WO2022201951A1 - 超電導コイル装置、超電導加速器および粒子線治療装置 - Google Patents
超電導コイル装置、超電導加速器および粒子線治療装置 Download PDFInfo
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- 239000002245 particle Substances 0.000 title claims description 48
- 238000002560 therapeutic procedure Methods 0.000 title description 10
- 230000007704 transition Effects 0.000 claims description 15
- 230000002093 peripheral effect Effects 0.000 claims description 6
- 238000002727 particle therapy Methods 0.000 claims 1
- 239000004020 conductor Substances 0.000 description 11
- 238000005452 bending Methods 0.000 description 9
- 238000005516 engineering process Methods 0.000 description 9
- -1 carbon ions Chemical class 0.000 description 7
- 239000002887 superconductor Substances 0.000 description 5
- 230000032258 transport Effects 0.000 description 4
- 230000001133 acceleration Effects 0.000 description 3
- 229910052799 carbon Inorganic materials 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 206010028980 Neoplasm Diseases 0.000 description 2
- 201000011510 cancer Diseases 0.000 description 2
- 239000010949 copper Substances 0.000 description 2
- 238000002347 injection Methods 0.000 description 2
- 239000007924 injection Substances 0.000 description 2
- 230000005405 multipole Effects 0.000 description 2
- 125000006850 spacer group Chemical group 0.000 description 2
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 1
- 229910052688 Gadolinium Inorganic materials 0.000 description 1
- XEEYBQQBJWHFJM-UHFFFAOYSA-N Iron Chemical group [Fe] XEEYBQQBJWHFJM-UHFFFAOYSA-N 0.000 description 1
- 229910020073 MgB2 Inorganic materials 0.000 description 1
- 229910052779 Neodymium Inorganic materials 0.000 description 1
- 241000920340 Pion Species 0.000 description 1
- 229910052772 Samarium Inorganic materials 0.000 description 1
- XKRFYHLGVUSROY-UHFFFAOYSA-N argon Substances [Ar] XKRFYHLGVUSROY-UHFFFAOYSA-N 0.000 description 1
- 229910052786 argon Inorganic materials 0.000 description 1
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 1
- 229910052788 barium Inorganic materials 0.000 description 1
- DSAJWYNOEDNPEQ-UHFFFAOYSA-N barium atom Chemical compound [Ba] DSAJWYNOEDNPEQ-UHFFFAOYSA-N 0.000 description 1
- 238000001816 cooling Methods 0.000 description 1
- 229910052802 copper Inorganic materials 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 229940079593 drug Drugs 0.000 description 1
- 239000000284 extract Substances 0.000 description 1
- UIWYJDYFSGRHKR-UHFFFAOYSA-N gadolinium atom Chemical compound [Gd] UIWYJDYFSGRHKR-UHFFFAOYSA-N 0.000 description 1
- 230000005484 gravity Effects 0.000 description 1
- 239000001307 helium Substances 0.000 description 1
- 229910052734 helium Inorganic materials 0.000 description 1
- 238000009434 installation Methods 0.000 description 1
- 150000002500 ions Chemical class 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- QEFYFXOXNSNQGX-UHFFFAOYSA-N neodymium atom Chemical compound [Nd] QEFYFXOXNSNQGX-UHFFFAOYSA-N 0.000 description 1
- 229910052754 neon Inorganic materials 0.000 description 1
- 229910000657 niobium-tin Inorganic materials 0.000 description 1
- 239000001301 oxygen Substances 0.000 description 1
- 229910052760 oxygen Inorganic materials 0.000 description 1
- 229910052761 rare earth metal Inorganic materials 0.000 description 1
- KZUNJOHGWZRPMI-UHFFFAOYSA-N samarium atom Chemical compound [Sm] KZUNJOHGWZRPMI-UHFFFAOYSA-N 0.000 description 1
- 238000004904 shortening Methods 0.000 description 1
- 229910052710 silicon Inorganic materials 0.000 description 1
- 239000010703 silicon Substances 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 230000001225 therapeutic effect Effects 0.000 description 1
- 238000011144 upstream manufacturing Methods 0.000 description 1
- 238000004804 winding Methods 0.000 description 1
- 229910052727 yttrium Inorganic materials 0.000 description 1
- VWQVUPCCIRVNHF-UHFFFAOYSA-N yttrium atom Chemical compound [Y] VWQVUPCCIRVNHF-UHFFFAOYSA-N 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1077—Beam delivery systems
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F6/00—Superconducting magnets; Superconducting coils
- H01F6/06—Coils, e.g. winding, insulating, terminating or casing arrangements therefor
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
- H05H13/00—Magnetic resonance accelerators; Cyclotrons
- H05H13/04—Synchrotrons
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
- H05H7/00—Details of devices of the types covered by groups H05H9/00, H05H11/00, H05H13/00
- H05H7/04—Magnet systems, e.g. undulators, wigglers; Energisation thereof
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
- A61N2005/1087—Ions; Protons
Definitions
- Particle beams must be accelerated to treat cancer cells deep within the body.
