CN117177428B - Superconducting cyclotron proton accelerator - Google Patents
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Abstract
The application discloses a superconducting cyclotron, which comprises a main accelerator system, an accelerator auxiliary system and an accelerator control system. The main accelerator system comprises an ion source, a central area, a superconducting magnet system, a radio frequency system and an extraction area, wherein the ion source is used for generating proton beam, the central area is used for extracting the proton beam of the ion source and focusing the beam in the central area, the radio frequency system extracts and accelerates the beam in the central area, a static magnetic field generated by the superconducting magnet system can restrain and accelerate the proton beam to target energy in the acceleration process of the proton beam, and the extraction area can extract the proton beam. In this way, the main accelerator system is used for generating proton beam and accelerating the proton beam to target energy, the beam is strong in energy and good in quality, the extracted proton energy meets the treatment requirement of more than 90% of cancer types in proton treatment, the accelerator structure is compact, and the equipment manufacturing cost and the integration space can be effectively reduced.
Description
Technical Field
The present application relates to the technical field of medical devices, and more particularly, to a superconducting cyclotron proton accelerator.
Background
Currently, the types of accelerators used for proton therapy are largely classified into three types of isochronous cyclotrons, synchrocyclotrons, and synchrocyclotrons. The isochronous cyclotron uses the mutual matching of the particle cyclotron frequency of a static magnetic field and the frequency of a fixed radio frequency electric field to realize particle acceleration, while the synchrotron needs a variable magnetic field and the frequency of a mobilizing electric field to realize particle acceleration, which is obviously insufficient for the isochronous cyclotron in terms of volume, construction and maintenance. The synchrocyclotron has the same compact characteristic as the isochronic cyclotron, and can effectively reduce the manufacturing cost, but because the electric field of the synchrocyclotron needs to be modulated, the extracted beam is pulsed, and compared with the continuous beam of the isochronic cyclotron, the dose of the beam is greatly reduced in the aspect of treatment effect. Therefore, the isochronous cyclotron has incomparable advantages for proton treatment, but the design difficulty of the isochronous cyclotron is high due to the complex physical structure design and high magnetic field requirement precision, and the isochronous cyclotron is also a reason for preventing the further development of the domestic accelerator.
Disclosure of Invention
Embodiments of the present application provide a superconducting cyclotron.
The superconducting cyclotron of an embodiment of the present application includes:
the main accelerator system comprises an ion source, a central area, a superconducting magnet system, a radio frequency system and an extraction area, wherein the ion source is used for generating proton beam, the central area is used for extracting the proton beam of the ion source and focusing the beam in the central area, the radio frequency system extracts and accelerates the beam in the central area, the static magnetic field generated by the superconducting magnet system can restrict and accelerate the proton beam to target energy in the proton beam acceleration process, and the extraction area can extract the proton beam;
an accelerator auxiliary system for providing a stable operation condition for the main accelerator system when accelerating the proton beam and providing a vacuum environment when accelerating the proton beam for the main accelerator system;
and the accelerator control system is used for operating each subsystem of the main accelerator system, adjusting the stability of the acceleration motion of the proton beam and effectively monitoring the current state of each subsystem.
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 comprises an ion source, a central area, a superconducting magnet system, a radio frequency system and an extraction area, wherein the ion source is used for generating proton beam, the central area is used for extracting the proton beam of the ion source and focusing the beam in the central area, the radio frequency system extracts and accelerates the beam in the central area, a static magnetic field generated by the superconducting magnet system can restrict and accelerate the proton beam to target energy in the acceleration process of the proton beam, and the extraction area can extract the proton beam; the accelerator auxiliary system is used for providing stable operation conditions for the main accelerator system when accelerating the proton beam and providing a vacuum environment when accelerating the proton beam for the main accelerator system; the accelerator control system is used for operating each subsystem of the main accelerator system, adjusting the stability of the acceleration motion of the proton beam and effectively monitoring the current state of each subsystem. Therefore, the superconducting cyclotron proton accelerator can generate proton beam through the main accelerator system, accelerate the proton beam to target energy, has strong beam current and good quality, and can lead out the proton energy to meet the treatment requirement of more than 90% of cancer types in proton treatment, so that the accelerator has compact structure, and can effectively reduce the equipment manufacturing cost and the integration space.
