Cyclotron particle therapy center provided with switchable therapy system linear acceleration type range shifter

Abstract

A cyclotron particle therapy center provided with a linear acceleration type range shifter of a switchable therapy system comprises a particle cyclotron (1), an energy selection system (2) and the linear acceleration type range shifter (3), wherein the energy selection system (2) and the linear acceleration type range shifter (3) are sequentially connected with the particle cyclotron (1) in series, and a multi-angle deflection magnet (4) receives a particle beam emitted by the linear acceleration type range shifter (3). The linear acceleration type measuring range shifter (3) is in butt joint with M beam transport sections (5) after deflection, M is larger than 1, the M beam transport sections (5) are in butt joint with a two-way scanning treatment system (6), the use of the linear acceleration type measuring range shifter (3) greatly improves the tumor depth scanning speed, the volume recoating scanning method is more efficient, the use method of the switchable treatment system achieves multiple purposes, and the application range of the linear acceleration type measuring range shifter (3) is wider than the application range of the linear acceleration type measuring range shifter (3), so that the application range of the linear acceleration type measuring range shifter (3) is wider than the application range of the linear acceleration type measuring range shifter (3). The path of a beam transport section is shortened, and the use number of electromagnetic components is reduced.

Description

Technical Field

[0001] The present invention relates to particle radiotherapy, wherein the particles may be light ions such as protons or heavy ions such as carbon ions. Background Art

[0002] Previously, the inventor applied for an invention patent for a series of parallel beam bidirectional scanning, which is of great significance for maximizing the focal-to-skin ratio, but has not yet effectively solved the problem of tumor movement faced by scanning irradiation therapy.

[0003] Among the various methods to solve the problem of tumor movement, volume recoating is an effective and easy-to-operate method.

[0004] Volume recoating places two rigid requirements on radiotherapy equipment: 1. The beam is continuous. Therefore, only particle cyclotron accelerators or particle linear accelerators that can continuously emit beams can be selected.

[0005] 2. Rapid energy adjustment, reaching the millisecond level. This cannot be achieved by cyclotron accelerators that change energy through an absorber-type energy selection system, nor by synchrotron accelerators that cannot adjust energy rapidly due to the acceleration cycle limit. Only linear accelerators can do this. However, linear accelerators are too expensive and have high operating costs, making them difficult to use in radiotherapy.

[0006] A research team suggested that the cyclotron accelerator be connected to the linear accelerator, with the cyclotron responsible for the low-energy part and the linear accelerator responsible for the medium and high-energy part, which is called a cyclotron linear accelerator. This solution can reduce manufacturing costs and operating costs to a certain extent, but the reduction is still not enough.

[0007] The inventors propose a more economical solution, which is to replace only the range shifter in the home treatment system in the cyclotron treatment center with a linear accelerator.

[0008] In order to further reduce the usage of accelerating cavities in the linear accelerator, the accelerating cavities can be made capable of both acceleration and deceleration. Compared with those capable of only acceleration, the number of accelerating cavities can be reduced by about half.

[0009] In the case of a multi-room treatment center, in order not to increase the number of linear accelerators in use, the linear accelerator range shifter can be switched between multiple treatment systems, allowing multiple treatment systems to share one linear accelerator range shifter.

[0010] By adopting the switching method, multiple linear beam transport sections in traditional treatment centers can also be omitted. The saved electromagnetic equipment can partially offset the increase in manufacturing costs caused by adding a linear accelerator-type range shifter.

[0011] The use of superconducting design can significantly reduce the power consumption of the linear accelerator part.

