High energy electron accelerator device for flash radiotherapy and boron neutron capture therapy

Abstract

This invention relates to a high-energy electron accelerator device capable of performing flash radiotherapy and boron neutron capture therapy (BNCT), comprising: a high-energy electron accelerator for providing a high-energy, high-power electron beam; an automatic beam duty cycle control system for precisely controlling the beam duty cycle of the accelerator to meet the dual-function requirements of flash radiotherapy and BNCT; at least one flash radiotherapy end for flash radiotherapy, converting the electron beam provided by the high-energy electron accelerator into an X-ray beam or electron beam required for treatment; and at least one BNCT end for boron neutron capture therapy, converting the electron beam provided by the high-energy electron accelerator into an ultrathermal neutron beam required for treatment. Multiple electron accelerators can be drawn from different locations of the high-energy electron accelerator or connected in series according to the energy requirements of the flash radiotherapy end and the BNCT end, achieving the high-energy electron beam requirement of tens of MeV. Depending on the needs of tumor treatment, flash radiotherapy or boron neutron capture therapy can be selected, or flash radiotherapy and BNCT can be performed simultaneously through beam splitting.

Description

Technical Field

[0001] This invention relates to the field of energy spectrometer technology, and more specifically, to a high-energy electron accelerator device capable of performing flash radiotherapy and boron neutron capture therapy. Background Technology

[0002] As the demand for and burden of cancer treatment continues to increase, the main treatment methods for cancer can be divided into surgery, chemotherapy, and radiotherapy. Among these, surgery and chemotherapy are currently the main methods, but they cannot be applied to metastatic malignant tumors, lack precise targeting, have low efficiency, and have significant side effects. Radiotherapy based on radiation (electron, X-ray, gamma ray, proton, etc.) is a local treatment method that directly or indirectly kills cancer cells. It has a wide range of indications and is effective in treating almost 95% of tumor types. It is in a stage of rapid development. Moreover, with the advancement of technology, new radiotherapy technologies continue to emerge, including flash radiotherapy (Flash-RT) and boron neutron capture therapy (BNCT).

[0003] Flash radiotherapy (FRT) is a radiotherapy method that uses ultra-high dose rate X-rays or electron beams (usually ≥100 Gy / s) to deliver the entire radiotherapy dose to the target area within an extremely short time (1–100 ms, meaning the pulse width of the X-ray or electron beam used for treatment is approximately 1 ms to 100 ms). It is currently a hot topic and cutting-edge technology in the field of radiotherapy. BNCT involves injecting X-rays or electron beams containing X-rays or electron beams into the target area within an extremely short time (1–100 ms). 10 A tumor-promoting drug derived from the beta-2 nuclide (with a large thermal neutron capture cross-section of 3837 barns) is administered to the patient via injection or oral administration. After the drug accumulates in the tumor tissue, the tumor site is irradiated with a superthermal neutron beam. The superthermal neutron beam is slowed down into a thermal neutron beam as it passes through normal tissue. 10 The B nuclide captures a thermal neutron and undergoes a fission reaction to produce a nuclear energy of approximately 1 MeV. 7 Li and alpha particles, through 7 Li and alpha particles are used to kill tumor cells. This is due to the production of... 7 Li and alpha particles have an interaction distance of approximately several μm within human tissues, comparable to the scale of a cell (10 μm), making it a targeted radiotherapy method with cellular-level precision. BNCT requires continuous, prolonged irradiation of the tumor region with a hyperthermic neutron beam to achieve the cumulative neutron flux, with irradiation time typically ranging from 30 minutes to 1 hour.

[0004] It is evident that flash therapy and BNCT utilize different particle beams, and their single treatment times also differ significantly. This corresponds to drastically different accelerator operating modes and requirements. Flash therapy requires the accelerator to output short-pulse (small pulse width) high-power particle beams with low duty cycles, while BNCT requires the accelerator to output continuous (very high duty cycle, with continuous waves approximating 100% duty cycle) high-power particle beams. Therefore, currently, no electron accelerator device simultaneously possesses both flash therapy and BNCT capabilities for these two novel and highly efficient radiotherapy methods.