In certain embodiments, the extraction region constrains the proton beam current by magnetic focusing. Therefore, the extraction area can focus the proton beam through the magnetic field, so that the proton beam is restrained, and the stability and the accuracy of the proton beam can be kept.
In some embodiments, the target energy after the proton beam passes through the extraction zone is between 230 and 250MeV. Therefore, the energy of the proton beam after being led out by the leading-out area can be accelerated to 230-250MeV, the energy of the proton beam is strong, the quality is good, and the treatment requirement of more than 90% of cancer types in proton treatment can be met.
In some embodiments, the central region is a raised metal structure, the central region is mounted at a central position of the superconducting cyclotron, the central region provides axial electric focusing and constrains proton beam trajectory motion through the central region, reducing proton beam losses. Therefore, the central region can generate a specific electric field structure, axial electric focusing is provided to restrain the beam track movement of the central region, the loss of proton beam is reduced, and the energy stability of the proton beam is ensured.
In certain embodiments, the ion source is a penning ion source mounted at a central location of the superconducting cyclotron, the ion source extending through the central zone. Thus, when the ion source arc chamber generates proton beam current, the proton beam current can be just accelerated by being pulled to the inside of the central region by the electric field of the central region.
In some embodiments, the superconductive cyclotron further comprises a three-dimensional moving platform, the ion source is mounted on the three-dimensional moving platform, and the angular position and the axial height position of the ion source are adjusted through the three-dimensional moving platform, so that extraction efficiency of the ion source beam current is improved. Therefore, the angle position and the axial height position of the ion source are adjusted through the three-dimensional moving platform, so that the extraction efficiency of the beam of the ion source is improved.
In certain embodiments, the main accelerator system further comprises a vertical deflector plate disposed in the central region, the vertical deflector plate configured to generate an electric field to effect precise adjustment of beam axial position. Thus, the vertical deflection plates can be symmetrical high-voltage electrodes, and when the power supply works, an electric field is formed in the middle of the vertical deflection plates, and the electric field can be adjusted by adjusting high-voltage inputs with different values. Therefore, the beam axial position can be accurately adjusted, the beam intensity can be accurately adjusted when the beam is led out from the central area, and the beam rapid turn-off function can be realized.
In certain embodiments, the superconducting magnet system includes a superconducting coil that is energized with a current to generate a particular static magnetic field. Therefore, current can be fed into the superconducting coil, the superconducting coil can generate a magnetic field under the action of the current, and the movement track of the proton beam is further restrained, so that the proton beam can be stably output to the outside of the accelerator.
In certain embodiments, the superconducting coils are implemented using a liquid helium cooling technique with double zero volatilization. Therefore, by the liquid helium cooling technology, the superconducting working state can be cooled by only a very small amount of liquid helium, so that the risk of converting the liquid helium into helium to expand under the condition of sudden quench is reduced, and the loss of converting the liquid helium into helium under the condition of sudden quench is reduced.
In certain embodiments, the superconducting magnet system further comprises a fast demagnetizer configured to effect demagnetization of the superconducting coil. Therefore, the rapid demagnetizer can complete demagnetization of the magnet in a short time after unexpected quench, and rapidly transfer and release the energy in the magnet to the outside so as to ensure the safety of the whole superconducting magnet system.
In certain embodiments, the radio frequency system includes a radio frequency source and a radio frequency cavity, the radio frequency source feeding power into the radio frequency cavity such that a high frequency voltage is generated within the radio frequency cavity. Therefore, the radio frequency source can emit high-frequency electric signals to the radio frequency cavity, so that the radio frequency cavity generates high-frequency voltage, and an acceleration environment is provided for proton beam current.
In some embodiments, the radio frequency cavity comprises a first cavity and a second cavity, the first cavity and the second cavity being independent of each other and being connected to separate power sources, respectively. Therefore, the independent regulation and control of the two radio frequency cavities can be realized through the independent power source, so that the operating pressure of the power source under full power can be reduced, the operating stability of the radio frequency cavities is improved, and the sparking risk of the radio frequency cavities is reduced. In addition, the phase coupling between the two cavities can be independently adjusted to obtain better acceleration efficiency.
