A compact medical isotope production cyclotron

Abstract

The present application relates to the transmission shaft paint spraying technical field, disclose a kind of compact medical isotope production's cyclotron: on support, wheel belt and paint spraying chamber, drying chamber and spray gun foundation, there are spin shift, pre-grinding and wipe clean department.Spin shift in transport makes transmission shaft rotate around shaft, to facilitate circumferential uniform paint spraying and drying;Pre-grinding is rotated pre-grinding by magnetic force to make friction piece and shaft body adhere;Wipe clean department removes iron filings dust by pushing away friction piece and reciprocating wiping shaft surface at set timing.The device completes pre-grinding, wiping, paint spraying and drying on continuous conveying path, improves the uniformity and adhesion of paint film.

Description

Technical Field

[0001] This invention relates to the field of cyclotron technology, and more specifically to a compact cyclotron for the production of medical isotopes. Background Technology

[0002] Medical isotopes (such as fluorine-18, carbon-11, nitrogen-13, and oxygen-15) play an irreplaceable role in modern medical imaging diagnosis (especially PET-CT scans) and targeted radiotherapy. Currently, hospitals and radiopharmaceutical production centers mainly rely on medical cyclotrons to produce these short-lived radioisotopes. With the popularization of precision medicine, the demand for cyclotrons in medical institutions is increasing, especially requiring equipment that is miniaturized, highly stable, and easy to maintain.

[0003] However, cyclotrons used for medical isotope production typically suffer from performance redundancy in practical applications, facing high space and cost barriers. They often prioritize high beam energies and extraction currents, resulting in significant performance redundancy for the preparation of conventional clinical radiopharmaceuticals. This leads to a large overall size, increased weight, and high manufacturing costs. Furthermore, high energy and high current also necessitate thicker radiation shielding, greatly increasing investment in supporting infrastructure. Additionally, large errors exist in magnet processing and assembly, making magnetic field compensation difficult. Magnetic field isochronism is crucial for the stable operation of cyclotrons, and the magnetic yoke and pole base are often fabricated separately and then assembled, making them highly susceptible to defects. Assembly gaps and accumulated errors occur at the joint surfaces, which in turn introduce harmful magnetic field first harmonics. A lot of time and effort is required for tedious magnetic field compensation work later. At the same time, the vacuum pumping speed is slow, the operation and maintenance costs are high, the vacuum chamber volume is huge, and it takes a long time to pump to high vacuum after each start-up or internal maintenance, resulting in low debugging efficiency. Moreover, the adjustment of key internal components is limited. Axial focusing in the accelerator center area and monitoring of the beam trajectory across the entire radius are crucial to ensuring high-quality beam extraction, but the existing beam diagnostic system often has detection blind spots. Improper arrangement of the ion source cooling pipeline can also cause mid-plane beam loss. Summary of the Invention

[0004] This invention provides a compact cyclotron for medical isotope production to solve the problems of large size, low precision in magnetic field processing and assembly, cumbersome magnetic field padding, slow pumping speed due to large vacuum chamber volume, and blind spots in beam monitoring.

[0005] To solve the above-mentioned technical problems, the technical solution of the present invention is as follows: In one aspect, a compact cyclotron for producing medical isotopes includes: a magnet system, an ion source system, a radio frequency system, a stripping extraction system, a target system, a beam diagnostic system, a hydraulic lifting system, and a vacuum system.

[0006] The magnet system includes a yoke, excitation coils, pole bases, poles, inserts, and a core. The yoke, pole base, and poles are integrally milled. The pole base and poles work together to form alternating peak and valley regions. The pole base has detachably connected inserts and a core, which achieve isochronous adjustment of the accelerator's magnetic field through cutting and padding. The core is mounted in the central region of the magnet system, with adjustable height, and is used to adjust the magnetic field gradient in the central region and provide axial focusing force.

[0007] The radio frequency system employs a compact structure and is matched with shallow valley magnets, sharing the same location within the valley region of the magnet system as the beam diagnostic system. The vacuum system includes a vacuum shroud mounted on a magnetic pole base. The target system utilizes a copper substrate and is equipped with a composite heat dissipation structure combining water and air cooling. The ion source system provides negative hydrogen ions, with water-cooled piping arranged on the upper and lower sides of the ion source cavity, avoiding the mid-plane beam path. The active detection radius of the beam diagnostic system is configured to be 60mm–360mm.

