WO2019242011A1 - 同步加速器控制方法、装置、设备及存储介质 - Google Patents

同步加速器控制方法、装置、设备及存储介质 Download PDF

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WO2019242011A1
WO2019242011A1 PCT/CN2018/092448 CN2018092448W WO2019242011A1 WO 2019242011 A1 WO2019242011 A1 WO 2019242011A1 CN 2018092448 W CN2018092448 W CN 2018092448W WO 2019242011 A1 WO2019242011 A1 WO 2019242011A1
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voltage
preset
radiation head
scanning radiation
synchrotron
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English (en)
French (fr)
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郑志鸿
刘铮铮
李凯若
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Newrt Medical Systems (wuxi) Co Ltd
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Newrt Medical Systems (wuxi) Co Ltd
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Priority to CN201880001046.1A priority Critical patent/CN108883304B/zh
Priority to PCT/CN2018/092448 priority patent/WO2019242011A1/zh
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/103—Treatment planning systems
    • A61N5/1031—Treatment planning systems using a specific method of dose optimization
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N5/1048—Monitoring, verifying, controlling systems and methods
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
    • A61N2005/1087—Ions; Protons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
    • A61N2005/1092—Details

Definitions

  • the present disclosure relates to the field of synchrotron technology, for example, to a synchrotron control method, device, device, and storage medium.
  • Medical synchrotrons usually use slow extraction and pencil beam scanning methods to output 70-230 megaelectron volt (MeV) proton beams for radiotherapy of tumors.
  • the position of each beam spot and the received dose are usually measured by scanning the double ionization chamber in the radiation head. If the dose of the current beam spot reaches a preset dose, the scanning radiation head moves to the next beam spot to be irradiated. The time for the scanning radiation head to shift from the current beam spot position to the next beam spot position to be irradiated is about 1 ms. During this time interval, the dose output by the scanning radiation head is called an unplanned dose. In order to improve the accuracy of radiotherapy dose control, it is necessary to reduce the influence of the unplanned dose on the radiotherapy effect as much as possible.
  • the embodiments of the present application provide a synchrotron control method, device, device, and storage medium to solve the problem that the unplanned dose output by the synchrotron's scanning radiation head during the movement between different beam spots is high.
  • An embodiment of the present application provides a synchrotron control method, including:
  • the synchrotron When the scanning radiation head satisfies a preset irradiation condition, the synchrotron is restored to a working state;
  • the synchrotron includes the electrostatic cutting plate configured to deflect a proton beam, the lateral high-frequency excitation electrode configured to excite the proton beam, and the proton beam output to a beam.
  • the scanning radiation head where the spot is located.
  • reducing the voltage of the electrostatic cutting plate and the voltage of the lateral high-frequency excitation electrode so that the intensity of the proton beam output from the scanning radiation head is less than or equal to a preset intensity threshold includes:
  • the preset stop condition includes at least one of the following:
  • the dose from the scanning radiation head to the position of the first beam spot reaches a preset dose
  • the position of the first beam spot moves outside a preset position range.
  • the voltage of the electrostatic cutting plate and the voltage of the lateral high-frequency excitation electrode are reduced, so that the output of the scanning radiation head is Proton beam intensity is less than or equal to a preset intensity threshold, including:
  • the voltage of the electrostatic cutting plate and the voltage of the lateral high-frequency excitation electrode are reduced within a preset voltage reduction time, so that The intensity of the proton beam output from the scanning radiation head is less than or equal to a preset intensity threshold.
  • the voltage of the electrostatic cutting plate and the voltage of the lateral high-frequency excitation electrode are reduced, so that the proton beam output by the scanning radiation head
  • the flow intensity is less than or equal to a preset intensity threshold, including at least one of the following:
  • the current position of the scanning beam head is kept unchanged, and the electrostatic cutting is reduced within a preset voltage reduction time.
  • the voltage of the plate and the voltage of the lateral high-frequency excitation electrode make the intensity of the proton beam output from the scanning radiation head less than or equal to the preset intensity threshold.
  • the synchrotron is restored to an operating state, including at least one of the following:
  • the voltage of the electrostatic cutting board is restored to the working voltage of the electrostatic cutting board within a preset boosting time, and the lateral high-frequency excitation is restored.
  • the voltage of the electrode to the working voltage of the lateral high-frequency excitation electrode, so that the intensity of the proton beam output from the scanning radiation head reaches the working intensity;
  • the scanning radiation head to the first beam spot When the dose of the scanning radiation head to the first beam spot is less than a preset dose, and the position of the first beam spot moves to a preset position range, within the preset boost time To restore the voltage of the electrostatic cutting board to the working voltage of the electrostatic cutting board, and restore the voltage of the lateral high-frequency excitation electrode to the working voltage of the lateral high-frequency excitation electrode, so that the scanning radiation head outputs The proton beam intensity reached the working intensity.
  • the value of the first preset voltage ranges from 50% to 80% of the working voltage of the electrostatic cutting board.
  • the value of the first preset voltage ranges from 60% to 75% of the working voltage of the electrostatic cutting board.
  • the preset voltage reduction time is less than 70us.
  • An embodiment of the present application further provides a synchrotron control device, including:
  • the beam stopping module is set to reduce the voltage of the electrostatic cutting board and the voltage of the lateral high-frequency excitation electrode when the irradiation of the first beam spot by the synchrotron's scanning radiation head meets a preset stop condition, so that the protons output by the scanning radiation head
  • the beam intensity is less than or equal to a preset intensity threshold
  • the synchrotron includes the electrostatic cutting plate configured to deflect a proton beam, the lateral high-frequency excitation electrode configured to excite the proton beam, and a proton beam output to a beam spot.
  • the scanning radiation head at the location.
  • An embodiment of the present application further provides a device, where the device includes:
  • One or more processors are One or more processors;
  • a storage device configured to store one or more programs
  • the one or more processors When the one or more programs are executed by the one or more processors, the one or more processors enable the synchronization accelerator control method described above.
  • An embodiment of the present application further provides a storage medium containing computer-executable instructions, and the computer-executable instructions are used to execute the foregoing synchrotron control method when executed by a computer processor.
  • the synchrotron control method provided in the embodiment of the present application reduces the beam intensity by reducing the voltage of the electrostatic cutting plate and the voltage of the lateral high-frequency excitation electrode, so that the beam intensity is rapidly reduced to a preset intensity threshold, and then when the scanning radiation head is in When transferring between two beam spots, the dose received by the patient is kept at a very low value.
