abut a gastroesophageal junction when placed in a gastric cardia. The ports are located between said first position and second position. The diameter of the positioning element is between 0.01 mm and 100 mm. The ablative agent is steam. The first positioning element comprises a circular body with a diameter between 0.01 mm and 10 cm.

In another embodiment, the present invention is directed toward a device to perform ablation of esophageal tissue, comprising a catheter having a hollow shaft through which steam can be transported; a first positioning element attached to said catheter shaft at a first position, wherein said first positioning element is configured to abut a gastroesophageal junction when placed in a gastric cardia; and an input port at a second position and in fluid communication with said catheter shaft in order to receive said steam wherein the shaft comprises a plurality of ports through which said steam can be released out of said shaft and wherein said ports are located between said first position and second position. The device further comprises a temperature sensor wherein said temperature sensor is used to control the release of said steam. The first positioning element comprises at least one of a wire mesh disc, a wire mesh cone, or an inflatable balloon. The first positioning element is separated from an ablation region by a distance of between 0 mm and 1 cm. The diameter of the first positioning element is between 1 mm and 100 mm.

In another embodiment, the present invention is directed to a device to perform ablation of gastrointestinal tissue, comprising a catheter having a hollow shaft through which steam can be transported; a first positioning element attached to said catheter shaft at a first position, wherein said first positioning element is configured to abut the gastrointestinal tissue; and an input port at a second position and in fluid communication with said catheter shaft in order to receive said steam wherein the shaft comprises one or more ports through which said steam can be released out of said shaft onto the gastrointestinal tissue.

Optionally, the device further comprises a temperature sensor wherein said temperature sensor is used to control the release of said steam. The first positioning element comprises at least one of a wire mesh disc and a wire mesh cone. The diameter of the first positioning element is 0.1 mm to 50 mm. The device is used to perform non-circumferential ablation.

In another embodiment, the present invention is directed to a device to perform ablation of endometrial tissue, comprising a catheter having a shaft through which an ablative agent can travel; a first positioning element attached to said catheter shaft at a first position, wherein said first positioning element is configured to center said catheter in a center of a cervix; and a shaft comprises a plurality of ports through which said ablative agent can be released out of said shaft.

In another embodiment, the present invention is directed toward a device to perform ablation of endometrial tissue, comprising a catheter having a hollow shaft through which steam can be delivered; a first positioning element attached to said catheter shaft at a first position, wherein said first positioning element is conical and configured to center said catheter in a center of a cervix; a second positioning element attached to said catheter shaft at a second position, wherein the second positioning element is elliptical shaped; a plurality of ports integrally formed in said catheter shaft, wherein steam can be released out of said ports and directed toward endometrial tissue and wherein said ports are located between said first position and second position; and at least one temperature sensor.

Optionally, the second positioning element has a predefined dimension and wherein said dimension is used to determine a uterine cavity size. The second positioning element has a diameter and wherein said diameter is used to calculate an amount of thermal energy needed to ablate the endometrial tissue. The temperature sensors are used to control delivery of said ablative agent. The first positioning element comprises wire mesh. The second positioning element has a disc shape that is oval and wherein said oval has a long axis between 0.01 mm and 10 cm and a short axis between 0.01 mm and 5 cm.

Optionally, the second positioning element can use one or more sources of infrared, electromagnetic, acoustic or radiofrequency energy to measure the dimensions of the hollow cavity. The energy is emitted from the sensor and is reflected back to the detector in the sensor. The reflected data is used to determine the dimension of the hollow cavity.

BRIEF DESCRIPTION OF THE DRAWINGS

The present invention is described by way of embodiments illustrated in the accompanying drawings wherein:

FIG. 1 illustrates an ablation device, in accordance with an embodiment of the present invention;

FIG. 2aillustrates a longitudinal section of an ablation device with ports distributed thereon;

FIG. 2billustrates a cross section of a port on the ablation device, in accordance with an embodiment of the present invention;

FIG. 2cillustrates a cross section of a port on the ablation device, in accordance with another embodiment of the present invention;

FIG. 2dillustrates a catheter of the ablation device, in accordance with an embodiment of the present invention;

FIG. 3aillustrates the ablation device placed in an upper gastrointestinal tract with Barrett esophagus to selectively ablate the Barrett tissue, in accordance with an embodiment of the present invention;

FIG. 3billustrates the ablation device placed in an upper gastrointestinal tract with Barrett esophagus to selectively ablate the Barrett tissue, in accordance with another embodiment of the present invention;

FIG. 3cis a flowchart illustrating the basic procedural steps for using the ablation device, in accordance with an embodiment of the present invention;

FIG. 4aillustrates the ablation device placed in a colon to ablate a flat colon polyp, in accordance with an embodiment of the present invention;

FIG. 4billustrates the ablation device placed in a colon to ablate a flat colon polyp, in accordance with another embodiment of the present invention;

FIG. 5aillustrates the ablation device with a coaxial catheter design, in accordance with an embodiment of the present invention;

FIG. 5billustrates a partially deployed positioning device, in accordance with an embodiment of the present invention;

FIG. 5cillustrates a completely deployed positioning device, in accordance with an embodiment of the present invention;

FIG. 5dillustrates the ablation device with a conical positioning element, in accordance with an embodiment of the present invention;

FIG. 5eillustrates the ablation device with a disc shaped positioning element, in accordance with an embodiment of the present invention;

FIG. 6 illustrates an upper gastrointestinal tract with a bleeding vascular lesion being treated by the ablation device, in accordance with an embodiment of the present invention;

FIG. 7 illustrates endometrial ablation being performed in a female uterus by using the ablation device, in accordance with an embodiment of the present invention;

FIG. 8 illustrates sinus ablation being performed in a nasal passage by using the ablation device, in accordance with an embodiment of the present invention;

FIG. 9 illustrates bronchial and bullous ablation being performed in a pulmonary system by using the ablation device, in accordance with an embodiment of the present invention;

FIG. 10 illustrates prostate ablation being performed on an enlarged prostrate in a male urinary system by using the device, in accordance with an embodiment of the present invention;

FIG. 11 illustrates fibroid ablation being performed in a female uterus by using the ablation device, in accordance with an embodiment of the present invention;

FIG. 12 illustrates a vapor delivery system using an RF heater for supplying vapor to the ablation device, in accordance with an embodiment of the present invention; and

FIG. 13 illustrates a vapor delivery system using a resistive heater for supplying vapor to the ablation device, in accordance with an embodiment of the present invention.

