Arc therapy device and operation method therefor, and accelerator and magnetic-field adjustment apparatus

Abstract

Provided in the present application are an arc therapy device and an operation method and device therefor, and a particle accelerator, a magnetic-field adjustment apparatus, a computer-readable storage medium and a computer program product. The particle accelerator, which is applied to a radiotherapy system, rotates along with a treatment frame during the rotation of the treatment frame. The magnetic-field adjustment apparatus is used for adjusting a particle deflection magnetic field in the particle accelerator on the basis of a change in the angle of a frame, such that under the action of the particle deflection magnetic field, particle beams generated by a particle radiation source meet a preset particle beam condition, which is used for indicating preset ranges of one or more parameters of the particle beams, i.e., the energy of particle beams, the size of beam spots and positions of beam spots. By means of the present application, it is ensured that changes in related parameters of particle beams are within an acceptable range during the rotation of a treatment frame.

Description

Arc radiotherapy equipment and operation method thereof, accelerator, and magnetic field adjustment device

[0001] This application claims priority to Chinese Patent Application No. 202311087319.8 filed on August 28, 2023, which is incorporated by reference in its entirety. Technical Field

[0002] The present application relates to an arc radiation therapy device and an operating method thereof, an operating device, a particle accelerator, a magnetic field adjustment device, a computer-readable storage medium, and a computer program product. Background Art

[0003] Particle radiotherapy is a modern cancer treatment method that uses high-energy particles to precisely target tumor cells, releasing energy precisely within them and killing them. Particle radiotherapy can precisely control the dose and range of radiation, minimizing damage to healthy tissue while enhancing treatment effectiveness.

[0004] Particle arc therapy (PAT) is a particle radiation therapy method in which the gantry rotates continuously during treatment to adjust the beam field angle. The PAT treatment planning system (TPS) distributes the uncertainty of the particle range across different angles, providing robustness. During gantry rotation, the coils that provide the particle deflection magnetic field may shift slightly, causing the magnetic field to shift in direction, ultimately affecting the stability of particle beam parameters.

[0005] Based on this, the present application provides an arc radiotherapy device and an operating method thereof, an operating device, a particle accelerator, a magnetic field adjustment device, a computer-readable storage medium, and a computer program product to improve the relevant technology.

[0006] Summary of the Invention

[0007] The purpose of the present application is to provide an arc radiotherapy device and an operating method thereof, an operating device, a particle accelerator, a magnetic field adjustment device, a computer-readable storage medium, and a computer program product to ensure that changes in relevant parameters of the particle beam are within an acceptable range during the rotation of the treatment gantry.

[0008] The purpose of this application is achieved by the following technical solutions:

[0009] In a first aspect, the present application provides a magnetic field adjustment device for use with a particle accelerator mounted on a treatment gantry in a radiotherapy system, wherein the particle accelerator rotates with the treatment gantry during rotation of the treatment gantry; the particle accelerator is a cyclotron accelerator, and the particle accelerator includes a magnetic field providing device, wherein the magnetic field providing device includes one or more superconducting coils capable of achieving a superconducting state;

[0010] The magnetic field adjustment device is used to adjust the particle deflection magnetic field in the particle accelerator according to the change of the treatment gantry angle, so that the particle beam generated by the particle radiation source meets the preset particle beam conditions under the action of the particle deflection magnetic field;

[0011] The particle beam condition is used to indicate a preset range of one or more parameters of the particle beam: energy, beam spot size, and beam spot position.

[0012] In some possible implementations, the magnetic field adjustment device includes a detection component, a control component, and one or more execution components;

[0013] The detection component is installed inside the particle accelerator and is used to detect magnetic field information of the particle deflection magnetic field;

[0014] The control component is used to calculate motion control information of the magnetic field providing device of the particle accelerator based on the magnetic field information and a preset magnetic field condition, and generate a first control instruction corresponding to each of the execution components based on the motion control information; wherein the preset magnetic field condition is determined according to the particle beam condition;

[0015] Each of the execution components is connected to the control component and the magnetic field providing device, and is used to adjust the position and / or direction of the magnetic field providing device according to its corresponding first control instruction.

[0016] In some possible implementations, the detection component includes one or more Hall detection units for detecting one or more positions of the particle deflection magnetic field to obtain the magnetic field information; and / or,

[0017] The magnetic field adjustment device includes first to fourth actuators, the first and second actuators are located on the first side of the magnetic field providing device, the third and fourth actuators are located on the second side of the magnetic field providing device, and the first and second sides of the magnetic field providing device are arranged opposite to each other; a first line is obtained by connecting the center of the first actuator and the center of the fourth actuator, and a second line is obtained by connecting the center of the second actuator and the center of the third actuator, and the first line intersects with the second line.

[0018] In some possible implementations, each of the execution components includes a first drive controller, a first drive mechanism, and a first transmission mechanism;

[0019] The control component is used to calculate the target displacement of each first transmission mechanism according to the motion control information, and generate a first control instruction corresponding to the execution component to which it belongs according to the target displacement of each first transmission mechanism;

[0020] In each of the execution components, the first transmission mechanism is fixedly connected to the magnetic field providing device, and the first drive controller is used to drive the first drive mechanism to move according to the first control instruction corresponding to the execution component, so that the first drive mechanism drives the first transmission mechanism to move the target displacement, thereby adjusting the position and / or direction of the magnetic field providing device.

[0021] In some possible implementations, each of the execution components further includes a position detection mechanism, and in each of the execution components:

[0022] The position detection mechanism is used to detect in real time the real-time displacement of the first transmission mechanism and send it to the control component, so that the control component generates a new first control instruction according to the real-time displacement and target displacement of the first transmission mechanism and sends it to the first drive controller;

[0023] The first drive controller is used to drive the first drive mechanism to move according to the new first control instruction, and drive the first transmission mechanism to move through the first drive mechanism, so that the real-time displacement of the first transmission mechanism matches the target displacement.

[0024] In some possible implementations, the first driving mechanism uses a motor; and / or,

[0025] The first transmission mechanism adopts a mechanical shaft; and / or,

[0026] The position detection mechanism adopts a potentiometer.

[0027] Each of the execution components is used to adjust the position and / or direction of the magnetic field providing device according to its corresponding first control instruction.

[0028] In a second aspect, the present application provides a particle accelerator for use in a radiotherapy system, wherein during rotation of a treatment gantry, the particle accelerator rotates along with the treatment gantry;

[0029] The particle accelerator comprises:

[0030] a particle radiation source for generating a particle beam;

[0031] a cavity for accelerating the particle beam therein;

[0032] a magnetic field providing device, for providing a particle deflection magnetic field for the cavity;

[0033] Any of the above-mentioned magnetic field adjustment devices is used to adjust the particle deflection magnetic field.

[0034] In some possible implementations, the particles corresponding to the particle beam are protons or heavy ions.

[0035] In some possible implementations, the particle accelerator further includes:

[0036] The beam spot size adjusting device is used to adjust the beam spot size of the particle beam.

[0037] In some possible implementations, the beam spot size adjustment device includes one or more adjustment components, each of which includes a second drive controller, a second drive mechanism, a second transmission mechanism, and a shielding mechanism;

[0038] In each of the adjustment components, the second transmission mechanism is fixedly connected to the shielding mechanism, and the second drive controller is used to drive the second drive mechanism to move according to the second control instruction corresponding to the adjustment component, so that the second drive mechanism drives the second transmission mechanism to move, thereby adjusting the shielding state of the shielding mechanism.

[0039] In some possible implementations, the second driving mechanism is a motor; and / or,

[0040] The second transmission mechanism adopts a screw rod; and / or,

[0041] The shielding mechanism adopts a plurality of shielding plates which are arranged in pairs and symmetrically along the center line.

[0042] In some possible implementations, the particle accelerator further includes:

[0043] a radio frequency device for providing an accelerating electric field to the cavity; and / or,

[0044] a vacuum device for providing a vacuum environment for the cavity; and / or,

[0045] A liquid cooling device is used to cool the cavity by using cooling liquid.

[0046] In a third aspect, the present application provides an arc-shaped radiotherapy device, comprising:

[0047] Any of the above particle accelerators for generating and regulating particle beams;

[0048] a beam delivery system for delivering the particle beam;

[0049] Patient positioning system, used to achieve patient positioning;

[0050] The treatment gantry is used to drive the particle accelerator and the beam distribution system to rotate around the isocenter to achieve particle arc radiotherapy.

[0051] In some possible implementations, the beam delivery system includes a treatment head, and the treatment head includes an active beam scanning treatment head and / or a passive scattering treatment head; and / or,

[0052] The patient positioning system includes a treatment couch and an imaging system.

[0053] In some possible implementations, the arc radiation therapy device further includes:

[0054] a safety interlocking system for performing safety monitoring on the particle accelerator, the beam delivery system, the patient positioning system, and the treatment gantry; and / or

[0055] a treatment planning system for generating a treatment plan based on the patient's preoperative medical imaging data; and / or,

[0056] The control software system is used to verify the treatment plan and record treatment process data.

[0057] In a fourth aspect, the present application provides a method for operating an arc radiotherapy device, for operating any of the above-mentioned arc radiotherapy devices, the method comprising:

[0058] Obtaining a treatment plan, the treatment plan including a plurality of preset angle intervals and a set dose corresponding to each of the preset angle intervals;

[0059] The treatment gantry is rotated to each of the preset angle intervals respectively to complete the irradiation process of the particle beam corresponding to each of the preset angle intervals, thereby completing the arc radiation therapy process.

[0060] In some possible implementations, the preset angle interval is a point value or a range value. That is, each preset angle interval may refer to an angle or an angle range.

[0061] In some possible implementations, before rotating the treatment gantry, the method further includes:

[0062] Adjust the treatment bed to the preset irradiation position;

[0063] Acquire the patient's intraoperative medical imaging data through the imaging system;

[0064] Performing image registration on the patient's intraoperative medical imaging data and the treatment plan to obtain treatment couch adjustment information;

[0065] The position and angle of the treatment bed are adjusted according to the treatment bed adjustment information.

[0066] In some possible implementations, after adjusting the position and angle of the treatment couch, the method further includes:

[0067] reacquiring intraoperative medical imaging data of the patient through the imaging system;

[0068] detecting whether the reacquired intraoperative medical imaging data and the treatment plan have been registered;

[0069] If the registration is completed, rotating the treatment gantry is performed;

[0070] If the registration is not completed, the treatment couch adjustment information is re-acquired to readjust the treatment couch.

[0071] In some possible implementations, the preset angle interval uses point values, represented by preset angles, and during arc radiation therapy, the following processing is performed:

[0072] S1: rotating the treatment gantry to a first preset angle;

[0073] S2: Extending the treatment head to start the particle beam irradiation process;

[0074] S3: monitoring the irradiation dose of the particle beam at the preset angle, and stopping the irradiation process of the particle beam when the irradiation dose of the particle beam reaches a set dose corresponding to the preset angle;

[0075] S4: retract the treatment head;

[0076] S5: Detect whether the next preset angle exists; if so, execute S6; if not, execute S7;

[0077] S6: Rotate the treatment gantry to the next preset angle and execute S2;

[0078] S7: End of arc radiation therapy process.

[0079] In some possible implementations, the preset angle interval uses a range value, and during arc radiation therapy, the following processing is performed:

[0080] R1: Rotate the treatment gantry to the first preset angle range;

[0081] R2: Extend the treatment head and start the particle beam irradiation process;

[0082] R3: monitoring the irradiation dose of the particle beam within the preset angle interval, and when the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle interval, detecting whether there is a next preset angle interval; if so, executing R4; if not, executing R5;

[0083] R4: Rotate the treatment gantry to the next preset angle interval and execute R3;

[0084] R5: Stop the irradiation process of the particle beam, retract the treatment head, and end the arc radiotherapy process.

[0085] In some possible implementations, the extended position of the treatment head does not exceed a preset position, and the preset position is determined according to a preset collision constraint condition.

[0086] In a fifth aspect, the present application provides an operating device for an arc radiotherapy device, for operating any of the above-mentioned arc radiotherapy devices, the operating device comprising a memory and one or more processors, the memory storing a computer program, the one or more processors being configured to implement the following steps when executing the computer program:

[0087] Obtaining a treatment plan, the treatment plan including a plurality of preset angle intervals and a set dose corresponding to each of the preset angle intervals;

[0088] The treatment gantry is rotated to each of the preset angle intervals respectively to complete the irradiation process of the particle beam corresponding to each of the preset angle intervals, thereby completing the arc radiation therapy process.

[0089] In a sixth aspect, the present application provides a computer-readable storage medium, which stores a computer program. When the computer program is executed by one or more processors, it implements the steps of any of the above methods or implements the functions of any of the above operating devices.

[0090] In a seventh aspect, the present application provides a computer program product, which includes a computer program, and when the computer program is executed by one or more processors, it implements the steps of any of the above methods or implements the functions of any of the above operating devices. BRIEF DESCRIPTION OF THE DRAWINGS

[0091] The present application is further described below with reference to the accompanying drawings and specific implementation methods.

[0092] FIG1 is a structural block diagram of an arc radiotherapy device provided in an embodiment of the present application.

[0093] FIG2 is a schematic diagram of a partial structure of an arc-shaped radiotherapy device provided in an embodiment of the present application.

[0094] FIG3 is a flow chart of an operating method of an arc radiotherapy device provided in an embodiment of the present application.

[0095] FIG4 is a schematic diagram of a process for adjusting a treatment bed provided in an embodiment of the present application.

[0096] FIG5 is a flow chart of a first implementation of an arc radiation therapy process provided in an embodiment of the present application.

[0097] FIG6 is a flow chart of a second implementation of an arc radiation therapy process provided in an embodiment of the present application.

[0098] FIG7 is a structural block diagram of an operating device provided in an embodiment of the present application.

[0099] FIG8 is a structural block diagram of a particle accelerator provided in an embodiment of the present application.

[0100] FIG9 is a schematic structural diagram of a beam spot size adjustment device provided in an embodiment of the present application.

[0101] FIG10 is a schematic structural diagram of a cover plate provided in an embodiment of the present application.

[0102] FIG11 is a structural block diagram of a magnetic field adjustment device provided in an embodiment of the present application.

[0103] FIG12 is a three-dimensional diagram of a magnetic field providing device and an execution component provided in an embodiment of the present application.

[0104] FIG13 is a structural block diagram of an execution component provided in an embodiment of the present application.

[0105] FIG14 is a schematic diagram of the structure of an execution component provided in an embodiment of the present application.

[0106] FIG15 is a side view of a magnetic field providing device and an execution component provided in an embodiment of the present application.

[0107] FIG16 is a top view of a magnetic field providing device and an execution component provided in an embodiment of the present application.

[0108] FIG17 is a control logic diagram of a magnetic field adjustment device provided in an embodiment of the present application.

[0109] FIG18 is a schematic diagram of the structure of a computer program product provided in an embodiment of the present application. DETAILED DESCRIPTION

[0110] The technical solutions in this application will be described below in conjunction with the accompanying drawings and specific implementation methods of this application. It should be noted that, under the premise of no conflict, the various implementation methods or technical features described below can be arbitrarily combined to form a new implementation method.

[0111] In the examples of this application, words such as "exemplary" or "for example" are used to indicate examples, illustrations, or descriptions. Any embodiment or design described as "exemplary" or "for example" in the examples of this application should not be interpreted as being preferred or advantageous over other embodiments or designs. Rather, the use of words such as "exemplary" or "for example" is intended to present the relevant concepts in a concrete manner.

[0112] The first, second, etc. descriptions appearing in the embodiments of the present application are only used for illustration and distinction of the description objects. There is no order, nor does it indicate a special limitation on the quantity in the embodiments of the present application, and cannot constitute any limitation on the embodiments of the present application.

[0113] The following is a brief description of the technical field and related terms of the embodiments of the present application.

[0114] Particle radiotherapy is a modern cancer treatment method that uses high-energy particles to precisely target tumor cells, releasing their energy precisely within them and killing them. Examples of these particles are protons and heavy ions (such as helium and carbon ions). Compared to traditional photon radiotherapy, particle radiotherapy allows for more precise control of the dose and range of radiation, minimizing damage to healthy tissue while improving treatment effectiveness.

[0115] Proton therapy is a radiotherapy technique that uses high-energy proton beams to precisely target tumors. Compared to traditional X-ray radiotherapy, proton therapy allows for better control of radiation dose delivery, reduces damage to normal tissue, and improves treatment efficacy. Proton therapy exploits the physical properties of protons: upon entering the body, the proton beam reaches its maximum dose (the Bragg peak) at a certain depth, then rapidly decreases until it reaches zero. This property enables the proton beam to deliver the maximum dose within the tumor while minimizing dose deposition in normal tissues behind the tumor, thereby reducing treatment side effects. Proton therapy is suitable for a wide range of tumor types, including pediatric tumors, brain tumors, head and neck tumors, chest tumors, abdominal tumors, bone tumors, and soft tissue tumors. Proton therapy is particularly suitable for tumors located near critical organs or those that are sensitive to radiation. Compared to traditional radiotherapy, proton therapy can better spare normal tissues and organs, reducing treatment side effects. Particularly for pediatric patients, proton therapy can reduce long-term treatment complications and lower the risk of secondary tumors. Several studies have shown that proton therapy can provide comparable therapeutic effects to traditional radiotherapy in certain situations, while reducing adverse reactions.

[0116] Particle Arc Therapy (PAT) is a particle radiation therapy method in which the treatment gantry can continuously rotate to adjust the beam angle during treatment. Two approaches can be used: after the treatment gantry rotates to a specific angle, the particle accelerator and treatment head can quickly recover (for example, in less than 5 seconds) and deliver the beam; during the rotation of the treatment gantry, the particle accelerator and treatment head can continuously generate and deliver the beam (the treatment head does not retract or extend). Compared with multi-field intensity modulated proton therapy (IMPT), PAT can reduce the integrated dose outside the target area without affecting the overall treatment time. The PAT treatment planning system (TPS) can distribute the uncertainty of the particle range across different angles, providing greater robustness.

[0117] This application provides a device that can provide particle arc radiotherapy, namely, an arc radiotherapy device. This device can reduce the integrated dose of the high-energy particle beam outside the target area by increasing the treatment field angle. Furthermore, because the treatment gantry can continuously irradiate during continuous rotation (or quickly resume irradiation after rotating to a specific angle), the overall treatment time is not affected.

[0118] Arc radiation therapy equipment, for example, includes the following parts:

[0119] 1. Particle accelerator: This subsystem generates proton and heavy ion beams, including helium and carbon ions, and delivers them to the beam delivery system. The accelerator subsystem includes an ion source, radio frequency (RF), magnets, vacuum, water cooling, adaptive coils, and beam spot size adjustment components.

[0120] 2. Beam delivery system: ensures the correct delivery of treatment prescription parameters. It includes treatment heads, including active beam scanning treatment heads and passive scattering treatment heads.

[0121] 3. Patient positioning system: Achieve accurate and efficient patient positioning, including treatment bed and imaging system.

[0122] 4. Treatment gantry: drives the particle accelerator and beam delivery system to rotate around the isocenter to achieve particle arc radiotherapy.

[0123] 5. Safety interlocking system: ensures the safety of the equipment during operation and treatment, prevents accidents and reduces potential risks.

[0124] 6. Control software system: controls the operation of the equipment and the treatment process, ensures the safety of patients and operators, verifies treatment plan data, and records treatment process data, etc.