[0012] After configuring the linear acceleration range shifter, the scanning speed in three directions is very fast. Not only can the volume recoating technology be adopted, but the scanning irradiation time can also be greatly shortened. Summary of the invention

[0013] The present invention aims at the difficulty of effectively exerting the effect of volume recoating method in the parallel beam bidirectional scanning irradiation treatment system invented by the inventor. In order to improve the scanning speed in the depth direction of the tumor, a linear acceleration range shifter is used to replace the traditional absorber range shifter, and the linear acceleration range shifter can be switched between multiple treatment systems. The work associated with this is to design and plan the style and function of the linear acceleration range shifter, and to transform the traditional style cyclotron treatment center. The specific plan is: A particle cyclotron is set up to produce a particle beam of fixed energy that meets the needs of radiotherapy.

[0014] Furthermore, an energy selection system is provided, which is responsible for selecting the energy downward by blocking the particle beam with an absorber on the basis of the fixed energy output by the cyclotron, and is responsible for controlling the increase in beam divergence and energy divergence caused by the energy selection, so as to facilitate subsequent arrangements and make the particle beam emitted by the energy selection system point vertically downward.

[0015] Furthermore, a linear acceleration range shifter is provided, which is responsible for changing the energy of the particle beam by accelerating and decelerating so as to modulate the range of the particle beam in the patient's body. One end of the linear acceleration range shifter receives the particle beam emitted vertically downward by the energy selection system, and the other end emits a horizontal particle beam.

[0016] Furthermore, a multi-angle deflection magnet is provided to receive the particle beam output by the linear acceleration range shifter, and can be deflected to M specific angles in the horizontal plane, M>1.

[0017] Furthermore, M horizontal beam transport sections are provided, the inlet of which receives Horizontal particle beam emitted by multi-angle deflection magnets.

[0018] Furthermore, M bidirectional scanning treatment systems are provided to respectively receive the particle beams emitted from the M horizontal beam transport sections.

[0019] Furthermore, a double-layer radiation shielding device is set up, in which the particle cyclotron and the energy selection system are placed in the upper layer; the linear acceleration range shifter, the multi-angle deflection magnet, M horizontal beam transport sections and M bidirectional scanning treatment systems are placed in the lower layer, and the treatment room where the M bidirectional scanning treatment systems are placed is separated from the machine room where the linear acceleration range shifter, the multi-angle deflection magnet and the M horizontal beam transport sections are placed.

[0020] Furthermore, M hollow rectangular through-the-wall passages (8) opening toward one side of the machine room are provided to achieve communication between the machine room and the M treatment rooms.

[0021] The above-arranged cyclotron particle therapy center configured with a switchable treatment system linear acceleration range shifter realizes multiple uses of one device while accelerating the scanning speed in the depth direction of the tumor, effectively controlling the increase in cost. At the same time, the M horizontal beam transport sections arranged in a fan shape directly connect the particle beam modulated by the linear acceleration range shifter and changed in angle by the multi-angle deflection magnet to the M bidirectional scanning treatment systems, saving many electromagnetic components and making up for the cost increase caused by the addition of the linear acceleration range shifter to a certain extent. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] Figure 1 , Composition and layout of electromagnetic components of the treatment center Figure 2 , Linear acceleration range shifter structure diagram Figure 3 , Multi-angle deflection magnet structure diagram Figure 4 , Multi-angle deflection magnets Schematic diagram of multi-angle deflection of particle beams Figure 5 , Horizontal beam transport section structure diagram Figure 6 , Appearance of the treatment center after installing radiation shielding device Figure 7 , Sectional view of the upper floor of the treatment center after the installation of radiation shielding device Figure 8 , Sectional view of the lower floor of the treatment center after the installation of radiation shielding device Symbols in the figure: 1. A particle cyclotron 2. An energy selection system 3. A linear acceleration range shifter 3-1. A 90° deflection magnet 3-2. N+1 Focusing Guide Section 3-2-1. A set of focusing magnets A 3-2-2. A bidirectional guide magnet A 3-2-3. An ionization chamber A 3-3. N phase-adjustable linear acceleration structure 3-4. N klystrons 300. Particle beam emitted from a linear acceleration range shifter 4. A multi-angle deflection magnet 4-1. Two magnetic poles 4-2, three groups, two winding poles each 4-3. Three groups of two excitation coils each 4-4. Two conjoined C-shaped yokes 400. After being deflected by a multi-angle deflection magnet, a particle beam is emitted at M determined angles 5. M horizontal beam transport sections 5-1. A horizontal guide magnet 5-2. A water vertical guide magnet 5-3. An ionization chamber B 5-4. A set of focusing magnets B 5-5. A bidirectional guide magnet B 5-6. An ionization chamber C 6. M bidirectional scanning treatment systems 7. A radiation shielding device 8. M wall-penetrating channels DETAILED DESCRIPTION

