Superconducting magnet devices, particle accelerators and radiotherapy equipment

Abstract

The present invention discloses a superconducting magnet device, a particle accelerator and a radiotherapy device, wherein the superconducting magnet device comprises a magnet assembly and a control assembly; the magnet assembly comprises an iron yoke, a coil frame, an iron core and a superconducting coil, and no cold shield is arranged outside the iron yoke; the superconducting coil is formed by winding a plurality of high-temperature superconducting tapes in a circumferential direction, the plurality of high-temperature superconducting tapes are arranged at intervals, and the height direction of the high-temperature superconducting tapes is parallel to the direction of the magnetic field generated by the superconducting coil after power is turned on; the control assembly comprises a refrigeration unit and an electrical unit, the refrigeration unit is used to provide a cold source to the superconducting coil so that the temperature at the superconducting coil reaches the working temperature of the superconducting coil, and the electrical unit is electrically connected to the superconducting coil to control the superconducting coil. The superconducting magnet device, the particle accelerator and the radiotherapy device of the present invention are used to increase the working temperature of the superconducting magnet, maintain the superconducting magnet to generate sufficient magnetic field strength, and reduce the use cost of the superconducting magnet device.

Description

Technical Field

[0001] The present invention relates to the technical field of high-end medical equipment, and in particular to superconducting magnet devices, particle accelerators and radiotherapy equipment. Background Art

[0002] Since the birth of superconducting technology in the early 20th century, people's understanding of the origin of superconductivity has been deepening with the development of science and technology. The development of new materials has led to the rapid rise of applied superconducting technology. In the medical field, a particle accelerator is a device that applies superconducting technology. The particle accelerator generates a magnetic field through a superconducting magnet, and uses this magnetic field to control the therapeutic particles to be ejected along the beam channel. After the therapeutic particles are emitted from the cyclotron beam, they irradiate the patient to treat the patient. One of the main components of the superconducting magnet of a particle accelerator is a superconducting coil wound with superconducting materials.

[0003] For example, low-temperature superconducting materials such as NbTi and Nb3Sn have excellent electromagnetic properties, and the process of thin-filament single-core and multi-filament composite superconducting wires is mature, and they are one of the materials for winding superconducting coils. In addition, there is also a method of combining low-temperature superconducting materials with high-temperature superconducting materials to make superconducting coils to improve the magnetic field strength that can be generated by the prepared superconducting magnets. Although the existing low-temperature superconducting materials, or superconducting magnets prepared by combining low-temperature superconducting materials with high-temperature superconducting materials, have met the needs of daily use, in order to keep the low-temperature superconducting materials, or the low-temperature superconducting materials with high-temperature superconducting materials in a superconducting state, it is necessary to have higher requirements on the working temperature of the superconducting coils, and its working temperature generally needs to be maintained at an extremely low condition of 1.8K (Kelvins).

[0004] Existing superconducting magnets have a relatively low operating temperature and need to be used with components such as cold shields, which results in a relatively complex structure and high cost for the superconducting magnet device. When the temperature is to reach a level below 4K, the design of the cryogenic equipment and the heat leakage prevention structure in the superconducting magnet poses certain challenges, and increases the operating and maintenance costs of superconducting applications. It also requires the provision of high-power cryogenic equipment and refrigerants, which makes the use of superconducting technology prohibitive for ordinary application scenarios such as ordinary hospitals or clinics. Summary of the invention

[0005] The object of the present invention is to provide a superconducting magnet device, a particle accelerator and a radiotherapy device, which are used to increase the working temperature of the superconducting magnet and maintain the superconducting magnet to generate sufficient magnetic field strength, reduce the use cost of the superconducting magnet device, and simplify the structure of the superconducting magnet device.

[0006] The purpose of the present invention is achieved by the following technical solutions:

[0007] A superconducting magnet device, comprising:

[0008] A magnet assembly, comprising an iron yoke, a coil frame, an iron core and a superconducting coil, wherein the iron yoke is surrounded to form an accommodation space, the coil frame and the iron core are arranged in the accommodation space, and the superconducting coil is arranged between the coil frame and the iron core, the axial direction of the superconducting coil is the same as the axial direction of the coil frame, and no cold shield is arranged outside the iron yoke; the superconducting coil is formed by winding a plurality of high-temperature superconducting tapes in a circumferential direction, the plurality of high-temperature superconducting tapes are arranged at intervals, and the height direction of the high-temperature superconducting tapes is parallel to the direction of the magnetic field generated by the superconducting coil after power is supplied;

[0009] The control component includes a refrigeration unit and an electrical unit. The refrigeration unit is used to provide a cold source to the superconducting coil so that the temperature at the superconducting coil reaches the working temperature of the superconducting coil. The electrical unit is electrically connected to the superconducting coil to control the superconducting coil.

