Superconducting proton cyclotron

Abstract

A superconducting proton cyclotron (100). The superconducting proton cyclotron (100) comprises a main cyclotron system (10), a cyclotron auxiliary system (20) and a cyclotron control system (30). The main cyclotron system (10) comprises an ion source (11), a central region (12), a superconducting magnet system (13), a radio frequency system (14) and a lead-out region (15). The ion source (11) is used for generating a proton beam; the central region (12) is used for leading out the proton beam of the ion source (11) and performing beam focusing inside the central region (12); the radio frequency system (14) leads out and accelerates the beam of the central region (12); a static magnetic field generated by the superconducting magnet system (13) can constrain the proton beam and accelerate same to target energy; the lead-out region (15) can lead out the proton beam.

Description

Superconducting Cyclotron Proton Accelerator

[0001] Priority information

[0002] This invention claims priority and benefits from patent application number 202311449516.X filed with the State Intellectual Property Office of China on November 2, 2023, and the entire text of which is incorporated herein by reference. Technical Field

[0003] The present application relates to the technical field of medical equipment, and more specifically, to a superconducting cyclotron proton accelerator. Background Art

[0004] Currently, accelerators used for proton therapy are primarily categorized as isochronous cyclotrons, synchrotrons, and synchrocyclotrons. Isochronous cyclotrons achieve particle acceleration by matching the particle gyration frequency of a static magnetic field with the frequency of a fixed radiofrequency electric field. Synchrotrons, on the other hand, require a variable magnetic field and a modulated electric field frequency to achieve particle acceleration. This significantly reduces the size, construction, and maintenance requirements of isochronous cyclotrons. Synchrocyclotrons, like isochronous cyclotrons, offer the same compactness, effectively reducing manufacturing costs. However, because the electric field of a synchrocyclotron must be modulated, the beam is pulsed, significantly reducing the therapeutic dose compared to the continuous beam of an isochronous cyclotron. Therefore, isochronous cyclotrons offer unparalleled advantages for proton therapy. However, due to their complex physical structure and the high precision required for the magnetic field, the design of isochronous cyclotrons is challenging, hindering the further development of accelerators in China.

[0005] Summary of the Invention

[0006] An embodiment of the present application provides a superconducting cyclotron proton accelerator.

[0007] The superconducting cyclotron proton accelerator according to the embodiment of the present application includes:

[0008] A main accelerator system comprising an ion source, a central region, a superconducting magnet system, a radio frequency system, and an extraction region. The ion source is used to generate a proton beam. The central region is used to extract the proton beam from the ion source and perform beam focusing within the central region. The radio frequency system extracts and accelerates the central region beam. The static magnetic field generated by the superconducting magnet system can confine the proton beam during proton beam acceleration and accelerate it to a target energy. The extraction region can extract the proton beam.

[0009] an accelerator auxiliary system, configured to provide the main accelerator system with stable operating conditions and a vacuum environment when accelerating the proton beam;

[0010] The accelerator control system is used to operate the various subsystems of the main accelerator system, adjust the stability of the proton beam acceleration motion, and effectively monitor the current status of each subsystem.

[0011] In the superconducting cyclotron proton accelerator of the embodiment of the present application, the superconducting cyclotron proton accelerator includes a main accelerator system, an accelerator auxiliary system and an accelerator control system. The main accelerator system includes an ion source, a central area, a superconducting magnet system, a radio frequency system and an extraction area. The ion source is used to generate a proton beam. The central area is used to extract the proton beam of the ion source and perform beam focusing inside the central area. The radio frequency system extracts and accelerates the central area beam. The static magnetic field generated by the superconducting magnet system can confine the proton beam and accelerate it to the target energy during the proton beam acceleration process. The extraction area can extract the proton beam. The accelerator auxiliary system is used to provide the main accelerator system with stable operating conditions and a vacuum environment when accelerating the proton beam. The accelerator control system is used to operate the various subsystems of the main accelerator system, adjust the stability of the proton beam acceleration motion, and effectively monitor the current status of each subsystem. In this way, the superconducting cyclotron proton accelerator can generate a proton beam through the main accelerator system and accelerate the proton beam to the target energy. The beam is strong and of good quality, and the proton energy can meet the treatment needs of more than 90% of cancer types in proton therapy. The accelerator structure is compact and can effectively reduce equipment manufacturing costs and integration space.