[0008] Preferably, the magnet system includes an upper magnet and a lower magnet that are aligned, and a hydraulic lifting system is symmetrically arranged on both sides of the magnet system. The fixed end is connected to the lower magnet, and the telescopic end is connected to the upper magnet, which facilitates the alignment and maintenance of the magnets.

[0009] Preferably, the radio frequency system includes a high-frequency electrode, a high-frequency electrode cooling water circuit, an outer conductor, and a coupling device; the stripping and extraction system includes a stripping and extraction device and a stripping membrane; and the beam diagnostic system includes a beam diagnostic system support, a transmission device, and a radial probe.

[0010] The above-described solution of the present invention has at least the following beneficial effects: By integrating the yoke, pole base, and poles through milling, assembly gaps and accumulated errors caused by multi-component splicing are eliminated, suppressing first harmonics of the magnetic field. Combined with detachable inserts and height-adjustable core columns, isochronous patching is more precise and convenient, shortening the debugging cycle. A compact RF system and shallow-valley magnet design, combined with a vacuum chamber layout relying on the pole base, effectively reduce the overall size and weight of the device, lowering manufacturing costs and radiation shielding pressure, facilitating deployment in space-constrained medical institutions. Optimized vacuum chamber volume shortens vacuuming time during start-up, shutdown, and maintenance, improving the equipment's online operating rate. Vertically and horizontally aligned ion source water-cooling pipelines reduce mid-plane beam loss. A beam diagnostic system with a 60mm–360mm detection range enables full beam trajectory monitoring. Core column adjustment ensures stable production of high-quality isotopes, achieving equipment miniaturization while significantly improving magnetic field uniformity, vacuuming efficiency, and beam extraction stability. Attached Figure Description

[0011] Figure 1 This is a schematic diagram of the overall structure of the cyclotron accelerator according to an embodiment of the present invention; Figure 2This is a schematic diagram of the main magnet system structure according to an embodiment of the present invention; Figure 3 This is a top sectional view of the cyclotron accelerator according to an embodiment of the present invention; Figure 4 This is a schematic diagram of the radio frequency system structure according to an embodiment of the present invention; Figure 5 This is a schematic diagram of the ion source system structure according to an embodiment of the present invention; Figure 6 This is a schematic diagram of the stripping and extraction system structure according to an embodiment of the present invention; Figure 7 This is a schematic diagram of the beam diagnosis system structure according to an embodiment of the present invention; Figure 8 This is a schematic diagram of the planar structure of the vacuum chamber according to an embodiment of the present invention; Figure 9 This is a schematic diagram of the target system structure according to an embodiment of the present invention.

[0012] Explanation of reference numerals in the attached figures: In the diagram: 1. Magnet system; 11. Magnetic yoke; 12. Excitation coil; 13. Magnetic pole base; 14. Magnetic pole; 15. Strip; 16. Core column; 17. Peak region; 18. Valley region; 2. Ion source system; 21. Ion source; 22. Ion source cooling pipeline; 3. Radio frequency system; 31. High-frequency electrode; 32. High-frequency electrode cooling water channel; 33. Outer conductor; 34. Coupling device; 4. Stripping and lead-out system; 41. Stripping membrane; 42. Stripping and extraction device; 5. Target system; 51. Water-cooled pipeline; 52. Air-cooled pipeline; 53. Liquid transfer pipeline; 54. Copper substrate; 55. Vacuum pipeline; 6. Hydraulic lifting system; 7. Vacuum system; 70. Vacuum hood; 71. Stripping and extraction opening; 72. Target opening; 73. High-frequency opening; 74. Beam diagnostic opening; 8. Beam diagnostic system; 81. Radial probe; 82. Transmission device; 83. Beam diagnostic system support. Detailed Implementation

[0013] Exemplary embodiments of the invention will now be described in more detail with reference to the accompanying drawings. While exemplary embodiments of the invention are shown in the drawings, it should be understood that the invention may be implemented in various forms and should not be limited to the embodiments set forth herein. Rather, these embodiments are provided so that this invention will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art.

