CN111686377A - Carbon ion beam superconducting rotating Gantry - Google Patents
Carbon ion beam superconducting rotating Gantry Download PDFInfo
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- CN111686377A CN111686377A CN202010547542.6A CN202010547542A CN111686377A CN 111686377 A CN111686377 A CN 111686377A CN 202010547542 A CN202010547542 A CN 202010547542A CN 111686377 A CN111686377 A CN 111686377A
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- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1048—Monitoring, verifying, controlling systems and methods
- A61N5/1064—Monitoring, verifying, controlling systems and methods for adjusting radiation treatment in response to monitoring
- A61N5/1069—Target adjustment, e.g. moving the patient support
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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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- 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
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- H—ELECTRICITY
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- 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
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N2005/002—Cooling systems
- A61N2005/005—Cooling systems for cooling the radiator
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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
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
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- 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
- H05H2007/043—Magnet systems, e.g. undulators, wigglers; Energisation thereof for beam focusing
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- 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
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- H05H2277/10—Medical devices
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Abstract
The invention relates to a carbon ion beam superconducting rotating Gantry, which comprises: rotating the bracket; the vacuum channel is arranged on the rotating support and used for providing a vacuum environment for the transmission of ion beam current; the combined magnet is arranged at the periphery of the vacuum channel and used for direction guidance and envelope control of the carbon ion beam; and the scanning magnet is arranged in front of the last magnet inlet of the combined magnet and is used for adjusting the position of the carbon ion beam spot in the plane of the radiation field at the tail end of the rotating Gantry. Compared with the traditional normal-temperature rotating Gantry, the miniaturized and lightweight carbon ion beam superconducting rotating Gantry provided by the invention adopts the international forefront warm iron superconducting technology at present, and the volume and weight of all magnets are greatly reduced except for scanning magnets.
Description
Technical Field
The invention relates to a miniaturized and light-weighted carbon ion beam superconducting rotating Gantry (frame) applied to a cancer treatment accelerator, and relates to the field of nuclear technology application.
Background
Ion beam rotation Gantry is a cancer treatment accelerator terminal delivery system for tumor treatment with pencil-shaped ion beams that can be rotated from 0-180 or 0-360, etc. centers during patient treatment to effectively perform multi-azimuthal treatment of tumors while mitigating radiation damage to normal tissues and organs caused by the ion beams. Since proton beam therapy of tumors proposed by r.r.wilson in 1946, developed countries have built dedicated ion accelerator devices in succession, aimed at providing variable energy, finely adjustable ion beams to achieve conformal treatment of lesions. The conformal treatment is a process of ion beam high-precision operation for matching the focus shape through the manipulation of transverse position and longitudinal energy distribution. In radiotherapy, a rotating Gantry capable of supplying beams at any angle is the most ideal ion beam therapy terminal distribution system for conformal therapy.
The international designs for rotating Gantry are largely classified by structure into two categories, centrifugal and centripetal. In the centrifugal Gantry, the ion beam rotates centrifugally around a fixed shaft, and the hospital bed rotates centrifugally synchronously with the rotation of the Gantry. In the centripetal Gantry, the ion beam also rotates centripetally around a fixed shaft, and the ion beam is firstly centrifuged and then centripetally and vertically directed to the axis. Compared with a centrifugal rotating Gantry, the centripetal rotating Gantry has higher control accuracy and simpler treatment operation, and is generally applied to a special proton cancer treatment device at present. Compared with the currently popular proton beam for treating cancer12C6+The typical heavy ion beam is the first choice for radiotherapy of tumors because of its higher physical Bragg energy loss effect and special relative biological effect. But due to12C6+The highest magnetic stiffness is 3 times that of protons (protons about 2.2Tm,12C6+ion is about 6.6Tm), so that the carbon ion rotating Gantry is not only bulky and weighs more than hundreds of tons (the weight of the rotating Gantry of conventional proton is generally not more than 100 tons), and the bulky and heavy rotating Gantry brings a series of serious problems such as material selection, structural design and fine control, and brings a serious challenge to the requirement of realizing millimeter-scale adjustment precision of the carbon ion beam rotating Gantry.