[0125] 7. Treatment Planning System: Used to plan, optimize, and simulate radiotherapy treatment plans. Generate high-quality arc irradiation plans based on the patient's medical image data.

[0126] There are two methods for operating the arc radiation therapy device:

[0127] Option 1: The treatment head needs to be retracted / extended before and after gantry rotation. The operation process includes loading the treatment plan, rotating the gantry to the predetermined angle, adjusting the treatment couch to the irradiation position, acquiring image data, image registration, adjusting the position and angle of the treatment couch, confirming the adjusted position of the treatment couch, extending the treatment head to start irradiation, stopping beam delivery when the set dose is reached, retracting the treatment head, rotating the gantry to the next predetermined angle, and repeating until irradiation is completed at all predetermined angles, thus concluding the treatment process.

[0128] Option 2: No need to retract / extend the treatment tip before and after gantry rotation. The procedure is similar to Option 1, but in this case, the extension and retraction of the treatment tip are based on a precalculated maximum extension position for the entire arc treatment plan, and this value is used as a limit to constrain the extension of the treatment tip.

[0129] The solutions provided in the embodiments of the present application relate to radiotherapy technology, which is specifically described through the following embodiments. It should be noted that the description order of the following embodiments does not limit the preferred order of the embodiments.

[0130] The following will first introduce the arc radiotherapy equipment and its operation method and operating equipment, and then introduce the particle accelerator and its magnetic field adjustment device.

[0131] (Arc radiation therapy equipment).

[0132] 1 and 2 , FIG1 is a structural block diagram of an arc-shaped radiotherapy device provided in an embodiment of the present application, and FIG2 is a partial structural schematic diagram of an arc-shaped radiotherapy device provided in an embodiment of the present application.

[0133] An embodiment of the present application provides an arc-shaped radiotherapy device, the arc-shaped radiotherapy device comprising:

[0134] particle accelerators, used to generate and manipulate particle beams;

[0135] a beam delivery system for delivering the particle beam;

[0136] Patient positioning system, used to achieve patient positioning;

[0137] The treatment gantry is used to drive the particle accelerator and the beam distribution system to rotate around the isocenter to achieve particle arc radiotherapy.

[0138] The arc radiotherapy device is an integrated radiotherapy device, which includes a particle accelerator, a beam delivery system, a patient positioning system and a treatment gantry.

[0139] Particle accelerators are used to generate and adjust particle beams. Particle accelerators generate high-energy particle beams according to the treatment plan. By adjusting the energy and spot size of the particle beam, precise irradiation of tumor tissue is achieved. Particle beams, such as high-energy proton beams or heavy ion beams (e.g., helium ions, carbon ions, etc.), are used to irradiate specific areas of the patient during radiotherapy to treat tumors. Particle accelerators, such as isochronous cyclotrons or synchrocyclotrons, are used.

[0140] The beam delivery system is responsible for delivering the particle beam from the particle accelerator to the patient. It uses magnetic field control to precisely deliver the particle beam to the treatment site, ensuring accurate positioning and delivery of the particle beam.

[0141] The patient positioning system is used to accurately position the patient. Before treatment begins, the patient will be placed in the correct position to ensure that the particle beam can accurately irradiate the tumor area while minimizing the impact on surrounding normal tissue.

[0142] The gantry is the supporting and rotating component of the entire system. It drives the particle accelerator and beam delivery system, rotating around the isocenter (point). This arc-shaped rotation allows the particle beam to irradiate the tumor from different angles, achieving comprehensive and precise radiotherapy.

[0143] The advantage of this is that the use of a particle accelerator allows for precise adjustment of the energy and spot size of the particle beam, thereby achieving high-precision treatment of tumors, reducing damage to surrounding normal tissues, and maximizing the protection of the patient's healthy tissues; the arc-shaped rotation of the treatment gantry allows the particle beam to irradiate the tumor from different angles, achieving all-round radiotherapy, which can more comprehensively irradiate tumor tissue and improve the treatment effect; the arc-shaped radiotherapy equipment has greater flexibility and can select appropriate radiation angles and treatment plans according to the patient's specific situation and treatment plan to achieve personalized treatment; the arc-shaped radiotherapy equipment can complete radiotherapy at multiple angles in a shorter time, thereby improving treatment efficiency and reducing the patient's stay in the treatment machine.

[0144] As an example, the treatment gantry uses an arc-shaped track that can guide and rotate around the beam within a 190° range (from -5° to 185°), as shown in Figure 2. The starting and ending points of the arc are defined as points above and below the lying patient, respectively. The gantry's motion, combined with the translation and rotation capabilities of the treatment couch, can cover all clinical treatment angles, meeting diverse treatment needs.

[0145] The benefits of this approach are that the treatment gantry can achieve highly flexible rotational motion, allowing the particle beam to rotate within a 190-degree range, covering a wide range of treatment angles and providing precise, multi-angle irradiation for different tumor locations and shapes, thereby improving treatment effectiveness. The gantry's motion, combined with the treatment couch's rotational capability, enables precise patient positioning. By ensuring accurate alignment of the particle beam with the target tumor, radiation damage to surrounding normal tissue is minimized, improving treatment accuracy and safety. The particle accelerator is mounted on the treatment gantry and can rotate with it. This design decision reduces the complexity of the device by eliminating the need for a beam transmission line, simplifying the device structure. This also improves beam stability, as beam transmission lines inevitably introduce beam instability. This eliminates the need for a beam transmission line, reducing maintenance costs and failure rates, while improving device stability and reliability. By reducing the introduction of instability, the beam motion is more stable, helping to maintain particle beam stability and ensure precise irradiation. The beam transmission line, also known as the beam transport line, comprises a series of components, including deflection magnets, quadrupoles, vacuum, water cooling, and beam diagnosis.

[0146] In some embodiments, the beam delivery system includes a treatment head, and the treatment head includes an active beam scanning treatment head and / or a passive scattering treatment head; and / or,

[0147] The patient positioning system includes a treatment couch and an imaging system.

[0148] The beam delivery system is responsible for delivering the particle beam from the particle accelerator to the target area of ​​the patient, ensuring the correct delivery of the dose set in the treatment plan. The beam delivery system includes an active beam scanning treatment head and / or a passive scattering treatment head.

[0149] An active beam scanning therapy head may, for example, include a scanning magnet, an ionization chamber, a range adjuster, and an adaptive aperture. Through these components, the particle beam can be quickly and accurately scanned within the target area, achieving precise irradiation of the tumor. The scanning magnet can refer to the particle beam scanning disclosed in patent CN105764567A, the adaptive aperture can refer to the adaptive aperture disclosed in patent CN108883295A, and the range adjuster can refer to the collimator and energy degrader disclosed in patent CN105848715A. Through precise scanning control, the active beam scanning therapy head can achieve precise irradiation of the tumor, reduce damage to surrounding normal tissue, and improve the accuracy of treatment. The adaptive aperture can be adaptively adjusted according to the shape and size of the target area, so that the shape and size of the particle beam can match the morphology of the tumor. The advantage of this adaptive irradiation is that it can better adapt to irregularly shaped tumors, improving the personalization and targeting of the irradiation plan. Active beam scanning treatment heads can rapidly scan and adjust the particle beam, enabling a more efficient treatment process. Compared to passive scattering treatment heads, they offer faster scanning speeds and shorter irradiation times, shortening treatment time and alleviating discomfort and anxiety for patients. The combination of components, including a scanning magnet, ionization chamber, range adjuster, and adaptive aperture, enables flexible treatment methods. Treatment plans can be adjusted and optimized in real time based on the patient's specific circumstances and evolving condition to better meet their treatment needs. The efficiency and precision of active beam scanning treatment heads can effectively reduce the requirements for particle accelerators. Compared to traditional radiotherapy equipment, active beam scanning treatment heads are technologically more advanced and sophisticated, and their design reduces system complexity and improves device stability and reliability.

[0150] Passive scattering involves using scatterers to increase the lateral width of a narrow particle beam, creating a wide-beam irradiation pattern. Passive scattering treatment heads, such as double-scattering or single-scattering treatment heads, are used to transform a high-energy proton beam into a wider, more dispersed beam spot to adapt to the shape and size of the target area. Through scattering and homogenization, the particle beam distribution can be more accurately adapted to the tumor's morphology. Passive scattering treatment heads can be used in conjunction with shielding components to create the desired particle beam distribution. Passive scattering treatment heads transform a high-energy proton beam into a wider, more dispersed beam spot. This allows the particle beam distribution to better adapt to the shape and size of the tumor, helping to ensure that the particle beam accurately covers the entire tumor area during treatment, thereby improving treatment precision and effectiveness. Through scattering and homogenization, passive scattering treatment heads achieve a more uniform energy distribution when irradiating the tumor area, helping to ensure a uniform dose distribution throughout the tumor area, reducing dose fluctuations, thereby minimizing damage to normal tissue and improving treatment safety. Passive scatter therapy heads can be used in conjunction with a shield assembly. By adjusting the position of the shield, the shape and distribution of the particle beam can be further controlled, enabling more refined irradiation planning and making treatment more precise and effective. Compared to active beam scanning therapy heads, passive scatter therapy heads are technically simpler and do not require complex equipment such as scanning magnets. This reduces the requirements for particle accelerators, reducing equipment costs and maintenance costs.

[0151] The patient positioning system is responsible for positioning the patient in the correct position to ensure that the particle beam can accurately irradiate the tumor area. The patient positioning system includes a treatment couch and an imaging system.

[0152] Treatment couches are electrically or mechanically driven and can translate, rotate, and elevate along multiple axes for precise positioning. Adjustable support plates and supports provide comfortable and stable patient positioning, ensuring accurate and efficient treatment. For example, treatment couches may have three, four, five, or six degrees of freedom.

[0153] Imaging systems capture images of the patient's anatomy, helping medical professionals determine the location and posture of the target area and align and verify it with the treatment plan. The use of imaging systems allows doctors to monitor the patient's position and anatomy in real time, ensuring the accuracy and safety of treatment.

[0154] The advantage of this is that the use of the treatment head enables the particle beam to be precisely irradiated to the tumor area, minimizing damage to surrounding normal tissues and improving the accuracy of treatment; the flexibility of the beam delivery system and the precise adjustment function of the patient positioning system allow for more personalized treatment plans, allowing for precise treatment based on the patient's specific condition and tumor characteristics; the use of the imaging system allows doctors to monitor the patient's position and anatomical structure, as well as their subtle changes, before and during surgery to ensure the correct delivery of the particle beam and the accuracy of treatment.

[0155] In some embodiments, the arc radiation therapy device further comprises:

[0156] a safety interlocking system for performing safety monitoring on the particle accelerator, the beam delivery system, the patient positioning system, and the treatment gantry; and / or

[0157] a treatment planning system for generating a treatment plan based on the patient's preoperative medical imaging data; and / or,

[0158] The control software system is used to verify the treatment plan and record treatment process data.

[0159] The safety interlock system is designed to ensure the safety of arc radiation therapy equipment during operation and treatment. It prevents accidents and reduces potential risks by monitoring and controlling the system's status and function. The safety interlock system monitors and controls the particle accelerator, treatment head, treatment gantry, treatment couch, and other key components to ensure their normal operation and stability. Radiation safety control is a key component, ensuring that the radiation dose (i.e., irradiation dose, or radiotherapy dose) is within a safe range, avoiding overexposure to patients and operators and protecting their safety.

[0160] For example, a treatment planning system is a type of medical software used to plan, optimize, and simulate radiotherapy treatment plans. It analyzes the patient's pre-operative medical imaging data and converts it into a three-dimensional model to help doctors determine the location, size, shape, and structure of the tumor and surrounding tissue. Based on this data, the treatment planning system can calculate the appropriate radiotherapy dose and irradiation plan to minimize damage to normal tissue and maximize the treatment effect. The treatment planning system generates a treatment plan to ensure accurate irradiation and multi-angle treatment of the particle beam to meet the treatment needs of different patients. For information on obtaining treatment plans, please refer to the patent CN115966281A, which discloses a method, device, equipment, and storage medium for generating arc radiotherapy plans.

[0161] The control software system is the core control component of the entire radiotherapy system, responsible for controlling the operation of all systems except the safety interlock system. It provides the user with a system interface, receives and manages treatment plan data, controls the treatment process, and ensures the safety of patients and operators during treatment. The control software system verifies the accuracy of treatment plans and records treatment data for treatment outcome assessment and subsequent efficacy analysis.

[0162] In summary, the safety interlock system, treatment planning system, and control software system all play critical and interrelated roles in arc radiotherapy equipment. The safety interlock system ensures the safety of system hardware and radiation dose, protecting the health of patients and operators. The treatment planning system generates precise treatment plans to maximize treatment effectiveness. The control software system is responsible for the operation and control of the entire arc radiotherapy equipment, ensuring efficient, accurate, and safe treatment processes and providing comprehensive support and assurance for radiotherapy. The effective integration of these systems ensures the successful implementation of arc radiotherapy and a positive patient experience.

[0163] Continuing to refer to FIG. 1 and FIG. 2 , in a specific application scenario, an embodiment of the present application further provides an arc-shaped radiotherapy device, the arc-shaped radiotherapy device comprising:

[0164] particle accelerators, used to generate and manipulate particle beams;

[0165] A beam delivery system for delivering the particle beam; the beam delivery system includes a treatment head, and the treatment head includes an active beam scanning treatment head and / or a passive scattering treatment head;

[0166] A patient positioning system is used to position the patient; the patient positioning system includes a treatment bed and an imaging system;

[0167] a treatment gantry, used to drive the particle accelerator and the beam delivery system to rotate around the isocenter to achieve particle arc radiotherapy;

[0168] A safety interlocking system for performing safety monitoring on the particle accelerator, the beam delivery system, the patient positioning system, and the treatment gantry;

[0169] a treatment planning system, configured to generate a treatment plan based on the patient's preoperative medical imaging data;

[0170] The control software system is used to verify the treatment plan and record treatment process data.

[0171] The aforementioned arc radiotherapy device, which provides particle arc radiotherapy, can reduce the integrated dose of the high-energy particle beam outside the target area by increasing the treatment field angle. Furthermore, because the treatment gantry can continuously deliver radiation during continuous rotation (or rapidly resume radiation after reaching a specific rotation angle), the overall treatment time is not affected.

[0172] In this embodiment, the arc radiotherapy equipment includes, for example, a particle accelerator, a beam delivery system, a safety interlock system, a patient positioning system, a treatment gantry, a control software system, and a treatment planning system.

[0173] Particle accelerators are used to generate particle beams (e.g., protons and heavy ions like helium and carbon) and deliver them to a beam delivery system. Particle accelerators typically include a particle radiation source, a radio frequency (RF) device, a magnetic field generator, a vacuum system, a water cooling system, an adaptive coil system (i.e., a magnetic field adjustment device), and a beam spot size adjustment device.

[0174] The particle accelerator is placed on the treatment gantry and rotates with the treatment gantry, as shown in Figure 2. During the rotation of the treatment gantry, the magnetic field providing device (for example, a magnet coil or a superconducting coil) used to provide the particle deflection magnetic field is affected by gravity and may be offset to a certain extent in the direction of gravity. The degree of offset of the magnetic field providing device is related to the angle of the treatment gantry. The offset of the magnetic field providing device causes the magnetic field direction of the particle deflection magnetic field to also be deflected, which ultimately affects the parameters such as the energy, beam spot size and beam spot position of the particle beam. In order to ensure that the changes in the parameters such as the energy, beam spot size and beam spot position of the particle beam during the rotation of the gantry are within an acceptable range, the adaptive coil system can adjust the position and direction of the magnetic field providing device according to the external gantry angle.

[0175] The beam delivery system ensures the correct delivery of treatment prescription parameters. The beam delivery system includes, for example, a beam transmission line and a treatment head. When a design without a beam transmission line is adopted, the beam delivery system mainly includes a treatment head. The treatment head is, for example, a passive scattering treatment head or an active beam scanning treatment head. The active beam scanning treatment head includes a scanning magnet, an ionization chamber, a range adjuster, an adaptive aperture, etc. The passive scattering treatment head is, for example, a double scattering treatment head, which is used to diffuse and homogenize the proton beam during treatment, converting the high-energy proton beam into a wider and more dispersed beam spot to adapt to the shape and size of the target area.

[0176] The patient positioning system enables accurate and efficient patient positioning for treatment and consists of a treatment couch and an imaging system. The treatment couch has an electric or mechanical drive that allows for translation, rotation, and elevation in multiple axes for precise positioning. The treatment couch has an adjustable support plate and support devices to provide comfortable and stable patient positioning. The imaging system helps medical professionals determine the position and posture of the target area by acquiring images of the patient's anatomy (i.e., medical imaging data), and aligns and verifies them with the treatment plan.

[0177] The treatment gantry drives the particle accelerator and beam delivery system to rotate around the isocenter. For example, the treatment gantry can rotate along an arc, thereby driving the beam to rotate a certain angle (for example, 190°, i.e., -5° to 185°, where the beam parallel to the treatment couch is marked as 90°, the beam perpendicular to the treatment couch and pointing downward is marked as 0°, and the beam perpendicular to the treatment couch and pointing upward is marked as 180°) while maintaining acceptable clinical angular accuracy. The starting point of the arc (for example, 0°) is defined as the point above the lying patient, and the end point of the arc (for example, 180°) is defined as the point below the patient. The movement of the treatment gantry combined with the ability to rotate the treatment couch is sufficient to cover all clinical treatment angles. A cyclotron, which serves as a particle accelerator, is mounted on the treatment gantry, for example. In a rectangular coordinate system (O-XYZ), point O is, for example, the isocenter, the rotation axis of the treatment gantry is, for example, the X-axis, the height direction of the treatment bed is, for example, the Z-axis, and the Y-axis can be determined based on the X-axis and the Z-axis. When the patient lies flat on the treatment bed, the patient can be considered to be in the horizontal direction, in the XOY plane.

[0178] The safety interlock system is designed to ensure equipment safety during operation and treatment. It monitors and controls equipment status and functionality to prevent unexpected events and mitigate potential risks. It includes monitoring and controlling the particle accelerator, treatment head, treatment gantry, treatment couch, and other critical components. The safety interlock system also includes radiation safety controls to ensure radiation doses remain within safe limits and avoid overexposure to patients and operators.

[0179] The control software system controls all of the aforementioned systems (except the safety interlock system) and provides a system interface for the user. It also receives and manages treatment plan data, controls the treatment process, ensures patient and operator safety during treatment, verifies treatment plan data, and records treatment progress data.

[0180] A Treatment Planning System (TPS) is medical software used to plan, optimize, and simulate radiotherapy treatments. It analyzes a patient's medical image data and converts it into a three-dimensional image model. This helps doctors determine the location, size, shape, and surrounding tissue structure of the tumor, and calculate the appropriate radiotherapy dose and irradiation plan to minimize damage to normal tissue and maximize treatment effectiveness.

[0181] Arc radiotherapy procedures require arc radiotherapy equipment to have arc rotation capabilities—that is, the ability for the treatment gantry to rotate around the patient. This capability allows the beam to rotate within a specific arc range, achieving more precise irradiation shape and dose distribution. Secondly, arc radiotherapy procedures require arc radiotherapy equipment to have high-precision gantry positioning and rotation capabilities, including a precise gantry positioning system, a stable gantry rotation mechanism, and an accurate gantry position detection system to ensure gantry accuracy and stability. Furthermore, arc radiotherapy procedures require arc radiotherapy equipment to be able to rapidly switch particle beam energy during treatment. Treatment plans typically include multiple arcs or angles, each of which may require a different particle beam energy to meet the patient's specific treatment needs. This rapid energy switching capability enables the equipment to quickly switch energy at each angle to achieve highly precise dose distribution and therapeutic efficacy. Furthermore, arc radiotherapy procedures require arc radiotherapy equipment to be equipped with advanced treatment planning systems and optimization algorithms that can generate high-quality arc irradiation plans tailored to the patient's anatomy and dose requirements.