[0010] Preferably, the high temperature superconducting tape is wound to form a multi-layer superconducting coil, and two adjacent layers of the superconducting coils are spaced apart;

[0011] The magnet assembly further comprises a quench detection and protection unit, which is used to detect whether the superconducting coil has a quench and protect the superconducting coil when the quench occurs; the quench detection and protection unit is arranged between two adjacent layers of the superconducting coils.

[0012] Preferably, the quench detection and protection units are evenly distributed between two adjacent layers of the superconducting coils, or the quench detection and protection units are concentrated at a portion of the gap between two adjacent layers of the superconducting coils.

[0013] Preferably, the quench detection and protection unit comprises a quench detection circuit and a quench protection circuit, the quench detection circuit is used to detect whether the superconducting coil is quenched according to a change in the voltage difference, and the quench protection circuit is used to protect the superconducting coil by quench heating.

[0014] Preferably, the material of the high temperature superconducting tape is REBCO, YBCO, MgB 2 , Bi2212 or Bi2223.

[0015] Preferably, the superconducting magnet device is not provided with a pipeline matching the refrigerant.

[0016] Preferably, the iron yoke is provided with a first connecting port extending therethrough, the coil frame is provided with a second connecting port, the second connecting port is used to connect the first connecting port and the superconducting coil, and the control component is connected to the superconducting coil via the first connecting port and the second connecting port.

[0017] Preferably, a D-shaped box is provided inside the iron core, and the magnet assembly is provided with a beam-emitting track, one end of the beam-emitting track extends to the D-shaped box, and the other end of the beam-emitting track passes through the magnet assembly; the D-shaped box is used to accelerate therapeutic particles, and the therapeutic particles are ejected through the beam-emitting track under the action of the magnetic field generated by the magnet assembly.

[0018] Preferably, the superconducting coil is installed in the accommodating space via a suspension device, the suspension device is connected to the iron yoke, and the connection position between the suspension device and the iron yoke is adjustable to adjust the position of the superconducting coil and adjust the beam direction of the therapeutic particles.

[0019] Preferably, the control assembly also includes a control box and a connecting pipe, and the control box is connected to the magnet assembly through the connecting pipe; the refrigeration unit includes a cold head and a refrigeration connection connected to the cold head, and the electrical unit includes an electrical integration and an electrical connection connected to the electrical integration, the cold head and the electrical integration are integrated on a first cover body of the control box, and the refrigeration connection second cover body and the electrical connection are connected to the magnet assembly through the connecting pipe.

[0020] Preferably, a connection cavity is formed in the connection pipe, and the control assembly further comprises a connection wire protection cover, and the connection wire protection cover is arranged in the connection cavity; the refrigeration connection is arranged in the connection cavity and is located outside the connection wire protection cover, and the electrical connection is arranged in the connection wire protection cover and is separated from the refrigeration connection by the connection wire protection cover;

[0021] And / or, the control box includes a second cover made of a transparent material.

[0022] Preferably, the second cover is made of carbon fiber reinforced polyimide composite material.

[0023] A particle accelerator comprises any one of the above-mentioned superconducting magnet devices.

[0024] A radiotherapy device comprises the above-mentioned particle accelerator.

[0025] Compared with the prior art, the beneficial effects of the present invention include at least:

[0026] By using high-temperature superconducting tape to form a superconducting coil, the required operating temperature of the superconducting coil can reach 20K. Therefore, the magnet assembly does not need to use a large amount of refrigerant, which can reduce the cost of the superconducting magnet device and simplify the structure of the superconducting magnet. By setting the height direction of the high-temperature superconducting tape to be parallel to the magnetic field direction, the critical magnetic field and critical current parameters of the high-temperature superconducting tape are high, which can fully meet the working requirements of the superconducting magnet device. BRIEF DESCRIPTION OF THE DRAWINGS

[0027] Figure 1 is a schematic structural diagram of a superconducting magnet device according to an embodiment of the present invention;

[0028] Figure 2 is a planar cross-sectional view of a superconducting magnet device according to an embodiment of the present invention;

[0029] Figure 3 is a planar cross-sectional view of a magnet assembly according to an embodiment of the present invention;

[0030] Figure 4 is a cross-sectional view of a magnet assembly according to an embodiment of the present invention in another cross-sectional view;

[0031] Figure 5 is a partial structural schematic diagram of a magnet assembly according to an embodiment of the present invention;

[0032] Figure 6 is a partial plan cross-sectional view of a superconducting coil according to an embodiment of the present invention;

[0033] Figure 7 is a schematic structural diagram of a coil skeleton according to an embodiment of the present invention;

[0034] Figure 8 Schematic diagram of the structure of the control component of the embodiment of the present invention.