[0005] Different patients or different tumor types may require different radiotherapy methods and treatment approaches. If two devices are needed to simultaneously perform flash radiotherapy and boron neutron capture therapy (BNCT), the construction and maintenance costs of the accelerator device are very high, increasing the overall cost of patient treatment and limiting the application of new radiotherapy technologies. Therefore, to address the current problems and needs, there is an urgent need to develop a high-energy electron accelerator device capable of performing both flash radiotherapy and boron neutron capture therapy. Summary of the Invention

[0006] The technical problem to be solved by this invention is that flash radiotherapy and boron neutron capture therapy cannot be performed on the same device.

[0007] To address the aforementioned technical problems, this invention provides a high-energy electron accelerator device capable of performing flash radiotherapy and boron neutron capture therapy (BNCT), comprising: a high-energy electron accelerator for providing a high-energy electron beam of several MeV to tens of MeV and a high-power electron beam of tens of kW to hundreds of kW; wherein the power of the accelerator device can be adjusted according to the actual treatment needs of the patient receiving flash radiotherapy or BNCT; an automatic beam duty cycle control system for high-precision automatic control of the accelerator's beam duty cycle to meet the dual-function requirement of flash radiotherapy and BNCT; at least one flash radiotherapy end for flash radiotherapy, converting the electron beam provided by the high-energy electron accelerator into an X-ray beam or electron beam required for treatment; typical parameters of the flash radiotherapy X-ray beam or electron beam provided by the flash radiotherapy end are a dose rate of 40-300 Gy / s and a duration of 1-100 ms; at least one BNCT end for boron neutron capture therapy, converting the electron beam provided by the high-energy electron accelerator into a hyperthermal neutron beam required for treatment; the hyperthermal neutron fluence rate provided by the BNCT end is ≥5E8 n / (cm²). 2 .s); where, according to the energy requirements of the flash therapy end and the BNCT end, multiple electron accelerators can be drawn from different positions of the high-energy electron accelerator or connected in series to achieve the high-energy electron beam requirement of tens of MeV.

[0008] According to an embodiment of the present invention, the high-energy electron accelerator may include: an electron gun, an accelerating cavity, and a beam conditioning system, wherein the electron gun is a grid-controlled electron gun, used to generate a low-energy electron beam with energies of tens of keV and to focus the electron beam so that its beam quality, including emittance, meets the requirements; the grid of the grid-controlled electron gun achieves pulse modulation emission of the electron beam by applying a pulse voltage of a certain timing.

[0009] According to an embodiment of the present invention, the accelerating cavity may have a microwave field provided by a microwave power source, and the electron beam emitted by the electron gun is injected into the accelerating cavity and accelerated to the required high energy by the microwave field placed in the accelerating cavity; after being accelerated by the accelerating cavity, the electron beam enters the beam current conditioning system.

[0010] According to an embodiment of the present invention, the accelerating cavity can be a high-frequency accelerating cavity, in which deflecting magnets are arranged at certain intervals in the same circumferential direction, and the electron gun is facing the center of the circle. After the electron beam is injected, it enters the accelerating cavity repeatedly under the action of the microwave field and the deflecting magnets for acceleration. Its trajectory is similar to a petal shape, and it is named a petal accelerator. In this case, the same accelerating cavity is repeatedly used for electron beam acceleration, resulting in high energy utilization efficiency.

[0011] According to an embodiment of the present invention, the accelerating cavity may be a linear accelerating cavity without a deflecting magnet, and the electron beam is accelerated in a linear direction, and the electron beam passes through the accelerating cavity in one go.

[0012] According to an embodiment of the present invention, the beam conditioning system may include an electronic lens group for adjusting parameters of the electron beam, including position, beam spot, and emittance, to ensure that the beam loss is minimized during subsequent transmission.

[0013] According to an embodiment of the present invention, the electron beam provided by the high-energy electron accelerator has an energy of 7MeV-50MeV and a beam power of 10kW-300kW.