[0012] In some embodiments, the extraction region constrains the proton beam by magnetic focusing. In this way, the extraction region can focus the proton beam by the magnetic field, thereby constraining the proton beam, so that the proton beam can maintain stability and accuracy.

[0013] In certain embodiments, the target energy of the proton beam after passing through the extraction region is 230-250 MeV. Thus, the proton beam can be accelerated to 230-250 MeV after exiting the extraction region. This high-energy and high-quality proton beam can meet the treatment requirements of over 90% of cancer types in proton therapy.

[0014] In certain embodiments, the central region is a raised metal structure mounted at the center of the superconducting cyclotron proton accelerator. The central region provides axial electric focusing and constrains the trajectory of the proton beam passing through the central region, thereby reducing proton beam losses. In this manner, the central region can generate a specific electric field structure, providing axial electric focusing while constraining the beam trajectory in the central region, thereby reducing proton beam losses and ensuring proton beam energy stability.

[0015] In certain embodiments, the ion source is a Penning ion source, which is mounted at the center of the superconducting cyclotron proton accelerator and extends through the central region. Thus, when a proton beam is generated in the ion source arc chamber, it is precisely drawn into the central region by the electric field and accelerated therein.

[0016] In certain embodiments, the superconducting cyclotron proton accelerator further includes a three-dimensional movable platform, on which the ion source is mounted, and the angular position and axial height position of the ion source are adjusted via the three-dimensional movable platform to improve the extraction efficiency of the ion source beam. Thus, the angular position and axial height position of the ion source are adjusted via the three-dimensional movable platform to improve the extraction efficiency of the ion source beam.

[0017] In some embodiments, the main accelerator system further includes vertical deflection plates positioned in the central region. These plates are configured to generate an electric field to precisely adjust the beam's axial position. The plates can be a pair of symmetrical high-voltage electrodes. When the power supply is operating, an electric field is generated between the plates. This electric field can be adjusted by varying the high-voltage input voltage. This allows for precise adjustment of the beam's axial position and the intensity of the central region's extracted beam, as well as rapid beam shutoff.

[0018] In certain embodiments, the superconducting magnet system includes superconducting coils that are fed with current to generate a specific static magnetic field. Thus, current can be fed into the superconducting coils, which, under the influence of the current, generate a magnetic field that constrains the trajectory of the proton beam and ensures stable delivery of the proton beam outside the accelerator.

[0019] In certain embodiments, the superconducting coils are cooled using double-zero-volatility liquid helium cooling technology. This allows for cooling of the coils using only a minimal amount of liquid helium during superconducting operation, minimizing the risk of liquid helium expanding during a quench and reducing losses during the conversion of liquid helium to helium gas.

[0020] In certain embodiments, the superconducting magnet system further includes a rapid demagnetizer configured to demagnetize the superconducting coils. This allows the rapid demagnetizer to demagnetize the magnets within a short period of time after an unexpected quench, rapidly transferring and discharging internal energy to the outside of the magnets to ensure the safety of the entire superconducting magnet system.

[0021] In certain embodiments, the RF system includes an RF source and an RF cavity. The RF source feeds power into the RF cavity, generating a high-frequency voltage within the cavity. The RF source can then transmit a high-frequency electrical signal to the cavity, generating a high-frequency voltage within the cavity, thereby providing an accelerating environment for the proton beam.

[0022] In certain embodiments, the RF cavity includes a first cavity and a second cavity, each of which is independent of the other and connected to a separate power source. This allows for independent regulation of the two RF cavities using a single power source, reducing the operating pressure of the power source at full power, improving the operational stability of the RF cavity, and reducing the risk of ignition. Furthermore, the phase coupling between the two cavities can be independently adjusted to achieve better acceleration efficiency.

[0023] In some embodiments, the accelerator auxiliary system includes a power supply system that provides power to the subsystem devices. In this way, the power supply system can provide electrical energy to the subsystem devices to ensure stable power supply to the superconducting cyclotron proton accelerator.

[0024] In some embodiments, the accelerator auxiliary system further includes a water cooling system, which cools the subsystems of the main accelerator system. Thus, the water cooling system can cool each subsystem by circulating water to ensure stable operation of the superconducting cyclotron proton accelerator.