In certain embodiments, the accelerator assist system includes a power supply system that provides power to subsystem devices. In this way, the power supply system can provide electric energy for subsystem equipment so as to ensure the power supply stability of the superconducting cyclotron.
In certain embodiments, the accelerator assist system further comprises a water cooling system that cools a subsystem of the main accelerator system. Therefore, the water cooling system can cool down all subsystems through circulating water so as to ensure the stable operation of the superconducting cyclotron proton accelerator.
In certain embodiments, the accelerator assistance system further comprises a vacuum system that provides a vacuum environment for the interior of the superconducting cyclotron. In this way, the proton beam can move in vacuum to avoid the influence of impurity molecules in the air on the proton beam.
Additional aspects and advantages of the application will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the application.
Drawings
The foregoing and/or additional aspects and advantages of the present application will become apparent and readily appreciated from the following description of the embodiments, taken in conjunction with the accompanying drawings, in which:
FIG. 1 is a schematic block diagram of a superconducting cyclotron according to an embodiment of the present application;
FIG. 2 is a schematic structural view of a superconducting cyclotron according to an embodiment of the present application;
FIG. 3 is another schematic structural view of a superconducting cyclotron according to an embodiment of the present application;
FIG. 4 is a schematic diagram of yet another configuration of a superconducting cyclotron according to an embodiment of the present application;
fig. 5 is a schematic view of still another structure of the superconducting cyclotron according to the embodiment of the present application.
Description of main reference numerals:
a superconducting cyclotron 100;
the main accelerator system 10, the ion source 11, the central region 12, the superconducting magnet system 13, the superconducting coils 131, the magnets 132, the magnetic poles 133, the radio frequency system 14, the extraction region 15, the electrostatic deflection plates 151, the magnetic flux channels 152, the vertical deflection plates 16, the accelerator auxiliary system 20, the power supply system 21, the water cooling system 22, the vacuum system 23, the accelerator control system 30, and the three-dimensional moving platform 40.
Detailed Description
Embodiments of the present application are described in detail below, examples of which are illustrated in the accompanying drawings, wherein the same or similar reference numerals refer to the same or similar elements or elements having the same or similar functions throughout. The embodiments described below by referring to the drawings are exemplary only for the purpose of explaining the present application and are not to be construed as limiting the present application.
In this application, unless expressly stated or limited otherwise, a first feature "above" or "below" a second feature may include both the first and second features being in direct contact, and may also include the first and second features not being in direct contact but being in contact with each other by way of additional features therebetween. Moreover, a first feature being "above," "over" and "on" a second feature includes the first feature being directly above and obliquely above the second feature, or simply indicating that the first feature is higher in level than the second feature. The first feature being "under", "below" and "beneath" the second feature includes the first feature being directly under and obliquely below the second feature, or simply means that the first feature is less level than the second feature.
The following disclosure provides many different embodiments or examples for implementing different structures of the present application. In order to simplify the disclosure of the present application, the components and arrangements of specific examples are described below. Of course, they are merely examples and are not intended to limit the present application. Furthermore, the present application may repeat reference numerals and/or letters in the various examples, which are for the purpose of brevity and clarity, and which do not in themselves indicate a relationship between the various embodiments and/or settings discussed. In addition, the present application provides examples of various specific processes and materials, but one of ordinary skill in the art may recognize the application of other processes and/or the use of other materials.
Referring to fig. 1 and 2, a superconducting cyclotron proton accelerator 100 according to an embodiment of the present application includes a main accelerator system 10, an accelerator auxiliary system 20, and an accelerator control system 30, where 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 for generating a proton beam, the central region 12 is used for extracting the proton beam of the ion source 11, and focusing the beam in the central region 12, the radio frequency system 14 extracts and accelerates the beam in the central region 12, a static magnetic field generated by the superconducting magnet system 13 can constrain and accelerate the proton beam to a target energy during acceleration of the proton beam, and the extraction region 15 can extract the proton beam. The accelerator assist system 20 is used to provide the main accelerator system 10 with stable operating conditions while accelerating the proton beam and a vacuum environment while 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 state of the various subsystems.
