Superconducting magnet for a magnetic resonance imaging system and processing tool and method therefor

Abstract

A processing tool for a superconducting magnet of a magnetic resonance imaging system includes a first winding portion (11) and a second winding portion (21). The first winding portion serves as a winding former for winding a main coil half. The second winding portion serves as a winding former for winding a shield coil. The processing tool has an impregnation cavity (40). The impregnation cavity includes a main coil accommodation region (41), a shield coil accommodation region (42), and a through region (43). The main coil accommodation region is for accommodating the main coil half wound on the first winding portion. The shield coil accommodation region is for accommodating the shield coil wound on the second winding portion. The main coil accommodation region is in communication with the shield coil accommodation region through the through region. The processing tool facilitates reducing the difficulty of processing the superconducting magnet. Furthermore, a processing method using the processing tool and a superconducting magnet processed using the processing method are provided.

Description

Technical Field

[0001] This invention relates to a processing tool, particularly a processing tool for processing superconducting magnets for magnetic resonance imaging systems, a processing method using the processing tool, and a superconducting magnet processed using the processing method. Background Technology

[0002] The superconducting magnet in a magnetic resonance imaging (MRI) system typically consists of a main coil and a shielding coil surrounding it. The main coil is used to generate the imaging magnetic field. The main coil and the shielding coil are maintained at a certain distance and connected by a connecting structure. Existing connecting structures are relatively complex, and their fabrication and assembly are difficult. Summary of the Invention

[0003] The purpose of this invention is to provide a processing tool for superconducting magnets in magnetic resonance imaging systems, which helps to reduce the difficulty of processing superconducting magnets.

[0004] Another objective of this invention is to provide a method for fabricating superconducting magnets for magnetic resonance imaging systems, which helps to reduce the difficulty of fabricating superconducting magnets.

[0005] Another object of the present invention is to provide a superconducting magnet for a magnetic resonance imaging system that is easy to manufacture.

[0006] This invention provides a fabrication tool for a superconducting magnet in a magnetic resonance imaging system. The fabrication tool includes a first winding section and a second winding section. The first winding section serves as a winding frame for winding a main coil half of the superconducting magnet. The second winding section serves as a winding frame for winding a shielding coil of the superconducting magnet. The fabrication tool has an injection cavity. The injection cavity includes a main coil receiving area, a shielding coil receiving area, and a through area. The main coil receiving area is used to receive the main coil half of the superconducting magnet wound on the first winding section. The shielding coil receiving area is used to receive the shielding coil of the superconducting magnet wound on the second winding section. The main coil receiving area is connected to the shielding coil receiving area through the through area.

[0007] The machining tools used in this magnetic resonance imaging system for superconducting magnets help reduce the difficulty of machining superconducting magnets.

[0008] In another illustrative embodiment of the fabrication tool for the superconducting magnet in a magnetic resonance imaging system, the main coil receiving area is tubular, and the shielding coil receiving area is annular. The shielding coil receiving area is coaxially arranged around the main coil receiving area to improve the stability of the superconducting magnet.

[0009] In another illustrative embodiment of the fabrication tool for the superconducting magnet in a magnetic resonance imaging system, the through-section is annular, with its inner edge connected to the main coil receiving area and its outer edge connected to the shielding coil receiving area. This is to improve the stability of the superconducting magnet structure.

[0010] In another illustrative embodiment of the machining tool for the superconducting magnet in a magnetic resonance imaging system, the through region is an annular plate extending along the side of a frustum, wherein the axis of the side of the frustum overlaps with the axis of the main coil receiving region. This is to improve the stability of the superconducting magnet structure.

[0011] In another illustrative embodiment of the fabrication tool for the superconducting magnet in a magnetic resonance imaging system, the through region comprises several separate through sections. Each through section is a strip extending along a straight line. One end of each through section connects to the main coil receiving area, and the other end of each through section connects to the shielding coil receiving area. The several through sections are evenly distributed circumferentially along the main coil receiving area, thereby reducing the material cost and weight of the superconducting magnet.

[0012] In another illustrative embodiment of the fabrication tool for the superconducting magnet in a magnetic resonance imaging system, each through-section is a strip extending along the generatrix of a frustum, wherein the axis of the frustum overlaps with the axis of the main coil accommodating area. This is to improve the stability of the superconducting magnet structure.