[0025] In some embodiments, the accelerator auxiliary system further includes a vacuum system, which provides a vacuum environment inside the superconducting cyclotron proton accelerator, so that the proton beam can move in a vacuum to prevent impurity molecules in the air from affecting the proton beam.

[0026] Additional aspects and advantages of the present application will be given in part in the description below, and in part will become obvious from the description below, or will be learned through practice of the present application. BRIEF DESCRIPTION OF THE DRAWINGS

[0027] The above and / or additional aspects and advantages of the present application will become apparent and easily understood from the description of the embodiments in conjunction with the following drawings, in which:

[0028] FIG1 is a schematic diagram of a module of a superconducting cyclotron proton accelerator according to an embodiment of the present application;

[0029] FIG2 is a schematic structural diagram of a superconducting cyclotron proton accelerator according to an embodiment of the present application;

[0030] FIG3 is another schematic structural diagram of a superconducting cyclotron proton accelerator according to an embodiment of the present application;

[0031] FIG4 is another schematic structural diagram of a superconducting cyclotron proton accelerator according to an embodiment of the present application;

[0032] FIG5 is another schematic structural diagram of the superconducting cyclotron proton accelerator according to the embodiment of the present application.

[0033] Description of the main component symbols: Superconducting cyclotron proton accelerator 100; main accelerator system 10, ion source 11, central area 12, superconducting magnet system 13, superconducting coil 131, magnet 132, magnetic pole 133, radio frequency system 14, extraction area 15, electrostatic deflection plate 151, magnetic channel 152, vertical deflection plate 16, accelerator auxiliary system 20, power supply system 21, water cooling system 22, vacuum system 23, accelerator control system 30, three-dimensional mobile platform 40. DETAILED DESCRIPTION

[0034] The embodiments of the present application are described in detail below, and examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present application, and should not be understood as limiting the present application.

[0035] In this application, unless otherwise expressly specified or limited, a first feature being "above" or "below" a second feature may include the first and second features being in direct contact, or may include the first and second features being in contact not directly but through another feature between them. Moreover, a first feature being "above," "above," and "above" a second feature may include the first feature being directly above or obliquely above the second feature, or may simply mean that the first feature is higher in level than the second feature. A first feature being "below," "below," and "below" a second feature may include the first feature being directly below or obliquely below the second feature, or may simply mean that the first feature is lower in level than the second feature.

[0036] The disclosure below provides many different embodiments or examples for realizing different structures of the present application. In order to simplify the disclosure of the present application, the components and settings of specific examples are described below. Of course, they are merely examples and are not intended to limit the present application. In addition, the present application may repeat reference numbers and / or reference letters in different examples, and such repetition is for the purpose of simplicity and clarity, and does not itself indicate the relationship between the various embodiments and / or settings discussed. In addition, the present application provides examples of various specific processes and materials, but those of ordinary skill in the art will appreciate the application of other processes and / or the use of other materials.

[0037] Referring to Figures 1 and 2, the superconducting cyclotron proton accelerator 100 of the embodiment of the present application includes a main accelerator system 10, an accelerator auxiliary system 20, and an accelerator control system 30. The main accelerator system 10 includes an ion source 11, a central region 12, a superconducting magnet system 13, a radio frequency system 14, and an extraction region 15. The ion source 11 is used to generate a proton beam. The central region 12 is used to extract the proton beam from the ion source 11 and perform beam focusing within the central region 12. The radio frequency system 14 extracts and accelerates the beam from the central region 12. The static magnetic field generated by the superconducting magnet system 13 can confine the proton beam during the proton beam acceleration process and accelerate it to the target energy. The extraction region 15 can extract the proton beam. The accelerator auxiliary system 20 is used to provide stable operating conditions for the main accelerator system 10 when accelerating the proton beam and to provide a vacuum environment when accelerating the proton beam. The accelerator control system 30 is used to operate the various subsystems of the main accelerator system 10, adjust the stability of the proton beam acceleration motion, and effectively monitor the current status of each subsystem.

