Device for asymmetric ice formation during cryoablation treatment

Abstract

A method (1200) of performing a cryoablation treatment includes initiating (1202) a flow of cryogen to a tip of a cryoprobe and obtaining (1204) ice formation data characterizing a shape of ice formed at a target tissue in a patient. The method (1200) further includes comparing (1206) the ice formation data to a predetermined ice formation profile and energizing (1210) a heated portion on the cryoprobe to limit growth of ice in a first direction relative to a predetermined location on the cryoprobe while refrigerant flows to the tip of the cryoprobe.

Description

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS

[0002] This application claims priority to and the benefit of U.S. Patent Application No. 17 / 664,231, filed on May 20, 2022, which is hereby incorporated by reference for all purposes as if fully set forth herein. Technical Field

[0003] The present disclosure relates to devices and methods for asymmetric formation of ice during cryoablation treatment. Background Art

[0004] This section provides background information related to the present disclosure which is not necessarily prior art.

[0005] Systems and methods for providing cryoablation treatment can include a cryoablation probe introduced at or near a target tissue in a patient's body. The cryoablation system can include an extremely cold cryogen (liquid, gas, or mixed phase) that can be transferred through a probe in thermal contact with the target tissue. Heat from the tissue is transferred from the tissue through the probe and into the cryogen, which removes heat from the target tissue. The removal of this heat causes the tissue to freeze, resulting in the destruction of the target tissue. When the tissue freezes, the ice is typically formed in the form of an ice ball. The ice ball can be in the form of a sphere, an ellipsoid, or other shapes. In existing systems, the ice ball is typically formed into a symmetrical shape. It is desirable to perform cryoablation treatment so that the target tissue is completely frozen and the freezing of surrounding tissues and / or body structures is minimized.

[0006] Conventional or existing cryoablation devices, cryoprobes, and methods suffer from various disadvantages. Conventional or existing systems and methods do not allow for the formation of ice that is asymmetric in shape relative to the cryoprobe. Therefore, ice formed using existing and conventional methods and systems may not perform as efficiently and effectively as desired. In addition, treatment using existing and conventional methods may unnecessarily form ice that freezes healthy tissue or body structures adjacent to or surrounding the target tissue. In addition, conventional and existing systems and methods may not destroy all of the target tissue due to a shape that does not correspond to the shape of the ice formed during treatment. Therefore, there is a need for improved cryoablation systems and methods to perform more efficiently and effectively with less harmful effects on healthy tissue. Summary of the invention

[0007] According to a first aspect of the present invention, a cryoablation probe as defined by claim 1 is provided.

[0008] According to a second aspect of the present invention, a cryoablation device as defined by claim 9 is provided.

[0009] According to a third aspect of the present invention, there is provided a method of performing a cryoablation treatment as defined by claim 11 .

[0010] Optional features are defined by the dependent claims.

[0011] This section provides a general summary of the disclosure, and is not a comprehensive disclosure of its full scope or all of its features.

[0012] In some embodiments of the present disclosure, devices and methods are provided that can form asymmetric ice shapes during cryoablation treatment. The ice formation can be formed into an asymmetric shape to correspond to the shape of the target tissue (e.g., a tumor). The ice formation can be formed into an asymmetric shape to prevent or reduce the likelihood that healthy tissue will be harmed.

[0013] The apparatus and methods of the present disclosure provide, in some embodiments, an improved cryoprobe. Such a cryoprobe may include various numbers of heating portions that may be independently controlled and / or activated during operation of the cryoprobe. The heating probe may reduce the formation of ice in one or more localized regions relative to the cryoprobe so that the ice is formed into a desired shape. The heating portions may be positioned in various configurations to allow control and growth of ice in a predetermined manner that may be desired for cryoablation treatment.

[0014] The apparatus and method of the present disclosure are improvements over existing and conventional apparatus and methods. The apparatus and method of the present disclosure can more effectively destroy or otherwise treat targeted tissue by forming ice corresponding to the shape of the target tissue. In addition, ice can be formed to reduce the amount of healthy tissue subjected to the low temperature of the ice. In this way, the harmful effects of cryoablation treatment on healthy tissue can be reduced and / or minimized.

[0015] In some embodiments of the present disclosure, a cryoablation system may include a plurality of heating sections, wherein each heating section of the plurality of heating sections is individually controllable to operate in an energized state and a de-energized state.

[0016] In one aspect, each heating portion of the plurality of heating portions may include a resistive heating element.

[0017] In another aspect, each of the plurality of heating portions can be coupled to a heater controller configured to change one or more of the plurality of heating portions from a de-energized state to an energized state to change ice growth characteristics of ice formed during a freezing cycle of a cryoablation treatment.

[0018] In another aspect, each of the plurality of heating portions can be located at a different peripheral position about a central axis of the cryoablation probe.

[0019] In another aspect, each heating section of the plurality of heating sections can be separate from adjacent heating sections.

[0020] In another aspect, the plurality of heating portions can include a first array of heating portions positioned at a first longitudinal position from the tip of the cryoablation probe, and a second array of heating portions positioned at a second longitudinal position from the tip of the cryoablation probe.

[0021] In another aspect, multiple heating portions can be located in the outer housing of the probe.

[0022] In another aspect, a cryoablation probe can include a cryogen supply and a housing positioned radially outward from the cryogen supply, wherein a plurality of heating portions are configured to operate in an energized state and a de-energized state while cryogen flows from the cryogen supply.

[0023] In some embodiments, a cryoablation apparatus is provided, which may include the cryoablation probe described above and at least one computing device coupled to a plurality of heating portions. The at least one computing device may be configured to compare ice formation data with a predetermined ice formation profile and to activate a heating portion of the plurality of heating portions to restrict ice growth in a first direction relative to a predetermined position on the cryoablation probe while cryogen flows toward the tip of the cryoprobe.

[0024] In one aspect, the at least one computing device may also be configured to modify at least one operating parameter of the cryoablation device. The at least one operating parameter of the cryoablation device may include one of a pressure, a flow rate, and a temperature of the cryogen.

[0025] In some embodiments of the present disclosure, a method of performing a cryoablation treatment may include: initiating a flow of a cryogen to a tip of a cryoprobe and obtaining ice formation data characterizing a shape of ice formed at a target tissue in a patient. The method may also include: comparing the ice formation data to a predetermined ice formation profile and activating a heating portion on the cryoprobe to restrict ice growth in a first direction relative to a predetermined location on the cryoprobe while the cryogen flows to the tip of the cryoprobe.

[0026] In one aspect, the heating portion is a first heating portion, and the method may further include energizing a second heating portion separate from the first heating portion to limit ice growth in a second direction relative to a predetermined position on the cryoprobe while the cryogen flows toward the top of the cryoprobe.

[0027] In another aspect, the heating portion is a first heating portion of a plurality of heating portions, and each heating portion of the plurality of heating portions is positioned circumferentially around the probe at a predetermined distance from a tip of the cryoprobe.

[0028] In another aspect, the step of energizing the heating portion causes growth of an asymmetric ice formation at the target tissue.