[0013] In another illustrative embodiment of the fabrication tool for a superconducting magnet in a magnetic resonance imaging system, one height direction of the fabrication tool is parallel to the axis of the superconducting magnet fabricated therefrom. The infusion cavity also includes several extension regions. Each extension region is rod-shaped and extends along the height direction. One end of each extension region connects to the through region, and the other end of each extension region is closed, in order to improve the stability of the superconducting magnet structure.

[0014] In another illustrative embodiment of a machining tool for a superconducting magnet in a magnetic resonance imaging system, a height direction of the machining tool is parallel to the axial direction of the superconducting magnet machined therefrom. The machining tool includes a first assembly, a second assembly, and a third assembly that are detachable along the height direction. The first assembly has a first winding portion. The first winding portion has a first outer cylindrical surface for winding a main coil half of the superconducting magnet. The axis of the first outer cylindrical surface is parallel to the height direction. The second assembly has a second winding portion. The second winding portion has a second outer cylindrical surface for winding a shielding coil of the superconducting magnet. The second outer cylindrical surface is coaxially arranged around the first outer cylindrical surface. The second assembly also has a first inner cylindrical surface and a first annular connecting surface. The first inner cylindrical surface is coaxially arranged with the first outer cylindrical surface and located between the first and second outer cylindrical surfaces. The outer edge of the first annular connecting surface connects to the second outer cylindrical surface, and the inner edge of the first annular connecting surface connects to the first inner cylindrical surface. The third assembly has a second inner cylindrical surface, a third inner cylindrical surface, and a second annular connecting surface. The second inner cylindrical surface is coaxially arranged on one side of the first inner cylindrical surface with the same diameter as the first inner cylindrical surface. The first outer cylindrical surface, the first inner cylindrical surface, and the second inner cylindrical surface form the main coil receiving area. The third inner cylindrical surface is coaxially arranged around the second outer cylindrical surface. The second outer cylindrical surface and the third inner cylindrical surface form the shielding coil receiving area. The outer edge of the second annular connecting surface connects to the third inner cylindrical surface, and the inner edge of the second annular connecting surface connects to the second inner cylindrical surface. The second annular connecting surface and the first annular connecting surface are arranged opposite each other along the height direction to form a through area. This structure is simple and easy to operate.

[0015] This invention also provides a method for fabricating a superconducting magnet for a magnetic resonance imaging system, using the aforementioned fabrication tool. The method includes: winding a main coil half of the superconducting magnet using a first winding section as the winding frame; winding a shielding coil of the superconducting magnet using a second winding section as the winding frame; injecting a filling material into the injection cavity and allowing the filling material to solidify; and removing the fabrication tool. This method helps to reduce the difficulty of fabricating superconducting magnets.

[0016] In another illustrative embodiment of the fabrication method for a superconducting magnet in a magnetic resonance imaging system, the number of the first winding section, second winding section, main coil receiving area, shielding coil receiving area, and through area of ​​the fabrication tool is all set to one. After removing the fabrication tool, a superconducting magnet half-body is formed. The fabrication method also includes connecting two superconducting magnet half-bodies after removing the fabrication tool to form a superconducting magnet. This helps to reduce the cost of the fabrication tool.

[0017] In another illustrative embodiment of the fabrication method for a superconducting magnet in a magnetic resonance imaging system, one height direction of the fabrication tool is parallel to the axis of the superconducting magnet fabricated therefrom. The infusion cavity also includes several extension regions, each extension region being rod-shaped and extending along the height direction. One end of each extension region connects to the through region, and the other end of each extension region is closed. In the fabrication method, after infusing the infusion cavity with infusion material and allowing the infusion material to solidify, a rod-shaped portion formed by the solidified infusion material is formed in each extension region, and a main coil infusion half-body formed by the solidified infusion material is formed in the main coil receiving region. The step of connecting two superconducting magnet halves to form a superconducting magnet includes: connecting the two superconducting magnet halves with a main coil infusion half-body, and connecting the free ends of the rod-shaped portions of the two superconducting magnet halves. This is to improve the stability of the superconducting magnet structure.