In the superconducting cyclotron 100 of the present embodiment, the superconducting cyclotron 100 includes a main accelerator system 10, an accelerator auxiliary system 20, and an accelerator control system 30. The main accelerator system 10 comprises an ion source 11, a central region 12, a superconducting magnet system 13, a radio frequency system 14 and an extraction region 15, wherein the ion source 11 is used for generating proton beam, the central region 12 is used for extracting the proton beam of the ion source 11 and focusing the beam in the central region 12, the radio frequency system 14 is used for extracting and accelerating the beam in the central region 12, the static magnetic field generated by the superconducting magnet system 13 can restrict and accelerate the proton beam to target energy in the process of accelerating the proton beam, and the extraction region 15 can extract the proton beam; the accelerator auxiliary system 20 is used for providing a stable operation condition for the main accelerator system 10 when accelerating the proton beam and providing 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 system 10, adjust the stability of the proton beam acceleration motion, and effectively monitor the current state of the various subsystems. In this way, the superconducting cyclotron 100 can generate proton beam through the main accelerator system 10, accelerate the proton beam to target energy, have strong beam current and good quality, and lead out proton energy to meet the requirement of more than 90% of cancer type treatment in proton treatment, so that the accelerator has compact structure, and can effectively reduce the manufacturing cost and the integration space of equipment.
Specifically, the main accelerator system 10 can generate a proton beam through the ion source 11, and accelerate the proton beam through other subsystems, so that the beam is stably accelerated to 230-250MeV from a low energy stage and then led out to a high energy transport line, finally reaches a treatment head, and carries out proton treatment on a cancer patient. The accelerator auxiliary system 20 provides a vacuum environment for the main accelerator system 10 to provide stable operation conditions for the accelerator when accelerating the proton beam and for the beam to accelerate; the accelerator control system 30 is used to operate the various subsystems of the main accelerator, adjust the stability of beam acceleration motion, and effectively monitor the current state of the various subsystems.
In the related art, the types of accelerators used for proton therapy are largely classified into three types of isochronous cyclotrons, synchrocyclotrons, and synchrocyclotrons. The isochronous cyclotron uses the mutual matching of the particle cyclotron frequency of a static magnetic field and the frequency of a fixed radio frequency electric field to realize particle acceleration, while the synchrotron needs a variable magnetic field and the frequency of a mobilizing electric field to realize particle acceleration, which is obviously insufficient for the isochronous cyclotron in terms of volume, construction and maintenance. The synchrocyclotron has the same compact characteristic as the isochronic cyclotron, and can effectively reduce the manufacturing cost, but because the electric field of the synchrocyclotron needs to be modulated, the extracted beam is pulsed, and compared with the continuous beam of the isochronic cyclotron, the dose of the beam is greatly reduced in the aspect of treatment effect. Thus, the method is applicable to a variety of applications. Isochronous cyclotrons have incomparable advantages for proton therapy, however, due to the complex physical structure design, the magnetic field requires high precision, resulting in great difficulty in designing isochronous cyclotrons.
In this embodiment, the central area 12 is configured to draw out and accelerate the proton beam of the ion source 11, and a specific electric field is generated by a puller structure inside the central area 12 and a specific magnetic field is generated by a plug structure to perform beam focusing, so as to finally improve the quality and beam intensity of the accelerated beam passing through the central area 12; the radio frequency system 14 accelerates to provide acceleration cavity pressure for the radio frequency cavity, so that the proton beam is accelerated to 230-250MeV; the superconducting magnet system 13 is used for generating a static magnetic field, so that the beam is restrained and accelerated to target energy in the acceleration process, and finally reaches the extraction area 15; the extraction region 15 includes an electrostatic deflector 151 and a magnetic channel 152 for completing extraction of the beam from the extraction region 15.
Referring to fig. 1 and 2, in some embodiments, the extraction region 15 constrains the proton beam current by magnetic focusing. In this way, the extraction region 15 can focus the proton beam through the magnetic field, and further restrict the proton beam, so that the proton beam can maintain stability and accuracy.
Further referring to fig. 1 and 2, in some embodiments, the target energy after the proton beam passes through the extraction zone 15 is between 230 and 250MeV. For example, the target energy of the proton beam stream after passing through the extraction zone 15 may be 230MeV, 231MeV, 232MeV, 233MeV, 234MeV, 235MeV, 236MeV, 237MeV, 238MeV, 239MeV, 240MeV, 241MeV, 242MeV, 243MeV, 244MeV, 245MeV, 246MeV, 247MeV, 248MeV, 249MeV, 250MeV.