[0029] In another aspect, the step of activating the heating portion may be performed when the ice formation data indicates that ice formed at the target tissue is greater than an ice formation target of the ice formation profile.

[0030] In another aspect, ice formation data may be obtained from an imaging device.

[0031] In another aspect, the method may further include deactivating the heating portion when the ice formation data indicates that ice formed at the target tissue is less than an ice formation target of the ice formation profile.

[0032] In another aspect, the step of energizing the heating portion may include applying power according to a predetermined duty cycle.

[0033] In another aspect, the predetermined duty cycle may include a pulse width modulation (PWM) duty cycle.

[0034] In another aspect, the step of energizing the heating portion causes heat to be generated asymmetrically at a desired location on the cryoprobe.

[0035] Further areas of applicability will become apparent from the description provided herein.The description and specific examples in this summary are intended for purposes of illustration only and are not intended to limit the scope of the present disclosure. BRIEF DESCRIPTION OF THE DRAWINGS

[0036] The drawings described herein are for illustrative purposes only of selected embodiments and not all possible implementations, and are not intended to limit the scope of the present disclosure.

[0037] Figure 1 is a diagram illustrating an example cryoablation system according to some embodiments of the present disclosure.

[0038] Figure 2 is a diagram showing an example cryoprobe of the present disclosure that can form the asymmetric ice ball shown.

[0039] Figure 3 is a cross-sectional view of an example cryoprobe of the present disclosure.

[0040] Figure 4 is an illustration of an example heating portion of the present disclosure.

[0041] Figure 5 is an illustration of another example heating portion of the present disclosure.

[0042] Figure 6 is a side view of another example cryoprobe including three arrays of heating sections.

[0043] Figure 7 is a cross-sectional view of another example cryoprobe of the present disclosure.

[0044] Figure 8 is a cross-sectional view of another example cryoprobe of the present disclosure.

[0045] Fig. 9 is a cross-sectional view of another example cryoprobe of the present disclosure.

[0046] Fig.10 is a flow chart illustrating an example method of forming asymmetric ice formations during cryoablation treatment.

[0047] Fig.11 is a flow chart illustrating another example method of forming asymmetric ice formations during cryoablation treatment.

[0048] Fig.12 is a flow chart illustrating another example of forming asymmetric ice formations during cryoablation treatment.

[0049] Fig.13 is a diagram illustrating an example computing device that may be used in conjunction with the apparatus and methods of the present disclosure.

[0050] Corresponding reference numerals indicate corresponding parts throughout the several views of the drawings. DETAILED DESCRIPTION

[0051] Example embodiments will now be described more fully with reference to the accompanying drawings.

[0052] Example embodiments are provided so that the present disclosure will be thorough and will fully convey the scope to those skilled in the art. Many specific details, such as examples of specific components, devices, and methods, are set forth to provide a thorough understanding of the embodiments of the present disclosure. It will be apparent to those skilled in the art that specific details need not be employed, that the example embodiments may be embodied in many different forms, and that they should not be construed as limiting the scope of the present disclosure. In some example embodiments, well-known processes, well-known device structures, and well-known techniques are not described in detail.

[0053] The terms used herein are only used to describe the purpose of specific example embodiments and are not intended to be restrictive. As used herein, the singular forms "one", "an" and "the" may also be intended to include plural forms unless the context clearly indicates otherwise. The terms "include", "comprise", "contain", and "have" are inclusive, and therefore specify the existence of stated features, integral bodies, steps, operations, elements and / or parts, but do not exclude the existence or addition of one or more other features, integral bodies, steps, operations, elements, parts and / or their groups. The method steps, processes and operations described herein should not be interpreted as necessarily requiring them to be performed in the specific order discussed or shown, unless specifically identified as the order of execution. It should also be understood that additional or alternative steps may be adopted.

[0054] When an element or layer is referred to as being "on," "engaged to," "connected to," or "coupled to" another element or layer, it may be directly on, directly engaged to, directly connected to, or directly coupled to another element or layer, or there may be intermediate elements or layers. In contrast, when an element is referred to as being "directly" "on," "directly engaged to," "directly connected to," or "directly coupled to" another element or layer, there may be no intermediate elements or layers. Other words used to describe the relationship between elements should be interpreted in a similar manner (e.g., "between" versus "directly between," "adjacent" versus "directly adjacent," etc.). As used herein, the term "and / or" includes any and all combinations of one or more of the associated listed items.

[0055] Although the terms first, second, third, etc. can be used herein to describe various elements, components, regions, layers and / or sections, these elements, components, regions, layers and / or sections should not be limited by these terms. These terms can only be used to distinguish an element, component, region, layer or section from another region, layer or section. Terms such as "first", "second" and other numerical terms do not imply order or sequence when used in this article unless clearly indicated by context. Therefore, the first element, component, region, layer or section discussed below can be referred to as the second element, component, region, layer or section without departing from the teaching of the exemplary embodiment.

[0056] Spatially relative terms such as "inside", "outside", "below", "below", "lower", "above", "upper", etc. may be used herein to describe the relationship between an element or feature as shown in the figure and another (one or more) element or feature for ease of description. Spatially relative terms may be intended to cover different orientations of the device in use or operation other than the orientation depicted in the figure. For example, if the device in the figure is turned over, the elements described as "below" or "below" other elements or features will be oriented to be "above" other elements or features. Therefore, the example term "below" can cover both the orientation above and below. The device can be oriented in other ways (rotated 90 degrees or in other orientations), and the spatially relative descriptors used herein are interpreted accordingly.

[0057] The devices and methods of the present disclosure can be used in conjunction with a cryoablation device, wherein a cryoablation probe can be inserted into a patient at or near the target tissue. When an appropriate cryogen is delivered to the probe, heat can be removed from the area near the cryoablation probe. When enough heat is removed, ice typically begins to form, thereby lowering the temperature of the target tissue and the area surrounding the cryoablation probe.

[0058] As can be appreciated, it is desirable to ensure that the entire target tissue (e.g., the entire tumor) is destroyed during a cryoablation treatment. To increase the likelihood of this occurring, it may be desirable to form an ice ball that corresponds to the shape of the target tissue. In some cases, the target tissue (e.g., a tumor) may have a substantially symmetrical shape, such as a sphere. However, in other cases, the target tissue may have an irregular or asymmetrical shape. Existing or conventional devices and methods typically produce an ice ball that is symmetrical about the cryoablation probe that produces the ice ball. Therefore, existing or conventional systems are unable to form an asymmetrical ice formation that can correspond to an irregular or asymmetrical target tissue.

[0059] This shortcoming of existing and conventional devices and methods may result in several disadvantages. First, conventional treatments may require the formation of an oversized ice ball in order to ensure that the target tissue is encapsulated within the ice ball to effectively destroy the target tissue. However, an oversized ice ball may subject healthy tissue surrounding the target tissue to freezing temperatures that may have a harmful effect on the healthy tissue. Second, the ice ball may be undersized to avoid subjecting healthy tissue to freezing conditions. Such an undersized ice ball may result in areas of the target tissue not being destroyed during treatment. Additionally, existing and conventional devices and methods do not allow for active control and shaping of ice in multiple directions during cryoablation treatment.