[0182] (How to operate arc radiation therapy equipment).

[0183] Refer to FIG3 , which is a flow chart of an operating method of an arc radiotherapy device provided in an embodiment of the present application.

[0184] The present application also provides an operating method of an arc radiation therapy device, for operating any of the above-mentioned arc radiation therapy devices, the method comprising:

[0185] Step S101: obtaining a treatment plan, wherein the treatment plan includes a plurality of preset angle intervals and a set dose corresponding to each of the preset angle intervals;

[0186] Step S102: rotating the treatment gantry to each of the preset angle intervals respectively to complete the irradiation process of the particle beam corresponding to each of the preset angle intervals, thereby completing the arc radiotherapy process.

[0187] In this embodiment, the treatment plan refers to a treatment plan for an arc radiotherapy device, which includes multiple preset angle intervals and the set doses corresponding to each preset angle interval. The treatment plan describes the particle beam's irradiation dose to the patient's target area at different angles, ensuring accurate irradiation throughout the treatment process.

[0188] The preset angle interval refers to the angular position of the particle beam irradiation during arc radiotherapy. The preset angle interval can be a point value or a range value. That is, each preset angle interval can refer to an angle or an angle range. For example, a treatment plan contains 10 preset angles, and each two adjacent angles differ by 15 degrees. Alternatively, a treatment plan contains 7 preset angle intervals, for example (-5°~15°, 30°±15°, 60°±15°, 90°±15°, 120°±15°, 150°±15°, 165°~185°). The embodiment of the present application does not limit the number of preset angle intervals, which can be, for example, 2, 3, 5, 10, 15, 20, 30, 60, 90, 120, 180, 360, 720, etc. When the number of preset angle intervals is large, the treatment gantry can achieve an effect similar to infinite rotation.

[0189] The set dose refers to the dose size of the particle beam irradiation set in each preset angle range.

[0190] The irradiation process of the particle beam corresponding to each preset angle interval means that in each preset angle interval, the particle accelerator releases the particle beam, and after being guided by the beam distribution system, the particle beam irradiates the target area of ​​the patient, completing the irradiation process in the preset angle interval.

[0191] This operating method is applicable to any of the above-mentioned arc radiotherapy devices. First, a treatment plan is obtained, which includes multiple preset angle intervals and the set dose corresponding to each preset angle interval, that is, the dose that the particle beam should irradiate in each preset angle interval. The treatment plan is formulated according to the patient's specific situation and condition, and is precisely designed by the doctor to maximize the treatment of the tumor while minimizing damage to normal tissue. Next, according to the requirements of the treatment plan, the treatment gantry is rotated so that it reaches each preset angle interval, and the particle accelerator and beam delivery system rotate accordingly. In each preset angle interval, the particle beam irradiates the target area in the patient's body according to the preset dose. After the irradiation process corresponding to the current preset angle interval is completed, the treatment gantry continues to rotate to the next preset angle interval until the irradiation process in all preset angle intervals is completed, thus completing the entire arc radiotherapy process.

[0192] The advantage of this is that the operating method is efficient, precise, and comprehensive. By obtaining the treatment plan, the arc radiotherapy device can accurately set the required treatment dose in each preset angle interval. The rotating treatment gantry can achieve multi-angle irradiation, covering a wide treatment range, maximizing irradiation to the tumor while reducing the radiation dose to normal tissue and maximizing the protection of the patient's health. In addition, due to the use of arc radiotherapy, compared with traditional fixed-angle radiotherapy, this method can better adapt to changes in tumor shape and differences in patient anatomy. This can improve the accuracy and effectiveness of treatment and help better control the growth and spread of tumors. In general, the application of this operating method in arc radiotherapy equipment helps patients achieve better treatment results and improves the overall quality and safety of radiotherapy.

[0193] See FIG4 , which is a schematic diagram of a process for adjusting a treatment couch provided in an embodiment of the present application.

[0194] In some embodiments, before rotating the treatment gantry, the method further comprises:

[0195] Adjust the treatment bed to the preset irradiation position;

[0196] Acquire the patient's intraoperative medical imaging data through the imaging system;

[0197] Performing image registration on the patient's intraoperative medical imaging data and the treatment plan to obtain treatment couch adjustment information;

[0198] The position and angle of the treatment bed are adjusted according to the treatment bed adjustment information.

[0199] The gantry is a component of the radiotherapy equipment that rotates around the isocenter to control the angle and direction of the particle beam.

[0200] The treatment couch is the platform on which the patient lies during radiotherapy. It is used to ensure the patient's stable position and posture so that the particle beam can accurately irradiate the target area.

[0201] The preset irradiation position refers to the patient's irradiation position preset in the treatment plan. This is the position where the patient should be positioned on the treatment bed to ensure that the particle beam is irradiated to the correct treatment area.

[0202] Imaging systems are devices used to obtain intraoperative medical imaging data from patients, such as X-ray equipment, CT scanners, and MR scanners. Through these imaging data, doctors can understand the patient's anatomical structure and tumor location.

[0203] Intraoperative medical imaging data is acquired during radiotherapy. This data can be used to locate the patient and perform registration to ensure correct particle beam irradiation.

[0204] Image registration refers to the process of matching and aligning intraoperative medical imaging data with the treatment plan to ensure that the adjustment of the treatment table is consistent with the treatment plan.

[0205] The treatment couch adjustment information refers to information obtained based on the image registration result, and is used to adjust the position and angle (or direction, orientation) of the treatment couch to ensure accurate irradiation of the particle beam.

[0206] In arc radiation therapy systems, the patient's irradiation position must be prepared before treatment begins. This is achieved by adjusting the treatment couch to a preset irradiation position. The couch can be translated, rotated, and raised in multiple axes to achieve precise positioning, ensuring that the patient's lesion or target area is correctly positioned for irradiation.

[0207] Next, an imaging system acquires intraoperative medical imaging data from the patient. This imaging system can use X-rays, CT scans, MRI scans, or other medical imaging techniques to capture image data of the patient's anatomical structures and lesion areas. This image data is used for registration, which is crucial for accurate treatment planning and progression.

[0208] Next, image registration is performed on the patient's intraoperative medical imaging data and the treatment plan. Image registration is the process of aligning and matching the patient's medical imaging data with the image data in the treatment plan to ensure the accuracy of the treatment plan and accurately guide the irradiation process.

[0209] The benefit of this is that by adjusting the treatment bed to the preset irradiation position, the patient's target area is correctly positioned, thereby ensuring the accuracy and effectiveness of irradiation. Intraoperative medical imaging data acquired by the imaging system can provide doctors with detailed information about the patient's anatomy, helping to determine the location, size, shape, and surrounding tissue structure of the tumor for more precise treatment planning. Image registration aligns the intraoperative medical imaging data with the treatment plan, ensuring its precise implementation and providing accurate positioning information. This ensures precision and accuracy during treatment, maximizing irradiation of the tumor area while minimizing damage to normal tissue.

[0210] Continuing with FIG4 , in some embodiments, after adjusting the position and angle of the treatment couch, the method further includes:

[0211] reacquiring intraoperative medical imaging data of the patient through the imaging system;

[0212] detecting whether the reacquired intraoperative medical imaging data and the treatment plan have been registered;

[0213] If the registration is completed, rotating the treatment gantry is performed;

[0214] If the registration is not completed, the treatment couch adjustment information is re-acquired to readjust the treatment couch.

[0215] The reacquired intraoperative medical imaging data is matched and aligned with the previous treatment plan to verify that the reacquired medical imaging data and treatment plan are properly aligned, i.e., that the alignment between the two is accurate. If the alignment is successful, i.e., the medical imaging data and treatment plan are properly aligned, the treatment gantry rotation step is performed to rotate the treatment gantry to the preset irradiation angle. If the alignment between the medical imaging data and the treatment plan is inaccurate, the treatment table adjustment information is reacquired to readjust the position and angle of the treatment table to ensure accurate particle beam irradiation. This adjustment process can be repeated and iterated multiple times until the intraoperative medical imaging data and treatment plan are fully aligned.

[0216] For example, during arc radiation therapy, the treatment couch needs to be adjusted to the preset irradiation position, and the patient's intraoperative medical imaging data is acquired through the imaging system. This intraoperative medical imaging data is then aligned with the treatment plan to obtain couch adjustment information. Based on this adjustment information, the position and angle of the treatment couch are adjusted to ensure accurate irradiation of the patient's target area. Since the position and angle of the treatment couch have been adjusted, the intraoperative medical imaging data is reacquired and a check is performed to determine if the alignment is complete. If the alignment is complete, the step of rotating the treatment gantry can be executed to rotate it to the first preset angle range. If the alignment is not complete, the couch adjustment information needs to be reacquired to readjust the treatment couch until accurate alignment is achieved. This ensures the accuracy of particle beam irradiation and the effectiveness of the treatment.

[0217] Therefore, in arc radiotherapy equipment, after adjusting the position and angle of the treatment couch, it is necessary to reacquire the patient's intraoperative medical imaging data to ensure treatment accuracy. This is because the patient's anatomy may undergo subtle changes when the couch's position and angle are adjusted, and these changes may affect the accuracy of the treatment plan. Reacquiring the patient's intraoperative medical imaging data is performed by an imaging system, which can use X-rays, CT scans, MRI scans, or other medical imaging technologies to reacquire image data of the patient's anatomy and lesion area. Next, the reacquired medical imaging data and the treatment plan are checked for registration. If registration is successful, the gantry rotation step can be performed. Gantry rotation is a key step in implementing arc radiotherapy. By rotating the gantry, the particle accelerator and beam delivery system rotate around the isocenter, achieving particle arc radiotherapy. If registration is not successful, further adjustment of the couch's position and angle is required, and the couch adjustment information must be reacquired to ensure accurate patient positioning and posture.

[0218] The benefit of this is that by reacquiring the patient's intraoperative medical imaging data, the patient's anatomical structure can be more accurately reflected, especially the subtle changes that may occur during treatment, helping to ensure the accuracy and effectiveness of the treatment plan to maximize irradiation to the tumor area and minimize damage to normal tissue. Detecting whether the intraoperative medical imaging data and the treatment plan are fully aligned can provide timely feedback information to ensure the real-time and accuracy of the treatment plan, thereby guiding the next treatment steps. If the alignment is not complete, the treatment bed adjustment information is reacquired and adjusted to ensure the patient's irradiation position and angle are accurately positioned, ultimately improving the accuracy and treatment effectiveness of radiotherapy. Overall, the real-time and precision of this operating method helps ensure the safety and effectiveness of arc radiotherapy, provide patients with a high level of personalized treatment, minimize the risk of complications, and improve the overall quality and success rate of treatment.

[0219] Refer to FIG5 , which is a flowchart of a first implementation method of an arc radiation therapy process provided in an embodiment of the present application.

[0220] In some embodiments, the preset angle interval is expressed as a point value and a preset angle. During the arc radiation therapy, the following processing is performed:

[0221] S1: rotating the treatment gantry to a first preset angle;

[0222] S2: Extending the treatment head to start the particle beam irradiation process;

[0223] S3: monitoring the irradiation dose of the particle beam at the preset angle, and stopping the irradiation process of the particle beam when the irradiation dose of the particle beam reaches a set dose corresponding to the preset angle;

[0224] S4: retract the treatment head;

[0225] S5: Detect whether the next preset angle exists; if so, execute S6; if not, execute S7;

[0226] S6: Rotate the treatment gantry to the next preset angle and execute S2;

[0227] S7: End of arc radiation therapy process.

[0228] The radiation dose refers to the energy released by the particle beam in the treatment area, expressed, for example, in units of prescription dose (MU) or Gray (Gy). The prescription dose (MU) is a measure of the machine output of the particle accelerator (e.g., a linear accelerator or orthovoltage unit) used for radiotherapy (i.e., the number of monitoring steps of the particle accelerator's dose monitoring device). The prescription dose (MU) is measured by a dose monitoring device, such as an ionization chamber that measures the beam delivered dose, which is built into the treatment head of the particle accelerator.

[0229] For example, during an arc radiotherapy treatment, the preset angles are set to 0°, 45°, 90°, 135°, and 180°, which means that the treatment gantry needs to be rotated to these five angles respectively. After the treatment gantry rotates to the first preset angle of 0°, the treatment head is extended and the particle beam irradiation process begins. When the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle of 0° (for example, 10MU), the irradiation is stopped and the treatment head is retracted. Then, it is detected whether there is the next preset angle. If it is detected that there is the next preset angle of 45°, the treatment gantry is rotated to the next preset angle of 45°, and the extension of the treatment head and the irradiation process are continued until the irradiation of all preset angles is completed. If the treatment gantry has rotated to the fifth preset angle of 180° and completed the corresponding irradiation process, after retracting the treatment head, it is detected that there is no next preset angle, and the arc radiotherapy treatment process is ended.

[0230] As can be seen, in this implementation, the arc radiation therapy process is achieved through a series of steps that utilize the rotation function of the treatment gantry and the telescopic control of the treatment head. In the arc radiation therapy equipment, the treatment gantry drives the particle accelerator and beam delivery system to rotate around the isocenter, realizing particle arc radiation therapy. During the treatment process, irradiation is performed according to pre-set angles until the set dose corresponding to all pre-set angles is completed. The specific operation steps are as follows:

[0231] S1: Rotate the treatment gantry to the first preset angle: The treatment gantry rotates the particle accelerator and beam delivery system to the starting angle of irradiation according to the preset angle setting.

[0232] S2: Extending the treatment head and commencing particle beam irradiation: The treatment head, the terminal device for beam irradiation, extends at a preset angle and begins releasing the particle beam, irradiating the patient. During this phase, the particle beam enters the patient's body at the preset dose and irradiation parameters, targeting the tumor for treatment.

[0233] S3: At the current preset angle, monitor the irradiation dose of the particle beam. When the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle, stop the irradiation process of the particle beam: according to the preset set dose, monitor the irradiation dose of the current preset angle during the irradiation process of each preset angle (that is, for each preset angle, independently count the irradiation dose corresponding to it). When the particle beam release reaches the required dose, it will automatically stop irradiation to ensure that the irradiation dose is accurate. This is to ensure that the irradiation dose of the particle beam meets the requirements of the treatment plan and prevent overexposure (or overexposure, overirradiation). In this embodiment, the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle, for example, it means that the irradiation dose of the particle beam is not less than the set dose corresponding to the preset angle. That is to say, once it is detected that the irradiation dose is equal to the set dose (or the absolute value of the difference between the irradiation dose and the set dose is not greater than the preset value), the particle accelerator will immediately stop releasing the particle beam. The present application does not limit the detection method of the irradiation dose. It can be achieved by the ionization chamber in the treatment head, or the irradiation dose can be detected by a detection device based on Cherenkov radiation.

[0234] S4: Retract the treatment head: After completing the current angle of irradiation, the treatment head automatically retracts to a safe position, ready for the next rotation or other operation. This ensures that the treatment head does not interfere with or collide with any part of the treatment gantry during rotation, ensuring the safety and stability of the treatment process.

[0235] S5: Check whether there is a next preset angle; if so, execute S6; if not, execute S7: Check whether there is a next preset angle, if so, continue to the next step; if not, it means that the irradiation process of all preset angles is completed, execute S7, and end the arc radiotherapy process.

[0236] S6: Rotate the gantry to the next preset angle, then execute S2: Rotate the gantry according to the next preset angle, extend the treatment tip again, and begin the particle beam irradiation process corresponding to the next preset angle. In this way, the arc radiotherapy system gradually completes the irradiation process corresponding to all preset angles, achieving comprehensive arc radiotherapy. During the irradiation process corresponding to each preset angle, the continuity of the entire treatment process is ensured by extending the treatment tip, irradiating the particle beam, stopping the beam, retracting the treatment tip, and checking whether the irradiation is complete. In other words, the treatment tip needs to be extended and retracted multiple times throughout the treatment process.

[0237] S7: Ending the arc radiation therapy process: When the irradiation processes corresponding to all preset angles are completed, the entire arc radiation therapy process ends.

[0238] The benefit of this approach is that, based on preset angles and set doses, the arc radiotherapy system automatically rotates the treatment gantry and delivers the particle beam, eliminating the need for manual intervention and improving treatment efficiency and consistency. Furthermore, by detecting when the dose has been reached, the particle beam's delivery is accurate, avoiding over-irradiation of the patient and ensuring the safety and effectiveness of the treatment. The telescopic control of the treatment head and the implementation of a safety interlock system ensure the safety and stability of the treatment process. This method allows for irradiation at different preset angles, achieving multi-angle, all-round irradiation, improving treatment precision and effectiveness.

[0239] Refer to FIG6 , which is a flow chart of a second implementation method of an arc radiation therapy process provided in an embodiment of the present application.

[0240] In some embodiments, the preset angle interval adopts a range value, and during the arc radiation therapy process, the following processing is performed:

[0241] R1: Rotate the treatment gantry to the first preset angle range;

[0242] R2: Extend the treatment head and start the particle beam irradiation process;

[0243] R3: monitoring the irradiation dose of the particle beam within the preset angle interval, and when the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle interval, detecting whether there is a next preset angle interval; if so, executing R4; if not, executing R5;

[0244] R4: Rotate the treatment gantry to the next preset angle interval and execute R3;

[0245] R5: Stop the irradiation process of the particle beam, retract the treatment head, and end the arc radiotherapy process.

[0246] For example, during an arc radiotherapy treatment, the preset angle intervals adopt range values ​​and are set to -5° to 22.5°, 45°±22.5°, 90°±22.5°, 135°±22.5°, and 157.5° to 185°. After the treatment gantry rotates to the first preset angle interval of -5° to 22.5°, the treatment head is extended to start the particle beam irradiation process. When the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle interval of -5° to 22.5° (for example, 10MU), the treatment gantry detects whether there is the next preset angle interval. If it is detected that there is the next preset angle interval 45°±22.5° (i.e., 22.5° to 67.5°), the treatment gantry is rotated to the next preset angle interval 45°±22.5°. When the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle interval 45°±22.5° (for example, 10MU), the treatment gantry detects whether there is the next preset angle interval. If it is detected that there is the next preset angle interval 90°±22.5°, the treatment gantry is rotated to the next preset angle interval 90°±22.5°. And so on. The particle beam irradiation process is continuously performed during the detection and rotation of the treatment gantry until the irradiation of all preset angle intervals is completed. If the treatment gantry has rotated to the fifth preset angle interval of 157.5° to 185° and completed the corresponding irradiation process, and then detects that there is no next preset angle interval, the particle beam irradiation process is stopped, the treatment head is retracted, and the arc radiotherapy process ends.

[0247] Therefore, this operating method is a description of the actual treatment steps during arc radiotherapy. In arc radiotherapy equipment, particle beam irradiation is achieved by executing a series of preset steps. During the treatment process, the treatment gantry drives the particle accelerator and the beam delivery system to rotate around the isocenter, and at the same time, the treatment head is extended to irradiate the particle beam, and irradiation is performed according to the preset angle interval and the set dose until the irradiation of all preset angle intervals is completed. Finally, the treatment head is retracted. During the entire treatment process, the treatment head is extended and retracted once, and there is no multiple extension and retraction. The specific operating steps are as follows:

[0248] R1: Rotate the treatment gantry to the first preset angle range: The treatment gantry rotates the particle accelerator and beam delivery system to the angle position for starting irradiation according to the settings of the preset angle range.