In recent years, with the rapid development of magnetic superconducting technology, the design and construction of miniaturized and lightweight heavy ion rotating Gantry are just about once. In foreign countries, although the first generation of superconducting carbon ion beam rotating Gantry with small size and light weight has been successfully developed and built in japan, compared with the conventional carbon ion rotating Gantry, the volume and the weight of the superconducting carbon ion beam rotating Gantry are both greatly reduced, but the whole Gantry still has huge volume, the whole length exceeds 20m, the rotating radius also reaches 5m, and the weight is nearly 200 tons. Because the Gantry is large in size and heavy in weight, the practical debugging convenience and operation efficiency are not ideal, and therefore, the development of the second generation of more compact superconducting carbon ion beam rotating Gantry is planned to be carried out in japan. Except for Japan, the research on the miniaturized and light superconducting carbon ion beam rotating Gantry in other countries at home and abroad is still not started, and the problems of material selection, structural design, fine control and the like in practical application of the conventional carbon ion beam rotating Gantry due to the problems of overlarge volume, overlarge weight and the like are solved.
Disclosure of Invention
In view of the above problems, an object of the present invention is to provide a superconducting rotating Gantry for a carbon ion beam that can simplify the layout of a terminal delivery system of a carbon ion treatment apparatus, and can be made compact and lightweight.
In order to achieve the purpose, the invention adopts the technical scheme that: a carbon ion beam superconducting rotating Gantry comprising:
rotating the bracket;
the vacuum channel is arranged on the rotating support and used for providing a vacuum environment for the transmission of ion beam current;
the combined magnet is arranged at the periphery of the vacuum channel and used for direction guidance and envelope control of the carbon ion beam;
and the scanning magnet is arranged in front of the last magnet inlet of the combined magnet and is used for adjusting the position of the carbon ion beam spot in the plane of the radiation field at the tail end of the rotating Gantry.
Preferably, the combined magnet includes first to third guiding dipole magnets and focusing quadrupole magnets, the first to third guiding dipole magnets are sequentially arranged at intervals according to a set sequence, and the focusing quadrupole superconducting magnet is embedded at an inlet and an outlet of each of the guiding dipole magnets.
Preferably, the deflection angle of the first and second guiding dipole magnets is 60 °, and the deflection angle of the third guiding dipole magnet is 90 °, wherein the deflection angle is a fan angle corresponding to an arc length of the beam passing through the dipole magnets.
Preferably, the scanning magnet is disposed between the second and third guide dipole magnets.
Preferably, each of the guiding dipole magnet and the focusing quadrupole magnet is of a warm iron superconducting design.
Preferably, the ion beam current adopts a parallel beam distribution mode, and the transmission paths of the ion beam reaching the irradiation field plane after rotating the Gantry are completely the same.
Preferably, the scanning mode of the scanning magnet adopts a pen-shaped spot scanning mode or a grid therapy mode.
Preferably, the device further comprises a low-temperature system arranged on the rotating bracket and used for taking away heat generated by the magnet coil during Gantry operation and maintaining the low-temperature environment of the guide dipolar magnet and the focusing quadrupole magnet.
Preferably, the rotary bracket is capable of 180-or 360-degree rotation.
Due to the adoption of the technical scheme, the invention has the following advantages:
1. compared with the traditional normal-temperature rotating Gantry, the miniaturized and light carbon ion beam superconducting rotating Gantry provided by the invention adopts the international foremost warm iron superconducting technology, the volume and the weight of all magnets are greatly reduced except for scanning magnets, the lightest carbon ion Gantry is designed internationally at present, and the integral weight is not more than 100 tons;
2. according to the invention, all focusing quadrupole magnets are embedded into the guiding dipolar magnets, so that the volume of the whole Gantry is greatly reduced, the whole length is not more than 15.0m, the rotating radius is less than 3.5m, and the invention effectively avoids the embarrassment situation that the traditional carbon ion rotating Gantry cannot be put into practical application due to the defects of large volume, heavy weight, high control and adjustment difficulty and the like, and lays a foundation for the development of more compact and advanced carbon ion treatment device treatment terminals.
Drawings
Various other advantages and benefits will become apparent to those of ordinary skill in the art upon reading the following detailed description of the preferred embodiments. The drawings are only for purposes of illustrating the preferred embodiments and are not to be construed as limiting the invention. Like reference numerals refer to like parts throughout the drawings. In the drawings:
FIG. 1 is a schematic diagram of a superconducting rotating Gantry structure for a carbon ion beam according to the present invention;
FIG. 2 is a diagram showing the beam effect in example 1 of the present invention;
the reference numbers in the figures are: 1. vacuum channel, 2, scanning power supply, 3, first stage 60 ° directed two-pole magnet, 4, second stage 60 ° directed two-pole magnet, 5, third stage 90 ° directed two-pole magnet, 6, focusing quadrupole magnet.