[0014] According to an embodiment of the present invention, the automatic beam duty cycle control system can, on the one hand, automatically generate a pulse trigger signal according to the duty cycle requirements of flash therapy and BNCT, and simultaneously send it to the microwave power source and the electron gun (pulse modulator). This synchronously controls the timing of the pulsed electron beam emitted by the electron gun and the pulse width and repetition frequency of the microwave power source, where the duty cycle = pulse width × pulse repetition frequency. This ensures precise synchronization between the electron injection pulse and the microwave pulse, achieving electron beam acceleration. By adjusting the pulse width and frequency of the microwave power source, the duty cycle can be adjusted, achieving a range from an ultra-low duty cycle of 0.01% to a continuous wave of 100%. On the other hand, the amplitude and phase of the microwave field within the high-frequency cavity can be detected in real time using a directional coupler and probes. The results are fed back to the LLRF. After signal processing, the LLRF compares the signal with the reference signal of the microwave power source. In the next pulse or the current pulse, the LLRF system adjusts the output amplitude and phase of the microwave source for real-time compensation, thereby achieving real-time monitoring and adjustment of the microwave field and ensuring stable output.

[0015] According to an embodiment of the present invention, the flash therapy end may include a beam deflection system, a bremsstrahlung X-ray conversion target or an electron beam transmission window, a collimator, and an X-ray shield. The beam deflection system is used to deflect the electron beam to the target according to the needs of flash therapy. The bremsstrahlung X-ray conversion target converts the electron beam provided by the high-energy electron accelerator into an X-ray beam. The collimator collimates the X-ray beam to the distribution required for treatment, thereby limiting the irradiation range to the treatment area. The shield is used to shield X-rays that are not in the treatment direction and are scattered.

[0016] According to an embodiment of the present invention, the BNCT end may include a beam deflection system, a neutron therapy target, a collimator, and a shield. The beam deflection system is used to deflect the electron beam to the target according to the BNCT treatment requirements. The neutron therapy target directly converts the electron beam into a neutron beam through bremsstrahlung radiation and photonuclear reactions, and slows down and shapes the neutron beam into the hyperthermal neutron beam required for BNCT treatment. The collimator is used to collimate the hyperthermal neutron beam to the distribution required for the treatment area, thereby limiting the irradiation range to the treatment area. The shield is used to shield neutrons, X-rays, and gamma rays from non-treatment directions and scattered radiation.

[0017] Among them, the flash therapy end and the BNCT end, according to the target point and power requirements of the treatment needs, use the electron beam scanning function or the beam expansion function of the deflection system to expand or scan the electron beam, disperse the high-power electron beam to the target surface, thereby improving the conversion target's tolerance to the electron beam power.

[0018] Compared with the prior art, the technical solution provided by the embodiments of the present invention can achieve at least the following beneficial effects:

[0019] The high-energy electron accelerator device of the present invention, capable of performing flash radiotherapy and boron neutron capture therapy, achieves two working modes—low duty cycle high pulse power output and continuous wave high average power output—through an automatic beam duty cycle control system, based on the beam requirements of flash radiotherapy and boron neutron capture therapy. It can be paired with different treatment targets to meet the needs of both flash radiotherapy and boron neutron capture therapy. Depending on the actual needs of tumor treatment, flash radiotherapy or boron neutron capture therapy can be selected, or flash radiotherapy and boron neutron capture therapy can be performed simultaneously through beam splitting.

[0020] This invention relates to a high-energy electron accelerator device capable of performing both flash radiotherapy and boron neutron capture therapy. The high-energy electron accelerator can achieve high power ranging from tens to hundreds of kilowatts, with an adjustable beam duty cycle, a compact structure, and controllable cost. Through a control system, it can achieve two distinct operating modes: short-pulse high power and continuous high average power, simultaneously meeting the needs of both flash radiotherapy and boron neutron capture therapy (BNCT). This realizes the dual-purpose use of a high-energy electron accelerator for radiotherapy, expands the treatment methods for radiotherapy, improves the technical level of tumor treatment, and reduces the overall cost of flash radiotherapy and BNCT. Attached Figure Description

[0021] To more clearly illustrate the technical solutions of the embodiments of the present invention, the accompanying drawings of the embodiments will be briefly described below. Obviously, the drawings described below only relate to some embodiments of the present invention and are not intended to limit the present invention.