  • this embodiment can increase the dose rate of radiotherapy, which can reduce the Radiotherapy time can reduce the unplanned dose, which can significantly improve the effect of radiotherapy.
  • FIG. 1 is a schematic diagram of a proton beam phase space provided by an embodiment of the present application.
  • FIG. 2a is a flowchart of a synchronization accelerator control method according to the first embodiment of the present application
  • FIG. 2b is a flowchart of another synchronous accelerator control method according to the first embodiment of the present application.
  • FIG. 3 is a flowchart of a synchrotron control method provided in Embodiment 2 of the present application.
  • FIG. 4 is a structural block diagram of a synchrotron control device provided in Embodiment 3 of the present application.
  • FIG. 5 is a structural block diagram of a synchrotron device provided in Embodiment 4 of the present application.
  • the synchrotron adjusts the operating point to a preset 1/3 integer resonance operating point through a four-stage magnet, and turns on the six-stage magnet to form the phase space shown in Figure 1.
  • Triangularly distributed first proton beam Under the excitation of the high-frequency excitation electrode, the protons slowly escape from the three corners of the triangle, and the second proton beam gradually approaches the electrostatic cutting plate and is extracted.
  • the extracted proton beam is transported to the scanning radiation head by the proton transport system, and then output by the scanning radiation head to the current beam spot (that is, the first beam spot).
  • the position of the beam spot and the dose received by the beam spot can be measured in real time through the dual ionization chamber in the scanning radiation head to determine whether the dose of the first beam spot has reached the preset dose and whether the scanning radiation head needs to be moved To the position of the next beam spot (ie, the second beam spot) to be irradiated.
  • the transfer time of the scanning radiation head between the two beam spots is about 1 ms. During this time interval, the dose output by the scanning radiation head is called an unplanned dose.
  • the unplanned dose should be less than 10% of the total planned dose. Therefore, for continuous beam emitting radiotherapy methods, the impact of unplanned doses on radiotherapy is usually reduced by reducing the dose rate of radiation therapy and optimizing the statistical method of dose.
  • these solutions can only reduce the impact of unscheduled doses on radiotherapy effects to a certain extent, and reducing the dose rate of radiation therapy also means prolonging the duration of radiation therapy.
  • this embodiment proposes a synchrotron control method, device, device, and storage medium. The synchrotron control method is described below.
  • FIG. 2a is a flowchart of a synchronization accelerator control method provided in Embodiment 1 of the present application.
  • the technical solution of this embodiment is applicable to the case of reducing the unplanned dose of radiation therapy.
  • This embodiment is described by taking proton radiotherapy based on a synchrotron as an example.
  • the method may be executed by a synchrotron control device provided in an embodiment of the present application.
  • the device may be implemented in at least one of the following ways: software and hardware, and the device is configured to be applied in a processor.
  • the method includes the following steps:
  • the synchrotron includes the electrostatic cutting plate configured to deflect a proton beam, the lateral high-frequency excitation electrode configured to excite the proton beam, and the proton beam output to a beam.
  • the scanning radiation head where the spot is located.
  • FIG. 2b is a flowchart of another synchrotron control method provided in Embodiment 1 of the present application. As shown in FIG. 2b, the method includes: S101.
  • the voltage of the electrostatic cutting plate and the voltage of the lateral high-frequency excitation electrode are reduced within a preset voltage reduction time, so that the intensity of the proton beam output from the scanning radiation head is less than or equal to a preset intensity threshold.
  • a tumor is usually divided into a plurality of energy layers perpendicular to the beam irradiation direction, and a plurality of beam spot positions of each energy layer and a preset dose of each beam spot are determined.
  • the synchrotron controls the scanning radiation head to sequentially irradiate each beam spot position in a preset order until the dose of the beam spot reaches the preset dose. That is, the preset stopping condition in this embodiment may be a preset dose.
  • the synchrotron excites the proton beam in the acceleration cavity through the transverse high-frequency excitation electrode to disturb it. After the transverse high-frequency excitation electrode stops exciting the proton beam in the synchrotron, no proton beam will be caused by the disturbance. The proton beams that have reached the outside of the stable region, but remain in the synchrotron outside the stable region, will still be extracted. In other words, the proton beam is still extracted during the process of reducing the voltage of the lateral high-frequency excitation electrode, until all the proton beams outside the stable region in the accelerator are extracted. Therefore, it takes a long time to reduce the beam intensity only by reducing the voltage of the lateral high-frequency excitation electrode, which is usually several hundred microseconds. Although the unscheduled dose output by the synchrotron during this process is less than the unscheduled dose of continuous beam radiation technology, this unscheduled dose is still a high-dose value that cannot be ignored, especially for radiation treatment using large dose rates Radiotherapy plan.
  • the proton beam reaching the preset energy is extracted by the proton deflection device.
  • the electrostatic cutting plate is the first step in deflecting a proton beam in a proton deflector.
  • the proton beam must be deflected out of the synchrotron by first passing through the deflection electric field of the electrostatic cutting plate, deviating from the original trajectory under the action of the deflection electric field, and then being led out of the accelerator through other parts of the proton deflector.
  • this embodiment reduces or removes the deflection electric field of the electrostatic cutting plate by reducing the voltage of the electrostatic cutting plate, so that the deflection electric field of the electrostatic cutting plate cannot shift the proton beam to a preset extraction trajectory.
  • the proton beam carrying the preset energy will not be able to deflect to the preset extraction trajectory because the deflection electric field is weak, and thus cannot be extracted by other parts of the proton deflection device, or the number of protons extracted is very small.
  • the proton beam carrying the preset energy will not be disturbed and deflected because it does not have a lateral excitation source and a deflection electric field, and remains in the acceleration cavity.
  • the value range of the first preset voltage is usually within 50% -80% of the working voltage of the electrostatic cutting board.
  • the value range of the first preset voltage is 60% -75% of the working voltage of the electrostatic cutting board.
  • the minimum voltage value of the electrostatic cutting plate required for the first deflection when the proton beam is extracted can be obtained first, and then the first preset voltage value is set to be less than the minimum voltage value.
  • the lateral high-frequency excitation electrode in order to prolong the service life of the synchrotron and accelerate the synchrotron to restore the working voltage of the lateral high-frequency excitation electrode, the lateral high-frequency excitation electrode will not be completely powered off, and the voltage of the lateral high-frequency excitation electrode will not be completely off. The proton beam in the acceleration cavity cannot be effectively excited.