[0035] In the figure: 1. magnet assembly; 11. accommodating space; 12. superconducting coil; 13. quench detection protection unit; 14. iron yoke; 141. first connection port; 15. coil frame; 151. second connection port; 152. mounting groove; 153. boss; 16. iron core; 17. D-shaped box; 18. beam output track; 2. control assembly; 21. refrigeration unit; 211. cold head; 22. electrical unit; 221. electrical integration; 23. control box; 231. first cover body; 232. second cover body; 24. connecting pipe; 241. connecting cavity; 25. connecting wire protection cover. DETAILED DESCRIPTION

[0036] Example embodiments will now be described more fully with reference to the accompanying drawings. However, example embodiments can be implemented in a variety of forms and should not be construed as limited to the embodiments set forth herein; rather, these embodiments are provided to make the present invention more comprehensive and complete and to fully convey the concepts of example embodiments to those skilled in the art. The same reference numerals in the figures represent the same or similar structures, and thus their repeated description will be omitted.

[0037] The words expressing positions and directions described in the present invention are all explained with reference to the accompanying drawings as examples, but they can be changed as needed, and all such changes are included in the protection scope of the present invention.

[0038] like Figures 1 to 8 As shown, the present invention provides a superconducting magnet device, including a magnet assembly 1 and a control assembly 2.

[0039] The magnet assembly 1 is used to generate a magnetic field. Specifically, the device for generating a magnetic field in the magnet assembly 1 is mainly a superconducting coil 12 arranged inside the magnet assembly 1. The superconducting coil 12 is formed by winding a plurality of high-temperature superconducting tapes in a circumferential direction, and the plurality of high-temperature superconducting tapes are arranged at intervals. When the superconducting coil 12 is energized, the superconducting coil 12 generates a magnetic field. Since the superconducting coil 12 is made of high-temperature superconducting material, the required working temperature of the superconducting coil 12 can reach 20K, which is much higher than the working temperature of the superconducting coil made of low-temperature superconducting material and the superconducting coil made of a combination of low-temperature superconducting material and high-temperature superconducting material. Therefore, the magnet assembly 1 of the present invention only needs a small amount of refrigerant, and does not need to use a large amount of refrigerant (such as liquid helium) to reach the required working temperature, which can reduce the use cost of the superconducting magnet device. In addition, since the superconducting magnet device only needs the participation of a small amount of refrigerant, the structure of the superconducting magnet is also simplified, and there is no need to provide a complex pipeline structure when a large amount of refrigerant is provided, and the magnet assembly 1 does not need to be provided with a cold screen structure. Among them, the material of the high temperature superconducting tape can be REBCO (rare earth barium oxide), YBCO (yttrium barium copper oxide), MgB 2 、Bi2212(Bi 2 Sr 2 CaCu 2 O 8 ) or Bi2223(Bi 2 Sr 2 Ca 2 Cu 3 O 10 ), preferably, the material of the high temperature superconducting tape is REBCO.

[0040] In order to improve the maximum magnetic field strength of the superconducting coil 12, the height direction of the high-temperature superconducting tape can be parallel to the magnetic field direction. When the height direction of the high-temperature superconducting tape is parallel to the magnetic field direction, the critical magnetic field and critical current parameters of the high-temperature superconducting tape are relatively high. At this time, the maximum magnetic field strength that can be generated by the superconducting coil 12 prepared by the high-temperature superconducting tape can reach 10T (Tesla), and the maximum magnetic field strength of the superconducting coil 12 along its axial direction can reach 9.6T, and the maximum magnetic field strength along its radial direction can reach 7T, achieving ultra-high field strength and better meeting the working requirements of the superconducting magnet device. Among them, the high-temperature superconducting tape can be wound along its circumferential direction to form a superconducting coil 12 with an annular structure.

[0041] In addition, the minimum quench energy of high-temperature superconducting materials is 2 to 3 orders of magnitude higher than that of low-temperature superconducting materials. When a superconducting magnet device using low-temperature superconducting materials quenches due to problems such as internal wire movement and missing filling materials, a superconducting magnet device using high-temperature superconducting materials can avoid quenching. Moreover, a superconducting magnet device using high-temperature superconducting materials also has better operating stability and robust control characteristics, which can improve the reliability of the superconducting magnet device.

[0042] Reference Figure 3 The magnet assembly 1 may specifically include an iron yoke 14, a coil frame 15, an iron core 16 and a superconducting coil 12, and the magnet assembly 1 does not need to be provided with a cold shield outside the iron yoke 14. The iron yoke 14 is surrounded by a receiving space 11, and the receiving space 11 is used to accommodate the coil frame 15, the iron core 16 and the superconducting coil 12. When the superconducting coil 12 generates a magnetic field, the iron yoke 14 can be used to gather the magnetic field and reduce the leakage magnetic field, and the iron yoke 14 can also be used to provide a saturated magnetic field of a certain field strength. Among them, the receiving space 11 can maintain a vacuum state during the operation process to achieve the vacuum degree required for the work, and maintain the required working temperature under the action of the control component 2, that is, the temperature is about 20K.