[0038] In the superconducting cyclotron proton accelerator 100 according to the embodiment of the present application, the superconducting cyclotron proton accelerator 100 includes a main accelerator system 10 , an accelerator auxiliary system 20 and an accelerator control system 30 . The main accelerator system 10 includes an ion source 11, a central area 12, a superconducting magnet system 13, a radio frequency system 14 and an extraction area 15. The ion source 11 is used to generate a proton beam. The central area 12 is used to extract the proton beam from the ion source 11 and perform beam focusing inside the central area 12. The radio frequency system 14 extracts and accelerates the beam from the central area 12. The static magnetic field generated by the superconducting magnet system 13 can confine the proton beam and accelerate it to the target energy during the proton beam acceleration process. The extraction area 15 can extract the proton beam; the accelerator auxiliary system 20 is used to provide stable operating conditions for the main accelerator system 10 when accelerating the proton beam and provide a vacuum environment when accelerating the proton beam; the accelerator control system 30 is used to operate the various subsystems of the main accelerator system 10, adjust the stability of the proton beam acceleration motion, and effectively monitor the current status of each subsystem. In this way, the superconducting cyclotron proton accelerator 100 can generate a proton beam through the main accelerator system 10 and accelerate the proton beam to the target energy. The beam flow is strong and of good quality. The extracted proton energy meets the treatment requirements of more than 90% of cancer types in proton therapy. The accelerator structure is compact and can effectively reduce equipment manufacturing costs and integration space.

[0039] Specifically, the main accelerator system 10 generates a proton beam through the ion source 11 and accelerates the proton beam through other subsystems, ensuring that the beam is stably accelerated from a low-energy stage to 230-250 MeV before being directed to a high-energy transport line and ultimately to the treatment head for proton therapy for cancer patients. The accelerator auxiliary system 20 provides stable operating conditions and a vacuum environment for the main accelerator system 10 when accelerating the proton beam. The accelerator control system 30 is used to operate the various subsystems of the main accelerator, adjust the stability of the beam acceleration motion, and effectively monitor the current status of each subsystem.

[0040] In the related art, accelerators used for proton therapy are mainly divided into three types: isochronous cyclotrons, synchrotrons, and synchrocyclotrons. Isochronous cyclotrons achieve particle acceleration by matching the particle cyclotron frequency of a static magnetic field with the frequency of a fixed radiofrequency electric field. Synchrotrons, on the other hand, require a variable magnetic field and a modulated electric field frequency to achieve particle acceleration. This significantly reduces the size, construction, and maintenance requirements of isochronous cyclotrons. Synchrocyclotrons, like isochronous cyclotrons, offer the same compactness, effectively reducing manufacturing costs. However, because the electric field of a synchrocyclotron needs to be modulated, the beam it produces is pulsed. Compared to the continuous beam of an isochronous cyclotron, the beam dose is significantly reduced in terms of therapeutic effectiveness. Therefore, isochronous cyclotrons offer unparalleled advantages for proton therapy. However, due to the complex physical structure design and the high precision required for the magnetic field, the design of isochronous cyclotrons is difficult.

[0041] In an embodiment of the present application, the central region 12 is used to extract and accelerate the proton beam from the ion source 11. The puller structure inside the central region 12 generates a specific electric field and the plug structure generates a specific magnetic field to focus the beam, thereby ultimately improving the quality and beam intensity of the accelerated beam passing through the central region 12; the radio frequency system 14 accelerates and provides an accelerating cavity pressure for the radio frequency cavity, accelerating the proton beam to 230-250MeV; the superconducting magnet system 13 is used to generate a static magnetic field, so that the beam is constrained and accelerated to the target energy during the acceleration process, and finally reaches the extraction region 15; the extraction region 15 includes an electrostatic deflection plate 151 and a magnetic channel 152, which are used to complete the extraction of the beam from the extraction region 15.

[0042] 1 and 2 , in some embodiments, the extraction region 15 confines the proton beam through magnetic focusing. Thus, the extraction region 15 can focus the proton beam through the magnetic field, thereby confining the proton beam and maintaining stability and accuracy.

[0043] 1 and 2 , in some embodiments, the target energy of the proton beam after passing through the extraction region 15 is 230-250 MeV. For example, the target energy of the proton beam after passing through the extraction region 15 may be 230 MeV, 231 MeV, 232 MeV, 233 MeV, 234 MeV, 235 MeV, 236 MeV, 237 MeV, 238 MeV, 239 MeV, 240 MeV, 241 MeV, 242 MeV, 243 MeV, 244 MeV, 245 MeV, 246 MeV, 247 MeV, 248 MeV, 249 MeV, or 250 MeV.