[0060] The apparatus and methods of the present disclosure address these deficiencies by providing an apparatus and method that can form asymmetrically shaped ice during a cryoablation procedure. The apparatus and methods of the present disclosure can also actively monitor, control and / or shape ice during a cryoablation treatment. The apparatus and methods of the present disclosure can activate one or more heating portions in a cryoablation probe while the cryoprobe is being actively cooled using a cryogen. Such control of the heating portions in the cryoablation probe can cause the ice to be shaped in a desired manner to produce an asymmetrical shape and / or to form ice in a shape that corresponds to the target tissue and can avoid healthy tissue.

[0061] Reference now Figure 1 , an example cryoablation system 100 is shown. The cryoablation system 100 may include a cryoablation computing device 102, an intelligent control 104, a plurality of measurement points 106, a pump 108, a cryogen source 110, an inlet valve 112, a cryogen supply 114, and a cryoprobe 128. The pump 108, the cryogen source 110, the inlet valve 112, the cryogen supply 114, and the cryoprobe 128 may be operated to deliver cryogen from the cryogen source 110 to the cryoprobe 128 to perform a cryoablation treatment. The cryogen (e.g., liquid nitrogen) may be stored in a cryogen source 110 (such as a Dewar flask or other suitable container) and then delivered to the cryoprobe 128 via the cryogen supply 114. The cryogen may expand at the tip 122 of the cryoprobe 128 and cool the tip 122 of the cryoprobe 128 to a temperature at which target tissue of the patient 120 begins to freeze, thereby forming an ice ball 118.

[0062] The term ice ball may be used in the present disclosure to describe various types of ice formation that may occur as a result of a cryoablation freezing cycle. Although the term ice ball may be used, it should be understood that the ice formed during a cryoablation treatment may have shapes other than a ball or sphere. The ice ball may be elliptical, or have an irregular or asymmetric shape that may be formed due to ice growth from the cryoprobe 128 in various directions, at different rates, and to different degrees.

[0063] The cryoprobe 128 can be positioned at or near a target tissue (e.g., a tumor) in the patient 120. In this way, the target tissue can be frozen, thereby destroying the target tissue. One or more freezing cycles can be performed to destroy the target tissue. An ice ball 118 can be formed at the target tissue in the patient 120 during the freezing cycle. It is desirable to control and form the ice ball 118 in a predetermined manner so that the ice ball 118 is formed at a desired size, shape, and / or rate so that the target tissue is frozen in the ice ball 118 for a desired period of time. It is also desirable to form the ice ball 118 at a desired size, shape, and / or rate so that healthy tissue or body structures near the target tissue are not damaged by the freezing cycle. For example, it may be desirable to limit the size of the ice ball 118 so that it does not form and freeze healthy tissue.

[0064] A treatment plan may be determined prior to performance of a cryoablation treatment. The treatment plan may detail and / or describe the various steps of the treatment and various aspects of the treatment, such as one or more of the following: the type of equipment to be used, the positioning of the cryoprobe, the temperature of the cryoprobe, the duration of the freeze (and thaw cycles), and the number of cycles. The treatment plan may also include the size, location, shape, growth rate, and / or duration of the ice ball. The treatment plan may be determined by a medical professional and / or by others. As will be further described, the treatment plan may be determined using one or more of the ice formation models created using the methods of the present disclosure.

[0065] In some examples, the cryoablation computing device 102 may determine or recommend a treatment plan after health, patient, and other information is input into the cryoablation computing device 102 or such information is retrieved or otherwise obtained by the cryoablation computing device 102. The cryoablation computing device 102 may be any suitable computing device, such as a workstation, computer, laptop, tablet, server, etc.

[0066] As further shown, the cryoablation system 100 includes an intelligent control 104, which can be coupled to the cryoablation computing device 102, the heating portion 116, and the pump 108. The intelligent control 104 can be any suitable controller, PLC, data acquisition unit, control unit, etc., which can perform the operations described herein. In some examples, the cryoablation computing device 102 and the intelligent control 104 can be combined in a single device. In other examples, they can be separate devices as shown. The intelligent control 104 can be operated to control one or more heating portions 116 on the cryoprobe 128. The heating portion 116 can be excited or de-excited to control the growth of the ice ball 118. The heating portion 116 can be used to form an asymmetric ice ball 118, for example.

[0067] The smart control 104 and / or the cryoablation computing device 102 may also obtain ice formation data or information. The ice formation information may include temperature and / or size information of the ice ball at various times during the freezing cycle. The ice formation information may be obtained from various measurement points. The ice formation information may provide temperature information at predetermined locations to provide information about the growth of ice at the target tissue. The measurement points may include temperature sensors, thermocouples, thermistors, impedance sensors, etc. Such measurement points may be incorporated into the cryoprobe 128 and / or into separate measurement leads.

[0068] The ice formation information may also include imaging data. The imaging data may be obtained from an imaging device such as an X-ray device, a CT scan device, an ultrasound device, an MRI device, etc. The imaging data may provide an indication of the size and / or shape of the ice ball 118 during various stages of the freezing cycle.

[0069] The intelligent control 104 can be operated to obtain ice formation information from the measurement point and provide the information to the cryoablation computing device 102. The cryoablation computing device 102 can then perform various operations to determine the characteristics of the ice formed during the cryoablation treatment. In addition, the cryoablation computing device 102 can perform operations to adjust, change, modify or otherwise control one or more operating parameters of the cryoablation system 100. In some examples, the cryoablation computing device 102 can adjust the cryogen flow provided to the cryoprobe 128 from the cryogen source 110. The cryoablation computing device 102 can be coupled to a pump 108. The pump 108 can be an adjustable, programmable or otherwise controllable pump. The pump 108 can allow the flow rate, flow rate, flow velocity, pressure or other characteristics of the cryogen flow to be modified, controlled or customized. In some examples, the pump 108 can be operated to deliver the cryogen to the cryoprobe 128 in a pulsed manner using pulse width modulation (PWM). In such examples, the pump 108 may be controlled to deliver the cryogen flow at a desired frequency, pulse width, pulse amplitude, or other desired flow characteristics.

[0070] Although not shown, the smart control 104 and / or cryoablation computing device 102 may also be coupled to other information sources. The smart control 104 and / or cryoablation computing device 102 may be coupled to a medical information database that may include information about the patient 120 and / or other clinical treatment processes, etc.

[0071] The disclosed apparatus and methods (including the cryoprobes described further below) are suitable for use in a variety of cryoablation systems, including variations of the cryoablation system 100 described above and other cryoablation systems. The disclosed cryoprobes and associated methods of use may be used, for example, in Joule Thompson (JT) cryoablation systems, liquid phase cooled cryoablation systems, mixed phase cooled cryoablation systems, supercritical phase cooled cryoablation systems, subcritical phase cooled cryoablation systems, and / or other cryoablation systems that may employ other types of cooling effects.

