CN111249633A - High momentum acceptance superconducting rotating gantry for proton therapy - Google Patents
High momentum acceptance superconducting rotating gantry for proton therapy Download PDFInfo
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- CN111249633A CN111249633A CN202010204373.6A CN202010204373A CN111249633A CN 111249633 A CN111249633 A CN 111249633A CN 202010204373 A CN202010204373 A CN 202010204373A CN 111249633 A CN111249633 A CN 111249633A
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- 238000002661 proton therapy Methods 0.000 title claims description 8
- 239000006185 dispersion Substances 0.000 claims abstract description 32
- 230000008030 elimination Effects 0.000 claims abstract description 14
- 238000003379 elimination reaction Methods 0.000 claims abstract description 14
- 239000001064 degrader Substances 0.000 claims abstract description 7
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 claims description 5
- 229910002804 graphite Inorganic materials 0.000 claims description 5
- 239000010439 graphite Substances 0.000 claims description 5
- 229910052580 B4C Inorganic materials 0.000 claims description 3
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 claims description 2
- INAHAJYZKVIDIZ-UHFFFAOYSA-N boron carbide Chemical compound B12B3B4C32B41 INAHAJYZKVIDIZ-UHFFFAOYSA-N 0.000 claims description 2
- 229910052802 copper Inorganic materials 0.000 claims description 2
- 239000010949 copper Substances 0.000 claims description 2
- 230000008859 change Effects 0.000 abstract description 6
- 238000010791 quenching Methods 0.000 abstract description 4
- 230000005540 biological transmission Effects 0.000 description 5
- 206010028980 Neoplasm Diseases 0.000 description 4
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- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 2
- 238000002729 3-dimensional conformal radiation therapy Methods 0.000 description 1
- 230000000712 assembly Effects 0.000 description 1
- 238000000429 assembly Methods 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
- A61N5/1042—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy with spatial modulation of the radiation beam within the treatment head
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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
- A61N5/1077—Beam delivery systems
- A61N5/1081—Rotating beam systems with a specific mechanical construction, e.g. gantries
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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
- 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
Abstract
The invention discloses a high momentum receptivity superconducting rotating rack for proton treatment, which comprises an energy degrader component, a first deflection superconducting magnet component, a second deflection superconducting magnet component and a treatment head component, wherein the energy degrader component is positioned at the entrance of the rack; the first deflection superconducting magnet assembly and the second deflection superconducting magnet assembly respectively comprise a deflection magnet and a focusing magnet and are of symmetrical structures; the deflection magnet is a combined superconducting magnet with a dipolar field and an alternating gradient quadrupole field; the superconducting rotating machine frame has high momentum acceptance by respectively realizing the dispersion elimination in the first deflection superconducting magnet assembly and the second deflection superconducting magnet assembly and utilizing the strong focusing characteristic of an alternating gradient quadrupole field to inhibit the maximum value of a dispersion function. Therefore, the weight and the size of the frame are remarkably reduced, and meanwhile, the problem of quench caused by the superconducting magnet under the rapid magnetic field change is avoided.
Description
Technical Field
The invention belongs to the technical field of proton treatment, and particularly relates to a high momentum receptivity superconducting rotating machine frame for proton treatment.
Background
Proton therapy is an accurate radiation therapy method for cancer. Based on the proton Bragg peak dose distribution characteristic, dose control at different depths can be realized by adjusting the energy of irradiated proton beams, and meanwhile, transverse beam irradiation is realized by utilizing the currently and commonly used pencil beam scanning technology, so that accurate three-dimensional conformal radiotherapy of tumors is realized, and the damage to peripheral healthy tissues is reduced.
The 180-degree or 360-degree rotating frame is a core subsystem of proton treatment, and can carry out multi-irradiation radiotherapy of different angles on a focus according to a treatment plan. The current rotating frame beam transport line on the market mainly adopts the traditional normal temperature electromagnet, the final dipolar magnet weight is about 10 tons, the whole frame weight usually exceeds 200 tons, the occupied area is large, and the manufacturing cost is high.
The introduction of superconducting magnet technology will significantly reduce the rack volume and weight, and in particular, can significantly reduce the weight of dipole magnets used for beam deflection in the rack beam line. The main technical problem faced by the superconducting scheme is that for the rapid change of energy in the proton treatment process (the current level is that the magnetic rigidity of a proton beam is changed by 1% within 100 ms), the corresponding superconducting magnetic field and coil current need to reach the same change speed, and quench and instability of the magnetic field are easily caused.
