Multi-frequency phase-controlled ultrasonic thermal ablation transducer with adjustable focal region
By using a combination of piezoelectric array and shell in a multi-frequency phased ultrasonic thermal ablation transducer, the ultrasonic focus point and ablation domain are controlled by using excitation frequency and phase, the problem of low accuracy in traditional ultrasonic ablation treatment is solved, and the problem of low accuracy is achieved. Accurate treatment of ovarian cancer.
Patent Information
- Application Number
- CN202411536933.2
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- Filing Date
- 2024-10-31
- Publication Date
- 2025-01-14
AI Technical Summary
The treatment accuracy of ovarian cancer in the prior art is low. Traditional ultrasound ablation treatment has fixed size and shape immobility in the ablation area, which is difficult to accurately control, resulting in the possible accidental injury of surrounding tissues and organs.
A multi-frequency phased ultrasonic thermal ablation transducer with adjustable focus domain is designed. Through the combination of piezoelectric array and shell, the size and shape of the ultrasonic focus point and ablation domain are controlled by different excitation frequencies and phases to achieve the goal of the ultrasonic focus point and ablation domain. Accurate control of the ablation domain.
It realizes precise regulation of the ablation domain, reduces damage to surrounding tissues, improves the accuracy and safety of treatment, and is suitable for tumors of different sizes and shapes.
Smart Images
Figure CN119302711A_ABST
Abstract
Description
Technical Field
[0001] The present disclosure relates to the technical field of tumor thermal ablation therapy, and more specifically, to a multi-frequency phase-controlled ultrasonic thermal ablation transducer with adjustable focal range. Background Art
[0002] The ovaries are located deep in the pelvic cavity and are the female reproductive glands that can produce eggs and secrete estrogen and progesterone, and have reproductive and endocrine functions. When the growth of ovarian cells is out of control, cancer will form, which is called ovarian cancer. Most patients have no obvious initial symptoms and are non-specific in shape. 70% are already in the late stage when they are discovered, and therefore have already spread seriously during treatment. Ovarian cancer is very likely to recur after treatment, with a recurrence rate of up to 85%. In addition, the five-year relative survival rate of patients is less than 45%, and the cure rate is very low, causing serious troubles to women's normal lives.
[0003] In the process of realizing the concept of the present disclosure, the inventors found that there are at least the following problems in the related art: the treatment accuracy of ovarian cancer in the related art is low. Summary of the invention
[0004] In view of this, the present disclosure provides a multi-frequency phase-controlled ultrasonic thermal ablation transducer with adjustable focal range.
[0005] One aspect of the present disclosure provides a multi-frequency phase-controlled ultrasonic thermal ablation transducer with adjustable focal range, comprising a housing and a piezoelectric array;
[0006] Wherein, a supporting surface is provided on one side of the shell, the supporting surface is in an arc shape, and the piezoelectric array is provided on the supporting surface;
[0007] The piezoelectric array includes a plurality of piezoelectric array elements, each of which includes a first resonance zone and a second resonance zone. The piezoelectric array element can cause at least one of the first resonance zone and the second resonance zone to resonate and generate ultrasonic waves under the action of different excitation frequencies, so as to form an ablation zone at the focal point of the ultrasonic wave.
[0008] According to an embodiment of the present disclosure, each of the piezoelectric array elements includes a piezoelectric layer and a backing layer. The piezoelectric layer and the backing layer are made of the same material but have different thicknesses. The backing layer is used to form the first resonance region.
[0009] According to an embodiment of the present disclosure, the piezoelectric array elements are arranged in sequence along the arc surface of the supporting surface, and the distance between two adjacent piezoelectric array elements is the same.
[0010] According to an embodiment of the present disclosure, the housing includes a front housing and a rear housing, and the first surface of the front housing is arc-shaped.
[0011] According to an embodiment of the present disclosure, the first surface of the front shell is provided with a recessed area, and the supporting surface is provided in the recessed area.
[0012] According to an embodiment of the present disclosure, the excitation frequency acts on each of the piezoelectric array elements individually.
[0013] According to an embodiment of the present disclosure, the ultrasonic focusing point position of the transducer is changed based on the ultrasonic electronic phase-controlled focusing principle by adjusting the phase of the excitation frequency acting on each of the piezoelectric array elements.
[0014] According to an embodiment of the present disclosure, the size and shape of the ablation zone at the ultrasound focal point are changed by adjusting the magnitude of the excitation frequency.