[0022] Figure 1 This is a schematic diagram of a high-energy electron accelerator device capable of performing flash radiotherapy and boron neutron capture therapy according to an embodiment of the present invention;

[0023] Figure 2 This is a schematic diagram illustrating an automatic control system for the accelerator beam duty cycle according to an embodiment of the present invention. Detailed Implementation

[0024] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of the present invention. Based on the described embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0025] Unless otherwise defined, the technical or scientific terms used herein shall have the ordinary meaning as understood by one of ordinary skill in the art to which this invention pertains. The terms “first,” “second,” and similar terms used in the specification and claims of this patent application do not indicate any order, quantity, or importance, but are merely used to distinguish different components. Similarly, the terms “an” or “a” and similar terms do not indicate a limitation of quantity, but rather indicate the presence of at least one.

[0026] Figure 1 This is a schematic diagram of a high-energy electron accelerator device capable of performing flash radiotherapy and boron neutron capture therapy according to an embodiment of the present invention.

[0027] like Figure 1 As shown, the high-energy electron accelerator device capable of performing flash radiotherapy and boron neutron capture therapy includes: a high-energy electron accelerator, at least one flash therapy end, at least one BNCT end, and an automatic beam duty cycle control system.

[0028] High-energy electron accelerators are used to provide high-energy electron beams of several MeV to tens of MeV and high-power electron beams of tens of kW to hundreds of kW; the power of the accelerator device can be adjusted according to the actual treatment needs of the patient receiving flash therapy or BNCT.

[0029] The beam duty cycle automatic control system is used to perform high-precision automatic control of the accelerator's beam duty cycle to meet the dual-function requirements of flash therapy and BNCT.

[0030] The flash therapy end is used for flash radiotherapy, converting the electron beam provided by the high-energy electron accelerator into the X-ray beam or electron beam required for treatment; the typical parameters of the flash therapy X-ray beam or electron beam provided by the flash therapy end are a dose rate of 40-300 Gy / s and a duration of 1-100 ms.

[0031] The BNCT end is used for boron neutron capture therapy, converting the electron beam provided by the high-energy electron accelerator into the hyperthermal neutron beam required for treatment; the hyperthermal neutron fluence rate provided by the BNCT end is ≥5E8 n / (cm²). 2 .s).

[0032] Among them, multiple electron accelerators can be drawn from different positions of the high-energy electron accelerator or connected in series according to the energy requirements of the flash therapy end and the BNCT end, so as to achieve the high-energy electron beam requirement of tens of MeV.

[0033] The high-energy electron accelerator device of the present invention, capable of performing flash radiotherapy and boron neutron capture therapy, achieves two working modes—low duty cycle high pulse power output and continuous wave high average power output—through an automatic beam duty cycle control system, based on the beam requirements of flash radiotherapy and boron neutron capture therapy. It can be paired with different treatment targets to meet the needs of both flash radiotherapy and boron neutron capture therapy. Depending on the actual needs of tumor treatment, flash radiotherapy or boron neutron capture therapy can be selected, or flash radiotherapy and boron neutron capture therapy can be performed simultaneously through beam splitting.

[0034] According to one or more embodiments of the present invention, the high-energy electron accelerator includes: an electron gun 11, an accelerating cavity 12, and a beam conditioning system 14. The electron gun 11 is a grid-controlled electron gun 11, used to generate a low-energy electron beam with energies of tens of keV and to focus the electron beam to ensure that its beam quality, including emittance, meets requirements. The grid of the grid-controlled electron gun 11 achieves pulse-modulated emission of the electron beam by applying pulse voltages of a specific timing.

[0035] According to one or more embodiments of the present invention, the acceleration cavity 12 has a microwave field provided by a microwave power source, and the electron beam emitted by the electron gun 11 is injected into the acceleration cavity 12 and accelerated to the required high energy by the microwave field placed in the acceleration cavity 12; after being accelerated by the acceleration cavity 12, the electron beam enters the beam current conditioning system 14.

[0036] According to one or more embodiments of the present invention, the acceleration cavity 12 is a high-frequency acceleration cavity 12, in which deflecting magnets 13 are arranged at certain intervals in the same circumferential direction, and the electron gun 11 is directly facing the center of the circle. After the electron beam is injected, it enters the acceleration cavity 12 repeatedly under the action of the microwave field and the deflecting magnets 13 for acceleration. Its trajectory is similar to a petal shape, and it is named a petal accelerator. The same acceleration cavity 12 is repeatedly used for electron beam acceleration, and the energy utilization efficiency is high.

