A medical 6MV x-band accelerator system

Abstract

The utility model relates to a kind of medical 6MV's X waveband accelerator system, belong to accelerator technical field, solve the accelerator radiation head in prior art Large volume and heavy, when being used for radiation therapy, the problem that cannot be realized in all directions in limited space irradiation, including: high-voltage generating module, microwave generating module, microwave transmission module and beam module;High-voltage generating module is oil-immersed pulse transformer;Microwave generating module includes magnetron;Microwave transmission module is transmitted to the microwave generated by microwave generating module to beam module;Beam module includes accelerating tube, for injecting the electron gun of electron into accelerating tube, and primary collimator, wherein, accelerating tube is X waveband 6MV accelerating tube, including acceleration cavity and the X-ray target being set in acceleration cavity terminal, and microwave feed-in interface is arranged on the outside of accelerating tube, for connecting accelerating tube with microwave transmission module;Beam module further includes titanium pump, and titanium pump is connected to the microwave feed-in interface of accelerating tube.

Description

Technical Field

[0001] This utility model relates to the field of accelerator technology, specifically to a medical 6MV X-band accelerator system. Background Technology

[0002] Multi-degree-of-freedom robot-based radiosurgery robotic systems are used for precise radiotherapy of solid tumors throughout the body. Combining advanced technologies such as multimodal image guidance, modern robots, and miniaturized linear accelerators, they achieve precise radiotherapy under precise image guidance for treating tumors of different sizes.

[0003] However, radiosurgical robotic systems based on multi-degree-of-freedom robots suffer from limited treatment space. The accelerators carried by these systems typically reach positions above and to the sides of the patient, creating a semi-spherical treatment space. However, since treatment is usually performed with the patient supine, this limited space restricts the irradiation of the treatment beam from the patient's lower abdomen and surrounding areas, especially for target areas near the back, such as the spine and the chest and abdomen. This makes it difficult to achieve the optimal dose distribution required for clinical practice.

[0004] Because the space beneath the treatment bed is extremely confined, it is very difficult for multi-degree-of-freedom robots carrying conventionally large and heavy accelerators to move into this limited space in order to deliver irradiation from below the patient. Therefore, miniaturized, compactly assembled accelerator systems are particularly important for radiosurgical robotic systems.

[0005] Furthermore, the heat dissipation of dry-type transformers used in the radiation heads of existing radiosurgical robotic systems relies on fan cooling, which results in uneven heat dissipation. The low thermal conductivity of air makes high-voltage components prone to localized overheating and damage. Additionally, the presence of leakage inductance and eddy currents, along with the transformer coils being exposed to the atmosphere, leads to significant operating noise from dry-type transformers. The electrostatic adsorption effect caused by high voltage also affects the stability of the adsorbed dust system. The high-voltage pulses from dry-type transformers also generate electromagnetic radiation, interfering with other electronic equipment.

[0006] Therefore, there is a need in the art for an improved accelerator system for radiotherapy that is miniaturized, reliable, durable, compact, has a high dose rate, and allows for flexible layout of an all-around, multi-angle irradiation system. Utility Model Content

[0007] To address the aforementioned issues, this invention provides a medical 6MV X-band accelerator system. Through improved structural design and layout, it achieves a smaller size while enhancing operational safety, reliability, and electromagnetic compatibility. It also reduces noise and effectively extends the service life of high-voltage components.

[0008] According to an embodiment of the present invention, a medical 6MV X-band accelerator system is provided for use in radiosurgery, comprising: a high-voltage generation module, a microwave generation module, a microwave transmission module, and a beam module. The high-voltage generation module is an oil-immersed pulse transformer; The microwave generating module includes a magnetron; The microwave transmission module transmits the microwaves generated by the microwave generation module to the beam module; The beam module includes an accelerating tube, an electron gun for injecting electrons into the accelerating tube, and a primary collimator. The accelerating tube is an X-band 6MV accelerating tube, which includes an accelerating cavity and an X-ray target located at the end of the accelerating cavity; and a microwave feed interface is provided on the outside of the accelerating tube for connecting the accelerating tube to the microwave transmission module. The X-ray target includes a base portion and finger-shaped portions extending outward from the base portion. The finger-shaped portions are slender cylindrical structures. When the accelerating tube is assembled with the primary collimator, the finger-shaped portions of the X-ray target extend into the primary collimator. The beam module also includes a titanium pump, which is connected to the microwave feed interface of the accelerating tube.

[0009] Optionally, the longitudinal distance between the microwave feed interface and the end plane of the X-ray target mounted in the accelerating tube cavity ranges from 295mm to 315mm.

[0010] Optionally, the beam module also includes a shielded box that houses the accelerating tube and the electron gun; wherein the total longitudinal length of the accelerating cavity of the accelerating tube after assembly with the electron gun and the X-ray target is 550mm-560mm.

[0011] Optionally, the shielding box has two 180° positioning pin holes symmetrically arranged at one end, and two threaded holes at the corresponding positions of the primary collimator. The two guide rods are passed through the positioning pin holes of the shielding box and the threaded holes of the primary collimator respectively to achieve alignment of the installation positions.

[0012] Optionally, the oil-immersed pulse transformer includes: a housing, and an expansion and contraction mechanism and high-voltage devices disposed inside the housing, wherein the housing is filled with insulating oil to immerse the expansion and contraction mechanism and high-voltage devices in the insulating oil.

[0013] Optionally, the expansion and contraction mechanism includes a central non-expandable straight tube and an outer multi-layered folded cylindrical metal cylinder, which expands and contracts axially relative to the central non-expandable straight tube under the action of the internal and external pressure difference.