In this way, the energy of the proton beam after being led out through the leading-out area 15 can be accelerated to 230-250MeV, the energy of the proton beam is strong, the quality is good, and the treatment requirement of more than 90% of cancer types in proton treatment can be met. Preferably, the energy of the proton beam after extraction from the extraction zone 15 can be accelerated to 240MeV, so that the extraction zone 15 provides a steady energy flow intensity for proton treatment of cancer patients.
Specifically, the extraction system includes an electrostatic deflector 151 and a magnetic channel 152, and the beam in the extraction area 15 is stripped and extracted by the electrostatic electric field generated by the classical deflector, and the quality and the beam intensity of the beam extraction are improved under the effect of axial magnetic focusing provided by the magnetic channel 152.
Referring to fig. 1 and 2, in some embodiments, the central region 12 is a convex metal structure, the central region 12 is mounted at the central position of the superconducting cyclotron 100, the central region 12 provides axial electric focusing and constrains the proton beam trajectory motion through the central region 12, reducing the proton beam loss. In this way, the central region 12 can generate a specific electric field structure to provide axial electric focusing to restrict the beam track movement of the central region 12, reduce the loss of proton beam and ensure the energy stability of the proton beam.
Specifically, the central region 12 of the main accelerator system 10 includes a de tip, a Dummy, a plug structure, and a plug structure, which are installed in the central region 12 region of the superconducting cyclotron proton accelerator 100, and are used for extracting and accelerating proton plasmas in the arc chamber of the ion source 11, during the acceleration process of the central region 12, a specific electric field structure and a specific magnetic field are generated in the central region 12 region of the accelerator by designing the puller and the plug structure of the central region 12, when the proton beam in the arc chamber of the ion source 11 is pulled out, axial electric focusing is provided when the puller structure generates a specific electric field to initially accelerate the proton beam, loss of the beam in the accelerating region of the central region 12 is reduced, and when the plug structure passes through, a specific magnetic field structure is generated to magnetically focus the beam in the extracting accelerating region, loss of the beam in the extracting region 15 region of the central region 12 is reduced, so that the beam quality of the proton beam passing through the central region 12 is improved.
Referring to fig. 1 and 2, in some embodiments, the ion source 11 is a penning ion source 11, the ion source 11 is mounted at the center of the superconducting cyclotron 100, and the ion source 11 extends through the central region 12. In this way, when the ion source 11 generates proton beam current, the proton beam current can be just accelerated by the electric field of the central region 12 drawn to the inside of the central region 12.
Specifically, the ion source 11 of the main accelerator system 10 is installed at the position of the central area 12 of the accelerator, the ion source 11 is operated by the control system, hydrogen is injected into the arc chamber of the ion source 11, the opposite cathode rods at two ends of the arc chamber input arc flow, electrons are generated for bombarding the hydrogen in the arc chamber, and thus proton plasma is generated. Through the magnetic channel 152 of the extraction area 15, the beam is drawn to the magnetic channel 152 under the action of the electrostatic deflector 151, and the axial focusing property of extraction is increased under the specific magnetic field structure of the magnetic channel 152, so that high-quality proton beam is obtained. The two symmetrical magnetic channels 152 are arranged, so that the first harmonic of the magnetic field of the accelerator can be improved, and the centering of the center of the particle motion orbit of the beam in the acceleration process can be effectively improved.
Referring to fig. 1 and 3, in some embodiments, the superconducting cyclotron proton accelerator 100 further includes a three-dimensional moving platform 40, the ion source 11 is mounted on the three-dimensional moving platform 40, and the angular position and the axial height position of the ion source 11 are adjusted by the three-dimensional moving platform 40 to improve the extraction efficiency of the beam current of the ion source 11. In this way, the adjustment of the angular position and the axial height position of the ion source 11 is achieved by the three-dimensional moving platform 40 to improve the extraction efficiency of the beam of the ion source 11.