[0018] In another illustrative embodiment of the fabrication method for a superconducting magnet in a magnetic resonance imaging system, the fabrication method further includes: laying a reinforcing core material before injecting the injection material into the injection cavity, so that the reinforcing core material is ultimately located within the injection cavity. This is to improve the stability of the superconducting magnet structure.

[0019] In another illustrative embodiment of the fabrication method for superconducting magnets in a magnetic resonance imaging system, the infusion material is resin, and the reinforcing core material is glass fiber. This is to improve the stability of the superconducting magnet structure.

[0020] In another illustrative embodiment of the fabrication method for a superconducting magnet in a magnetic resonance imaging system, the fabrication method includes: winding a main coil half of the superconducting magnet using a first winding portion as the winding skeleton; winding a shielding coil of the superconducting magnet using a second winding portion as the winding skeleton; assembling a first assembly, a second assembly, and a third assembly to form a perfusion cavity; perfusing the perfusion cavity with a perfusion material and allowing the perfusion material to solidify; and removing the fabrication tools. This makes the fabrication operation more convenient.

[0021] This invention also provides a superconducting magnet for a magnetic resonance imaging system, which is manufactured using the aforementioned processing method. The superconducting magnet includes a main coil, two shielding coils, and a liquid-solidified infusion body. The two shielding coils are respectively arranged around the two ends of the main coil along its axial direction. The infusion body includes a first molding part, two second molding parts, and two connecting parts. The first molding part is bonded to the main coil by impregnation and curing. Each second molding part is bonded to a shielding coil by impregnation and curing. Each connecting part connects the first molding part and a second molding part. This superconducting magnet has good structural stability and is easy to manufacture.

[0022] In another illustrative embodiment of the superconducting magnet in a magnetic resonance imaging system, the superconducting magnet includes a main coil, two shielding coils, and a liquid-solidified infusion body. The two shielding coils are respectively arranged around the two ends of the main coil along its axial direction. The infusion body includes a first molding portion, two second molding portions, two connecting portions, and a set of reinforcing portions. The first molding portion is bonded to the main coil by impregnation and curing. Each second molding portion is bonded to one shielding coil by impregnation and curing. Each connecting portion connects the first molding portion and one second molding portion. Each reinforcing portion is rod-shaped, extending along the axial direction of the main coil, and each end of the reinforcing portion is connected to the two connecting portions, thereby improving the stability of the superconducting magnet structure.

[0023] In another illustrative embodiment of the superconducting magnet in a magnetic resonance imaging system, a reinforcing core material is embedded within the infusion body to improve the stability of the superconducting magnet structure. Attached Figure Description

[0024] The following figures are for illustrative purposes only and do not limit the scope of the invention.

[0025] Figure 1 A cross-sectional view of a schematic embodiment of a machining tool for a superconducting magnet in a magnetic resonance imaging system.

[0026] Figure 2 for Figure 1 An exploded view of the machining tool shown.

[0027] Figure 3 This is a flowchart illustrating one embodiment of a method for fabricating a superconducting magnet for a magnetic resonance imaging system.

[0028] Figure 4 For use Figure 1 The diagram shows the structure of a superconducting magnet half-body processed by the machining tool shown.

[0029] Figure 5 for Figure 4 The diagram shows a superconducting magnet composed of superconducting magnet halves.

[0030] Figure 6 for Figure 5 The cross-sectional view of the superconducting magnet shown.

[0031] Figure 7 This is a schematic diagram of the structure of a second assembly, representing another illustrative embodiment of a machining tool for a superconducting magnet in a magnetic resonance imaging system.

[0032] Figure 8 An exploded view of another illustrative embodiment of a machining tool for a superconducting magnet in a magnetic resonance imaging system.

[0033] Figure 9 For use Figure 8 The diagram shows the structure of a superconducting magnet half-body processed by the machining tool shown.

[0034] Figure 10 for Figure 9 The diagram shows a superconducting magnet composed of superconducting magnet halves.

[0035] Figure 11 for Figure 10 The cross-sectional view of the superconducting magnet shown.

