A Miniaturized Ridged-Waveguide Hyperthermia Antenna and Hyperthermia Equipment

Abstract

The present invention relates to the technical field of hyperthermia antennas, and particularly relates to a miniaturized ridged waveguide hyperthermia antenna and a hyperthermia device; it includes a probe and a radiation cover body for connecting with an external hyperthermia device, and a unilateral opening structure for fitting against the patient's skin is formed on the radiation cover body; the probe is arranged in the radiation cover body through a fixing column and is close to the opening side of the radiation cover body; an antenna ridge is arranged between the two fixing columns, and the antenna ridge is fixed in the radiation cover body.

Description

Technical Field

[0001] The present invention relates to the technical field of hyperthermia antennas, and particularly relates to a miniaturized ridged waveguide hyperthermia antenna and a hyperthermia device. Background Art

[0002] At present, microwave hyperthermia has gradually become an important technology for treating tumors. The most important part of microwave hyperthermia technology is the design of the hyperthermia antenna, which plays a key role in the treatment range, treatment time, impact on normal tissues, and system stability. The external radiator irradiates the diseased tissues of the human body, using the unique physical properties of microwaves, namely the biological thermal effect and non-thermal effect. Since tumor cells contain a large amount of water, when the microwave hyperthermia antenna irradiates the tumor cells and the tumor cells absorb microwaves and produce a thermal effect, when the intracellular temperature reaches above 42°C, the replication of RND and the reverse transcription of DNA in the tumor cells will be inhibited, which will greatly damage the tumor cells and cause the death of the tumor cells.

[0003] The frequencies used in medical external microwave hyperthermia systems are generally 433 MHz, 915 MHz, and 2450 MHz, which have a great impact on the penetration effect of microwaves. The penetration depth of microwaves at 2450 MHz is 1 - 2 cm, but the diathermy depth at 915 MHz can reach 9 cm. At the same time, the volume of the antenna will increase exponentially with the decrease of the frequency. Most of the existing antennas for external hyperthermia are large antennas, and their sizes are generally above 200 mm. For example, a rectangular cavity microwave physiotherapy radiator with the application number 202010811835.0 is used for microwave hyperthermia, and the length range of its action surface is 340 mm - 400 mm, and the value range of the width b is 130 mm - 180 mm, which is a large external hyperthermia antenna in the prior art. For example, a magnetic excitation 915 MHz circular waveguide radiator with the application number 202010629042.7 has an inner diameter of 160 mm and an inner cavity length of 140 mm. This application further reduces the size range of the antenna on the basis of the existing large antennas.

[0004] The infiltration depth and the maximum diameter line of different cancer cells are also different. For example, the infiltration depth of cervical cancer is 5 mm, and the maximum diameter line is 2 cm. Another example is that breast cancer is mostly located in the upper outer quadrant of the breast, followed by the upper inner quadrant and the middle part. The tumors are mostly round or oval, with different sizes, and usually 2 - 3 cm masses are more common; and they generally grow deep in the breast. The sizes of the existing microwave hyperthermia antennas are much larger than those of some superficial small tumors. Directly using large hyperthermia antennas for hyperthermia will irradiate normal cells over a large area, and long-term irradiation will damage normal cells. Therefore, it is necessary to miniaturize the hyperthermia antenna.

[0005] If the existing hyperthermia antenna is reduced proportionally, its center frequency remains unchanged, and other influencing factors in the antenna volume calculation formula are fixed values. Therefore, when the antenna size becomes smaller, it will inevitably lead to deterioration of its S11 and SAR diagrams, thus failing to meet the actual usage requirements. Summary of the Invention

[0006] In order to solve the technical problems existing in the prior art, such as the large volume of the hyperthermia antenna, which cannot meet the miniaturization requirements for the treatment of superficial tumors, the present invention provides a miniaturized ridged waveguide hyperthermia antenna and a hyperthermia device, aiming to provide a miniaturized hyperthermia antenna with a small volume and a hyperthermia effect close to that of a large hyperthermia antenna.

[0007] The technical solution used in the present invention is as follows: A miniaturized ridged waveguide hyperthermia antenna includes a probe and a radiation cover body for connecting with an external hyperthermia device. A unilateral opening structure for fitting against the patient's skin is formed on the radiation cover body; the probe is arranged in the radiation cover body through a fixing column and is close to the opening side of the radiation cover body; an antenna ridge is arranged between two fixing columns, and the antenna ridge is fixed in the radiation cover body.