- Devices that accelerate particle beams are generally classified into two types. One is a linear accelerator that arranges accelerators in a straight line. The other is a circular accelerator in which a deflection device that bends the beam trajectory is arranged in a circular shape and an accelerator is arranged in a part of the circular orbit.
- a linear accelerator that accelerates the low energy band immediately after beam generation and a circular accelerator to accelerate the high energy band.
- Saddle-shaped coils are common among conventional superconducting coils for accelerators.
- spacers protrusions
- the superconducting wires are provided between the superconducting wires at the ends of the coils in order to generate a uniform magnetic field, that is, to reduce the high-order multipolar component. Therefore, there is a problem that the coil ends are extended and the superconducting coil is enlarged.
- the embodiment of the present invention has been made in consideration of such circumstances, and aims to provide a superconducting technology that can reduce the size of a superconducting coil device.
- FIG. 1 is a conceptual diagram showing a particle beam therapy system of this embodiment; FIG. The top view which shows a circular accelerator.
- FIG. 2 is a plan view showing a first-layer superconducting coil; FIG. 2 is a side view showing the superconducting coil of the first layer; VV sectional view of FIG. VI-VI sectional view of FIG. The top view which shows the superconducting coil of a 2nd layer. The side view which shows the superconducting coil of a 2nd layer.
- FIG. 2 is a plan view showing a state in which the superconducting coils of the first layer and the second layer are overlaid; FIG.
- FIG. 2 is a side view showing a state in which the superconducting coils of the first layer and the second layer are superposed.
- FIG. 3 is an exploded perspective view showing a superconducting coil of a modified example; The top view which shows the conventional superconducting coil.
- the embodiment of the present invention provides a superconducting technology that can reduce the size of the superconducting coil device.
- the particle beam therapy system 1 uses charged particles such as negative pions, protons, helium ions, carbon ions, neon ions, silicon ions, or argon ions as the particle beam B for therapeutic irradiation.
- charged particles such as negative pions, protons, helium ions, carbon ions, neon ions, silicon ions, or argon ions as the particle beam B for therapeutic irradiation.
- the inside of the vacuum duct 6 is maintained in a vacuum state.
- beam loss due to scattering between the particle beam B and the air is suppressed.
- This vacuum duct 6 continues until just before the location of the affected area T of the patient.
- the particle beam B that has passed through the vacuum duct 6 is irradiated onto the affected area T of the patient.
- the beam generator 2 is a device that generates a particle beam B.
- it is a device that extracts ions generated using electromagnetic waves or lasers.
- the beam accelerator 3 is provided downstream of the beam generator 2 .
- This beam accelerator 3 is a device that accelerates the particle beam B to a predetermined energy.
- This beam accelerator 3 is composed of, for example, two stages of a front-stage accelerator and a rear-stage accelerator.
- a linear accelerator 7 composed of a drift tube linac (DTL) or a radio frequency quadrupole linear accelerator (RFQ) is used as the pre-accelerator.