[0072] Reference now Figure 2 , an example cryoprobe 200 is shown. The cryoprobe 200 can be used in the aforementioned cryoablation system 100. The cryoprobe 200 can be used to ablate target tissue during a freezing cycle of a cryoablation treatment. The cryoprobe 200 can include a cryogen supply device configured as a tube or other conduit to deliver cryogen from a cryogen source to a tip 206. The cryogen supply device can be positioned along the central axis of the cryoprobe 200. The housing 202 can form an outer surface of the cryoprobe 200 and can be located radially outside the cryogen supply device. The cryogen can flow back from the tip 206 along a return path, which is defined as a space between the inner surface of the housing 202 and the outer surface of the cryogen supply device. The cryoprobe 200 can also include one or more heating portions 204, which can be positioned at various positions circumferentially around the cryoprobe and at different longitudinal positions relative to the tip 206 of the cryoprobe 200. Each of the heating portions 204 can be coupled to a heating controller 210. The heating portion 204 may be electrically coupled via a physical wired connection or via other connections.

[0073] In operation, the cryoprobe 200 is configured to remove heat from the target tissue of the patient. This operation causes an ice ball 220 to be formed at the target tissue. The ice ball 220 can be formed at an appropriate temperature to destroy the target tissue. The ice ball 220 can be formed to have various temperature boundaries or isotherms. Figure 2 The example shown in shows an ice ball 220 having a first isotherm 222, a second isotherm 224, and a third isotherm 226. The first isotherm 222 may correspond to the outer edge of the ice ball 220 defining a 0°C isotherm. The first isotherm 222 may correspond to a boundary where, for example, the temperature of the ice has reached a temperature of 0°C or less. The second isotherm 224 may be positioned inside the first isotherm 222. The second isotherm 224 may define a temperature boundary where the ice has reached a temperature of -20°C or less. The third isotherm 226 may be positioned inside both the first isotherm 222 and the second isotherm 224. The third isotherm 226 may correspond to a temperature boundary where the ice ball 220 has reached a temperature of -40°C or less.

[0074] It is desirable to position the cryoprobe 200 and form the ice ball 220 in such a manner that the second isotherm 224 and / or the third isotherm 226 are located around the target tissue. It has been observed that tissue is damaged when subjected to temperatures of at least -20°C.

[0075] The heating controller 210 can be a suitable controllable power supply, a PLC or a computing device or a combination thereof that can selectively deliver a power signal to the heating portion 204. The heating controller 210 can activate or deactivate each of the heating portions 204a and 204b independently of each other. The heating controller 210 can activate the heating portions 204a, 204b so that the heating portions generate heat. The heat generated from the heating portions 204a, 204b can in turn limit the growth of ice in areas near the heating portions 204a and / or 204b.

[0076] As the cryogen is dispensed into the cryoprobe 200 and expands at the tip 206, the temperature of the cryogen (e.g., liquid nitrogen) decreases and causes ice to form at the cryoprobe 200. Such ice may be formed generally symmetrically about the cryoprobe 200, at least symmetrically about the central axis of the cryoprobe 200. Thus, the ice ball 220 may be formed in the shape of a sphere or an ellipsoid. However, it may be desirable to limit the growth of the ice in one or more directions relative to the central axis of the cryoprobe 200. To limit the growth, the heating controller 210 may activate one or more of the heating portions 204a, 204b.

[0077] In the example shown, the ice ball 220 has an asymmetric shape. To achieve the shape shown, the heating controller may have activated the heating portion 204a (shown on the lower portion on the cryoprobe 208). The heating portion may generate heat via a resistive heater, a microwave antenna, a radio frequency (RF) heater, a laser heater, etc. This heat may reduce the amount of heat extracted by the probe via the cryogen in a local area near the heating portion 204a. Similarly, the heating controller 210 may activate the heating portion 204b to limit the growth of heat at the upper area of ​​the cryoprobe 200.

[0078] The heating controller 210 can selectively, independently and / or variably energize or actuate the heating portions 204a, 204b to control the growth of ice. The heating controller 210 can control the formation of ice so that an ice ball 220 is formed at a certain size, shape and / or temperature so that the ice ball 220 including the first isotherm 222, the second isotherm 224 and the third isotherm 226 corresponds to the location, size and / or shape of the target tissue (e.g., a tumor). The heating controller 210 can also control the formation of ice so that the size, shape, location and / or temperature of the ice ball 220 minimizes or reduces the harmful effects of ice on healthy tissue that may be located near the target tissue.

[0079] like Figure 3 As shown in , another example cryoprobe 300 may include four heating portions 304a, 304b, 304c, 304d. The heating portions 304 may be positioned and placed circumferentially around the center of the cryoprobe 300. The heating portions 304 may be evenly spaced around the outer surface 302 of the cryoprobe 300. In the example shown, the heating portions are positioned at 90 degree intervals around the periphery of the cryoprobe 300. As previously discussed, when ice is formed at the target tissue, the heating portions 304 may be independently, selectively and / or variably actuated or energized to heat a localized area, thereby locally limiting the growth of ice and forming an asymmetric ice ball.

[0080] The heating portion 304 can be configured in various ways, including as a resistive heater, an RF heater, a laser heater, etc. Figure 4 In one example shown in FIG. 4 , the heating portion 400 can be configured as a resistive heater, wherein a resistive wire 404 can be routed in a heater body 402. The resistive wire can be routed through the heater body 402 in a longitudinally wound manner.

[0081] In such Figure 5 In an alternative example shown in , the heating portion 500 may also include a resistive wire 504 routed through the heater body 502. In this example, the resistive wire 504 may be routed through the heater body in a transversely wound manner. As can be appreciated, the heating portion may also be configured to have other structures to provide localized heating in the cryoprobe.

[0082] The cryoprobe may also be configured to have multiple arrays of heating portions that may be located at different longitudinal positions relative to the tip of the cryoprobe. Figure 6 600. As shown, the cryoprobe 600 may include a first heating array 620 including a plurality of heating portions 606 located around the periphery of the cryoprobe 600. The cryoprobe 600 may also include a second heating array 622. The second heating array 622 may also include a plurality of heating portions 608 located around the periphery of the housing 602 of the cryoprobe 600. The second heating array 622 is located further away from the top 604 than the first heating array 620. The cryoprobe 600 may also include a third heating array 624, which is located further away from the top 604. The third heating array 624 may include a plurality of heating portions 610 located around the periphery of the housing 602.

[0083] The heating portions of each heating array can be independently, selectively, and / or variably operated as previously described to enable control and / or shaping of the puck. Although not shown, each heating portion of the first heating array 620, the second heating array 622, and the third heating array 624 can be individually coupled to a heating controller to provide operation and / or control as previously described.

