Magnetic resonance guided radiotherapy equipment

Abstract

The utility model relates to the technical field of medical instruments, and discloses magnetic resonance guided radiotherapy equipment, which comprises a radiotherapy component, a magnetic resonance guided radiotherapy component and a magnetic resonance guided radiotherapy component, a magnet member provided with a treatment space; the magnet part comprises a coil assembly and a shell forming a treatment space, the coil assembly is arranged in the inner space of the shell, the coil assembly continuously extends around the treatment space and is of an annular structure, at least one communication space is formed in the shell, and the communication space penetrates through the shell and is communicated with the treatment space; the first driving assembly is arranged around the shell, the treatment head is connected with the first driving assembly, and the first driving assembly is used for driving the treatment head to move relative to the magnet component. According to the magnetic resonance guided radiotherapy equipment provided by the invention, the problem that the treatment precision and the treatment effect are influenced and the treatment efficiency is greatly reduced because the radiotherapy rays emitted by the radiotherapy part need to penetrate through the magnet part to irradiate the patient in the related technology can be solved.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and in particular to a magnetic resonance-guided radiotherapy device. Background Technology

[0002] Magnetic resonance-guided radiotherapy (MR-LINAC) is an integrated device combining magnetic resonance (MR) and linear accelerator (LINAC). Compared to CT (Computed Tomography)-guided radiotherapy, MR-LINAC delivers a lower radiation dose and provides higher imaging resolution for soft tissue structures, thus gaining wider application.

[0003] In related technologies, magnetic resonance-guided radiotherapy equipment generally includes a gantry, a radiotherapy unit, and a magnet unit. The magnet unit comprises a coil assembly and a housing filled with liquid helium. During use, the patient is placed inside the magnet unit. The radiotherapy rays emitted by the radiotherapy unit must pass through the magnet unit to reach the patient. Because the radiotherapy rays experience energy attenuation as they penetrate the coil assembly and housing, and because the different heights of liquid helium the radiotherapy rays penetrate cause differences in radiation dose, the treatment accuracy and efficacy are affected, resulting in a significant reduction in treatment efficiency. Utility Model Content

[0004] This application provides a magnetic resonance-guided radiotherapy device that can improve the problem in related technologies where the radiotherapy rays emitted by the radiotherapy component need to pass through a magnet component before they can reach the patient, thus affecting the treatment accuracy and effect and resulting in a significant reduction in treatment efficiency.

[0005] This application provides a magnetic resonance-guided radiotherapy device, including:

[0006] A radiotherapy unit, the radiotherapy unit including a treatment head;

[0007] A magnet component is provided with a treatment space; the magnet component includes a coil assembly and a housing constituting the treatment space, the coil assembly is disposed in the internal space of the housing, the coil assembly extends continuously around the treatment space and has a ring structure, and the housing is provided with at least one communicating space, the communicating space penetrates the housing and communicates with the treatment space;

[0008] A first drive assembly is disposed around the housing, and the treatment head is connected to the first drive assembly. The first drive assembly is used to drive the treatment head to move relative to the magnet component.

[0009] In some embodiments, the magnet component is provided with a plurality of the communicating spaces, and the plurality of communicating spaces are spaced apart circumferentially along the housing. The first driving component is used to drive the treatment head to rotate around the axis of the housing. The magnetic resonance guided radiotherapy device further includes a second driving component, which is connected to the housing and is used to drive the housing to rotate around the axis of the housing.

[0010] In some embodiments, the angle between the axes of two adjacent connected spaces is 10°-45°.

[0011] In some embodiments, the housing includes an inner container, a heat shield layer, and an outer container arranged sequentially from the inside out; the treatment space is the space surrounded by the inner container; the connecting space passes through the inner container, the heat shield layer, and the outer container; the coil assembly is disposed in the internal space of the inner container; and the internal space of the inner container is also provided with liquid helium.

[0012] In some embodiments, the housing is provided with an installation space in which at least one of the first drive assembly and the radiotherapy component is located.

[0013] In some embodiments, the length direction of the mounting space is parallel to or perpendicular to the axis of the housing.

[0014] In some embodiments, the magnetic resonance-guided radiotherapy device further includes a second drive assembly connected to the housing and used to drive the housing to rotate about the axis of the housing.

[0015] In some embodiments, multiple interconnecting spaces, mounting spaces, first driving components, and radiotherapy components are provided, and the multiple interconnecting spaces, mounting spaces, first driving components, and radiotherapy components are provided in a one-to-one correspondence, with the multiple interconnecting spaces spaced apart circumferentially along the housing.

[0016] In some embodiments, the magnetic resonance-guided radiotherapy device further includes a connected carrier and a third drive assembly, the carrier being disposed in the treatment space and used to support the patient, and the third drive assembly being used to drive the carrier to move relative to the magnet component.

[0017] In some embodiments, the third drive assembly is used to drive the carrier to rotate about the axis of the magnet component; and / or, the third drive assembly is used to drive the carrier to move in a direction parallel to or perpendicular to the axis of the housing.

[0018] The magnetic resonance-guided radiotherapy device provided in this application has the following advantages: Since the magnet component has a treatment space for placing the patient, and the housing of the magnet component also has a communicating space connected to the treatment space, the coil assembly is located inside the housing. The coil assembly extends continuously around the treatment space in a ring structure, and the first drive assembly is arranged around the housing. The treatment head of the radiotherapy component is connected to the first drive assembly. Therefore, after the radiotherapy rays emitted from the treatment head of the radiotherapy component irradiate one part of the patient, the first drive assembly drives the treatment head of the radiotherapy component to move relative to the magnet component, so that the radiotherapy rays pass through the communicating space and irradiate another part of the patient. This not only allows for irradiation treatment of multiple parts of the patient, but also ensures that the radiotherapy rays emitted from the treatment head of the radiotherapy component directly irradiate the patient, guaranteeing treatment accuracy and effectiveness, and improving treatment efficiency. Attached Figure Description

[0019] To more clearly illustrate the technical solutions in the embodiments of this application, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0020] Figure 1 This is a schematic diagram of the structure of the magnetic resonance-guided radiotherapy device in the first embodiment of this application;

[0021] Figure 2 yes Figure 1 The diagram shows the internal structure of a magnetic resonance-guided radiotherapy device.

[0022] Figure 3 yes Figure 1 The diagram shows an axial cross-sectional view of the magnetic resonance-guided radiotherapy device.

[0023] Figure 4 yes Figure 3 A schematic diagram of a partial structure of the coil assembly in a magnetic resonance-guided radiotherapy device is shown.

[0024] Figure 5 yes Figure 1 A side view of the magnetic resonance-guided radiotherapy device shown.

[0025] Figure 6 yes Figure 5 The diagram shown illustrates the working principle of a magnetic resonance-guided radiotherapy device.