[0014] like Figures 1 to 9 As shown in the first embodiment of the present invention, this embodiment provides a compact cyclotron accelerator for the production of medical isotopes, which mainly includes a magnet system 1, an ion source system 2, a radio frequency system 3, a stripping extraction system 4, a target system 5, a hydraulic lifting system 6, a vacuum system 7, and a beam diagnostic system 8.

[0015] The magnet system 1 includes an upper magnet and a lower magnet arranged opposite each other. An ion source system 2 is located in the central region inside the magnet system 1; a radio frequency system 3 is symmetrically arranged in the valley region 18 inside the magnet system 1; a stripping extraction system 4 is installed through one side of the magnet system 1; and a target system 5 is located inside the magnet system 1. A hydraulic lifting system 6 is symmetrically arranged on both sides of the magnet system 1, with its fixed end connected to the lower magnet via a fixing component and its telescopic end connected to the upper magnet via a connecting component, used for opening, closing, and maintaining the upper magnet; a vacuum system 7 is connected below the magnet system 1; and a beam diagnostic system 8 is located outside the magnet system 1 and extends to the valley region 18, spatially independent of the radio frequency system 3.

[0016] When the subsystems work together: Ion source system 2 generates negative hydrogen ions near the mid-plane; magnet system 1 provides an isochronous magnetic field; radio frequency system 3 repeatedly accelerates ions in valley region 18; beam diagnostic system 8 monitors beam quality in real time within a radius of 60mm to 360mm; after the negative hydrogen ions are accelerated to the rated energy, electrons are stripped away by stripping extraction system 4 to form a proton beam and bombard target system 5 to produce isotopes; vacuum system 7 maintains high vacuum in the acceleration region; hydraulic lifting system 6 ensures magnet alignment accuracy and ease of maintenance.

[0017] In practical applications, the entire system of this embodiment can be deployed in a hospital radiopharmaceutical preparation workshop or isotope production center. After the equipment is powered on, each subsystem operates in a coordinated manner in the following order: vacuuming, magnetization, radio frequency application, ion extraction, acceleration, stripping extraction, and target firing: the vacuum system 7 first establishes a working vacuum, the ion source system 2 and the radio frequency system 3 work together in the magnetic field provided by the magnet system 1 to accelerate negative hydrogen ions, the beam diagnostic system 8 provides feedback on the beam status throughout the process, and the stripping extraction system 4 converts high-energy negative ions into a proton beam and delivers it to the target system 5 to complete the preparation of short-lived isotopes such as fluorine and carbon; during routine maintenance, the hydraulic lifting system 6 lifts the upper magnet, which facilitates the inspection and replacement of the radio frequency system 3, beam diagnostic system 8, and ion source system 2 in the valley area 18, significantly reducing the difficulty of operation and maintenance and meeting the comprehensive requirements of medical institutions for equipment compactness, stability, and ease of maintenance.

[0018] Example 2, as Figure 2 As shown, the main magnet system 1 includes a yoke 11, an excitation coil 12, a magnetic pole base 13, a magnetic pole 14, an inlay 15, and a core column 16.

[0019] In this embodiment, the magnetic yoke 11, magnetic pole base 13 and magnetic pole 14 are integrally milled and formed by a large CNC machine tool, eliminating the mechanical gap and cumulative error generated at the joint surface in the traditional splicing process, reducing the first harmonic of the magnetic field and reducing the amount of subsequent padding work; the magnetic pole 14 and magnetic pole base 13 are integrally formed and form an X-shaped symmetrical layout, and the two together form a peak area 17 and valley area 18 that are alternately distributed in the circumferential direction.

[0020] The insert 15 is symmetrically and detachably connected to the magnetic pole base 13, located between the magnetic pole 14 and the magnetic pole base 13. During the commissioning phase, the main magnetic field is precisely adjusted isochronously by cutting and padding the insert 15; the core column 16 is set in the middle of the magnetic pole base 13, and its height is physically adjustable. By finely adjusting its up and down position, the magnetic field gradient in the central area is changed, providing axial focusing force for accelerating ions in the initial stage and suppressing beam divergence.