  • the scanning radiation head of the synchrotron can be depressurized on the electrostatic cutting board.
  • the beam emission is stopped or the beam is emitted at a very low dose rate within a time period up to the first preset voltage, thereby greatly reducing the time during which the beam intensity output by the synchrotron decreases to less than or equal to the preset intensity threshold.
  • the synchrotron can keep the scanning radiation head at the first beam spot position, and reduce the voltage of the electrostatic cutting board to the first preset voltage within a preset step-down time, and set the lateral high frequency
  • the voltage of the excitation electrode is reduced to a second preset voltage.
  • the scanning radiation head can be moved to the position of the second beam spot, and during the movement, the voltage of the electrostatic cutting plate is reduced to the first preset voltage, and the horizontal height is increased.
  • the voltage of the frequency excitation electrode is reduced to a second preset voltage. No matter which voltage reduction method is used, when the scanning radiation head is moved to the second beam spot position, the synchrotron is controlled to return to a preset working state.
  • the synchrotron radiation head When the synchrotron radiation head is located at the beam spot position to be irradiated, the synchrotron returns to the preset working state and outputs the beam current to the position of the first beam spot until the dose detected by the ionization chamber reaches the preset dose until. At this time, the irradiation of the first radiation spot by the scanning radiation head meets the preset stop condition, then the working voltage of the electrostatic cutting board is reduced to the first preset voltage, and the voltage of the lateral high-frequency excitation electrode is reduced to the second preset voltage, in that order. By analogy, until the dose of the last beam spot reaches the preset dose.
  • the preset irradiation conditions in this embodiment are: the ionization chamber detects that the scanning radiation head moves to the beam spot position to be irradiated.
  • the percentage of unplanned dose to the total dose of the entire radiotherapy plan is determined by the scanning time of a single layer.
  • the scanning time of a single layer is 1s
  • the number of scanning points is 200
  • the radiation head is scanned
  • the transfer time between the two beam spots is 1 ms
  • the scanning time of a single layer is 1s and the number of scanning points is 200
  • the time taken for the voltage of the electrostatic cutting board to decrease to 70% of the working voltage is 50us
  • the transfer time of the scanning radiation head between the two beam spots is 1ms.
  • This embodiment can greatly reduce the percentage of the unplanned dose to the total planned dose, so that the dose rate of radiation therapy can be increased, the time of single-layer scanning can be reduced, and then the total time of each radiation therapy can be reduced, and the difficulty of treatment placement can be reduced, and Reduce the fear of patients during radiation therapy.
  • this embodiment can increase the dose rate of radiotherapy. This can reduce the time of radiotherapy and reduce the unplanned dose, which can significantly improve the effect of radiotherapy.
  • FIG. 3 is a flowchart of a synchrotron control method provided in Embodiment 2 of the present application.
  • the embodiment of the present application introduces real-time position detection on the basis of the foregoing embodiments, that is, discloses a synchronous accelerator control method combined with real-time position detection. As shown in Figure 3, the method includes:
  • the position of the first beam spot and the dose received by the first beam spot are detected in real time.
  • the real-time position detection device detects in real time whether the position of the first beam spot is within a preset range, and detects whether the dose received by the first beam spot has reached the preset dose through the ionization chamber.
  • the real-time position detection device may be respiratory gating, cone beam computed tomography (CBCT), or other devices capable of detecting changes in tumor position in real time, which is not limited in this embodiment.
  • CBCT cone beam computed tomography
  • the position of the first beam spot moves outside the preset position range, that is, if the position deviation between the position of the first beam spot and the preset position of the beam spot is greater than the preset position deviation, reduce the The voltage to the first preset voltage reduces the voltage of the lateral high-frequency excitation electrode to the second preset voltage, so that the beam intensity is less than or equal to the preset intensity threshold.
  • the preset intensity threshold is 0, the scanning radiation head stops emitting beams.
  • the synchrotron is controlled to resume the working state, and the beam is re-emerged.
  • the voltage of the electrostatic cutting plate is reduced to the first preset Voltage to reduce the voltage of the lateral high-frequency excitation electrode to a second preset voltage so that the beam intensity is less than or equal to a preset intensity threshold.
  • the scanning radiation head moves to the position of the beam spot to be irradiated (that is, the second beam spot); or when the dose of the first beam spot is less than the preset dose and moves to the preset position range; or the scanning radiation head moves to the first The position of the two beam spots, while the dose of the first beam spot is smaller than the preset dose and moved to the preset position range, the voltage of the electrostatic cutting board is restored to the working voltage of the electrostatic cutting board within a preset boost time, and The voltage of the lateral high-frequency excitation electrode is restored to the working voltage of the lateral high-frequency excitation electrode, so that the synchrotron is in a preset working state, and the beam current is output again.
  • a dose irradiated by the scanning radiation head to the position of the first beam spot reaches a preset dose and the position of the first beam spot moves Outside the preset position range
  • the voltage of the electrostatic cutting board and the voltage of the lateral high-frequency excitation electrode are reduced within a preset step-down time, so that the intensity of the proton beam output from the scanning radiation head is less than or equal to a preset intensity threshold.
  • the position of the radiation head to be scanned is moved to the position of the second beam spot and the dose of the scanning radiation head to the first beam spot is less than a preset dose and the position of the first beam spot
  • the voltage of the electrostatic cutting board is restored to the working voltage of the electrostatic cutting board
  • the voltage of the lateral high-frequency excitation electrode is restored to the working voltage of the lateral high-frequency excitation electrode, so that the scanning radiation is
  • the intensity of the proton beam output from the head reaches the working intensity, so that the synchrotron is in a preset working state.
  • the unplanned dose output when the scanning radiation head is transferred between the two beam spots is reduced, because the synchrotron can reduce or stop the two beams.
  • the dose between plaques therefore, it is not necessary to reduce the unplanned dose by reducing the dose rate of radiotherapy, which can increase the dose rate of radiotherapy and shorten the time of radiotherapy.
  • FIG. 4 is a structural block diagram of a synchrotron control device provided in Embodiment 3 of the present application.
  • the device is configured to execute the synchrotron control method provided in any of the above embodiments, and the device may be implemented by software or hardware.