[0023] The specific embodiments of the present invention are described in detail below in conjunction with the accompanying drawings. Without violating the scope of the present invention, the present invention is not limited by the specific embodiments disclosed below.

[0024] This embodiment is a cyclotron particle therapy center equipped with a switchable therapy system linear acceleration range shifter.

[0025] The drawings of this embodiment are designed by taking proton as an example.

[0026] like Figure 1 As shown, this embodiment includes a particle cyclotron 1, which is responsible for generating a particle beam with a fixed energy that can meet the needs of radiotherapy.

[0027] The fixed energy is determined according to the range of the particle beam in the human body required for radiotherapy. The higher the energy, the longer the range.

[0028] Taking protons as an example, when the maximum range in the body is 30cm, the fixed output energy must reach 250MeV.

[0029] like Figure 1 As shown, this embodiment further includes an energy selection system 2, which is responsible for selecting energy downward based on the fixed energy output by the cyclotron 1 by blocking the particle beam with an absorber.

[0030] The energy selection system 2 mainly consists of five functional sections: 1. Preparation The preparation section is mainly composed of a focusing magnet and a guide magnet. While adjusting the divergence of the particle beam and the position of the particle beam axis, the beam waist of the particle beam is adjusted to the position of the energy degrader as described later.

[0031] 2. Energy reduction stage The energy reduction section is mainly composed of an energy reducer. The core of the energy reducer is an absorber with adjustable thickness. When the particle beam passes through the absorber, the energy is reduced due to absorption. The thicker the absorber, the greater the energy reduction. The energy reduction can be adjusted by adjusting the thickness of the absorber through which the particle beam passes. The maximum energy reduction is determined by the shortest range of the particle beam in the human body required for radiotherapy, such as 70MeV~250MeV.

[0032] 3. Dissipation stage This section is mainly composed of focusing magnets and beam limiting slits. When the particle beam passes through the absorber of the energy degrader, in addition to the energy being reduced, it will also cause the particle beam to diverge greatly. It is first adjusted by the focusing magnet, and the divergent particles exceeding a certain value are filtered out by the beam limiting slit.

[0033] 4. Energy dissipation section The energy dissipation section is mainly composed of deflection magnets and beam limiting slits. When the particle beam passes through the absorber of the energy degrader, it will also cause energy divergence. The deflection magnet can be used to distinguish the energy divergent particle beam, and the particles whose energy divergence exceeds a certain value can be filtered out by the beam limiting slit.

[0034] The deflection direction of the deflection magnet in the energy dissipation section is arbitrary. According to the overall layout requirements of this embodiment, the particle beam deflected by the deflection magnet is allowed to be ejected vertically downward.

[0035] 5. Beam preparation section After the emittance of the particle beam is determined, the cross section and divergence angle of the particle beam are constantly changing during operation and need to be adjusted in time. This section is mainly composed of a set of focusing magnets and a bidirectional guide magnet. The focusing magnet is responsible for adjusting the beam divergence; the bidirectional guide magnet is responsible for adjusting the beam axis position.

[0036] The energy selection system is a mature technology. Its specific structure can change, but the basic function remains unchanged. Therefore, this patent does not make claims for it, nor does it provide a detailed description of its structure.

[0037] like Figure 1 and Figure 2 As shown, this embodiment further includes a linear acceleration range shifter 3, which is responsible for changing the energy of the particle beam and thus modulating the range of the particle beam in the patient's body.