Disclosure of Invention
Aiming at the defects and improvement requirements of the prior art, the invention aims to introduce the combined superconducting magnet to the bent section of the beam line of the rack so as to obviously reduce the weight and the size of the rack, and simultaneously improve the acceptance of the proton momentum (or kinetic energy) of the beam line of the whole rack by one magnitude compared with the existing scheme through beam optical design and optimization so as to realize that the magnetic field of the superconducting magnet is kept fixed under the condition of a large energy range (corresponding water transmission depth range) of the proton beam and further avoid the quench problem of the superconducting magnet under the condition of rapid magnetic field change.
To achieve the above object, the present invention providesA high momentum receptivity superconducting rotating gantry for proton therapy is provided, comprising: the energy degrader component is positioned at the inlet of the rack; deflection angle theta1The first deflection superconducting magnet assembly of (a); deflection angle theta2A second deflection superconducting magnet assembly of (a); a treatment head assembly with pencil beam scanning function;
wherein, theta1Take 45-60 degrees theta2Takes 135 to 150 degrees and satisfies theta2-θ1＝90°；
The first deflection superconducting magnet assembly and the second deflection superconducting magnet assembly respectively comprise a deflection magnet and a focusing magnet and are of symmetrical structures; the deflection magnet is a combined superconducting magnet with a dipolar field and an alternating gradient quadrupole field;
the superconducting rotating machine frame has high momentum acceptance by respectively realizing the dispersion elimination in the first deflection superconducting magnet assembly and the second deflection superconducting magnet assembly and utilizing the strong focusing characteristic of an alternating gradient quadrupole field to inhibit the maximum value of a dispersion function.
Further, the first deflecting superconducting magnet assembly includes: a first deflection magnet, a second deflection magnet, a first focusing magnet, a second focusing magnet, and a third focusing magnet;
the first deflection magnet and the second deflection magnet are combined superconducting magnets with dipolar fields and alternating gradient quadrupole fields, and respectively realize theta12, deflecting the beam;
the first focusing magnet, the second focusing magnet and the third focusing magnet are quadrupole field and hexapole field combined magnets, are positioned between the first deflection magnet and the second deflection magnet, and are used for matching with the first deflection magnet and the second deflection magnet to realize beam focusing and local dispersion elimination.
Further, the second deflection superconducting magnet assembly includes: a third deflection magnet, a fourth deflection magnet, and a fourth focusing magnet;
the third deflection magnet and the fourth deflection magnet are combined superconducting magnets with dipolar fields and alternating gradient quadrupole fields, and the effects are realized respectivelyθ22, deflecting the beam;
the fourth focusing magnet is a quadrupole field and hexapole field combined magnet, is positioned between the third deflection magnet and the fourth deflection magnet, and is used for matching with the third deflection magnet and the fourth deflection magnet to realize beam focusing and local dispersion elimination.
Further, the maximum range of a dipolar field in the first deflection superconducting magnet assembly is 2T-3.3T, and the maximum gradient of a quadrupole field is less than or equal to 60T/m; the maximum range of a dipolar field in the second deflection superconducting magnet assembly is 2T-3.3T, and the maximum gradient of a quadrupole field is less than or equal to 30T/m.
Further, the degrader assembly comprises: a pair of wedge-shaped energy-reducing blocks driven by a motor, and a collimator module disposed downstream of the wedge-shaped energy-reducing blocks.
Furthermore, the wedge-shaped energy reducing block is made of graphite or boron carbide, and the overall size of the wedge-shaped energy reducing block along the beam direction is smaller than 260 mm.
Furthermore, the collimator module is made of copper and graphite, and the overall size of the collimator module along the beam direction is smaller than 700 mm.
Further, the treatment head assembly comprises a scanning magnet located downstream of the second deflection superconducting magnet assembly, and the source wheelbase is less than or equal to 2 m.
Further, the superconducting rotating gantry has a total length of less than or equal to 7m and a radius of rotation of less than or equal to 4m, and is configured to rotate plus or minus 180 degrees.
Further, the superconducting rotating gantry can receive the initial energy E of the front-end proton acceleratoriThe range is 220-250 MeV, and the energy range of the proton beam for isocenter treatment is 70 MeV-Ei(ii) a Can be configured as a single or multi-compartment proton therapy system.