[0026] Figure 7 yes Figure 5The diagram shows another state of operation of the magnetic resonance-guided radiotherapy device.

[0027] Figure 8 This is a schematic diagram of the structure of the magnetic resonance-guided radiotherapy device in the second embodiment of this application;

[0028] Figure 9 yes Figure 8 The diagram shows another state of operation of the magnetic resonance-guided radiotherapy device.

[0029] Figure 10 This is a schematic diagram of the structure of the magnetic resonance-guided radiotherapy device in the third embodiment of this application;

[0030] Figure 11 This is a schematic diagram of the structure of the magnet component of the magnetic resonance-guided radiotherapy device in the fourth embodiment of this application;

[0031] Figure 12 This is a schematic diagram of the structure of the magnetic resonance-guided radiotherapy device in the fifth embodiment of this application;

[0032] Figure 13 yes Figure 12 The diagram shows an axial cross-sectional view of the magnetic resonance-guided radiotherapy device.

[0033] Figure 14 yes Figure 12 A radial cross-sectional view of the magnetic resonance-guided radiotherapy device shown.

[0034] Figure 15 yes Figure 13 A schematic diagram of a partial structure of the coil assembly in a magnetic resonance-guided radiotherapy device is shown.

[0035] Figure 16 yes Figure 12 Another axial cross-sectional view of the magnetic resonance-guided radiotherapy device shown;

[0036] Figure 17 This is a schematic diagram of the structure of the magnetic resonance-guided radiotherapy device in the sixth embodiment of this application;

[0037] Figure 18 yes Figure 17 The diagram shows another state of operation of the magnetic resonance-guided radiotherapy device.

[0038] Figure 19 This is a schematic diagram of the structure of the magnetic resonance-guided radiotherapy device in the seventh embodiment of this application.

[0039] The markings in the diagram mean:

[0040] 100. Magnetic resonance-guided radiotherapy equipment;

[0041] 10. Radiotherapy components;

[0042] 20. Magnet components;

[0043] 201. Treatment space; 202. Connecting space; 2021. Inner piping; 2022. Middle piping; 2023. Outer piping; 21. Coil assembly; 203. Spacing area; 204. Installation space; 211. Inner coil; 212. Inner coil frame; 2121. Clearance opening; 213. Outer coil; 214. Outer coil frame; 215. Connector; 22. Shell; 221. Inner container; 2211. Inner cylinder of the inner container; 2212. Inner container end cap; 2213. Outer cylinder of the inner container; 2222. Thermal shielding layer; 2221. Inner cylinder of the shielding layer; 2222. End cap of the shielding layer; 2223. Outer cylinder of the shielding layer; 2231. Inner cylinder of the outer container; 2232. End cap of the outer container; 2233. Outer cylinder of the outer container; 23. Refrigeration unit; 24. Overpressure relief device;

[0044] 30. First driving component;

[0045] 40. Second drive component;

[0046] 50. Load-bearing components;

[0047] 60. Third drive component;

[0048] 200. Patient. Detailed Implementation

[0049] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.

[0050] It should be noted that when a component is referred to as being "fixed to" or "set on" another component, it can be directly on or indirectly on that other component. When a component is referred to as being "connected to" another component, it can be directly connected to or indirectly connected to that other component.

[0051] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, "multiple" means two or more, unless otherwise explicitly specified.

[0052] In this specification, references to "one embodiment," "some embodiments," or simply "embodiment" mean that one or more embodiments of this application include a specific feature, structure, or characteristic described in connection with that embodiment. Therefore, the phrases "in one embodiment," "in some embodiments," "in other embodiments," "in still other embodiments," etc., appearing in different parts of this specification do not necessarily refer to the same embodiment, but rather mean "one or more, but not all, embodiments," unless otherwise specifically emphasized. Furthermore, in one or more embodiments, specific features, structures, or characteristics may be combined in any suitable manner.

[0053] To illustrate the technical solution of this application, the following description is provided in conjunction with specific accompanying drawings and embodiments.

[0054] In related technologies, magnetic resonance-guided radiotherapy equipment generally includes a gantry, a radiotherapy unit, and a magnet unit. The magnet unit comprises a coil assembly and a housing filled with liquid helium. During use, the patient is placed inside the magnet unit. The radiotherapy rays emitted by the radiotherapy unit must pass through the magnet unit to reach the patient. Because the radiotherapy rays experience energy attenuation as they penetrate the coil assembly and housing, and because the different heights of liquid helium the radiotherapy rays penetrate cause differences in radiation dose, the treatment accuracy and efficacy are affected, resulting in a significant reduction in treatment efficiency.

[0055] In view of this, this application provides a magnetic resonance-guided radiotherapy device. The magnet component has a treatment space for placing the patient. The housing of the magnet component also has a connecting space that communicates with the treatment space. A coil assembly is located inside the housing, extending continuously around the treatment space in a ring structure. A first drive assembly is arranged around the housing, and the treatment head of the radiotherapy component is connected to the first drive assembly. Therefore, after the radiotherapy rays emitted from the treatment head of the radiotherapy component irradiate one part of the patient, the first drive assembly drives the treatment head of the radiotherapy component to move relative to the magnet component, allowing the radiotherapy rays to pass through the connecting space and irradiate another part of the patient. This not only allows for irradiation treatment of multiple parts of the patient, but the existence of the connecting space also ensures that the radiotherapy rays emitted from the treatment head of the radiotherapy component directly irradiate the patient, guaranteeing treatment accuracy and effectiveness, and improving treatment efficiency.

[0056] Please refer to Figures 1 to 7 The first embodiment of this application provides a magnetic resonance-guided radiotherapy device 100, including a radiotherapy component 10, a magnet component 20 and a first drive assembly 30.

[0057] The radiotherapy component 10 includes a treatment head for emitting radiotherapy rays.

[0058] The treatment head is a radiation source and may include a linear accelerator, a target, and a collimator. The linear accelerator is used to accelerate electrons to generate an electron beam, the target can receive accelerated charged particles or ions to generate radiation rays for radiotherapy, and the collimator is used to control the shape of the radiation rays for radiotherapy. The treatment head may be configured as one or more groups.

[0059] The magnet component 20 is provided with a treatment space 201, which is used to place the patient 200.

[0060] The magnet component 20 includes a coil assembly 21 and a housing 22 constituting the treatment space 201. The coil assembly 21 is disposed in the internal space of the housing 22 and extends continuously around the treatment space 201 in a ring structure. The housing 22 is provided with at least one communicating space 202, which penetrates the housing 22 and communicates with the treatment space 201. The radiotherapy beam can pass through the communicating space 202 and be used to irradiate a part of the patient 200.

[0061] The internal space of the shell 22 is not connected to the treatment space 201, and the internal space of the shell 22 is not connected to the connected space 202.