[0044] Thus, the proton beam extracted by extraction region 15 can be accelerated to an energy of 230-250 MeV. This high-energy, high-quality proton beam can meet the treatment requirements of over 90% of cancer types in proton therapy. Preferably, the proton beam extracted by extraction region 15 can be accelerated to an energy of 240 MeV, providing a stable energy intensity for proton therapy of cancer patients.

[0045] Specifically, the extraction system includes an electrostatic deflection plate 151 and a magnetic channel 152. The electrostatic electric field generated by the classical deflection plate is used to strip off the beam in the extraction area 15 and extract it. Under the action of axial magnetic focusing provided by the magnetic channel 152, the quality and intensity of the beam extraction are improved.

[0046] Referring to Figures 1 and 2 , in certain embodiments, central region 12 is a raised metal structure mounted at the center of superconducting cyclotron proton accelerator 100. Central region 12 provides axial electric focusing and constrains the trajectory of the proton beam passing through central region 12, thereby reducing proton beam losses. Thus, central region 12 can generate a specific electric field structure, providing axial electric focusing while constraining the beam trajectory in central region 12, reducing proton beam losses and ensuring proton beam energy stability.

[0047] Specifically, the central area 12 of the main accelerator system 10 includes a Dee tip, a Dummy, a plug structure and a puller structure, which are installed in the central area 12 of the superconducting cyclotron proton accelerator 100 and are used to extract and accelerate the proton plasma inside the arc chamber of the ion source 11. During the acceleration process in the central area 12, by designing the puller and plug structures of the central area 12, a specific electric field structure and magnetic field are generated in the central area 12 of the accelerator. When the proton beam inside the arc chamber of the ion source 11 is pulled out, a specific electric field is generated in the puller structure to provide axial electric focusing for the initial acceleration of the proton beam, thereby reducing the loss of the beam in the acceleration domain of the central area 12. When passing through the plug structure, a specific magnetic field structure is generated to provide magnetic focusing for the beam in the extraction acceleration area, thereby reducing the loss of the beam in the extraction area 15 of the central area 12, thereby improving the beam quality of the proton beam passing through the central area 12.

[0048] Referring to Figures 1 and 2 , in some embodiments, the ion source 11 is a Penning ion source 11 , which is mounted at the center of the superconducting cyclotron proton accelerator 100 and extends through the central region 12 . Thus, when a proton beam is generated in the arc chamber of the ion source 11 , it is precisely drawn into the central region 12 by the electric field of the central region 12 for acceleration.

[0049] Specifically, the ion source 11 of the main accelerator system 10 is installed in the central region 12 of the accelerator. The control system operates the ion source 11, injecting hydrogen into the arc chamber of the ion source 11. The cathode rods at both ends of the arc chamber input arc currents, generating electrons that bombard the hydrogen inside the arc chamber, thereby forming a proton plasma. Through the magnetic channel 152 of the extraction region 15, the beam is pulled into the magnetic channel 152 under the action of electrostatic deflection plates 151. The specific magnetic field structure of the magnetic channel 152 increases the axial focusing of the extraction, thereby obtaining a high-quality proton beam. The establishment of two symmetrical magnetic channels 152 structures can improve the first harmonic of the accelerator's magnetic field, thereby effectively improving the centering of the beam at the center of the particle motion orbit during the acceleration process.

[0050] Referring to Figures 1 and 3 , in certain embodiments, the superconducting cyclotron proton accelerator 100 further includes a three-dimensional movable platform 40, on which the ion source 11 is mounted. The three-dimensional movable platform 40 is used to adjust the angular position and axial height of the ion source 11 to improve the extraction efficiency of the ion source beam 11. Thus, the three-dimensional movable platform 40 is used to adjust the angular position and axial height of the ion source 11 to improve the extraction efficiency of the ion source beam 11.