[0008] Further, the probe is a connector for electrically connecting with an external radio frequency end device, and the connector is fixed to the outer edge of the radiation cover body through a locking member.

[0009] Further, the fixing column is a plate-like structure in the shape of a rectangular cuboid, and one side of it is fixed to the bottom of the radiation cover body; one of the fixing columns is close to the opening side and has a semi-circular card slot for clamping the probe; one of the fixing columns is close to the opening side and is provided with a receiving groove for receiving the inner metal conductor of the probe.

[0010] Further, the radiation cover body has a circular cross-section.

[0011] Further, the radiation cover body includes an antenna wall and an antenna cover, and the antenna cover is fixed to the antenna wall through a locking member such as a bolt.

[0012] Further, the antenna ridge is fixed to the antenna cover.

[0013] Further, there is a fitting gap between both sides of the antenna ridge and the two fixing columns, and the fitting gap is 0.1 mm - 0.2 mm.

[0014] Further, the radius of the radiation cover body is 19 mm and the height is 36 mm; the antenna ridge is a rectangular block structure with a length of 30 mm, a width of 20 mm, and a height of 28 mm; the length of the probe is 42 mm.

[0015] A hyperthermia device, characterized in that: it includes a radio frequency end and the miniaturized waveguide hyperthermia antenna as claimed in claim 1, and the radio frequency end is connected to the miniaturized waveguide hyperthermia antenna.

[0016] The beneficial effects achieved by the present invention are as follows: Microwave energy can be input through a coaxial input line. At an appropriate treatment time and a center frequency of 915 MHz, effective treatment can be carried out on superficial tumors about 0 - 9 cm below the epidermis. From the test echo loss diagram, it can be seen that the echo loss is about -12.690 dB at 915 MHz, indicating a relatively high antenna effectiveness. It can be known from this that the fixed column and the antenna ridge of the extracorporeal microwave hyperthermia antenna provided by the present invention jointly constitute an antenna ridge with a special structure, enabling the antenna to have no special requirements for the external environment and can be directly used in the air. While ensuring its small size, it can emit radiation energy close to that of a large waveguide hyperthermia antenna. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] Figure 1 It is a schematic diagram of S11 after HFSS simulation of a common waveguide antenna.

[0018] Figure 2 It is a SAR diagram of a common waveguide hyperthermia antenna.

[0019] Figure 3 It is a schematic diagram of S11 after HFSS simulation of a common waveguide antenna scaled down in the same proportion.

[0020] Figure 4 It is a SAR diagram of a common waveguide hyperthermia antenna scaled down in the same proportion.

[0021] Figure 5 It is a schematic diagram of the overall structure of the present invention.

[0022] Figure 6 It is a schematic diagram of the sectional structure of the present invention.

[0023] Figure 7 It is a schematic diagram of the fixed column structure of the present invention.

[0024] Figure 8 It is a schematic diagram of the radiation cover structure of the present invention.

[0025] Figure 9 It is a schematic diagram of S11 after HFSS simulation of the small waveguide hyperthermia antenna of the present invention.

[0026] Figure 10 It is a SAR diagram of the small waveguide hyperthermia antenna of the present invention.

[0027] Figure 11 It is a schematic diagram of the size of the small waveguide hyperthermia antenna of the present invention.

[0028] Figure 12 It is an electric field distribution diagram of the present invention.

[0029] Figure 13 It is a comparison diagram of S11 showing the influence of the length of the antenna ridge of the present invention on the waveguide hyperthermia antenna.

[0030] Figure 14 It is a comparison diagram of S11 showing the influence of the width of the antenna ridge of the present invention on the microwave hyperthermia antenna.

[0031] Figure 15 It is a comparison diagram of S11 showing the influence of the height of the antenna ridge of the present invention on the microwave hyperthermia antenna.

[0032] Figure 16 It is a comparison diagram of S11 showing the influence of the length of the probe of the present invention on the microwave hyperthermia antenna.

[0033] Figure 17 It is a schematic diagram of the physical object of the present invention.

[0034] Figure 18 It is a schematic diagram of the physical construction of the miniaturized microwave hyperthermia antenna of the present invention.

[0035] Figure 19 Figure a is a diagram of the experimental environment for performing the phantom test, and figure b is the phantom after feeding 20 W of energy for heating for 30 minutes.

[0036] Figure 20 It is a schematic diagram of the change in the temperature of the phantom after different heating times of the present invention.