[0062] The magnet component 20 may include components such as a superconducting magnet, a gradient coil, and a radio frequency coil. The gradient coil may be installed in the inner cylindrical hole of the superconducting magnet, while the radio frequency coil and other components may be placed in the inner cylindrical hole of the gradient coil. The shape of the connecting space 202 may be cylindrical, cuboid, or cylindrical.

[0063] A superconducting magnet typically includes a coil assembly 21, a housing 22, a cryostat 23, and an overpressure relief device 24. The center position of the superconducting magnet is O, which is also the center position of the magnet component 20. The imaging space (Diameter Sphere Volume, DSV) formed by it is located within the treatment space 201 and is essentially located at the center O. The axis Z of the superconducting magnet is the axis of the magnet component 20. The coil assembly 21 and the housing 22 can also be cylindrical, coaxial with the axis Z of the superconducting magnet, and have a rotationally symmetrical structure.

[0064] The first drive assembly 30 is disposed around the housing 22, and the treatment head is connected to the first drive assembly 30. The first drive assembly 30 is used to drive the treatment head to move relative to the magnet component 20 so that the radiotherapy beam passes through the communicating space 202 and is used to irradiate another part of the patient 200.

[0065] The first drive assembly 30 may include a motor driver, a transmission device (such as a belt, gear, or rack and pinion drive), and a position sensing device, and may also include a hydraulic cylinder or a pneumatic cylinder. The first drive assembly 30 can drive the treatment head to move or rotate relative to the magnet component 20, so that the radiation beam passes through the communicating space 202 and is used to irradiate another part of the patient 200. The treatment head may be at least partially mounted on its respective gantry and can rotate circumferentially in a "roller-like" manner about the axis of the gantry.

[0066] As can be seen from the above, the magnetic resonance-guided radiotherapy device 100 provided in this application embodiment has a treatment space 201 provided in the magnet component 20 for placing the patient 200. The housing 22 of the magnet component 20 also has a communicating space 202 connected to the treatment space 201. The coil assembly 21 is located in the internal space of the housing 22, extends continuously around the treatment space 201 and has a ring structure. The first driving assembly 30 is arranged around the housing 22, and the treatment head of the radiotherapy component 10 is connected to the first driving assembly 30. Therefore, it can... After the radiotherapy beam emitted from the treatment head of the radiotherapy component 10 irradiates one part of the patient 200, the first drive component 30 drives the treatment head of the radiotherapy component 10 to move relative to the magnet component 20, so that the radiotherapy beam passes through the connecting space 202 and is used to irradiate another part of the patient 200. This not only allows for irradiation treatment of multiple parts of the patient 200, but also ensures that the radiotherapy beam emitted from the treatment head of the radiotherapy component 10 directly irradiates the patient 200, thus guaranteeing treatment accuracy and effectiveness and improving treatment efficiency.

[0067] The magnetic resonance-guided radiotherapy device 100 provided in this embodiment has a through-space 202 in the path of the radiotherapy beam, allowing the radiotherapy beam to pass through the through-space 202 and ultimately enter the treatment space 201 to perform radiotherapy on the patient 200. Because the radiotherapy beam has little or no metal obstruction within the through-space 202, it can directly reach the lesion of the patient 200 with little or no attenuation.

[0068] It should be noted that the magnetic resonance-guided radiotherapy device 100 provided in this application embodiment may also include a control system (not shown in the figure) for controlling the radiotherapy process of the treatment head of the radiotherapy component 10, including beam output, power adjustment, treatment head orientation, etc., as well as the scanning process of the magnetic resonance device, including the linkage scanning of superconducting magnets, gradient coils and radio frequency coils, signal transmission and reception and image processing, etc., and coordinating radiotherapy and magnetic resonance scanning, etc.

[0069] It should also be noted that the connecting space 202 is provided between the coil assembly 21 and the housing 22 to better avoid obstructing the radiotherapy rays. The coil assembly 21 has several inner coils 211 and outer coils 213 that are symmetrical about the front and back of the central plane XY of the magnet component 20, as well as inner coil frame 212 and outer coil frame 214 that support the inner coils 211 and outer coils 213 respectively.

[0070] Please refer to Figures 1 to 7 In the first embodiment, the magnet component 20 is provided with a plurality of communicating spaces 202, and the plurality of communicating spaces 202 are arranged circumferentially along the housing 22. The radiotherapy beam can pass through one of the communicating spaces 202 and be used to irradiate a part of the patient 200. The first driving component 30 is used to drive the treatment head to rotate around the axis of the housing 22, so that the radiotherapy beam passes through another communicating space 202 and is used to irradiate another part of the patient 200. The magnetic resonance guided radiotherapy device 100 also includes a second driving component 40, which is connected to the housing 22 and is used to drive the housing 22 to rotate around the axis of the housing 22.

[0071] By adopting the above scheme, while the first drive assembly 30 drives the treatment head to move relative to the magnet component 20, the second drive assembly 40 drives the housing 22 to rotate around the axis of the magnet component 20, so that it passes through another connecting space 202 and is used to irradiate another part of the patient 200, avoiding the gap area 203 between two adjacent connecting spaces 202 from blocking the radiotherapy rays.

[0072] It should be noted that the second drive assembly 40 may include a motor driver, a transmission device (such as a belt, gear, or rack and pinion drive), and a position sensing device. It may be disposed on the outside of the housing 22. The axis of the connecting space 202 is also substantially located on the central symmetry plane XY of the magnet component 20, and this axis passes through or approximately through the center O of the magnet component 20. Multiple connecting spaces 202 may be circumferentially symmetrically distributed with the Z-axis as the axis of rotation, and the angle between the axes of two adjacent connecting spaces 202 on the XY plane is θ.

[0073] The second drive assembly 40 can drive the housing 22 to rotate around its axis by a preset angle, and the axis of the housing 22 can be the Z-axis in the figure. Specifically, taking the vertical surface OB of the magnet component 20 as a reference, the range of rotation of the OB surface around the Z-axis is + / -φ.

[0074] The relationship between the rotation angle φ of the shell 22 and the angle θ between the two adjacent connected spaces 202 is: θ = 2φ.

[0075] During radiotherapy, when the treatment head rotates to the axial position of the connecting space 202, the radiotherapy beam can be directly emitted into the treatment space 201 through the connecting space 202 without any metal obstruction in the radiation path. When the treatment head rotates to the center plane OA of the barrier zone between two adjacent connecting spaces 202, the angle between this plane and the vertical central symmetry plane YZ of the housing 22 is φ. At this time, the beam will face the obstruction of multiple metal materials and liquid helium, causing attenuation and scattering. At this time, the housing 22 is driven to rotate around the Z-axis by an angle φ through the second drive component 40, and the vertical plane OB of the housing 22 coincides with the center plane OA of the barrier zone. At this time, the treatment head is facing the connecting space 202 and can be directly emitted into the treatment space 201 through the connecting space 202 without any obstruction in the radiation path. This means that when the aforementioned radiotherapy component 10 needs to be rotated to any obstruction zone for radiation, the housing 22 is simultaneously driven to rotate around the Z-axis by an angle not exceeding + / -φ via the second drive component 40. This allows the treatment head to be realigned with a connected space 202 near the treatment head, thereby achieving unobstructed radiation, which is equivalent to achieving 360° unobstructed radiation to the patient 200.