[0021] The excitation coil 12 is arranged in a ring inside the magnetic yoke 11 and surrounds the magnetic pole base 13. After being energized, it establishes the main magnetic field. The outer side of the magnetic yoke 11 is connected to the fixed end of the hydraulic lifting system 6, forming a closed magnetic circuit and mechanical support.

[0022] In practical applications, the magnet system 1 ensures magnetic field symmetry through integrated milling during the equipment manufacturing stage. After leaving the factory, only a small amount of padding is required to achieve isochronism requirements. During equipment installation and commissioning, technicians perform targeted cutting on the insert 15 based on magnetic field measurement results to correct the circumferential magnetic field distribution. Simultaneously, the height of the core column 16 is adjusted to optimize axial focusing in the central region, ensuring that the beam drawn from the ion source 21 remains compact in the initial acceleration phase. After the excitation coil 12 is energized, the alternating magnetic field distribution in the peak region 17 and valley region 18 guides the ions to perform cyclotron motion, providing a stable magnetic confinement environment for repeated acceleration by the radio frequency system 3. Compared with separately assembled magnets, this embodiment significantly shortens the magnetic field padding cycle and improves equipment delivery and on-site commissioning efficiency.

[0023] Example 3 Figure 3 , Figure 4 As shown, in order to achieve device compactness, the radio frequency system 3 adopts a compact resonant cavity structure that matches the shallow valley magnet and is placed in the valley region 18.

[0024] The radio frequency system 3 includes a high-frequency electrode 31, a high-frequency electrode cooling water channel 32, an outer conductor 33, and a coupling device 34. The high-frequency electrode 31 is located at the acceleration gap in the valley region 18. The high-frequency electrode cooling water channel 32 is arranged around the inner edge of the high-frequency electrode 31 to remove the heat generated by high-frequency power loss. The outer conductor 33 is symmetrically arranged on both sides of the high-frequency electrode 31 to form the outer wall of the resonant cavity and constrain the electromagnetic field distribution. The coupling device 34 is located at the end of the high-frequency electrode 31 away from the core column 16 and is connected to the high-frequency electrode cooling water channel 32 to realize the connection between power feed and cooling circuit.

[0025] The radio frequency system 3 provides an accelerating voltage for ions within the valley region 18. Its compact structure, in conjunction with the shallow valley magnet, avoids occupying additional radial space and is one of the keys to the miniaturization of the entire device.

[0026] In practical applications, the radio frequency system 3 receives energy fed from an external high-frequency power source through the coupling device 34, and establishes an accelerating electric field in the resonant cavity composed of the high-frequency electrode 31 and the outer conductor 33. The negative hydrogen ions pass through the accelerating gap in the valley region 18 twice and gain energy after each revolution. After dozens to hundreds of revolutions, the rated energy required for the production of medical isotopes is reached. The high-frequency electrode cooling water circuit 32 continuously removes the heat generated by the electrodes during the continuous operation of the equipment, preventing the resonant frequency from drifting and the accelerating voltage from becoming unstable due to temperature rise. The radio frequency system 3 is matched with the shallow valley structure of the magnet system 1, making full use of the space in the valley region 18 without increasing the radial dimension of the magnet, so that the whole machine can adapt to the installation requirements of medical institutions with limited space.

[0027] Example 4, as Figure 5 As shown, the ion source system 2 adopts an internal ion source 21 structure, including the ion source 21 and the ion source cooling pipe 22.

[0028] Ion source 21 is located in the central region of magnetic pole base 13 and is used to generate and extract negative hydrogen ions. During operation, ion source 21 generates a large amount of heat, which is carried away by ion source cooling pipe 22. In this embodiment, ion source cooling pipe 22 is arranged on the upper and lower sides of the cavity of ion source 21, so that the pipe is completely offset from the plane of the accelerator. Structurally, this avoids the beam hitting the pipe and causing loss, thereby improving extraction efficiency and beam quality.