Generally, by the above technical solution conceived by the present invention, the following beneficial effects can be obtained:
(1) the combined superconducting magnet with the dipolar field and the alternating gradient quadrupole field is adopted to replace the traditional normal-temperature electromagnet, and the number, the aperture and the weight of the rack magnets are optimized, so that the weight and the size of the rack are obviously reduced, and the manufacturing, the installation and the operation cost of the rack are further reduced.
(2) The invention realizes local dispersion elimination through the symmetrical structure of each deflection superconducting magnet assembly, and utilizes the strong focusing characteristic of an alternating gradient quadrupole field to inhibit the maximum value of a dispersion function, thereby obviously reducing the size increase of transverse beam caused by dispersion in the beam transmission process and realizing the large momentum acceptance of +/-10%. Based on the acceptance, the transferred proton energy range can cover the depth of the main type tumor focus on the premise of not changing the magnetic field of the superconducting magnet; for tumors with a large depth range, a global depth coverage can be achieved by varying the magnetic field 1 to 2 times. Therefore, on the premise of high momentum acceptance, the superconducting magnet does not need to change the magnetic field of the superconducting magnet rapidly, thereby avoiding the quench problem caused by the change of the superconducting magnet in a rapid magnetic field (or exciting current) and simultaneously meeting the technical requirement of rapid pencil beam scanning.
Drawings
FIG. 1 is a schematic view of a high momentum receptivity superconducting rotating gantry configuration for proton therapy provided in accordance with the present invention;
fig. 2 is a schematic diagram of beam envelopes in vertical and horizontal directions of a rotating gantry beam line in an embodiment of the invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention is described in further detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention. In addition, the technical features involved in the embodiments of the present invention described below may be combined with each other as long as they do not conflict with each other.
The invention provides a high momentum receptivity superconducting rotating machine frame for proton treatment, which comprises: the energy degrader component is positioned at the inlet of the rack; deflection angle theta1The first deflection superconducting magnet assembly of (a); deflection angle theta2A second deflection superconducting magnet assembly of (a); a treatment head assembly 40 with pencil beam scanning function; wherein, theta1Take 45-60 degrees theta2Takes 135 to 150 degrees and satisfies theta2-θ190 °; due to the angle of deflection theta2The increase results in a magnet that is too long to be easily manufactured, preferably, θ1Take 45 degrees theta2Take 135 deg.
In the following by theta1Take 45 degrees theta2The present invention will be described in further detail with reference to 135 ° as an example.
As shown in fig. 1, the gantry beam streamline 02 is coupled at the front end to a proton accelerator (not explicitly depicted) that receives a proton beam from the accelerator, typically having an energy in the range of 220MeV to 250MeV, and a fixed energy. At the coupling point 00, the beam current is matched into a mirror image beam current through a main beam current line at the front end, and the size of a beam spot standard deviation for treatment is about 3.5mm at the isocenter 01. The gantry beam line 02 generally employs a post-scan approach, i.e., the scan magnet 41 is placed downstream of the last deflection magnet, with a source wheelbase SAD of less than or equal to 2 m.
The energy reducer assembly is positioned at the front end of the whole machine frame beam streamline and comprises a pair of wedge-shaped energy reducing blocks 10, a first collimator module 11 and a second collimator module 12. Wherein a pair of wedge-shaped energy reducing blocks 10 realize proton energy adjustment of 70MeV at the lowest; preferably linear motor drive to achieve rapid motion control, typically with 5mm water transmission depth step, the energy conditioning time is no more than 50 ms; the preferred density of the wedge-shaped energy reducing block 10 material is higher than 1.95g/cm3Isotropic graphite, or a graphite-boron carbide mixed material with higher transmission efficiency can be selected; the first collimator module 11 and the second collimator module 12 are located at the downstream of the pair of wedge-shaped energy reducing blocks 10, control over beam size and divergence angle is achieved respectively, and selection of root-mean-square emission degree within a range of 3-10 pi · mm · mrad can be achieved generally by switching collimator aperture under driving of a motor.