  • the device includes:
  • the beam stopping module 11 is configured to reduce the voltage of the electrostatic cutting plate and the voltage of the lateral high-frequency excitation electrode when the irradiation of the first beam spot by the synchrotron's scanning radiation head meets a preset stop condition, so that the scanning radiation head outputs
  • the proton beam intensity is less than or equal to a preset intensity threshold
  • the synchrotron includes the electrostatic cutting plate configured to deflect a proton beam, the lateral high-frequency excitation electrode configured to excite the proton beam, and a proton beam output to a beam spot.
  • the scanning radiation head at the location.
  • the synchrotron control device provided in the embodiment of the present application reduces the beam intensity by reducing the voltage of the electrostatic cutting plate and the voltage of the lateral high-frequency excitation electrode, so that the beam intensity is rapidly reduced to a preset intensity threshold, so that when the scanning radiation head is at When the two beam spots are transferred, the dose received by the patient is kept at a very low value.
  • this embodiment can increase the dose rate of radiotherapy, which can reduce the time of radiotherapy and Can reduce unplanned doses, which can significantly improve the effect of radiotherapy.
  • the synchrotron control device provided in the embodiment of the present application can execute the synchrotron control method provided in any embodiment of the present application, and has corresponding function modules and beneficial effects of the execution method.
  • FIG. 5 is a schematic structural diagram of a synchrotron device provided in Embodiment 4 of the present application.
  • the device includes a processor 201, a memory 202, an input device 203, and an output device 204.
  • the number of processors 201 in the device may be One or more, a processor 201 is taken as an example in FIG. 5; the processor 201, the memory 202, the input device 203, and the output device 204 in the device may be connected through a bus or other methods, and the connection through the bus is taken as an example in FIG. 5 .
  • the memory 202 is a computer-readable storage medium, and may be configured to store a software program, a computer-executable program, and a module, such as a program instruction / module corresponding to the synchronization accelerator control method in the embodiment of the present application (for example, the stop beam emitting module 11 And start the beam exit module 12).
  • the processor 201 executes each function application and data processing of the device by running software programs, instructions, and modules stored in the memory 202, that is, the above-mentioned synchronous accelerator control method is implemented.
  • the memory 202 may mainly include a storage program area and a storage data area, where the storage program area may store an operating system and application programs required for at least one function; the storage data area may store data created according to the use of the terminal, and the like.
  • the memory 202 may include a high-speed random access memory, and may further include a non-volatile memory, such as at least one magnetic disk storage device, a flash memory device, or other non-volatile solid-state storage device.
  • the memory 202 may include memory remotely set relative to the processor 201, and these remote memories may be connected to the device through a network. Examples of the above network include, but are not limited to, the Internet, an intranet, a local area network, a mobile communication network, and combinations thereof.
  • the input device 203 may be configured to receive inputted numeric or character information and generate key signal inputs related to user settings and function control of the device.
  • the output device 204 may include a display device such as a display screen, for example, a display screen of a user terminal.
  • Embodiment 5 of the present application further provides a storage medium containing computer-executable instructions.
  • the computer-executable instructions are used to execute a synchronization accelerator control method when executed by a computer processor.
  • the method includes:
  • the voltage of the electrostatic cutting plate and the voltage of the lateral high-frequency excitation electrode are reduced, so that the intensity of the proton beam output from the scanning radiation head is less than or Equal to a preset intensity threshold;
  • the synchrotron When the scanning radiation head satisfies a preset irradiation condition, the synchrotron is restored to a working state;
  • the synchrotron includes the electrostatic cutting plate configured to deflect a proton beam, the lateral high-frequency excitation electrode configured to excite the proton beam, and the proton beam output to a beam.
  • the scanning radiation head where the spot is located.
  • a storage medium including computer-executable instructions provided in the embodiments of the present application, and the computer-executable instructions are not limited to the method operations described above, and may also perform related operations in the synchronization accelerator control method provided by any embodiment of the present application. operating.
  • the computer software product can be stored in a computer-readable storage medium, such as a computer's floppy disk or read-only memory (ROM). ), Random Access Memory (RAM), Flash (FLASH), hard disk or optical disk, etc., including multiple instructions to make a computer device (can be a personal computer, server, or network device, etc.) execute this Apply for the synchrotron control method described in each embodiment.
  • a computer-readable storage medium such as a computer's floppy disk or read-only memory (ROM). ), Random Access Memory (RAM), Flash (FLASH), hard disk or optical disk, etc.
  • each unit and module included is divided according to functional logic, but it is not limited to the above-mentioned division, that is, a corresponding function can be realized.
  • the name of each functional unit is to facilitate distinguishing from each other, and is not used to limit the protection scope of the present application.