[0014] Optionally, the oil-immersed pulse transformer includes a water-cooling pipe disposed on one side outside the housing. The input end of the water-cooling pipe receives cooling water, and the cooling water flowing through the water-cooling pipe exchanges heat with the insulating oil inside the housing. The cooling water after heat exchange flows out through the output end. A water-cooled pipe is installed around the accelerator tube. The water-cooled inlet and water-cooled outlet of the water-cooled pipe extend from one side of the accelerator tube. The water-cooled inlet receives cooling water, circulates along the water-cooled pipe, and then discharges it from the water-cooled outlet. The water-cooled outlet outside the accelerator tube is connected to the input end of the water-cooled pipe outside the oil-immersed pulse transformer. Cooling water flows sequentially through the water-cooled pipe outside the accelerator tube and the water-cooled pipe outside the oil-immersed pulse transformer.

[0015] Optionally, the microwave transmission module includes a four-terminal circulator, a waveguide transmission assembly, and an automatic frequency control device.

[0016] Optionally, the waveguide transmission assembly includes, in connection order, a first E-plane single-bend waveguide, an H-plane single-bend waveguide, a non-twistable waveguide, a first E-plane double-bend waveguide, an inflatable sampling straight waveguide, a second E-plane double-bend waveguide, a rectangular right-hand twisted waveguide, and a second E-plane single-bend waveguide. The four-terminal circulator is connected between the gas-filled sampling straight waveguide and the second E-plane double-bent waveguide. The input port of the first E-plane single-bend waveguide is connected to the output of the microwave generation module; The output port of the second E-plane single-bend waveguide is connected to the microwave feed interface of the accelerating tube.

[0017] Optionally, it also includes a mechanical support frame that integrates and supports the high-voltage generating module, microwave generating module, microwave transmission module and beam module.

[0018] Compared with the prior art, the medical 6MV X-band accelerator system provided according to the embodiments of this utility model has at least the following beneficial effects: by setting an oil-immersed pulse transformer, the heat dissipation effect is more stable and uniform due to the uniform fluidity of insulating oil compared to air, resulting in more stable and reliable operation, less prone to damage, and a longer system life; the design and installation method of the mechanical support frame and microwave transmission module achieves a compact layout structure of the accelerator beam system and reduces losses during microwave transmission; the combined layout design of each component ensures a compact space while effectively avoiding electromagnetic interference caused by the close arrangement of high magnetic components; after the accelerator beam system of this utility model is assembled onto the robot motion frame, the robot motion frame drives the accelerator beam system to rotate in space, which can increase the angle range of the spherical treatment space, realize a large-range spherical non-coplanar treatment technology, achieve a 360° irradiation range, and thus achieve irradiation from above, to the side, and below the treatment bed. Attached Figure Description

[0019] To more clearly illustrate the technical solutions in the embodiments of this utility model or the prior art, the drawings used in the embodiments will be briefly introduced below. By referring to the drawings, the features and advantages of this utility model can be more clearly understood. The drawings are schematic and should not be construed as limiting this utility model in any way. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0020] Figure 1 A schematic diagram of a medical 6MV X-band accelerator system after assembly is shown according to an embodiment of the present invention.

[0021] Figure 2 A schematic diagram of the mounting components and oil-immersed pulse transformer in a medical 6MV X-band accelerator system provided according to an embodiment of the present invention is shown.

[0022] Figure 3 A schematic diagram of an oil-immersed pulse transformer is shown in a medical 6MV X-band accelerator system provided according to an embodiment of the present invention.

[0023] Figure 4 A schematic diagram of a waveguide transmission component is shown in a medical 6MV X-band accelerator system provided according to an embodiment of the present invention.

[0024] Figure 5 A schematic diagram of the beam module in a medical 6MV X-band accelerator system provided according to an embodiment of the present invention is shown.

[0025] Figure 6 A schematic diagram of the assembly of the X-ray target of the accelerator tube is shown in a medical 6MV X-band accelerator system provided according to an embodiment of the present invention.

[0026] Figure 7a A schematic diagram of an automatic frequency control device for a microwave transmission module in a medical 6MV X-band accelerator system provided according to an embodiment of the present invention is shown.

[0027] Figure 7b This diagram shows another angle of the automatic frequency control device for the microwave transmission module in a medical 6MV X-band accelerator system provided according to an embodiment of the present invention.

[0028] Explanation of reference numerals in the attached figures 100. High voltage generating module; 110. Oil-immersed pulse transformer; 120. Housing; 130. Expansion and telescopic mechanism; 150. Water-cooled pipe; 200. Microwave generating module; 210. Magnetron; 220. Magnetron shielding cover; 300. Microwave transmission module; 310. Four-terminal circulator; 320. Waveguide transmission assembly; 321. First E-plane single-bend waveguide; 322. H-plane single-bend waveguide; 323. Non-twistable waveguide; 324. First E-plane double-bent waveguide; 325. Gas-filled sampling straight waveguide; 326. Second E-plane single / double-bent waveguide; 327. Rectangular right-hand twisted waveguide; 328. Second E-plane single-bent waveguide; 330. Automatic frequency control device; 331. Primary amplifier; 332. Phase detector; 333. Phase shift adjustment knob; 334. Incident wave sampling input interface; 335. Reflected wave sampling input interface; 336. A signal output interface; 337. B signal output interface; 4 00. Beam module; 410. Accelerator tube; 414. Water-cooled inlet; 415. Water-cooled outlet; 416. Microwave feed interface; 417. Positioning pin hole; 420. X-ray target; 422. Base part; 424. Finger part; 430. Primary collimator; 432. Guide rod; 440. Shielding box; 500. Mechanical support frame; 510. Substrate; 520. Accelerator tube support plate; 530. Collimator support plate; 540. Rear support frame; 550. Square hole. Detailed Implementation

[0029] To better understand the above-mentioned objectives, features, and advantages of this utility model, the present utility model will be further described in detail below with reference to the accompanying drawings and specific embodiments. It should be noted that, unless otherwise specified, the embodiments of this utility model and the features thereof can be combined with each other.

[0030] Many specific details are set forth in the following description in order to provide a full understanding of the present invention. However, the present invention may also be implemented in other ways different from those described herein. Therefore, the scope of protection of the present invention is not limited to the specific embodiments disclosed below.