The first deflection superconducting magnet assembly performs 45-degree beam deflection, focusing and local dispersion elimination and comprises a first deflection magnet 21, a second deflection magnet 22, a first focusing magnet 23, a second focusing magnet 24 and a third focusing magnet 25. The first deflection magnet 21 and the second deflection magnet 22 are combined superconducting magnets with dipole fields and alternating gradient quadrupole fields, are symmetrical structures, and respectively realize 22.5-degree beam deflection, and preferably adopt a helical coil-type (CCT) superconducting magnet; the bending radius is 0.75m-1m, preferably 1m, the maximum dipolar field corresponding to a proton beam with central energy of 230MeV is 2.32T, and the alternating gradient quadrupole field is not more than 60T/m; the first focusing magnet 23, the second focusing magnet 24 and the third focusing magnet 25 are all quadrupole field and hexapole field combined magnets, are placed between the first deflection magnet 21 and the second deflection magnet 22, are of symmetrical structures, and are matched with the first deflection magnet 21 and the second deflection magnet 22 to realize beam focusing and local dispersion elimination, wherein hexapole field components are used for compensating high-order chromatic aberration.
The second deflection superconducting magnet assembly completes 135-degree beam deflection, focusing and local dispersion elimination, and comprises: a third deflection magnet 31, a fourth deflection magnet 32, and a fourth focusing magnet 33. The third deflection magnet 31 and the fourth deflection magnet 32 are combined superconducting magnets with dipole fields and alternating gradient quadrupole fields, are symmetrical structures, and respectively realize 67.5-degree beam deflection, and preferably adopt a helical coil-type (CCT) superconducting magnet; the bending radius is 0.75m-1m, preferably 1m, the maximum dipolar field corresponding to a proton beam with central energy of 230MeV is 2.32T, and the alternating gradient quadrupole field is not more than 30T/m; the fourth focusing magnet 33 is a quadrupole field and hexapole field combined magnet, is placed between the third deflection magnet 31 and the fourth deflection magnet 32, and is matched with the third deflection magnet 31 and the fourth deflection magnet 32 to realize beam focusing and local dispersion elimination, wherein hexapole field components are used for compensating high-order chromatic aberration.
At present, the frame beam optics based on the normal-temperature magnet adopts global dispersion elimination, namely, a dispersion function is distributed on the whole beam line and is adjusted to be 0 only at the tail part; in the present invention, however, at the end points of the first deflecting superconducting magnet assembly and the second deflecting superconducting magnet assembly, the dispersion is vanished, that is, the local dispersion is vanished.
Generally, the invention adopts the local achromatic science design and remarkably reduces the size increase of transverse beams caused by dispersion in the beam transmission process by a dispersion function inhibition method, thereby realizing the large momentum acceptance of +/-10%. The local de-dispersion optical design is realized by respectively realizing de-dispersion in 45-degree and 135-degree deflection superconducting magnet assemblies through an optical matching design, and particularly is realized through a symmetrical structure of each deflection superconducting magnet assembly; the dispersion function suppression method is to suppress the maximum value of the dispersion function by utilizing the strong focusing characteristic of the alternating gradient magnet.
Specifically, as shown in fig. 1, each of the first deflection superconducting magnet assembly and the second deflection superconducting magnet assembly has a symmetrical structure, for example, in the first deflection superconducting magnet assembly, the first deflection magnet 21 and the second deflection magnet 22, the first focusing magnet 23 and the third focusing magnet 25 are symmetrical in position to the left and right with respect to the second focusing magnet 24, and the first focusing magnet 23 and the third focusing magnet 25 have the same magnetic field parameter. Under the structure, the dispersion function reaches the maximum value in the middle of each segment of deflection superconducting magnet assembly and is reduced to zero at the tail part, and local dispersion elimination is realized.
Fig. 2 is a schematic diagram of beam envelopes of a beam line of a rotating gantry in the vertical and horizontal directions in the embodiment of the present invention, where a curve 50 is a beam envelope in the Y direction, a curve 60 is a beam envelope in the X direction with a single energy (momentum dispersion dp/p is 0), a curve 61 is a beam envelope in the X direction with a momentum dispersion dp/p of 10%, and a curve 70 is a dispersion function. The beam envelope shows that the invention can realize the momentum acceptance of +/-10%.
It should be understood by those skilled in the art that the foregoing is only a preferred embodiment of the present invention, and is not intended to limit the scope of the invention, and that any modifications, equivalent substitutions, improvements, etc., such as alternative to the alternating gradient combined deflection magnet, adjustable deflection angles (45 degrees and 135 degrees) of the two segment deflection magnet assembly, etc., within the spirit and principle of the present invention, are all included in the scope of the present invention.