[0038] The linear acceleration range shifter 3 includes a 90° deflection magnet 3 - 1 , which is responsible for deflecting the particle beam emitted vertically downward from the energy selection system 2 to the horizontal direction.

[0039] The linear acceleration range shifter 3 also includes N+1 focusing guide sections 3-2 composed of a group of focusing magnets A3-2-1, a bidirectional guide magnet A3-2-2 and an ionization chamber A3-2-3 for detecting the axial position of the particle beam, which are used to adjust the divergence and axial position of the particle beam, and N is an integer such as 1, 3, 5, etc.

[0040] The linear acceleration range shifter 3 also includes N phase-adjustable linear acceleration structures 3 - 3 .

[0041] The linear acceleration structure 3-3 of this embodiment adopts an edge-coupled cavity with adjustable phase. When adjusted to the acceleration phase, it is used to accelerate the particle beam passing through it to increase its energy; when adjusted to the deceleration phase, it is used to decelerate the particle beam passing through it to reduce its energy.

[0042] The energy difference of the particle beam caused by the total acceleration and the total deceleration of the N linear acceleration structures 3-3 is determined by the width of the extended Bragg peak required for radiotherapy.

[0043] The starting points of acceleration and deceleration of the N linear acceleration structures 3-3 are determined by the energy selection system 2 according to treatment needs.

[0044] The N linear acceleration structures 3-3 may also adopt other acceleration structures.

[0045] After configuring N linear acceleration structures 3-3, the energy adjustment amplitude of the energy selection system 2 can be adjusted by subtracting the amplitude of the increase in particle beam energy due to acceleration of the N linear acceleration structures 3-3 at the upper limit, and by increasing the amplitude of the decrease in particle beam energy due to deceleration of the N linear acceleration structures 3-3 at the lower limit. This can reduce the maximum thickness of the adjustable thickness absorber in the energy selection system 2 and reduce the beam intensity loss caused by energy selection to a certain extent.

[0046] The linear acceleration range shifter 3 also includes N klystrons 3-4, each of which is connected to a linear acceleration structure 3-3 to feed high-frequency power thereto.

[0047] Among the above components: N+1 focusing guide segments 3-2 and N linear acceleration structures 3-3 are connected in series alternately, so that the first focusing guide segment 3-2 is connected to the 90° deflection magnet 3-1, and the particle beam 300 is emitted horizontally from the N+1th focusing guide segment 3-2.

[0048] As described above, the 90° deflection magnet 3-1, N+1 focusing guide sections 3-2, N linear acceleration structures 3-3 and N klystrons 3-4 in the linear acceleration range shifter 3 all adopt superconducting design. The linear acceleration structure 3-3 and the klystron 3-4 adopt superconducting design to reduce power consumption and save operating costs. Since the N+1 focusing guide sections 3-2 and the N linear acceleration structures 3-3 are arranged alternately, the refrigeration mechanism specially configured for the N linear acceleration structures 3-3 and the N klystrons 3-4 can be borrowed nearby. After implementing superconductivity, the volume of the electromagnetic components in the 90° deflection magnet 3-1 and the N+1 focusing guide section 3-2 can be reduced, the total length of the linear acceleration range shifter 3 can be shortened, and the power consumption of the excitation can also be reduced.

[0049] like Figure 1 and Figure 3 As shown, this embodiment further includes a multi-angle deflection magnet 4 for changing the direction of the particle beam 300 emitted from the linear acceleration range shifter 3 within a horizontal plane according to M determined angles.