DETAILED DESCRIPTION OF THE INVENTION

The present invention provides an ablation device comprising a catheter with one or more centering or positioning attachments at one or more ends of the catheter to affix the catheter and its infusion port at a fixed distance from the ablative tissue which is not affected by the movements of the organ. The arrangement of one or more spray ports allows for uniform spray of the ablative agent producing a uniform ablation of large area such as Barrett esophagus. The flow of ablative agent is controlled by the microprocessor and depends upon one or more of the length or area of tissue to be ablated, type and depth of tissue to be ablated and distance of the infusion port from the tissue to be ablated.

“Treat,” “treatment,” and variations thereof refer to any reduction in the extent, frequency, or severity of one or more symptoms or signs associated with a condition.

“Duration” and variations thereof refer to the time course of a prescribed treatment, from initiation to conclusion, whether the treatment is concluded because the condition is resolved or the treatment is suspended for any reason. Over the duration of treatment, a plurality of treatment periods may be prescribed during which one or more prescribed stimuli are administered to the subject.

“Period” refers to the time over which a “dose” of stimulation is administered to a subject as part of the prescribe treatment plan.

The term “and/or” means one or all of the listed elements or a combination of any two or more of the listed elements.

The terms “comprises” and variations thereof do not have a limiting meaning where these terms appear in the description and claims.

Unless otherwise specified, “a,” “an,” “the,” “one or more,” and “at least one” are used interchangeably and mean one or more than one.

For any method disclosed herein that includes discrete steps, the steps may be conducted in any feasible order. And, as appropriate, any combination of two or more steps may be conducted simultaneously.

Also herein, the recitations of numerical ranges by endpoints include all numbers subsumed within that range (e.g., 1 to 5 includes 1, 1.5, 2, 2.75, 3, 3.80, 4, 5, etc.). Unless otherwise indicated, all numbers expressing quantities of components, molecular weights, and so forth used in the specification and claims are to be understood as being modified in all instances by the term “about.” Accordingly, unless otherwise indicated to the contrary, the numerical parameters set forth in the specification and claims are approximations that may vary depending upon the desired properties sought to be obtained by the present invention. At the very least, and not as an attempt to limit the doctrine of equivalents to the scope of the claims, each numerical parameter should at least be construed in light of the number of reported significant digits and by applying ordinary rounding techniques. Notwithstanding that the numerical ranges and parameters setting forth the broad scope of the invention are approximations, the numerical values set forth in the specific examples are reported as precisely as possible. All numerical values, however, inherently contain a range necessarily resulting from the standard deviation found in their respective testing measurements.

Ablative agents such as steam, heated gas or cryogens such as but not limited to liquid nitrogen are inexpensive and readily available, and are directed via the infusion port onto the tissue, held at a fixed and consistent distance, targeted for ablation. This allows for uniform distribution of the ablative agent on the targeted tissue. The flow of the ablative agent is controlled by a microprocessor according to a predetermined method based on the characteristic of the tissue to be ablated, required depth of ablation, and distance of the port from the tissue. The microprocessor may use temperature, pressure or other sensing data to control the flow of the ablative agent. In addition, one or more suction ports are provided to suction the ablation agent from the vicinity of the targeted tissue. The targeted segment can be treated by a continuous infusion of the ablative agent or via cycles of infusion and removal of the ablative agent as determined and controlled by the microprocessor.

It should be appreciated that the devices and embodiments described herein are implemented in concert with a controller that comprises a microprocessor executing control instructions. The controller can be in the form of any computing device, including desktop, laptop, and mobile device, and can communicate control signals to the ablation devices in wired or wireless form.

The following disclosure is provided in order to enable a person having ordinary skill in the art to practice the invention. Exemplary embodiments are provided only for illustrative purposes and various modifications will be readily apparent to persons skilled in the art. The general principles defined herein may be applied to other embodiments and applications without departing from the spirit and scope of the invention. Also, the terminology and phraseology used is for the purpose of describing exemplary embodiments and should not be considered limiting. Thus, the present invention is to be accorded the widest scope encompassing numerous alternatives, modifications and equivalents consistent with the principles and features disclosed. For purpose of clarity, details relating to technical material that is known in the technical fields related to the invention have not been described in detail so as not to unnecessarily obscure the present invention. The present invention will now be discussed in context of embodiments as illustrated by the accompanying drawings.

FIG. 1 illustrates an ablation device, in accordance with an embodiment of the present invention. The ablation device comprises acatheter10 having a distal centering or positioning attachment which is aninflatable balloon11. Thecatheter10 is made of or covered with an insulated material to prevent the escape of ablative energy from the catheter body. The ablation device comprises one ormore infusion ports12 for the infusion of ablative agent and one ormore suction ports13 for the removal of ablative agent. In one embodiment, theinfusion port12 andsuction port13 are the same. Ablative agent is stored in areservoir14 connected to thecatheter10. Delivery of the ablative agent is controlled by amicroprocessor15 and initiation of the treatment is controlled by a treating physician using an input device, such as a foot-paddle16. In other embodiments, the input device could be a voice recognition system (that is responsive to commands such as “start”, “more”, “less”, etc.), a mouse, a switch, footpad, or any other input device known to persons of ordinary skill in the art. In one embodiment,microprocessor15 translates signals from the input device, such as pressure being placed on the foot-paddle or vocal commands to provide “more” or “less” ablative agent, into control signals that determine whether more or less ablative agent is dispensed.Optional sensor17 monitors changes in an ablative tissue or its vicinity to guide flow of ablative agent. Optional infrared, electromagnetic, acoustic or radiofrequency energy emitter andsensor18 measures the dimensions of the hollow organ.