- a circular accelerator 8 composed of a synchrotron or a cyclotron is used as the post-stage accelerator.
- a beam trajectory of the particle beam B is formed by the linear accelerator 7 and the circular accelerator 8 .
- the beam transporter 4 is provided downstream of the beam accelerator 3 .
- the beam transport device 4 is a device that transports the accelerated particle beam B to the affected area T of the patient, which is the object to be irradiated.
- the vacuum duct 6 As the axis, it is composed of a deflection device, a convergence/divergence device, a sextupole device, a beam trajectory correction device, a control device thereof, and the like.
- the beam irradiation device 5 is provided downstream of the beam transport device 4 .
- the beam irradiation device 5 controls the beam trajectory of the particle beam B so that the particle beam B having a predetermined energy that has passed through the beam transport device 4 is correctly incident on the set irradiation point of the affected area T of the patient.
- the irradiation position and irradiation dose of the particle beam B on the affected area T are monitored.
- the beam accelerator 3 and the beam transporter 4 use superconducting technology that enables high magnetic field and miniaturization.
- the circular accelerator 8 of the beam accelerator 3 is exemplified as an application example of superconducting technology. That is, the particle beam therapy system 1 of this embodiment includes a circular accelerator 8 as a superconducting accelerator. At least part of the beam trajectory for accelerating the particle beam B is formed by the circular accelerator 8 .
- the circular accelerator 8 circulates the particle beam B along the vacuum duct 6 by bending the trajectory of the particle beam B injected from the linear accelerator 7 via the injection device 9 with the deflection device 11 .
- the particle beam B is stably circulated.
- the particle beam B revolves around the beam orbit of the circular accelerator 8
- an acceleration force is applied to the particle beam B by the acceleration force application device 14.
- the particle beam B is accelerated to a predetermined energy, and the accelerated particle beam B is emitted from the emission device 10 and reaches the diseased part T.
- the deflection device 11 deflects the particle beam B with a magnetic field. , the beam trajectory radius increases. As a result, the circular accelerator 8 becomes large as a whole. In order to suppress the size increase of the circular accelerator 8, it is necessary to increase the strength of the magnetic field generated by the deflection device 11. FIG. In this embodiment, by applying the superconducting technology to the deflection device 11, it becomes possible to increase the magnetic field, and the size of the circular accelerator 8 can be reduced.
- the superconducting wire is a low - temperature superconductor such as NbTi, Nb3Sn , Nb3Al , MgB2 , or a high - temperature superconductor such as a Bi2Sr2Ca2Cu3O10 wire or an REB2C3O7 wire . Configured.
- RE in “REB 2 C 3 O 7 " includes at least one of rare earth elements (e.g., neodymium (Nd), gadolinium (Gd), holminium (Ho), samarium (Sm), etc.) and yttrium elements.
- Nd neodymium
- Gd gadolinium
- Ho holminium
- Sm samarium
- yttrium elements means.
- B means barium (Ba).
- C means copper (Cu).
- O oxygen (O).
- Superconducting coil 80 is provided on the side surface of tubular structure 81 having a cylindrical shape.
- This superconducting coil 80 includes a plurality of conductor portions 82 around which a superconducting wire is wound.
- Each conductor portion 82 is divided into a coil longitudinal portion 83 and a coil end portion 84 .
- the distance between the conductor portions 82 in the circumferential direction is not uniform, and the desired magnetic field distribution is generated in the central beam passage area of the superconducting coil 80 depending on the distance.
- a spacer 85 (gap) is provided at the coil end 84 in order to suppress this negative sextupole magnetic field.
- a positive sextupole magnetic field is generated and a desired uniform magnetic field is obtained.
- the superconducting wires are arranged appropriately to obtain a desired uniform magnetic field and to reduce the size of the superconducting coil 80 .
- FIG. 1 a side view of the superconducting coil device 20 when viewed from the Y direction when the axial direction in which the particle beam B passes (the direction in which the axis C extends) is the X direction.