[0029] In practical applications, after the equipment is started, the ion source 21 is first ignited and stably generates a negative hydrogen ion beam. The ion beam is injected into the central region of the magnetic field along the plane of the accelerator. Cooling water is circulated through the ion source cooling pipe 22 to remove the heat generated by the ion source 21 during operation, ensuring the stability of the ion source 21 during long-term operation and the consistency of ion yield. Since the ion source cooling pipe 22 is arranged on the upper and lower sides of the cavity of the ion source 21 rather than in the middle plane, the negative hydrogen ion beam will not physically collide with the pipe during the extraction and initial acceleration stages, avoiding beam loss and impurity introduction. This results in the beam entering the subsequent acceleration orbit having higher intensity and better quality, laying the foundation for the final high-quality isotope production.

[0030] Example 5, such as Figure 6 As shown, the peeling and extraction system 4 includes a peeling and extraction device 42 and a peeling membrane 41.

[0031] The stripping extraction device 42 is installed through the magnetic yoke 11, and the stripping membrane 41 is installed at its driving end and located in the extraction channel on the magnetic pole 14. When the negative hydrogen ions are accelerated to the rated energy, the ion beam enters the extraction channel and strips two electrons at the stripping membrane 41 to convert them into a proton beam. The beam is then guided to the target system 5 by the stripping extraction device 42. This structure realizes the functional conversion of negative hydrogen ion acceleration and proton extraction, which meets the needs of medical isotope production for proton bombardment target materials.

[0032] In practical applications, once the beam diagnostic system 8 confirms that the beam energy and position meet the extraction conditions, the negative hydrogen ion beam deflects along the extraction channel on the magnetic pole 14 and enters the stripping extraction system 4. When the ion beam passes through the stripping membrane 41, two electrons are stripped, and the beam is converted into a proton beam, which is then precisely guided to the target surface of the target system 5 by the stripping extraction device 42. This process achieves a smooth transition from negative ion acceleration to proton target hitting, avoiding the dependence of traditional positive ion cyclotron accelerators on the central ion source and simplifying the extraction structure. The stripping membrane 41 can be replaced according to the usage conditions, and the through-type arrangement of the stripping extraction device 42 facilitates maintenance from outside the accelerator, ensuring the continuity and reliability of isotope production.

[0033] Example 6, as Figure 1 , Figure 3 and Figure 9 As shown, the target system 5 includes a copper substrate 54, a vacuum pipe 55, a liquid transfer pipe 53, a water-cooled pipe 51, and an air-cooled pipe 52.

[0034] The copper substrate 54 is located inside the magnetic yoke 11 and on one side of the beam system 8. It has water-cooling channels inside and air-cooling fins on the outside. The vacuum pipe 55 is located at one end of the copper substrate 54 and connected to the vacuum system 7 to ensure vacuum in the target area. The liquid transmission pipe 53 is symmetrically arranged on both sides of the copper substrate 54 and corresponds to the water-cooling channels. The water-cooling pipe 51 is located at the other end of the copper substrate 54 and corresponds to the water-cooling channels, forming a circulating water-cooling system. The air-cooling pipe 52 is located at the end of the copper substrate 54 and corresponds to the air-cooling fins to enhance surface heat dissipation.

[0035] When the proton beam bombards the target material on the copper substrate 54, a large amount of heat is generated. The combined heat dissipation structure of water cooling and air cooling works together: the water cooling channel removes the heat inside the target material, and the air cooling fins accelerate the heat dissipation on the outer surface, ensuring thermal stability under long-term high-load target bombardment and extending the life of the target material.

[0036] In practical applications, the proton beam, after being extracted by the stripping system 4 and introduced into the target system 5, bombards the enriched target material (such as oxygen, water, etc.) mounted on the copper substrate 54, generating the desired radioactive isotopes through nuclear reactions. During the firing process, the liquid transport pipeline 53 and the water cooling pipeline 51 deliver coolant to the water cooling channels inside the copper substrate 54, quickly removing heat from the core area of ​​the target material. The air cooling pipeline 52 delivers air to the air cooling fins, enhancing heat dissipation from the outer surface of the copper substrate 54. The combined operation of water cooling and air cooling keeps the target material temperature within a safe range, preventing production interruptions caused by target melting or vaporization. The vacuum pipeline 55 is connected to the vacuum system 7, ensuring a high vacuum environment is maintained in the firing area, reducing beam scattering and radioactive gas accumulation, and improving isotope yield and production safety.