[0036] Label Explanation

[0037] 10 First Assembly Components

[0038] 11 First winding section

[0039] 20 Second Assembly Components

[0040] 21 Second winding section

[0041] 22 slots

[0042] 30 Third Assembly Components

[0043] 40 Infusion chamber

[0044] 41 Main coil housing area

[0045] 42 Shielded coil housing area

[0046] 43 Through Area

[0047] 44 Extension Area

[0048] W1 First outer cylindrical surface

[0049] W2 Second outer cylindrical surface

[0050] N1 First inner cylindrical surface

[0051] N2 Second Inner Cylindrical Surface

[0052] N3 Third Inner Cylindrical Surface

[0053] H1 First annular connecting surface

[0054] H2 Second Annular Connecting Surface

[0055] 60 main coil

[0056] 61 Main coil half

[0057] 70 Shielded Coil

[0058] 80 Injection Body

[0059] 81 First Molding Section

[0060] 82 Second Molding Section

[0061] 83 Connecting part

[0062] 831 Connection Division

[0063] 84 Reinforcement Section

[0064] 90 Reinforced core material

[0065] 100 Superconducting Magnet

[0066] 101 Superconducting Magnet Half-Body

[0067] 102 Main coil injection half body

[0068] 103 Pole

[0069] H (height direction) Detailed Implementation

[0070] To provide a clearer understanding of the technical features, objectives, and effects of the invention, specific embodiments of the invention are now described with reference to the accompanying drawings. In the drawings, the same reference numerals indicate components with the same or similar structures but the same function.

[0071] In this document, “illustrative” means “serving as an example, illustration or description”, and any illustration or implementation described herein as “illustrative” should not be construed as a more preferred or advantageous technical solution.

[0072] In this document, terms such as "first" and "second" do not indicate their importance or order, but are only used to distinguish them to facilitate the description of the document.

[0073] To keep the drawings simple, each drawing only schematically shows the parts related to the present invention, and they do not represent the actual structure of the product.

[0074] Figure 1 A cross-sectional view of a schematic embodiment of a machining tool for a superconducting magnet in a magnetic resonance imaging system. Figure 2 for Figure 1 An exploded view of the machining tool shown. (As shown) Figure 1 and Figure 2 As shown, the fabrication tool for the superconducting magnet in a magnetic resonance imaging system includes a first assembly 10, a second assembly 20, and a third assembly 30 that are detachable along a height direction H. This height direction H of the fabrication tool is parallel to the axial direction of the superconducting magnet fabricated therefrom.

[0075] The first assembly 10 is provided with a first winding section 11. The first winding section 11 serves as a winding frame for winding a main coil half of a superconducting magnet. Figure 2 The diagram schematically shows a main coil half 61 of a superconducting magnet wound on a first winding portion 11. In this illustrative embodiment, the main coil of the superconducting magnet is composed of two main coil halves arranged along its axial direction. In this illustrative embodiment, the first winding portion 11 has a first outer cylindrical surface W1 for winding the main coil half of the superconducting magnet, the axis of which is parallel to the height direction H.

[0076] The second assembly 20 is provided with a second winding section 21. The second winding section 21 serves as a winding frame for winding a shielded coil of a superconducting magnet. Figure 2 The diagram schematically shows a shielding coil 70 of a superconducting magnet wound on a second winding portion 21. In this illustrative embodiment, the second winding portion 21 has a second outer cylindrical surface W2 for winding the shielding coil of the superconducting magnet. The second outer cylindrical surface W2 is coaxially disposed around a first outer cylindrical surface W1.

[0077] like Figure 1 As shown, the first assembly 10, the second assembly 20, and the third assembly 30 form a filling cavity 40. The filling cavity 40 includes a main coil receiving area 41, a shielded coil receiving area 42, a through area 43, and several extension areas 44. Figure 1 (Only two of them are visible in the image). The main coil receiving area 41 is used to receive the main coil half of the superconducting magnet wound on the first winding portion 11. The shielding coil receiving area 42 is used to receive the shielding coil of the superconducting magnet wound on the second winding portion 21. The main coil receiving area 41 is connected to the shielding coil receiving area 42 through the through area 43.