Referring to fig. 4 and 5, in some embodiments, the main accelerator system 10 further includes a vertical deflector 16 disposed in the central region 12, the vertical deflector 16 configured to generate an electric field to achieve precise adjustment of the beam axial position. Thus, the vertical deflection plates 16 may be symmetrical high voltage electrodes, and when the power supply is in operation, an electric field is formed between the vertical deflection plates 16, and the adjustment of the electric field may be achieved by adjusting the high voltage inputs to different values. Thus, the accurate adjustment of the axial position of the beam current and the accurate adjustment of the intensity of the beam current led out of the central area 12 can be realized, and in addition, the rapid turn-off function of the beam current can be realized.
Specifically, the power supply system 21 may further include a power source that may be coupled to and power the ion source 11. Meanwhile, the current of the cathode power supply can be adjusted to realize the function of adjusting the beam intensity of the ion source 11. The ion source 11 is arranged on the three-dimensional moving platform 40, and the adjustment of the angle position and the axial height position of the ion source 11 is realized through the three-dimensional moving platform 40 so as to better match an electromagnetic field, thereby improving the extraction efficiency of the beam current of the ion source 11.
Further, the vertical deflection plate 16 may be made of oxygen-free copper, the vertical deflection plate 16 is also connected with a power supply, an electric field can be formed in the middle of the vertical deflection plate 16 when the power supply works, and the electric field can be adjusted by adjusting high-voltage inputs with different values.
Illustratively, the current of the cathode power supply of the ion source 11 is adjusted to realize coarse adjustment of the intensity of the extracted beam, and the voltage of the vertical deflection plate 16 on the central area 12 is adjusted in a matching manner to realize fine adjustment of the intensity of the extracted beam.
Referring to fig. 1 and 2, in some embodiments, superconducting magnet system 13 includes superconducting coils 131, superconducting coils 131 being energized with a current to generate a particular static magnetic field. In this way, current can be fed into the superconducting coil 131, the superconducting coil 131 can generate a magnetic field under the action of the current, so that the movement track of the proton beam is restrained, and the proton beam can be stably output to the outside of the accelerator.
Specifically, the superconducting cyclotron 100 is designed to use the superconducting technology to design the superconducting magnet system 13, so that the overall weight of the superconducting cyclotron 100 and the size of the superconducting cyclotron 100 are greatly reduced, the occupied area of the superconducting cyclotron 100 required to be placed is reduced, and the cost of manufacturing and occupied area construction of the superconducting cyclotron 100 is reduced. The superconducting magnet system 13 comprises a superconducting coil 131, a magnet 132 and a magnetic pole 133, wherein a power supply of the accelerator control system 30 operates the power supply system 21 to supply current to the superconducting coil 131, so that a specific static magnetic field is generated on the surface of the magnetic pole 133, the accelerating motion of the beam in the superconducting cyclotron 100 is restrained, a magnetic loop is generated in the magnet 132, and the magnetic leakage phenomenon of the magnetic field of the superconducting cyclotron 100 is reduced.
Referring to fig. 2 and 4, in some embodiments, superconducting coil 131 is implemented using a double zero volatilization liquid helium cooling technique. Therefore, by the liquid helium cooling technology, the superconducting working state can be cooled by only a very small amount of liquid helium, so that the risk of converting the liquid helium into helium to expand under the condition of sudden quench is reduced, and the loss of converting the liquid helium into helium under the condition of sudden quench is reduced.
Referring to fig. 1, in some embodiments, superconducting magnet system 13 further includes a fast demagnetizer (not shown in the figures) configured to effect demagnetization of superconducting coil 131. Therefore, the rapid demagnetizer can complete demagnetization of the magnet in a short time after unexpected quench, and rapidly transfer and release the energy in the magnet to the outside so as to ensure the safety of the whole superconducting magnet system.
In some embodiments, the superconducting magnet system 13 adopts a design of four-spiral fan distribution and an elliptical cambered surface, so that the axial focusing performance of the proton beam is effectively improved, and the axial loss of the proton beam in the acceleration process can be reduced. Meanwhile, the superconducting magnet system 13 can keep a symmetrical design as far as possible, so that the influence of a primary harmonic magnetic field on the proton beam running track is reduced, and meanwhile, a movable small magnet is introduced, so that the influence of the harmonic magnetic field on the proton beam running track is actively controlled, and the proton beam running track accords with the expected design.