[0249] R2: Extend the treatment head and start the particle beam irradiation process: Extend the treatment head, the particle accelerator starts to release the particle beam, and the extended treatment head distributes the particle beam, irradiating the radiation into the patient's body according to the preset angle range.

[0250] R3: Monitor the irradiation dose of the particle beam in the current preset angle interval. When the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle interval, detect whether there is the next preset angle interval; if so, execute R4; if not, execute R5: Monitor the irradiation dose during the irradiation process. When the irradiation dose reaches the set dose, detect whether there is the next preset angle interval. If so, proceed to the next step; if not, it means that the irradiation process of all preset angle intervals is completed.

[0251] R4: Rotate the gantry to the next preset angle interval, and execute R3: Rotate the gantry according to the next preset angle interval, while continuing the particle beam irradiation process. That is, particle beam irradiation continues both during the step of detecting whether the next preset angle interval exists and during the step of rotating the gantry to the next preset angle interval.

[0252] R5: Stop the particle beam irradiation process, retract the treatment head, and end the arc radiotherapy process: After the irradiation process of all preset angle intervals is completed, stop the particle beam irradiation process, retract the treatment head to a safe position, and the entire arc radiotherapy process ends.

[0253] The advantage of this approach is that it eliminates the need to adjust the position of the treatment head while rotating the gantry, saving time and improving treatment efficiency. Furthermore, this method maintains precise irradiation and dose control within the pre-set angle range, ensuring the accuracy and safety of radiotherapy.

[0254] The arc radiation therapy process may adopt the first implementation method in S1 to S7 and the second implementation method in R1 to R5.

[0255] In the first implementation mode, the preset angle interval adopts a point value: by retracting / extending the treatment head before and after the rotation of the treatment gantry, it is ensured that the particle beam can accurately irradiate the target area of ​​the patient at each preset angle, avoiding irradiation deviation and error, and ensuring the accuracy and effect of the treatment; after the irradiation process at each preset angle is completed, the treatment head will retract, avoiding the risk of collision between the treatment head and the patient or equipment, improving the safety of the treatment, and protecting the safety of the patient and equipment; by setting the dose, it is ensured that the particle accelerator stops the beam after the set treatment dose is reached, thereby ensuring the precise control of the irradiation dose of the particle beam, avoiding overexposure, and reducing harm to the patient; since there is an independent irradiation process at each preset angle, the irradiation parameters can be flexibly adjusted according to the patient's specific situation and treatment needs to achieve personalized treatment.

[0256] In the second implementation, the preset angle intervals use range values: Continuous irradiation is achieved during gantry rotation, eliminating the need to retract the treatment head after each angle irradiation. This improves treatment efficiency and helps reduce total treatment time. Adjusting the treatment head position before and after gantry rotation simplifies the operation process, reduces the number of steps, and reduces operational difficulty, thereby improving convenience and efficiency. Because the treatment head does not need to be extended or retracted before and after gantry rotation, adjustment and control steps are reduced, reducing the complexity of the equipment and operating methods, and improving the stability and reliability of the arc radiotherapy system. Furthermore, in this implementation, the maximum extension position of the treatment head throughout the entire treatment plan can be precalculated and used as a limit to constrain its extension, avoiding collisions between the treatment head and the patient or equipment and unnecessary adjustments of the treatment head during rotation. This improves treatment efficiency and shortens treatment time.

[0257] For example, in the first implementation, the set doses corresponding to the preset angles of 0°, 45°, 90°, 135°, and 180° are 10MU, 10MU, 10MU, 10MU, and 10MU, respectively. In the second implementation, the set doses corresponding to the preset angle ranges of -5° to 22.5°, 45°±22.5°, 90°±22.5°, 135°±22.5°, and 157.5° to 185° are 10MU, 10MU, 10MU, 10MU, and 10MU, respectively. In the second implementation, the particle beam continues to irradiate during the detection step and the treatment gantry rotation step, so the total irradiation dose remains consistent with the first implementation.

[0258] In the first implementation, the dose at each preset angle is set to 10 MU. This means that at each preset angle, after the gantry rotates to a specific angle, the treatment head extends and begins irradiating the particle beam until the particle beam dose reaches 10 MU. The irradiation process then stops and the treatment head retracts. Each preset angle is an independent irradiation process, with a constant dose of 10 MU.

[0259] In the second implementation, the doses for the preset angle intervals are set at 10MU, 10MU, 10MU, 10MU, and 10MU, respectively. In this implementation, the gantry continuously irradiates the patient during rotation, so the irradiation between adjacent preset angle intervals is continuous, rather than performing a separate irradiation process for each preset angle interval.

[0260] Comparing the two implementation methods, in the first implementation method, each preset angle interval is an independent irradiation process, and the treatment head retracts at each angle, ensuring the accuracy and safety of irradiation. This method is suitable for treatment situations that require high irradiation precision, especially for patients with complex target shapes and those who require fine adjustment of dose distribution, which can achieve more personalized treatment. In the second implementation method, through continuous irradiation, the number of times the treatment head is extended and retracted during treatment can be reduced, simplifying the operation process, improving treatment efficiency, and helping to reduce the total treatment time. While reducing the number of treatment head extension and retraction steps, it also reduces the risk of collision with the patient or equipment, increasing the safety of treatment. It is suitable for general radiotherapy, especially for large-area, regularly shaped targets, and can achieve more efficient treatment.

[0261] In summary, both the S1-S7 and R1-R5 implementations have their own advantages and applicable scenarios. Choosing the appropriate implementation depends on the performance of the treatment machine and the specific condition of the patient. Choosing the appropriate implementation based on the patient's specific condition and treatment needs can achieve more personalized and efficient particle arc radiotherapy. For situations requiring more precise adjustment and personalized treatment, the S1-S7 implementation may be more suitable; for situations seeking high efficiency and simplified operational processes, the R1-R5 implementation may be more suitable. In actual applications, doctors can flexibly select the appropriate implementation based on the patient's condition and treatment goals to achieve the best treatment effect. At the same time, for the second implementation, the set dose for each preset angle interval is precalculated and determined to ensure that the total irradiation dose remains consistent, guaranteeing the accuracy and effectiveness of the treatment.

[0262] In some embodiments, when the number of preset angle intervals is large (for example, greater than 30, such as 90, 180, or even 360, 720), the second implementation method can achieve a stepless control process similar to continuous rotation + continuous irradiation, thereby bringing about a qualitative change from quantitative change. Its beneficial effects include:

[0263] 1. Smooth and continuous irradiation: As the number of preset angle intervals increases, the irradiation process becomes smoother and more continuous, and the movement of the particle beam is almost seamless, with no noticeable gaps. This continuous irradiation can make the dose distribution more uniform, avoid discontinuities in the dose distribution, and thus improve the accuracy and uniformity of irradiation.

[0264] 2. Efficient treatment speed: With 360 or more preset angle intervals, there is no need to retract the treatment head after each preset angle interval, greatly reducing the number of times the treatment head needs to be extended and retracted during the treatment process and simplifying the operation process. At the same time, because the gantry rotates continuously, there is no noticeable pause during the treatment process, which greatly improves treatment efficiency, helps shorten the entire treatment process, and reduces patient discomfort and anxiety.

[0265] 3. Precise dose control: As the number of preset angle intervals increases, the continuous irradiation process of the particle beam at different angles can better compensate for the unevenness of the dose distribution. By precalculating and determining the set dose, the total irradiation dose is ensured to remain consistent, ensuring precise control of the irradiation dose, avoiding overexposure or underexposure, and ensuring safe and effective treatment.

[0266] 4. Personalized Treatment Planning: With a large number of preset angle intervals, treatment planning flexibility is enhanced. Physicians can adjust the number and spacing of preset angle intervals based on the patient's specific condition and treatment needs to achieve more personalized treatment. Different tumor types and locations may require a different number of preset angle intervals. By adjusting the preset angle intervals, different treatment needs can be better adapted.

[0267] 5. Improved robustness: The implementation of a large number of pre-set angle intervals can improve the robustness of the treatment plan. Even if there are image registration or other technical uncertainties at certain angles, the continuous rotation and irradiation of the gantry ensure that the entire treatment process remains stable and accurate, without significant dose errors caused by a specific angle.

[0268] In some embodiments, the extended position of the treatment head does not exceed a preset position, and the preset position is determined according to a preset collision constraint condition.

[0269] This application does not limit the collision constraint conditions, which may include, for example: the closest distance between the treatment head and the patient is not less than L1, and / or the closest distance between the treatment head and the treatment couch is not less than L2. L1 can be, for example, 0.1, 0.2, 0.3, 0.5, 1, 2, 3, 5, or 10 cm, and L2 can be, for example, 1, 2, 3, 5, 10, 15, or 20 cm.

[0270] Therefore, the extension position of the treatment head is limited by pre-set collision constraints. During arc radiation therapy, the arc radiation therapy device calculates the maximum extension position of the treatment head along the entire arc path based on the pre-set collision constraints and uses this position as a limit to ensure that the treatment head does not exceed the preset position at any time. During treatment, the arc radiation therapy device automatically controls the extension position of the treatment head to maintain it within the preset range, avoiding collisions with the patient (or other parts of the device) and ensuring the safety and accuracy of treatment.

[0271] The benefits of this approach are that by limiting the extension position of the treatment head, the risk of collision between the treatment head and the patient is avoided. This helps protect patients from accidental injury and improves the overall safety of treatment. The extension position of the treatment head does not exceed the preset position, maintaining the appropriate distance between the treatment head and the predetermined target area, ensuring that the particle beam correctly irradiates the patient's target area, helping to improve the accuracy of treatment and reduce side effects that damage normal tissue. By avoiding collisions between the treatment head and the patient, accidental damage and failure of the system can be reduced, reducing the cost of equipment repair and maintenance. Pre-setting collision constraints ensures that the extension position of the treatment head is always within a safe range, reducing adjustment and pause time during treatment, improving treatment efficiency and smoothing the process. Automatically controlling the extension position of the treatment head eliminates the need for manual intervention, simplifying the operating process, reducing the burden on operators and the possibility of errors, and improving the ease of use of the device.

[0272] Without a restriction on the maximum extension position of the treatment head (i.e., the extension position of the treatment head does not exceed the preset position), the maximum extension position of the treatment head may exceed the safe range during rotation, resulting in increased irradiation errors and affecting the accuracy and effectiveness of disease treatment. Without restrictions, the treatment head may collide with the patient or other parts of the equipment during rotation, causing safety risks and patient injury. Frequent adjustments to the position of the treatment head during treatment will increase treatment time, reduce treatment efficiency, and affect the hospital's work efficiency and resource utilization.

[0273] By setting a constraint on the maximum extension position of the treatment head, the maximum extension position of the treatment head is limited, ensuring that the treatment head does not exceed a safe range and avoids collision with the patient or other parts of the device, thereby improving treatment safety and stability. Pre-calculating the maximum extension position of the treatment head avoids unnecessary adjustments during treatment, reducing treatment time, improving treatment efficiency, and conserving valuable medical resources. The constraint simplifies the operation process, reduces the number of steps and complexity, reduces the risk of human error, and improves the device's ease of use and reliability.

[0274] Continuing to refer to FIG. 3 to FIG. 6 , in a specific application scenario, an embodiment of the present application further provides a method for operating an arc radiation therapy device, for operating any of the above-mentioned arc radiation therapy devices, the method comprising:

[0275] Obtaining a treatment plan, the treatment plan including a plurality of preset angle intervals and a set dose corresponding to each of the preset angle intervals; in this step, the treatment plan is loaded into the control software system of the arc radiotherapy device and parsed into machine setting information for corresponding configuration;

[0276] Adjust the treatment bed to the preset irradiation position;

[0277] Obtaining intraoperative medical imaging data of the patient through an imaging system; the intraoperative medical imaging data will be used to locate and verify the consistency of the patient's position and anatomical structure with the treatment plan;

[0278] performing image registration on the patient's intraoperative medical imaging data and the treatment plan to obtain treatment couch adjustment information; using image registration technology to register the acquired imaging data with the treatment plan to determine adjustment requirements for the treatment couch;

[0279] Adjusting the position and angle of the treatment bed according to the treatment bed adjustment information; adjusting the position and angle of the treatment bed according to the image registration result;

[0280] Reacquiring intraoperative medical imaging data of the patient through the imaging system; detecting whether the reacquired intraoperative medical imaging data and the treatment plan have been registered; if so, rotating the treatment gantry; if not, performing image registration on the reacquired intraoperative medical imaging data and the treatment plan to reacquire treatment couch adjustment information, thereby re-adjusting the treatment couch; this step is intended to confirm whether the treatment couch adjustment is accurate and ensure accurate positioning;

[0281] The treatment gantry is rotated to each of the preset angle intervals respectively to complete the irradiation process of the particle beam corresponding to each of the preset angle intervals, thereby completing the arc radiation therapy process.

[0282] Arc radiation therapy can be delivered in one of two ways:

[0283] In the first implementation, the preset angle interval uses point values ​​and is expressed as preset angles:

[0284] S1: rotating the treatment gantry to a first preset angle;

[0285] S2: Extending the treatment head to start the irradiation process of the particle beam; starting the particle accelerator to release the particle beam to irradiate the treatment area of ​​the patient;

[0286] S3: monitoring the irradiation dose of the particle beam at the current preset angle, and stopping the irradiation process of the particle beam when the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle; controlling the irradiation dose at each preset angle to ensure that the particle accelerator stops the beam flow after reaching the set treatment dose;

[0287] S4: Retract the treatment head; retract the treatment head to the set position to ensure safety and prepare for the next step;

[0288] S5: Detect whether the next preset angle exists; if so, execute S6; if not, execute S7;

[0289] S6: rotating the treatment gantry to the next preset angle and executing S2; sequentially executing the irradiation process at each preset angle until irradiation at all preset angles is completed;

[0290] S7: End of arc radiation therapy process.

[0291] The second implementation method uses a range value for the preset angle interval:

[0292] R1: Rotate the treatment gantry to the first preset angle range;

[0293] R2: Extending the treatment tip to start the particle beam irradiation process; the extension position of the treatment tip does not exceed a preset position to avoid collision between the treatment tip and the patient (or other parts of the device), and the preset position is determined according to preset collision constraints;

[0294] R3: monitoring the irradiation dose of the particle beam in the current preset angle interval. When the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle interval, detecting whether there is a next preset angle interval; if so, executing R4; if not, executing R5;

[0295] R4: Rotate the treatment gantry to the next preset angle interval and execute R3;

[0296] R5: Stop the irradiation process of the particle beam, retract the treatment head, and end the arc radiotherapy process.

[0297] Assume that a plan requires 10 preset angle intervals, and the center angles of every two adjacent angle intervals differ by 15° (excluding the first preset angle interval and the last preset angle interval).

[0298] In the first implementation, irradiation takes less than 5 seconds for each preset angle, the gantry rotates and stops within 5 seconds, and the adaptive coil system adjusts, retracts, and extends the treatment head within 5 seconds. This translates to a total of 150 seconds for all 10 preset angles. Adjustment of the adaptive coil system occurs after the gantry angle is adjusted, allowing for simultaneous retraction and extension of the treatment head.

[0299] In the second implementation, for each preset angle interval, the irradiation time is within 5 seconds, the gantry rotation and stop time is within 5 seconds, and the adaptive coil system adjustment time is within 5 seconds. Therefore, the 10 preset angle intervals require a total of 150 seconds (or less). The adaptive coil system adjustment must be completed after the gantry angle adjustment is completed.

[0300] It should be noted that, under the premise of being feasible, the order of the steps in the above embodiments can be adjusted, and this application does not limit this.

[0301] (Operating device).

[0302] The embodiment of the present application also provides an operating device for an arc radiotherapy device, the specific embodiments of which are consistent with the embodiments described in the above method embodiments and the technical effects achieved, and some contents will not be repeated here.

[0303] The operating device is used to operate any of the above-mentioned arc radiation therapy devices, and the operating device includes a memory and one or more processors, the memory stores a computer program, and the one or more processors are configured to implement the following steps when executing the computer program:

[0304] Obtaining a treatment plan, the treatment plan including a plurality of preset angle intervals and a set dose corresponding to each of the preset angle intervals;

[0305] The treatment gantry is rotated to each of the preset angle intervals respectively to complete the irradiation process of the particle beam corresponding to each of the preset angle intervals, thereby completing the arc radiation therapy process.

[0306] In some embodiments, before rotating the treatment gantry, the one or more processors are configured to further implement the following steps when executing the computer program:

[0307] Adjust the treatment bed to the preset irradiation position;

[0308] Acquire the patient's intraoperative medical imaging data through the imaging system;

[0309] Performing image registration on the patient's intraoperative medical imaging data and the treatment plan to obtain treatment couch adjustment information;

[0310] The position and angle of the treatment bed are adjusted according to the treatment bed adjustment information.

[0311] In some embodiments, after adjusting the position and angle of the treatment couch, the one or more processors are configured to further implement the following steps when executing the computer program:

[0312] reacquiring intraoperative medical imaging data of the patient through the imaging system;

[0313] detecting whether the reacquired intraoperative medical imaging data and the treatment plan have been registered;

[0314] If the registration is completed, rotating the treatment gantry is performed;

[0315] If the registration is not completed, the treatment couch adjustment information is re-acquired to readjust the treatment couch.

[0316] In some embodiments, the preset angle interval is expressed as a point value and a preset angle, and the one or more processors are configured to perform the following processing during the arc radiation therapy when executing the computer program:

[0317] S1: rotating the treatment gantry to a first preset angle;

[0318] S2: Extending the treatment head to start the particle beam irradiation process;

[0319] S3: When the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle, stopping the irradiation process of the particle beam;

[0320] S4: retract the treatment head;

[0321] S5: Detect whether the next preset angle exists; if so, execute S6; if not, execute S7;

[0322] S6: Rotate the treatment gantry to the next preset angle and execute S2;

[0323] S7: End of arc radiation therapy process.

[0324] In some embodiments, the preset angle interval adopts a range value, and the one or more processors are configured to perform the following processing during the arc radiation therapy when executing the computer program:

[0325] R1: Rotate the treatment gantry to the first preset angle range;

[0326] R2: Extend the treatment head and start the particle beam irradiation process;

[0327] R3: When the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle interval, detecting whether there is a next preset angle interval; if so, executing R4; if not, executing R5;

[0328] R4: Rotate the treatment gantry to the next preset angle interval and execute R3;

[0329] R5: Stop the irradiation process of the particle beam, retract the treatment head, and end the arc radiotherapy process.

[0330] In some embodiments, the extended position of the treatment head does not exceed a preset position, and the preset position is determined according to a preset collision constraint condition.

[0331] Refer to FIG. 7 , which is a structural block diagram of an operating device 10 provided in an embodiment of the present application.

[0332] The operating device 10 may include, for example, one or more memories 11 , one or more processors 12 , and a bus 13 connecting different platform systems.

[0333] The memory 11 may include (computer) readable media in the form of volatile memory, such as random access memory (RAM) 111 and / or cache memory 112, and may further include read-only memory (ROM) 113. The memory 11 also stores a computer program, which can be executed by the processor 12, causing the processor 12 to implement the steps of any of the above methods. The memory 11 may also include a utility 114 having one or more program modules 115. Such program modules 115 include, but are not limited to, an operating system, one or more application programs, other program modules, and program data. Each of these examples, or some combination thereof, may include an implementation of a network environment.