[0037] In the figure, 1 is the probe; 2 is the radiation cover body; 3 is the fixing column; 4 is the card slot; 5 is the accommodating groove; 6 is the antenna ridge; 7 is the connector; 8 is the antenna wall; 9 is the antenna cover. Specific Embodiments

[0038] To facilitate the understanding of the present invention by those skilled in the art, the specific embodiments of the present invention will be described below with reference to the accompanying drawings.

[0039] In the description of the present invention, it should be noted that unless otherwise clearly defined and limited, the terms "mounted", "connected" and "connected" should be understood in a broad sense. For example, it may be a fixed connection, a detachable connection, or an integral connection; it may be a mechanical connection or an electrical connection; it may be directly connected or indirectly connected through an intermediate medium, and it may be the communication inside two elements; for those of ordinary skill in the art, the specific meanings of the above terms in the present invention can be understood through specific situations.

[0040] First, the application scenario of the present application will be introduced: the invasion depth and the maximum diameter line of different cancer cells are also different; the size of the existing microwave hyperthermia antenna is much larger than the size of some superficial small tumors; directly using a large hyperthermia antenna for hyperthermia will irradiate normal cells over a large area. The existing ordinary microwave hyperthermia antenna includes a horn-shaped cover, and a coaxial line is arranged in the middle, with a radius of 100 mm and a height of 110 mm. Figure 1 、Figure 2 The S11 and SAR diagrams after HFSS simulation of the ordinary waveguide antenna. At 915 MHz, its S11 is -16.690 dB, and the highest SAR value is 45 W / kg. To meet the miniaturization requirements, the above ordinary waveguide antenna was scaled down proportionally. The radius of the scaled-down ordinary waveguide hyperthermia antenna is 19 mm and the height is 21 m. Figure 3 The S11 diagram after HFSS simulation of the scaled-down ordinary waveguide hyperthermia antenna. At the frequency point of 915 MHz, all the fed energy will return along the original path, and no energy acts on the skin. Figure 4 The SAR diagram of the scaled-down ordinary waveguide hyperthermia antenna also verifies this point. The SAR value is close to 0, and the heat cannot reach 45 °C no matter how long it is heated.

[0041] As Figures 5-6 shown, the present invention provides a miniaturized ridged waveguide hyperthermia antenna, which includes a probe 1 and a radiation cover 2. The radiation cover 2 is a cover structure with a single-sided opening, and the opening of the radiation cover 2 is used to fit against the patient's skin; the probe 1 is arranged in the radiation cover 2 through a fixing column 3 and is close to the opening side of the radiation cover 2; as Figure 7 shown, the two fixing columns 3 are in the shape of rectangular parallelepiped plates. One side of them is fixed to the bottom of the radiation cover 2 through a locking member. One of the fixing columns 3 is close to the opening side and has a semi-circular groove 4 for clamping the probe 1; one of the fixing columns 3 is close to the opening side and is provided with a receiving groove 5 for receiving the inner metal conductor of the probe 1. The fixing column 3 is used to fix the probe 1 and also serves as an auxiliary ridge to reflect and superimpose the fed energy. Figure 6 shown, an antenna ridge 6 is arranged between the two fixing columns 3. The antenna ridge 6 is fixed in the radiation cover 2, and there is a fitting gap between both sides of the antenna ridge 6 and the two fixing columns 3. The fitting gap is 0.1 mm - 0.2 mm; the radiation cover 2, the fixing column 3, and the antenna ridge 6 are all made of metal, preferably aluminum alloy; a connector 7 is provided at the input end of the probe 1. Through the connector 7, it can be electrically connected to the external radio frequency terminal device, and the probe 1 is used to realize the transmission connection between the miniaturized waveguide hyperthermia antenna and the frequency terminal device, and the probe 1 is used for feeding; the connector 7 is fixed to the outer edge of the radiation cover 2 through a locking member; the connector 7 can be an SMA connector 7. The probe 1 includes an inner metal conductor made of copper and an outer sleeve made of polytetrafluoroethylene. Specifically, the input end of the inner metal conductor is connected to the probe end of the SMA connector 7, and the output end of the inner metal conductor is connected to the fixing column 3.