[0031] The following detailed description, with reference to the accompanying drawings, illustrates a medical 6MV X-band accelerator system according to an embodiment of the present invention. This medical 6MV X-band accelerator system can be used for radiotherapy, enabling non-coplanar treatment in spherical space. Due to its compact structure, miniaturized appearance, and lightweight design, this medical 6MV X-band accelerator system is suitable for mounting on robotic motion gantry systems, robotic arms, etc., of radiotherapy equipment, providing a larger non-coplanar treatment range and achieving a 360° rotation range, thereby enabling irradiation from above, to the side, and below the treatment bed from more directions.

[0032] like Figure 1As shown, a medical 6MV X-band accelerator system according to an embodiment of this utility model, used in radiosurgery, includes: a high-voltage generating module 100, a microwave generating module 200, a microwave transmission module 300, and a beam module 400. Under the action of the high-voltage generating module 100, the microwave generating module 200 generates microwaves, which are fed into the beam module 400 via the microwave transmission module 300 to establish an accelerating electric field. Electrons emitted in the beam module 400 rotate continuously under the oscillation of the microwaves, reaching a certain speed before striking a target to form X-rays. The X-rays are collimated by a collimator system and reach the patient, irradiating the lesions. The medical 6MV X-band accelerator system provided in this embodiment may also include a mechanical support frame 500 for integrating, assembling, and supporting the high-voltage generating module 100, the microwave generating module 200, the microwave transmission module 300, and the beam module 400.

[0033] The high-voltage generating module 100 provides the necessary high-voltage pulses for system operation. The high-voltage generating module 100 is an oil-immersed pulse transformer 110, in which the internal space is filled with insulating oil, and it can be loaded with full load power at any angle in the entire space.

[0034] like Figure 3 As shown, in this embodiment, the oil-immersed pulse transformer 110 is generally rectangular in shape, and its vertical right-angled sides can be chamfered. The oil-immersed pulse transformer 110 includes a generally rectangular housing 120, inside which an expansion and contraction mechanism 130 and high-voltage components are disposed. Insulating oil is filled into the housing 120 to immerse the internal components (i.e., the expansion and contraction mechanism 130 and the high-voltage components) in the insulating oil. The generally rectangular housing 112 can have chamfered edges formed on its four vertical edges. The housing 120 of the oil-immersed pulse transformer 110 can be made of metal to effectively prevent electromagnetic radiation. The dimensions of the metal housing 120 are set as follows: length 400mm-450mm; width 300mm-350mm; height 120mm-130mm; chamfered edge width 25-35mm. See also... Figure 3 Here, "length" refers to the horizontal direction in the view, "width" refers to the vertical direction in the view, and "height" refers to the vertical direction perpendicular to the illustration. It should be understood that the orientation here is for illustrative purposes only, and in other embodiments, it can be set separately as needed.

[0035] To accommodate movement across all spatial angles, the oil-immersed pulse transformer 110 has a metal casing 120. Adjacent casing walls of the casing 120, including the top, bottom, left, and right sides, are fitted together with multiple screws to achieve a tight fit. The gaps between adjacent casing walls are filled with insulating sealing strips to ensure sealing at all angles and guarantee that the insulating oil is sealed within the internal space of the casing 120. Thus, the oil-immersed pulse transformer 110 forms a sealed box-like structure with the metal casing 120 as its outer shell.

[0036] The housing 120 may have a primary-side high-voltage pulse input insulating terminal 122 and a signal measurement and filament input interface 124 provided on one side of the housing wall. The primary-side high-voltage output insulating terminal 122 extends from the inside of the oil-immersed pulse transformer 110 to the outside, and the external terminal is connected to an external thyristor, thereby providing the high-voltage pulse received by the external thyristor to the primary side of the high-voltage device.

[0037] The expansion and telescopic mechanism 130 is in the form of a telescopic cylindrical elastic metal sheet. It may include a central non-telescopic straight tube and an outer multi-layered folded cylindrical metal cylinder. The metal cylinder can expand and contract axially relative to the central straight tube. By adjusting the volume through the internal and external pressure difference, it ensures that the insulating oil fills the interior of the oil-immersed pulse transformer 110 without leaving any gaps.

[0038] The high-voltage devices may include a secondary high-voltage output insulating terminal 126, a high-voltage pulse current and voltage sampling assembly (not shown in the figure), primary and secondary high-voltage winding assemblies (not shown in the figure), a high-voltage capacitor assembly (not shown in the figure), a high-voltage resistor assembly (not shown in the figure), and a primary high-voltage pulse input insulating terminal 122, etc. By placing the high-voltage devices and the expansion and contraction mechanism 130 inside the housing 120 of the oil-immersed pulse transformer 110, the external space occupied is reduced, resulting in a more compact structure. The secondary high-voltage output insulating terminal 126 extends from the inside of the oil-immersed pulse transformer 110 to the outside, and the external part is connected to the cathode filament contact of the magnetron 210, leading out the secondary high-voltage pulse after being boosted by the high-voltage devices of the oil-immersed pulse transformer 110.

[0039] During operation, the primary high-voltage pulse of the oil-immersed pulse transformer 110 is received from the outside via the insulated terminal 122. After being stepped up by the high-voltage device, the secondary high-voltage pulse is obtained. The secondary high-voltage pulse is then provided to the magnetron 210 of the microwave generation module 200 via the secondary high-voltage output insulated terminal 126. This causes the magnetron 210 to oscillate and generate microwaves, which are then provided to the beam module 400 via the microwave transmission module 300.

[0040] See Figure 2 and Figure 3The oil-immersed pulse transformer 110 may include a water-cooled pipe 150 disposed on one side outside the housing 120 for cooling the insulating oil inside the transformer 110. The inlet of the water-cooled pipe 150 is connected to an external cooling water source. The cooling water flowing through the water-cooled pipe 150 exchanges heat with the insulating oil inside the housing 120, thereby cooling the insulating oil. The cooled water after heat exchange flows out through the outlet. The temperature rise of the insulating oil on the side away from the water-cooled pipe is no more than 5°C compared to the temperature on the side closer to the water-cooled pipe. The water-cooled pipe 150 may include two parallel and connected U-shaped circulation pipes to achieve a compact layout and provide sufficient cooling for the insulating oil.