[0078] In this illustrative embodiment, the main coil receiving area 41 is tubular (in this text, tubular refers to a straight tube with a circular cross-section), and its axis overlaps with the axis of the first outer cylindrical surface W1. For this purpose, the second assembly 20 also has a first inner cylindrical surface N1, which is coaxially arranged with the first outer cylindrical surface W1 and located between the first outer cylindrical surface W1 and the second outer cylindrical surface W2. The third assembly 30 has a second inner cylindrical surface N2, which is of the same diameter as the first inner cylindrical surface N1 and coaxially arranged on one side of the axial direction of the first inner cylindrical surface N1. The first outer cylindrical surface W1, the first inner cylindrical surface N1, and the second inner cylindrical surface N2 form the main coil receiving area 41.

[0079] In this illustrative embodiment, the shielded coil receiving area 42 is annular. The shielded coil receiving area 42 is coaxially arranged around the main coil receiving area 41. For this purpose, the third assembly 30 also has a third inner cylindrical surface N3, which is coaxially arranged around the second outer cylindrical surface W2. The second outer cylindrical surface W2 and the third inner cylindrical surface N3 are used to enclose the shielded coil receiving area 42.

[0080] In this illustrative embodiment, the through area 43 is an annular plate extending along the side of a frustum of a cone, with its inner edge connecting to the main coil receiving area 41 and its outer edge connecting to the shielding coil receiving area 42. The axis of the side of the frustum of a cone overlaps with the axis of the main coil receiving area 41. For this purpose, the second assembly 20 also has a first annular connecting surface H1, the outer edge of which connects to the second outer cylindrical surface W2, and the inner edge of which connects to the first inner cylindrical surface N1. The third assembly 30 has a second annular connecting surface H2. The outer edge of the second annular connecting surface H2 connects to the third inner cylindrical surface N3, and the inner edge of which connects to the second inner cylindrical surface N2. Both the second annular connecting surface H2 and the first annular connecting surface H1 are frustum of a cone and are arranged opposite each other along the height direction H to form the through area 43. However, this is not a limitation; in other illustrative embodiments, the through area 43 can also be other forms of annulus, such as an annulus unfolding along a plane.

[0081] like Figure 1 As shown, each extension region 44 is rod-shaped, extending along the height direction H. One end of each extension region 44 is connected to the through region 43, and the other end of each extension region 44 is closed. In this illustrative embodiment, there are 8 extension regions 44, which are evenly distributed around the axis of the main coil receiving region 41. However, this is not the only embodiment. In other illustrative embodiments, the number and arrangement of the extension regions 44 can be adjusted as needed, or the extension regions 44 may not be provided.

[0082] The following is an illustrative embodiment of a method for fabricating a superconducting magnet for a magnetic resonance imaging system using this fabrication tool, such as... Figure 3 As shown, the process includes the following steps S10 to S70:

[0083] S10: A main coil half 61 of a superconducting magnet is wound using the first winding part 11 of the first assembly 10 as the winding skeleton;

[0084] S20: A shielded coil 70 of a superconducting magnet is wound using the second winding part 21 of the second assembly 20 as the winding skeleton;

[0085] S30: Lay the reinforcing core material so that the reinforcing core material is finally located in the injection cavity 40; wherein the reinforcing core material is, for example, glass fiber material, and its shape can be set as needed, such as strip or sheet;

[0086] S40: Assemble the first assembly 10, the second assembly 20 and the third assembly 30 along the height direction H to form the injection cavity 40;

[0087] S50: Injecting the injection material into the injection cavity 40 and allowing the injection material to solidify; during the injection process, the injection material will impregnate into the gaps between the main coil half and the shielding coil; after solidification, a rod portion 103 formed by the solidification of the injection material is formed in each extension area 44 (see...). Figure 4 In the main coil receiving area 41, a main coil filling half 102 formed by the curing of the filling material is formed (see...). Figure 4 The injection material is, for example, resin, such as epoxy resin.

[0088] S60: Dismantle the processing tools to form a... Figure 4 The superconducting magnet half 101 shown has a shape that matches the shape of the infusion cavity 40;

[0089] S70: Two superconducting magnet halves 101 are connected along the axis to form... Figure 5 The superconducting magnet 100 shown specifically connects the main coil injection half 102 of the two superconducting magnet halves 101 and the free end of the rod portion 103 of the two superconducting magnet halves 101, the connection being, for example, by adhesive or by bolt.