[0037] According to one or more embodiments of the present invention, the acceleration cavity 12 is a linear acceleration cavity 12 without a deflection magnet 13, the electron beam is accelerated in a linear direction, and the electron beam passes through the acceleration cavity 12 in one go.

[0038] According to one or more embodiments of the present invention, the beam conditioning system 14 includes an electronic lens group for adjusting parameters of the electron beam, including position, beam spot, and emittance, to ensure that the beam loss is minimized during subsequent transmission.

[0039] According to one or more embodiments of the present invention, the electron beam provided by the high-energy electron accelerator has an energy of 7MeV-50MeV and a beam power of 10kW-300kW.

[0040] Figure 2This is a schematic diagram illustrating an automatic control system for the accelerator beam duty cycle according to an embodiment of the present invention.

[0041] like Figure 2 As shown, the automatic beam duty cycle control system automatically generates pulse trigger signals based on the duty cycle requirements of flash therapy and BNCT, and simultaneously sends them to the microwave power source and electron gun 11 (pulse modulator). This synchronously controls the timing of the pulsed electron beam emitted by the electron gun 11 and the pulse width and repetition frequency of the microwave power source. The duty cycle is calculated as pulse width × pulse repetition frequency, ensuring precise synchronization between the electron injection pulse and the microwave pulse, thus accelerating the electron beam. The duty cycle is adjusted by regulating the pulse width and frequency of the microwave power source, achieving a range from an ultra-low duty cycle of 0.01% to a continuous wave of 100%. Furthermore, the system uses directional couplers and probes to detect the amplitude and phase of the microwave field within the high-frequency cavity in real time. The results are fed back to the LLRF. After signal processing, the LLRF compares the signal with the reference signal from the microwave power source. Within the next pulse or the current pulse, the LLRF system adjusts the output amplitude and phase of the microwave source for real-time compensation, thereby achieving real-time monitoring and regulation of the microwave field and ensuring stable output.

[0042] According to one or more embodiments of the present invention, the flash therapy end includes a beam deflection system 2, a bremsstrahlung X-ray conversion target 3 or an electron beam transmission window, a collimator, and an X-ray shield. The beam deflection system 2 is used to deflect the electron beam to the target according to the needs of flash therapy. The bremsstrahlung X-ray conversion target 3 converts the electron beam provided by the high-energy electron accelerator into an X-ray beam. The collimator collimates the X-ray beam to the distribution required for treatment, thereby limiting the irradiation range to the treatment area. The shield is used to shield X-rays that are not in the treatment direction and are scattered.

[0043] According to one or more embodiments of the present invention, the BNCT end includes a beam deflection system 2, a neutron therapy target 4, a collimator, and a shield. The beam deflection system 2 is used to deflect the electron beam to the target according to the BNCT treatment requirements. The neutron therapy target 4 directly converts the electron beam into a neutron beam through bremsstrahlung radiation and photonuclear reactions, and slows down and shapes the neutron beam into the hyperthermal neutron beam required for BNCT treatment. The collimator is used to collimate the hyperthermal neutron beam to the distribution required for the treatment area, thereby limiting the irradiation range to the treatment area. The shield is used to shield neutrons, X-rays, and gamma rays from non-treatment directions and scattered radiation. The flash therapy end and the BNCT end, according to the target point and power requirements of the treatment, utilize the electron beam scanning or beam expanding function of the deflection system to expand or scan the electron beam, dispersing the high-power electron beam onto the target surface, thereby improving the conversion target's tolerance to the electron beam's power.

[0044] This invention relates to a high-energy electron accelerator device capable of performing both flash radiotherapy and boron neutron capture therapy. The high-energy electron accelerator can achieve high power ranging from tens to hundreds of kilowatts, with an adjustable beam duty cycle, a compact structure, and controllable cost. Through a control system, it can achieve two distinct operating modes: short-pulse high power and continuous high average power, simultaneously meeting the needs of both flash radiotherapy and boron neutron capture therapy (BNCT). This realizes the dual-purpose use of a high-energy electron accelerator for radiotherapy, expands the treatment methods for radiotherapy, improves the technical level of tumor treatment, and reduces the overall cost of flash radiotherapy and BNCT.