[0334] Accordingly, the processor 12 can execute the aforementioned computer program and can execute the utility 114. The processor 12 can be implemented as one or more application specific integrated circuits (ASICs), DSPs, programmable logic controllers (PLCs), complex programmable logic devices (CPLDs), field programmable gate arrays (FPGAs), or other electronic components.

[0335] The bus 13 may represent one or more of several types of bus structures, including a memory bus or memory controller, a peripheral bus, an accelerated graphics port, a processor, or a local bus using any of a variety of bus architectures.

[0336] The operating device 10 can also communicate with one or more external devices, such as a keyboard, pointing device, Bluetooth device, etc., one or more devices capable of interacting with the operating device 10, and / or any device that enables the operating device 10 to communicate with one or more other computing devices (e.g., a router, modem, etc.). Such communication can occur via an input / output interface 14. Furthermore, the operating device 10 can communicate with one or more networks (e.g., a local area network (LAN), a wide area network (WAN), and / or a public network, such as the Internet) via a network adapter 15. The network adapter 15 can communicate with other modules of the operating device 10 via the bus 13. It should be understood that, although not shown in the figures, other hardware and / or software modules may be used in conjunction with the operating device 10 in actual applications, including but not limited to microcode, device drivers, redundant processors, external disk drive arrays, RAID systems, tape drives, and data backup storage platforms.

[0337] (Particle accelerator).

[0338] See FIG8 , which is a structural block diagram of a particle accelerator provided in an embodiment of the present application.

[0339] The embodiment of the present application further provides a particle accelerator, which is applied to a radiotherapy system. During the rotation of a treatment gantry, the particle accelerator rotates along with the treatment gantry.

[0340] The particle accelerator comprises:

[0341] a particle radiation source for generating a particle beam;

[0342] a cavity for accelerating the particle beam therein;

[0343] a magnetic field providing device, for providing a particle deflection magnetic field for the cavity;

[0344] A magnetic field adjustment device is used to adjust the particle deflection magnetic field.

[0345] A particle accelerator is a device used to accelerate charged particles (such as protons or heavy ions) to high energies. In radiotherapy, particle accelerators are used to generate particle beams—high-energy streams of particles—for irradiating tumor tissue within a patient's body. Examples of particle accelerators include electrostatic field accelerators, electromagnetic field accelerators, cyclotrons, linear accelerators, and voltage-multiplying accelerators.

[0346] The gantry is a rotating component in a radiotherapy system that drives the particle accelerator and beam delivery system around the isocenter, allowing particle beams to be irradiated at varying angles, thereby covering the entire tumor area. Medical particle accelerators are designed based on the isocenter principle. Theoretically, within the full range of operating angles of an arc radiotherapy system, the device's three rotational axes (the gantry, the treatment head, and the treatment couch) should intersect at a single point (e.g., within the patient's body), known as the isocenter (ISO) or isocenter point.

[0347] A particle radiation source refers to a source used to generate a particle beam, for example, a component that generates high-energy charged particles.

[0348] The cavity (or chamber) refers to the space in the particle accelerator for accelerating the particle beam. The cavity can be, for example, a resonant cavity or a radio frequency resonant cavity, which is not limited in this application.

[0349] A magnetic field generator is a device or component that provides a particle deflection magnetic field to the cavity. As the particle beam moves within the particle accelerator, the particle deflection magnetic field deflects it, thereby maintaining its trajectory.

[0350] A magnetic field adjustment device is a device or component used to adjust the magnetic field that deflects particles. By adjusting the strength or direction of the magnetic field, the trajectory and irradiation position of the particle beam can be controlled, thereby achieving precise dose control.

[0351] For example, a particle accelerator in a radiotherapy system can generate a high-energy proton beam. During treatment, the treatment gantry can rotate continuously, and the particle accelerator rotates with the gantry. The particle accelerator includes a cavity for accelerating the proton beam. The cavity is located in a particle deflection magnetic field provided by a magnetic field providing device. Furthermore, a magnetic field adjustment device is located outside the cavity to adjust the direction and strength of the particle deflection magnetic field, thereby controlling the deflection of the proton beam and achieving particle beam irradiation at different angles. As an example, the magnetic field providing device is a superconducting coil used to generate the required strong magnetic field. The magnetic field adjustment device can be a controllable motion device for adjusting the position and / or direction of the magnetic field providing device; alternatively, the magnetic field adjustment device can be a group of magnets (e.g., one or more) that can adjust the magnetic field strength and direction, thereby achieving precise control of the proton beam at different angles.

[0352] Therefore, the particle accelerator is applied to the radiotherapy system and rotates together with the treatment gantry. The particle accelerator includes a particle radiation source, a cavity and a magnetic field providing device (all devices of the particle accelerator rotate along with the treatment gantry). During the rotation of the treatment gantry, the particle accelerator rotates with the treatment gantry and performs radiotherapy through a particle beam. The particle radiation source is a component that generates a particle beam. During the radiotherapy process, it generates a high-energy particle beam for irradiating tumor cells in the patient's body. The cavity is a space where the particle beam is accelerated. When the particle beam passes through the cavity, it will be further accelerated in it to reach the required energy level for radiotherapy. The magnetic field providing device is used to provide a particle deflection magnetic field for the cavity. By adjusting the strength and direction of the particle deflection magnetic field, the motion trajectory and parameters of the particle beam, such as energy, beam spot size and beam spot position, can be controlled.

[0353] The advantage of this is that by using a magnetic field adjustment device, the particle deflection magnetic field can be precisely adjusted and controlled, so that the motion trajectory and parameters of the particle beam can be precisely adjusted, thereby ensuring the accuracy and therapeutic effect of radiotherapy; the particle accelerator rotates together with the treatment gantry, increasing the flexibility and applicability of radiotherapy. Through the rotation of the gantry, irradiation at different angles and directions can be achieved, making the treatment more comprehensive and efficient; the particle radiation source produces a high-energy particle beam that can better penetrate tissue, allowing the treatment to act more deeply on tumor cells while minimizing damage to healthy tissue; due to the precise control and high-energy characteristics of the particle beam, the particle accelerator can provide more accurate and higher-quality radiotherapy, helping patients achieve better treatment results.

[0354] In some embodiments, the particles corresponding to the particle beam are protons or heavy ions.

[0355] In some embodiments, the magnetic field providing device includes one or more superconducting coils. As an example, the magnetic field providing device includes one superconducting coil. As another example, the magnetic field providing device includes multiple superconducting coils.

[0356] A particle beam is a stream of charged particles used for radiation therapy.

[0357] Protons are positively charged particles that form part of the nucleus of an atom. In radiotherapy, proton beams can be used to precisely irradiate tumor tissue, delivering high doses to the tumor area while minimizing damage to surrounding normal tissue.

[0358] Heavy ions are ions with a relatively large atomic mass, such as helium, carbon, and oxygen ions. Heavy ions have high energy deposition and strong biological effects, and can be used to irradiate deep tumors in radiotherapy.

[0359] A superconducting coil is a special coil made of superconducting material that can achieve a superconducting state at low temperatures (or even room temperature), allowing current to flow unimpeded inside it. In radiotherapy equipment, superconducting coils are used to generate high-intensity magnetic fields to deflect and control the movement of particle beams. As an example, liquid helium can be used to create a low-temperature environment (for example, 4 Kelvin, close to absolute zero). Among them, superconducting materials are materials that have the property of exhibiting zero resistance and repelling magnetic lines of force under certain low-temperature conditions. It has been discovered that 28 elements and thousands of alloys and compounds can become superconductors. Superconducting materials can be divided into elemental materials, alloy materials, compound materials and superconducting ceramics according to their chemical composition.

[0360] The embodiment of the present application does not limit the material of the superconducting coil, which may be, for example, a metal material or an alloy material. Specifically, for example, copper oxide, niobium-titanium alloy, niobium-tin alloy, etc. may be used.

[0361] The embodiment of the present application does not limit the number of superconducting coils, which can be, for example, 1, 2, 3, 4, 10, etc.

[0362] For example, the radiotherapy system may be an arc radiotherapy system that uses protons or heavy ions as a particle beam for irradiation. For example, the treatment system may be a proton therapy system, in which a proton beam is used to irradiate a patient's tumor. Furthermore, the magnetic field providing device may utilize a superconducting coil as a magnet to generate the required strong magnetic field. For example, the superconducting coil may be a toroidal coil winding made of a superconducting material that can achieve a superconducting state at low temperatures, generating a sufficiently strong magnetic field to control the deflection of the proton beam.

[0363] Therefore, the particle beam can be protons or heavy ions. Protons and heavy ions are the types of particle beams commonly used in radiotherapy. They have high penetrating power and strong killing power, and can treat tumor cells with high precision.

[0364] The magnetic field providing device uses one or more superconducting coils. A superconducting coil is a coil made of special materials that can work at low temperatures and generate an extremely strong magnetic field, thereby achieving efficient control of the particle beam.

[0365] The advantages of this are that protons and heavy ions have higher penetrating power and smaller lateral diffusion, which can target tumor cells more accurately, reduce damage to surrounding healthy tissues, and help improve the accuracy and therapeutic effect of radiotherapy; protons and heavy ions have higher linear energy transfer and Bragg peak, which can accurately release more doses in tumor tissue, maximize the killing of malignant cells, and improve the success rate of treatment; using superconducting coils as magnetic field providers can generate extremely strong magnetic fields, thereby achieving efficient control of particle beams. The high efficiency and stability of superconducting coils can improve the performance and reliability of the accelerator, reduce energy loss and magnetic field leakage; the high precision and strong lethality of protons and heavy ions, combined with the advantages of superconducting coils, enable the particle accelerator to provide more accurate and higher-quality radiotherapy in radiotherapy, helping patients achieve better treatment results.

[0366] Refer to FIG9 , which is a schematic structural diagram of a beam spot size adjustment device provided in an embodiment of the present application.

[0367] In some embodiments, the particle accelerator further comprises:

[0368] The beam spot size adjusting device is used to adjust the beam spot size of the particle beam.

[0369] Beam spot size refers to the width of the beam at 50% of the dose distribution peak on the plane perpendicular to the beam reference axis.

[0370] The beam spot size adjustment device is used to adjust the beam spot size of the particle beam to meet the requirements of different patients or different treatment needs.

[0371] In this embodiment, a particle accelerator is used to generate a particle beam, and the beam spot size of the particle beam can be adjusted by a beam spot size adjustment device. For example, when it is necessary to treat tumors of different sizes, the beam spot size can be adjusted to adapt to different tumor sizes and shapes. Assume that the beam spot size adjustment device can adjust the size of the beam spot under different settings. For example, at the minimum setting, the beam spot size can be adjusted to a diameter of 1 cm, which is suitable for smaller tumors; while at the maximum setting, the beam spot size can be adjusted to a diameter of 1.5 cm, which is suitable for larger tumors. In this way, doctors can flexibly adjust the beam spot size according to the patient's specific situation and treatment needs to achieve a personalized treatment plan. Adjusting the beam spot size can more accurately cover the tumor area and reduce radiation damage to surrounding normal tissues, thereby improving the accuracy and safety of radiotherapy.

[0372] Therefore, in addition to the particle radiation source, cavity, magnetic field providing device, and magnetic field adjustment device, the particle accelerator is also equipped with a beam spot size adjustment device. The beam spot size adjustment device is used to adjust the beam spot size of the particle beam. By adjusting the beam spot size, it can be adapted to different treatment needs, making radiotherapy more flexible and personalized.

[0373] The advantage of this is that different patients or tumors in different parts of the body may require different beam spot sizes to achieve the best treatment effect. With the beam spot size adjustment device, the treating physician can adjust the beam spot size of the particle beam according to the specific situation, realize personalized treatment plan, and improve the targetedness and effect of treatment; the beam spot size adjustment of the particle beam can better match the shape and size of the tumor, thereby reducing damage to surrounding healthy tissue. The beam spot size adjustment device makes radiotherapy more precise and accurate, and protects the surrounding normal tissue to the greatest extent; appropriate adjustment of the beam spot size can better distribute the irradiation dose at different depths and volumes, help to more comprehensively cover the tumor area, ensure that tumor cells receive sufficient treatment dose, and improve the treatment effect; the beam spot size adjustment device increases the flexibility of radiotherapy, and doctors can flexibly adjust the beam spot size of each treatment stage and treatment angle in the treatment plan according to actual needs, respond to possible changes during the treatment process, and achieve more accurate and effective treatment.

[0374] Continuing to refer to FIG9 , in some embodiments, the beam spot size adjustment device includes one or more adjustment components, each of which includes a second drive controller (not shown), a second drive mechanism 301 , a second transmission mechanism 303 , and a shielding mechanism 305 ;

[0375] In each of the adjustment components, the second transmission mechanism 303 is fixedly connected to the shielding mechanism 305, and the second drive controller is used to drive the second drive mechanism 301 to move according to the second control instruction corresponding to the adjustment component, so that the second drive mechanism 301 drives the second transmission mechanism 303 to move, thereby adjusting the shielding state of the shielding mechanism 305.

[0376] The adjustment assembly is used to adjust the beam spot size. Each adjustment assembly comprises several components, such as a second drive controller, a second drive mechanism 301, a second transmission mechanism 303, and a shielding mechanism 305. This embodiment of the present application does not limit the number of adjustment assemblies; for example, the number may be 1, 2, 3, 4, 6, or 8. Accordingly, the number of second drive controllers, second drive mechanisms 301, second transmission mechanisms 303, and shielding mechanisms 305 may be 1, 2, 3, 4, 6, or 8, etc.

[0377] The shielding mechanism 305 is used to control the scattering effect of the particle beam, thereby adjusting the beam spot size. For example, by opening or closing a specific shielding mechanism 305 (for example, a cover plate), the scattering effect of the particle beam is limited or changed. That is, the shielding state of the shielding mechanism 305 includes offline (that is, the shielding mechanism 305 is turned on) and online (that is, the shielding mechanism 305 is closed). When the number of adjustment components is multiple, the number of shielding mechanisms 305 is multiple, and multiple shielding mechanisms 305 can be arranged along the circumferential direction of the particle beam. As an example, the number of shielding mechanisms 305 is 2, and the two shielding mechanisms 305 are mirror-symmetrical on both sides of the particle beam.

[0378] The second drive controller is a control unit in the beam spot size adjustment device, and is used to control the movement of the adjustment component, for example, receiving a second control instruction and converting it into a control signal for the second drive mechanism 301 .

[0379] The second drive mechanism 301 is a mechanical component in the beam spot size adjustment device, used to achieve the movement of the shielding mechanism 305. For example, by receiving a control signal from the second drive controller, the second transmission mechanism 303 is driven to move, thereby driving the movement of the shielding mechanism 305 to adjust the beam spot size.

[0380] The second transmission mechanism 303 is fixedly connected to the shielding mechanism 305 and is used to transmit the movement of the second driving mechanism 301 , thereby adjusting the shielding state of the shielding mechanism 305 .

[0381] For example, the beam spot size adjustment device is composed of an adjustment component, which includes a second drive controller, a second drive mechanism 301, a second transmission mechanism 303 and a shielding mechanism 305. When the beam spot size needs to be adjusted, the second drive controller receives the corresponding control instruction (i.e., the second control instruction), and then drives the second drive mechanism 301 to move. The movement of the second drive mechanism 301 is transmitted through the second transmission mechanism 303, and finally adjusts the shielding state of the shielding mechanism 305. By adjusting the opening and closing degree of the shielding mechanism 305, the beam spot size of the particle beam can be adjusted. For example, when the shielding mechanism 305 is turned on (i.e., the shielding mechanism 305 is offline), the beam spot size of the particle beam is smaller; and when the shielding mechanism 305 is turned off (i.e., the shielding mechanism 305 is online), the beam spot size of the particle beam is larger.

[0382] Thus, the beam spot size adjustment device includes one or more adjustment components, each of which includes a second drive controller, a second drive mechanism 301, a second transmission mechanism 303, and a shielding mechanism 305. The shielding mechanism 305 is a key component of the beam spot size adjustment device, used to control the beam spot size of the particle beam. By adjusting the shielding mechanism 305, the particle beam can be scattered or not scattered, thereby changing the size of the beam spot. The second transmission mechanism 303 is fixedly connected to the shielding mechanism 305. By adjusting the position of the second transmission mechanism 303, the shielding state of the shielding mechanism 305 can be controlled, thereby adjusting the beam spot size. The second drive controller is used to drive the movement of the second drive mechanism 301 according to the second control command corresponding to the adjustment component. By controlling the movement of the second drive mechanism 301, the position of the shielding mechanism 305 can be adjusted.

[0383] The advantage of this is that by adjusting the second drive controller in the component, the beam spot size can be flexibly adjusted; the beam spot size adjustment device allows real-time adjustment of the beam spot size according to the size and position of the tumor during treatment, which can optimize the treatment plan, ensure that the particle beam is fully covered in the target area, and improve the treatment effect; by precisely controlling the beam spot size, radiation damage to surrounding normal tissues can be reduced, and excessive irradiation of healthy tissues can be avoided, which helps to improve the safety and tolerability of treatment; adjusting the beam spot size can better match the shape and size of the tumor, so that the energy of the particle beam is more effectively utilized, thereby improving treatment efficiency.

[0384] 9 and 10 , FIG10 is a schematic structural diagram of a cover plate provided in an embodiment of the present application.

[0385] In some embodiments, the second driving mechanism 301 is a motor; and / or,

[0386] The second transmission mechanism 303 uses a screw rod; and / or,

[0387] The shielding mechanism 305 is a shielding plate.

[0388] As an example, the shielding mechanism 305 adopts a plurality of shielding plates that are provided in pairs and arranged symmetrically along the center line.

[0389] In this embodiment, the second driving mechanism 301 adopts a motor, receives a control signal corresponding to the second control instruction, and drives the movement of the cover plate through a screw rod, thereby adjusting the beam spot size.

[0390] A motor is a device that converts electrical energy into mechanical energy, and drives the motion of other devices by rotation or linear motion. Here, the motor is used to drive the screw rod, thereby controlling the motion of the shielding mechanism 305.

[0391] A lead screw is a mechanical component, typically a helical rod with threads on its surface, that mates with a nut to convert rotational motion into linear motion. Here, the lead screw serves as the second transmission mechanism 303, connected to the shielding mechanism 305. Rotating the lead screw adjusts the opening and closing of the shielding mechanism 305, thereby adjusting the beam spot size.

[0392] The shield plate is, for example, a flat plate that can be opened (i.e., offline) or closed (i.e., online) to scatter the particle beam (online) or not (offline). Here, the shield plate is used as a shielding mechanism 305. By opening or closing the shield plate, the beam spot size is adjusted to achieve precise irradiation of radiotherapy. The present application does not limit the shape of the shield plate, which may be, for example, L-shaped, square, circular, trapezoidal, triangular, annular, fan-shaped or irregular. The present application does not limit the thickness of the shield plate, which may be, for example, 0.01, 0.02, 0.03, 0.05, 0.1, 0.2, 0.3, 0.5, 1, 2, 3, 5, 10 mm, etc. The present application does not limit the material of the shield plate, which may be, for example, boron carbide or polycarbonate.