[0084] Each of the heating portions 606 , 608 , 610 of the first heating array 620 , the second heating array 622 , and the third heating array 624 , respectively, can be positioned in any desired configuration around the housing 602 of the cryoprobe 600 . Figure 7 and Figure 8 Two example configurations of the cryoprobe 600 at one or more cross sections are shown. Figure 7 In FIG. 7 , cross section 700 may include four heating sections 704 evenly positioned about 90 degrees apart around the cryoprobe. Figure 8 As shown in the figure, cross section 800 may include three heating sections 804 located around the housing 802 of the cryoprobe. Each heating array may include the same spacing and / or number of heating sections, or the various heating arrays may have different spacing and / or number of heating sections. In other examples not shown, the heating sections have different spacings, and each array may include more than four heating sections or less than three heating sections.

[0085] exist Fig. 9 900. In this example, cross section 900 shows a cryogen supply 910, which is positioned at the center of the central axis 912 of the cryoprobe. In this example, a heating portion 904 is positioned at intervals within the housing 902 of the cryoprobe. As can be seen, the heating portion can be embedded in the housing 902 so that the heating portion 904 does not extend radially inward from the inner surface 906 of the housing 902. The heating portion 904 also may not extend radially outward from the outer surface 908 of the housing 902. The housing 902 of the cryoprobe 900 can be formed to have such a structure in various ways. In one example, the housing 902 can be formed using 3D printing or additive manufacturing processing to embed the heater structure in the housing 902. For example, during the construction of the cryoprobe, the resistor wire can be deposited as one material and the heater body can be deposited as another material. In other examples, other processes and techniques can be used to construct the cryoprobe 900.

[0086] The previously described cryoprobes and / or heating portions can be used in conjunction with various cryoablation treatments and systems that can use one or more types of cooling to form ice at the target tissue. The cryoprobes and / or heating portions and heating arrays can be used in cryoprobes that utilize Joule-Thompson cooling, liquid phase cooling, mixed phase cooling, supercritical phase cooling, subcritical phase cooling, and / or other cooling treatments.

[0087] Reference now Fig.10 , an example method 1000 for performing a cryoablation treatment is shown. In some embodiments, the method 1000 can be performed using the cryoablation system 100. The method 1000 can also be performed using other cryoablation systems. For the sake of brevity, the method 1000 is described with reference to the cryoablation system 1000. However, it should be appreciated that other cryoablation devices and systems can also be used.

[0088] Method 1000 begins at step 1002. At step 1002, cryoablation computing device 102 may begin processing of a cryoablation treatment. Cryoablation computing device 102 may, for example, obtain preset conditions or obtain other data characterizing the treatment to be performed. Cryoablation computing device 102 may automatically obtain such information, or the information may be input by a medical professional.

[0089] The method 1000 may then proceed to step 1004. At step 1004, the cryoablation computing device 102 may check the status of the cryoablation system 100, including the status and / or position of the cryoprobe 128. The cryoablation computing device 102 may also verify the operating condition of the cryoablation system. The cryoablation computing device 102 may perform step 1004 by obtaining data or information from measurement points, imaging systems, sensors, or other diagnostic devices, which may provide such information to the cryoablation computing device 102.

[0090] At step 1006, the cryoablation computing device can determine whether an anomaly or other problem (e.g., a leak) may be occurring. The cryoablation computing device 102 can determine whether an anomaly exists by comparing the operating conditions of the cryoablation system 100 with predetermined stored values ​​or activation conditions, which can be retrieved from a database or other treatment material. If an anomaly is detected, the method 1000 can proceed to step 1008. At step 1008, the cryoablation computing device 102 delivers a message or other indication to the user of the cryoablation system 100. In response, the medical professional or other user can change the position of the cryoprobe 128 and / or modify or correct the treatment device. The method can return to step 1004 after step 1008.

[0091] If the cryoablation computing device 102 determines that there is no abnormality, the method 1000 can proceed to step 1010. At step 1010, a freezing cycle of the cryoablation treatment can be initiated. To initiate the freezing cycle, the cryoablation computing device 102 can initiate the flow of cryogen to the tip of the cryoprobe 128. The flow of cryogen can be initiated using one or more preset operating conditions, which can characterize the pressure, flow rate, flow rate, temperature, or other parameters of the cryoablation system 100.

[0092] The method 1000 may then proceed to step 1012. At step 1012, the cryoablation computing device 102 may monitor one or more of the following: the size, shape, growth, and other characteristics of the ice ball formed at the cryoprobe 128. For example, the cryoablation computing device 102 may obtain ice formation data characterizing the size, shape, temperature, and / or other characteristics of the ice ball. The cryoablation computing device 102 may obtain the ice formation data from an imaging device, a temperature sensor, an impedance sensor, or other data source.

[0093] At step 1014, the cryoablation computing device 102 may determine whether the ice ball is growing as expected. In some examples, the cryoablation computing device 102 may compare the ice formation data to a treatment plan and / or ice formation profile. The cryoablation computing device 102 may compare the size, location, growth rate, temperature, or other information to target information or threshold information. In some examples, the predetermined target and / or threshold may be obtained from an ice formation model.

[0094] If the ice ball is not growing as expected, the method can proceed to step 1016. At step 1016, the cryoablation computing device can perform operations to adjust, change, or modify the growth of the ice ball. Such operations can include energizing or de-energizing the heating portion of the cryoprobe 128. The cryoablation computing device can also tune the power delivered to the heating portion and / or energize the heating portion according to a predetermined power profile, which can include a pulse width modulation (PWM) profile or can have a desired frequency or other characteristics. Such actions can cause heat to be generated at a local area at the cryoprobe 128 to cause the growth of the ice ball to change. After step 1016, the method 1000 can return to step 1012 to re-execute steps 1012, 1014, as previously described.

[0095] If the ice ball is growing as expected, the method 1000 can proceed to step 1018. At step 1018, the cryoablation computing device 102 can examine all directions of ice ball growth to determine if the ice ball is growing too fast in any direction. Various directions can be established so that the cryoablation computing device 102 can determine the growth characteristics of the ice ball along different directions from the cryoprobe 128. Because the cryoablation system of the present disclosure can enable the growth of an ice ball with an asymmetric profile, the ice ball can grow at different rates along different directions from a predetermined location on the cryoprobe 128. Therefore, the cryoablation computing device can obtain ice formation data in different directions from a common point on the cryoprobe 128.

[0096] By monitoring the size, shape, position, temperature and / or other characteristics of the ice ball during the freezing cycle, the cryoablation computing device can compare the growth rate of the ice ball with a predicted or predetermined growth rate. If the cryoablation computing device 102 determines that the ice ball is growing too fast in one or more directions, the method 1000 can proceed to step 1016. At step 1016, the cryoablation computing device 102 can perform operations to adjust, change and / or reduce the growth of ice in the direction that has been identified as growing too fast. In this case, the cryoablation computing device 102 can excite, adjust or tune the power delivered to the heating portion on the cryoprobe 128 located in the corresponding position. For example, if it is determined that the top of the ice ball is growing too fast, the cryoablation computing device 102 can excite the heating portion located on the top of the cryoprobe 128 to generate heat and slow the growth of ice in that area.