[0043] Reference Figure 5 and Figure 7 The coil skeleton 15 is provided with a mounting groove 152 for mounting the superconducting coil 12, and the axial direction of the mounting groove 152 may be the same as the axial direction of the superconducting coil 12. The axis of the mounting groove 152 may be parallel to the axis of the superconducting coil 12, and the wall forming the mounting groove 152 may abut against the outer peripheral wall of the superconducting coil 12. The coil skeleton 15 may generate a certain pre-tightening force on the superconducting coil 12 disposed in the mounting groove 152. Specifically, the coil skeleton 15 may generate a pre-tightening force on the superconducting coil 12 by thermal contraction. For example, the radial cross-section of the mounting groove 152 can be slightly smaller than the radial cross-section of the superconducting coil 12, so that the mounting groove 152 and the superconducting coil 12 have an interference fit; when installing the superconducting coil 12, the superconducting coil 12 will be pre-cooled first to shrink the superconducting coil 12, and then the shrunk superconducting coil 12 will be installed in the mounting groove 152. The superconducting coil 12 will expand in the process of returning to normal temperature. Therefore, the superconducting coil 12 can fit tightly with the coil frame 15, and the wall forming the mounting groove 152 in the coil frame 15 can generate a pre-tightening force on the superconducting coil 12.

[0044] In some specific embodiments, the coil frame 15 may be provided with two mounting grooves 152, each of which may be used to mount the superconducting coil 12. The two mounting grooves 152 are spaced apart along the axial direction of the coil frame 15; the coil frame 15 is also provided with a boss 153 extending from the inner wall of the coil frame 15 toward the center of the coil frame 15, and the boss 153 is used to separate the two mounting grooves 152. The boss 153 may be an annular structure, and the inner hollow portion of the boss 153 may be connected to the two mounting grooves 152.

[0045] Reference Figure 3 In some specific embodiments, the superconducting coil 12 needs to be connected to the control assembly 2 so that the superconducting coil 12 can generate a magnetic field under the action of the current provided by the control assembly 2. To facilitate the connection between the superconducting coil 12 and the control assembly 2, the iron yoke 14 can be provided with a first connecting port 141 that penetrates through. The first connecting port 141 is used to connect the external space of the magnet assembly 1 with the accommodating space 11 inside the iron yoke 14. The coil skeleton 15 can be provided with a second connecting port 151, one end of the second connecting port 151 is connected to the first connecting port 141, and the other end is connected to the installation groove 152 for accommodating the superconducting coil 12, so that the first connecting port 141 and the second connecting port 151 together form a channel extending from the outside of the magnet assembly 1 to the superconducting coil 12, and the superconducting coil 12 can be connected to the control assembly 2 through the channel formed by the first connecting port 141 and the second connecting port 151.

[0046] There may be multiple first connection ports 141 and second connection ports 151. Among them, at least one first connection port 141 and the corresponding at least one second connection port 151 are used to realize the connection between the superconducting coil 12 and the control component 2. For example, when the first connection port 141 and the second connection port 151 are both set to four, each first connection port 141 and the corresponding second connection port 151 constitute a connection channel, wherein one connection channel is used to connect with the control component 2, another connection channel can be sealed and connected with the vacuum flange so that the vacuum equipment can evacuate the accommodating space 11 in the iron yoke 14, and another connection channel can be used as a beam outlet for the therapeutic particles to emit a beam. Another connection channel can be used as a radio frequency port for connecting a radio frequency device, and the radio frequency device can be used to connect the D-shaped box 17 in the iron core 16 to periodically change the polarity of the D-shaped box so that the particles are accelerated in the magnetic field until the beam is emitted. It should be noted that when the magnet assembly 1 needs to be connected to other external components, the first connection port 141 and the second connection port 151 can be set to more than 4, for example, 5 or 6, so that the magnet assembly 1 can be connected to the required external device as needed.

[0047] Reference Figure 7In some specific embodiments, the second connection port 151 can extend from the outer wall of the coil skeleton 15 to the inner wall of the boss 153. When the control component 2 extends to the internal hollow portion of the boss 153 through the second connection port 151, since the internal hollow portion of the boss 153 can be connected to the two installation grooves 152, the control component 2 can be connected to the superconducting coils 12 in the two installation grooves 152, thereby simplifying the connection structure between the control component 2 and the superconducting coil 12.

[0048] Reference Figure 3 The iron core 16 is arranged inside the superconducting coil 12, so that the superconducting coil 12 is sandwiched between the coil frame 15 and the iron core 16. The iron core 16 and the iron yoke 14 are made of high magnetic permeability materials, have high magnetic flux density and low magnetic resistance, and can effectively guide and concentrate the magnetic field. Therefore, the iron core 16 and the iron yoke 14 can be used together to provide a saturated magnetic field with a certain field strength inside the magnet assembly 1.

[0049] Reference Figure 4 In some specific embodiments, the magnet assembly 1 is further provided with a beam-emission track 18. The beam-emission track 18 may pass through the iron core 16 and the coil frame 15. Specifically, the beam-emission track 18 extends from the inside of the iron core 16 to the boss 153 of the coil frame 15, and continues to extend to pass through the coil frame 15, and can be connected to the outside of the magnet assembly 1 through a first connection port 141 of the iron yoke 14. Among them, the beam-emission track 18 may be arranged in a spiral shape. A D-shaped box 17 may be arranged inside the iron core 16, and the D-shaped box 17 may be connected to the control assembly 2. The D-shaped box 17 is used to accelerate the cooling particles. The therapeutic particles are ejected along the beam-emission track 18 under the action of the magnetic field inside the magnet assembly 1, and then pass through other interface devices to perform particle irradiation therapy on the patient.