Referring to fig. 1 and 2, in some embodiments, the rf system 14 includes an rf source and an rf cavity, the rf source feeding power into the rf cavity such that a high frequency voltage is generated within the rf cavity. Therefore, the radio frequency source can emit high-frequency electric signals to the radio frequency cavity, so that the radio frequency cavity generates high-frequency voltage, and an acceleration environment is provided for proton beam current.
In some embodiments, the radio frequency cavity includes a first cavity and a second cavity (not shown in the figures) that are independent of each other and are each connected to a separate power source. Therefore, the independent regulation and control of the two radio frequency cavities can be realized through the independent power source, so that the operating pressure of the power source under full power can be reduced, the operating stability of the radio frequency cavities is improved, and the sparking risk of the radio frequency cavities is reduced. In addition, the phase coupling between the two cavities can be independently adjusted to obtain better acceleration efficiency.
In this application embodiment, through design four spiral fan distributions, two disconnect-type cavitys of radio frequency cavity design form four magnetic pole two-chamber overall arrangement, can carry out the function extension in two other cavitys, arrange other required pipeline of accelerator operation or easily receive the part of high frequency electric field influence, promoted the flexibility of accelerator design. The main magnet is designed as symmetrically as possible, so that the influence of a primary harmonic magnetic field on the proton beam running track is reduced, meanwhile, a movable small magnet is introduced, and the influence of the harmonic magnetic field on the proton beam running track is actively controlled, so that the proton beam running track accords with the expected design; the radio frequency cavity adopts a two-cavity separation design, is respectively connected with an independent power source, can realize independent regulation and control of the two radio frequency cavities, reduces the operating pressure of the power source, improves the operating stability of the radio frequency cavity, and can also independently regulate the phase coupling between the two cavities so as to obtain better acceleration efficiency. In addition, only 1 electrostatic deflection plate and 3 magnetic focusing structures are used for extraction, so that the number of components is small, the structure is simple, the adjustment is convenient, and the adjustment difficulty of beam extraction is reduced.
Specifically, the superconducting cyclotron proton accelerator 100 designs 2 accelerating cavities through the radio frequency cavity, so that the cost of the radio frequency source can be reduced, the phase coupling between the accelerating cavities is realized, the accelerating efficiency of protons is improved, the protons are subjected to 2-order harmonic acceleration under the condition that the frequency of the radio frequency cavity is 77.8MHz, and the finally accelerated energy of proton beam is ensured to reach 240MeV. By the isochronal shim of the magnetic pole 133, the overall slip phase of the proton beam when accelerating to the extraction region 15 is less than +/-20 degrees, so that the proton beam can be normally accelerated. Due to the characteristics of the 2 accelerating cavities, the function expansion in the valley region of the magnet 132 is facilitated, and the flexibility of the accelerator design is improved.
Referring to fig. 1, in some embodiments, the accelerator assist system 20 includes a power supply system 21, the power supply system 21 providing power to subsystem devices. In this way, the power supply system 21 can provide electrical energy to the subsystem devices to ensure stable power supply to the superconducting cyclotron 100.
Referring to FIG. 1, in some embodiments, the accelerator assist system 20 further includes a water cooling system 22, the water cooling system 22 cooling the subsystems of the main accelerator system 10. In this manner, the water cooling system 22 may cool down the various subsystems through the circulating water to ensure stable operation of the superconducting cyclotron 100.
Referring to fig. 1, in some embodiments, the accelerator assist system 20 further comprises a vacuum system 23, the vacuum system 23 providing a vacuum environment for the interior of the superconducting cyclotron proton accelerator 100. In this way, the proton beam can move in vacuum to avoid the influence of impurity molecules in the air on the proton beam.
Specifically, vacuum system 23 provides a vacuum environment for the generation, acceleration, and extraction of proton beam current. The power supply system 21 supplies electric current to the main accelerator system 10 and the auxiliary system. The water cooling system 22 is used to cool the temperature of the various subsystem devices of the accelerator during operation. The accelerator control system 30 is used to operate subsystems of the main accelerator system 10 to achieve adjustment of proton beam current, and monitor the operation state of each subsystem through the accelerator control system 30 to reduce occurrence of equipment failure.