[0097] If the cryoablation computing device 102 determines that the ice ball is not growing too fast in any direction, the method 1000 can proceed to step 1020. At step 1020, the cryoablation computing device 102 determines whether the size or shape of the ice ball meets or corresponds to the expected ice ball size and / or shape. In some examples, when determining the treatment plan, the expected ice ball size and / or shape can be determined. For example, the treatment plan can describe the overall size and / or shape of the ice ball to be produced during the freezing cycle. The overall size and / or shape can be determined, for example, to correspond to the size and / or shape of the target tissue (e.g., a tumor) that is expected to be destroyed. The overall size and / or shape of the ice ball in the treatment plan can also be determined by avoiding healthy tissue or body structures that are located close to the target tissue in the patient's body. The overall size and / or shape of the ice ball in the treatment plan can have an asymmetric shape. That is, the outer edge can have different distances or radii from a common point on the cryoprobe 128 in one or more directions.

[0098] The cryoablation computing device 102 may compare the overall size and / or shape of the puck formed during the freezing cycle with the overall size and / or shape of the puck expected for the treatment plan. The cryoablation computing device 102 may compare, for example, imaging data characterizing the size, shape, and / or position of the puck with the expected size, shape, and / or position of the treatment plan. The size, shape, and / or position of the puck may be compared at various intervals during the freezing cycle.

[0099] If the size, shape, and / or position of the puck does not correspond to the expected size, shape, and / or position of the puck, the method 1000 may proceed to step 1022. At step 1022, the cryoablation computing device 102 may perform operations to adjust, change, and / or modify the size, shape, and / or position of the puck. The cryoablation computing device 102 may energize, de-energize, or modify the power level / profile of one or more heating portions of the cryoprobe 128.

[0100] If the size, shape, and / or position of the puck corresponds to the desired size, shape, and / or position, the method 1000 may proceed to step 1024. At step 1024, the cryoablation computing device 102 may continue the freezing cycle. The cryoablation computing device 102 may continue to flow cryogen to the cryoprobe 128 and may continue to energize, deenergize, and / or otherwise operate the heated portion of the cryoprobe to grow and size the puck to the desired size, shape, and / or position.

[0101] At step 1026, the cryoablation computing device 102 can determine whether the ice ball has achieved the desired size, shape, position and / or duration relative to the target tissue. The final or overall size, shape, position and / or duration can be described in the treatment plan. The cryoablation computing device 102 can compare the size, shape, position and / or duration with the details of the treatment plan. If the size, shape, position and / or duration of the ice ball does not meet the requirements described in the treatment plan or other treatment specifications, the method returns to step 1012 to re-execute steps 1012 to 1026. If the size, shape, position and / or duration of the ice ball meets the requirements, the method 1000 can proceed to step 1028, at which point the method can be completed. As can be appreciated, the method 1000 can be followed by a thawing process, or the method 1000 can be re-executed if the cryoablation treatment includes multiple freezing cycles.

[0102] Reference now Fig.11, another method 1100 of performing a cryoablation treatment is provided. The method 1100 may be performed by the cryoablation device 100. In other examples, other cryoablation devices may be used. For the sake of brevity, the method 1100 is described with reference to the device 100. However, it should be appreciated that other devices and / or systems may also be used.

[0103] Method 1100 is similar in some aspects to method 1000 described previously. Method 1100 can incorporate the use of an ice formation model. The ice formation model can predict the growth of ice during a freezing cycle of a cryoablation treatment based on tissue type, tissue location, patient information, operating conditions of the cryoablation device, and / or other factors. In some examples, an affine ice formation model is used, which can be constructed to predict the growth of ice in multiple directions from a predetermined point on the cryoprobe 128. In other examples, other ice formation models can be used.

[0104] At step 1102, a freezing cycle of a cryoablation treatment may be initiated. For example, the cryoablation computing device 102 may initiate the flow of cryogen to the cryoprobe 128. The cryoablation computing device 102 may initiate the flow using one or more preset operating conditions of the cryoablation system 100. Such preset operating conditions may, for example, describe the flow rate, pressure, temperature, and / or other parameters of the cryogen. The preset operating conditions may also describe the operating conditions of the heating portion of the cryoprobe 128. One or more of the heating portions may be activated to heat an area of ​​the cryoprobe 128, thereby achieving growth of an ice ball in a localized area.

[0105] The method 1100 may proceed to step 1104. At step 1104, the cryoablation computing device 102 may monitor, calculate, quantify, and / or evaluate the ice ball being formed at the target tissue. The cryoablation computing device 102 may obtain ice formation information, which may describe the size, location, temperature, and / or other characteristics of the ice ball being formed at the target tissue. The cryoablation computing device 102 may obtain such information from any suitable data source, such as a database, an imaging device, a temperature sensor, an impedance sensor, etc.

[0106] At step 1106, the cryoablation computing device 102 may determine whether the ice ball growth characteristics match the predicted ice ball growth characteristics of the ice formation model. The cryoablation computing device 102 may compare the ice formation information obtained at step 1104 with the corresponding characteristics of the ice formation model. For example, the ice ball growth rate, ice ball size, ice ball position, etc. may be compared with the corresponding predicted growth rate, size and / or position predicted by the ice formation model. The cryoablation computing device 102 may compare such characteristics with a predetermined threshold or predetermined range that may be provided or obtained from the ice formation model. If the cryoablation computing device determines that the ice ball growth characteristics do not match the predicted ice growth characteristics, the method 1100 may proceed to step 1108.

[0107] At step 1108, the cryoablation computing device 102 may excite or otherwise adjust or modify the operation of one or more heating portions located on the cryoprobe 128. The cryoablation computing device 102 may excite a heating portion located on the cryoprobe 128 at a location corresponding to a location where the ice ball growth characteristics do not match the predicted growth characteristics. In other examples, the cryoablation computing device 102 may adjust the duty cycle provided to the one or more heating portions. Thus, the energy distribution to the (one or more) heating portions may be modified as needed to change the growth of ice in a local area. The cryoablation computing device 102 may also change, modify or adjust other operating characteristics of the cryoablation system 100, such as the pressure, flow rate, flow rate, temperature or other parameters of the cryogen provided to the cryoprobe 128. After performing step 1108, the method 1100 may return to step 1106 to re-perform the above operations.

[0108] If the cryoablation computing device 102 determines that the ice ball growth characteristics match the predicted growth characteristics, the method 1100 can proceed from step 1106 to step 1110. At step 1110, the cryoablation computing device 102 can determine whether the final ice ball growth state and duration have been achieved. As previously described, the freezing cycle of the cryoablation treatment generally describes the desired final size of the ice ball corresponding to the target tissue and the duration of maintaining the final size of the ice ball to destroy the target tissue. The cryoablation computing device 102 can compare the size, shape, position and / or duration to the desired final characteristics of the ice ball. If the ice ball has achieved the desired final size, shape, position and / or duration, the method 1100 can proceed to step 1114, at which the freezing cycle is completed.

[0109] If the puck has not achieved the desired final size, shape, position, and / or duration, method 1100 may proceed to step 1112. At step 1112, the cryoablation computing device may maintain the operating conditions of the cryoablation system 100 and continue the freezing cycle. Method 1100 may then return to step 1104 to re-execute steps 1104 to 1110 as previously described until such time as the cryoablation computing device determines that the final puck characteristics are achieved.