[0050] Reference Figure 6 , the high temperature superconducting material can be wound into multiple layers of superconducting coils 12, and the adjacent layers of superconducting coils 12 are spaced apart. Specifically, the superconducting coils 12 can form multiple rows along the radial direction, each row includes multiple spaced-apart superconducting coils 12; at the same time, the superconducting coils 12 can form multiple columns along the axial direction, each column includes multiple spaced-apart superconducting coils 12. The gaps between the multiple superconducting coils 12 can be filled with resin to insulate the multiple superconducting coils 12 from each other.

[0051] When the superconducting coil 12 is working, the superconducting coil 12 may be quenched due to equipment failure or human factors, that is, a position of the superconducting coil 12 loses superconductivity. At this time, a large amount of heat will be generated when the current passes through this part. The quenching conduction speed of the high-temperature superconducting material is slow, which will cause the heat to be unable to dissipate quickly, and then concentrate at the quenching position. As the heat continues to accumulate, the superconducting coil 12 will be damaged. In order to avoid the superconducting coil 12 from being damaged due to quenching, the magnet assembly 1 is also provided with a quench detection and protection unit 13. The quench detection and protection unit 13 can be arranged between two adjacent layers of superconducting coils 12. The quench detection and protection unit 13 is used to detect whether the superconducting coil 12 is quenched and protect the superconducting coil 12 when quenched. Among them, the reaction speed of the quench detection and protection unit 13 is relatively sensitive, and it can react quickly after detecting that the superconducting coil 12 is quenched to protect the superconducting coil 12. The quench detection protection unit 13 can be started manually or automatically. For example, the quench detection protection unit 13 can be automatically started after a quench is detected, or the quench detection protection unit 13 can be started by a staff member through a control switch after a quench occurs.

[0052] The quench detection and protection units 13 may be evenly distributed between two adjacent layers of superconducting coils 12. For example, the quench detection and protection units 13 are arranged in the gaps in the radial direction of the adjacent superconducting coils 12, and the circumferential profile of the quench detection and protection units 13 is adapted to the circumferential profile of the superconducting coils 12, so that corresponding quench detection and protection units 13 are arranged in the circumferential direction of the superconducting coils 12. Therefore, the quench detection and protection units 13 can detect all positions of the superconducting coils 12 in the circumferential direction.

[0053] In addition, the quench detection and protection units 13 can also be concentrated at some positions of the gap between two adjacent layers of superconducting coils 12. For example, the quench detection and protection units 13 are arranged in the gaps in the radial direction of the adjacent superconducting coils 12, and only some positions along the circumferential direction of the superconducting coils 12 are provided with quench detection and protection units 13, so that the quench detection and protection units 13 detect and protect the positions; wherein, the some positions can occupy 1 / 3, 1 / 2 or 2 / 3 of the superconducting coils 12. According to different use conditions and use occasions, the quench detection and protection units 13 can be selected according to specific needs to detect and protect all positions of the superconducting coils 12, or only the parts of the superconducting coils 12 with quench risks can be detected and protected.

[0054] Among them, along the radial direction of the superconducting coil 12, the quench detection and protection unit 13 may be arranged between all adjacent superconducting coils 12, or the quench detection and protection unit 13 may be arranged between some of the superconducting coils 12. Specifically, in any installation slot 152, along the radial direction of the superconducting coil 12, a quench detection and protection unit 13 may be arranged every certain number of columns of superconducting coils 12, and the length of the quench detection and protection unit 13 along the axial direction of the superconducting coil 12 is the same as or similar to the total length of a column of superconducting coils 12. Since the distance between adjacent superconducting coils 12 along the radial direction of the superconducting coil 12 is small, the quench detection and protection unit 13 can detect and protect not only the adjacent superconducting coils 12, but also the superconducting coils 12 adjacent to the quench detection and protection unit 13. Even if a quench detection and protection unit 13 is provided for every certain number of columns of superconducting coils 12, the superconducting coils 12 can still remain adjacent to the quench detection and protection unit 13, so the quench detection and protection unit 13 can detect and protect a certain number of columns of superconducting coils 12 in the radial direction of the superconducting coils 12. The certain number of columns may be two columns, three columns, four columns, etc. In this embodiment, a quench detection and protection unit 13 may be provided for every three columns of superconducting coils 12 in the radial direction of the superconducting coils 12.