[0015] According to an embodiment of the present disclosure, the shell is further provided with a water inlet and a water outlet, the water inlet is used to discharge cooling liquid to cool the piezoelectric array in a working state, and the water outlet is used to discharge the cooling liquid.
[0016] According to an embodiment of the present disclosure, the housing is further provided with a wire outlet for connecting the connecting wires of the piezoelectric array.
[0017] According to an embodiment of the present disclosure, there is provided a multi-frequency phased ultrasonic thermal ablation transducer with adjustable focal range, comprising a shell and a piezoelectric array; wherein a supporting surface is provided on one side of the shell, the supporting surface is in an arc shape, and the piezoelectric array is arranged on the supporting surface; the piezoelectric array comprises a plurality of piezoelectric array elements, each of which comprises a first resonance zone and a second resonance zone, and the piezoelectric array element can make at least one of the first resonance zone and the second resonance zone resonate and generate ultrasonic waves under the action of different excitation frequencies, so as to form an ablation domain at the focal point of the ultrasonic wave, and changing the excitation frequency can generate ablation domains of different sizes and shapes, and changing the excitation phase of the resonance frequency can adjust the position of the focal point based on the ultrasonic electronic phased focusing principle, thereby achieving precise control of the ablation domain. BRIEF DESCRIPTION OF THE DRAWINGS
[0018] The above and other objects, features and advantages of the present disclosure will become more apparent through the following description of the embodiments of the present disclosure with reference to the accompanying drawings, in which:
[0019] Figure 1 A schematic diagram showing the structure of a multi-frequency phase-controlled ultrasonic thermal ablation transducer with adjustable focal range according to an embodiment of the present disclosure;
[0020] Figure 2 A schematic diagram of a piezoelectric array generating ultrasonic waves according to an embodiment of the present disclosure is schematically shown;
[0021] Figure 3 The structure diagram of the piezoelectric array element and the schematic diagram of the partitioned multi-frequency resonance according to the embodiment of the present disclosure are schematically shown;
[0022] Figure 4 A schematic diagram schematically shows the relationship between the excitation frequency and phase of a piezoelectric array element according to an embodiment of the present disclosure;
[0023] Figure 5A The schematic diagram shows the acoustic pressure distribution diagram at the shortest distance between the ablation zone and the transducer;
[0024] Figure 5B The schematic diagram shows the acoustic pressure distribution diagram at the arc geometric focus of the ablation area from the transducer;
[0025] Figure 5C The schematic diagram shows the acoustic pressure distribution at the longest distance of the ablation zone from the transducer;
[0026] Figure 5D The schematic diagram shows the temperature distribution at the shortest distance of the ablation zone from the transducer;
[0027] Figure 5E The schematic diagram shows the temperature distribution of the ablation zone at the arc geometric focus of the transducer;
[0028] Fig. 5F The schematic diagram shows the temperature distribution at the longest distance of the ablation zone from the transducer;
[0029] Figure 5G The schematic diagram shows the distribution of the ablation field at the shortest distance from the transducer;
[0030] Figure 5H The schematic diagram shows the distribution of the ablation domain at the arc geometric focus of the transducer;
[0031] Fig.5I The schematic diagram shows the distribution of the ablation field at the longest distance of the ablation field from the transducer;
[0032] Fig. 6A The schematic diagram shows a schematic diagram of a transducer rotating left and right to perform tumor ablation at a single cross section; and
[0033] Figure 6B The schematic diagram shows the transducer moving up and down to perform tumor ablation in different cross sections. DETAILED DESCRIPTION
[0034] Hereinafter, embodiments of the present disclosure will be described with reference to the accompanying drawings. However, it should be understood that these descriptions are exemplary only and are not intended to limit the scope of the present disclosure. In the following detailed description, for ease of explanation, many specific details are set forth to provide a comprehensive understanding of the embodiments of the present disclosure. However, it is apparent that one or more embodiments may also be implemented without these specific details. In addition, in the following description, descriptions of known structures and technologies are omitted to avoid unnecessary confusion of the concepts of the present disclosure.
[0035] The terms used herein are only for describing specific embodiments and are not intended to limit the present disclosure. The terms "comprise", "include", etc. used herein indicate the existence of the features, steps, operations and / or components, but do not exclude the existence or addition of one or more other features, steps, operations or components.
[0036] All terms (including technical and scientific terms) used herein have the meanings commonly understood by those skilled in the art unless otherwise defined. It should be noted that the terms used herein should be interpreted as having a meaning consistent with the context of this specification and should not be interpreted in an idealized or overly rigid manner.