In the description of embodiments of the present application, the terms "first," "second," and the like are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include one or more of the described features. In the description of the embodiments of the present application, the meaning of "a plurality" is two or more, unless explicitly defined otherwise.
In the description of the present specification, reference to the terms "one embodiment," "some embodiments," "illustrative embodiments," "examples," "specific examples," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the present application. In this specification, schematic representations of the above terms do not necessarily refer to the same embodiments or examples. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples.
While embodiments of the present application have been shown and described above, it will be understood that the above embodiments are illustrative and not to be construed as limiting the present application, and that variations, modifications, alternatives, and variations may be made to the above embodiments by one of ordinary skill in the art within the scope of the present application.
Claims (12)
1. A superconducting cyclotron, comprising:
the main accelerator system comprises an ion source, a central area, a superconducting magnet system, a radio frequency system and an extraction area, wherein the ion source is used for generating proton beam, the central area is used for extracting the proton beam of the ion source and focusing the beam in the central area, the radio frequency system extracts and accelerates the beam in the central area, the static magnetic field generated by the superconducting magnet system can restrict and accelerate the proton beam to target energy in the proton beam acceleration process, and the extraction area can extract the proton beam;
an accelerator auxiliary system for providing a stable operation condition for the main accelerator system when accelerating the proton beam and providing a vacuum environment when accelerating the proton beam for the main accelerator system;
the accelerator control system is used for operating each subsystem of the main accelerator system, adjusting the stability of the acceleration motion of the proton beam and effectively monitoring the current state of each subsystem;
the target energy of the proton beam after passing through the extraction area is 230-250MeV;
the radio frequency system comprises a radio frequency source and a radio frequency cavity, wherein the radio frequency source feeds power into the radio frequency cavity so that high-frequency voltage is generated in the radio frequency cavity, the radio frequency cavity comprises a first cavity and a second cavity, the first cavity and the second cavity are mutually independent and are respectively connected with an independent power source, and phase coupling can be realized between the first cavity and the second cavity;
the superconducting magnet system adopts four-spiral fan distribution and elliptical cambered surface design, and magnetic poles of the superconducting magnet system are matched with the first cavity and the second cavity to form four-magnetic pole two-cavity layout, so that function expansion can be carried out in the other two cavities, and other pipelines required by the operation of the superconducting cyclotron or parts which are easily influenced by a high-frequency electric field are arranged.
2. The superconducting cyclotron of claim 1, wherein the extraction zone constrains the proton beam current by magnetic focusing.
3. The superconducting cyclotron of claim 1, wherein the central zone is a raised metal structure, the central zone being mounted at a central location of the superconducting cyclotron, the central zone providing axial electrical focusing and restricting proton beam trajectory movement through the central zone, reducing proton beam losses.
4. The superconducting cyclotron of claim 3, wherein the ion source is a penning ion source, the ion source being mounted at a central location of the superconducting cyclotron, the ion source extending through the central zone.
5. The superconducting cyclotron of claim 3, further comprising a three-dimensional moving platform on which the ion source is mounted, the angular position and axial height position of the ion source being adjusted by the three-dimensional moving platform to increase extraction efficiency of the ion source beam.
6. The superconducting cyclotron of claim 3, wherein the main accelerator system further comprises a vertical deflection plate disposed at the central zone, the vertical deflection plate configured to generate an electric field to effect precise adjustment of beam axial position.
7. The superconducting cyclotron of claim 1, wherein the superconducting magnet system comprises a superconducting coil that is energized with a current to produce a specific static magnetic field.
8. The superconducting cyclotron of claim 7, wherein the superconducting coils are implemented using a double zero volatilization liquid helium cooling technique.
9. The superconducting cyclotron of claim 7, wherein the superconducting magnet system further comprises a fast demagnetizer configured to effect demagnetization of the superconducting coil.
10. The superconducting cyclotron of claim 1, wherein the accelerator auxiliary system comprises a power supply system that provides power to subsystem devices.
11. The superconducting cyclotron proton accelerator of claim 1, wherein the accelerator auxiliary system further comprises a water cooling system that cools a subsystem of the main accelerator system.
12. The superconducting cyclotron of claim 1, wherein the accelerator assistance system further comprises a vacuum system that provides a vacuum environment for the superconducting cyclotron interior.
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