[0050] The multi-angle deflection magnet 4 comprises: The two magnetic poles 4-1 are horizontal, and the upper and lower magnetic poles are mirror-symmetrical with respect to the horizontal plane containing the axis line 300 of the incident particle beam; the upper and lower magnetic poles are mirror-symmetrical with respect to the vertical plane containing the axis line 300 of the incident particle beam; The three groups of two excitation coil windings 4-2 are mirror-symmetrical with respect to the horizontal plane containing the axis of the incident particle beam 300, and the three groups of two excitation coil windings 4-2 are mirror-symmetrical with respect to the vertical plane containing the axis of the incident particle beam 300; Three groups of two excitation coils 4-3, each group is wound on an excitation coil winding column 4-2; The two connected C-shaped yokes are simultaneously connected to the upper and lower end surfaces of three groups of two excitation coil winding columns 4-2 in each group.

[0051] Figure 3 In the figure, the two connected C-shaped yokes are sectioned according to the symmetry plane of the magnetic poles.

[0052] Figure 1 The multi-angle deflection magnet 4 is equipped with a vacuum cover.

[0053] like Figure 4 As shown, the multi-angle deflection magnet 4 deflects the incident particle beam 300 into M specific directions respectively.

[0054] like Figure 1 and Figure 5 As shown, this embodiment further includes M horizontal beam transport sections 5, which respectively receive particle beams 400 emitted from the multi-angle deflection magnet 4 at M determined angles.

[0055] The horizontal beam transport section 5 includes a horizontal direction guide magnet 5 - 1 composed of two horizontal deflection magnets with magnetic pole faces, which is used to correct the horizontal position and direction of the particle beam 400 emitted from the multi-angle deflection magnet 4 .

[0056] like Figure 4 As shown, the multi-angle deflection magnet 4 changes the direction of the particle beam according to M determined angles, and the particle beam deflected between the magnetic poles is in an arc shape, which assumes that the magnetic field distribution between the magnetic poles is absolutely uniform. If the magnetic field distribution is not absolutely uniform, the particle beam trajectory between the magnetic poles is no longer a pure circle, which will cause the emitted particle beam to deviate from the specified position and direction, and the direction and position cannot be adjusted at the same time. At this time, the horizontal direction guide magnet 5-1 composed of two magnetic pole surface horizontal deflection magnets can be used to translate the particle beam and change the direction of the particle beam.

[0057] The horizontal beam transport section 5 also includes a vertical direction guide magnet 5 - 2 composed of a magnetic pole face vertical deflection magnet, which is used to correct the direction of the particle beam emitted from the multi-angle deflection magnet 4.

[0058] The horizontal beam transport section 5 also includes an ionization chamber B5-3 for detecting the axial position of the particle beam, which is located behind the vertical guide magnet 5-1 and is used to detect the position offset of the particle beam 400 emitted from the multi-angle deflection magnet 4 and provide displacement correction parameters for the horizontal guide magnet 5-1 and the vertical guide magnet 5-2.

[0059] According to the direction of particle beam travel, the one ahead is behind and the one lagging behind is in front.

[0060] The horizontal beam transport section 5 also includes a set of focusing magnets B5-4, which are located behind the ionization chamber B5-3 and are used to adjust the divergence of the particle beam.

[0061] The horizontal beam transport section 5 also includes a bidirectional guiding magnet B5-5 for correcting the direction of the particle beam.

[0062] The horizontal beam transport section 5 also includes an ionization chamber C5-6 for detecting the axial position of the particle beam, which is located behind the bidirectional guide magnet B5-5. Together with the ionization chamber B5-3, it is used to detect the angular deflection of the axial line 400 of the particle beam emitted from the multi-angle deflection magnet 4, provide angle correction parameters for the horizontal direction guide magnet 5-1, and provide correction parameters for a group of focusing magnets B5-4 and bidirectional guide magnets B5-5.

[0063] like Figure 1 As shown, this embodiment further includes M bidirectional scanning treatment systems 6 , which respectively receive the particle beams emitted by the M horizontal beam transport sections 5 .

[0064] like Figure 6 As shown, this embodiment also includes a double-layer radiation shielding device 7, in which the particle cyclotron 1, the energy selection system 2, the linear acceleration range shifter 3, the multi-angle deflection magnet 4, M horizontal beam transport sections 5 and M bidirectional scanning treatment systems 6 are placed.