Claims (10)
1. A high momentum receptivity superconducting rotating gantry for proton therapy, comprising:
the energy degrader component is positioned at the inlet of the rack; deflection angle theta1The first deflection superconducting magnet assembly of (a); deflection angle theta2A second deflection superconducting magnet assembly of (a); with pencil beam scanningA functional treatment head assembly;
wherein, theta1Take 45-60 degrees theta2Takes 135 to 150 degrees and satisfies theta2-θ1＝90°；
The first deflection superconducting magnet assembly and the second deflection superconducting magnet assembly respectively comprise a deflection magnet and a focusing magnet and are of symmetrical structures; the deflection magnet is a combined superconducting magnet with a dipolar field and an alternating gradient quadrupole field;
the superconducting rotating machine frame has high momentum acceptance by respectively realizing the dispersion elimination in the first deflection superconducting magnet assembly and the second deflection superconducting magnet assembly and utilizing the strong focusing characteristic of an alternating gradient quadrupole field to inhibit the maximum value of a dispersion function.
2. The superconducting rotating gantry of claim 1 wherein the first deflective superconducting magnet assembly comprises: a first deflection magnet (21), a second deflection magnet (22), a first focusing magnet (23), a second focusing magnet (24), and a third focusing magnet (25);
the first deflection magnet (21) and the second deflection magnet (22) are combined superconducting magnets having a dipole field and an alternating gradient quadrupole field, and respectively realize theta12, deflecting the beam;
the first focusing magnet (23), the second focusing magnet (24) and the third focusing magnet (25) are quadrupole field and hexapole field combined magnets, are located between the first deflection magnet (21) and the second deflection magnet (22), and are used for matching the first deflection magnet (21) and the second deflection magnet (22) to realize beam focusing and local dispersion elimination.
3. The superconducting rotating gantry of claim 1 wherein the second deflective superconducting magnet assembly comprises: a third deflection magnet (31), a fourth deflection magnet (32), and a fourth focusing magnet (33);
the third deflection magnet (31) and the fourth deflection magnet (32) are combined superconducting magnets with dipolar fields and alternating gradient quadrupole fields, and respectively realize theta22, deflecting the beam;
the fourth focusing magnet (33) is a quadrupole field and hexapole field combined magnet, is positioned between the third deflection magnet (31) and the fourth deflection magnet (32), and is used for matching the third deflection magnet (31) and the fourth deflection magnet (32) to realize beam focusing and local dispersion elimination.
4. The superconducting rotating gantry of any one of claims 1 to 3,
the maximum range of a dipolar field in the first deflection superconducting magnet assembly is 2T-3.3T, and the maximum gradient of a quadrupole field is less than or equal to 60T/m;
the maximum range of a dipolar field in the second deflection superconducting magnet assembly is 2T-3.3T, and the maximum gradient of a quadrupole field is less than or equal to 30T/m.
5. The superconducting rotating gantry of claim 1 wherein the degrader assembly comprises: a pair of wedge-shaped energy-reducing blocks driven by a motor, and a collimator module disposed downstream of the wedge-shaped energy-reducing blocks.
6. The superconducting rotating gantry of claim 5 wherein the wedge shaped energy reducing block is made of graphite or boron carbide and has an overall dimension along the beam direction of less than 260 mm.
7. The superconducting rotating gantry of claim 5 wherein the collimator modules are made of copper and graphite and have an overall dimension along the beam direction of less than 700 mm.
8. The superconducting rotating gantry of claim 1 wherein the treatment head assembly comprises a scanning magnet downstream of the second deflection superconducting magnet assembly, and wherein a source wheelbase is less than or equal to 2 m.
9. The superconducting rotating gantry of claim 1, wherein the superconducting rotating gantry has a total length of less than or equal to 7m, a radius of rotation of less than or equal to 4m, and is configured to rotate plus or minus 180 degrees.
10. The superconducting rotating gantry of claim 1 wherein the superconducting rotating gantry can accept a front end proton accelerator initial energy EiThe range is 220-250 MeV, and the energy range of the proton beam for isocenter treatment is 70 MeV-Ei(ii) a Can be configured as a single or multi-compartment proton therapy system.
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN111686377A (en) * | 2020-06-16 | 2020-09-22 | 中国科学院近代物理研究所 | Carbon ion beam superconducting rotating Gantry |
| CN116585623A (en) * | 2023-05-06 | 2023-08-15 | 华中科技大学 | Large momentum acceptance superconductive rotating frame for proton cancer treatment device |
| WO2024032049A1 (en) * | 2022-08-09 | 2024-02-15 | 合肥中科离子医学技术装备有限公司 | Superconducting rotating rack and proton therapy device |
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