[0110] Method 1100 describes a freeze cycle for a cryoablation treatment. As can be appreciated, method 1100 may be followed by a thaw cycle, or method 1100 may be re-executed a second, third, or other additional times as may be defined in a treatment plan. Method 1100 is an improvement over conventional and existing systems because control and operation of various heating portions on the cryoprobe may allow the cryoablation computing device 102 to control, shape, and / or grow an ice ball having an asymmetric shape.

[0111] Reference now Fig.12 , another example method 1200 for performing a cryoablation treatment is shown. The method 1200 can be used to perform a freezing cycle and grow an ice ball having an asymmetric shape. The method 1200 can be performed using various cryoablation devices and systems such as the cryoablation system 100. For the sake of brevity, the method 1200 is described with reference to the cryoablation system 100. However, it should be appreciated that other cryoablation devices and systems can also be used.

[0112] Method 1200 begins with step 1202. At step 1202, the cryoablation computing device 102 can start the flow of cryogen. For example, the flow of cryogen can be started by opening a valve and allowing cryogen to flow to the top of the cryoprobe 128 to cool the top and start the formation of ice. Although not shown, the cryoprobe 128 is positioned in a predetermined position at the target tissue. This position and other startup information (e.g., initial operating parameters of the cryoablation system 100) can be included as part of the treatment plan that can be obtained by the cryoablation computing device 102. In other examples, a medical professional or other user can input the startup information into the cryoablation computing device 102.

[0113] The method 1200 may then proceed to step 1204. At step 1204, the cryoablation computing device 102 may obtain ice formation data. The ice formation data may describe various characteristics of the ice ball formed at the target tissue. The ice formation data may be obtained, for example, from an imaging device, a sensor, a temperature sensor, and / or an impedance sensor, etc. The ice formation data may characterize the size, temperature, shape, and / or location of the ice ball, among other characteristics.

[0114] At step 1206, the cryoablation computing device 102 may compare the ice formation data to an ice formation profile. The ice formation profile may be provided with or using an ice formation model. The ice formation profile may predict various aspects of the ice ball. For example, the ice formation profile may predict the size, shape, location, growth rate, and / or temperature and other characteristics of the ice ball at various intervals during the freezing cycle. For each characteristic, a target threshold or target range may be provided. At step 1206, the cryoablation computing device 102 may compare the ice formation data characterizing the actual ice ball being formed to the ice formation profile.

[0115] At step 1208, the cryoablation computing device 102 may determine whether one or more characteristics of the actual ice being formed are greater than one or more corresponding characteristics described in the ice formation profile. The cryoablation computing device 102 may compare the value of the one or more characteristics to a predetermined threshold or a predetermined range. If the value is greater than the predetermined threshold or the predetermined range, this may indicate that the ice is growing too fast or has grown too fast. If the cryoablation computing device 102 determines that such a condition exists, the method 1200 may proceed to step 1210.

[0116] At step 1210, the cryoablation computing device may activate the heating portion. The heating portion may generate heat that may reduce the growth of ice and / or slow the growth of ice in the desired location. In other examples, the cryoablation computing device may increase the power level to the heating portion and / or change the duty cycle being delivered to the heating portion. The cryoablation computing device 102 may take any appropriate action to reduce or slow the growth of ice in the desired location. After performing such an action, the method 1200 may return to step 1204 and re-execute steps 1204 to 1208.

[0117] If the cryoablation computing device 102 determines that the ice formed during the freezing cycle is not larger than the ice formation profile, the method 1200 proceeds to step 1212. At step 1212, the cryoablation computing device determines whether the ice formation data indicates that the ice growth is less than the ice growth described in the ice formation profile. The cryoablation computing device 102 can perform operations similar to the operations previously described at step 1208, except that the cryoablation computing device determines whether the ice growth is slower than the predicted ice growth or whether the size of the ice ball is smaller than the size predicted by the ice formation profile. If the cryoablation computing device determines that the ice formation is smaller than the predicted ice formation or has a slower growth rate than the predicted ice formation, the method 1200 can proceed to step 1214.

[0118] At step 1214, the cryoablation computing device 102 can adjust, change, or deactivate one or more heating portions on the cryoprobe 128. Since the cryoablation computing device has determined that the ice is smaller or grows slower than predicted or expected, it is necessary to reduce the heat being introduced by the heating portion. To achieve this, the cryoablation computing device can deactivate the heating portion, change the power level delivered to the heating portion, and / or modify the duty cycle being delivered to the heating portion. The cryoablation computing device 102 can also modify other operating parameters of the cryoablation system 100, such as modifying the pressure, temperature, flow rate, flow rate, or other characteristics of the cryogen. After performing such operations, method 1200 can return to re-execute steps 1204 to 1212.

[0119] If the cryoablation computing device 102 determines that the ice formation is not less than the ice formation described in the ice formation profile, the method can proceed to step 1216, at which time the operating conditions of the cryoablation system 100 are maintained until the ice is formed to the desired size, location, shape, and / or duration. After step 1216, the freezing cycle can end.

[0120] As can be appreciated, if the treatment plan requires multiple freeze cycles, method 1200 can be re-executed, or method 1200 can be followed by a thaw cycle. Method 1200 allows the cryoablation computing device to monitor, control and / or adjust the growth of ice in multiple directions to allow an asymmetric ice ball to be formed at the target tissue. As previously described, the position of the heating portion on the cryoprobe 128 can be energized, de-energized or otherwise controlled to affect the growth of ice at the localized area around the cryoprobe. This control is an improvement over existing and conventional systems.

[0121] Reference now Fig.13 , an example computing device 1300 is shown. The cryoablation system 100 may include one or more computing devices 1300. For example, the cryoablation computing device 102 may have Fig.13 The methods of the present disclosure, such as methods 1000 , 1100 , and 1200 , may be performed by computing device 1300 , or the steps of such methods may be performed by computing device 1300 .

[0122] As shown, computing device 1300 may include one or more processors 1302, a working memory 1304, one or more input / output devices 1306, an instruction memory 1308, a transceiver 1312, one or more communication ports 1314, and a display 1316, all operably coupled to one or more data buses 1310. Data buses 1310 allow communication between the various devices. Data buses 1310 may include wired or wireless communication channels.

[0123] The processor 1302 may include one or more different processors, each of which has one or more cores. Each of the different processors may have the same or different structures. The processor 1302 may include one or more central processing units (CPUs), one or more graphics processing units (GPUs), application specific integrated circuits (ASICs), digital signal processors (DSPs), etc.

[0124] The processor 1302 may be configured to perform a specific function or operation by executing a code embodying the function or operation stored in the instruction memory 1308. For example, the processor 1302 may be configured to perform one or more of any functions, steps, methods, or operations disclosed herein.