[0055] The quench detection and protection unit 13 may specifically include a quench detection circuit and a quench protection circuit. The quench detection circuit may be connected to the control component 2, and the quench detection circuit is used to detect whether the superconducting magnet is quenched according to the change of the voltage difference. Specifically, the quench detection circuit will generate a certain voltage difference when working, and when a certain part of the superconducting coil 12 is quenched, the magnetic field generated by the part of the superconducting coil 12 disappears, and the quench detection circuit will generate a large change in the voltage difference. If the changed voltage difference does not fall back within a certain time, such as 0.1s, 0.5s, etc., it is judged that the superconducting coil 12 is quenched. At this time, the quench detection circuit can be fed back to the control component 2, and the control component 2 can control the quench protection circuit to start. Among them, the quench detection circuit may include a wire and a pressure-sensitive material. The pressure-sensitive material may include multiple, and the multiple pressure-sensitive materials may be distributed at intervals along the circumference of the superconducting coil 12 to detect each position of the superconducting coil 12. Multiple pressure-sensitive materials are connected in series through wires, and the quench detection circuit can also be connected to the control unit through wires. The varistor material is a material that is sensitive to voltage signals, such as semiconductor materials such as silicon and germanium.

[0056] The quench protection circuit is used to protect the superconducting coil 12 by quench heating. Specifically, when the superconducting coil 12 quenches, the quench protection circuit will be activated, and the connection circuit between the control component 2 and the superconducting coil 12 will be cut off, and quench heating will be performed to generate heat, and the heat will be transferred to various parts of the superconducting coil 12, so that the temperature of the superconducting coil 12 rises, and each position of the superconducting coil 12 will be quenched, so that the heat generated by the quench of the superconducting coil 12 is dispersed to various positions of the superconducting coil 12, avoiding the heat from being concentrated in one position, causing the superconducting coil 12 at this position to be damaged. Among them, the quench detection circuit may include a wire and a heating element, the heating element may be set to a plurality, the plurality of heating elements may be distributed at intervals along the circumference of the superconducting coil 12, and the plurality of heating elements may be connected in series through a wire; wherein the heating element may be a resistor. When the superconducting coil 12 quenches, part of the magnetic field of the superconducting coil 12 changes, so that the quench detection circuit generates an induced current and heats the heating element. The heating element conducts heat to various positions of the superconducting coil 12, so that various positions of the superconducting coil 12 quench due to temperature rise, thereby dispersing the energy generated by the quench of the superconducting coil 12 to various positions of the superconducting coil 12 to protect the superconducting coil 12.

[0057] In some specific embodiments, due to the tolerances of the various components of the superconducting magnet device during processing, and after the various components are assembled together, due to the accumulation of tolerances, the angle of the therapeutic particles when they are emitted may deviate from the predetermined angle. In order to adjust the emission direction of the therapeutic particles, the superconducting magnet device may further include a suspension device (not shown). The suspension device is installed on the iron yoke 14 and connected to the coil frame 15 and the superconducting coil 12, so that the coil frame 15 and the superconducting coil 12 can be suspended in the iron yoke 14 through the suspension device. The connection position of the suspension device and the iron yoke 14 is adjustable, so that the position of the coil frame 15 and the superconducting coil 12 on the iron yoke 14 is adjustable, thereby adjusting the beam direction of the therapeutic particles so that the emission angle of the therapeutic particles is the same as the predetermined angle.

[0058] The suspension device can be specifically formed by a combination of multiple bolts and sensors. The sensor is used to detect the tension of the bolts on the coil skeleton 15 and the superconducting coil 12 in the iron yoke 14. The bolts are used to suspend the coil skeleton 15 and the superconducting coil 12 in the iron yoke 14. To facilitate the adjustment of the suspension assembly, the superconducting magnet device can be connected to an external adjustment device, and the external adjustment device can extend into the interior of the iron yoke 14 through one or more first connection ports 141 in the iron yoke 14. The external adjustment device may include a wrench portion extending into the interior of the iron yoke 14, and a control portion for controlling the wrench portion. The control portion can control the wrench portion knob or loosen the bolt to adjust the position of the coil skeleton 15 and the superconducting coil 12 in the iron yoke 14.

[0059] Reference Figure 2 and Figure 7 , the control assembly 2 may include a control box 23, a connecting pipe 24, a refrigeration unit 21 and an electrical unit 22. The refrigeration unit 21 is used to provide a cold source to the superconducting coil 12 so that the temperature of the superconducting coil 12 reaches the working temperature of the superconducting coil 12. Specifically, the refrigeration unit 21 includes a cold head 211 and a refrigeration connection connected to the cold head 211 (not shown). The cold head 211 is used to generate a cold source. The refrigeration connection is connected to the magnet assembly 1 to transfer the cold source generated by the cold head 211 to the magnet assembly 1, thereby making the temperature of the superconducting coil 12 reach the working temperature of the superconducting coil 12. Among them, the refrigeration connection can be a structure such as a line for conveying a cold source.