In one embodiment, the inflatable balloon has a diameter of between 1 mm and 10 cm. In one embodiment, the inflatable balloon is separated from the ports by a distance of 1 mm to 10 cm. In one embodiment, the size of the port openings are between 1 μm and 1 cm. It should be appreciated that the inflatable balloon is used to fix the device and therefore is configured to not contact the ablated area. The inflatable balloon can be any shape that contacts the hollow organ at 3 or more points. One of ordinary skill in the art that, using triangulation, one can calculate the distance of the catheter from the lesion. Alternatively the infrared, electromagnetic, acoustic or radiofrequency energy emitter andsensor18 can measure the dimensions of the hollow organ. The infrared, electromagnetic, acoustic or radiofrequency energy is emitted from theemitter18 and is reflected back from the tissue to the detector in theemitter18. The reflected data can be used to determine the dimension of the hollow cavity. It should be appreciated that the emitter andsensor18 can be incorporated into a single transceiver that is capable of both emitting energy and detecting the reflected energy.

FIG. 2aillustrates a longitudinal section of the ablation device, depicting a distribution of infusion ports.FIG. 2billustrates a cross section of a distribution of infusion ports on the ablation device, in accordance with an embodiment of the present invention. The longitudinal and cross sectional view of thecatheter10 as illustrated inFIGS. 2aand2brespectively, show one arrangement of theinfusion ports12 to produce a uniform distribution ofablative agent21 in order to provide a circumferential area of ablation in ahollow organ20.FIG. 2cillustrates a cross section of a distribution of infusion ports on the ablation device, in accordance with another embodiment of the present invention. The arrangement of theinfusion ports12 as illustrated inFIG. 2cproduce a focal distribution ofablative agent21 and a focal area of ablation in ahollow organ20.

For all embodiments described herein, it should be appreciated that the size of the port, number of ports, and distance between the ports will be determined by the volume of ablative agent needed, pressure that the hollow organ can withstand, size of the hollow organ as measured by the distance of the surface from the port, length of the tissue to be ablated (which is roughly the surface area to be ablated), characteristics of the tissue to be ablated and depth of ablation needed. In one embodiment, there is at least one port opening that has a diameter between 1 μm and 1 cm. In another embodiment, there is two or more port openings that have a diameter between 1 μm and 1 cm and that are equally spaced around the perimeter of the device.

FIG. 2dillustrates another embodiment of the ablation device. The vapor ablation catheter comprises aninsulated catheter21 with one ormore positioning attachments22 of knownlength23. The vapor ablation catheter has one or morevapor infusion ports25. Thelength24 of thevapor ablation catheter21 withinfusion ports25 is determined by the length or area of the tissue to be ablated.Vapor29 is delivered through thevapor infusion ports25. Thecatheter21 is preferably positioned in the center of thepositioning attachment22, and theinfusion ports25 are arranged circumferentially for circumferential ablation and delivery of vapor. In another embodiment, thecatheter21 can be positioned toward the periphery of thepositioning attachment22 and theinfusion ports25 can be arranged non-circumferentially, preferably linearly on one side for focal ablation and delivery of vapor. Thepositioning attachment23 is one of an inflatable balloon, a wire mesh disc with or without an insulated membrane covering the disc, a cone shaped attachment, a ring shaped attachment or a freeform attachment designed to fit the desired hollow body organ or hollow body passage, as further described below. Optional infrared, electromagnetic, acoustic or radiofrequency energy emitter andsensor28 are incorporated to measures the dimensions of the hollow organ.

The vapor ablation catheter may also comprise an optionalcoaxial sheet27 to restrain thepositioning attachment22 in a manner comparable to a coronary metal stent. In one embodiment, the disc is made of memory metal or memory material with a compressed linear form and a non-compressed form in the shape of the positioning attachment. Alternatively, the channel of an endoscope may perform the function of restraining thepositioning attachment22 by, for example, acting as a constraining sheath.Optional sensor26 is deployed on the catheter to measure changes associated with vapor delivery or ablation. The sensor is one of temperature, pressure, photo or chemical sensor.

Optional, one or more, infrared, electromagnetic, acoustic or radiofrequency energy emitter andsensor28 can measure the dimensions of the hollow organ. The infrared, electromagnetic, acoustic or radiofrequency energy is emitted from theemitter18 and is reflected back from the tissue to the detector in theemitter18. The reflected data can be used to determine the dimension of the hollow cavity. The measurement is performed at one or multiple points to get an accurate estimate of the dimension of the hollow organ. The data can also be used to create a topographic representation of the hollow organ.