[0042] A waveguide antenna is an antenna that guides radio frequency energy from the air medium into the waveguide. The cut-off frequency of the waveguide antenna plays a crucial role in the transmission of energy. The function of the radiation cover 2 is to reduce the energy spillage. After the energy is reflected by the antenna wall 8, the energy is injected into the skin. By the reflection and superposition of the waves, the energy intensity injected into the skin is increased. The radiation cover 2 can be of any structure with a single-sided opening, and it can have a rectangular cross-section or a circular cross-section; the volumes of the rectangular cross-section and the circular cross-section are not the same at the same frequency. The calculation formula for converting the circular cross-section to the rectangular cross-section is:

[0043]

[0044] where, R is the radius of the circular cross-section, a is the length of the rectangular cross-section, and b is the width of the rectangular cross-section;

[0045] It can be seen from the formula that at the same frequency, the diameter of the circular waveguide is times the length of the rectangular waveguide; the cut-off frequency of the waveguide antenna plays a crucial role in the transmission of energy. The larger the radius of the radiation cover 2, the larger the wavelength, and the smaller the cut-off frequency, so the energy intensity injected into the skin is lower; for the miniaturized waveguide antenna, the circular radiation cover 2 is preferably selected in the choice of the waveguide shape.

[0046] As Figure 8 shown, the radiation cover 2 can be an integrally formed cover structure; in another embodiment, the radiation cover 2 includes an antenna wall 8 and an antenna cover 9, and the antenna cover 9 is fixed to the antenna wall 8 through locking parts such as bolts; the antenna ridge 6 can be integrally formed with the antenna cover 9. Of course, the antenna cover 9 and the antenna ridge 6 can also be a split structure and are fixed to the antenna cover 9 through locking parts such as bolts.

[0047] The present invention selects a center frequency of 915 MHz, further deepens the reduction range of the antenna by using the hybrid miniaturization technology, and while adding a ridge to the antenna, a probe is added to reduce the radius of the radiation cover 2 to 19 mm (the radius of the existing antenna is greater than 200 mm). This antenna adopts a waveguide form. Through the radiation cover 2, the energy spillage is reduced and the energy radiated by the probe 1 is reflected to the human body, which is superposed with the energy directly radiated to the human body. At the same time, the energy radiated inside the antenna bounces in all directions and is reflected when hitting the antenna wall or the added ridge. Part of the reflected energy is superposed with the previous energy on the skin, and the other part continues to be reflected until 90% of the fed energy acts on the human body and 10% returns along the coaxial line in the continuous reflection. Therefore, there are no special requirements for external conditions and it can be directly used in the air; it ensures that it has a small size while maintaining performance.

[0048] Embodiment 1

[0049] As Figure 11As shown, a miniaturized ridged waveguide hyperthermia antenna uses a radiation cover 2 with a circular cross-section, having a radius (L3) of 19 mm and a height (L1) of 36 mm; the length (L4) of the antenna ridge 6 is 30 mm, the width is 20 mm, and the height (L2) is 28 mm; the length (L5) of the probe 1 is 42 mm; the HFSS simulation model of this waveguide hyperthermia antenna is as Figure 9 shown, and its S11 at 915 MHz is -12.690 dB; Figure 10 The SAR diagram of the miniaturized waveguide hyperthermia antenna also verifies this, with the SAR value being 45.387 W / kg; for the waveguide hyperthermia antenna, with a center frequency of 915 MHz, when S11 is below -10 dB, it meets the usage requirements. Therefore, the waveguide hyperthermia antenna of this application has achieved the engineering requirements in terms of antenna performance while reducing the volume, and has the advantages of small volume, light weight, and flexible treatment range compared with ordinary waveguides, while having the advantages of more concentrated energy, low return loss, high SAR value, and being able to meet the actual requirements compared with the waveguide antenna after being scaled down proportionally;

[0050] At the same time, as shown in the figure, HFSS can automatically calculate the antenna SAR value after simulation. In the present invention, the SAR diagram is obtained after inputting energy through the SMA head. Part of the energy is radiated towards the skin, and part of it enters the antenna wall 8. The energy is reflected by the antenna wall 8 and the ridge and then radiated into the skin, and the simulated SAR diagram is achieved through the reflection and superposition of waves. Figure 12 The electric field distribution diagram is shown. The energy is radiated into the radiation cover 2 of the antenna from all directions through the probe, and then reflected and superposed.