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Abstract

一种同步加速器控制方法、控制装置、设备以及存储介质，该控制方法包括：当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使扫描辐射头输出的质子束流强度小于或等于预设强度阈值；当所述扫描辐射头满足预设照射条件，所述同步加速器恢复至工作状态。

Description

同步加速器控制方法、装置、设备及存储介质 技术领域
本公开涉及同步加速器技术领域，例如，涉及一种同步加速器控制方法、装置、设备及存储介质。
背景技术
医用同步加速器通常使用慢引出配合笔形束扫描的方法来输出70-230兆电子伏特(MeV)的质子束对肿瘤进行放射性治疗。为了使患者实际接收的放疗剂量与放疗计划的剂量一致，通常通过扫描辐射头里的双电离室来测量每一个束斑的位置和接收的剂量。若当前束斑的剂量达到预设剂量，则扫描辐射头移动至下一个待照射束斑。扫描辐射头从当前束斑位置转移至下一个待照射束斑位置的时间约为1ms，在此时间间隔内，扫描辐射头输出的剂量称为计划外剂量。为了提高放疗剂量控制的准确性，需要尽可能地降低该计划外剂量对放疗效果的影响。
相关技术通常采用连续出束的方式进行放射治疗，为了降低计划外剂量对放疗效果的影响，通常采用降低放射治疗的剂量率的方式，来降低扫描辐射头在不同束斑之间的移动过程中输出的计划外剂量，这就导致了放射治疗时间较长，而较长时间的放射治疗一方面需要准确性较高的放疗摆位，另一方面也会增加病人接收放射治疗过程中的心理恐惧。
发明内容
本申请实施例提供一种同步加速器控制方法、装置、设备及存储介质，以解决相关技术中同步加速器的扫描辐射头在不同束斑之间的移动过程中输出的计划外剂量较高的问题。
本申请实施例提供了一种同步加速器控制方法，包括：
当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使束流强度小于或等于预设强度阈值；
当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态；
其中，所述同步加速器包括：设置为对质子束流进行偏转的所述静电切割板、设置为对质子束流进行激励的所述横向高频激励电极、以及设置为将质子束流输出至束斑所在位置的所述扫描辐射头。
可选的，降低静电切割板的电压和横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于预设强度阈值，包括：
将所述静电切割板的电压降低到第一预设电压，同时将所述横向高频激励电极的电压降低到第二预设电压，以使所述扫描辐射头输出的质子束流强度小于或等于所述预设强度阈值，其中，所述第一预设电压高于所述第二预设电压。
可选的，所述预设停止条件包括下述至少之一：
所述扫描辐射头照射至所述第一束斑所在位置的剂量达到预设剂量；
所述第一束斑的位置移动至预设位置范围外。
可选的，所述当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于预设强度阈值，包括：
当所述扫描辐射头对所述第一束斑的照射符合预设停止条件时，在预设降压时间内，降低所述静电切割板的电压和所述横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于预设强度阈值。
可选的，所述当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使扫描辐射头输出的质子束流强度小于或等于预设强度阈值，包括下述至少一项：
当所述扫描辐射头对所述第一束斑的照射符合所述预设停止条件时，保持所述扫描辐射头当前所在位置不变，并在预设降压时间内，降低所述静电切割板的电压和所述横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于所述预设强度阈值；
当所述扫描辐射头对所述第一束斑的照射符合所述预设停止条件时，将所述扫描辐射头向第二束斑的位置移动，并在移动过程中，降低所述静电切割板的电压和横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于所述预设强度阈值。
可选的，所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态，包括以下至少之一：
当所述扫描辐射头移动至第二束斑的位置时，在预设升压时间内，恢复所述静电切割板的电压至所述静电切割板的工作电压，以及恢复所述横向高频激励电极的电压至所述横向高频激励电极的工作电压，使所述扫描辐射头输出的质子束流强度达到工作强度；
在所述扫描辐射头照射至所述第一束斑的剂量小于预设剂量，且所述第一束斑的位置移动至预设位置范围内的情况下，在所述预设升压时间内，恢复所述静电切割板的电压至所述静电切割板的电压工作电压，以及恢复所述横向高频激励电极的电压至所述横向高频激励电极的工作电压，使所述扫描辐射头输出的质子束流强度达到工作强度。
可选的，所述第一预设电压的取值范围为所述静电切割板的工作电压的50％-80％。
可选的，所述第一预设电压的取值范围为所述静电切割板的工作电压的60％-75％。
可选的，所述预设降压时间小于70us。
本申请实施例还提供了一种同步加速器控制装置，包括：
停止出束模块，设置为当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使扫描辐射头输出的质子束流强度小于或等于预设强度阈值；
启动出束模块，设置为当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态；
其中，所述同步加速器包括设置为对质子束流进行偏转的所述静电切割板、设置为对质子束流进行激励的所述横向高频激励电极、以及设置为将质子束流输出至束斑所在位置的所述扫描辐射头。
本申请实施例还提供了一种设备，所述设备包括：
一个或多个处理器；
存储装置，设置为存储一个或多个程序；
当所述一个或多个程序被所述一个或多个处理器执行，使得所述一个或多个处理器实现上述的同步加速器控制方法。
本申请实施例还提供了一种包含计算机可执行指令的存储介质，所述计算机可执行指令在由计算机处理器执行时用于执行上述的同步加速器控制方法。
本申请实施例提供的同步加速器控制方法，通过降低静电切割板的电压和横向高频激励电极的电压来降低束流强度，使束流强度迅速降低到预设强度阈值，进而当扫描辐射头在两束斑之间转移时使患者所接受的剂量所接受的剂量保持在一个极低值，相较于通过降低剂量率来降低计划外剂量，本实施例可以提高放疗剂量率，这样既能减少放疗时间，又能减少计划外剂量，进而可以显著提高放疗效果。
附图说明
图1是本申请实施例提供的质子束相空间示意图；
图2a是本申请实施例一提供的一种同步加速器控制方法的流程图；
图2b是本申请实施例一提供的另一种同步加速器控制方法的流程图；
图3是本申请实施例二提供的同步加速器控制方法的流程图；
图4是本申请实施例三提供的同步加速器控制装置的结构框图；
图5是本申请实施例四提供的同步加速器设备的结构框图。
具体实施方式