Detailed Description
Exemplary embodiments of the present invention will be described in more detail below with reference to the accompanying drawings. While exemplary embodiments of the invention are shown in the drawings, it should be understood that the invention can be embodied in various forms and should not be limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art.
It is to be understood that the terminology used herein is for the purpose of describing particular example embodiments only, and is not intended to be limiting. As used herein, the singular forms "a", "an" and "the" may be intended to include the plural forms as well, unless the context clearly indicates otherwise. The terms "comprises," "comprising," and "having" are inclusive and therefore specify the presence of stated features, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, steps, operations, elements, components, and/or groups thereof. The method steps, processes, and operations described herein are not to be construed as necessarily requiring their performance in the particular order described or illustrated, unless specifically identified as an order of performance. It should also be understood that additional or alternative steps may be used.
Although the terms first, second, third, etc. may be used herein to describe various elements, components, regions, layers and/or sections, these elements, components, regions, layers and/or sections should not be limited by these terms. These terms may be only used to distinguish one element, component, region, layer or section from another region, layer or section. Terms such as "first," "second," and other numerical terms when used herein do not imply a sequence or order unless clearly indicated by the context. Thus, a first element, component, region, layer or section discussed below could be termed a second element, component, region, layer or section without departing from the teachings of the example embodiments.
For convenience of description, spatially relative terms, such as "inboard", "outboard", "below", "upper" and the like, may be used herein to describe one element or feature's relationship to another element or feature as illustrated in the figures. Such spatially relative terms are intended to encompass different orientations of the device in use or operation in addition to the orientation depicted in the figures.
As shown in fig. 1, the miniaturized and lightweight carbon ion beam superconducting rotating Gantry applied to a cancer treatment accelerator provided by the present invention comprises:
the rotary bracket is used for positioning and mounting other devices; preferably, the rotating bracket is a bracket capable of rotating at 180 ° or 360 °, the rotating bracket is a skeleton of the superconducting rotating Gantry of the carbon ion beam, and supports components of all other systems thereon, and the structural design of the rotating bracket needs to meet the deformation and environmental temperature difference requirements, and the specific structure is not limited and can be designed according to actual needs.
And the vacuum channel 1 is transversely arranged on the rotating bracket and is used for providing a vacuum environment for the transmission of ion beam current.
The combined warm iron superconducting magnet is arranged on the periphery of the vacuum channel 1 and is used for being responsible for direction guidance and envelope control of carbon ion beams, wherein the envelope control mainly refers to restraint of the ion beams in a transverse motion state.
And the scanning magnet 2 is arranged in front of the last magnet inlet of the combined warm iron superconducting magnet and is used for adjusting the position of the carbon ion beam spot in the plane of the radiation field at the tail end of the rotary Gantry.
In some embodiments of the present invention, the combination-type warm iron superconducting magnet includes first 60 ° guide two-pole magnet 3, second 60 ° guide two-pole magnet 4, and third 90 ° guide two-pole magnet 5. The two-pole magnets are used for guiding the direction of the carbon ion beam, the carbon ion beam is guided to the two-pole magnet 3 through the first table 60 ° and then moves off-axis, and is guided to the opposite two-pole magnets of the two-pole magnet 4 through the second table 60 ° and the second table 90 ° and then moves concentrically with the vertical rotation axis, wherein 60 ° and 90 ° refer to the deflection angles of the two-pole magnets, and the opposite 90 ° refer to the two-pole magnets deflected in opposite directions by 90 °, and both 60 ° and 90 ° refer to the deflection angles, and the deflection angles refer to fan angles corresponding to the arc lengths of the beam passing through the two-pole magnets.
In some embodiments of the present invention, a focusing quadrupole magnet 6 is embedded at the inlet and the outlet of each guiding dipole magnet, and is mainly responsible for the constraint of the transverse motion state of the carbon ion beam, so that all distributed beam current makes paraxial motion along a reference track set by the guiding dipole magnet, and a required circular beam spot is formed at the axis.
In some embodiments of the present invention, the scanning magnet 2 is two normal temperature scanning magnets, the two scanning magnets 2 are used for forming a required irradiation area and shape in a downstream irradiation field, the two scanning magnets 2 are perpendicular to each other, the scanning magnet 2 is disposed between the second 60 ° guiding diode magnet 4 and the third 90 ° guiding diode magnet 5, and after the particle beam is transversely scanned by the two scanning magnets 2, the irradiation area at the end of the system is formed to be about 20cm × 20cm (the irradiation area of 20cm × 20cm is that most of the irradiation fields of tumors are within the irradiation area range, and the irradiation area of each tumor is too large, so that the tumors with individual irradiation faces can be irradiated one by one). The ion beam scanned by the scanning magnet 2, after passing through the third stage 90 ° directed diode magnet 5, exhibits a parallel beam state, which is an optimum ion beam transport state with the rotated Gantry end, as a change in the intensity of the scanning ferromagnetic field.