FIG. 3aillustrates the ablation device placed in an upper gastrointestinal tract with Barrett esophagus to selectively ablate the Barrett tissue, in accordance with an embodiment of the present invention. The upper gastrointestinal tract comprisesBarrett esophagus31,gastric cardia32,gastroesophageal junction33 and displaced squamo-columnar junction34. The area betweengastroesophageal junction33 and displaced squamo-columnar junction34 isBarrett esophagus31, which is targeted for ablation. Distal to thecardia32 is thestomach35 and proximal to thecardia32 is theesophagus36. The ablation device is passed into theesophagus36 and thepositioning device11 is placed in thegastric cardia32 abutting thegastroesophageal junction33. This affixes theablation catheter10 and itsports12 in the center of theesophagus36 and allows for uniform delivery of theablative agent21 to theBarrett esophagus31. In one embodiment, the positioning device is first affixed to an anatomical structure, not being subjected to ablation, before ablation occurs. Where the patient is undergoing circumferential ablation or first time ablation, the positioning attachment is preferably placed in the gastric cardia, abutting the gastroesophageal junction. Where the patient is undergoing a focal ablation of any residual disease, it is preferable to use the catheter system shown inFIG. 4b, as discussed below. In one embodiment, the positioning attachment must be separated from the ablation region by a distance of greater than 0 mm, preferably 1 mm and ideally 1 cm. In one embodiment, the size of the positioning device is in the range of 10 to 100 mm, preferably 20-40 mm, although one of ordinary skill in the art would appreciate that the precise dimensions are dependent on the size of the patient's esophagus.

The delivery ofablative agent21 through theinfusion port12 is controlled by themicroprocessor15 coupled with the ablation device. The delivery of ablative agent is guided by predetermined programmatic instructions, depending on the tissue to be ablated and the depth of ablation required. In one embodiment, the target procedural temperature will need to be between −100 degrees Celsius and 200 degrees Celsius, preferably between 50 degrees Celsius and 75 degrees Celsius, as further shown in the dosimetery table below. In one embodiment, esophageal pressure should not to exceed 5 atm, and is preferably below 0.5 atm. In one embodiment, the target procedural temperature is achieved in less than 1 minute, preferably in less than 5 seconds, and is capable of being maintained for up to 10 minutes, preferably 1 to 10 seconds, and then cooled to body temperature. One of ordinary skill in the art would appreciate that the treatment can be repeated until the desired ablation effect is achieved.

Optional sensor

17 monitors intraluminal parameters such as temperature and pressure and can increase or decrease the flow ofablative agent21 through theinfusion port12 to obtain adequate heating or cooling, resulting in adequate ablation. Thesensor17 monitors intraluminal parameters such as temperature and pressure and can increase or decrease the removal ofablative agent21 through theoptional suction port13 to obtain adequate heating or cooling resulting in adequate ablation ofBarrett esophagus31.FIG. 3billustrates the ablation device placed in an upper gastrointestinal tract with Barrett esophagus to selectively ablate the Barrett tissue, in accordance with another embodiment of the present invention. As illustrated inFIG. 3b, thepositioning device11 is a wire mesh disc. In one embodiment, the positioning attachment must be separated from the ablation region by a distance of greater than 0 mm, preferably 1 mm and ideally 1 cm. In one embodiment, the positioning attachment is removably affixed to the cardia or EG junction (for the distal attachment) or in the esophagus by a distance of greater than 0.1 mm, preferably around 1 cm, above the proximal most extent of the Barrett tissue (for the proximal attachment).

FIG. 3bis another embodiment of the Barrett ablation device where thepositioning element11 is a wire mesh disc. The wire mesh may have optional insulated membrane to prevent the escape of the ablative agent. In the current embodiment, two wire mesh discs are used to center the ablation catheter in the esophagus. The distance between the two discs is determined by the length of the tissue to ablated which, in this case, would be the length of the Barrett esophagus. Optional infrared, electromagnetic, acoustic or radiofrequency energy emitter andsensor18 are incorporated to measures the diameter of the esophagus.

FIG. 3cis a flowchart illustrating the basic procedural steps for using the ablation device, in accordance with an embodiment of the present invention. Atstep302, a catheter of the ablation device is inserted into a hollow organ which is to be ablated. For example, in order to perform ablation in a Barrett esophagus of a patient the catheter is inserted into the Barrett esophagus via the esophagus of the patient.

Atstep304, a positioning element of the ablation device is deployed. In an embodiment, where the positioning element is a balloon, the balloon is inflated in order to position the ablation device at a known fixed distance from the tissue to be ablated. The diameter of the hollow organ may either be predetermined by using radiological tests such as barium X-rays or computer tomography (CT) scan, or by using pressure volume cycle, i.e. by determining volume needed to raise pressure to a fixed level (say 1 atm) in a fixed volume balloon. In another embodiment, where the positioning device is disc shaped, circumferential rings are provided in order to visually communicate to an operating physician the diameter of the hollow organ. In various embodiments of the present invention, the positioning device enables centering of the catheter of the ablation device in a non-cylindrical body cavity, and the volume of the cavity is measured by the length of catheter or a uterine sound.

Optional, one or more, infrared, electromagnetic, acoustic or radiofrequency energy emitter and sensor can be used to measure the dimensions of the hollow organ. The infrared, electromagnetic, acoustic or radiofrequency energy is emitted from the emitter and is reflected back from the tissue to a detector in the emitter. The reflected data can be used to determine the dimension of the hollow cavity. The measurement can be performed at one or multiple points to get an accurate estimate of the dimension of the hollow organ. The data from multiple points can also be used to create a topographic representation of the hollow organ or to calculate the volume of the hollow organ.

In one embodiment, the positioning attachment must be separated from the ports by a distance of 0 mm or greater, preferably greater than 0.1 mm, and more preferably 1 cm. The size of the positioning device depends on the hollow organ being ablated and ranges from 1 mm to 10 cm. In one embodiment, the diameter of the positioning element is between 0.01 mm and 100 mm. In one embodiment, the first positioning element comprises a circular body with a diameter between 0.01 mm and 10 cm.