[0051] Experiment 1

[0052] Study the influence of the length of the antenna ridge 6 on the miniaturization of the waveguide hyperthermia antenna

[0053] The radius of the radiation cover 2 is 19 mm and the height is 36 mm; the width of the antenna ridge 6 is 20 mm and the height is 28 mm; the length of the probe 1 is 42 mm; the length of the antenna ridge 6 is set to 2 mm, 4 mm, 8 mm, 10 mm, 16 mm, 24 mm, and 30 mm respectively for HFSS simulation calculation, and the comparison of its S11 is as Figure 13 shown. At 915 MHz, 30 mm meets the actual usage requirements.

[0054] Experiment 2

[0055] Study the influence of the width of the antenna ridge 6 on the miniaturization of the waveguide hyperthermia antenna

[0056] The radius of the radiation cover 2 is 19 mm and the height is 36 mm; the length of the antenna ridge 6 is 30 mm and the height is 28 mm; the length of the probe 1 is 42 mm; after setting the widths of the antenna ridge 6 to 1.5 mm, 7.5 mm, 9 mm, 10.5 mm, 15 mm, and 20 mm respectively, the S11 after HFSS calculation and simulation is compared as Figure 14 shown. At 915 MHz, the width of the antenna ridge 6 of 20 mm meets the actual usage requirements.

[0057] Experiment Three

[0058] Study the influence of the height of the antenna ridge 6 on the miniaturization of the microwave hyperthermia antenna

[0059] The radius of the radiation cover 2 is 19 mm and the height is 36 mm; the length of the antenna ridge 6 is 30 mm and the width is 20 mm; the length of the probe 1 is 42 mm; after setting the heights of the antenna ridge 6 to 2 mm, 4 mm, 8 mm, 12 mm, 16 mm, 20 mm, and 28 mm respectively, the S11 after HFSS calculation and simulation is compared as Figure 15 shown. At 915 MHz, the height of the antenna ridge 6 of 28 mm meets the actual usage requirements.

[0060] Experiment Four

[0061] Study the influence of the length of the probe 1 on the miniaturization of the microwave hyperthermia antenna

[0062] The radius of the radiation cover 2 is 19 mm and the height is 36 mm; the length of the antenna ridge 6 is 30 mm, the width is 20 mm, and the height is 28 mm; after adjusting the lengths of the probe 1 to 15 mm, 20 mm, 25 mm, 30 mm, 36 mm, 38 mm, 40 mm, and 42 mm for simulation, the S11 after HFSS calculation and simulation is compared as Figure 16 shown. Only the two lengths of 42 mm and 30 mm meet the actual engineering requirements. At 42 mm, the lowest point of S11 is at 915 MHz; at 30 mm, the lowest point of S11 is at 3200 MHz; if the lowest point of its S11 is to be at 915 MHz, it needs to be enlarged by 3.49 times as a whole; considering miniaturization, the coaxial cable length of 42 mm is selected as the probe length of the present invention.

[0063] Embodiment Two

[0064] As Figures 17-18As shown, a physical setup of the miniaturized microwave hyperthermia antenna is carried out. Due to the influence of various factors, the actual antenna performance will be different from the simulation experiment. A physical setup is built for performance evaluation and testing. Before testing, the vector network analyzer needs to be calibrated first, and the value range and center frequency point need to be set; after the vector network analyzer is modulated, the connector 7 of the present invention is connected with a patch cord; first, a layer of deionized water is applied to the surface of the arm, and then the open side of the radiation cover 2 is placed above the arm close to the skin to check the vector network analyzer data. As shown in the figure, its S11 is -12.690 dB at 915 MHz, and the test effect is good, meeting the requirements.

[0065] Then a phantom experiment is carried out to complete the performance evaluation of the antenna; first is the preparation of the phantom. One portion of the phantom requires 8.45 g of TX150, 75.45 g of deionized water, 15.2 g of polyethylene, 0.9 g of Nacl, and 0.5 g of color-changing material. After stirring them evenly, put them into a mold, and place a water bag with deionized water and the antenna above it.

[0066] Then the connector 7 of the present invention is connected to the microwave therapy instrument, and the time and power are set on the microwave hyperthermia instrument, and then the microwave hyperthermia instrument is started. Figure 19 The left side is a picture of the experimental environment for phantom testing. Immediately after the heating is over, the temperature of the phantom is photographed with an infrared camera. Figure 19 The right side is the phantom after being fed with 20 W of energy and heated for 30 min. It can be seen that the color-changing part basically coincides with the shape of the SAR diagram of the simulation experiment. Figure 20 The following shows the change in the temperature of the phantom after different heating times. It can be seen that the temperature rises gradually; after heating for 30 min, the temperature of the phantom is measured and reaches 45 °C (43 °C - 45 °C is the optimal temperature for treating tumors).