In some embodiments of the present invention, the superconducting rotating Gantry further comprises a cryogenic system disposed on the rotating support for removing heat generated by the coils during operation of the Gantry to maintain a cryogenic environment with the steering dipole magnet and the focusing quadrupole magnet. To date, superconducting magnet technology has been developed to enable magnets to produce magnetic fields at low temperatures far above conventional ambient temperature magnets. Preferably, the cryogenic system is a cooling system for suppressing heat generation of the magnet coil, and air cooling or water cooling is generally used for normal temperature cooling, and liquid nitrogen is generally used for cryogenic cooling.
In some embodiments of the present invention, the total length of the Gantry system is no more than 15.0m, wherein the total length of the rotating portion is no more than 13.0m, the horizontal length of the rotating portion (which is the horizontal linear distance of the rotating portion that the Gantry needs to rotate about a horizontal axis by 180 ° or 360 ° during use) is no more than 9.0m, and the vertical height (which is the vertical distance from the horizontal rotation axis to the farthest end of the rotating portion) is no more than 3.5m, so the Gantry system of the present invention has small scale, light weight, and flexible operation.
In some embodiments of the invention, all the guiding dipolar magnets adopt the international foremost protected-cobalt-Theta Dipole (CCTD) warm iron superconducting technology, the superconducting dipolar magnets adopting the technology only comprise a vacuum pipeline and a winding coil, and do not contain iron cores, the magnetic field intensity of the superconducting dipolar magnets can reach 5.0T, and the weight of the dipolar magnets is greatly reduced while the magnetic field of the dipolar magnets is greatly improved.
In some embodiments of the present invention, the focusing quadrupole magnet 6 also adopts a Canted-Cosine-Theta Quad (CCTQ) warm iron superconducting technology, and the focusing quadrupole magnet 6 of this type is also only composed of a vacuum pipe and a wound coil, and does not include an iron core, so that the weight of the quadrupole magnet is greatly reduced while the magnetic field of the quadrupole magnet is greatly increased. Furthermore, the guiding dipolar magnet and the focusing quadrupole magnet can adopt a novel design mode of combining two into one, namely the quadrupole magnet is positioned inside the dipolar magnet, namely a mode of increasing the quadrupole coil at the local position of the dipolar coil is adopted, and a superimposed effect of the dipolar field and the quadrupole field at the local position is formed. The combined magnet shown in fig. 1 has both quadrupole field components and dipole field components, which are superimposed, so that the magnet combination has the functions of guiding the ion beam direction and restraining the beam transverse state.
In some embodiments of the invention, the transverse states of the inlet ion beam and the outlet ion beam are designed by circular beams, the transverse sizes of the inlet beam and the outlet beam are completely equal, the outlet beam state is not changed along with the rotation of the Gantry, and the design mode is convenient for the running and debugging of the Gantry.
In some embodiments of the present invention, the physical focusing structure of the system employs advanced ion beam distribution mode design, such as complete de-dispersion, unit matrix, and end-beam parallel, i.e., employing anti-symmetric structural features. The complete dispersion elimination and the unit matrix transmission enable the beam spot size of the ion beam to be not influenced by momentum dispersion and Gantry rotation after the ion beam passes through the rotating Gantry.
When the miniaturized and light-weighted carbon ion beam superconducting rotary Gantry is used, a carbon ion beam led out by a front-stage accelerator system enters the vacuum pipeline 1 of the rotary Gantry, passes through two 60-degree guide two-pole magnets and one 90-degree guide two-pole magnet on the Gantry, is guided to the axis of a rotating shaft to perform concentric movement, is synchronously focused to the axis position by using a focusing four-pole magnet, and forms a beam spot required by treatment, and the beam spot forms an irradiation field with the maximum area of 20cm × 20cm after being transversely scanned by the scanning magnet 2 between the 60-degree guide two-pole magnet and the 90-degree guide two-pole magnet.