Atstep306, the organ is ablated by automated delivery of an ablative agent such as steam via infusion ports provided on the catheter. The delivery of the ablative agent through the infusion ports is controlled by a microprocessor coupled with the ablation device. The delivery of ablative agent is guided by predetermined programmatic instructions depending on the tissue to be ablated and the depth of ablation required. In an embodiment of the present invention where the ablative agent is steam, the dose of the ablative agent is determined by conducting dosimetery study to determine the dose to ablate endometrial tissue. The variable that enables determination of total dose of ablative agent is the volume (or mass) of the tissue to be treated which is calculated by using the length of the catheter and diameter of the organ (for cylindrical organs). The determined dose of ablative agent is then delivered using micro-processor controlled steam generator.

In one embodiment, the dose is provided by first determining what the disorder being treated is and what the desired tissue effect is, and then finding the corresponding temperature, as shown in the tables below.


Temp	Tissue Effect

37-40	No significant tissue effect
41-44	Reversible cell damage in few hours
45-49	Irreversible cell damage at shorter intervals
50-69	Irreversible cell damage -ablation necrosis atshorter intervals
70	Threshold temp for tissue shrinkage, H-bond breakage
70-99	Coagulation and Hemostasis
100-200	Desiccation and Carbonization of tissue
>200	Charring of tissue glucose

	Disorder	Max. Temp

	ENT/Pulmonary
	Nasal Polyp	60-80 C.
	Turbinectomy	70-85 C.
	Bullous Disease	70-85 C.
	Lung Reduction	70-85 C.
	Genitourinary
	Uterine Menorrhagia	80-90 C.
	Endometriosis	80-90 C.
	Uterine Fibroids	90-100 C.
	Benign Prostatic Hypertrophy	90-100 C.
	Gastroenterology
	Barrett Esophagus	60-75 C.
	Esophageal Dysplasia	60-80 C.
	Vascular GI Disorders	55-75 C.
	Flat Polyps	60-80 C.

In addition, the depth of ablation desired determines the holding time at the maximum temperature. For superficial ablation (Barrett), the holding time at the maximum temperature is very short (flash burn) and does not allow for heat to transfer to the deeper layers. This will prevent damage to deeper normal tissue and hence prevention patient discomfort and complication. For deeper tissue ablation, the holding time at the maximum temperature will be longer, thereby allowing the heat to percolate deeper.

FIG. 4aillustrates the ablation device placed in a colon to ablate a flat colon polyp, in accordance with an embodiment of the present invention. Theablation catheter10 is passed through acolonoscope40. Thepositioning device11 is placed proximal to a flatcolonic polyp41 which is to be ablated, in thenormal colon42. Thepositioning device11 is one of an inflatable balloon, a wire mesh disc with or without an insulated membrane covering the disc, a cone shaped attachment, a ring shaped attachment or a freeform attachment designed to fit the colonic lumen. Thepositioning device11 has thecatheter10 located toward the periphery of thepositioning device11 placing it closer to thepolyp41 targeted for non-circumferential ablation. Hence, thepositioning device11 fixes the catheter to thecolon42 at a predetermined distance from thepolyp41 for uniform and focused delivery of theablative agent21. The delivery ofablative agent21 through theinfusion port12 is controlled by themicroprocessor15 attached to the ablation device and depends on tissue and the depth of ablation required. The delivery ofablative agent21 is guided by predetermined programmatic instructions depending on the tissue to be ablated and the area and depth of ablation required. The ablation device allows for focal ablation of diseased polyp mucosa without damaging the normal colonic mucosa located away from the catheter ports.

In one embodiment, the positioning attachment must be separated from the ablation region by a distance of greater than 0.1 mm, ideally more than 5 mm. In one embodiment, the positioning element is proximal to the colon polyp. For this application, the embodiment shown inFIG. 4bwould be preferred.

FIG. 4billustrates the ablation device placed in a colon to ablate a flat colon polyp, in accordance with another embodiment of the present invention. As illustrated inFIG. 4b, the positioning device is a conical attachment at the tip of the catheter. The conical attachment has a known length ‘l ’ and diameter ‘d’ that is used to calculate the amount of thermal energy needed to ablate the flat colon polyp. In one embodiment, the positioning attachment must be separated from the ablation region by a distance of greater than 0.1 mm, preferably 1 mm and more preferably 1 cm. In one embodiment, the length ‘l ’ is greater than 0.1 mm, preferably between 5 and 10 mm. In one embodiment, diameter ‘d’ depends on the size of the polyp and can be between 1 mm and 10 cm, preferably 1 to 5 cm. This embodiment can also be used to ablate residual neoplastic tissue at the edges after endoscopic snare resection of a large sessile colon polyp.

FIG. 5aillustrates the ablation device with a coaxial catheter design, in accordance with an embodiment of the present invention. The coaxial design has ahandle52a, aninfusion port53a, aninner sheath54aand anouter sheath55a. Theouter sheath55ais used to constrain thepositioning device56ain the closed position and encompassesports57a.FIG. 5bshows a partially deployedpositioning device56b, with theports57bstill within theouter sheath55b. Thepositioning device56bis partially deployed by pushing thecatheter54bout ofsheath55b.

FIG. 5cshows a completely deployedpositioning device56c. Theinfusion ports57care out of thesheath55c. The length ‘l ’ of thecatheter54cthat contains theinfusion port57cand the diameter ‘d’ of thepositioning element56care predetermined/known and are used to calculate the amount of thermal energy needed.FIG. 5dillustrates a conical design of the positioning element. The positioning element56dis conical with a known length ‘l ’ and diameter ‘d’ that is used to calculate the amount of thermal energy needed for ablation.FIG. 5eillustrates a disc shaped design of thepositioning element56ecomprising circumferential rings59e. The circumferential rings59eare provided at a fixed predetermined distance and are used to estimate the diameter of a hollow organ or hollow passage in a patient's body.