[0076] Optionally, the included angle θ between the axes of two adjacent connected spaces 202 is 10°-45°, such as 10°, 15°, 20°, 25°, 30°, 35°, 40° or 40°.

[0077] This configuration allows the first drive assembly 30 to drive the radiotherapy component 10 to move relative to the magnet component 20, while the second drive assembly 40 drives the housing 22 to rotate around the axis of the housing 22 by a small preset angle. This enables the radiotherapy component to pass through another connecting space 202 and be used to irradiate another part of the patient 200. This avoids the gap 203 between two adjacent connecting spaces 202 from blocking the radiotherapy rays. It also prevents the uniformity of the magnet component from changing due to the spatial position change relative to the site environment caused by the large-angle rotation of the housing 22, which would affect the imaging quality and thus the treatment process and effect.

[0078] Optionally, the housing 22 includes an inner container 221, a heat shield layer 222, and an outer container 223 arranged sequentially from the inside to the outside. The treatment space 201 is the space surrounded by the inner container 221. The connecting space 202 passes through the inner container 221, the heat shield layer 222, and the outer container 223. The coil assembly 21 is located in the internal space of the inner container 221. Liquid helium is also provided in the internal space of the inner container 221.

[0079] This design allows for a simpler structure of the housing 22 and enables the use of liquid helium to immerse and cool the coil assembly 21.

[0080] In order to minimize the electromagnetic influence of the magnetic field on the radiotherapy rays, the beam exit point of the treatment head is located on the XY plane of the central symmetry of the magnet component 20. At the same time, the treatment head can rotate around the central axis Z of the magnet component 20. The coil assembly 21 generates a uniform axial magnetic field in the central region of the magnet component 20. The shell 22 is coaxially assembled with the coil assembly 21 and consists of an inner container 221, at least one heat shield layer 222, and an outer container 223 from the inside out. Each container layer includes an inner cylinder, a head, and an outer cylinder, corresponding to: inner cylinder 2211, inner cylinder head 2212, inner cylinder outer cylinder 2213, inner shield layer inner cylinder 2221, inner shield layer head 2222, outer shield layer outer cylinder 2223, inner cylinder 2231, outer container head 2232, and outer container outer cylinder 2233, respectively.

[0081] The connecting space 202 is composed of three layers of hollow pipes (inner pipe 2021, middle pipe 2022 and outer pipe 2023). Openings that mate with the three layers of hollow pipes are provided on the inner container outer cylinder 2213, the shielding layer outer cylinder 2223 and the outer container outer cylinder 2233 respectively. Openings that mate with the other end of the inner pipe 2021, the middle pipe 2022 and the outer pipe 2023 are provided on the inner container inner cylinder 2211, the shielding layer inner cylinder 2221 and the outer container inner cylinder 2231 respectively.

[0082] The two ends of the inner tube 2021 are connected and sealed at their openings to the outer cylinder 2213 and the inner cylinder 2211 of the inner container, respectively (usually by welding or other methods), thereby separating the internal space of the middle tube 2022 from the internal cavity of the inner container 221; similarly, the two ends of the middle tube 2022 are connected at their openings to the outer cylinder 2223 and the inner cylinder 2221 of the shielding layer, respectively (usually by welding or other methods), thereby separating the internal space of the middle tube 2022 from the internal cavity of the shielding layer; the two ends of the outer tube 2023 are connected at their openings to the outer cylinder 2233 and the inner cylinder 2231 of the outer container, respectively (usually by welding or other methods), thereby separating the internal space of the outer tube 2023 from the internal cavity of the outer container 223. At the same time, the inner tube 2021, the middle tube 2022, and the outer tube 2023 are nested within each other and separated from each other (similar to a nesting doll structure).

[0083] Correspondingly, coil assemblies 21 are not installed at the axial positions of the radiation rays emitted by the radiotherapy unit 10 and the aforementioned inner conduits 2021, middle conduits 2022, and outer conduits 2023. Typically, several inner coils 211 and outer coils 213 are symmetrically distributed along the Z-axis on the left and right sides of the inner conduits 2021, middle conduits 2022, and outer conduits 2023, respectively. Simultaneously, a clearance opening 2121 is provided on the inner coil frame 212 or the outer coil frame 214, and the size of this clearance opening 2121 allows the passage of the three nested inner conduits 2021, middle conduits 2022, and outer conduits 2023.

[0084] In the above configuration, the innermost inner conduit 2021 can pass through the multi-layer magnet container and the inner coil frame 212, directly connecting the cylindrical treatment space 201 inside the magnet component 20 and the external environment of the magnet component 20, thus ultimately forming a connecting space 202 that connects the outside of the magnet component 20 and the treatment space 201. When the radiotherapy beam is radiated from the opening of the outer cylinder 2233 of the outer container along the extension direction of the connecting space 202 into the treatment space 201 inside the magnet component 20, there is no metal material blocking the radiation path of the radiotherapy beam. This maximizes the protection of the beam energy from attenuation or scattering, resulting in good treatment effect and high precision.

[0085] It should be noted that the included angle θ between the axes of two adjacent connected spaces 202 is related to the number of connected spaces 202 and the required radiotherapy irradiation cross-sectional area. Under the premise of ensuring that the openings on the outer container 223 and the openings on each container do not interfere with each other (i.e., the holes on each layer of the cylinder will not be connected), θ can be 10°-45°, and the corresponding number of connected spaces 202 is 8-25.

[0086] It is understood that the included angle θ between the axes of the two adjacent connected spaces 202 is 10°-45°, so the range φ of the second drive assembly 40 driving the magnet component 20 to rotate around the Z-axis can not exceed 22.5°.

[0087] The magnetic resonance-guided radiotherapy device 100 provided in this application embodiment only needs to drive the magnet component 20 to rotate a small angle (not exceeding 22.5°) during radiotherapy to achieve a 360° radiation scan of the treatment head in the circumferential direction of the magnet component 20. At any angle of 360°, the radiotherapy beam is directly facing a hollow connected space 202. There is no metal material blocking the radiation path, so the radiotherapy beam will not be attenuated or scattered, and the beam energy and accuracy are greatly improved.