下面将结合附图对本申请实施例中的技术方案进行描述，所描述的实施例是本申请的一部分实施例，而不是全部的实施例，是为了阐述本申请的原理，而不是要将本申请限制于这些实施例。采用医用同步加速器对肿瘤进行质子束放射性治疗时，通常使用慢引出配合笔形束扫描的方法来输出70-230兆电子伏特(MeV)的质子束，而且通常选择1/3整数共振点慢引出机制做剥离。如图1所示，质子束在加速腔加速完毕后，同步加速器通过四级磁铁调整工作点至预设的1/3整数共振工作点附近，开启六级磁铁形成如图1所示的相空间三角型分布的第一质子束。在高频激励电极的激励作用下，质子从三角形的三个角缓慢逸出，作为第二质子束逐渐接近静电切割板从而被引出。被引出的质子束流被质子输运系统输送至扫描辐射头，然后由扫描辐射头输出至当前束斑(即第一束斑)。
束斑的位置以及束斑所接收的剂量均可通过扫描辐射头里的双电离室进行实时测量，用以确定第一束斑的剂量是否已达到预设剂量，以及是否需要将扫描辐射头移动至下一待照射的束斑(即第二束斑)的位置。扫描辐射头在两束斑之间的转移时间约为1ms，在此时间间隔内，扫描辐射头所输出的剂量称为计划外剂量。
根据行业标准，计划外剂量要小于计划总剂量的10％。因此对于连续出束的放疗方法，通常通过降低放射治疗的剂量率以及优化剂量统计方法的方式，来降低计划外剂量对放射治疗的影响。但是，这些解决方式仅能在一定程度上降低计划外剂量对放疗效果的影响，而且降低放射治疗的剂量率还意味着延长放射治疗的时间。基于此，本实施例提出一种同步加速器控制方法、装置、设 备及存储介质，下面对同步加速器控制方法进行介绍。
实施例一
图2a是本申请实施例一提供的一种同步加速器控制方法的流程图。本实施例的技术方案适用于降低放射治疗的计划外剂量的情况，本实施例以基于同步加速器的质子放疗为例进行说明。该方法可以由本申请实施例提供的同步加速器控制装置来执行，该装置可以采用下述至少一种方式实现：软件和硬件，该装置配置在处理器中应用。该方法包括如下步骤：
S110、当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低所述静电切割板的电压和所述横向高频激励电极的电压，使扫描辐射头输出的质子束流强度小于或等于预设强度阈值。
S120、当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态；
其中，所述同步加速器包括：设置为对质子束流进行偏转的所述静电切割板、设置为对质子束流进行激励的所述横向高频激励电极、以及设置为将质子束流输出至束斑所在位置的所述扫描辐射头。
图2b是本申请实施例一提供的另一种同步加速器控制方法的流程图，如图2b所示，该方法包括：S101、当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，在预设降压时间内，降低静电切割板的电压和横向高频激励电极的电压，使扫描辐射头输出的质子束流强度小于或等于预设强度阈值。
在质子放疗过程中，通常将肿瘤划分为多个垂直于束流照射方向的能量层，并确定每一能量层的多个束斑位置和每一束斑的预设剂量。放疗开始后，同步加速器控制扫描辐射头按照预设顺序，依次照射每个束斑位置直至该束斑的剂量达到预设剂量。也就是说，本实施例的预设停止条件可以是预设剂量。
同步加速器通过横向高频激励电极对加速腔内的质子束进行激励以对其进行扰动，在横向高频激励电极停止对同步加速器内的质子束进行激励后，将不会有质子束因扰动而达到稳定区外，但之前留存在同步加速器内处于稳定区外的质子束还是会被引出。也就是说，横向高频激励电极在降低电压的过程中仍 有质子束被引出，直至加速器内位于稳定区外的质子束全部被引出。因此，仅通过降低横向高频激励电极的电压来降低束流强度需要较长的时间，通常为几百微秒。虽然同步加速器在该过程中所输出的计划外剂量小于连续出束的放疗技术的计划外剂量，但这个计划外剂量仍然是一个不可忽视的高剂量值，尤其是对于使用大剂量率进行放射治疗的放疗计划。
对于同步加速器，当质子束被加速到预设能量后，通过质子偏转装置将达到预设能量的质子束引出。静电切割板是质子偏转装置中对质子束进行偏转的第一步。也就是说，质子束要偏转出同步加速器，首先经过静电切割板的偏转电场，在偏转电场的作用下偏离原有的运动轨迹，然后经过质子偏转装置的其他部分被引出以离开加速器。基于此，本实施例通过降低静电切割板的电压，来减弱或是去掉静电切割板的偏转电场，使静电切割板的偏转电场不能将质子束偏移至预设引出轨迹。此时，携带有预设能量的质子束会因为偏转电场较弱而不足以偏转至预设引出轨迹，进而不能被质子偏转装置的其他部分引出，或是被引出的质子数量非常的少。或者，携带有预设能量的质子束因为没有横向激励源和偏转电场的存在而不会产生扰动和偏转，继续留在加速腔内。
本实施例中的横向高频激励电极从工作电压降低至第二预设电压通常需要几百微秒，远远大于静电切割板的电压降低至第一预设电压的时间。第一预设电压的取值范围通常在静电切割板的工作电压的50％-80％内，可选地，第一预设电压的取值范围在静电切割板工作电压的60％-75％内。当静电切割板从工作电压降低到工作电压的70％时，所需时间小于70us。若静电切割板的电压控制装置的性能较好，第一预设时间可以低于50us。实际使用时，可以先获取质子束引出时第一次偏转所需的静电切割板的最低电压值，然后将第一预设电压值设置为小于该最低电压值。在一实施例中，为了延长同步加速器的使用寿命，以及加快同步加速器恢复横向高频激励电极的工作电压，通常不会使横向高频激励电极处于完全断电状态，横向高频激励电极的电压不能对加速腔内的质子束进行有效激励即可。
综上所述，通过降低静电切割板的电压至第一预设电压的同时，降低横向高频激励电极的电压至第二预设电压，可以使同步加速器的扫描辐射头在静电 切割板降压至第一预设电压的时间内停止出束或是以极低的剂量率出束，进而可以大幅缩短同步加速器所输出的束流强度降低至小于或等于预设强度阈值的时间。
在一实施例中，同步加速器可以保持扫描辐射头位于第一束斑位置不变，并在预设降压时间内，将静电切割板的电压降低至第一预设电压，并将横向高频激励电极的电压降低至第二预设电压。也可以在第一束斑符合预设停止条件时，将扫描辐射头向第二束斑位置移动，并在移动过程中，将静电切割板的电压降低至第一预设电压，并将横向高频激励电极的电压降低至第二预设电压。无论采用前述哪一种电压降低方式，当扫描辐射头移动至第二束斑位置时，控制同步加速器恢复至预设工作状态。
S102、当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态。
当同步加速器辐射头位于待照射的束斑位置时，同步加速器恢复至预设工作状态，并向第一束斑的位置输出束流，直至电离室检测到第一束斑的剂量达到预设剂量为止。此时，扫描辐射头对第一束斑的照射符合预设停止条件，则降低静电切割板的工作电压至第一预设电压，降低横向高频激励电极的电压至第二预设电压，依次类推，直至最后一个束斑的剂量达到预设剂量为止。
本实施例中的预设照射条件为：电离室检测到扫描辐射头移动至待照射的束斑位置。