[0037] When using expressions such as "at least one of A, B, and C, etc.", they should generally be interpreted according to the meaning of the expression commonly understood by those skilled in the art (for example, "a system having at least one of A, B, and C" should include but is not limited to a system having A alone, B alone, C alone, A and B, A and C, B and C, and / or A, B, C, etc.).
[0038] In the embodiments of the present disclosure, the collection, updating, analysis, processing, use, transmission, provision, disclosure, storage, etc. of the data involved (for example, including but not limited to user personal information) are in compliance with the provisions of relevant laws and regulations, are used for legitimate purposes, and do not violate public order and good morals. In particular, necessary measures are taken for user personal information to prevent illegal access to user personal information data and maintain the security of user personal information and network security.
[0039] In the embodiments of the present disclosure, the user's authorization or consent is obtained before obtaining or collecting the user's personal information.
[0040] In the related art, the treatment method of ovarian cancer is usually to make a 15-20cm incision in the abdomen and perform laparotomy to remove the tumor visible to the naked eye. After the tumor reduction surgery, drug chemotherapy is performed to control the primary and metastatic lesions of the tumor. However, the mainstream tumor resection treatment method has many disadvantages: large wounds, slow recovery, and tumor rupture is prone to infection, and it reduces the patient's immune ability and affects postoperative recovery. Chemotherapy drugs will indiscriminately attack body cells, causing a series of side effects that make the survival rate and recurrence rate of ovarian cancer patients not optimistic.
[0041] Thermal ablation for tumor treatment is a treatment technology that destroys tumor cells by generating high temperatures. Its basic principle is to use the biological effect of thermal energy to directly apply high temperatures to tumor tissues, causing tumor cell protein denaturation and DNA coagulation, thereby killing tumor cells.
[0042] Thermal ablation therapy can precisely target tumor tissue and minimize damage to surrounding normal tissue. Compared with traditional surgical procedures, thermal ablation therapy does not require surgery. Instead, it only requires the treatment probe to be introduced into the body through skin puncture, so it is less traumatic and has a quicker recovery. It also has relatively few complications. Thermal ablation technology is applicable to a variety of tumors, especially small tumors. Its operation is repeatable. For advanced tumors, it can alleviate symptoms and prolong survival. Thermal ablation therapy provides a new option for the treatment of ovarian tumors, especially for patients who cannot or are unwilling to undergo surgery. Thermal ablation therapy provides an effective, safe, and minimally invasive treatment method.
[0043] Microwave ablation heats up tumor tissue through dielectric heating under the action of an external electromagnetic field, thereby inactivating tumor cells. The damage to surrounding tissues is small, but due to the long wavelength of microwaves, the ablation domain is generally an ellipsoid, and the controllability of the ablation domain dimension is also limited. Radiofrequency ablation uses the heat generated by radiofrequency current to make the local tissue temperature reach 60-100°C, causing tumor cell protein denaturation and DNA coagulation, thereby inactivating tumor cells. However, patients may need multiple treatments, complications are prone to occur during treatment, and it is not suitable for treating larger tumors. Laser ablation involves thermal, chemical and mechanical effects. For low laser flux, its thermal effect is caused by the absorbed laser energy; the penetration depth of commonly used lasers ranges from 3-8 mm, and the ablation domain is shallower than other methods. Therefore, microwave, radiofrequency, laser and other ablation methods have deficiencies in the controllability of the ablation domain dimension, and it is difficult to adapt to the characteristics of tumor size and shape.
[0044] The principle of ultrasound ablation for the treatment of ovarian cancer is: using ultrasound as a treatment source, effectively utilizing ultrasound's physical properties such as good directionality, penetration and focusability in biological tissues, and physically focusing the ultrasound energy to form a focus, causing the tissue to heat up, destroying cancer cells in the body and causing coagulative necrosis of tumor tissue. In this process, ultrasound images are used to monitor and locate the cancer lesions in real time.
[0045] Traditional ultrasound ablation for ovarian cancer is an in vitro method. Doctors use ultrasound images to determine the location and size of the tumor and determine the treatment plan before treatment. During treatment, doctors guide the ultrasound probe across the body surface, aiming at the tumor tissue, and control the energy and direction of the ultrasound to destroy the tumor tissue and protect the surrounding healthy tissue. Its advantages: patients recover quickly after surgery, reducing many inconveniences in life; ultrasound, as a mechanical wave, is safe and radiation-free to the human body; and this process can be repeated to reduce postoperative complications.