[0393] Therefore, the beam spot size adjustment device uses a motor as the second driving mechanism 301, a lead screw as the second transmission mechanism 303, and a cover plate as the shielding mechanism 305. The second driving mechanism 301 is powered by a motor, which drives the movement of the lead screw through the rotation of the motor. The motor can precisely control the position and direction of movement of the lead screw; the second transmission mechanism 303 uses a lead screw, which is a rod-shaped part with threads. When driven by the motor, the lead screw will move linearly along the direction of its threads. The movement of the lead screw can be used to control the position of the cover plate; the cover plate serves as the shielding mechanism 305, and moves through the transmission of the lead screw. The movement range and position of the cover plate can be controlled by the movement of the lead screw, thereby achieving adjustment of the beam spot size of the particle beam.

[0394] The advantage of doing this is that by using a motor and a lead screw as the second driving mechanism 301 and the second transmission mechanism 303 respectively, precise beam spot size adjustment can be achieved, and the beam spot size adjustment device can accurately adjust the position of the cover plate according to the second control instruction, thereby achieving precise control of the beam spot size of the particle beam; the motor and the lead screw are both stable and reliable motion control devices with good performance and life, which can ensure the stable operation and long-term use of the adjustment device; using a motor and a lead screw as the second driving mechanism 301 and the second transmission mechanism 303 can achieve fast and efficient beam spot size adjustment, which helps to improve the efficiency of radiotherapy and reduce treatment time; using a cover plate as the shielding mechanism 305 can flexibly adjust the beam spot size of the particle beam, and can flexibly select and control the appropriate beam spot size according to the patient's condition and treatment plan to achieve a personalized treatment plan.

[0395] Continuing to refer to Figure 9, in one embodiment, the beam spot size adjustment device is located downstream of the beam outlet of the particle accelerator, and includes a motor, a coupling 302, a screw, a bearing 304 and two individually controllable cover plates. The bearing 304 is, for example, a seated bearing. The thickness of the cover plate is, for example, 0.5 mm and 1 mm, respectively, and is made of boron carbide or polycarbonate. The motor drives the cover plate to perform linear motion through the screw. When the particle beam hits the cover plate, scattering occurs, and the beam spot size and beam energy will change. The beam spot size adjustment device can be used to increase the beam size to meet specific irradiation requirements. Two cover plates (referred to as cover plate 1 and cover plate 2) can provide four beam spot size options:

[0396] 1. Cover plate 1Off, cover plate 2Off;

[0397] 2. Cover plate 1 is on, cover plate 2 is off;

[0398] 3. Cover plate 1 Off, cover plate 2 On;

[0399] 4. Cover plate 1On, cover plate 2On.

[0400] The "Off" setting indicates that the shield is offline and does not scatter the beam; the "On" setting indicates that the shield is online and scatters the beam, which has a certain impact on the beam spot size and energy. When debugging a particle accelerator, it is necessary to obtain the beam spot size parameters for different settings.

[0401] Continuing to refer to FIG8 , in some embodiments, the particle accelerator further includes:

[0402] a radio frequency device for providing an accelerating electric field to the cavity; and / or,

[0403] a vacuum device for providing a vacuum environment for the cavity; and / or,

[0404] A liquid cooling device is used to cool the cavity by using cooling liquid.

[0405] A radiofrequency device is a device within a particle accelerator that provides an accelerating electric field within the cavity. This field, through the action of a radiofrequency electromagnetic field, accelerates particles within the cavity, forming a high-speed particle beam for radiotherapy. The accelerating field is the electric field within the particle accelerator, which imparts kinetic energy to particles, accelerating them to the speed required for treatment. The radiofrequency electromagnetic field generated by the radiofrequency device creates this accelerating field.

[0406] A vacuum device is a device within a particle accelerator that provides a vacuum environment within the cavity. During particle acceleration, to prevent energy loss from collisions between particles and gas, the cavity is maintained in a vacuum or near-vacuum state, ensuring stability and efficiency during the acceleration process.

[0407] Liquid cooling is a device within a particle accelerator that cools the cavity using a cooling liquid. Particle accelerators generate a significant amount of heat during operation. Liquid cooling is used to maintain a controllable cavity temperature and prevent damage to the equipment caused by overheating. The cooling liquid used is, for example, water or another coolant.

[0408] For example, a particle accelerator is used to deliver proton beams for radiotherapy. This particle accelerator is equipped with a radio frequency (RF) device that generates an accelerating electric field through a radio frequency electromagnetic field, accelerating the protons within a cavity. To ensure stable proton acceleration within the cavity, the particle accelerator is also equipped with a vacuum device to maintain a vacuum state and prevent gas collisions from affecting the protons' motion. Furthermore, since the proton acceleration process generates a large amount of heat, to prevent overheating, the particle accelerator is equipped with a liquid cooling device that uses water to dissipate heat from the cavity and maintain the device's operating temperature within a controllable range. Such a particle accelerator can provide high-quality proton beams for radiotherapy, ensuring the efficiency and safety of the treatment process.

[0409] Therefore, in addition to including a particle radiation source, a cavity, a magnetic field providing device, and a magnetic field adjustment device, the particle accelerator is also equipped with some auxiliary devices, such as a radio frequency device, a vacuum device, and a liquid cooling device. The radio frequency device is used to provide an accelerating electric field for the cavity. During the particle acceleration process, the particles are subjected to the accelerating electric field in the cavity, thereby accelerating to the required energy level. The radio frequency device generates a high-frequency electric field, allowing the particles to continuously gain energy in the cavity, thereby forming a high-energy particle beam. The vacuum device is used to provide a vacuum environment for the cavity. During the particle acceleration process, the particles need to propagate in a vacuum to avoid energy loss due to collisions with gas molecules. The vacuum device ensures that the interior of the cavity is in a high vacuum state to ensure the stability and efficiency of the particle acceleration process. The liquid cooling device uses a cooling liquid (for example, water) to cool the cavity. During the particle acceleration process, the cavity generates a large amount of heat. The liquid cooling device absorbs this heat through the cooling liquid, keeping the cavity within a suitable temperature range to ensure stable operation and long-term use of the equipment.

[0410] The advantage of this is that the radio frequency device provides a high-frequency accelerating electric field, allowing particles to quickly obtain the required energy, thereby improving particle acceleration efficiency and reducing treatment time; the vacuum device maintains a high vacuum inside the cavity to avoid collisions between gas molecules and particles, ensuring the stability and reliability of the particle transmission process; the liquid cooling device effectively reduces the heat generated during the acceleration process by cooling the cavity, keeping the cavity within a suitable temperature range, preventing the equipment from overheating and damage, and improving the stability and reliability of the equipment; these auxiliary devices ensure the stable operation and precise control of the particle accelerator, thereby improving the precision and accuracy of radiotherapy. Doctors can more finely control the energy and direction of the particle beam, achieve more personalized treatment plans, and improve treatment effects.

[0411] Continuing to refer to FIG8 , in a specific application scenario, an embodiment of the present application further provides a particle accelerator, which is applied to a radiotherapy system. During the rotation of the treatment gantry, the particle accelerator rotates along with the treatment gantry.

[0412] The particle accelerator comprises:

[0413] A particle radiation source, used to generate a particle beam; the particles corresponding to the particle beam are protons or heavy ions;

[0414] a cavity for accelerating the particle beam therein;

[0415] A magnetic field providing device, used for providing a particle deflection magnetic field for the cavity; the magnetic field providing device comprises a superconducting coil;

[0416] A magnetic field adjustment device, used for adjusting the particle deflection magnetic field;

[0417] A beam spot size adjustment device for adjusting the beam spot size of the particle beam; the beam spot size adjustment device includes one or more adjustment components, each of which includes a second drive controller, a second drive mechanism, a second transmission mechanism, and a shielding mechanism; in each of the adjustment components, the second transmission mechanism is fixedly connected to the shielding mechanism, and the second drive controller is used to drive the second drive mechanism to move according to the second control instruction corresponding to the adjustment component, so that the second drive mechanism drives the second transmission mechanism to move, thereby adjusting the shielding state of the shielding mechanism; the second drive mechanism adopts a motor; the second transmission mechanism adopts a screw; the shielding mechanism adopts a plurality of cover plates arranged in pairs and symmetrically arranged along the center line;

[0418] a radio frequency device, for providing an accelerating electric field for the cavity;

[0419] A vacuum device, used to provide a vacuum environment for the cavity;

[0420] A liquid cooling device is used to cool the cavity by using cooling liquid.

[0421] (Magnetic field adjustment device).

[0422] See FIG. 11 , which is a structural block diagram of a magnetic field adjustment device provided in an embodiment of the present application.

[0423] The embodiment of the present application further provides a magnetic field adjustment device, which is applied to a particle accelerator in a radiotherapy system. During the rotation of the treatment gantry, the particle accelerator rotates along with the treatment gantry.

[0424] The magnetic field adjustment device is used to adjust the particle deflection magnetic field in the particle accelerator according to the change of the gantry angle, so that the particle beam generated by the particle radiation source meets the preset particle beam conditions under the action of the particle deflection magnetic field;

[0425] The particle beam condition is used to indicate a preset range of one or more parameters of the particle beam: energy, beam spot size, and beam spot position.

[0426] A magnetic field adjustment device is used in particle accelerators within radiotherapy systems. Its function is to adjust the particle deflection magnetic field within the particle accelerator based on changes in the gantry angle. By adjusting the particle deflection magnetic field, the particle beam generated by the particle radiation source can be adjusted to meet preset beam conditions under the influence of the magnetic field.

[0427] Gantry angle refers to the angle of the treatment gantry. For example, a treatment gantry consists of two arms and a gantry body between them. The two arms are each pivotally connected to a fixed base, and the particle accelerator is mounted on the gantry body. For example, the length of the arms parallel to the treatment bed can be considered zero degrees, and the gantry angle is the rotation angle of the arms around their rotational axes.

[0428] The particle deflection field is a magnetic field in a particle accelerator that controls the trajectory of a particle beam. By adjusting the magnitude and direction of the particle deflection field, the direction and position of the particle beam can be precisely controlled.

[0429] Beam conditions refer to the preset ranges of parameters such as beam energy, spot size, and spot position. These parameters are used to predetermine and guide the radiotherapy process. The spot size refers to the distribution of a narrow beam of particles in a plane perpendicular to the beam's reference axis. The spot size, or beam spot size, is the width of the beam at 50% of the peak dose distribution in a plane perpendicular to the beam's reference axis. The spot position refers to the center of the beam's dose distribution in a plane perpendicular to the beam's reference axis. The energy of the particle beam determines its penetration depth and irradiation range, while the spot size and spot position determine the precise location and shape of the irradiation.

[0430] Taking protons as an example, the energy of a proton beam is expressed in units of, for example, mega-electron volts (MeV). For example, treating a tumor at a depth of 5 cm under the skin may require a proton beam with an energy of about 100 MeV, while treating a tumor at a depth of 30 cm may require a proton beam with an energy of about 230 MeV. This application does not limit the energy of the particle beam. The beam spot size is, for example, in millimeters. The beam spot size determines the irradiation area of ​​the particle beam on the target tissue. For example, in order to treat a tumor with a diameter of 3 cm, the proton beam spot size may need to be around 5 mm to ensure accurate irradiation of the target area.

[0431] This application does not limit the preset ranges of parameters such as particle beam energy, beam spot size, and beam spot position, which can be determined based on the patient's condition, specific treatment needs, and treatment plan.

[0432] Therefore, the magnetic field adjustment device is applied to a particle accelerator in a radiotherapy system. The particle accelerator is placed on a treatment gantry and rotates with the treatment gantry. During the rotation of the treatment gantry, the device used to provide the particle deflection magnetic field may deviate slightly, causing the magnetic field direction to deflect, thereby affecting the stability of relevant particle beam parameters (such as energy, beam spot size, and beam spot position).

[0433] To ensure that changes in particle beam parameters such as energy, beam spot size, and beam spot position remain within an acceptable range during the rotation of the treatment gantry, the magnetic field adjustment device can adjust the magnetic field according to changes in the (treatment) gantry angle to counteract the influence of factors such as gravity and maintain the stability of the magnetic field direction.

[0434] The advantage of this is that the design of the magnetic field adjustment device enables the particle deflection magnetic field to be adjusted according to changes in the gantry angle, effectively counteracting magnetic field changes caused by factors such as gravity. Through the adjustment of the magnetic field adjustment device, the particle deflection magnetic field in the particle accelerator can remain stable during the rotation of the treatment gantry, ensuring that the particle beam generated by the particle radiation source meets the preset particle beam conditions and keeps parameters such as the particle beam energy, beam spot size and beam spot position within an acceptable range; the magnetic field adjustment device has an automatic adjustment function and can quickly adjust the magnetic field according to the gantry angle, making the entire magnetic field adjustment process more intelligent and efficient, and reducing the workload of the operator; in addition, the particle beam conditions can be preset according to the patient's specific situation and treatment plan to ensure more individualized treatment. The automatic adjustment function enables particle radiotherapy to better adapt to the needs of different patients.

[0435] 11 and 12 , FIG12 is a three-dimensional diagram of a magnetic field providing device and an execution component provided in an embodiment of the present application.

[0436] In some embodiments, the magnetic field adjustment device includes a detection component, a control component, and one or more execution components;

[0437] The detection component is used to detect magnetic field information of the particle deflection magnetic field;

[0438] The control component is used to calculate motion control information of the magnetic field providing device of the particle accelerator based on the magnetic field information and a preset magnetic field condition, and generate a first control instruction corresponding to each of the execution components based on the motion control information; wherein the preset magnetic field condition is determined according to the particle beam condition;

[0439] Each of the execution components is used to adjust the position and / or direction of the magnetic field providing device according to its corresponding first control instruction.

[0440] In radiotherapy systems, the magnetic field adjustment device can control the movement trajectory and irradiation range of the particle beam by adjusting the particle deflection magnetic field, thereby achieving precise radiotherapy.

[0441] The detection component is used to detect the particle deflection magnetic field in the particle accelerator and measure the magnetic field information.

[0442] The control component is used to calculate the motion control information of the magnetic field providing device (i.e., information used to control the motion of the magnetic field providing device) based on the measured magnetic field information and preset magnetic field conditions, and generate a first control instruction corresponding to each execution component.

[0443] Each actuator is located in a portion or region of the particle accelerator, and the mounting base of the actuator remains relatively stationary with respect to the treatment gantry. For example, the mounting base of the actuator is removably mounted on the treatment gantry. The actuator is configured to adjust the magnetic field providing device that generates the particle deflection magnetic field according to its corresponding first control instruction. That is, when the number of actuators is greater than one, the multiple actuators can jointly adjust the position and / or direction of the magnetic field providing device so that the particle deflection magnetic field meets the preset magnetic field conditions. This application does not limit the number of actuators, and it can be, for example, 1, 2, 3, 4, 6, 8, 12, etc.

[0444] As an example, the number of the actuators is 2, and the two actuators are arranged on both sides of the magnetic field providing device, with one on each side.

[0445] As another example, as shown in Figure 12, the number of actuators is four, with two actuators disposed on each side of the magnetic field providing device. The length directions of the two actuators on the same side can be parallel or skew (including the special case of skew perpendicularity).

[0446] For example, assume that a particle accelerator in a radiotherapy system has four actuators (A, B, C, and D).

[0447] The detection component will detect the particle deflection magnetic field and obtain the corresponding magnetic field information.

[0448] The control component calculates the motion control information of the magnetic field providing device based on the measured magnetic field information and the preset magnetic field range. Assume that the magnetic induction intensity corresponding to the preset magnetic field condition is 8T±0.5% (the magnetic induction intensity corresponding to the preset magnetic field condition can also be 5T±1%, 7T±0.1%, 9T±0.2%, etc., and this application does not limit this), and the unit T is Tesla. If the measured magnetic field deviates from the numerical range corresponding to the preset magnetic field condition, the control component will calculate the offset that the magnetic field providing device needs to adjust (including position offset and / or posture offset), and generate the first control instructions corresponding to the execution components A, B, C, and D respectively.

[0449] After receiving its corresponding first control instruction, actuator A will execute movement according to the instruction to adjust the position and / or orientation of the magnetic field providing device, thereby adjusting the particle deflection magnetic field it generates. Similarly, actuators B, C, and D will also adjust the position and / or orientation of the magnetic field providing device according to their respective corresponding first control instructions, thereby adjusting the particle deflection magnetic field. In other words, actuators A, B, C, and D jointly adjust the position and / or orientation of the magnetic field providing device to achieve adjustment of the particle deflection magnetic field.

[0450] Thus, the magnetic field adjustment device includes a detection component, a control component and one or more execution components. The detection component is used to detect the magnetic field information of the particle deflection magnetic field. By using a sensor or other measuring device, the detection component can monitor the size and direction parameters of the magnetic field in the particle accelerator in real time. The control component calculates motion control information based on the magnetic field information obtained by the detection component and the preset magnetic field conditions. The preset magnetic field conditions are determined according to the particle beam conditions and are used to indicate the preset range of magnetic field parameters such as the magnetic field direction and magnetic field size. The control component generates a first control instruction corresponding to each execution component based on this information. Each execution component is responsible for adjusting the position and / or direction of the magnetic field providing device according to its corresponding first control instruction, thereby adjusting the particle deflection magnetic field. By adjusting the magnetic field providing device (for example, a superconducting coil, a magnet coil or other magnetic field providing device), the execution component can achieve real-time adjustment of the particle deflection magnetic field.

[0451] The advantage of this is that the magnetic field information is monitored in real time by the detection component, and the motion control information is calculated by the control component. The magnetic field adjustment device can accurately adjust the particle deflection magnetic field, which helps to ensure that the particle beam generated by the particle radiation source meets the preset particle beam conditions, thereby improving the accuracy of radiotherapy; the control component calculates the motion control information based on the magnetic field information and the preset magnetic field conditions, so that the first control instruction corresponding to each execution component can adjust the particle deflection magnetic field in real time, ensuring that the parameters such as the energy, beam spot size and beam spot position of the particle beam are within an acceptable range, ensuring the stability and consistency of the treatment; the control component can autonomously calculate the motion control information based on the magnetic field information and generate the first control instruction of the execution component. This automated adjustment makes the entire magnetic field adjustment process more intelligent and efficient, reducing labor costs.

[0452] In some embodiments, the detection component includes one or more Hall detection units for detecting one or more positions of the particle deflection magnetic field to obtain the magnetic field information.

[0453] The Hall detection unit is a sensor unit in the detection assembly. Each Hall detection unit is used to detect a position of the particle deflection magnetic field in the particle accelerator and obtain magnetic field information at that position through the Hall effect. The Hall detection unit can be, for example, a Hall probe.

[0454] The Hall effect is a phenomenon that converts electric and magnetic fields into voltage differences, which can be used to measure the strength and direction of magnetic fields. When a Hall effect detector is placed at a specific location in a particle accelerator, if a magnetic field is present, the detector will generate a voltage difference. This voltage difference is related to the strength and direction of the magnetic field, thus providing information about the magnetic field at that location (for example, the magnetic induction intensity).

[0455] The present application does not limit the number of Hall detection units, which may be 1, 2, 3, 4, 6, etc. The magnetic field adjustment device can calculate the magnetic field strength and direction at different positions, thereby obtaining magnetic field information at one or more positions.

[0456] For example, assume that a particle accelerator in a radiotherapy system uses a detection assembly to monitor the particle deflection magnetic field. The detection assembly includes two Hall effect detector units, which are placed at different positions X and Y in the particle accelerator.