- a state when the superconducting coil device 20 is viewed from the Z direction will be described as a plan view (top view). Since this superconducting coil device 20 is not a device that is affected by gravity, there is no vertical distinction.
- the superconducting coil device 20 of this embodiment has a two-layer structure.
- This superconducting coil device 20 includes a first layer tubular structure portion 21 which is arranged on the innermost circumference and forms a tubular shape, and a second tubular structure portion 21 which is arranged on the outer circumference of the first layer tubular structure portion 21 and forms a tubular shape.
- a layered tubular structure 22 is provided. These tubular structures 21 and 22 are arranged concentrically around the axis C. As shown in FIG. That is, they are arranged coaxially with each other.
- the superconducting coil device 20 includes two superconducting coils 23 provided above and below the tubular structure 21 of the first layer. As shown in FIGS. 7 to 10, the superconducting coil device 20 includes two superconducting coils 24 provided above and below the tubular structure 22 of the second layer. That is, at least two superconducting coils 23 and 24 are laminated in the radial direction of the tubular structures 21 and 22 . A magnetic field can be generated in the passage area P of the particle beam B by these superconducting coils 23 and 24 .
- Each of the superconducting coils 23 and 24 has a shape that follows the outer peripheral surfaces of the tubular structures 21 and 22.
- Tubular structures 21 and 22 are members that support superconducting coils 23 and 24 .
- the innermost first-layer tubular structure 21 is arranged at the axis C of the superconducting coil device 20 .
- This first layer tubular structure 21 forms part of the vacuum duct 6 .
- the tubular structure 21 may be a member separate from the vacuum duct 6 . That is, the vacuum duct 6 may be provided inside the tubular structure 21 .
- the superconducting coils 23 and 24 are formed by winding a superconducting wire into a ring.
- one superconducting coil 23, 24 is formed by a plurality of turns 25, 26, where one turn 25, 26 is a portion of the superconducting wire that is wound one round.
- FIG. 3 shows three turns 25 forming one superconducting coil 23 .
- five turns 26 are shown to form one superconducting coil 24 .
- one superconducting coil 23, 24 is formed by tens to hundreds of turns 25, 26.
- the superconducting coil 24 of the second layer is larger than the superconducting coil 23 of the first layer. of turns 26 can be placed.
- the superconducting coil device 20 is applied, for example, to the deflection device 11 (FIG. 2) of the circular accelerator 8.
- the deflection device 11 is provided with a vacuum duct 6 which is curved with a constant curvature. Therefore, the tubular structures 21 and 22 used in the actual superconducting coil device 20 are also members bent with a constant curvature. However, in FIGS. 3, 4, 7, 8, 11, and 12, the tubular structures 21 and 22 are shown as linear members for better understanding. Also, the axial centers C of the tubular structures 21 and 22 are shown as straight lines, although they are actually curved with a constant curvature.
- the tubular structures 21 and 22 have an elliptical shape when viewed in cross section.
- each of the tubular structures 21 and 22 has an elliptical shape with a larger diameter in the Y direction than in the Z direction. That is, the tubular structures 21 and 22 have an elliptical shape in which the diameter increases in the bending direction.
- the superconducting coil device 20 can generate a magnetic field suitable for the direction in which the particle beam B bends.
- the respective turns 25 and 26 have coil longitudinal portions 27 and 27 extending linearly along the axial direction (X direction) of the tubular structures 21 and 22.
- 28 and coil end portions 29, 30 extending from the coil longitudinal portions 27, 28 along the circumferential direction of the tubular structures 21, 22.
- boundary lines L1 and L2 indicating boundaries between the coil longitudinal portions 27 and 28 and the coil end portions 29 and 30 in the respective turns 25 and 26 are aligned with the tubular structures.
- the portions 21 and 22 are inclined with respect to the reference line K extending in the circumferential direction.
- the boundary line L1 of the superconducting coil 23 of the first layer and the boundary line L2 of the superconducting coil 24 of the second layer are inclined in the same direction with respect to the reference line K. As shown in FIG.