[0046] There are also problems with traditional ultrasound ablation technology for tumors. Ultrasound waves accumulate into a focus, producing an elliptical ablation zone. The focus is transformed from a point to a surface, from a surface to a line, and from a line to a body, eliminating the entire tumor mass. However, since the size of the ablation area is fixed, it may accidentally injure surrounding normal tissues and organs, including blood vessels. In addition, the ovaries are deep in the pelvic cavity, and the ultrasound waves will lose energy before reaching the tumor, which will cause the ablation control to be inaccurate. The inadequacy of ablation control leads to limitations in the traditional ultrasound ablation treatment of ovarian tumors.
[0047] In view of this, an embodiment of the present disclosure provides a multi-frequency phased ultrasonic thermal ablation transducer with adjustable focal range, including a shell and a piezoelectric array; wherein one side of the shell is provided with a supporting surface, the supporting surface is in an arc shape, and the piezoelectric array is provided on the supporting surface; the piezoelectric array includes a plurality of piezoelectric array elements, each of which includes a first resonance area and a second resonance area, and the piezoelectric array element can cause at least one of the first resonance area and the second resonance area to resonate and generate ultrasonic waves under the action of different excitation frequencies, so as to form an ablation domain at the focus point of the ultrasonic wave, and changing the excitation frequency can generate ablation domains of different sizes and shapes, and changing the excitation phase of the resonance frequency can adjust the position of the focus point based on the ultrasonic electronic phased focusing principle. By controlling the resonance area of the piezoelectric array element to generate ultrasonic waves through different excitation frequencies, ablation domains of different sizes and shapes can be generated, thereby achieving precise control of the ablation domain.
[0048] Figure 1 The structure of a multi-frequency phase-controlled ultrasonic thermal ablation transducer with adjustable focal range according to an embodiment of the present disclosure is schematically shown.
[0049] like Figure 1 As shown, a multi-frequency phase-controlled ultrasonic thermal ablation transducer 100 with adjustable focal range includes a housing 110 and a piezoelectric array 120 .
[0050] Among them, a supporting surface 111 is provided on one side of the shell 110, and the supporting surface is arc-shaped, and the piezoelectric array 120 is arranged on the supporting surface 111; the piezoelectric array 120 includes a plurality of piezoelectric array elements 121, and each piezoelectric array element 121 includes a first resonance zone and a second resonance zone. The piezoelectric array element 121 can make at least one of the first resonance zone and the second resonance zone resonate and generate ultrasonic waves under the action of different excitation frequencies, so as to form an ablation domain at the focal point of the ultrasonic wave.
[0051] According to an embodiment of the present disclosure, the supporting surface is configured to be in an arc shape so that the ultrasonic waves generated by the piezoelectric array disposed on the supporting surface can be gathered at a focal point to form an ablation zone.
[0052] According to an embodiment of the present disclosure, by using excitation frequencies of different frequencies, at least one of the first resonance area and the second resonance area of the piezoelectric array element can resonate to generate ultrasonic waves. By adjusting the frequency of the excitation frequency, the size of the ultrasonic wave can be adjusted, thereby changing the size and position of the ablation zone, thereby forming an ablation zone in the target area. The target area can be the area where the tumor is to be eliminated.
[0053] According to the embodiments of the present disclosure, by controlling the resonance region of the piezoelectric array element to generate ultrasonic waves through different excitation frequencies, ablation domains of different sizes and shapes can be generated, thereby achieving precise control of the ablation domain.
[0054] like Figure 1 As shown, the housing 110 includes a front housing 112 and a rear housing 113, and the first surface of the front housing 112 is arc-shaped. The first surface of the front housing 112 is provided with a recessed area, and the supporting surface 111 is provided in the recessed area. The housing 110 is also provided with a water inlet 114 and a water outlet 115. The water inlet 114 is used to discharge cooling liquid to cool the piezoelectric array in the working state, and the water outlet 115 is used to discharge the cooling liquid. The housing 110 is also provided with a wire outlet 116 for connecting the connecting wires of the piezoelectric array. A wiring port is also provided next to the piezoelectric array for connecting the connecting wires of the piezoelectric sheets in the piezoelectric array.
[0055] Figure 2 The schematic diagram of a piezoelectric array generating ultrasonic waves according to an embodiment of the present disclosure is schematically shown.