[0051] Referring to Figures 4 and 5 , in certain embodiments, the main accelerator system 10 further includes vertical deflection plates 16 disposed in the central region 12. These plates are configured to generate an electric field to precisely adjust the beam's axial position. In this case, the plates 16 can be a pair of symmetrical high-voltage electrodes. When the power supply is operating, an electric field is formed between the plates 16. This electric field can be adjusted by varying the high-voltage input voltage. This allows for precise adjustment of the beam's axial position and the intensity of the beam extracted from the central region 12. Furthermore, rapid beam shutoff is possible.

[0052] Specifically, the power supply system 21 may also include a power supply that can be connected to the ion source 11 and power the ion source. Simultaneously, the current of the cathode power supply can be adjusted to achieve regulation of the intensity of the beam extracted from the ion source 11. The ion source 11 is mounted on a three-dimensional movable platform 40, which can be used to adjust the angular position and axial height of the ion source 11 to better match the electromagnetic field, thereby improving the extraction efficiency of the ion source 11 beam.

[0053] Furthermore, the material of the vertical deflection plate 16 can be oxygen-free copper, and the vertical deflection plate 16 is also connected to a power supply. When the power supply is working, an electric field can be formed in the middle of the vertical deflection plate 16, and the electric field can be adjusted by adjusting the high-voltage input of different values. Its function is to achieve precise adjustment of the axial position of the beam and precise adjustment of the beam current intensity drawn out of the central area 12, and it can also achieve the function of quickly shutting down the beam.

[0054] For example, by adjusting the current of the cathode power supply of the ion source 11, the coarse adjustment of the extracted beam current intensity is achieved, and by coordinating the voltage adjustment of the vertical deflection plate 16 on the central area 12, the fine adjustment of the extracted beam current intensity is achieved. Through the coordination of the above two components, the extracted beam current intensity can be finely adjusted.

[0055] Referring to Figures 1 and 2 , in certain embodiments, the superconducting magnet system 13 includes superconducting coils 131 , which are connected to an electric current to generate a specific static magnetic field. This current can be fed into the superconducting coils 131 , generating a magnetic field that, in turn, constrains the trajectory of the proton beam, ensuring stable delivery of the proton beam to the accelerator.

[0056] Specifically, the superconducting cyclotron proton accelerator 100 utilizes superconducting technology to design a superconducting magnet system 13, significantly reducing the overall weight and size of the superconducting cyclotron proton accelerator 100, reducing the floor space required for the superconducting cyclotron proton accelerator 100, and lowering the manufacturing and construction costs of the superconducting cyclotron proton accelerator 100. The superconducting magnet system 13 comprises superconducting coils 131, magnets 132, and magnetic poles 133. The accelerator control system 30 operates the power supply system 21 to supply current to the superconducting coils 131, generating a specific static magnetic field on the surface of the magnetic poles 133. This constrains the accelerated motion of the beam within the superconducting cyclotron proton accelerator 100 and creates a magnetic loop within the magnets 132, reducing magnetic leakage within the superconducting cyclotron proton accelerator 100.

[0057] Referring to Figures 2 and 4 , in certain embodiments, the superconducting coil 131 utilizes double-zero-volatility liquid helium cooling technology. This technology allows the superconducting coil 131 to be cooled with only a minimal amount of liquid helium during operation, minimizing the risk of liquid helium expanding during a quench and reducing losses during the conversion to helium gas.

[0058] Referring to FIG. 1 , in certain embodiments, the superconducting magnet system 13 further includes a rapid demagnetizer (not shown) configured to demagnetize the superconducting coils 131. This allows the rapid demagnetizer to demagnetize the magnet within a short period of time after an unexpected quench, rapidly transferring and discharging the energy within the magnet to the outside, thereby ensuring the safety of the entire superconducting magnet system.

[0059] In some embodiments, the superconducting magnet system 13 employs a quad-spiral fan distribution and an elliptical arc surface design, effectively improving the axial focusing performance of the proton beam and reducing axial losses during the acceleration process. Furthermore, the superconducting magnet system 13 can maintain a symmetrical design as much as possible to reduce the impact of the native harmonic magnetic field on the proton beam's trajectory. Furthermore, a movable small magnet is introduced to actively control the impact of the harmonic magnetic field on the proton beam's trajectory, ensuring that the proton beam's trajectory conforms to the intended design.