[0088] For the existing 360° rotating magnet component 20, due to the working direction of the refrigerator 23 and the cooling method, it cannot be cooled by liquid helium immersion and can only use permanent magnet, conductive cooling and other structural magnets. However, in this embodiment, since the rotation angle of the above-mentioned magnet component 20 is small (usually not exceeding 22.5°), this rotation angle will not affect the normal operation of the refrigerator 23. Therefore, a normal liquid helium immersion cooled superconducting magnet can be used. At the same time, the structure of the traditional liquid helium immersion magnet can be retained to the greatest extent. There is no need to set up an additional liquid helium connection device. The structure is simple and has good stability. There is no liquid helium in the hollow connection space 202, so the adverse effects of liquid helium and liquid helium level on the attenuation and scattering effect of radiation are also eliminated.

[0089] On the other hand, the magnetic resonance equipment installed on the site needs to be homogenized before imaging. However, due to the influence of the magnetic field environment of the site, the uniformity of the 360° rotating magnetic component may change significantly, resulting in poor imaging quality or even failure to image at certain angles. In this embodiment, the magnetic component 20 only rotates a very small angle, which greatly reduces the possibility of it being affected by the environmental magnetic field, resulting in better imaging quality and stronger system stability. At the same time, the complexity of the small-angle rotation mechanism is also significantly lower than that of the 360° rotation structure.

[0090] In addition, traditional magnets often include an axially extending connector 215 to connect and strengthen the structural strength of the inner coil frame 212 and the outer coil frame 214, resisting the strong electromagnetic force generated by the coil assembly 21 during operation. However, if this connector 215 is located in the rotation plane XY of the radiotherapy beam, it will obstruct the radiotherapy beam. Furthermore, the actual manufacturing process of superconducting magnets involves complex electronic components and electrical connections, such as superconducting connectors and coil protection devices. These electronic components and electrical connections cannot be directly irradiated by radiotherapy beams, otherwise, serious consequences such as magnet quenching may occur. The area where radiotherapy beams cannot effectively scan forms the so-called radiotherapy "blind zone." Existing magnetic resonance-guided radiotherapy equipment 100 often uses complex structures such as discrete magnets to eliminate or reduce the influence range of the "blind zone." In this embodiment, the connector 215 and superconducting electronic and electrical components can be disposed in the interval 203 between two adjacent connected spaces 202. In the linkage scanning mode of the magnet component 20 and the radiotherapy component 10, the connector 215 and superconducting electronic and electrical components in the interval 203 are completely not irradiated by radiotherapy rays.

[0091] Compared to the separate coil groups and coil frames specially designed for radiotherapy equipment in the prior art, as well as the corresponding discrete coil and container structures, the structure of the superconducting magnet in this embodiment is greatly simplified. Its multi-layer container main structure is consistent with that of a conductive superconducting magnet, which is simple in structure, high in strength, and low in cost. Moreover, the magnet component 20 is still a single connected cavity, without the pressure imbalance problem of discrete cavities. The entire magnet component 20 only requires one set of refrigerator 23 and overpressure relief device 24, and no additional communicating pipe is needed. Its coil group, coil frame and connector 215 are the same as or similar to those of conventional magnets. The coil frame has good structural strength and can withstand large electromagnetic forces. The overall processing and assembly precision of the coil and coil frame is high, which is suitable for the design of coils and coil frames with various field strengths. At the same time, the superconducting connector and coil manufacturing process of the coil assembly 21 are consistent with those of traditional magnets, which also greatly simplifies the manufacturing process of the magnet component 20.

[0092] Optionally, the connecting space 202 is set as a circular hole, and the inner diameter of the connecting space 202 is 50mm-300mm, such as 50mm, 100mm, 150mm, 200mm, 250mm or 300mm.

[0093] This configuration allows the connecting space 202 to have the maximum flux with a fixed cross-sectional area, meaning that the radiation beam emitted from the radiotherapy component 10 has the largest irradiation range when passing through the connecting space 202, while the magnet assembly as a whole has good strength.

[0094] It should be noted that in other embodiments, the communicating space 202 can be configured as a square hole, in which case the cross-section of the communicating space 202 is square. Alternatively, the communicating space 202 can be configured as a conical hole. Since the radiotherapy rays are emitted from the radiation head of the radiotherapy component 10 in a divergent manner from the outside to the inside during treatment, such a conical hole usually does not affect the irradiation range of the radiotherapy rays.

[0095] Please refer to Figure 8 and Figure 9 In the second embodiment, the magnetic resonance-guided radiotherapy device 100 further includes a carrier 50 and a third drive assembly 60 connected to each other. The carrier 50 is disposed in the treatment space 201 and is used to support the patient 200. The third drive assembly 60 is used to drive the carrier 50 to move relative to the magnet component 20.

[0096] By adopting the above scheme, the magnet component 20 can be avoided from blocking the radiotherapy rays, and the irradiation angle and range of the radiotherapy rays on the patient's lesion 200 can be increased, thereby increasing the scanning and treatment field of view and range.

[0097] It should be noted that the support component 50 may include a hospital bed and restraint mechanisms, etc. The third drive assembly 60 may include a motor driver, a transmission device (such as a belt, gear, or rack and pinion drive), and a position sensing device, etc. The control system can control the second drive assembly 40 and the third drive assembly 60 to perform position adjustments, etc.

[0098] Optionally, the third drive assembly 60 is used to drive the carrier 50 to rotate about the axis of the magnet component 20; and / or, the third drive assembly 60 is used to drive the carrier 50 to move in a direction parallel to the axis of the housing 22 or in a direction perpendicular to the axis of the housing 22.

[0099] With this configuration, the third drive assembly 60 can be used to drive the carrier 50 to rotate or move relative to the magnet component 20, thus meeting the usage requirements.

[0100] For example, the third drive assembly 60 can drive the hospital bed to rotate around the axis of the housing 22 by a certain angle. Specifically, taking the vertical surface OC of the hospital bed as a reference, the range of rotation of the OC surface around the axis (Z-axis) of the housing 22 is + / -γ, and the relationship between the rotation angle γ of the hospital bed and the angle θ between the two adjacent connected spaces 202 is: θ = 2γ.

[0101] During radiotherapy, when the treatment head rotates to the axial position of the connecting space 202, the radiotherapy beam can be directly emitted into the treatment space 201 through the connecting space 202 without any metal material obstructing the radiation path. When the treatment head needs to rotate to the center position (surface OB) of the obstruction zone 82 between two adjacent connecting spaces 202 to perform radiotherapy on the patient 200, the angle between the OB surface and the vertical central symmetry plane YZ of the shell 22 is γ. At this time, the radiotherapy beam will face the obstruction of multiple metal materials and liquid helium, causing attenuation and scattering. If the treatment head is driven back to the OA position, and the third drive component 60 drives the bed to rotate the patient 200 around the Z-axis by an angle γ, the vertical surface OC of the bed coincides with the OB surface. At this time, the treatment head is facing the connecting space 202, and the angle between the radiotherapy beam and the vertical surface OC of the bed is γ. It can then be directly emitted into the treatment space 201 through the connecting space 202 without any obstruction in the radiation path, and the radiation angle meets the preset requirements.