[0060] The electrical unit 22 is used to be electrically connected to the superconducting coil 12 to control the superconducting coil 12. Specifically, the electrical unit 22 includes an electrical integration 221 and an electrical connection (not shown) connected to the electrical integration 221. The electrical integration 221 can be integrated into the control box 23. The electrical connection is used to connect the electrical integration 221 to components such as the superconducting coil 12, the quench detection and protection unit 13 or an external sensor. Among them, the electrical connection can be an electrical connection structure such as a wire or a connector.

[0061] The control box 23 may include a plurality of covers. The plurality of covers may be arranged together to form a housing cavity, which is used to accommodate a part of the structure of the refrigeration connection and the electrical connection. The plurality of covers may include a first cover 231 and a second cover 232. The first cover 231 is used to integrate the cold head 211 and the electrical integration 221. Since the superconducting magnet device of the present invention only needs to use a small amount of refrigerant, the control box 23 does not need to integrate a complex pipeline structure when a large amount of refrigerant is provided, so that the cold head 211 and the electrical integration 221 can be highly integrated, for example, the cold head 211 and the electrical integration 221 are centrally arranged on the first cover 231. In some specific embodiments, in order to facilitate the observation of the state of the refrigeration connection and the electrical connection inside the control box 23, the second cover 232 can be made of a transparent material, so that when the superconducting magnet device is working, the staff can observe the state of the refrigeration connection and the electrical connection in the control box 23 through the second cover 232, and can quickly locate the fault location when it fails, so as to locate and repair the fault location, thereby increasing the maintenance efficiency of the equipment. The second cover 232 may be made of a carbon fiber reinforced polyimide composite material.

[0062] The control box 23 can be connected to the magnet assembly 1 through a connecting tube 24. Specifically, one end of the connecting tube 24 can be connected to the control box 23, and the other end can pass through the first connecting port 141 of the iron yoke 14 and the second connecting port 151 of the coil skeleton 15 to extend to the vicinity of the superconducting coil 12. The connecting tube 24 can be a hollow tube body, and a connecting cavity 241 is formed inside. The refrigeration connection and the electrical connection can pass through the connecting tube 24 from the inside of the control box 23, so that the refrigeration connection can supply a cold source to the superconducting coil 12, and the electrical connection can be connected to the superconducting coil 12 and the quench detection protection unit 13.

[0063] In some specific embodiments, the control assembly 2 may further include a connection wire protection cover 25, which may be disposed in the connection cavity 241 of the connection tube 24. The electrical connection may be disposed in the connection wire protection cover 25, and the refrigeration connection may be disposed in the connection cavity 241 and located outside the connection wire protection cover 25. Therefore, the electrical connection and the refrigeration connection may be separated by the connection wire protection cover 25 to avoid the influence of the refrigeration connection and the electrical connection, thereby ensuring the reliability of the operation of the device.

[0064] The present invention also provides a particle accelerator, which includes the above-mentioned superconducting magnet device. The particle accelerator is applied in the medical field and can be used to accelerate therapeutic particles, and the accelerated therapeutic particles can be used to treat patients.

[0065] In addition, since the superconducting magnet device does not need to be provided with a complex piping structure for providing a large amount of refrigerant, the superconducting magnet device is basically not restricted by the piping, which limits the rotation angle of the superconducting magnet device. For example, the existing superconducting magnet device can only achieve 190° rotation due to the restriction of complex piping. Therefore, when treating patients, for some positions where the superconducting magnet device needs to rotate at an angle greater than 190°, it is necessary to move the treatment bed and the rotating superconducting magnet device in a coordinated manner. The superconducting magnet device of the present invention is basically not affected by the structure such as the piping matched with the refrigerant, and can achieve 360° rotation. Therefore, the treatment beam emitted by the particle accelerator can be emitted in all directions, and the treatment bed does not need to be moved.

[0066] The present invention also provides a radiotherapy device, which comprises the above-mentioned particle accelerator.

[0067] Although the embodiments of the present invention have been shown and described above, it is to be understood that the above embodiments are exemplary and are not to be construed as limitations on the present invention. A person skilled in the art may change, modify, substitute and modify the above embodiments within the scope of the invention without departing from the principles and purpose of the present invention. All such changes should fall within the scope of protection of the claims of the present invention.