[0037] Example 7, as Figure 7As shown, the beam diagnostic system 8 includes a beam diagnostic system support 83, a transmission device 82, and a radial probe 81.

[0038] The beam diagnostic system support 83 is located on the outside of the magnetic yoke 11. The transmission device 82 is fixed to the upper end of the beam diagnostic system support 83. The radial probe 81 is located at the driving end of the transmission device 82 and extends into the valley area 18 above the magnetic pole base 13. The transmission device 82 drives the radial probe 81 to move radially along the magnetic yoke 11. The active detection radius is 60mm to 360mm, covering the area from the central lead-out area to the peripheral high-energy area, eliminating the detection blind zone.

[0039] The beam diagnostic system 8 and the radio frequency system 3 are both located in the valley region 18, but their functions are independent: the radio frequency system 3 is responsible for acceleration, while the beam diagnostic system 8 is responsible for monitoring the beam position and profile, providing real-time data for debugging and operation, and ensuring the stability of isotope production quality.

[0040] In practical applications, the beam diagnostic system 8 plays a crucial role in both equipment commissioning and daily operation. During commissioning, operators drive the radial probe 81 through the transmission device 82 to scan gradually within a range of 60mm to 360mm, acquiring information on the position, profile, and current intensity of the beam at different radii. Based on this, the height of the insert 15, the core post 16, and the parameters of the RF system 3 are adjusted to optimize beam quality. During normal operation, the beam diagnostic system 8 periodically monitors the beam at key radii. Once beam deviation or divergence is detected, an alarm is issued for timely intervention. The radial probe 81 extends into the valley region 18 for detection without interfering with the RF system 3, achieving full beam monitoring from the center region to the extraction region and eliminating the detection blind spots of traditional equipment.

[0041] Example 8, as Figure 8 As shown, the vacuum system 7 also includes a vacuum pump located below the magnetic yoke 11. The suction end of the vacuum pump is connected to the vacuum cover 70 through a connecting pipe passing through the magnetic yoke 11. The core of the vacuum system 7 is the vacuum cover 70. The vacuum cover 70 is tightly attached to and supported by the magnetic pole base 13. Unlike the traditional bulky vacuum chamber that wraps the whole machine, it significantly compresses the volume of the vacuum chamber, improves the pumping efficiency, and shortens the vacuuming time for start-up, shutdown, and maintenance.

[0042] The vacuum chamber 70 has a stripping lead-out opening 71, a target opening 72, a high-frequency opening 73, and a beam diagnostic opening 74, which are respectively used for the stripping lead-out system 4, the target system 5, the radio frequency system 3, and the beam diagnostic system 8 to pass through, so as to achieve the integrated integration of each subsystem with the vacuum chamber while ensuring sealing.

[0043] In practical applications, the vacuum system 7 is started first after each power-on or internal maintenance. The vacuum pump group evacuates the inner cavity of the vacuum cover 70, which is set against the magnetic pole base 13. Since the vacuum cover 70 is close to the magnetic pole base 13 and its volume is much smaller than the vacuum chamber that traditionally wraps the whole machine, the time to reach a high vacuum state is greatly shortened, and the equipment can enter the accelerated operation state more quickly. The stripping lead-out hole 71, target hole 72, high frequency hole 73 and beam diagnostic hole 74 are sealed while being connected to the stripping lead-out system 4, target system 5, radio frequency system 3 and beam diagnostic system 8, to avoid leakage affecting the vacuum level. During daily operation, the vacuum system 7 continuously maintains a high vacuum environment in the acceleration area, reducing beam loss caused by collisions between the ion beam and residual gas. After maintenance, the vacuum is quickly restored, improving the online operation rate and overall utilization efficiency of the equipment.

[0044] The above description represents the preferred embodiments of the present invention. It should be noted that those skilled in the art can make various improvements and modifications without departing from the principles of the present invention, and these improvements and modifications should also be considered within the scope of protection of the present invention.