[0041] The high-voltage generating module 100 is mounted on the bottom base plate 510 of the mechanical support frame 500, providing the high-voltage pulse power required for the operation of the magnetron 210. The base plate 510 of the mechanical support frame 500 can be connected to the flange of the robotic arm. Since the oil-immersed transformer 110 is a sealed box structure with a metal shell, it becomes an integral part after being fixed to the base plate 510, increasing the overall rigidity. The accelerator tube 410, magnetron 210, four-terminal circulator 310 of the microwave transmission module 300, and waveguide, etc., can be fixed on the upper surface of the metal sealed shell 120 of the oil-immersed transformer 110, realizing a compact accelerator beam system. The accelerator beam system achieves global surface space movement under the drive of the robotic arm, and can remain stable and firm in different postures, effectively reducing deviations caused by deformation.

[0042] In this embodiment, the microwave generating module 200 includes a magnetron 210. The magnetron 210 may have a length of approximately 34 cm and a radial diameter of approximately 16 cm. The microwave transmission module 300 is connected to the magnetron 210 and is used to transmit the microwaves generated by the magnetron 210 to the beam module 400. The microwave generating module 200 may also include a magnetron shield 220 surrounding the magnetron 210. The magnetron shield 220 may be made of a metallic material and may have a honeycomb-shaped aperture distribution, with the aperture size being much smaller than 1 / 4 wavelength of the operating frequency, thus achieving better protection against electromagnetic radiation. A fan may also be installed at the bottom of the magnetron shield 220 for heat dissipation.

[0043] like Figure 5As shown, the beam module 400 includes: an accelerating tube 410 having an accelerating cavity and an X-ray target 420; an electron gun for injecting electrons into the accelerating cavity; and a primary collimator 430. The X-ray target 420 is located at the end of the accelerating tube 410. The beam module 400 uses microwave power transmitted from a microwave transmission system to accelerate electrons injected into the accelerating cavity of the accelerating tube 410 by the electron gun, continuously increasing the electron energy, and bombarding the X-ray target 420 at the end of the accelerating tube 410, causing bremsstrahlung radiation and producing X-rays. The beam module 400 is an X-band accelerator. The front end of the accelerating tube 410 is connected to an electron gun (not shown in the figure), which is a grid-controlled electron gun. Electrons are emitted by the electron gun and injected into the accelerating tube 410. The operation of the electron gun requires electron gun drive control. To reduce the size, the electron gun drive power supply can be located outside the radiation head, and the heating, emission, and interruption operations of the electron gun can be controlled only through shielded cables.

[0044] Optionally, in this embodiment, the accelerating tube 410 is an X-band 6MV accelerating tube, which is characterized by its small size and light weight. The medical 6MV X-band accelerator system including the X-band 6MV accelerating tube provided by this embodiment can be applied to X-ray stereotactic radiosurgery equipment. In this embodiment, to ensure global surface range motion, the longitudinal length of the accelerating tube 410 can be set to 420mm-445mm; this length is the longitudinal length of the accelerating tube 410 from the end face connected to the electron gun to the end face connected to the X-ray target 420 (i.e., excluding the length of the X-ray target 420). The total longitudinal length of the accelerating cavity of the accelerating tube 410 after assembly with the electron gun and the X-ray target 420 can be 550mm-560mm.

[0045] like Figure 5 and Figure 6 As shown, the X-ray target 420 includes a base portion 422 and a finger-shaped portion 424 extending from the base portion. The base portion 422 can be circular or square and is fixedly connected to one end of the accelerating tube 410. The finger-shaped portion 424 is an elongated cylindrical structure extending outward from the base portion 422. The X-ray target 420 is located at the end of the accelerating tube 410, and the finger-shaped portion 424 protrudes outward. The X-ray target 414 is located at the end of the accelerating tube 410 and is in the form of a finger-shaped target. The elongated finger-shaped X-ray target 420 enters the center of the primary collimator 430, satisfying the space shielding requirements while reducing the volume.

[0046] A water-cooling inlet 414, a water-cooling outlet 415, and a microwave feed interface 416 can be provided on the outside of the accelerator tube 410. A water-cooling pipe is arranged around the outside of the accelerator tube 410. The water-cooling inlet 414 receives cooling water from an external water-cooling system, circulates along the water-cooling pipe, and discharges from the water-cooling outlet 415, achieving the effect of cooling the accelerator tube 410. The microwave feed interface 416 is connected to the acceleration cavity of the accelerator tube 410. The microwave feed interface 416 can be located on one side of the accelerator tube, but is not limited to the specific location shown in the figure. Optionally, the accelerator tube 410 can be configured in an asymmetrical layout, with the microwave feed interface 416 located on the left side of the middle of the accelerator tube 410, that is, the microwave feed interface 416 is connected to the left half of the accelerator tube 410, close to the electron gun.

[0047] In this embodiment, the water-cooled outlet 415 of the water-cooled pipe surrounding the accelerator tube 410 can be connected to the input end of the water-cooled pipe 150 of the oil-immersed pulse transformer 110. Cooling water flows sequentially through the water-cooled pipe surrounding the accelerator tube 410 and the water-cooled pipe 150 of the oil-immersed pulse transformer 110, providing cooling for multiple components of the accelerator beam system through continuous cooling water circulation. Optionally, water-cooled pipes can also be provided for the magnetron 210, the four-terminal circulator 310, etc., and all water-cooled pipes can be connected sequentially, so that the cooling water circulation sequentially passes through the water-cooled pipes surrounding the accelerator tube 410, the four-terminal circulator 310, the magnetron 210, and the oil-immersed pulse transformer 110, respectively.