[0056] like Figure 1 and Figure 2 As shown, the piezoelectric array elements are arranged in sequence along the arc surface of the supporting surface, the number of piezoelectric array elements is schematically 8, and the distance between two adjacent piezoelectric array elements is the same. The piezoelectric elements are equidistantly and tangentially arranged on the same arc line, and the emitted ultrasonic waves can be focused at one point.
[0057] Figure 3 The structure diagram of the piezoelectric array element and the schematic diagram of the partitioned multi-frequency resonance according to the embodiment of the present disclosure are schematically shown.
[0058] like Figure 3 As shown, the piezoelectric array element 320 includes a first resonance area S1 and a second resonance area S2, and each piezoelectric array element 320 includes a piezoelectric layer 321 and a backing layer 322. The thickness of the piezoelectric layer 321 and the backing layer 322 are different, and the backing layer 322 is used to form the first resonance area. The piezoelectric layer and the backing layer are made of the same material, both of which are piezoelectric sheets.
[0059] According to the embodiments of the present disclosure, since the piezoelectric array element is polarized in the thickness direction, Figure 3 (A) is the admittance-frequency characteristic diagram of the transducer. When the excitation frequency is the resonance frequency f1 of the first resonance area S1, Figure 3 In (B), the first resonance area S1 of the piezoelectric element of the transducer resonates, releases ultrasound, and produces an ablation domain; when the excitation frequency is the resonance frequency f2 of the second resonance area S2, Figure 3 In (C), the second resonance area S2 of the piezoelectric element of the transducer resonates, releases ultrasound, and produces a second ablation domain; when the excitation frequency is the resonance frequency f3 of the third resonance area, Figure 3 In (B), the first resonance zone of the piezoelectric element of the transducer generates high-frequency resonance, releases ultrasonic waves, and generates the third ablation domain. By utilizing the approximately proportional relationship between the acoustic attenuation of biological tissue and the ultrasonic frequency, low-frequency ultrasonic waves penetrate deeply into the tissue and have a deep ablation domain, while high-frequency ultrasonic waves penetrate shallowly into the tissue and have a shallow ablation domain. Therefore, the depth of the first ablation domain is deeper than that of the third ablation domain, and the excitation frequency is then used to achieve regulation of the ablation depth. The ablation area is controlled by exciting the local resonance of the first and second resonance zones of the array element and driving with a multi-frequency modulated signal. The eight array elements of the ultrasonic transducer are individually controlled, and the size and shape of the ablation domain can be flexibly adjusted and controlled.
[0060] Figure 4 The diagram schematically shows the relationship between the excitation frequency and phase of the piezoelectric array element according to an embodiment of the present disclosure.
[0061] like Figure 4 As shown, the excitation frequency acts on each piezoelectric array element individually. By adjusting the phase of the excitation frequency acting on each piezoelectric array element, the position of the ultrasonic focus point of the transducer is changed based on the ultrasonic electronic phase-controlled focusing principle. By adjusting the magnitude of the excitation frequency, the size and shape of the ablation zone at the ultrasonic focus point are changed.
[0062] Figure 5A The schematic diagram shows the acoustic pressure distribution at the shortest distance from the ablation zone to the transducer. Figure 5B The schematic diagram shows the acoustic pressure distribution diagram at the arc geometric focus of the ablation zone from the transducer. Figure 5C The schematic diagram shows the acoustic pressure distribution at the longest distance of the ablation zone from the transducer. Figure 5DThe schematic diagram shows the temperature distribution of the ablation zone at the shortest distance from the transducer. Figure 5E The schematic diagram shows the temperature distribution of the ablation zone at the circular arc geometric focus of the transducer. Fig. 5F The schematic diagram shows the temperature distribution of the ablation zone at the longest distance from the transducer. Figure 5G The schematic diagram shows the distribution of the ablation zone at the shortest distance from the transducer. Figure 5H The schematic diagram shows the distribution of the ablation zone at the arc geometric focus of the transducer. Fig.5I The schematic diagram shows the distribution of the ablation zone at the longest distance of the ablation zone from the transducer.
[0063] Depend on Figure 5A to Figure 5I It can be seen that the transducer proposed in the embodiment of the present disclosure can achieve the position movement of the focus of the ablation field, as well as the change of the size and shape.
[0064] Fig. 6A The schematic diagram shows the transducer rotating left and right to perform tumor ablation at a single cross section.
[0065] Figure 6B The schematic diagram shows the transducer moving up and down to perform tumor ablation in different cross sections.