[0067] This application also proposes a microwave hyperthermia device, including a radio frequency end and the miniaturized microwave hyperthermia antenna of any of the above embodiments. The radio frequency end is connected to the miniaturized microwave hyperthermia antenna; during treatment, microwave energy can be transmitted through the coaxial input line. Under appropriate treatment time and feeding power, it can effectively treat superficial tumors about 0 - 9 cm below the epidermis. From the test return loss diagram, it can be seen that the return loss is about -12.690 dB at 915 M, and the antenna effectiveness is relatively high. It can be seen that the fixed column 3 and the antenna ridge 6 of the extracorporeal microwave hyperthermia antenna provided by the present invention jointly constitute the antenna ridge 6 with a special structure, enabling the antenna to have no special requirements for the external environment and can be directly used in the air, ensuring that it can have a smaller size.

[0068] In the above, if the fixing method is not introduced separately, common technical means in the industry are used, such as welding, nesting, or screw fixing, etc.

[0069] In the description of this specification, the descriptions referring to terms such as "one embodiment", "example", "specific example", etc. mean that the specific features, structures, materials or characteristics described in connection with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic representations of the above terms do not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described can be combined in a suitable manner in any one or more embodiments or examples.

[0070] The above-described embodiments of the present invention do not constitute a limitation on the protection scope of the present invention. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principle of the present invention shall be included within the protection scope of the claims of the present invention.

Claims

1. A miniaturized ridged waveguide hyperthermia antenna, characterized in that: It includes a probe (1) for connecting with an external hyperthermia device and a metal radiation cover (2). A unilateral opening structure for fitting on the patient's skin is formed on the radiation cover (2). The probe (1) is arranged in the radiation cover (2) through a fixing column (3) and is close to the opening side of the radiation cover (2). A metal antenna ridge (6) is arranged between the two fixing columns (3), and the antenna ridge (6) is fixed in the radiation cover (2). There is a fitting gap between both sides of the antenna ridge (6) and the two fixing columns (3). There is a spacing between the antenna ridge (6) and the probe (1). There is a spacing between the probe (1) and the opening of the radiation cover (2). The fixing column (3) and the antenna ridge (6) together form an antenna ridge (6) with a special structure.

2. The miniaturized ridged waveguide hyperthermia antenna according to claim 1, wherein: A connector (7) is provided at the input end of the probe (1), and the probe (1) can be electrically connected to an external radio frequency end device through the connector (7). The connector (7) is fixed to the outer edge of the radiation cover (2) through a locking member.

3. The miniaturized ridged waveguide hyperthermia antenna according to claim 1, wherein: The fixing column (3) is a rectangular parallelepiped metal plate-like structure, and one side of it is fixed to the bottom of the radiation cover (2). One of the fixing columns (3) is close to the opening side and has a semi-circular clamping groove (4) for clamping the probe (1). The other fixing column (3) is close to the opening side and is provided with a receiving groove (5) for receiving the inner metal conductor of the probe (1).

4. A miniaturized ridged waveguide hyperthermia antenna according to claim 1, characterized in that: The radiation cover (2) has a circular cross-section.

5. A miniaturized ridged waveguide hyperthermia antenna according to claim 4, characterized in that: The radiation cover (2) includes an antenna wall (8) and an antenna cover (9), and the antenna cover (9) is fixed to the antenna wall (8) through a locking member.

6. A miniaturized ridged waveguide hyperthermia antenna according to claim 5, wherein: The antenna ridge (6) is fixed to the antenna cover (9) through a locking member.

7. A miniaturized ridged waveguide hyperthermia antenna according to claim 1, characterized in that: The fitting gap between the antenna ridge (6) and the fixing column (3) is 0.1 mm - 0.2 mm.

8. A miniaturized ridged waveguide hyperthermia antenna according to claim 1, characterized in that: The radius of the radiation cover (2) is 19 mm and the height is 36 mm. The antenna ridge (6) is a rectangular block structure with a length of 30 mm, a width of 20 mm, and a height of 28 mm. The length of the probe (1) is 42 mm.

9. A thermotherapy device, characterized in that: It includes a radio frequency end and a miniaturized ridged wave-guide hyperthermia antenna as described in claim 1, and the radio frequency end is connected to the miniaturized ridged wave-guide hyperthermia antenna.

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