[0045] According to one or more embodiments of the present invention, the high-energy electron accelerator is typically a high-energy petal accelerator, used to generate high-power electron beams with a maximum energy of 10 MeV. The maximum power of the electron beam can reach over 250 kW. The treatment control system has the capability to perform precise closed-loop control of the current intensity and pulse pattern of each electron beam according to the treatment requirements, thereby achieving precise adjustment of the current intensity and beam timing structure required for flash therapy and BNCT.

[0046] In use, depending on the needs of tumor treatment, if flash therapy is required, the electron beam of the petal accelerator is deflected to the flash therapy target according to the dose plan requirements of the treatment. It is then converted into an X-ray beam by the bremsstrahlung conversion target. The focal spot is about a few millimeters, typically 1-5 millimeters. The maximum dose rate at a distance of 1m from the target tip can reach more than 200 Gy / s. Within 1-100ms, the dose can be delivered to the target area to be treated by collimators (such as multi-leaf gratings MLC), thereby realizing flash radiotherapy of the tumor.

[0047] To meet the needs of tumor treatment, if boron neutron capture therapy is required, the electron beam from the petal accelerator is deflected to the neutron target system at the BNCT end. The BNCT target then converts the electron beam into a hyperthermal neutron beam required for treatment, with parameters meeting the IAEA-recommended neutron parameter requirements, typically such as a neutron beam spot diameter of 10 cm, neutron energy of 0.5 eV-10 keV, and a hyperthermal neutron fluence rate ≥5E8 n / (cm²). 2 (.s), thermal neutron / hyperthermal neutron flux ratio ≤0.05, fast neutron dose per unit hyperthermal neutron flux ≤7E-13 Gy / cm 2 The gamma-ray dose per unit superthermal neutron flux is ≤2E-13 Gy / cm. 2 wait.

[0048] The above description is merely an exemplary embodiment of the present invention and is not intended to limit the scope of protection of the present invention, which is determined by the appended claims.

Claims

1. A high-energy electron accelerator device capable of performing flash radiotherapy and boron neutron capture therapy, wherein, include: High-energy electron accelerators are used to provide high-energy electron beams of several MeV to tens of MeV and high-power electron beams of tens of kW to hundreds of kW; the power of the accelerator device can be adjusted according to the actual treatment needs of the patient receiving flash therapy or BNCT. The beam duty cycle automatic control system is used to perform high-precision automatic control of the accelerator's beam duty cycle to meet the dual-function requirements of flash therapy and BNCT. At least one flash therapy end, said flash therapy end being used for flash radiotherapy, converting the electron beam provided by the high-energy electron accelerator into an X-ray beam or electron beam required for treatment; At least one BNCT end, the BNCT end being used for boron neutron capture therapy, converting an electron beam provided by a high-energy electron accelerator into a superthermal neutron beam required for therapy; Depending on the energy requirements of the flash therapy end and the BNCT end, multiple electron accelerators can be drawn from different positions of the high-energy electron accelerator or connected in series to achieve the high-energy electron beam requirement of tens of MeV.

2. The high-energy electron accelerator device for flash radiotherapy and boron neutron capture therapy as described in claim 1, wherein, The high-energy electron accelerator includes: an electron gun, an acceleration cavity, and a beam modulation system. Among them, the electron gun is a grid-controlled electron gun, which is used to generate a low-energy electron beam with tens of keV and focus the electron beam to ensure that the beam quality, including emittance, meets the requirements; the grid of the grid-controlled electron gun achieves pulse modulation emission of the electron beam by applying a pulse voltage with a certain timing.

3. The high-energy electron accelerator device for flash radiotherapy and boron neutron capture therapy as described in claim 2, wherein, The acceleration cavity contains a microwave field provided by a microwave power source. The electron beam emitted by the electron gun is injected into the acceleration cavity and accelerated to the required high energy by the microwave field inside the acceleration cavity. After being accelerated by the acceleration cavity, the electron beam enters the beam current adjustment system.