[0066] like Fig. 6A and Figure 6B As shown in the figure, the ultrasonic transducer rotates left and right to control the movement of the ablation domain in a plane; the ultrasonic transducer moves up and down, east and west to control the movement of the ablation domain from plane 1 to plane 2. It can be seen that the transducer can realize the regulation of the ablation domain in three dimensions.
[0067] According to the embodiments of the present disclosure, the transducer in the present disclosure can realize three-dimensional control of the ablation domain by switching the resonance frequency and the phase difference between each piezoelectric array element, and the transducer has the characteristics of precise ablation, simple structure and convenient control.
[0068] The flowcharts and block diagrams in the accompanying drawings illustrate the possible implementation architecture, functions and operations of the systems, methods and computer program products according to various embodiments of the present disclosure. In this regard, each box in the flowchart or block diagram may represent a module, a program segment, or a part of a code, and the above-mentioned module, program segment, or a part of the code contains one or more executable instructions for implementing the specified logical function. It should also be noted that in some alternative implementations, the functions marked in the box may also occur in an order different from that marked in the accompanying drawings. For example, two boxes represented in succession can actually be executed substantially in parallel, and they can sometimes be executed in the opposite order, depending on the functions involved. It should also be noted that each box in the block diagram or flowchart, and the combination of boxes in the block diagram or flowchart, can be implemented with a dedicated hardware-based system that performs a specified function or operation, or can be implemented with a combination of dedicated hardware and computer instructions. It can be understood by those skilled in the art that the features recorded in the various embodiments of the present disclosure can be combined and / or combined in a variety of ways, even if such a combination or combination is not explicitly recorded in the present disclosure. In particular, without departing from the spirit and teaching of the present disclosure, the features described in the various embodiments of the present disclosure may be combined and / or combined in a variety of ways. All of these combinations and / or combinations fall within the scope of the present disclosure.
[0069] The embodiments of the present disclosure are described above. However, these embodiments are only for illustrative purposes and are not intended to limit the scope of the present disclosure. Although the embodiments are described above, this does not mean that the measures in the various embodiments cannot be used in combination to advantage. Without departing from the scope of the present disclosure, those skilled in the art may make a variety of substitutions and modifications, which should all fall within the scope of the present disclosure.
Claims
1. A multi-frequency phase-controlled ultrasonic thermal ablation transducer with adjustable focal range, comprising a housing and a piezoelectric array; in, A supporting surface is provided on one side of the shell, the supporting surface is in an arc shape, and the piezoelectric array is provided on the supporting surface; The piezoelectric array includes a plurality of piezoelectric array elements, each of which includes a first resonance area and a second resonance area. The piezoelectric array element can cause at least one of the first resonance area and the second resonance area to resonate and generate ultrasonic waves under the action of different excitation frequencies, so as to form an ablation zone at the focus point of the ultrasonic waves.
2. The thermal ablation transducer according to claim 1, wherein: Each of the piezoelectric array elements includes a piezoelectric layer and a backing layer. The piezoelectric layer and the backing layer are made of the same material but have different thicknesses. The backing layer is used to form the first resonance region.
3. The thermal ablation transducer according to claim 2, wherein: The piezoelectric array elements are arranged in sequence along the arc surface of the supporting surface, and the distance between two adjacent piezoelectric array elements is the same.
4. The thermal ablation transducer according to claim 1, wherein: The housing comprises a front housing and a rear housing, and the first surface of the front housing is in an arc shape.
5. The thermal ablation transducer according to claim 4, wherein: The first surface of the front shell is provided with a recessed area, and the supporting surface is provided in the recessed area.
6. The thermal ablation transducer according to any one of claims 1 to 5, wherein: The excitation frequency acts on each of the piezoelectric array elements individually.
7. The thermal ablation transducer according to claim 6, wherein: By adjusting the phase of the excitation frequency acting on each piezoelectric array element, the position of the ultrasonic focusing point of the transducer is changed based on the ultrasonic electronic phase-controlled focusing principle.
8. The thermal ablation transducer according to any one of claims 1 to 5, wherein: The size and shape of the ablation area at the ultrasound focal point are changed by adjusting the magnitude of the excitation frequency.
9. According to the thermal ablation transducer according to any one of claims 1 to 5, the shell is also provided with a water inlet and a water outlet, the water inlet is used to discharge cooling liquid to cool the piezoelectric array in a working state, and the water outlet is used to discharge the cooling liquid.
10. The thermal ablation transducer according to any one of claims 1 to 5, wherein: The housing is also provided with a wire outlet for connecting the connecting wires of the piezoelectric array.