[0060] Referring to Figures 1 and 2 , in certain embodiments, the RF system 14 includes an RF source and an RF cavity. The RF source feeds power into the RF cavity, generating a high-frequency voltage within the cavity. The RF source then transmits a high-frequency electrical signal to the cavity, generating a high-frequency voltage within the cavity, thereby providing an accelerating environment for the proton beam.

[0061] In some embodiments, the RF cavity includes a first cavity and a second cavity (not shown in the figure), which are independent of each other and are connected to separate power sources. In this way, the two RF cavities can be independently regulated by a separate power source, which can reduce the operating pressure of the power source at full power, improve the operating stability of the RF cavity, and also reduce the risk of ignition of the RF cavity. In addition, the phase coupling between the two cavities can also be adjusted separately to obtain better acceleration efficiency.

[0062] In the embodiment of the present application, by designing a four-spiral fan distribution, the radio frequency cavity is designed with two separate cavities to form a four-pole two-cavity layout. The other two cavities can be used for functional expansion, and pipelines required for other accelerator operations or components susceptible to high-frequency electric fields can be arranged, thereby improving the flexibility of the accelerator design. The main magnet maintains a symmetrical design as much as possible to reduce the impact of the native harmonic magnetic field on the proton beam orbit. At the same time, a movable small magnet is introduced to actively control the impact of the harmonic magnetic field on the proton beam orbit, so that the motion orbit of the proton beam conforms to the expected design; the radio frequency cavity adopts a two-cavity separation design, which is connected to a separate power source respectively, and can realize separate regulation of the two radio frequency cavities, reducing the operating pressure of the power source, improving the operating stability of the radio frequency cavity, and can also adjust the phase coupling between the two cavities separately to obtain better acceleration efficiency. In addition, only one electrostatic deflection plate and three magnetic focusing structures are used for extraction, with a small number of components, a simple structure, and easy adjustment, which reduces the difficulty of adjusting the beam extraction.

[0063] Specifically, the superconducting cyclotron proton accelerator 100 uses a radio frequency cavity to design two accelerating cavities, which can reduce the cost of the radio frequency source, accelerate the phase coupling between the cavities, and improve the acceleration efficiency of the protons. When the frequency of the radio frequency cavity is set at 77.8MHz, the protons are accelerated by second harmonics to ensure that the energy of the proton beam ultimately reaches 240MeV. After isochronous padding of the magnetic pole 133, the overall phase slip of the proton beam when it is accelerated to the extraction area 15 is less than ±20°, ensuring that the proton beam can be accelerated normally. Due to the characteristics of the two accelerating cavities, it is convenient to subsequently expand the function in the valley area of ​​the magnet 132, thereby improving the flexibility of the accelerator design.

[0064] 1 , in some embodiments, the accelerator auxiliary system 20 includes a power supply system 21 that provides power to the subsystem devices. Thus, the power supply system 21 can provide electrical energy to the subsystem devices to ensure stable power supply to the superconducting cyclotron proton accelerator 100.

[0065] Referring to FIG1 , in some embodiments, the accelerator auxiliary system 20 further includes a water cooling system 22, which cools the subsystems of the main accelerator system 10. Thus, the water cooling system 22 can cool each subsystem via circulating water to ensure stable operation of the superconducting cyclotron proton accelerator 100.

[0066] 1 , in some embodiments, the accelerator auxiliary system 20 further includes a vacuum system 23, which provides a vacuum environment within the superconducting cyclotron proton accelerator 100. This allows the proton beam to move in a vacuum, preventing impurity molecules in the air from affecting the proton beam.

[0067] Specifically, the vacuum system 23 provides a vacuum environment for proton beam generation, acceleration, and extraction. The power supply system 21 provides current to the main accelerator system 10 and auxiliary systems. The water cooling system 22 is used to cool the accelerator's subsystems during operation. The accelerator control system 30 operates the subsystems of the main accelerator system 10 to regulate the proton beam and monitors the operating status of each subsystem to minimize equipment failures.

[0068] In the description of the embodiments of this application, the terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly specifying the number of the indicated technical features. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include one or more of the described features. In the description of the embodiments of this application, the meaning of "plurality" is two or more, unless otherwise clearly and specifically defined.