Claims

1. A compact cyclotron for producing medical isotopes, characterized in that, The accelerator includes: a magnet system and an ion source system disposed within the magnet system; The magnet system includes an upper magnet and a yoke arranged in pairs, an excitation coil, a magnetic pole base, magnetic poles, inserts, and a core post; wherein, the magnetic pole base and the magnetic poles are integrally milled; the magnetic pole base is provided with detachably connected inserts and core posts, and the inserts and core posts are configured to achieve isochronous adjustment of the accelerator's magnetic field through cutting padding; the magnetic pole base and the magnetic poles cooperate to form alternating peak and valley regions; A radio frequency system is symmetrically arranged inside the magnet system. A stripping and extraction system is provided through one side of the magnet system. A target system is arranged inside the magnet system. A hydraulic lifting system is symmetrically arranged on both sides of the magnet system. The fixed end of the hydraulic lifting system is connected to the lower magnet through a fixing component, and the telescopic end is connected to the upper magnet through a connecting component. A vacuum system is connected to the bottom of the magnet system. A beam diagnostic system is arranged on the outside of the magnet system. The radio frequency system adopts a compact structure and is matched with a shallow valley magnet, and is set in the valley region of the magnet system; the beam diagnostic system is set in the valley region of the magnet system, and the active detection radius is configured to be 60mm~360mm; The vacuum system includes a vacuum shroud, which is mounted on a magnetic pole base; The ion source system is used to provide negative hydrogen ions and includes ion source water-cooling pipelines arranged on the upper and lower sides of the ion source cavity to avoid the beam trajectory on the plane of the accelerator.

2. The compact cyclotron for medical isotope production according to claim 1, characterized in that, The magnet system includes an upper magnet and a lower magnet that are coupled together; the fixed end of the hydraulic lifting system is connected to the lower magnet through a fixing component, and the telescopic end is connected to the upper magnet through a connecting component.

3. The compact cyclotron for medical isotope production according to claim 2, characterized in that, The magnetic pole and the magnetic pole base are integrally milled to form an X-shaped symmetrical layout; the core column is installed in the central area of ​​the magnet system, and the height of the core column is adjustable to adjust the magnetic field gradient in the central area and provide axial focusing force.

4. The compact cyclotron for medical isotope production according to claim 3, characterized in that, The magnet system is manufactured as a single unit and is configured to reduce the first harmonic of the magnetic field and reduce the difficulty of magnet padding.

5. The compact cyclotron for medical isotope production according to claim 4, characterized in that, The radio frequency system includes: a high-frequency electrode, a high-frequency electrode cooling water channel arranged around the inner edge of the high-frequency electrode, an outer conductor symmetrically arranged on both sides of the high-frequency electrode, and a coupling device disposed at the end of the high-frequency electrode away from the core post; the coupling device is connected to the high-frequency electrode cooling water channel.

6. The compact cyclotron for medical isotope production according to claim 5, characterized in that, The stripping extraction system includes a stripping extraction device disposed through the magnetic yoke, and a stripping membrane disposed at the drive end of the stripping extraction device and located within the magnetic pole extraction channel, for converting negative hydrogen ions into proton beams.

7. The compact cyclotron for medical isotope production according to claim 6, characterized in that, The target system includes a copper substrate with water-cooled channels machined inside and air-cooled heat dissipation fins arranged on the outside. It is also equipped with water-cooled pipes and air-cooled pipes to form a composite heat dissipation structure that combines water cooling and air cooling.

8. The compact cyclotron for medical isotope production according to claim 7, characterized in that, The beam diagnostic system includes a beam diagnostic system bracket disposed on the outside of the magnetic yoke, a transmission device fixed to the upper end of the beam diagnostic system bracket, and a radial probe disposed on the drive end of the transmission device and extending above the magnetic pole base, the radial probe being configured to move radially along the magnetic yoke.

9. The compact cyclotron for producing medical isotopes according to claim 8, characterized in that, The ion source is located in the central region of the magnetic pole base.

10. The compact cyclotron for medical isotope production according to claim 9, characterized in that, The vacuum cover is provided with stripping lead-out holes, target holes, high-frequency holes and beam diagnostic holes.

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