[0102] The magnetic resonance-guided radiotherapy device 100 provided in this application embodiment, during radiotherapy, when the aforementioned treatment head needs to be rotated to the obstruction zone for radiation, first rotates the treatment head to a position directly opposite a nearby connected space 202, and at the same time drives the bed to rotate around the Z-axis by an angle not exceeding + / -γ through the third drive component 60, so that the angle between the radiotherapy ray and the vertical plane of the bed reaches a preset value, which is equivalent to being able to perform 360° unobstructed radiation on the patient 200.

[0103] Because the rotation angle γ of the hospital bed in the above embodiment is small, the lateral sliding force generated by the patient 200's gravity during the rotation of the hospital bed is small. At the same time, the hospital bed in this embodiment can also be equipped with a restraint mechanism to restrain the patient 200 on the hospital bed and ensure that the two do not move relative to each other during the rotation of the hospital bed. The restraint mechanism can usually be a concave hospital bed, restraint straps, deformable air cushion and space capsule-type hospital bed, etc.

[0104] Since the magnet component 20 in the second embodiment of this application does not need to rotate during the entire treatment process, the uniformity of the magnet component 20 will not change, the magnetic field stability is good, and the structure is simple. In contrast, setting the third drive component 60 on the bed position is simpler in structure, easier to implement, and has a lower overall cost than driving the magnet component 20 to rotate.

[0105] In other embodiments, during radiotherapy using radiotherapy rays, the third drive assembly 60 can also drive the bed to move in any of the X / Y / Z directions, thereby further increasing the irradiation angle and irradiation range of the radiotherapy rays on the lesions of the patient 200, and increasing the scanning and treatment field of view and range.

[0106] In some embodiments, the connecting space 202 is asymmetrically distributed with respect to the Z-axis; in other embodiments, the magnet component 20 is an asymmetrical magnet, and the intersection of the plane containing the connecting space 202 and the axis of the magnet component 20 is located within or near the scanning field of view of the magnet component 20.

[0107] Among them, the gradient coil and radio frequency coil (especially the vertical emission coil) of the magnetic resonance device may also be provided with openings corresponding to the position of the connecting space 202, so that the attenuation and scattering of the radiotherapy rays on the path from the treatment head to the lesion are less.

[0108] Please refer to Figure 10 In the third embodiment, it should be noted that a second driving component 40 and a third driving component 60 are provided simultaneously. A first opening that mates with one end of the inner tube 2021 is provided on the outer cylinder 2213 of the inner container, and a second opening that mates with the other end of the inner tube 2021 is provided on the inner cylinder 2211 of the inner container. The two ends of the inner tube 2021 are connected and sealed to the outer cylinder 2213 and the inner cylinder 2211 of the inner container at the first opening and the second opening, respectively (usually by welding or other methods). This separates the internal space of the inner tube 2021 from the internal cavity of the inner container 221, thus forming a communicating space 202.

[0109] The central axis of rotation of the connecting space 202 is located approximately on the XY plane of symmetry of the magnet component 20, and this axis passes through or approximately through the center O of the magnet component 20. There are multiple connecting spaces 202, which can be symmetrically distributed around the Z-axis. The angle between the axes of two adjacent connecting spaces 202 on the XY plane is θ, which can be between 10° and 45°. In this case, the number of connecting spaces 202 is between 8 and 25.

[0110] Correspondingly, no coil assembly 21 is provided at the axial position of the radiotherapy ray and the aforementioned inner conduit 2021. Typically, several inner coils 211 and outer coils 213 are symmetrically distributed along the Z-axis on the left and right sides of the inner conduit 2021, the middle conduit 2022, and the outer conduit 2023, respectively. At the same time, a clearance opening 2121 is provided on the inner coil frame 212 or the outer coil frame 214, and the size of the clearance opening 2121 allows the aforementioned inner conduit 2021 to pass through.

[0111] In this embodiment, the heat shield 222 and outer container 223 are conventionally configured, making the manufacturing and assembly process of the entire coil assembly 21 and housing 22 simpler and reducing container cost. Simultaneously, during 360° radiotherapy using the aforementioned synergistic method, the radiotherapy beam is emitted from the outer cylinder 2233 of the outer container along the extension direction of the connecting space 202 towards the treatment space 201 inside the magnet component 20. The radiation path is blocked by the heat shield 222 and the outer container 223. Although there is partial blocking of the radiation path compared to the previous embodiment, the thickness of the blocking material remains consistent, and the attenuation and scattering ratio of the radiotherapy beam remain consistent, ensuring good intensity and accuracy of the radiotherapy beam irradiation.

[0112] Please refer to Figure 10 In the fourth embodiment, the connecting space 202 is set as an oblong hole. The length of the oblong hole is along the circumference of the housing 22. The width of the oblong hole can ensure the radiotherapy range in the Z direction. Compared with setting the connecting space 202 as a round hole, the number of connecting spaces 202 can be greatly reduced when the connecting space 202 is set as an oblong hole. At this time, the rotation angle of the magnet component 20 will be very small, such as within + / -10°. It is only necessary to avoid the connection part of two adjacent oblong holes, making the operation simpler and more convenient.

[0113] Please refer to Figures 12 to 16 In the fifth embodiment, the housing 22 is provided with an installation space 204, and at least one of the first drive assembly 30 and the radiotherapy component 10 is provided in the installation space 204.

[0114] By adopting the above solution, at least one of the first drive component 30 and the radiotherapy component 10 can be arranged inside the magnet component 20. There is no need to arrange a large rotating mechanism outside the magnet component 20. Instead, a small fixed frame is used, which greatly reduces the size of the entire device and significantly reduces the complexity of motion control, and the cost will also be greatly reduced.

[0115] Optionally, the length direction of the mounting space 204 is perpendicular to the axis of the housing 22, and the first drive assembly 30 is used to drive the treatment head to move within the mounting space 204 in a direction perpendicular to the axis of the housing.

[0116] With this setup, radiotherapy can be administered to 200 different parts of the patient using radiation rays emitted from the treatment head.

[0117] It should be noted that the first drive component 30 may include a motor driver, a transmission device (such as a belt, gear or rack drive, etc.) and a position sensing device, and may also include a hydraulic cylinder or a pneumatic cylinder.