[0048] The accelerating tube 410 is connected to the feed waveguide of the microwave transmission module 300 via a microwave feed interface 416 on its side wall. Microwaves enter the accelerating cavity inside the accelerating tube 410 through the feed waveguide, forming a standing wave electric field to accelerate electrons. In this embodiment, the feed waveguide of the microwave transmission module 300 is a second E-plane single-bend waveguide 328.

[0049] refer to Figure 4 and Figure 5 When the accelerating tube 410 is assembled with the primary collimator 430, the finger-shaped portion 424 of the X-ray target 420 installed at the end of the accelerating tube 410 is embedded in the deep hole of the cylindrical primary collimator 430 to form a tight fit.

[0050] Optionally, the beam module 400 may further include a shielding box 440 for housing the accelerating tube 410 and the electron gun. The accelerating tube 410 is placed inside the shielding box 440 to shield internal electron radiation and external electromagnetic interference. A rectangular opening is formed on one side of the shielding box 440 for leading out the microwave feed interface 416, the water-cooling inlet 414, and the water-cooling outlet 415. Microwave transmission in the microwave transmission module 300 will generate losses. To reduce microwave losses, the distance between the input port of the second E-plane single-bend waveguide 328 and the center of the accelerating tube 410 is minimized. In this embodiment, the microwave feed interface 416 is located in the middle or slightly to the left of the middle of the accelerating tube 410, close to the electron gun. Furthermore, the longitudinal length of the accelerating tube 410 is set to be less than or equal to 445 mm; the microwave feed interface 416 is located on the end plane of the X-ray target 420 connected to the accelerating tube 410 (i.e., Figure 5 and Figure 6 The longitudinal distance between the right-end plane of the accelerating tube 410 (excluding the X-ray target 420) and the electron gun direction shown in the figure is greater than or equal to 222 mm. The closer to the electron gun direction, the fewer waveguides are used in the microwave transmission module 300, and the shorter the total length. To optimize the layout of the microwave feed interface 416 and the water-cooling interface, the microwave feed interface 416 can be further positioned at a longitudinal distance of 295 mm to 315 mm between the microwave feed interface 416 and the end plane of the X-ray target 420 (the right-end plane of the accelerating tube 410 in the figure, excluding the X-ray target 420). This positioning of the microwave feed interface 416 helps to shorten the total length of the microwave transmission module 300, reduce microwave loss during transmission, and improve the overall system efficiency. It also reserves suitable installation space for external connection devices of the accelerating tube 410, enabling a more compact and reliable installation of the various components of the beam module, connecting pipes, and externally connected devices.

[0051] The beam module 400 may also include a titanium pump, which is connected to the microwave feed interface 416. The titanium pump is connected to the microwave feed interface 416 via a copper conduit. The beam module 400 may also include a knife-edge flange, which can be connected to the copper conduit connected to the titanium pump via a bent copper conduit. The knife-edge flange is used for sealing and maintaining system vacuum. The shielding box 440 may be constructed of multiple layers of materials, with an outer ferromagnetic material and an inner lead shielding layer. The longitudinal length of the shielding box 440 accommodating the accelerating tube 410 and the electron gun is no more than 530 mm, excluding the length of the X-ray target 120. The total length of the shielding box 440 and the X-ray target 120 after assembly is no more than 600 mm.

[0052] Optionally, two 180° locating pin holes 417 are symmetrically provided on the shielding box 440 at the end of the X-ray target 420 mounted on the accelerating tube 410, and two threaded holes are opened at the corresponding positions on the primary collimator 430. Two guide rods 432 are passed through the locating pin holes 417 of the shielding box 440 and the threaded holes of the primary collimator 430 respectively to achieve alignment of the installation positions. When installing the accelerating tube 410 and the primary collimator 430, first mate the locating pin holes 417 of the shielding box 440 with the guide rods 430, and then slowly move the shielding box 440 and the accelerating tube 410 until the accelerating tube 410 is in contact with the mounting surface of the primary collimator 430. Then, pass the guide rods 432 through the threaded holes of the primary collimator 430 and tighten them. By using the above settings and installation methods, it can be ensured that the X-ray emitted from the accelerating tube 410 coincides with the central axis of the primary collimator 430, thus ensuring accuracy; and it can also prevent the X-ray target 420 from being damaged by colliding with the side wall of the primary collimator 430 due to misalignment during installation.

[0053] like Figure 4 As shown, the microwave transmission module 300 may include a four-terminal circulator 310, a waveguide transmission component 320, and an automatic frequency control device 330. These are used to transmit microwaves, prevent microwave power reflected from the accelerating tube 410 from entering the magnetron 210, and automatically adjust the microwave frequency output by the magnetron 210 to match the resonant frequency of the accelerating tube 410. The microwave power level output by the magnetron 210 determines the dose rate limit. This embodiment of the microwave transmission module 300 provides an improved microwave transmission link and utilizes a high-performance, low-insertion-loss four-terminal circulator 310. At least 1.5 MW of microwave power can be obtained at the entrance of the accelerating tube 410, effectively increasing the electric field strength within the accelerating tube 410 and thus increasing the particle acceleration energy. The higher the particle energy, the closer the speed is to the speed of light, the higher the X-ray conversion efficiency of the beam, and the higher the cumulative dose of a single beam pulse, which manifests as a higher dose rate under the same repetition frequency conditions. The four-terminal circulator 310 is an isolation device that can eliminate the influence of the accelerating tube 410 as a load on the magnetron 210 during transmission, so as to ensure the stable operation of the system.