Example 1:
as shown in fig. 2, the physical and optical design of the miniaturized and light-weighted superconducting rotating Gantry for carbon ion beam provided by the present embodiment has the following characteristics:
firstly, the whole system adopts a complete achromatic design mode, the complete achromatic design belongs to the physical design category of an accelerator, and the complete achromatic design is divided into a forward achromatic mode and a reverse achromatic mode, and structurally mainly embodies that the deflection directions of two or more guide dipolar magnets are the same (forward achromatic) or reverse (reverse achromatic), and the design of the Gantry adopts a reverse achromatic structure;
secondly, the inlet and the outlet of the system transversely form circular ion beam spots with the same size;
thirdly, the most advanced international parallel beam scanning mode is adopted, namely, the scanning is realized by adopting a point-to-parallel optical principle, and the scanning is specifically completed by a scanning magnet, a 90-degree guide diode magnet at the downstream of the Gantry and two focusing quadrupole magnets embedded in the scanning magnet.
The miniaturized and light-weight carbon ion beam superconducting rotary Gantry provided by the embodiment comprises a rotary bracket capable of rotating 180-degree or 360-degree and fixing other components, a vacuum channel positioned on the rotary bracket, a plurality of combined type warm iron superconducting magnets and normal temperature scanning magnets wound around the periphery of the vacuum channel according to technical requirements, and a low-temperature system for providing a low-temperature environment for the warm iron superconducting magnets.
In the above embodiment, the combined type warm iron superconducting magnet is guided to the two pole magnets 3, the magnetic field value is 2.0T-5.0T, and the deflection angles are 60 ° and 90 °, respectively.
In the above embodiments, the combined type warm iron superconducting magnet has 8 focusing quadrupole magnets, and the magnetic field value of the pole face is 0.5T-2.5T.
In the above embodiments, the maximum pole face magnetic field of 2 normal temperature scanning magnets is not more than 0.55T.
The above embodiments are only used for illustrating the present invention, and the structure, connection mode, manufacturing process, etc. of the components may be changed, and all equivalent changes and modifications performed on the basis of the technical solution of the present invention should not be excluded from the protection scope of the present invention.
Claims (9)
1. A superconducting rotating Gantry for carbon ion beams, comprising:
rotating the bracket;
the vacuum channel is arranged on the rotating support and used for providing a vacuum environment for the transmission of ion beam current;
the combined magnet is arranged at the periphery of the vacuum channel and used for direction guidance and envelope control of the carbon ion beam;
and the scanning magnet is arranged in front of the last magnet inlet of the combined magnet and is used for adjusting the position of the carbon ion beam spot in the plane of the radiation field at the tail end of the rotating Gantry.
2. The carbon ion beam superconducting rotary Gantry according to claim 1, wherein the combined magnet includes first to third guiding dipole magnets and focusing quadrupole magnets, the first to third guiding dipole magnets are sequentially arranged at intervals according to a predetermined sequence, and the focusing quadrupole superconducting magnet is embedded at an inlet and an outlet of each of the guiding dipole magnets.
3. The carbon ion beam superconducting rotating Gantry of claim 2, wherein the deflection angle of the first and second steering dipole magnets is 60 ° and the deflection angle of the third steering dipole magnet is 90 °, wherein the deflection angle is a fan angle corresponding to the arc length of the beam passing through the dipole magnets.
4. The carbon ion beam superconducting rotating Gantry of claim 2 wherein the scanning magnet is disposed between the second and third steering diode magnets.
5. The carbon ion beam superconducting rotary Gantry according to any one of claims 2 to 4, wherein each of the steering dipole magnets and the focusing quadrupole magnets is of a warm iron superconducting design.
6. The carbon ion beam superconducting rotating Gantry according to any one of claims 1 to 4, wherein the ion beam current adopts a parallel beam distribution mode, and the transmission paths of the ion beam reaching the irradiation field plane after the ion beam current passes through the rotating Gantry are completely the same.
7. The superconducting rotating Gantry of claim 4 wherein the scanning magnet is scanned in a pencil beam spot scanning or raster therapy mode.
8. The carbon ion beam superconducting rotary Gantry according to any one of claims 2 to 4, further comprising a low temperature system arranged on the rotary support and used for taking away heat generated by the magnet coil during Gantry operation and maintaining a low temperature environment of the two-pole guide magnet and the four-pole focusing magnet.
9. The carbon ion beam superconducting rotary Gantry of any of claims 1 to 4, wherein the rotary support is capable of 180 or 360 degree rotation.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010547542.6A CN111686377A (en) | 2020-06-16 | 2020-06-16 | Carbon ion beam superconducting rotating Gantry |
Applications Claiming Priority (1)
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Application publication date: 20200922 |