[0065] like Figure 7 As shown, the upper layer of the radiation shielding device 7 places the cyclotron 1 and the energy selection system 2 therein.

[0066] Figure 7 The ray shielding device 7 in the figure is subjected to cross-section processing.

[0067] like Figure 8 As shown, the lower layer of the radiation shielding device 7 places the linear acceleration range shifter 3, the multi-angle deflection magnet 4, M horizontal beam transport sections 5 and M bidirectional scanning treatment systems 6 therein, and separates the treatment room where the M bidirectional scanning treatment systems 6 are placed from the machine room where the linear acceleration range shifter 3, the multi-angle deflection magnet 4 and the M horizontal beam transport sections 5 are placed.

[0068] like Figure 8 As shown, M hollow rectangular through-wall passages 8 with openings toward one side of the machine room are used to connect the machine room with the M treatment rooms. The through-wall passages are made of metal and have a shielding effect equivalent to that of a shielding wall.

[0069] Among all the electromagnetic components constituting the treatment center, the bases of the cyclotron 1, the multi-angle deflection magnet 4 and the M bidirectional scanning treatment systems 6 are connected to the ground of the double-layer radiation shielding device 7; other components are connected to the nearest part of the radiation shielding device 7 via a connecting frame.

[0070] Figure 8 The ray shielding device 7 in the figure is subjected to cross-section processing.

Claims

1. A cyclotron particle therapy center configured with a switchable therapy system linear acceleration range shifter comprises: A particle cyclotron (1) responsible for generating a particle beam with a fixed energy, wherein the fixed energy is determined according to the maximum range of the particle beam in the human body required for radiotherapy; An energy selection system (2) is connected to the particle cyclotron (1) and is responsible for selecting energy downward based on the fixed energy output by the cyclotron (1) by using an absorber to block the particle beam. The maximum amplitude of energy reduction is determined according to the shortest range of the particle beam in the human body required for radiotherapy. The energy selection system (2) also controls the increase of beam divergence and energy divergence caused by energy selection. The particle beam emitted from the energy selection system (2) is vertically downward. A linear acceleration range shifter (3) is connected to the energy selection system (2) to change the energy of the particle beam by accelerating and decelerating the particle beam, thereby modulating the range of the particle beam in the patient's body. The amplitude of the particle beam energy change caused by the acceleration and deceleration of the particle beam by the linear acceleration range shifter (3) is determined by the width of the extended Bragg peak required for radiotherapy; A multi-angle deflection magnet (4) receives the horizontal particle beam (300) output by the linear acceleration range shifter (3) and can deflect it to M specific angles in the horizontal plane, M>1; M horizontal beam transport sections 5, respectively receiving particle beams (400) emitted by multi-angle deflection magnets (4); M bidirectional scanning treatment systems (6), respectively receiving particle beams emitted from the M horizontal beam transport sections (6); A radiation shielding device (7) having a double-layer design, wherein the particle cyclotron (1) and the energy selection system (2) are placed in the upper layer; The lower layer houses the linear acceleration range shifter (3), the multi-angle deflection magnet (4), M horizontal beam transport sections 5 and M bidirectional scanning treatment systems (6), and separates the treatment room housing the M bidirectional scanning treatment systems (6) from the machine room housing the linear acceleration range shifter (3), the multi-angle deflection magnet (4) and the M horizontal beam transport sections (5); M hollow rectangular through-the-wall passages (8) with openings toward one side of the machine room are used to achieve communication between the machine room and the M treatment rooms. The cyclotron (1), the energy selection system (2), the linear acceleration range shifter (3), the multi-angle deflection magnet (4), the M horizontal beam transport sections (5) and the M bidirectional scanning treatment systems (6) are connected to the bottom surface and relevant parts of the radiation shielding device 7 via their respective bases and connecting frames.