[0054] Continue to refer to Figure 4In this embodiment, the waveguide transmission assembly 320, in the order of connection, may include a first E-plane single-bent waveguide 321, an H-plane single-bent waveguide 322, a non-twistable waveguide 323, a first E-plane double-bent waveguide 324, an inflatable sampling straight waveguide 325, a second E-plane double-bent waveguide 326, a rectangular right-hand twisted waveguide 327, and a second E-plane single-bent waveguide 328. A four-terminal circulator 310 is connected between the inflatable sampling straight waveguide 325 and the second E-plane double-bent waveguide 326. Each waveguide of the waveguide transmission assembly 320 may be made of steel to achieve the transmission of radio frequency energy and provide good mechanical properties; the internal surfaces of each waveguide of the waveguide transmission assembly 320 are polished to reduce surface roughness, and a silver-plated coating is used on the internal surfaces of each waveguide of the waveguide transmission assembly 320 to improve conductivity. Since waves with frequencies lower than the cutoff frequency of the waveguide cannot propagate in the waveguide transmission assembly 320, to reduce energy loss, the internal cavity structure of each waveguide in the waveguide transmission assembly 320 is designed as rectangular, and its dimensions match the wavelength of the electromagnetic wave. The non-twistable waveguide 323 is a soft waveguide, capable of withstanding forces in different directions. This embodiment of the waveguide transmission assembly 320 uses only one soft waveguide, achieving flexible installation while avoiding the problems caused by the easily lost nature of using multiple soft waveguides.

[0055] The waveguide transmission assembly 320 is connected as follows: The input port of the first E-plane single-bend waveguide 321 is connected to the outlet of the magnetron 210, and its output port is connected to the input port of the H-plane single-bend waveguide 322; the output port of the H-plane single-bend waveguide 322 is connected to the input port of the first E-plane double-bend waveguide 324 via the non-twistable waveguide 323; the output port of the first E-plane double-bend waveguide 324 is connected to the input port of the gas-filled sampling straight waveguide 325; the four-terminal circulator 310 is connected between the gas-filled sampling straight waveguide 325 and the second E-plane double-bend waveguide 326. The output port of the gas-filled sampling straight waveguide 325 is connected to the first port of the four-terminal circulator 310, and the second port of the four-terminal circulator 310 is connected to the input port of the second E-plane double-bent waveguide 326. The output port of the second E-plane double-bent waveguide 326 is connected to the input port of the rectangular right-hand twisted waveguide 327. The output port of the rectangular right-hand twisted waveguide 327 is connected to the input port of the second E-plane single-bent waveguide 328, and the output port of the second E-plane single-bent waveguide 328 is connected to the microwave feed interface 416 of the accelerating tube 410. Optionally, the gas-filled sampling straight waveguide 325 can be connected to an external attenuator, detector crystal, and duct connector. The duct connector is connected to an insulating gas connector, which allows insulating gas to be introduced to fill the internal cavity of the waveguide transmission assembly 320, ensuring that the internal cavity is filled with inert gas and that air is vented.

[0056] In this embodiment, the two connection ports between the interconnected waveguides in the waveguide transmission assembly 320 are choke-type and planar contact-type connections to provide a better sealing effect. For example, the ports of each waveguide can be configured as follows: the input and output ports of the first E-plane single-bend waveguide 321 are both choke-type, the input and output ports of the gas-filled sampling straight waveguide 325 are both planar contact-type, and the input ports of the remaining waveguides are planar contact-type, while the output ports are choke-type. Specifically, for example, the input and output ports of the first E-plane single-bent waveguide 321 can be configured as choke-type; the input port of the H-plane single-bent waveguide 322 can be a planar contact type (to match the choke-type output port of the first E-plane single-bent waveguide 321), and the output port can be choke-type; the input port of the non-twistable waveguide 323 can be a planar contact type (to match the choke-type output port of the H-plane single-bent waveguide 322), and the output port can be choke-type; the input port of the first E-plane double-bent waveguide 324 can be a planar contact type (to match the choke-type output port of the non-twistable waveguide 323), and the output port can be choke-type; the input and output ports of the gas-filled sampling straight waveguide 325 can both be planar contact types, respectively... The input port of the first E-plane double-bent waveguide 324 is matched with the choke-type output port, and the first port of the four-terminal circulator 310 is matched with the first port; the input port of the second E-plane double-bent waveguide 326 is planar contact type (to match the second port of the four-terminal circulator 310), and the output port is choke type; the input port of the rectangular right-hand twisted waveguide 327 is planar contact type (to match the choke-type output port of the second E-plane double-bent waveguide 326), and the output port is choke type; the input port of the second E-plane single-bent waveguide 328 is planar contact type (to match the choke-type output port of the rectangular right-hand twisted waveguide 327), and the output port is choke type, for connection to the feed interface (microwave feed interface 416) of the accelerating tube 410.

[0057] See Figure 1 and Figure 3Optionally, the bending angle of the first E-plane single-bent waveguide 321 can be set to an obtuse angle, for example, greater than 150°, so that after installation it extends forward and upward from the outlet of the magnetron 210; the bending angle of the first H-plane single-bent waveguide 322 can be set to 90°, so that after installation it extends forward and turns to the right from the outlet end of the first E-plane single-bent waveguide 321; the first E-plane double-bent waveguide 324 and the second E-plane double-bent waveguide 326 each have two bending angles, and each of their two bending angles is designed to be 90°, and the concave surfaces of the two E-plane double-bent waveguides face inward. Thus, the assembled waveguide transmission assembly 320, consisting of a portion of the H-plane single-bend waveguide 322, a non-twistable waveguide 323, a first E-plane double-bend waveguide 324, an inflatable sampling straight waveguide 325, a four-terminal circulator 310, a second E-plane double-bend waveguide 326, a rectangular right-hand twisted waveguide 327, and a portion of the second E-plane single-bend waveguide 328, is arranged in a generally planar, spiral shape. The waveguide transmission assembly 320 transmits the microwaves output from the upper magnetron 210 to the feed structure of the lower front accelerator tube 410, achieving a compact assembly with the magnetron 210, accelerator tube 410, and other structures. Figure 1 and Figure 4 As shown, the first E-plane single-bend waveguide 321 on the upper part of the waveguide transmission assembly 320 connects to the outlet of the magnetron 210, receives microwaves, and transmits them through the internal cavity path of the waveguide transmission assembly 320 upward, forward, right, downward, left, upward, and upper right, then through the output port of the second E-plane single-bend waveguide 328 to the microwave feed interface 416 of the accelerating tube 410, thus finally looping back and transmitting into the accelerating tube 410 below the magnetron 210. Through the above design, the waveguide transmission assembly 320 is rationally arranged in a limited space, which is beneficial to the compact layout of the accelerator beam system as a whole.