- the regions in which the coil longitudinal portions 27 and 28 are provided are divided into main magnetic field generation regions 51A and 52A, transition regions 51B and 52B, and magnetic field correction regions 51C and 52C. divided.
- the main magnetic field generation regions 51A and 52A are regions in which the superconducting coils 23 and 24 generate the main magnetic field.
- the main magnetic field generating regions 51A and 52A are central portions of the coil longitudinal portions 27 and 28 in the axial direction (X direction) of the tubular structures 21 and 22, respectively.
- the magnetic field correction regions 51C and 52C are regions in which magnetic fields for correction are generated near the ends of the superconducting coils 23 and 24.
- the magnetic field correction regions 51C and 52C are provided at the ends of the coil longitudinal portions 27 and 28 in the axial direction (X direction) of the tubular structure portions 21 and 22, respectively.
- the magnetic field correction regions 51C and 52C can correct the magnetic field generated by the end portions of the coil longitudinal portions 27 and 28 .
- the transition regions 51B and 52B are regions provided between the main magnetic field generation regions 51A and 52A and the magnetic field correction regions 51C and 52C.
- the transition regions 51B and 52B allow the magnetic field to smoothly and continuously transition from the ends of the main magnetic field generation regions 51A and 52A to the magnetic field correction regions 51C and 52C.
- the coil longitudinal portions 27, 28 have base portions 27A, 28A, tapered portions 27B, 28B, and offset portions 27C, 28C.
- the base portions 27A and 28A are portions corresponding to the main magnetic field generating regions 51A and 52A.
- the tapered portions 27B and 28B are portions corresponding to the transition regions 51B and 52B.
- the offset portions 27C and 28C are portions corresponding to the magnetic field correction regions 51C and 52C.
- the offset portions 27C and 28C of the coil longitudinal portions 27 and 28 are displaced in the circumferential direction of the tubular structures 21 and 22. .
- the offset portions 27C and 28C are displaced toward the inner peripheral side of the superconducting coils 23 and 24 in plan view of the tubular structural portions 21 and 22, respectively. In this way, the magnetic fields generated in the magnetic field correction regions 51C and 52C can be made different from the magnetic fields generated in the main magnetic field generation regions 51A and 52A.
- the range R1 in which the base portion 27A of the first layer is provided and the range R2 in which the offset portion 27C is provided are different.
- the offset portion 27C is disposed above or below the base portion 27A (offset).
- the range R3 where the base portion 28A of the second layer is provided and the range R4 where the offset portion 28C is provided are different.
- the offset portion 28C is disposed above or below the base portion 28A (offset).
- the range R1 in which the base portion 27A of the first layer is provided and the range R3 in which the base portion 28A of the second layer is provided are different. Further, the range R2 in which the offset portion 27C of the first layer is provided and the range R4 in which the offset portion 28C of the second layer is provided are different.
- the magnetic fields generated in the magnetic field correction regions 51C and 52C may not only cancel the error magnetic field, but may also be a predetermined magnetic field based on the magnetic field distribution required for the superconducting coils 23 and 24.
- the magnetic fields generated in the magnetic field correction regions 51C and 52C may be used to reinforce the main magnetic fields generated in the main magnetic field generation regions 51A and 52A.
- the high-order multipole components to be superimposed are not limited to the ends of the coil, and may be at any place, and different high-order multipole components may be added on the upstream side and the downstream side of the coil.
- the axial dimension (X direction) of the transition region 51B of the first-layer superconducting coil 23 and the axial dimension of the transition region 52B of the second-layer superconducting coil 24 are different from each other. different.
- the axial dimension of the transition region 52B of the second layer is larger than the axial dimension of the transition region 51B of the first layer. In this way, an appropriate magnetic field can be formed by the superconducting coils 23 of the first layer and the superconducting coils 24 of the second layer.
- the axial dimension (X direction) of the magnetic field correction region 51C of the first layer and the axial dimension of the magnetic field correction region 52C of the second layer are also different from each other.