[0457] When the particle accelerator starts running and generates a particle deflection magnetic field, the two Hall detection units will respectively detect the magnetic fields at the positions X and Y, and obtain the magnetic induction intensity of the two positions X and Y as magnetic field information, that is, the magnetic field information includes the measured values ​​of the magnetic induction intensity at the positions X and Y. The preset magnetic field conditions are, for example, used to indicate the set values ​​of the magnetic induction intensity at the positions X and Y. Feedback control can be performed by the measured values ​​and set values ​​of the magnetic induction intensity at each position (X, Y). For example, the position and / or direction of the magnetic field providing device is adjusted by one or more actuators, thereby adjusting the particle deflection magnetic field at the positions X and Y so that the measured values ​​and set values ​​of the magnetic induction intensity at the positions X and Y are equal, thereby achieving more accurate particle beam control.

[0458] Therefore, the detection component in the magnetic field adjustment device uses one or more Hall effect detectors to detect one or more locations of the particle deflection magnetic field, thereby obtaining magnetic field information. A Hall effect detector is a sensor used to measure magnetic fields. In this magnetic field adjustment device, the Hall effect detector is placed inside the particle accelerator or at other locations capable of detecting the particle deflection magnetic field to sense changes in the magnetic field. Once the Hall effect detector is installed, it can sense magnetic field information of the particle deflection magnetic field based on its location and then transmit this magnetic field information to the control component.

[0459] The advantages of this approach are that the Hall detection unit is a precision magnetic field sensor that can accurately measure the magnetic field information of the particle deflection magnetic field, ensuring that the magnetic field adjustment device can obtain high-quality magnetic field data and provide an accurate basis for subsequent adaptive control. The detection component uses one or more Hall detection units. When there are multiple Hall detection units, magnetic field changes can be detected simultaneously at different locations. By detecting at multiple locations, the magnetic field adjustment device can obtain more comprehensive magnetic field information, making the magnetic field adjustment process more precise and comprehensive. Because the Hall detection unit can sense magnetic field changes in real time, the detection component can provide real-time magnetic field information, allowing the control component to calculate and adjust the magnetic field in a timely manner based on the magnetic field information, maintaining the stability and accuracy of the magnetic field. The use of Hall detection units for magnetic field detection makes their placement adjustable and flexible. According to the specific structure and needs of the particle accelerator, the installation location of the Hall detection unit can be freely selected to meet the magnetic field monitoring requirements in different situations. Overall, the detection component using Hall detection units provides high-precision, real-time magnetic field information, providing reliable data support for the control component, enabling the magnetic field adjustment device to more accurately adjust the particle deflection magnetic field, maintain the stability and accuracy of the particle beam, and thus improve the effect of radiotherapy.

[0460] Referring to Figures 13 to 16, Figure 13 is a structural block diagram of an execution component provided in an embodiment of the present application, Figure 14 is a structural schematic diagram of an execution component provided in an embodiment of the present application, Figure 15 is a side view of a magnetic field providing device and an execution component provided in an embodiment of the present application, and Figure 16 is a top view of a magnetic field providing device and an execution component provided in an embodiment of the present application.

[0461] The number of execution components is N, where N is, for example, 1, 2, 4, 6, 8, 12, etc.

[0462] In some embodiments, the magnetic field adjustment device includes first to fourth actuators, the first and second actuators are located on the first side of the magnetic field providing device, the third and fourth actuators are located on the second side of the magnetic field providing device, and the first and second sides of the magnetic field providing device are arranged relative to each other; the center of the first actuator and the center of the fourth actuator are connected to obtain a first line, and the center of the second actuator and the center of the third actuator are connected to obtain a second line, and the first line intersects with the second line.

[0463] In some embodiments, each of the execution components includes a first drive controller 201, a first drive mechanism 202 and a first transmission mechanism 203;

[0464] The control component is used to calculate the target displacement of each first transmission mechanism 203 according to the motion control information, and generate a first control instruction corresponding to the execution component to which it belongs according to the target displacement of each first transmission mechanism 203;

[0465] In each of the execution components, the first transmission mechanism 203 is fixedly connected to the magnetic field providing device, and the first drive controller 201 is used to drive the first drive mechanism 202 to move according to the first control instruction corresponding to the execution component, so that the first drive mechanism 202 drives the first transmission mechanism 203 to move the target displacement, thereby adjusting the position and / or direction of the magnetic field providing device.

[0466] The actuator component is a component in the magnetic field adjustment device that is used to adjust the position and / or direction of the magnetic field providing device.

[0467] The first driving controller 201 is a controller in the execution component, and is used to receive a first control instruction corresponding to the execution component and control the movement of the first driving mechanism 202 according to the first control instruction corresponding to the execution component.

[0468] The first drive mechanism 202 is responsible for actual motion driving and executes corresponding motion according to the instructions of the first drive controller 201. The first drive mechanism 202 is provided with a housing, for example, which is fixedly connected to the treatment gantry (or the portion of the particle accelerator that remains relatively stationary with the treatment gantry) via a mounting base.

[0469] The first transmission mechanism 203 is fixedly connected to the magnetic field providing device. The first transmission mechanism 203 is, for example, provided with a connector and is fixedly connected to the magnetic field providing device via the connector. The magnetic field providing device can be provided with a connector that matches the connector. The first transmission mechanism 203 can transmit the motion of the first driving mechanism 202 to the magnetic field providing device, and adjust the position and / or direction of the magnetic field providing device to achieve adjustment of the particle deflection magnetic field. Adjusting the position and / or direction of the magnetic field providing device can affect the particle deflection magnetic field, thereby changing the energy, beam spot size and beam spot position of the particle beam, ultimately meeting the preset particle beam conditions. The present application does not limit the motion form of the first transmission mechanism 203, and for example, it can be translation and / or rotation.

[0470] As an example, as shown in Figures 12, 15, and 16, the first transmission mechanism 203 of each actuator (i.e., actuators A, B, C, and D) can translate along its corresponding preset straight line to move closer to or further away from the magnetic field providing device. Each first transmission mechanism 203 can translate along its corresponding preset straight line to achieve its corresponding target displacement. As can be seen, this translation is directional and can be directed toward or away from the magnetic field providing device. The first transmission mechanisms 203 of the actuators arranged on opposite sides of the magnetic field providing device (for example, upper left A corresponds to lower right D, and lower left B corresponds to upper right C) can achieve angular control of the magnetic field providing device. For example, the first transmission mechanism 203 of actuator A on the upper left side of the magnetic field providing device translates a distance (for example, target displacement S) away from the magnetic field providing device, and the first transmission mechanism 203 of actuator D on the lower right side of the magnetic field providing device translates away from the magnetic field providing device (for example, target displacement S), at which point the magnetic field providing device will rotate about its axis.

[0471] The magnetic field providing device has three attitude angles. If multiple attitude angles of the magnetic field providing device need to be adjusted, the first transmission mechanism 203 of actuator B on the lower left side of the magnetic field providing device and the first transmission mechanism 203 of actuator C on the upper right side of the magnetic field providing device can also be appropriately translated to achieve directional adjustment of the magnetic field providing device. When the magnetic field providing device needs to be translated, for example, the first transmission mechanisms 203 of actuators A and B on the left side of the magnetic field providing device can be controlled to translate away from the magnetic field providing device, while the first transmission mechanisms 203 of actuators C and D on the right side of the magnetic field providing device can be controlled to translate toward the magnetic field providing device. The position adjustment of the magnetic field providing device is achieved under the combined force of the left-side pulling force and the right-side pushing force.

[0472] For example, assuming that a magnetic field adjustment device is used in a particle accelerator of a radiotherapy system to adjust the energy of a particle beam, the magnetic field adjustment device includes four execution components, each of which receives its own corresponding first control instruction.

[0473] In each actuator, the first drive controller 201 receives the first control instruction corresponding to the actuator, controls the movement of the first drive mechanism 202, and drives the position and / or direction of the magnetic field providing device to change through the first transmission mechanism 203, thereby adjusting the position and / or direction of the magnetic field providing device. For example, if the energy of the particle beam needs to be reduced from 230 MeV to 229 MeV, each first drive controller 201 will move the magnetic field providing device to the corresponding position and / or direction via the first drive mechanism 202 and the first transmission mechanism 203, so that the energy of the particle beam can be adjusted. For another example, if the beam spot size of the particle beam needs to be reduced from 1.5 cm to 1.2 cm, each first drive controller 201 will adjust the position and / or direction of the magnetic field providing device via the first drive mechanism 202 and the first transmission mechanism 203, so that the beam spot size of the particle beam can be adjusted. For another example, if the beam spot position of the particle beam needs to be moved from the left side to the right side of the patient, the first drive controller 201 will adjust the magnetic field providing device to the corresponding position and / or direction through the first drive mechanism 202 and the first transmission mechanism 203 so that the beam spot position of the particle beam can be adjusted.

[0474] Thus, in the magnetic field adjustment device, each actuator includes a first drive controller 201, a first drive mechanism 202, and a first transmission mechanism 203. The first transmission mechanism 203 is fixedly connected to the magnetic field providing device, meaning that their movements are closely related. Each actuator is equipped with a first drive controller 201, which controls movement according to the first control instruction corresponding to the actuator. The first drive mechanism 202 is the power source of the actuator. It moves according to the signal of the first drive controller 201 and adjusts the position and / or direction of the magnetic field providing device by driving the first transmission mechanism 203. The first transmission mechanism 203 performs the role of transmission and adjustment, converting the movement from the first drive mechanism 202 into the position and / or direction adjustment of the magnetic field providing device. Through the posture control of the magnetic field providing device by the first drive controller 201, the first drive mechanism 202, and the first transmission mechanism 203 of each component, the position and / or direction of the magnetic field providing device can be changed accordingly, thereby affecting the direction, size, etc. of the particle deflection magnetic field.

[0475] The advantage of this is that each actuator has an independent first drive controller 201 and a first drive mechanism 202, so that the magnetic field adjustment device can achieve precise control of the particle deflection magnetic field. By controlling the movement of the first transmission mechanism 203 and the magnetic field providing device, the position and direction of the magnetic field can be precisely adjusted to achieve precise radiotherapy. Each actuator is an independent unit, and the movement between them can be adjusted relatively independently, so that the magnetic field adjustment device can flexibly adapt to different treatment conditions and the needs of different patients, achieving more individualized and customized radiotherapy. The first drive controller 201 drives the movement of the first drive mechanism 202 according to the first control instruction, and the first drive mechanism 202 drives the movement of the first transmission mechanism 203 to achieve real-time adjustment of the magnetic field providing device, so that the magnetic field adjustment device can quickly respond to changes in the actual magnetic field and maintain the stability and consistency of the particle beam parameters. By precisely controlling the position and direction of the magnetic field providing device, the particle deflection magnetic field generated by the magnetic field adjustment device can achieve high controllability of the particle beam parameters, thereby improving the accuracy and treatment effect of radiotherapy and minimizing damage to healthy tissue.

[0476] Continuing to refer to FIG13 , in some embodiments, each of the execution components further includes a position detection mechanism 204 . In each of the execution components:

[0477] The position detection mechanism 204 is used to detect the real-time displacement of the first transmission mechanism 203 in real time and send it to the control component, so that the control component generates a new first control instruction according to the real-time displacement of the first transmission mechanism 203 and the target displacement and sends it to the first drive controller 201;

[0478] The first drive controller 201 is used to drive the first drive mechanism 202 to move according to the new first control instruction, and the first transmission mechanism 203 is driven to move by the first drive mechanism 202 so that the real-time displacement of the first transmission mechanism 203 matches the target displacement.

[0479] In this embodiment, the target displacement refers to the predetermined displacement that each first transmission mechanism 203 needs to achieve. This target displacement is set based on the magnetic field adjustment requirements and can determine the target position to which the first transmission mechanism 203 is adjusted. In a radiotherapy system, as the treatment gantry rotates, particle beam parameters need to be adjusted according to the treatment plan. Each actuator adjusts the position and / or direction of the magnetic field providing device by receiving the target displacement of its corresponding first transmission mechanism 203.

[0480] The target displacement of the first transmission mechanism 203 corresponding to each preset angle interval can be calculated in real time according to the magnetic field information (measured in real time) and the preset magnetic field conditions after the treatment gantry is rotated.

[0481] Alternatively, the target displacement of the first transmission mechanism 203 corresponding to each preset angle interval can be pre-calibrated and specified in the treatment plan to guide the position adjustment of the magnetic field providing device. The pre-calibration method can reduce the amount of calculation during the treatment process, reduce the delay that may be caused by the calculation process, and improve the accuracy of motion control and treatment efficiency. As an example, during the rotation of the treatment gantry, the target displacement of the first transmission mechanism 203 corresponding to each preset angle interval is pre-set according to the treatment plan. For example, the target displacements of each first transmission mechanism 203 corresponding to the preset angles of 0°, 45°, 90°, 135°, and 180° can be pre-calibrated.

[0482] The position detection mechanism 204 is used to detect the real-time displacement of the first transmission mechanism 203 and send the real-time displacement to the control component. The real-time displacement refers to the real-time movement distance of the first transmission mechanism 203, which is obtained in real time by the position detection mechanism 204.

[0483] For example, assume a radiotherapy system has four actuators, A, B, C, and D, used to adjust particle beam energy. The treatment plan requires that the particle beam energy be reduced from 230 MeV to 229 MeV after the gantry rotates from 0° to 45°. Therefore, after the gantry rotates to 45°, the target displacements of the first actuators of actuators A, B, C, and D are set to 10, 30, 30, and 10 centimeters, respectively, with the movement directions being toward the cavity, away from the cavity, away from the cavity, and toward the cavity, respectively. Each actuator is equipped with a position detection mechanism 204 that can detect the real-time displacement of the first transmission mechanism 203.

[0484] Assuming that the real-time displacement of the first transmission mechanism 203 of the execution component A is detected to be 5 (the direction is close to the cavity), the control component will generate a new first control instruction and send it to the first drive controller 201 of the execution component A, so that the first drive controller 201 drives the first drive mechanism 202 to move, and the first drive mechanism 202 drives the first transmission mechanism 203 to continue to move in the direction close to the cavity.

[0485] After a preset time (e.g., 2 seconds), the real-time displacement of the first transmission mechanism 203 of the actuator A is detected again. Assuming that the real-time displacement at this time is 8, which is still less than 10, the control component will generate a new first control instruction again and send it to the first drive controller 201 of the actuator A, so that the first drive controller 201 drives the first drive mechanism 202 to move, and the first drive mechanism 202 drives the first transmission mechanism 203 to continue to move toward the direction close to the cavity, and finally the real-time displacement of the first transmission mechanism 203 of the actuator A reaches 10 (i.e., the target displacement). The control process of the actuators B, C, and D is similar and will not be repeated here.

[0486] For each actuator, through continuous motion feedback and adjustment, the first transmission mechanism 203 in the actuator precisely adjusts the position and / or orientation of the magnetic field providing device, thereby achieving precise adjustment of the particle deflection magnetic field and the particle beam energy. A similar process also applies to adjusting parameters such as beam spot size and position, and will not be further described here.

[0487] Therefore, in this magnetic field adjustment device, each actuator further includes a position detection mechanism 204 for detecting the real-time displacement of the first transmission mechanism 203 and transmitting it to the control component. The control component generates a new first control instruction corresponding to the actuator based on the real-time displacement and the target displacement, and transmits it to the first drive controller 201 of the actuator. In the actuator, the first drive controller 201 drives the first drive mechanism 202 according to the new first control instruction, which in turn drives the first transmission mechanism 203 through the first drive mechanism 202, thereby causing the magnetic field providing device to move to the corresponding target position and / or target posture. The advantage of doing this is that by combining the target displacement with the real-time displacement detected by the position detection mechanism 204, the control component can generate a new first control instruction for each execution component, and drive the movement of the first drive mechanism 202 through the first drive controller 201 to achieve precise adjustment and control of the magnetic field providing device, thereby ensuring the stability and accuracy of the parameters of the particle beam; the position detection mechanism 204 can detect the real-time displacement of the first transmission mechanism 203 in real time, so that the control component can generate the first control instruction in real time according to the real-time displacement and the target displacement, thereby achieving real-time adjustment and control of the magnetic field providing device; the control component can automatically generate a new first control instruction corresponding to each execution component, with a high degree of automation; by precisely controlling the position and / or direction of the magnetic field providing device, the magnetic field adjustment device can achieve high controllability of the particle beam parameters, which helps to improve the accuracy and treatment effect of radiotherapy and minimize damage to healthy tissue.

[0488] In some embodiments, the first driving mechanism 202 is a motor; and / or,

[0489] The first transmission mechanism 203 uses a mechanical shaft; and / or,

[0490] The position detection mechanism 204 is a potentiometer.

[0491] In this embodiment, the first driving mechanism 202 is a motor that can convert electrical energy into mechanical energy. As an example, the first driving mechanism 202 is a DC motor.

[0492] A mechanical axis is used as the first transmission mechanism 203 to adjust the position and / or direction of the magnetic field providing device. A mechanical axis is a mechanical device that can achieve the movement of an object by adjusting its position or direction. As an example, the first transmission mechanism 203 uses a rotary axis or a linear axis as the mechanical axis.

[0493] The position detection mechanism 204 uses a potentiometer, which is a sensor capable of measuring position or displacement and can determine position changes based on changes in measured voltage. For example, when the first transmission mechanism 203 moves, the potentiometer can detect the position change (i.e., distance) and send a corresponding signal to the control component.

[0494] Therefore, the magnetic field adjustment device utilizes an adaptive coil system, comprising a detection component (e.g., one or more Hall effect probes), a control component, and one or more actuator components. The Hall effect probes, installed within the particle accelerator, sense the magnitude of the magnetic field and generate a voltage proportional to the measured magnetic field, providing the required position of the magnetic coil for subsequent control. The actuator components include a first drive controller 201 (e.g., a motor controller), a first drive mechanism 202 (e.g., a motor), a first transmission mechanism 203 (e.g., a mechanical shaft), and a position detection mechanism 204 (e.g., a potentiometer). The magnetic field providing device utilizes, for example, a magnetic coil. The mechanical shaft is fixed to a support for the magnetic coil and can adjust the position and / or orientation of the magnetic coil. The motor is driven by the motor controller, which controls the movement of the mechanical shaft. The potentiometer monitors the real-time displacement of the mechanical shaft, thereby monitoring and controlling the position and / or orientation of the magnetic coil.

[0495] During the rotation of the treatment gantry, the Hall probe senses the magnetic field size of the particle accelerator and feeds back the magnetic field information to the control component. The control component calculates motion control information based on the actual magnetic field information and the preset magnetic field conditions, such as the displacement data that needs to be adjusted for each mechanical axis (i.e., the target displacement), and instructs the motor controller to drive the motor to move. The motor drives the magnetic coil through the mechanical axis. The potentiometer monitors the movement distance of the mechanical axis in real time and feeds back the information to the control component. Through multiple rounds of movement and feedback, the motor drives the mechanical axis to reach the preset position, and also causes the magnetic coil to reach its corresponding target position and / or target posture (i.e., target direction). When the treatment gantry rotates from one preset angle range to the next preset angle range, the change in the gantry angle may cause a change in the magnetic field. The Hall probe continuously monitors the magnetic field size in the particle accelerator and continuously drives the action of the entire actuator until the particle deflection magnetic field in the particle accelerator cavity reaches an acceptable range (i.e., the preset magnetic field conditions).