[0058] The automatic frequency control device 330 integrates a phase detector and a primary amplifier, reducing its size. Internally, the automatic frequency control device 330 integrates a phase shifter, mixer, attenuator, detector crystal, and amplifier. Interfaces for connecting to the gas-filled sampling straight waveguide 325 and the four-terminal circulator 310 are located on both sides of the automatic frequency control device 330, allowing for flexible spatial arrangement. For the shortest possible installation distance to the interface of the four-terminal circulator 310, the automatic frequency control device 330 can be installed on the outer edge of the oil-immersed pulse transformer 110, parallel to the four-terminal circulator 310 and the gas-filled sampling straight waveguide 325.

[0059] See Figure 7a and Figure 7bAs an example, the automatic frequency control device 330 is configured with a primary amplifier 331 at the top and a phase detector 332 at the bottom. The left side of the phase detector 332 includes a phase shift adjustment knob 333, an incident wave sampling input interface 334, and a reflected wave sampling input interface 335. The incident wave sampling input interface 334 is connected to the gas-filled sampling straight waveguide 325 to receive the incident wave signal; the reflected wave sampling input interface 335 is connected to the four-terminal circulator 310 to receive the reflected wave signal. The right side of the phase detector 332 has an A signal output interface 336 and a B signal output interface 337, which output the signals detected by the phase detector 332. These signals are provided to the control circuit of the automatic frequency control device. After processing by the control circuit, an error signal is output to the motor driver, which then drives the motor. The motor then drives the connected transmission components, thereby driving the tuning lever of the magnetron to adjust the magnetron 210. The configuration of the automatic frequency control device 330 is not limited to this structural arrangement. The incident wave and reflected wave signals introduced through the incident wave sampling input interface 334 and the reflected wave sampling input interface 335 are amplified by the phase detector 332 and then sent to the primary amplifier 331 for signal amplification. They are then output from the A signal output interface 336 and the B signal output interface 337 to the control circuit for frequency control of the magnetron 210.

[0060] The above-mentioned configuration of the automatic frequency control device 330 optimizes the spatial layout, allowing it to be installed in any space, facilitating a compact space and a neat appearance.

[0061] See Figure 1 and Figure 2 The compact high-gradient accelerator system provided in this embodiment may also include a mechanical support frame 500 for integrating and supporting the high-voltage generation module 100, microwave generation module 200, microwave transmission module 300, and beam module 400. The assembled medical 6MV X-band accelerator system has a generally cubic compact structure, which facilitates further installation into devices such as robotic arms of radiotherapy equipment.

[0062] like Figure 2 As shown, the mechanical support frame 500 may include a base plate 510 at the bottom, an accelerator tube support plate 520 disposed above the base plate 510 and parallel to the base plate 510, a collimator support plate 530 with an opening fixed to the right side of the base plate 510, and a rear support frame 540 fixed to the left side of the base plate 510. The accelerator tube support plate 520 and the collimator support plate 530 are fixedly connected; the top of the rear support frame 540 is fixedly connected to the accelerator tube support plate 520, for example, by means of angle iron. The rear support frame 540 provides support for the accelerator tube support plate 520 from the left side. Here, for ease of understanding, the directions up, down, left, right, front, and rear are references. Figure 1 and Figure 2The direction shown may be adjusted as needed in other embodiments.

[0063] During assembly, the high-voltage generating module 100 (oil-immersed pulse transformer 110) is fixed to the surface of the substrate 510, thereby positioning the high-voltage generating module 100 between the substrate 510 and the accelerating tube support plate 520. The magnetron 210 of the microwave generating module 200 and the beam module 400 including the accelerating tube 410 are mounted above the accelerating tube support plate 520, with the magnetron 210 located directly behind the beam module 400. This forms a two-layer mounting configuration, with the high-voltage generating module 100 on the lower layer and the magnetron 210 and the beam module 400 including the accelerating tube 410 on the upper layer. The lower-layer high-voltage generating module 100 can provide support for the upper-layer magnetron 210 and beam module 400. The primary collimator 430 at the right end of the accelerating tube 410 passes through the opening in the collimator support plate 530 and is fixedly mounted. The microwave transmission module 300 is located in front of the accelerating tube 410 and the high-voltage generating module 100, and the waveguide of the lower part of the microwave transmission module 300 (i.e., the lower part of the gas-filled sampling straight waveguide 325 and the second E-plane double-bent waveguide 326) and the four-terminal circulator 310 are fixed to the substrate 510; thus forming a front-to-back two-layer mounting method, that is, the high-voltage generating module 100, the magnetron 210 and the accelerating tube 410 are on the rear side, and the microwave transmission module 300 is set on the front side. The planar portion of the microwave transmission module 300 is vertically arranged on the front side. Figure 1 As shown, the medical 6MV X-band accelerator system assembled in the above three-dimensional manner has a compact structure in the form of a roughly cubic shape and has a stable assembly relationship.

[0064] Optionally, the non-load-bearing portions of each support plate of the mechanical support frame 500 can form multiple square holes 550 to reduce the overall weight; the load-bearing portions of each support plate, as well as the portions where the high-voltage generating module 100 is installed, can be reinforced with steel bars to provide enhanced strength and reliable support, and the steel bars can be protruding mechanical frames. The above design can better achieve the effect of lightweighting and rigidity of the overall structure.

[0065] The assembled medical 6MV X-ray accelerator system has an overall length (from the right end to the end of the primary collimator) ranging from 600mm to 700mm and a total weight of less than 160kg. It can be fixedly mounted to external robotic arms, robots, or other devices via the base plate 510 of the mechanical support frame 500. This allows for flexible adjustment of orientation and movement to the desired position during radiotherapy and other procedures, enabling global spatial motion while maintaining overall system stability and robustness under different postures, effectively reducing deviations caused by deformation.