- the superconducting coil device 20 of this embodiment can suppress the generation of an error magnetic field (unnecessary magnetic field component) disturbed from the desired magnetic field distribution near the ends of the superconducting coils 23 and 24 .
- the error magnetic field at the end of the superconducting coil 23 of the first layer can be canceled by the magnetic field generated by the end of the superconducting coil 24 of the second layer.
- the turns 25 and 26 (superconducting wire) can be densely arranged at the coil ends 29 and 30, respectively. Therefore, the width (length in the X direction) of the coil ends 29 and 30 can be reduced.
- the plurality of superconducting coils 23 and 24 are laminated in the radial direction of the tubular structures 21 and 22, many turns 25 and 26 (superconducting wire rods) are formed in the circumferential direction when viewed in cross section. ) can be placed. Therefore, a stronger magnetic field can be generated.
- the tubular structures 21 and 22 are laminated in the radial direction, the outer circumference length increases, so the outer layer (second layer) has more turns 26 than the inner layer (first layer). can be placed. By arranging many turns 25 and 26 with a small number of layers, a strong magnetic field can be generated.
- FIG. 13 the illustration of the tubular structure is omitted and only the arrangement of the superconducting coils 23 and 24 is shown to aid understanding.
- the superconducting coil device 40 of the modified example includes two superconducting quadrupole coils 41 that are provided in the first layer and generate a quadrupole magnetic field, and one superconducting dipole coil 42 that is provided in the second layer and generates a dipole magnetic field. Prepare.
- One superconducting quadrupole coil 41 is formed by four superconducting coils 23 . Two superconducting quadrupole coils 41 are arranged side by side in the axial direction (X direction).
- one superconducting dipole coil 42 is formed by two superconducting coils 24 .
- the superconducting two-pole coil 42 and the superconducting four-pole coil 41 are arranged coaxially with each other.
- the modified superconducting coil device 40 can appropriately control the particle beam B with the dipole magnetic field generated by the superconducting dipole coil 42 and the quadrupole magnetic field generated by the superconducting quadrupole coil 41 .
- tubular structures 21 and 22 are elliptical in cross section in the above-described embodiment, they may be in other forms.
- the tubular structures 21 and 22 may have a perfect circular shape or an elliptical shape when viewed in cross section.
- the tubular structures 21 and 22 have an elliptical shape with a diameter that increases in the bending direction, but may be in another form.
- the tubular structures 21 and 22 may have an elliptical shape with a smaller diameter in the bending direction.
- the boundary line L1 of the superconducting coil 23 of the first layer and the boundary line L2 of the superconducting coil 24 of the second layer are inclined in the same direction with respect to the reference line K. It may be a mode.
- the boundary line L1 of the superconducting coils 24 of the first layer and the boundary line L2 of the superconducting coils 24 of the second layer may be inclined in opposite directions with respect to the reference line K.
- FIG. In this way, the magnetic fields generated at the ends of the superconducting coils 23 of the first layer and the magnetic fields generated at the ends of the superconducting coils 24 of the second layer have different forms.
- the arrangement of the coil longitudinal portions is different between the main magnetic field generation region for generating the main magnetic field and the magnetic field correction region for generating the magnetic field for correction. Miniaturization can be achieved.