[0496] The advantage of this is that the Hall probe senses the magnetic field size in the particle accelerator, and the position of the magnetic coil is adjusted in real time through the execution component to achieve precise adjustment of the particle deflection magnetic field, which helps to improve the accuracy and treatment effect of radiotherapy; the position detection mechanism 204 uses a potentiometer to monitor the distance of the mechanical axis in real time, so that the control component can understand the position of the mechanical axis in real time and make timely adjustments, ensuring the real-time and accuracy of the magnetic field adjustment process; the control component automatically updates the first control instruction based on the position feedback of the first transmission mechanism 203, and automatically drives the motor to move through the motor controller to achieve automatic adjustment of the magnetic coil. This automatic adjustment makes the entire magnetic field adjustment process more intelligent and efficient; by precisely controlling the position and / or direction of the magnetic field providing device, the adaptive coil system can achieve high controllability of the particle beam parameters, which helps to improve the accuracy and treatment effect of radiotherapy and minimize damage to healthy tissue.

[0497] 11 to 17 , FIG17 is a control logic diagram of a magnetic field adjustment device provided in an embodiment of the present application.

[0498] In a specific application scenario, an embodiment of the present application further provides a magnetic field adjustment device, which is applied to a particle accelerator in a radiotherapy system. During the rotation of the treatment gantry, the particle accelerator rotates with the treatment gantry.

[0499] The magnetic field adjustment device is used to adjust the particle deflection magnetic field in the particle accelerator according to the change of the gantry angle, so that the particle beam generated by the particle radiation source meets the preset particle beam conditions under the action of the particle deflection magnetic field; the particle beam conditions are used to indicate the preset range of one or more parameters of the particle beam: energy, beam spot size, and beam spot position;

[0500] Wherein, the magnetic field adjustment device includes a detection component, a control component and one or more execution components;

[0501] The detection component is used to detect magnetic field information of the particle deflection magnetic field; the detection component includes one or more Hall detection units, which are used to detect one or more positions of the particle deflection magnetic field to obtain the magnetic field information;

[0502] The control component is used to calculate motion control information of the magnetic field providing device of the particle accelerator based on the magnetic field information and a preset magnetic field condition, and generate a first control instruction corresponding to each of the execution components based on the motion control information; wherein the preset magnetic field condition is determined according to the particle beam condition; and the motion control information is used to indicate a target displacement of each of the magnetic field providing devices;

[0503] The magnetic field adjustment device includes first to fourth actuators, the first and second actuators being located on a first side of the magnetic field providing device, and the third and fourth actuators being located on a second side of the magnetic field providing device, with the first and second sides of the magnetic field providing device being arranged opposite each other; a first connecting line is obtained by connecting the center of the first actuator and the center of the fourth actuator, and a second connecting line is obtained by connecting the center of the second actuator and the center of the third actuator, and the first connecting line intersects the second connecting line;

[0504] Each of the first to fourth actuators is configured to adjust the position and / or direction of the magnetic field providing device according to its corresponding first control instruction; each actuator comprises a first drive controller 201, a first drive mechanism 202, a first transmission mechanism 203, and a position detection mechanism 204; the first transmission mechanism 203 is fixedly connected to the magnetic field providing device; the first drive mechanism 202 employs a motor; the first transmission mechanism 203 employs a mechanical shaft; and the position detection mechanism 204 employs a potentiometer;

[0505] As shown in Figure 17, two types of closed-loop control are performed for each execution component:

[0506] The first closed-loop control (or large closed-loop control): the detection component detects a change in the magnetic field → the control component calculates (or queries pre-calibrated) motion control information and generates a first control instruction → the first drive controller 201 drives the first drive mechanism 202 to move → the first drive mechanism 202 drives the first transmission mechanism 203 to move, and the position of the first transmission mechanism 203 is adjusted → the position / direction of the magnetic field providing device is adjusted; specifically, the first drive controller 201 is used to drive the first drive mechanism 202 to move according to the first control instruction corresponding to the execution component, so that the first drive mechanism 202 drives the first transmission mechanism 203 to move the target displacement, thereby adjusting the position and / or direction of the magnetic field providing device;

[0507] The second type of closed-loop control (or small closed-loop control): the position detection mechanism 204 detects the real-time displacement → the control component generates a new first control instruction based on the real-time displacement and the target displacement → the first drive controller 201 drives the first drive mechanism 202 to move → the first drive mechanism 202 drives the first transmission mechanism 203 to move, and the position of the first transmission mechanism 203 is adjusted → the position / direction of the magnetic field providing device is adjusted; specifically, the position detection mechanism 204 is used to detect the real-time displacement of the first transmission mechanism 203 in real time and send it to the control component, so that the control component generates a new first control instruction based on the real-time displacement and target displacement of the first transmission mechanism 203 and sends it to the first drive controller 201; the first drive controller 201 is used to drive the first drive mechanism 202 to move according to the new first control instruction, and drive the first transmission mechanism 203 to move through the first drive mechanism 202, so that the real-time displacement of the first transmission mechanism 203 matches the target displacement.

[0508] The real-time displacement and the target displacement may match each other completely, or the absolute value of the difference between the two may be less than a preset value, or the ratio of the absolute value of the difference between the two to the target displacement may be less than a preset ratio.

[0509] As an example, a magnetic field adjustment device employs an adaptive coil system consisting of two Hall effect probes, four actuators, and one control component. The Hall effect probes, located within the particle accelerator, generate a voltage proportional to the measured magnetic field, providing position feedback of the magnetic coils. Each actuator component includes a mechanical shaft, a motor, a motor controller, and a potentiometer. The four mechanical shafts are fixed to the supports of the magnetic coils, enabling precise adjustment of the relative position and orientation of the magnetic coils. The potentiometers determine the position of the mechanical shafts, enabling monitoring and control of the adaptive coil system.

[0510] The control logic of the adaptive coil system is shown in Figure 17. During gantry rotation, the Hall probes detect an anomaly in the particle accelerator's magnetic field (the anomaly detection criteria can be pre-set, such as a mismatch with the set magnetic induction intensity at the current position) and provide feedback to the control system. Based on the current magnetic field information and pre-set magnetic field conditions, the control system calculates the required adjustment for each mechanical axis (e.g., target displacement) and instructs the motor controller to begin driving the motors. The motors move the mechanical axes along a pre-set straight line, moving them closer to or further away from the magnetic field providing device. Potentiometers monitor the movement distance (i.e., real-time displacement) of each mechanical axis in real time and provide feedback to the motor controllers. After multiple cycles of movement and feedback, the motors drive the mechanical axes to the pre-set position, at which point the movement distance reaches the target displacement. Accordingly, the magnetic coils reach their set positions. The Hall probes continue to monitor the magnetic field in the particle accelerator and drive the entire adaptive coil system until the particle deflection magnetic field in the particle accelerator reaches an acceptable range.

[0511] (Computer readable storage medium).

[0512] The embodiment of the present application also provides a computer-readable storage medium, the specific embodiment of which is consistent with the embodiment described in the above method embodiment and the technical effects achieved, and some contents will not be repeated here.

[0513] The computer-readable storage medium stores a computer program, which, when executed by one or more processors, implements the steps of any of the above methods or the functions of any of the above operating devices.

[0514] Computer readable medium can be a computer readable signal medium or a computer readable storage medium. In an embodiment of the present application, a computer readable storage medium can be any tangible medium containing or storing a program, which can be used by an instruction execution system, device or device or used in combination with it. Computer readable storage medium can be, for example, but not limited to, a system, device or device of electricity, magnetism, light, electromagnetic, infrared, or semiconductor, or any combination thereof. More specific examples (non-exhaustive list) of computer readable storage medium include: an electrical connection with one or more wires, a portable disk, a hard disk, a random access memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber, a portable compact disk read-only memory (CD-ROM), an optical storage device, a magnetic storage device, or any suitable combination thereof.

[0515] A computer-readable storage medium may include a data signal propagated in baseband or as part of a carrier wave, carrying readable program code. This propagated data signal may take a variety of forms, including but not limited to electromagnetic signals, optical signals, or any suitable combination thereof. A computer-readable storage medium may also be any computer-readable medium that can transmit, propagate, or transfer a program for use by or in conjunction with an instruction execution system, apparatus, or device. The program code contained on the computer-readable storage medium may be transmitted using any suitable medium, including but not limited to wireless, wired, optical cable, RF, or any suitable combination thereof. The program code used to perform the operations of the present invention may be written in any combination of one or more programming languages, including Java, C++, Python, C#, JavaScript, PHP, Ruby, Swift, Go, Kotlin, and the like. The program code may be executed entirely on the user computing device, partially on the user device, as a standalone software package, partially on the user device and partially on a remote computing device, or entirely on a remote computing device or server. Where a remote computing device is involved, the remote computing device may be connected to the user device through any type of network, including a local area network (LAN) or a wide area network (WAN), or may be connected to an external computing device (e.g., through the Internet using an Internet service provider).

[0516] (Computer program product).

[0517] The embodiments of the present application also provide a computer program product, the specific embodiments of which are consistent with the embodiments described in the above method embodiments and the technical effects achieved, and some contents will not be repeated here.

[0518] The computer program product includes a computer program, and when the computer program is executed by one or more processors, the computer program implements the steps of any of the above methods or implements the functions of any of the above operating devices.

[0519] See Figure 18, which is a structural diagram of a computer program product provided in an embodiment of the present application.

[0520] The computer program product is used to implement the steps of any of the above methods or to implement the functions of any of the above operating devices. The computer program product may be a portable compact disc read-only memory (CD-ROM) and include program code, and may be run on a terminal device, such as a personal computer. However, the computer program product of the present invention is not limited thereto and may be implemented in any combination of one or more computer-readable media.

[0521] This application is explained from the perspectives of purpose of use, effectiveness, progress and novelty. The above description and drawings of this application are only preferred embodiments of this application and are not intended to limit this application. Therefore, all structures, devices, features, etc. that are similar or identical to those of this application, that is, all equivalent replacements or modifications made in accordance with the scope of the patent application of this application, should fall within the scope of protection of the patent application of this application.

Claims

1. A magnetic field adjustment device, applied to a particle accelerator installed on a treatment gantry in a radiotherapy system, wherein the particle accelerator rotates with the treatment gantry during rotation of the treatment gantry; the particle accelerator is a cyclotron accelerator, and the particle accelerator comprises a magnetic field providing device, wherein the magnetic field providing device comprises one or more superconducting coils capable of achieving a superconducting state; The magnetic field adjustment device is used to adjust the particle deflection magnetic field in the particle accelerator according to the change of the treatment gantry angle, so that the particle beam generated by the particle radiation source meets the preset particle beam condition under the action of the particle deflection magnetic field; The particle beam condition is used to indicate a preset range of one or more parameters of the particle beam: energy, beam spot size, and beam spot position.

2. The magnetic field adjustment device according to claim 1, wherein: The magnetic field adjustment device includes a detection component, a control component and one or more execution components; The detection component is installed inside the particle accelerator and is used to detect the magnetic field information of the particle deflection magnetic field; The control component is used to calculate the motion control information of the magnetic field providing device of the particle accelerator according to the magnetic field information and the preset magnetic field condition, and generate the first control instruction corresponding to each of the execution components according to the motion control information; wherein the preset magnetic field condition is determined according to the particle beam condition; Each of the execution components is connected to the control component and the magnetic field providing device, and is used to adjust the position and / or direction of the magnetic field providing device according to the first control instruction corresponding to itself.

3. The magnetic field adjustment device according to claim 2, wherein: The detection component includes one or more Hall detection units, which are used to detect one or more positions of the particle deflection magnetic field to obtain the magnetic field information; and / or, The magnetic field adjustment device includes first to fourth actuators, the first and second actuators are located on the first side of the magnetic field providing device, the third and fourth actuators are located on the second side of the magnetic field providing device, and the first and second sides of the magnetic field providing device are arranged opposite to each other; a first line is obtained by connecting the center of the first actuator and the center of the fourth actuator, and a second line is obtained by connecting the center of the second actuator and the center of the third actuator, and the first line intersects with the second line.

4. The magnetic field adjustment device according to claim 2, wherein: Each of the execution components includes a first drive controller, a first drive mechanism and a first transmission mechanism; The control component is used to calculate the target displacement of each first transmission mechanism according to the motion control information, and generate a first control instruction corresponding to the execution component to which it belongs according to the target displacement of each first transmission mechanism; In each of the execution components, the first transmission mechanism is fixedly connected to the magnetic field providing device, and the first drive controller is used to drive the first drive mechanism to move according to the first control instruction corresponding to the execution component, so that the first drive mechanism drives the first transmission mechanism to move the target, thereby The position and / or direction of the magnetic field providing device is adjusted.

5. The magnetic field adjustment device according to claim 4, wherein: Each of the execution components further includes a position detection mechanism, in each of the execution components: The position detection mechanism is used to detect in real time the real-time displacement of the first transmission mechanism and send it to the control component, so that the control component generates a new first control instruction according to the real-time displacement and target displacement of the first transmission mechanism and sends it to the first drive controller; The first drive controller is used to drive the first drive mechanism to move according to the new first control instruction, and drive the first transmission mechanism to move through the first drive mechanism, so that the real-time displacement of the first transmission mechanism matches the target displacement.

6. The magnetic field adjustment device according to claim 5, wherein: The first driving mechanism uses a motor; and / or, The first transmission mechanism adopts a mechanical shaft; and / or, The position detection mechanism adopts a potentiometer.

7. A particle accelerator, applied to a radiotherapy system, wherein during the rotation of the treatment gantry, the particle accelerator rotates with the treatment gantry; The particle accelerator comprises: A particle radiation source for generating a particle beam; a cavity for accelerating the particle beam therein; A magnetic field providing device, used for providing a particle deflection magnetic field for the cavity; The magnetic field adjustment device according to any one of claims 1 to 6 is used to adjust the particle deflection magnetic field.

8. The particle accelerator according to claim 7, wherein: The particles corresponding to the particle beam are protons or heavy ions.

9. The particle accelerator according to claim 7, wherein: The particle accelerator further comprises: The beam spot size adjusting device is used to adjust the beam spot size of the particle beam.

10. The particle accelerator according to claim 9, wherein: The beam spot size adjustment device includes one or more adjustment components, each of which includes a second drive controller, a second drive mechanism, a second transmission mechanism and a shielding mechanism; In each of the adjustment components, the second transmission mechanism is fixedly connected to the shielding mechanism, and the second drive controller is used to drive the second drive mechanism to move according to the second control instruction corresponding to the adjustment component, so that the second drive mechanism drives the second transmission mechanism to move, thereby adjusting the shielding state of the shielding mechanism.

11. The particle accelerator according to claim 10, wherein: The second driving mechanism uses a motor; and / or, The second transmission mechanism adopts a screw rod; and / or, The shielding mechanism adopts a plurality of shielding plates which are arranged in pairs and symmetrically along the center line.

12. The particle accelerator according to claim 7, wherein: The particle accelerator further comprises: a radio frequency device for providing an accelerating electric field to the cavity; and / or, A vacuum device, used to provide a vacuum environment for the cavity; and / or, A liquid cooling device is used to cool the cavity by using cooling liquid.

13. An arc-shaped radiotherapy device, comprising: The particle accelerator according to any one of claims 7 to 12, used for generating and adjusting a particle beam; A beam delivery system, used for delivering the particle beam; Patient positioning system, used to achieve patient positioning; The treatment frame is used to drive the particle accelerator and the beam distribution system to rotate around the isocenter to achieve particle arc radiotherapy.

14. The arc radiation therapy device according to claim 13, wherein: The beam delivery system comprises a treatment head, wherein the treatment head comprises an active beam scanning treatment head and / or a passive scattering treatment head; and / or, The patient positioning system includes a treatment bed and an imaging system.

15. The arc radiation therapy device according to claim 13, wherein: The arc radiation therapy device also includes: a safety interlocking system for performing safety monitoring on the particle accelerator, the beam delivery system, the patient positioning system and the treatment gantry; and / or, a treatment planning system for generating a treatment plan based on the patient's preoperative medical imaging data; and / or, The control software system is used to verify the treatment plan and record the treatment process data.

16. A method for operating an arc radiation therapy device, for operating the arc radiation therapy device according to any one of claims 13 to 15, the method comprising: Acquire a treatment plan, the treatment plan comprising a plurality of preset angle intervals and a set dose corresponding to each of the preset angle intervals; The treatment gantry is rotated to each of the preset angle intervals respectively to complete the irradiation process of the particle beam corresponding to each of the preset angle intervals, thereby completing the arc radiation therapy process.

17. The method for operating an arc radiation therapy device according to claim 16, wherein: Before rotating the treatment gantry, the method further includes: Adjust the treatment bed to the preset irradiation position; Acquire the patient's intraoperative medical imaging data through the imaging system; Performing image registration on the intraoperative medical imaging data of the patient and the treatment plan to obtain treatment bed adjustment information; The position and angle of the treatment bed are adjusted according to the treatment bed adjustment information.

18. The method for operating an arc radiation therapy device according to claim 17, wherein: After adjusting the position and angle of the treatment couch, the method further includes: reacquiring intraoperative medical imaging data of the patient through the imaging system; Detecting whether the reacquired intraoperative medical imaging data and the treatment plan have been registered; If the registration has been completed, performing the step of rotating the treatment gantry; If the registration is not completed, the treatment couch adjustment information is reacquired to readjust the treatment couch.

19. The method for operating an arc radiation therapy device according to claim 16, wherein: The preset angle interval adopts point values, which are expressed as preset angles. During the arc radiation therapy, the following processing is performed: S1: Rotate the treatment frame to a first preset angle; S2: Extending the treatment head to start the irradiation process of the particle beam; S3: monitoring the irradiation dose of the particle beam at the preset angle, and stopping the irradiation process of the particle beam when the irradiation dose of the particle beam reaches a set dose corresponding to the preset angle; S4: retract the treatment head; S5: Detect whether there is a next preset angle; if so, execute S6; if not, execute S7; S6: Rotate the treatment frame to the next preset angle and execute S2; S7: End of arc radiation therapy process.

20. The method for operating an arc radiation therapy device according to claim 16, wherein: The preset angle interval adopts a range value, and during the arc radiation therapy, the following processing is performed: R1: Rotate the treatment frame to the first preset angle interval; R2: Extend the treatment head and start the irradiation process of the particle beam; R3: monitoring the irradiation dose of the particle beam in the preset angle interval, and when the irradiation dose of the particle beam reaches the set dose corresponding to the preset angle interval, detecting whether there is a next preset angle interval; If it exists, execute R4; if it does not exist, execute R5; R4: Rotate the treatment frame to the next preset angle interval and execute R3; R5: Stop the irradiation process of the particle beam, retract the treatment head, and end the arc radiotherapy process.

21. The method for operating an arc radiation therapy device according to claim 20, wherein: The extended position of the treatment head does not exceed a preset position, and the preset position is determined according to a preset collision constraint condition.

22. An operating device for arc radiation therapy equipment, used to operate the arc radiation therapy equipment according to any one of claims 13 to 15, the operating device comprising a memory and one or more processors, the memory storing a computer program, the one or more processors being configured to implement the following steps when executing the computer program: Acquire a treatment plan, the treatment plan comprising a plurality of preset angle intervals and a set dose corresponding to each of the preset angle intervals; The treatment gantry is rotated to each of the preset angle intervals respectively to complete the irradiation process of the particle beam corresponding to each of the preset angle intervals, thereby completing the arc radiation therapy process.

23. A computer-readable storage medium storing a computer program, wherein the computer program, when executed by one or more processors, implements the steps of the method according to any one of claims 16 to 21 or implements the functions of the operating device according to claim 22.

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