[0118] For example, an installation space 204 is arranged above the magnet, and its through direction can be horizontal (i.e., along the X-axis in the figure). The treatment head of the radiotherapy component 10 is disposed in the installation space 204. The treatment head of the radiotherapy component 10 can emit radiotherapy rays. The radiotherapy rays will pass through the outer tube 2023, the middle tube 2022 and the inner tube 2021 in sequence, and then pass through the coil assembly 21, the inner cylinder of the inner container 2211, the inner cylinder of the shielding layer 2221 and the inner cylinder of the outer container 2231, as well as the gradient coil, radio frequency coil and outer shell inside the magnet component 20 (not shown in the figure), and finally reach the lesion site of the patient 200.

[0119] The outer tubing 2023, the middle tubing 2022, and the inner tubing 2021, as well as the corresponding container interface, can be rectangular passages with uniform cross-sectional dimensions and sufficiently large cross-sectional dimensions, such as 40cm*50cm, to accommodate the radiotherapy component 10. Alternatively, tubing with circular or irregular cross-sections can be used. Each tubing needs to have a certain thickness to resist various pressures and mechanical loads from the inner container 221, the heat shield layer 222, and the outer container 223.

[0120] To minimize the electromagnetic influence of the magnetic field on the radiotherapy beams, the beam exit point of the radiotherapy component 10 can be located on the XY plane of symmetry of the housing 22. Accordingly, no coil assembly 21 is provided at the axial position of the radiotherapy beams emitted from the treatment head. Typically, several inner coils 211 and outer coils 213 are symmetrically distributed on the left and right sides of the radiotherapy component 10 along the Z-axis. At the same time, a clearance opening 2121 is provided on the inner coil frame 212, so that the radiotherapy beams can pass directly without being blocked by the coils or the coil frame.

[0121] The first drive assembly 30 includes a motor driver, a transmission device (such as a belt, gear, or rack and pinion drive), and a position sensing device. These are respectively connected to the treatment head and the magnet component 20 (or gantry) located within the installation space 204, and drive the treatment head to move within the installation space 204 along the through direction (left-right direction in the figure). The maximum distance the treatment head can move in the left-right direction is L, which can be 30cm-60cm, ensuring that when the radiotherapy beam moves along the X-axis, it can irradiate all parts of the patient 200 on the XY section at that position. Furthermore, the irradiation of all parts of the patient 200 can be achieved by moving the support member 50 along the Z-axis.

[0122] In this design, the treatment head, which can move along the X-axis, provides a new degree of freedom in the selection of radiation positions, allowing for a larger irradiation range without rotating the treatment head.

[0123] It should be noted that when the treatment head radiates inward from different X-ray positions, the curvature of the shell 22 through which the radiotherapy rays pass varies, and the thickness of the material penetrated also changes, thus affecting the scattering or attenuation differences of the radiotherapy rays. However, since the overall diameter of the shell 22 is relatively large and the thickness is relatively small compared to the diameter, the above effects are not significant. Furthermore, the above-mentioned scattering or attenuation differences can be compensated for through theoretical calculations and experimental calibration, thereby improving the accuracy of radiotherapy. In addition, changes in the position of the treatment head may affect the uniformity of the magnet component 20, leading to poor MR imaging quality. Accordingly, a shielding component can be placed near the treatment head to eliminate this effect, or a high-order shimming coil can be installed on the magnet component 20 to compensate for the aforementioned magnetic field errors in real time.

[0124] Since the exit point of the treatment head is closer to the patient 200, the beam size of the radiation beam when passing through the inner coil 211 is greatly reduced. Therefore, the Z-direction width of the clearance opening 2121 on the inner coil frame 212 can be reduced, which means that the inner coils 211 on both sides of the treatment head can be closer together. For the design of the coil assembly 21, this reduction in size can greatly reduce its design difficulty, as well as the bus length and cost of the coil assembly 21.

[0125] Optionally, the magnetic resonance-guided radiotherapy device 100 further includes a second drive assembly 40, which is connected to the housing 22 and is used to drive the housing 22 to rotate about the axis of the housing 22.

[0126] With this configuration, the second drive assembly 40 can be used to drive the magnet component 20 to rotate around the axis of the housing, thereby achieving a full circumference scan of the patient 200.

[0127] Optionally, the magnetic resonance-guided radiotherapy device 100 also includes a carrier 50 and a third drive assembly 60 connected to each other. The carrier 50 is disposed in the treatment space 201 and is used to support the patient 200. The third drive assembly 60 is used to drive the carrier 50 to move relative to the magnet component 20.

[0128] By adopting the above scheme, the magnet component 20 can be avoided from blocking the radiotherapy rays, and the irradiation angle and range of the radiotherapy rays on the patient's lesion 200 can be increased, thereby increasing the scanning and treatment field of view and range.

[0129] Please refer to Figure 17 and Figure 18 In the sixth embodiment, multiple communication spaces 202, mounting spaces 204, first driving components 30 and radiotherapy components 10 are provided, and the multiple communication spaces 202, multiple mounting spaces 204, multiple first driving components 30 and multiple radiotherapy components 10 are provided in a one-to-one correspondence. The multiple communication spaces 202 are spaced apart along the circumferential direction of the housing 22.

[0130] By adopting the above scheme, 360° circumferential radiotherapy can be performed on patient 200 in treatment space 201.

[0131] It should be noted that multiple installation spaces 204 can be provided. The magnetic resonance-guided radiotherapy device 100 in the sixth embodiment also includes a gantry that connects multiple radiotherapy components 10 respectively, and a linear accelerator shared by the treatment heads in the multiple radiotherapy components 10.

[0132] A second drive assembly 40 can be provided, which is connected to the magnet component 20 and is used to drive the magnet component 20 to rotate around the axis of the housing 22 by a preset angle. Specifically, taking the vertical plane YZ of the housing 22 as a reference, the range of rotation of the YZ plane around the Z-axis is + / -φ. When three sets of symmetrical treatment heads are arranged, φ can be 60°, that is, the housing 22 only needs to rotate 60° to achieve 360° full-circle radiotherapy for the patient 200 within the treatment space 201.

[0133] For existing 360° circumferentially rotating magnets, due to the working direction of the refrigerator 23 and the cooling method, they cannot be cooled by liquid helium immersion and can only use permanent magnets, conductive cooling and other structural magnets. However, in this embodiment, since the rotation angle of the above-mentioned magnet component 20 is small, this rotation angle will not affect the normal operation of the refrigerator 23, so a normal liquid helium immersion cooled superconducting magnet can be used.

[0134] In addition, the magnetic resonance equipment installed on the site needs to be homogenized before imaging. However, due to the influence of the magnetic field environment of the site, the uniformity of the 360° rotating magnet component 20 may change significantly, resulting in poor imaging quality or even failure to image at certain angles. In this embodiment, the magnet component 20 only rotates a very small angle, which greatly reduces the possibility of it being affected by the environmental magnetic field, resulting in better imaging quality and stronger system stability. At the same time, the complexity of the small-angle rotation mechanism is also significantly lower than that of the 360° rotation structure.