FIG. 6 illustrates an upper gastrointestinal tract with a bleeding vascular lesion being treated by the ablation device, in accordance with an embodiment of the present invention. The vascular lesion is avisible vessel61 in the base of anulcer62. Theablation catheter63 is passed though the channel of anendoscope64. Theconical positioning element65 is placed over thevisible vessel61. Theconical positioning element65 has a known length ‘l ’ and diameter ‘d’, which are used to calculate the amount of thermal energy needed for coagulation of the visible vessel to achieve hemostasis. The conical positioning element has an optional insulated membrane that prevents escape of thermal energy or vapor away from the disease site.

In one embodiment, the positioning attachment must be separated from the ablation region by a distance of greater than 0.1 mm, preferably 1 mm and more preferably 1 cm. In one embodiment, the length ‘l ’ is greater than 0.1 mm, preferably between 5 and 10 mm. In one embodiment, diameter ‘d’ depends on the size of the lesion and can be between 1 mm and 10 cm, preferably 1 to 5 cm.

FIG. 7 illustrates endometrial ablation being performed in a female uterus by using the ablation device, in accordance with an embodiment of the present invention. A cross-section of the female genital tract comprising avagina70, acervix71, auterus72, anendometrium73,fallopian tubes74,ovaries75 and the fundus of theuterus76 is illustrated. Acatheter77 of the ablation device is inserted into theuterus72 through thecervix71. In an embodiment, thecatheter77 has two positioning elements, aconical positioning element78 and a disc shapedpositioning element79. Thepositioning element78 is conical with an insulated membrane covering theconical positioning element78. Theconical element78 positions thecatheter77 in the center of the cervix71 and the insulated membrane prevents the escape of thermal energy or ablative agent through thecervix71. The second disc shapedpositioning element79 is deployed close to the fundus of theuterus76 positioning thecatheter71 in the middle of the cavity. Anablative agent778 is passed throughinfusion ports777 for uniform delivery of theablative agent778 into the uterine cavity. Predetermined length “l” of the ablative segment of the catheter and diameter ‘d’ of thepositioning element79 allows for estimation of the cavity size and is used to calculate the amount of thermal energy needed to ablate the endometrial liningOptional temperature sensors7 deployed close to the endometrial surface are used to control the delivery of theablative agent778. Optional topographic mapping using multiple infrared, electromagnetic, acoustic or radiofrequency energy emitter and sensor can be used to define cavity size and shape in patients with irregular or deformed uterine cavity due to conditions such as fibroids.

In an embodiment, the ablative agent is steam which contracts on cooling. Steam turns to water which has a lower volume as compared to a cryogen that will expand or a hot fluid used in hydrothermal ablation whose volume stays constant. With both cryogens and hot fluids, increasing energy delivery is associated with increasing volume of the ablative agent which, in turn, requires mechanisms for removing the agent, otherwise the medical provider will run into complications. However, steam, on cooling, turn into water which occupies significantly less volume; therefore, increasing energy delivery is not associated with an increase in volume of the residual ablative agent, thereby eliminating the need for continued removal. This further decreases the risk of leakage of the thermal energy via thefallopian tubes74 or thecervix71, thus reducing any risk of thermal injury to adjacent healthy tissue.

In one embodiment, the positioning attachment must be separated from the ablation region by a distance of greater than 0.1 mm, preferably 1 mm and more preferably 1 cm. In another embodiment, the positioning attachment can be in the ablated region as long as it does not cover a significant surface area. For endometrial ablation, 100% of the tissue does not need to be ablated to achieve the desired therapeutic effect.

In one embodiment, the preferred distal positioning attachment is an uncovered wire mesh that is positioned proximate to the mid body region. In one embodiment, the preferred proximal positioning device is a covered wire mesh that is pulled into the cervix, centers the device, and occludes the cervix. One or more such positioning devices may be helpful to compensate for the anatomical variations in the uterus. The proximal positioning device is preferably oval, with a long axis being between 0.1 mm and 10 cm (preferably 1 cm to 5 cm) and a short axis between 0.1 mm and 5 cm (preferably 0.5 cm to 1 cm). The distal positioning device is preferably circular with a diameter between 0.1 mm and 10 cm, preferably 1 cm to 5 cm.

FIG. 8 illustrates sinus ablation being performed in a nasal passage by using the ablation device, in accordance with an embodiment of the present invention. A cross-section of the nasal passage andsinuses comprising nares81,nasal passages82,frontal sinus83,ethemoid sinus84, anddiseased sinus epithelim85 is illustrated. Thecatheter86 is inserted into thefrontal sinus83 or theethemoid sinus84 through thenares81 andnasal passages82.

In an embodiment, thecatheter86 has two positioning elements, aconical positioning element87 and a disc shapedpositioning element88. Thepositioning element87 is conical and has an insulated membrane covering. Theconical element87 positions thecatheter86 in the center of thesinus opening80 and the insulated membrane prevents the escape of thermal energy or ablative agent through the opening. The second disc shapedpositioning element88 is deployed in thefrontal sinus cavity83 orethemoid sinus cavity84, positioning thecatheter86 in the middle of either sinus cavity. Theablative agent8 is passed through theinfusion port89 for uniform delivery of theablative agent8 into the sinus cavity. The predetermined length “l” of the ablative segment of the catheter and diameter ‘d’ of thepositioning element88 allows for estimation of the sinus cavity size and is used to calculate the amount of thermal energy needed to ablate thediseased sinus epithelium85.Optional temperature sensors888 are deployed close to thediseased sinus epithelium85 to control the delivery of theablative agent8. In an embodiment, theablative agent8 is steam which contracts on cooling. This further decreases the risk of leakage of the thermal energy thus reducing any risk of thermal injury to adjacent healthy tissue. In one embodiment, the dimensional ranges of the positioning elements are similar to those in the endometrial application, with preferred maximum ranges being half thereof. Optional topographic mapping using multiple infrared, electromagnetic, acoustic or radiofrequency energy emitter and sensor can be used to define cavity size and shape in patients with irregular or deformed nasal cavity due to conditions such as nasal polyps.