示例性的，计划外剂量占整个放疗计划总剂量的百分比由单层的扫描时间决定，对于连续放射治疗的技术方案来说，假设单层扫描时间为1s，扫描点数是200个，扫描辐射头在两束斑之间的转移时间为1ms，那么计划外剂量与剂量总剂量的百分比关系为：1ms/2/(1s/200)＝10％。所以为了降低这个百分比，普通机器就必须被迫延长单层扫描时间，也就相当于延长整个治疗时间。治疗时间太长的话，对于病人的舒适度，治疗摆位和病人吞吐率等都有影响。
对于本申请实施例，若单层扫描时间1s是，扫描点数200个，静电切割板的电压降低至工作电压的70％所用时间为50us，扫描辐射头在两束斑之间的转移时间为1ms，则计划外剂量占整个计划总剂量的百分比小于 50us/1ms*10％＝0.5％。本实施例可以大幅降低计划外剂量所占计划总剂量的百分比，从而可以提高放射治疗的剂量率，减少单层扫描时间，进而降低每次放射治疗的总时间，降低治疗摆位的难度，以及降低患者放射治疗时的恐惧感。
本申请实施例提供的同步加速器控制方法，当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，在预设降压时间内，降低静电切割板的电压和横向高频激励电极的电压，使束流强度小于或等于预设强度阈值，使当扫描辐射头在两束斑之间转移时使患者所接受的剂量保持在一个极低值，相较于通过降低剂量率来降低计划外剂量，本实施例可以提高放疗剂量率，这样既能减少放疗时间，又能减少计划外剂量，进而可以显著提高放疗效果。
实施例二
图3是本申请实施例二提供的同步加速器控制方法的流程图。本申请实施例在上述实施例的基础上引入实时位置检测，即公开一种结合实时位置检测的同步加速器控制方法。如图3所示，该方法包括：
S200、实时检测第一束斑的位置，以及所述第一束斑所接收的剂量。
通过实时位置检测装置实时检测第一束斑的位置是否在预设范围内，通过电离室检测第一束斑所接收的剂量是否已达到预设剂量。实时位置检测装置可以是呼吸门控、锥形束计算机断层扫描(Cone beam Computed Tomography，CBCT)，或者其他能够实时检测肿瘤位置变化的装置，本实施例对此不予限定。
S210、当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，在预设降压时间内，降低静电切割板的电压和横向高频激励电极的电压，使扫描辐射头输出的质子束流强度小于或等于预设强度阈值。
若第一束斑的位置移动至预设位置范围外，即：在第一束斑的位置与束斑的预设位置之间的位置偏差大于预设位置偏差的情况下，降低静电切割板的电压至第一预设电压，将横向高频激励电极的电压降低至第二预设电压，使束流强度小于或等于预设强度阈值。当预设强度阈值为0时，则扫描辐射头停止出束。待到第一束斑移动至预设位置范围内时，控制同步加速器恢复工作状态，重新出束。
若第一束斑的剂量达到预设剂量，或者第一束斑的位置移动至预设位置范围外同时第一束斑的剂量达到预设剂量，则降低静电切割板的电压至第一预设电压，将横向高频激励电极的电压降低至第二预设电压，使束流强度小于或等于预设强度阈值。
S220、当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态。
当扫描辐射头移动至待照射的束斑(即第二束斑)的位置时；或者第一束斑的剂量小于预设剂量且移动至预设位置范围内时；或者扫描辐射头移动至第二束斑的位置，同时第一束斑的剂量小于预设剂量且移动至预设位置范围内时，在预设升压时间内，恢复静电切割板的电压至静电切割板的工作电压，以及恢复横向高频激励电极的电压至横向高频激励电极的工作电压，使同步加速器处于预设工作状态，重新输出束流。
本申请实施例提供的同步加速器控制方法，若发生下述至少一项：所述扫描辐射头照射至所述第一束斑所在位置的剂量达到预设剂量和所述第一束斑的位置移动至预设位置范围外，则在预设降压时间内，降低静电切割板的电压和横向高频激励电极的电压，使扫描辐射头输出的质子束流强度小于或等于预设强度阈值。若发生下述至少一项：待扫描辐射头移动至第二束斑的位置以及在所述扫描辐射头照射至所述第一束斑的剂量小于预设剂量且所述第一束斑的位置移动至预设位置范围内的情况下，则恢复静电切割板的电压至静电切割板的工作电压，以及恢复横向高频激励电极的电压至横向高频激励电极的工作电压，使所述扫描辐射头输出的质子束流强度达到工作强度，使同步加速器处于预设工作状态。结合实时位置检测装置，通过控制静电切割板与横向高频激励电极的电压变化，减少扫描辐射头在两束斑之间转移时所输出的计划外剂量，由于可以降低或停止同步加速器在两束斑之间的剂量，因此无需通过降低放疗剂量率来降低计划外剂量，即可以提高放疗剂量率，缩短放疗时间。
实施例三
图4是本申请实施例三提供的同步加速器控制装置的结构框图。该装置设 置为执行上述任意实施例所提供的同步加速器控制方法，该装置可选为软件或硬件实现。该装置包括：
停止出束模块11，设置为当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使扫描辐射头输出的质子束流强度小于或等于预设强度阈值；
启动出束模块12，设置为当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态；
其中，所述同步加速器包括设置为对质子束流进行偏转的所述静电切割板、设置为对质子束流进行激励的所述横向高频激励电极、以及设置为将质子束流输出至束斑所在位置的所述扫描辐射头。
本申请实施例提供的同步加速器控制装置，通过降低静电切割板的电压和横向高频激励电极的电压来降低束流强度，使束流强度迅速降低到预设强度阈值，使当扫描辐射头在两束斑之间转移时使患者所接受的剂量保持在一个极低值，相较于通过降低剂量率来降低计划外剂量，本实施例可以提高放疗剂量率，这样既能减少放疗时间，又能减少计划外剂量，进而可以显著提高放疗效果。
本申请实施例所提供的同步加速器控制装置可执行本申请任意实施例所提供的同步加速器控制方法，具备执行方法相应的功能模块和有益效果。
实施例四
图5为本申请实施例四提供的同步加速器设备的结构示意图，如图5所示，该设备包括处理器201、存储器202、输入装置203以及输出装置204；设备中处理器201的数量可以是一个或多个，图5中以一个处理器201为例；设备中的处理器201、存储器202、输入装置203以及输出装置204可以通过总线或其他方式连接，图5中以通过总线连接为例。
存储器202作为一种计算机可读存储介质，可设置为存储软件程序、计算机可执行程序以及模块，如本申请实施例中的同步加速器控制方法对应的程序指令/模块(例如，停止出束模块11和启动出束模块12)。处理器201通过运行存储在存储器202中的软件程序、指令以及模块，从而执行设备的每种功能应 用以及数据处理，即实现上述的同步加速器控制方法。
存储器202可主要包括存储程序区和存储数据区，其中，存储程序区可存储操作系统、至少一个功能所需的应用程序；存储数据区可存储根据终端的使用所创建的数据等。此外，存储器202可以包括高速随机存取存储器，还可以包括非易失性存储器，例如至少一个磁盘存储器件、闪存器件、或其他非易失性固态存储器件。在一些实例中，存储器202可以包括相对于处理器201远程设置的存储器，这些远程存储器可以通过网络连接至设备。上述网络的实例包括但不限于互联网、企业内部网、局域网、移动通信网及其组合。