Claims

1. A superconducting magnet device, characterized in that: include: A magnet assembly (1) comprises an iron yoke (14), a coil frame (15), an iron core (16) and a superconducting coil (12), wherein the iron yoke (14) is arranged to form a containing space (11), the coil frame (15) and the iron core (16) are arranged in the containing space (11), and the superconducting coil (12) is arranged between the coil frame (15) and the iron core (16), the axial direction of the superconducting coil (12) is the same as the axial direction of the coil frame, and no cold shield is arranged outside the iron yoke (14); the superconducting coil (12) is formed by winding a plurality of high-temperature superconducting tapes in a circumferential direction, the plurality of high-temperature superconducting tapes are arranged at intervals, and the height direction of the high-temperature superconducting tapes is parallel to the direction of the magnetic field generated by the superconducting coil after power is supplied; A control component (2) comprising a refrigeration unit (21) and an electrical unit (22), wherein the refrigeration unit (21) is used to provide a cold source to the superconducting coil (12) so that the temperature at the superconducting coil (12) reaches the working temperature of the superconducting coil (12), and the electrical unit (22) is electrically connected to the superconducting coil (12) so as to control the superconducting coil (12); The iron yoke (14) is provided with a first connecting port (141) extending therethrough, the coil frame (15) is provided with a second connecting port (151), the second connecting port (151) being used to connect the first connecting port (141) and the superconducting coil (12), and the control component (2) is connected to the superconducting coil (12) via the first connecting port (141) and the second connecting port (151); The coil frame (15) is provided with two installation grooves (152), each of which is used to install the superconducting coil (12); wherein the two installation grooves (152) are spaced apart along the axial direction of the coil frame (15); the coil frame (15) is further provided with a boss (153) extending from the inner wall of the coil frame (15) toward the center of the coil frame (15), the boss (153) being used to separate the two installation grooves (152); the boss (153) is an annular structure, and the inner hollow portion of the boss (153) is connected to the two installation grooves (152); The second connection port (151) extends from the outer wall of the coil frame (15) to the inner wall of the boss (153), and the control component (2) extends to the inner hollow portion of the boss (153) through the second connection port (151).

2. The superconducting magnet device according to claim 1, characterized in that: The high-temperature superconducting tape is wound to form a plurality of layers of superconducting coils (12), with two adjacent layers of the superconducting coils (12) being spaced apart; The magnet assembly (1) further comprises a quench detection and protection unit (13), the quench detection and protection unit (13) being used to detect whether the superconducting coil (12) is quenched and to protect the superconducting coil (12) when quenched; the quench detection and protection unit (13) is arranged between two adjacent layers of the superconducting coils (12).

3. The superconducting magnet device according to claim 2, characterized in that: The quench detection and protection units (13) are evenly distributed between two adjacent layers of superconducting coils (12), or the quench detection and protection units (13) are concentrated at a portion of the gap between two adjacent layers of superconducting coils (12).

4. The superconducting magnet device according to claim 2, characterized in that: The quench detection and protection unit (13) comprises a quench detection circuit and a quench protection circuit, the quench detection circuit being used to detect whether the superconducting coil (12) is quenched according to a change in a voltage difference, and the quench protection circuit being used to protect the superconducting coil (12) by quench heating.

5. The superconducting magnet device according to claim 1, characterized in that: The material of the high temperature superconducting tape is one or more of REBCO, YBCO, MgB2, Bi2212 or Bi2223.

6. The superconducting magnet device according to claim 1, characterized in that: The superconducting magnet device is not provided with a pipeline matching the refrigerant.

7. The superconducting magnet device according to claim 1, characterized in that: A D-shaped box (17) is arranged inside the iron core (16); the magnet assembly (1) is provided with a beam-emitting track (18); one end of the beam-emitting track (18) extends to the D-shaped box, and the other end of the beam-emitting track (18) passes through the magnet assembly (1); the D-shaped box (17) is used to accelerate therapeutic particles, and the therapeutic particles are ejected through the beam-emitting track (18) under the action of the magnetic field generated by the magnet assembly (1).

8. The superconducting magnet device according to claim 7, characterized in that: The superconducting coil (12) is installed in the accommodating space (11) via a suspension device, the suspension device is connected to the iron yoke (14), and the connection position between the suspension device and the iron yoke (14) is adjustable to achieve adjustment of the position of the superconducting coil (12) and to adjust the beam direction of the therapeutic particles.

9. The superconducting magnet device according to claim 1, characterized in that: The control assembly (2) further comprises a control box (23) and a connecting pipe (24), wherein the control box (23) is connected to the magnet assembly (1) via the connecting pipe (24); the refrigeration unit (21) comprises a cold head (211) and a refrigeration connection connected to the cold head (211), the electrical unit (22) comprises an electrical integration (221) and an electrical connection connected to the electrical integration (221), the cold head (211) and the electrical integration (221) are integrated on a first cover (231) of the control box (23), and the refrigeration connection second cover and the electrical connection are connected to the magnet assembly (1) through the connecting pipe (24).

10. The superconducting magnet device according to claim 9, characterized in that: A connection cavity (241) is formed in the connection pipe (24), and the control assembly (2) further comprises a connection wire protection cover (25), and the connection wire protection cover (25) is arranged in the connection cavity (241); the refrigeration connection is arranged in the connection cavity (241) and is located outside the connection wire protection cover (25); the electrical connection is arranged in the connection wire protection cover (25) and is separated from the refrigeration connection by the connection wire protection cover (25); And / or, the control box (23) comprises a second cover (232) made of a transparent material.

11. The superconducting magnet device according to claim 10, characterized in that: The second cover body (232) is made of carbon fiber reinforced polyimide composite material.

12. A particle accelerator, characterized in that: Comprising a superconducting magnet device as described in any one of claims 1-11.

13. A radiotherapy device, characterized in that: Comprising the particle accelerator of claim 12.

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