[0125] Instruction memory 1308 may store instructions that may be accessed (e.g., read) and executed by processor 1302. For example, instruction memory 1308 may be a non-transitory computer-readable storage medium such as a read-only memory (ROM), an electrically erasable programmable read-only memory (EEPROM), a flash memory, a removable disk, a CD-ROM, any non-volatile memory, or any other suitable memory.

[0126] The processor 1302 may store data to and read data from the working memory 1304. For example, the processor 1302 may store a set of working instructions to the working memory 1304, such as instructions loaded from the instruction memory 1308. The processor 1302 may also use the working memory 1304 to store dynamic data generated during operation of the cryoablation computing device 102. The working memory 1304 may be a random access memory (RAM), such as a static random access memory (SRAM) or a dynamic random access memory (DRAM), or any other suitable memory.

[0127] Input-output device 1306 may include any suitable device that allows data input or output. For example, input-output device 1306 may include one or more of the following: a keyboard, a touch pad, a mouse, a stylus, a touch screen, physical buttons, a speaker, a microphone, or any other suitable input or output device.

[0128] Communication port(s) 1314 may include, for example, a serial port, such as a universal asynchronous receiver / transmitter (UART) connection, a universal serial bus (USB) connection, or any other suitable communication port or connection. In some examples, communication port(s) 1314 allow programming of executable instructions in instruction memory 1308. In some examples, communication port(s) 1314 allow transmission (e.g., upload or download) of data, such as ice formation measurement data.

[0129] The display 1316 may display a user interface 1318. The user interface 1318 may enable a user to interact with the cryoablation computing device 102. For example, the user interface 1318 may be a user interface that allows an operator to interact, communicate, control, and / or modify different messages, settings, or features that may be presented or otherwise displayed to a user. The user interface 1318 may include a slider, a dialog box, or other input fields that allow a user to control, communicate, or modify settings, limitations, or inputs used in cryoablation treatment. In addition, the user interface 1318 may include one or more input fields or controls that allow a user to modify or control optional features or customizable aspects of the cryoablation computing device 102 and / or operating parameters of the cryoablation system 100. In some examples, a user may interact with the user interface 1318 by engaging the input-output device 1306. In some examples, the display 1316 may be a touch screen, wherein the user interface 1318 is displayed on the touch screen. In other examples, the display 1316 may be a computer display that may be interacted with using a mouse or keyboard.

[0130] The transceiver 1312 allows for communication with a network. In some examples, the transceiver 1312 is selected based on the type of communication network in which the cryoablation computing device 102 will operate. The processor(s) 1302 are operable to receive data from or send data to a network, such as a wired or wireless network, that couples the elements of the cryoablation system 100.

[0131] The foregoing description of the embodiments has been provided for the purpose of illustration and description. It is not intended to be exhaustive or to limit the present disclosure. The individual elements or features of a particular embodiment are generally not limited to that particular embodiment, but are interchangeable where applicable and can be used in selected embodiments, even if not specifically shown or described. The individual elements or features of a particular embodiment can also be varied in a variety of ways. Such variations should not be considered as departing from the present disclosure, and all such modifications are intended to be included within the scope of the present disclosure.

Claims

1. A cryoablation probe, comprising: A plurality of heating sections, each heating section of the plurality of heating sections being individually controllable to operate in an energized state and a de-energized state.

2. The cryoablation probe of claim 1, wherein each of the plurality of heating sections comprises a resistive heating element.

3. A cryoablation probe according to claim 1 or claim 2, wherein each of the multiple heating sections is coupled to a heater controller, and the heater controller is configured to change one or more of the multiple heating sections from the de-energized state to the energized state to change the ice growth characteristics of ice formed during a freezing cycle of a cryoablation treatment.

4. A cryoablation probe according to any preceding claim, wherein each of the plurality of heating portions is located at a different peripheral position around a central axis of the cryoablation probe.

5. The cryoablation probe of any preceding claim, wherein each heating portion of the plurality of heating portions is separated from adjacent heating portions.

6. A cryoablation probe according to any preceding claim, wherein the plurality of heating sections comprises: a first array of heating portions positioned at a first longitudinal position from a tip of the cryoablation probe; as well as A second array of heating portions is positioned at a second longitudinal position from the tip of the cryoablation probe.

7. A cryoablation probe according to any preceding claim, wherein the plurality of heating portions are located in an outer housing of the probe.

8. The cryoablation probe according to any preceding claim further comprises a cryogen supply device and a shell positioned radially outside the cryogen supply device, wherein the plurality of heating portions are configured to operate in the energized state and the de-energized state while cryogen flows from the cryogen supply device.

9. A cryoablation device, comprising: The cryoablation probe according to any one of claims 1 to 8; as well as at least one computing device coupled to the plurality of heating portions, the at least one computing device being configured to: comparing the ice formation data to a predetermined ice formation profile; as well as A heating portion of the plurality of heating portions is energized to restrict ice growth in a first direction relative to a predetermined location on the cryoablation probe while cryogen flows toward the tip of the cryoprobe.

10. The cryoablation apparatus of claim 9, wherein the at least one computing device is further configured to: At least one operating parameter of the cryoablation device is modified, the at least one operating parameter of the cryoablation device comprising one of a pressure, a flow rate, and a temperature of a cryogen.

11. A method of performing a cryoablation treatment, comprising: Initiate the flow of cryogen to the tip of the cryoprobe; obtaining ice formation data characterizing a shape of ice formed at a target tissue within a patient; comparing the ice formation data to a predetermined ice formation profile; as well as A heating portion on the cryoprobe is energized to restrict ice growth in a first direction relative to a predetermined location on the cryoprobe while the cryogen flows toward the tip of the cryoprobe.

12. The method of claim 11, wherein the heating portion is a first heating portion, and the method further comprises: A second heating portion separate from the first heating portion is energized to restrict ice growth in a second direction relative to the predetermined location on the cryoprobe while the cryogen flows toward the tip of the cryoprobe.

13. A method according to claim 11 or claim 12, wherein the heating portion is the first heating portion among a plurality of heating portions, and each of the plurality of heating portions is circumferentially positioned around the probe at a predetermined distance from the top end of the cryoprobe.

14. The method of any one of claims 11 to 13, wherein the step of energizing the heating portion causes asymmetric ice formation to grow at the target tissue.

15. The method of any one of claims 11 to 14, wherein the step of activating the heating portion is performed when the ice formation data indicates that ice formed at the target tissue is greater than an ice formation target of the ice formation profile.

16. The method of any one of claims 11 to 15, wherein the ice formation data is obtained from an imaging device.

17. The method according to any one of claims 11 to 16, further comprising: The heating portion is deactivated when the ice formation data indicates that ice formed at the target tissue is less than an ice formation target of the ice formation profile.

18. A method according to any one of claims 11 to 17, wherein the step of energizing the heating portion comprises applying power according to a predetermined duty cycle.

19. The method of claim 18, wherein the predetermined duty cycle comprises a pulse width modulation (PWM) duty cycle.

20. The method of any one of claims 11 to 19, wherein the step of energizing the heating portion causes heat to be generated asymmetrically at desired locations on the cryoprobe.

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