[0066] The descriptions of directions here, including up, down, front, and back, are for reference only. Figure 1 and Figure 2The purpose of each assembly structure is clearly explained, but the present invention is not limited to that specific orientation.

[0067] All the above-mentioned optional technical solutions can be combined in any way to form optional embodiments of this utility model, and will not be described in detail here.

[0068] It should be understood that the sequence number of each step in the above embodiments does not imply the order of execution. The execution order of each process should be determined by its function and internal logic, and should not constitute any limitation on the implementation process of this utility model embodiment.

[0069] The above description is only a preferred embodiment of the present utility model, but the protection scope of the present utility model is not limited thereto. Any changes or substitutions that can be easily conceived by those skilled in the art within the technical scope disclosed in the present utility model should be included within the protection scope of the present utility model.

Claims

1. A medical 6MV X-band accelerator system for use in radiosurgery, characterized in that, include: High voltage generating module (100), microwave generating module (200), microwave transmission module (300) and beam module (400); The high voltage generating module (100) is an oil-immersed pulse transformer (110). The microwave generating module (200) includes a magnetron (210). The microwave transmission module (300) transmits the microwaves generated by the microwave generation module (200) to the beam module (400). The beam module (400) includes an acceleration tube (410), an electron gun for injecting electrons into the acceleration tube (410), and a primary collimator (430). The accelerating tube (410) is an X-band 6MV accelerating tube, including an accelerating cavity and an X-ray target (420) disposed at the end of the accelerating cavity; and a microwave feed interface (416) is disposed on the outside of the accelerating tube (410) for connecting the accelerating tube (410) to the microwave transmission module (300). The X-ray target (420) includes a base portion (422) and a finger-shaped portion (424) extending outward from the base portion. The finger-shaped portion (424) has a slender cylindrical structure. When the accelerating tube (410) is assembled with the primary collimator (430), the finger-shaped portion (424) of the X-ray target (420) extends into the primary collimator (430). The beam module (400) also includes a titanium pump connected to the microwave feed interface (416) of the accelerating tube (410).

2. The medical 6MV X-band accelerator system according to claim 1, characterized in that, The longitudinal distance between the microwave feed interface (416) and the end plane of the X-ray target (420) mounted on the accelerating cavity of the accelerating tube (410) ranges from 295 mm to 315 mm.

3. The medical 6MV X-band accelerator system according to claim 1, characterized in that, The beam module (400) also includes a shielded box (440) that houses the accelerating tube (410) and the electron gun. The total longitudinal length of the acceleration cavity of the acceleration tube (410) after assembly with the electron gun and the X-ray target (420) is 550mm-560mm.

4. The medical 6MV X-band accelerator system according to claim 3, characterized in that, The shielding box (440) has two 180° positioning pin holes (417) symmetrically arranged at one end, and two threaded holes are opened at the corresponding positions of the primary collimator (430). The two guide rods (432) are passed through the positioning pin holes (417) of the shielding box (440) and the threaded holes of the primary collimator (430) respectively to achieve the alignment of the installation positions.

5. The medical 6MV X-band accelerator system according to claim 1, characterized in that, The oil-immersed pulse transformer (110) includes: a housing (120), and an expansion and contraction mechanism (130) and high-voltage devices disposed inside the housing (120), wherein the housing (120) is filled with insulating oil to immerse the expansion and contraction mechanism (130) and high-voltage devices in the insulating oil.

6. The medical 6MV X-band accelerator system according to claim 5, characterized in that, The expansion and contraction mechanism (130) includes a central non-expandable straight tube and an outer multi-layered folded cylindrical metal tube, which expands and contracts axially relative to the central non-expandable straight tube under the action of the internal and external pressure difference.

7. The medical 6MV X-band accelerator system according to claim 5, characterized in that, The oil-immersed pulse transformer (110) includes a water-cooled pipe (150) disposed on one side outside the housing (120). The input end of the water-cooled pipe (150) receives cooling water. The cooling water flowing through the water-cooled pipe (150) exchanges heat with the insulating oil inside the housing (120). The cooling water after heat exchange flows out through the output end. A water-cooled pipe is provided on the outer periphery of the acceleration tube (410). The water-cooled inlet (414) and water-cooled outlet (415) of the water-cooled pipe extend from one side of the outer periphery of the acceleration tube (410). The water-cooled inlet (414) receives cooling water and circulates along the water-cooled pipe before being discharged from the water-cooled outlet (415). The water-cooled outlet (415) outside the acceleration tube (410) is connected to the input end of the water-cooled pipe (150) outside the oil-immersed pulse transformer (110). Cooling water flows through the water-cooled pipe outside the acceleration tube (410) and the water-cooled pipe (150) outside the oil-immersed pulse transformer (110) in sequence.

8. The medical 6MV X-band accelerator system according to claim 1, characterized in that, The microwave transmission module (300) includes a four-terminal circulator (310), a waveguide transmission assembly (320), and an automatic frequency control device (330).

9. The medical 6MV X-band accelerator system according to claim 8, characterized in that, The waveguide transmission assembly (320) includes, in the following order: a first E-plane single-bend waveguide (321), an H-plane single-bend waveguide (322), a non-twistable waveguide (323), a first E-plane double-bend waveguide (324), an inflatable sampling straight waveguide (325), a second E-plane double-bend waveguide (326), a rectangular right-hand twisted waveguide (327), and a second E-plane single-bend waveguide (328). Among them, the four-terminal circulator (310) is connected between the gas-filled sampling straight waveguide (325) and the second E-plane double-bend waveguide (326); The input port of the first E-plane single-bend waveguide (321) is connected to the output of the microwave generation module (200); The output port of the second E-plane single-bend waveguide (328) is connected to the microwave feed interface (416) of the accelerating tube (410).

10. The medical 6MV X-band accelerator system according to claim 1, characterized in that, It also includes a mechanical support frame (500), which integrates and supports the high voltage generating module (100), microwave generating module (200), microwave transmission module (300) and beam module (400).

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