[0069] Throughout this specification, reference to terms such as "one embodiment," "some embodiments," "illustrative embodiments," "examples," "specific examples," or "some examples" means that a specific feature, structure, material, or characteristic described in conjunction with the embodiment or example is included in at least one embodiment or example of the present application. In this specification, the schematic representations of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples.

[0070] Although the embodiments of the present application have been shown and described above, it can be understood that the above embodiments are exemplary and cannot be understood as limitations on the present application. Ordinary technicians in this field can change, modify, replace and modify the above embodiments within the scope of the present application.

Claims

1. A superconducting cyclotron proton accelerator, wherein: The superconducting cyclotron proton accelerator comprises: A main accelerator system, comprising an ion source, a central region, a superconducting magnet system, a radio frequency system and an extraction region, wherein the ion source is used to generate a proton beam, the central region is used to extract the proton beam of the ion source and perform beam focusing inside the central region, the radio frequency system extracts and accelerates the central region beam, the static magnetic field generated by the superconducting magnet system can constrain the proton beam during the proton beam acceleration process and accelerate it to a target energy, and the extraction region can extract the proton beam; An accelerator auxiliary system, used for providing stable operating conditions for the main accelerator system when accelerating the proton beam and providing a vacuum environment when accelerating the proton beam; The accelerator control system is used to operate the various subsystems of the main accelerator system, adjust the stability of the proton beam acceleration motion, and effectively monitor the current status of each subsystem.

2. The superconducting cyclotron proton accelerator according to claim 1, wherein: The extraction region confines the proton beam by magnetic focusing.

3. The superconducting cyclotron proton accelerator according to claim 1, wherein: The target energy of the proton beam after passing through the extraction region is 230-250 MeV.

4. The superconducting cyclotron proton accelerator according to claim 1, wherein: The central area is a raised metal structure, which is installed at the central position of the superconducting cyclotron proton accelerator. The central area provides axial electric focusing and constrains the trajectory movement of the proton beam passing through the central area, thereby reducing the loss of the proton beam.

5. The superconducting cyclotron proton accelerator according to claim 4, wherein: The ion source is a Penning ion source, which is installed at the center of the superconducting cyclotron proton accelerator and runs through the center area.

6. The superconducting cyclotron proton accelerator according to claim 4, wherein: The superconducting cyclotron proton accelerator also includes a three-dimensional mobile platform, and the ion source is mounted on the three-dimensional mobile platform. The angular position and axial height position of the ion source are adjusted by the three-dimensional mobile platform to improve the extraction efficiency of the ion source beam.

7. The superconducting cyclotron proton accelerator according to claim 4, wherein: The main accelerator system further includes a vertical deflection plate disposed in the central region, wherein the vertical deflection plate is configured to generate an electric field to achieve precise adjustment of the axial position of the beam.

8. The superconducting cyclotron proton accelerator according to claim 1, wherein: The superconducting magnet system includes a superconducting coil, and an electric current is connected to the superconducting coil to generate a specific static magnetic field.

9. The superconducting cyclotron proton accelerator according to claim 8, wherein: The superconducting coil is realized by using double zero-volatile liquid helium cooling technology.

10. The superconducting cyclotron proton accelerator according to claim 8, wherein: The superconducting magnet system further includes a rapid demagnetizer configured to achieve demagnetization of the superconducting coil.

11. The superconducting cyclotron proton accelerator according to claim 1, wherein: The radio frequency system includes a radio frequency source and a radio frequency cavity. The radio frequency source feeds power into the radio frequency cavity, so that a high frequency voltage is generated inside the radio frequency cavity.

12. The superconducting cyclotron proton accelerator according to claim 1, wherein: The radio frequency cavity comprises a first cavity and a second cavity, wherein the first cavity and the second cavity are independent of each other and are respectively connected to separate power sources.

13. The superconducting cyclotron proton accelerator according to claim 1, wherein: The accelerator auxiliary system includes a power supply system, which provides power to subsystem devices.

14. The superconducting cyclotron proton accelerator according to claim 1, wherein: The accelerator auxiliary system also includes a water cooling system, which cools down the subsystems of the main accelerator system.

15. The superconducting cyclotron proton accelerator according to claim 1, wherein: The accelerator auxiliary system also includes a vacuum system, which provides a vacuum environment inside the superconducting cyclotron proton accelerator.

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