[0090] Figure 6 for Figure 5 A cross-sectional view of a superconducting magnet is shown. Figure 5 and Figure 6 As shown, the final superconducting magnet 100 includes a main coil 60, two shielding coils 70, and a liquid-solidified injection body 80. The main coil 60 includes two main coil halves 61. The two shielding coils 70 are respectively arranged around the two ends of the main coil 60 along its axial direction.

[0091] The infusion body 80 includes a first molding part 81, two second molding parts 82, two connecting parts 83, and a set of reinforcing parts 84 (eight in this illustrative embodiment). The first molding part 81 is formed by connecting two main coil infusion halves 102 of the superconducting magnet halves 101, and is bonded to the main coil 60 by impregnation and curing. After the infusion material cures, a second molding part 82 formed by the curing of the infusion material is formed in the shielding coil receiving area 42, and each second molding part 82 is bonded to a shielding coil 70 by impregnation and curing. After the infusion material cures, a connecting part 83 formed by the curing of the infusion material is formed in the through area 43, and each connecting part 83 connects the first molding part 81 and a second molding part 82. Each reinforcing part 84 is formed by connecting the rod parts 103 of the two superconducting magnet halves 101, and each reinforcing part 84 is rod-shaped extending along the axial direction of the main coil 60. The two ends of each reinforcing part 84 are respectively connected to the two connecting parts 83. The main body of the injection is 80mm infilled with a reinforcing core material 90mm.

[0092] use Figure 1 The machining tools shown reduce the difficulty of machining superconducting magnets. Using... Figure 1 The processing method of the superconducting magnet of the magnetic resonance imaging system shown is simple to operate, which helps to reduce the difficulty of processing superconducting magnets, and the processed superconducting magnet has good structural stability.

[0093] Figure 7 and Figure 8 Another illustrative embodiment of a machining tool for a superconducting magnet used in a magnetic resonance imaging system. The machining tool of this illustrative embodiment is similar to... Figure 1 The similarities to the processing tools shown will not be repeated here. The difference lies in the through-section 43, which in this illustrative embodiment includes several separate through-section sections. Therefore, as... Figure 7 As shown, the second assembly 20 has several slots 22 ( Figure 7 (Only two are schematically shown in the diagram), each slot 22 corresponds to a through section. Each through section is a strip extending in a straight line. In this schematic embodiment, each through section is a strip extending along the generatrix of a frustum, wherein the axis of the frustum overlaps with the axis of the main coil receiving area 41, but is not limited thereto. One end of each through section connects to the main coil receiving area 41, and the other end of each through section connects to the shielding coil receiving area 42. Several through sections are evenly distributed circumferentially along the main coil receiving area 41.

[0094] The processing method for superconducting magnets using this processing tool is, for example, the same as that used above. Figure 1 The processing method for the superconducting magnets shown is the same, and will not be repeated here. Figure 9 For use Figure 8The diagram shows the structure of a superconducting magnet half-body fabricated using the shown processing tool. This superconducting magnet half-body is related to... Figure 4 The superconducting magnet half shown differs only in the structure of the connecting part 83. For example... Figure 9 As shown, the connecting portion 83 includes several separate connecting portions 831 ( Figure 9 (Only two of them are schematically marked in the text), each connecting section 831 corresponds to a through section. Figure 10 for Figure 9 The diagram shows a superconducting magnet composed of superconducting magnet halves. The structure of the connecting part 83 helps to reduce the material cost and overall weight of the superconducting magnet. Figure 11 for Figure 10 The cross-sectional view of the superconducting magnet shown.

[0095] use Figure 8 The machining tools shown reduce the difficulty of machining superconducting magnets. Using... Figure 8 The processing method of the superconducting magnet of the magnetic resonance imaging system shown is simple to operate, which helps to reduce the difficulty of processing superconducting magnets, and the processed superconducting magnet has good structural stability.

[0096] It should be understood that although this specification is described according to various embodiments, not every embodiment contains only one independent technical solution. This way of describing the specification is only for clarity. Those skilled in the art should regard the specification as a whole. The technical solutions in each embodiment can also be appropriately combined to form other implementation methods that can be understood by those skilled in the art.