FIG. 9 illustrates bronchial and bullous ablation being performed in a pulmonary system by using the ablation device, in accordance with an embodiment of the present invention. A cross-section of the pulmonarysystem comprising bronchus91,normal alveolus92,bullous lesion93, and abronchial neoplasm94 is illustrated.

In one embodiment, thecatheter96 is inserted through the channel of abronchoscope95 into thebronchus91 and advanced into abullous lesion93. Thecatheter96 has two positioning elements, aconical positioning element97 and a disc shapedpositioning element98. Thepositioning element97 is conical having an insulated membrane covering. Theconical element97 positions thecatheter96 in the center of thebronchus91 and the insulated membrane prevents the escape of thermal energy or ablative agent through the opening into the normal bronchus. The second disc shapedpositioning element98 is deployed in thebullous cavity93 positioning thecatheter96 in the middle of thebullous cavity93. Anablative agent9 is passed through theinfusion port99 for uniform delivery into the sinus cavity. Predetermined length “l” of the ablative segment of thecatheter96 and diameter ‘d’ of thepositioning element98 allow for estimation of the bullous cavity size and is used to calculate the amount of thermal energy needed to ablate the diseasedbullous cavity93. Optionally the size of the cavity can be calculated from radiological evaluation using a chest CAT scan or MRI. Optional temperature sensors are deployed close to the surface of thebullous cavity93 to control the delivery of theablative agent9. In an embodiment, the ablative agent is steam which contracts on cooling. This further decreases the risk of leakage of the thermal energy into the normal bronchus thus reducing any risk of thermal injury to adjacent normal tissue.

In one embodiment, the positioning attachment must be separated from the ablation region by a distance of greater than 0.1 mm, preferably 1 mm and more preferably 1 cm. In another embodiment, the positioning attachment can be in the ablated region as long as it does not cover a significant surface area.

In one embodiment, there are preferably two positioning attachments. In another embodiment, the endoscope is used as one fixation point with one positioning element. The positioning device is between 0.1 mm and 5 cm (preferably 1 mm to 2 cm). The distal positioning device is preferably circular with a diameter between 0.1 mm and 10 cm, preferably 1 cm to 5 cm.

In another embodiment for the ablation of abronchial neoplasm94, thecatheter96 is inserted through the channel of abronchoscope95 into thebronchus91 and advanced across thebronchial neoplasm94. Thepositioning element98 is disc shaped having an insulated membrane covering. Thepositioning element98 positions the catheter in the center of thebronchus91 and the insulated membrane prevents the escape of thermal energy or ablative agent through the opening into the normal bronchus. Theablative agent9 is passed through theinfusion port99 in a non-circumferential pattern for uniform delivery of the ablative agent to thebronchial neoplasm94. The predetermined length “l” of the ablative segment of the catheter and diameter ‘ d’ of thepositioning element98 are used to calculate the amount of thermal energy needed to ablate thebronchial neoplasm94.

FIG. 10 illustrates prostate ablation being performed on an enlarged prostrate in a male urinary system by using the device, in accordance with an embodiment of the present invention. A cross-section of a male genitourinary tract having anenlarged prostate101,bladder102, andurethra103 is illustrated. Theurethra103 is compressed by theenlarged prostate101. Theablation catheter105 is passed through thecystoscope104 positioned in theurethra103 distal to the obstruction. Thepositioning elements106 are deployed to center the catheter in theurethra103 andinsulated needles107 are passed to pierce theprostate101. The vaporablative agent108 is passed through theinsulated needles107 thus causing ablation of the diseased prostatic tissue resulting in shrinkage of the prostate.

In one embodiment, the positioning attachment must be separated from the ablation region by a distance of greater than 0.1 mm, preferably 1 mm to 5 mm and no more than 2 cm. In another embodiment, the positioning attachment can be deployed in the bladder and pulled back into the urethral opening/neck of the bladder thus fixing the catheter. In one embodiment, the positioning device is between 0.1 mm and 10 cm.

FIG. 11 illustrates fibroid ablation being performed in a female uterus by using the ablation device, in accordance with an embodiment of the present invention.

A cross-section of a female genitourinary tract comprising auterine fibroid111,uterus112, andcervix113 is illustrated. Theablation catheter115 is passed through thehysteroscope114 positioned in the uterus distal to thefibroid111. Theablation catheter115 has apuncturing tip120 that helps puncture into thefibroid111. Thepositioning elements116 are deployed to center the catheter in the fibroid andinsulated needles117 are passed to pierce thefibroid tissue111. The vaporablative agent118 is passed through theneedles117 thus causing ablation of theuterine fibroid111 resulting in shrinkage of the fibroid.

FIG. 12 illustrates a vapor delivery system using an RF heater for supplying vapor to the ablation device, in accordance with an embodiment of the present invention. In an embodiment, the vapor is used as an ablative agent in conjunction with the ablation device described in the present invention.RF heater64 is located proximate apressure vessel42 containing a liquid44.RF heater64

heats vessel

42, in turn heating the liquid44. The liquid44 heats up and begins to evaporate causing an increase in pressure inside thevessel42. The pressure insidevessel42 can be kept fairly constant by providing athermal switch46 that controlsresistive heater64. Once, the temperature of the liquid44 reaches a predetermined temperature, thethermal switch46 shuts offRF heater64. The vapor created inpressure vessel42 may be released via acontrol valve50. As the vapor exitsvessel42, a pressure drop is created in the vessel resulting in a reduction in temperature. The reduction of temperature is measured bythermal switch46, andRF heater64 is turned back on toheat liquid44. In one embodiment, the target temperature ofvessel42 may be set to approximately 108° C., providing a continuous supply of vapor. As the vapor is released, it undergoes a pressure drop, which reduces the temperature of the vapor to a range of approximately 90-100° C. Asliquid44 invessel42 evaporates and the vapor exitsvessel42, the amount ofliquid44 slowly diminishes. Thevessel42 is optionally connected toreservoir43 containingliquid44 via apump49 which can be turned on by thecontroller24 upon sensing a fall in pressure or temperature invessel42 delivering additional liquid44 to thevessel42.