4. The high-energy electron accelerator device for flash radiotherapy and boron neutron capture therapy as described in claim 2, wherein, The accelerating cavity is a high-frequency accelerating cavity. It uses deflecting magnets arranged at certain intervals in the same circumferential direction. The electron gun is directly facing the center of the circle. After the electron beam is injected, it enters the accelerating cavity repeatedly under the action of the microwave field and the deflecting magnets. Its trajectory is similar to a petal shape, hence the name petal accelerator. The same accelerating cavity is repeatedly used for electron beam acceleration, resulting in high energy utilization efficiency.

5. The high-energy electron accelerator device for flash radiotherapy and boron neutron capture therapy as described in claim 2, wherein, The acceleration cavity is a linear acceleration cavity without deflection magnets. The electron beam is accelerated in a straight line and passes through the acceleration cavity in one go.

6. The high-energy electron accelerator device for flash radiotherapy and boron neutron capture therapy as described in claim 2, wherein, The beam conditioning system includes an electronic lens group for adjusting parameters of the electron beam, including position, beam spot, and emissivity, to ensure that beam loss is minimized during subsequent transmission.

7. The high-energy electron accelerator device for flash radiotherapy and boron neutron capture therapy as described in claim 1, wherein, The electron beams provided by the high-energy electron accelerator have energies of 7MeV-50MeV and beam currents of 10kW-300kW.

8. The high-energy electron accelerator device for flash radiotherapy and boron neutron capture therapy as described in claim 2, wherein, The automatic beam duty cycle control system automatically generates pulse trigger signals based on the duty cycle requirements of flash therapy and BNCT, and simultaneously sends them to the microwave power source and electron gun. It synchronously controls the timing of the pulsed electron beam emitted by the electron gun and the pulse width and repetition frequency of the microwave power source. The duty cycle is calculated as pulse width × pulse repetition frequency, ensuring precise synchronization between the electron injection pulse and the microwave pulse for electron beam acceleration. The duty cycle is adjusted by regulating the pulse width and frequency of the microwave power source, achieving a range from an ultra-low duty cycle of 0.01% to a continuous wave of 100%. Furthermore, the system uses directional couplers and probes to detect the amplitude and phase of the microwave field within the high-frequency cavity in real time. The results are fed back to the LLRF (Limited-Low Frequency Reduction Regulator). After signal processing, the LLRF compares the signal with the reference signal from the microwave power source. Within the next pulse or the current pulse, the LLRF system adjusts the output amplitude and phase of the microwave source for real-time compensation, thereby achieving real-time monitoring and adjustment of the microwave field and ensuring stable output.

9. The high-energy electron accelerator device for flash radiotherapy and boron neutron capture therapy as described in claim 1, wherein, The flash therapy unit includes a beam deflection system, a bremsstrahlung X-ray conversion target or an electron beam transmission window, a collimator, and an X-ray shield. The beam deflection system is used to deflect the electron beam to the target according to the needs of flash therapy. The bremsstrahlung X-ray conversion target converts the electron beam provided by the high-energy electron accelerator into an X-ray beam. The collimator collimates the X-ray beam to the distribution required for treatment, thereby limiting the irradiation range to the treatment area. The shield is used to block X-rays from non-treatment directions and scattered X-rays.

10. The high-energy electron accelerator device for flash radiotherapy and boron neutron capture therapy as described in claim 9, wherein, The BNCT unit includes a beam deflection system, a neutron therapy target, a collimator, and a shield. The beam deflection system deflects the electron beam to target the target according to the BNCT treatment requirements. The neutron therapy target directly converts the electron beam into a neutron beam through bremsstrahlung radiation and photonuclear reactions, and then slows down and shapes the neutron beam into the hyperthermal neutron beam required for BNCT treatment. The collimator collimates the hyperthermal neutron beam to the distribution required for the treatment area, thereby limiting the irradiation range to the treatment area. The shield blocks neutrons, X-rays, and gamma rays from non-treatment directions and scattered radiation. The flash therapy end and BNCT end, according to the target point and power requirements of the treatment, use the electron beam scanning function or the beam expansion function of the deflection system to expand or scan the electron beam, disperse the high-power electron beam to the target surface, thereby improving the conversion target's tolerance to the electron beam power.

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