[0097] The detailed descriptions listed above are merely specific descriptions of feasible embodiments of the present invention and are not intended to limit the scope of protection of the present invention. All equivalent implementation schemes or modifications made without departing from the spirit of the present invention, such as combinations, divisions or repetitions of features, should be included within the scope of protection of the present invention.

Claims

1. A tool for processing superconducting magnets for magnetic resonance imaging systems, characterized in that: The processing tools include: A first winding section (11), which serves as the winding frame for winding a main coil half of a superconducting magnet, and A second winding section (21) serves as the winding frame for winding a shielded coil of a superconducting magnet; The processing tool has an injection cavity (40), the injection cavity (40) comprising: A main coil receiving area (41) is provided for receiving the main coil half of the superconducting magnet wound on the first winding portion (11). A shielded coil receiving area (42) for receiving the shielded coil of the superconducting magnet wound on the second winding portion (21), and A through area (43) is provided, through which the main coil receiving area (41) is connected to the shielding coil receiving area (42).

2. The tool of claim 1 wherein, The main coil receiving area (41) is in the shape of a cylindrical tube, and the shielding coil receiving area (42) is in the shape of a ring. The shielding coil receiving area (42) is arranged coaxially around the main coil receiving area (41).

3. The tool of claim 2 wherein, The through area (43) is annular, with its inner edge connected to the main coil receiving area (41) and its outer edge connected to the shielding coil receiving area (42).

4. The tool of claim 3 wherein, The through area (43) is an annular plate extending along the side of a frustum, and the axis of the side of the frustum overlaps with the axis of the main coil receiving area (41).

5. The tool of claim 2 wherein, The through area (43) includes several separate through sections, each of which is a strip extending along a straight line. One end of each through section is connected to the main coil receiving area (41), and the other end of each through section is connected to the shielding coil receiving area (42). The several through sections are evenly distributed around the circumference of the main coil receiving area (41).

6. The tool of claim 5 wherein, Each of the through sections is a strip extending along the generatrix of a truncated cone, and the axis of the truncated cone overlaps with the axis of the main coil receiving area (41).

7. The machining tool as described in claim 1, characterized in that, The height direction (H) of the processing tool is parallel to the axis of the superconducting magnet processed therefrom. The infusion cavity (40) also includes several extension regions (44), each of the extension regions (44) being rod-shaped and extending along the height direction (H). One end of each extension region (44) is connected to the through region (43), and the other end of each extension region (44) is closed.

8. The processing tool as described in claim 1, characterized in that, One height direction (H) of the machining tool is parallel to the axis of the superconducting magnet processed therefrom; the machining tool includes components detachable along the height direction (H): A first assembly (10) is provided with a first winding portion (11), the first winding portion (11) having a first outer cylindrical surface (W1) for winding a main coil half of a superconducting magnet, the axis of the first outer cylindrical surface (W1) being parallel to the height direction (H). A second assembly (20) is provided with a second winding portion (21), the second winding portion (21) having a second outer cylindrical surface (W2) for winding a shielded coil of a superconducting magnet, the second outer cylindrical surface (W2) being coaxially disposed around the first outer cylindrical surface (W1), the second assembly (20) further having: A first inner cylindrical surface (N1), which is coaxially arranged with the first outer cylindrical surface (W1) and located between the first outer cylindrical surface (W1) and the second outer cylindrical surface (W2), and A first annular connecting surface (H1), the outer edge of which connects to a second outer cylindrical surface (W2), and the inner edge of which connects to a first inner cylindrical surface (N1). A third assembly (30) having: A second inner cylindrical surface (N2) is provided on one side of the first inner cylindrical surface (N1) with the same diameter and coaxiality as the first inner cylindrical surface (N1). The first outer cylindrical surface (W1), the first inner cylindrical surface (N1) and the second inner cylindrical surface (N2) are used to form the main coil receiving area (41). A third inner cylindrical surface (N3) is coaxially disposed around the second outer cylindrical surface (W2), the second outer cylindrical surface (W2) and the third inner cylindrical surface (N3) forming the shielding coil receiving area (42), and A second annular connecting surface (H2) is provided, the outer edge of which is connected to the third inner cylindrical surface (N3), and the inner edge of which is connected to the second inner cylindrical surface (N2). The second annular connecting surface (H2) and the first annular connecting surface (H1) are arranged opposite to each other along the height direction (H) to form the through area (43).