Vapor delivery catheter

16 is connected tovessel42 via afluid connector56. Whencontrol valve50 is open,vessel42 is in fluid communication withdelivery catheter16 viaconnector56.Control switch60 may serve to turn vapor delivery on and off viaactuator48. For example,control switch60 may physically open and close thevalve50, viaactuator48, to control delivery of vapor stream from thevessel42.Switch60 may be configured to control other attributes of the vapor such as direction, flow, pressure, volume, spray diameter, or other parameters. Instead of, or in addition to, physically controlling attributes of the vapor, switch60 may electrically communicate with acontroller24.Controller24 controls theRF heater64, which in turn controls attributes of the vapor, in response to actuation ofswitch60 by the operator. In addition,controller24 may control valves temperature or pressure regulators associated withcatheter16 orvessel42. Aflow meter52 may be used to measure the flow, pressure, or volume of vapor delivery via thecatheter16. Thecontroller24 controls the temperature and pressure in thevessel42 and the time, rate, flow, volume of vapor flow through thecontrol valve50. These parameters are set by theoperator11. The pressure created invessel42, using the target temperature of 108° C., may be in the order of 25 pounds per square inch (psi) (1.72 bars).

FIG. 13 illustrates a vapor delivery system using a resistive heater for supplying vapor to the ablation device, in accordance with an embodiment of the present invention. In an embodiment, the generated vapor is used as an ablative agent in conjunction with the ablation device described in the present invention.Resistive heater40 is located proximate apressure vessel42.Vessel42 contains a liquid44.Resistive heater40

heats vessel

42, inturn heating liquid44. Accordingly, liquid44 heats and begins to evaporate. Asliquid44 begins to evaporate, the vapor insidevessel42 causes an increase in pressure in the vessel. The pressure invessel42 can be kept fairly constant by providing athermal switch46 that controlsresistive heater40. When the temperature ofliquid44 reaches a predetermined temperature,thermal switch46 shuts offresistive heater40. The vapor created inpressure vessel42 may be released via acontrol valve50. As the vapor exitsvessel42,vessel42 experiences a pressure drop. The pressure drop ofvessel42 results in a reduction of temperature. The reduction of temperature is measured bythermal switch46, andresistive heater40 is turned back on toheat liquid44. In one embodiment, the target temperature ofvessel42 may be set to approximately 108° C., providing a continuous supply of vapor. As the vapor is released, it undergoes a pressure drop, which reduces the temperature of the vapor to a range of approximately 90-100° C. Asliquid44 invessel42 evaporates and the vapor exitsvessel42, the amount ofliquid44 slowly diminishes. Thevessel42 is connected to anothervessel43 containingliquid44 via apump49 which can be turned on by thecontroller24 upon sensing a fall in pressure or temperature invessel44 delivering additional liquid44 to thevessel42.

Vapor delivery catheter

16 is connected tovessel42 via afluid connector56. Whencontrol valve50 is open,vessel42 is in fluid communication withdelivery catheter16 viaconnector56.Control switch60 may serve to turn vapor delivery on and off viaactuator48. For example,control switch60 may physically open and close thevalve50, viaactuator48, to control delivery of vapor stream from thevessel42.Switch60 may be configured to control other attributes of the vapor such as direction, flow, pressure, volume, spray diameter, or other parameters. Instead of, or in addition to, physically controlling attributes of the vapor, switch60 may electrically communicate with acontroller24.Controller24 controls theresistive heater40, which in turn controls attributes of the vapor, in response to actuation ofswitch60 by the operator. In addition,controller24 may control valves temperature or pressure regulators associated withcatheter16 orvessel42. Aflow meter52 may be used to measure the flow, pressure, or volume of vapor delivery via thecatheter16. Thecontroller24 controls the temperature and pressure in thevessel42 as well as time, rate, flow, volume of vapor flow through thecontrol valve50. These parameters are set by theoperator11. The pressure created invessel42, using the target temperature of 108° C., may be on the order of 25 pounds per square inch (psi) (1.72 bars).

The device and method of the present invention can be used to cause controlled focal or circumferential ablation of targeted tissue to varying depth in a manner in which complete healing with re-epithelialization can occur. The dose and manner of treatment can be adjusted based on the type of tissue and the depth of ablation needed. The ablation device can be used not only for the treatment of Barrett esophagus and esophageal dysplasia, flat colon polyps, gastrointestinal bleeding lesions, endometrial ablation, pulmonary ablation, but also for the treatment of any mucosal, submucosal or circumferential lesion, such as inflammatory lesions, tumors, polyps and vascular lesions. The ablation device can also be used for the treatment of focal or circumferential mucosal or submucosal lesion of any hollow organ or hollow body passage in the body. The hollow organ can be one of gastrointestinal tract, pancreaticobiliary tract, genitourinary tract, respiratory tract or a vascular structure such as blood vessels. The ablation device can be placed endoscopically, radiologically, surgically or under direct visualization. In various embodiments, wireless endoscopes or single fiber endoscopes can be incorporated as a part of the device.

While the exemplary embodiments of the present invention are described and illustrated herein, it will be appreciated that they are merely illustrative. It will be understood by those skilled in the art that various changes in form and detail may be made therein without departing from or offending the spirit and scope of the invention.