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Abstract
Description
Claims (11)
- 環状に巻き回された超電導線材の1周巻き回された部分を1つのターンとしたときに、複数の前記ターンで形成された少なくとも1つの超電導コイルを備え、
前記超電導コイルは、管状を成す管状構造部の外周面に沿う形状を成し、
前記ターンは、前記管状構造部の軸方向に沿って延びるコイル長手部を有し、
前記コイル長手部の配置形態が、主磁場を発生させる主磁場発生領域と補正用の磁場を発生させる磁場補正領域とで互いに異なっている、
超電導コイル装置。 - 前記管状構造部の側面視で、前記コイル長手部の前記磁場補正領域の部分が前記管状構造部の周方向に変位されている、
請求項1に記載の超電導コイル装置。 - 前記コイル長手部の前記磁場補正領域の部分が前記超電導コイルの内周側に変位されている、
請求項1または請求項2に記載の超電導コイル装置。 - 前記コイル長手部の端部が前記磁場補正領域の部分となっている、
請求項1から請求項3のいずれか1項に記載の超電導コイル装置。 - 前記ターンは、前記コイル長手部から前記管状構造部の周方向に沿って延びるコイル端部を有し、
前記磁場補正領域は、少なくとも前記コイル端部で発生する不要な磁場成分を打ち消す磁場を発生させる、
請求項4に記載の超電導コイル装置。 - 前記主磁場発生領域と前記磁場補正領域との間に遷移領域が設けられ、前記コイル長手部の前記遷移領域の部分が、前記コイル長手部の前記主磁場発生領域および前記磁場補正領域の部分に対して傾いている、
請求項1から請求項5のいずれか1項に記載の超電導コイル装置。 - 少なくとも2つの前記超電導コイルが前記管状構造部の径方向に積層されており、
第1層の前記超電導コイルの前記遷移領域の寸法と第2層の前記超電導コイルの前記遷移領域の寸法が互いに異なっている、
請求項6に記載の超電導コイル装置。 - 前記管状構造部は、一定の曲率で曲がっているとともに断面視で楕円形状を成している、
請求項1から請求項7のいずれか1項に記載の超電導コイル装置。 - 複数の前記超電導コイルにより形成され、二極磁場を発生させる超電導二極コイルと、
複数の前記超電導コイルにより形成され、四極磁場を発生させる超電導四極コイルと、
を備え、
前記超電導二極コイルと前記超電導四極コイルとが互いに同軸に配置されている、
請求項1から請求項8のいずれか1項に記載の超電導コイル装置。 - 請求項1から請求項9のいずれか1項に記載の超電導コイル装置を備え、
複数の前記超電導コイル装置により粒子線ビームを加速するビーム軌道が形成される、
超電導加速器。 - 請求項10に記載の超電導加速器を備え、
前記超電導加速器により前記粒子線ビームを加速し、前記粒子線ビームを患部に照射して治療を行う、
粒子線治療装置。
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KR1020237023739A KR20230119191A (ko) | 2021-03-23 | 2022-02-10 | 초전도 코일 장치, 초전도 가속기 및 입자선 치료 장치 |
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JP2009301992A (ja) * | 2008-06-17 | 2009-12-24 | Toshiba Corp | 超電導コイル装置 |
JP2010118457A (ja) * | 2008-11-12 | 2010-05-27 | Sumitomo Electric Ind Ltd | 超電導コイルおよび該超電導コイルの製造方法 |
JP2013206635A (ja) * | 2012-03-27 | 2013-10-07 | Natl Inst Of Radiological Sciences | 偏向電磁石コイル設計方法、偏向電磁石コイル設計装置、超電導電磁石、加速器、及びコイル配置最適化プログラム |
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JPH10144521A (ja) | 1996-11-07 | 1998-05-29 | Hitachi Ltd | 360°ヘリカル回転二極磁場生成電磁石 |
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JP2009301992A (ja) * | 2008-06-17 | 2009-12-24 | Toshiba Corp | 超電導コイル装置 |
JP2010118457A (ja) * | 2008-11-12 | 2010-05-27 | Sumitomo Electric Ind Ltd | 超電導コイルおよび該超電導コイルの製造方法 |
JP2013206635A (ja) * | 2012-03-27 | 2013-10-07 | Natl Inst Of Radiological Sciences | 偏向電磁石コイル設計方法、偏向電磁石コイル設計装置、超電導電磁石、加速器、及びコイル配置最適化プログラム |
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CN116170933A (zh) * | 2023-01-09 | 2023-05-26 | 中国科学院近代物理研究所 | 用于应用型等时性回旋加速器的磁场装置 |
CN116170933B (zh) * | 2023-01-09 | 2023-09-05 | 中国科学院近代物理研究所 | 用于应用型等时性回旋加速器的磁场装置 |
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