9. A method for fabricating a superconducting magnet for a magnetic resonance imaging system, characterized in that, The processing method uses the processing tool as described in any one of claims 1 to 8, and the processing method includes: A main coil half (61) of a superconducting magnet is wound using the first winding part (11) as the winding skeleton. A shielded coil (70) of a superconducting magnet is wound using the second winding part (21) as the winding skeleton. Injecting a filling material into the filling cavity (40) and allowing the filling material to solidify; and Remove the processing tools.

10. The processing method as described in claim 9, characterized in that, The processing tool has one of each of the first winding part (11), the second winding part (21), the main coil accommodating area (41), the shielding coil accommodating area (42), and the through area (43). In the processing method, a superconducting magnet half (101) is formed after the processing tool is removed. The processing method also includes connecting two superconducting magnet half (101) to form a superconducting magnet after the processing tool is removed.

11. The processing method as described in claim 10, characterized in that, The height direction (H) of the processing tool is parallel to the axis of the superconducting magnet processed therefrom. The injection cavity (40) further includes several extension regions (44), each of the extension regions (44) being rod-shaped extending along the height direction (H). One end of each extension region (44) is connected to the through region (43), and the other end of each extension region (44) is closed. In the processing method, after injecting injection material into the injection cavity (40) and allowing the injection material to solidify, a rod portion (103) formed by solidifying the injection material is formed in each of the extension regions (44), and a main coil injection half (102) formed by solidifying the injection material is formed in the main coil receiving area (41). The step of connecting two superconducting magnet half (101) to form a superconducting magnet includes: The main coil injection half (102) connecting the two superconducting magnet halves (101), and The free end of the rod (103) connecting the two superconducting magnet halves (101).

12. The processing method as described in claim 9, characterized in that, The processing method further includes laying a reinforcing core material before injecting the injection material into the injection cavity (40), so that the reinforcing core material is finally located in the injection cavity (40).

13. The processing method as described in claim 12, characterized in that, The infusion material is resin, and the reinforcing core material is glass fiber.

14. A method for fabricating a superconducting magnet for a magnetic resonance imaging system, characterized in that, The processing method uses the processing tool as described in claim 8, and the processing method includes: A main coil half (61) of a superconducting magnet is wound using the first winding part (11) as the winding skeleton. A shielded coil (70) of a superconducting magnet is wound using the second winding part (21) as the winding skeleton. Assemble the first assembly (10), the second assembly (20) and the third assembly (30) to form the infusion cavity (40); Injecting a filling material into the filling cavity (40) and allowing the filling material to solidify; and Remove the processing tools.

15. A superconducting magnet for a magnetic resonance imaging system, characterized in that, The superconducting magnet is manufactured by the processing method according to any one of claims 9 to 14, and the superconducting magnet comprises: One main coil (60); Two shielding coils (70) are respectively arranged around the two ends of the main coil (60) in the axial direction; and An infusion body (80) formed by solidification of a liquid, comprising: A first molding part (81) is bonded to the main coil (60) by impregnation and curing. Two second molding portions (82), each of the second molding portions (82) being bonded to one of the shielding coils (70) by impregnation and curing, and Two connecting parts (83) are provided, each connecting part (83) connecting the first molding part (81) and the second molding part (82).

16. The superconducting magnet as described in claim 15, characterized in that, The injection body (80) contains a reinforcing core material (90).

17. A superconducting magnet for a magnetic resonance imaging system, characterized in that, The superconducting magnet is manufactured by the processing method described in claim 11, and the superconducting magnet comprises: One main coil (60); Two shielding coils (70) are respectively arranged around the two ends of the main coil (60) in the axial direction; and An infusion body (80) formed by solidification of a liquid, comprising: A first molding part (81) is bonded to the main coil (60) by impregnation and curing. Two second molding portions (82), each of which is bonded to one of the shielding coils (70) by impregnation and curing. Two connecting portions (83), each of which connects the first molding portion (81) and a second molding portion (82), and A set of reinforcing parts (84), each of the reinforcing parts (84) is a rod-shaped part extending along the axial direction of the main coil (60), and the two ends of each of the reinforcing parts (84) are respectively connected to two connecting parts (83).

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