2. The linear acceleration range shifter (3) according to claim 1, comprising: A 90° deflection magnet (3-1) is responsible for deflecting the particle beam emitted vertically downward from the energy selection system (2) to the horizontal direction; N+1 focusing guide sections (3-2) composed of a group of focusing magnets A (3-2-1), a bidirectional guide magnet A (3-2-2) and an ionization chamber A (3-2-3) for detecting the axis position of the particle beam, used to adjust the divergence and axis position of the particle beam, N≧1; N phase-adjustable linear acceleration structures (3-3) are used to accelerate and decelerate the particle beam passing therethrough to change its energy. The N linear acceleration structures (3-3) are connected in series with N+1 focusing guide sections (3-2) alternately, so that the first focusing guide section (3-2) is connected to the 90° deflection magnet (3-1); and the N+1th focusing guide section (3-2) is connected to the multi-angle deflection magnet (4); N klystrons (3-4) are respectively connected to a linear acceleration structure (3-3) to feed high-frequency power thereto.

3. The N phase-adjustable linear acceleration structures (3-3) in the linear acceleration range shifter (3) as claimed in claims 1 and 2 are side-coupled cavities.

4. The 90° deflection magnet (3-1), N+1 focusing guide sections (3-2), N linear acceleration structures (3-3), and N klystrons (3-4) in the linear acceleration range shifter (3) as claimed in claim 2 all adopt a superconducting design, which can reduce the power consumption of the linear acceleration structure (3-3) and the klystron (3-4), and can reduce the volume of the electromagnetic components in the 90° deflection magnet (3-1) and the focusing guide section (3-2).

5. The multi-angle deflection magnet (4) according to claim 1, comprising: The two magnetic poles (4-1) have horizontal magnetic pole surfaces, and the upper and lower magnetic pole surfaces are mirror-symmetrical relative to a horizontal plane containing the axis line of the incident particle beam (300); the upper and lower magnetic poles are mirror-symmetrical relative to a vertical plane containing the axis line of the incident particle beam (300); Three groups of two excitation coil windings (4-2) each, the three upper and three lower excitation coil windings (4-2) are mirror-symmetrical relative to a horizontal plane containing the axis line of the incident particle beam (300), and the three groups of two excitation coil windings (4-2) are mirror-symmetrical relative to a vertical plane containing the axis line of the incident particle beam (300); Three groups of two excitation coils (4-3), each group is wound around an excitation coil winding column (4-2); Two connected C-shaped magnetic yokes are simultaneously connected to the upper and lower end surfaces of three groups of two excitation coil winding columns (4-2).

6. The horizontal beam transport section (5) according to claim 1, comprising: A horizontal direction guide magnet (5-1) composed of two magnetic pole surface horizontal deflection magnets, used to correct the horizontal position and direction of the particle beam (400) emitted from the multi-angle deflection magnet (4); A vertical direction guide magnet (5-2) composed of a magnetic pole face vertical deflection magnet, used to correct the direction of the particle beam (400) emitted from the multi-angle deflection magnet (4); An ionization chamber B (5-3) for detecting the axial position of a particle beam is located behind the vertical direction guide magnet (5-1) and is used to detect the position deviation of the particle beam (400) emitted from the multi-angle deflection magnet (4) and provide displacement correction parameters for the horizontal direction guide magnet (5-1) and the vertical direction guide magnet (5-2); A set of focusing magnets B (5-4), located behind the ionization chamber B (5-3), is used to adjust the divergence of the particle beam; A bidirectional guide magnet B (5-5) for correcting the direction of the particle beam; An ionization chamber C (5-6) for detecting the axial position of a particle beam is located behind the bidirectional guide magnet B (5-5) and is used together with the ionization chamber B (5-1) to detect the angular deflection of the axial line of the particle beam (400) emitted from the multi-angle deflection magnet (4), provide angle correction parameters for the horizontal guide magnet (5-1), and provide correction parameters for a group of focusing magnets B (5-4) and the bidirectional guide magnet B (5-5).

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