[0135] It should be noted that in some embodiments, the installation space 204 is asymmetrically distributed with respect to the Z-axis. In other embodiments, the magnet component 20 is an asymmetrical magnet, and the intersection of the surface where the treatment head is located and the axis of the housing 22 is located within or near the scanning field of view of the magnet component 20, or at a certain angle to the vertical plane XY.

[0136] Please refer to Figure 19 In the seventh embodiment, the length direction of the mounting space 204 is parallel to the axis of the housing 22. The first driving component 30 is used to drive the treatment head to move in the mounting space 204 in a direction parallel to the axis of the housing. Multiple connecting spaces 202, mounting spaces 204, first driving components 30 and radiotherapy components 10 are provided, and the multiple connecting spaces 202, multiple mounting spaces 204, multiple first driving components 30 and multiple radiotherapy components 10 are provided in a one-to-one correspondence. The multiple connecting spaces 202 are spaced apart along the circumference of the housing 22.

[0137] By adopting the above method, radiotherapy can be performed on different parts of the patient using radiation rays emitted from the treatment head.

[0138] It should be noted that, in the seventh embodiment, the housing 22 is provided with a plurality of axially arranged installation spaces 204. The installation space 204 is composed of three layers of inner pipes 2021, middle pipes 2022 and outer pipes 2023. At the same time, the inner container end cap 2212, the shielding layer end cap 2222 and the outer container end cap 2232 inside the housing 22 are respectively provided with a first opening, a second opening and a third opening that respectively cooperate with the two ends of the inner pipes 2021, the middle pipes 2022 and the outer pipes 2023.

[0139] Both ends of the inner pipe 2021 can be connected to and sealed with the inner container end cap 2212 at the first opening (usually by welding), thus separating the internal space of the inner pipe 2021 from the internal cavity of the inner container 221. Similarly, both ends of the middle pipe 2022 can be connected to the shielding layer end cap 2222 at the second opening, thus separating the internal space of the middle pipe 2022 from the internal cavity of the shielding layer. Both ends of the outer pipe 2023 can be connected to the outer container end cap 2232 at the third opening, thus separating the internal space of the outer pipe 2023 from the internal cavity of the outer container 223. The inner pipe 2021, middle pipe 2022, and outer pipe 2023 are nested and separated from each other (similar to a nesting doll structure), and the internal cavity of the installation space 204 is actually connected to the atmosphere.

[0140] Multiple radiotherapy units 10 are disposed in different installation spaces 204, and a second drive assembly 40 is also included, which can drive the housing 22 to rotate around its axis by a certain angle. When six sets of symmetrical radiotherapy units 10 are arranged, φ is preferably 30°, that is, the housing 22 only needs to rotate 30° to achieve 360° circumferential radiotherapy for the patient 200 in the treatment space 201.

[0141] In this design, the linear accelerator and power components of the treatment head of the radiotherapy component 10 can be arranged at the end of the housing 22. The housing 22 requires a smaller rotation angle, the magnetic resonance-guided radiotherapy system is more compact, the housing 22 is easier to manufacture, and more installation space 204 and radiotherapy component 10 can be arranged as needed.

[0142] The above embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application, and should all be included within the protection scope of this application.

Claims

1. A magnetic resonance-guided radiotherapy device, characterized in that, include: A radiotherapy component (10), the radiotherapy component (10) including a treatment head; A magnet component (20) is provided with a treatment space (201); the magnet component (20) includes a coil assembly (21) and a housing (22) constituting the treatment space (201). The coil assembly (21) is disposed in the internal space of the housing (22). The coil assembly (21) extends continuously around the treatment space (201) and has a ring structure. At least one communicating space (202) is provided on the housing (22). The communicating space (202) penetrates the housing (22) and communicates with the treatment space (201). A first drive assembly (30) is disposed around the housing (22), and the treatment head is connected to the first drive assembly (30). The first drive assembly (30) is used to drive the treatment head to move relative to the magnet component (20).

2. The magnetic resonance-guided radiotherapy device according to claim 1, characterized in that, The magnet component (20) is provided with a plurality of communicating spaces (202), and the plurality of communicating spaces (202) are arranged circumferentially spaced along the housing (22). The first driving component (30) is used to drive the treatment head to rotate around the axis of the housing (22). The magnetic resonance guided radiotherapy device (100) further includes a second driving component (40), which is connected to the housing (22) and is used to drive the housing (22) to rotate around the axis of the housing (22).

3. The magnetic resonance-guided radiotherapy device according to claim 2, characterized in that, The included angle between the axes of two adjacent connected spaces (202) is 10°-45°.

4. The magnetic resonance-guided radiotherapy device according to claim 1, characterized in that, The housing (22) includes an inner container (221), a heat shield layer (222), and an outer container (223) arranged sequentially from the inside to the outside. The treatment space (201) is the space surrounded by the inner container (221). The connecting space (202) passes through the inner container (221), the heat shield layer (222), and the outer container (223). The coil assembly (21) is located in the internal space of the inner container (221). Liquid helium is also provided in the internal space of the inner container (221).

5. The magnetic resonance-guided radiotherapy device according to claim 1, characterized in that, The housing (22) is provided with an installation space (204), and at least one of the first drive assembly (30) and the radiotherapy component (10) is located in the installation space (204).

6. The magnetic resonance-guided radiotherapy device according to claim 5, characterized in that, The length direction of the installation space (204) is parallel to or perpendicular to the axis of the housing (22).

7. The magnetic resonance-guided radiotherapy device according to claim 6, characterized in that, The magnetic resonance-guided radiotherapy device (100) further includes a second drive assembly (40), which is connected to the housing (22) and is used to drive the housing (22) to rotate about the axis of the housing (22).

8. The magnetic resonance-guided radiotherapy device according to claim 5, characterized in that, Multiple communication spaces (202), multiple installation spaces (204), multiple first drive components (30) and multiple radiotherapy components (10) are provided, and the multiple communication spaces (202), multiple installation spaces (204), multiple first drive components (30) and multiple radiotherapy components (10) are provided in a one-to-one correspondence. The multiple communication spaces (202) are arranged at intervals along the circumference of the housing (22).

9. The magnetic resonance-guided radiotherapy device according to any one of claims 1 to 8, characterized in that, The magnetic resonance-guided radiotherapy device (100) further includes a carrier (50) and a third drive assembly (60) connected to each other. The carrier (50) is located in the treatment space (201) and is used to support the patient (200). The third drive assembly (60) is used to drive the carrier (50) to move relative to the magnet component (20).

10. The magnetic resonance-guided radiotherapy device according to claim 9, characterized in that, The third drive assembly (60) is used to drive the carrier (50) to rotate about the axis of the magnet component (20); and / or, the third drive assembly (60) is used to drive the carrier (50) to move in a direction parallel to the axis of the housing (22) or perpendicular to the axis of the housing (22).

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