输入装置203可以设置为接收输入的数字或字符信息，以及产生与设备的用户设置以及功能控制有关的键信号输入。
输出装置204可以包括显示屏等显示设备，例如，用户终端的显示屏。
实施例五
本申请实施例五还提供一种包含计算机可执行指令的存储介质，所述计算机可执行指令在由计算机处理器执行时用于执行一种同步加速器控制方法，该方法包括：
当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于预设强度阈值；
当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态；
其中，所述同步加速器包括：设置为对质子束流进行偏转的所述静电切割板、设置为对质子束流进行激励的所述横向高频激励电极、以及设置为将质子束流输出至束斑所在位置的所述扫描辐射头。本申请实施例所提供的一种包含计算机可执行指令的存储介质，其计算机可执行指令不限于如上所述的方法操作，还可以执行本申请任意实施例所提供的同步加速器控制方法中的相关操作。
通过以上关于实施方式的描述，所属领域的技术人员可以清楚地了解到，本申请可借助软件和通用硬件来实现，当然也可以通过硬件实现，但很多情况下前者是更佳的实施方式。基于这样的理解，本申请的技术方案本质上可以以 软件产品的形式体现出来，该计算机软件产品可以存储在计算机可读存储介质中，如计算机的软盘、只读存储器(Read-Only Memory，ROM)、随机存取存储器(Random Access Memory，RAM)、闪存(FLASH)、硬盘或光盘等，包括多个指令用以使得一台计算机设备(可以是个人计算机，服务器，或者网络设备等)执行本申请每个实施例所述的同步加速器控制方法。
在上述同步加速器控制装置的实施例中，所包括的，每个单元和模块是按照功能逻辑进行划分的，但并不局限于上述的划分，即能够实现相应的功能即可。另外，每个功能单元的名称是为了便于相互区分，并不用于限制本申请的保护范围。

Claims (12)

  1. 一种同步加速器控制方法，包括：
    当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于预设强度阈值；
    当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态；
    其中，所述同步加速器包括：设置为对质子束流进行偏转的所述静电切割板、设置为对质子束流进行激励的所述横向高频激励电极、以及设置为将质子束流输出至束斑所在位置的所述扫描辐射头。
  2. 根据权利要求1所述的方法，其中，所述降低静电切割板的电压和横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于预设强度阈值，包括：
    将所述静电切割板的电压降低到第一预设电压，同时将所述横向高频激励电极的电压降低到第二预设电压，以使所述扫描辐射头输出的质子束流强度小于或等于所述预设强度阈值，其中，所述第一预设电压高于所述第二预设电压。
  3. 根据权利要求1或2所述的方法，其中，所述预设停止条件包括下述至少之一：
    所述扫描辐射头照射至所述第一束斑所在位置的剂量达到预设剂量；
    所述第一束斑的位置移动至预设位置范围外。
  4. 根据权利要求1、2或3所述的方法，其中，所述当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于预设强度阈值，包括：
    当所述扫描辐射头对所述第一束斑的照射符合预设停止条件时，在预设降压时间内，降低所述静电切割板的电压和所述横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于预设强度阈值。
  5. 根据权利要求1、2或3所述的方法，其中，所述当同步加速器的扫描辐射头对第一束斑的照射符合预设停止条件时，降低静电切割板的电压和横向 高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于预设强度阈值，包括下述至少一项：
    当所述扫描辐射头对所述第一束斑的照射符合所述预设停止条件时，保持所述扫描辐射头当前所在位置不变，并在预设降压时间内，降低所述静电切割板的电压和所述横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于所述预设强度阈值；
    当所述扫描辐射头对所述第一束斑的照射符合所述预设停止条件时，将所述扫描辐射头向第二束斑的位置移动，并在移动过程中，降低所述静电切割板的电压和所述横向高频激励电极的电压，使所述扫描辐射头输出的质子束流强度小于或等于所述预设强度阈值。
  6. 根据权利要求1-5任一项所述的方法，其中，所述当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态，包括以下至少之一：
    当所述扫描辐射头移动至第二束斑的位置时，在预设升压时间内，恢复所述静电切割板的电压至所述静电切割板的工作电压，以及恢复所述横向高频激励电极的电压至所述横向高频激励电极的工作电压，使所述扫描辐射头输出的质子束流强度达到工作强度；
    在所述扫描辐射头照射至所述第一束斑的剂量小于预设剂量，且所述第一束斑的位置移动至预设位置范围内的情况下，在所述预设升压时间内，恢复所述静电切割板的电压至所述静电切割板的电压工作电压，以及恢复所述横向高频激励电极的电压至所述横向高频激励电极的工作电压，使所述扫描辐射头输出的质子束流强度达到工作强度。
  7. 根据权利要求2所述的方法，其中，所述第一预设电压的取值范围为所述静电切割板的工作电压的50％-80％。
  8. 根据权利要求2所述的方法，其中，所述第一预设电压的取值范围为所述静电切割板的工作电压的60％-75％。
  9. 根据权利要求4或5所述的方法，其中，所述预设降压时间小于70us。
  10. 一种同步加速器控制装置，包括：
    停止出束模块，设置为当同步加速器的扫描辐射头对第一束斑的照射符合 预设停止条件时，降低静电切割板的电压和横向高频激励电极的电压，使扫描辐射头输出的质子束流强度小于或等于预设强度阈值；
    启动出束模块，设置为当所述扫描辐射头满足预设照射条件时，所述同步加速器恢复至工作状态；
    其中，所述同步加速器包括：设置为对质子束流进行偏转的所述静电切割板、设置为对质子束流进行激励的所述横向高频激励电极、以及设置为将质子束流输出至束斑所在位置的所述扫描辐射头。
  11. 一种设备，所述设备包括：
    一个或多个处理器；
    存储装置，设置为存储一个或多个程序；
    当所述一个或多个程序被所述一个或多个处理器执行，使得所述一个或多个处理器实现如权利要求1-9中任一项所述的同步加速器控制方法。
  12. 一种包含计算机可执行指令的存储介质，所述计算机可执行指令在由计算机处理器执行时用于执行如权利要求1-9中任一项所述的同步加速器控制方法。
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