CN109224319B - Full superconducting proton treatment system - Google Patents
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- CN109224319B CN109224319B CN201810892018.5A CN201810892018A CN109224319B CN 109224319 B CN109224319 B CN 109224319B CN 201810892018 A CN201810892018 A CN 201810892018A CN 109224319 B CN109224319 B CN 109224319B
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- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1077—Beam delivery systems
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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
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Abstract
The invention discloses a full-superconducting proton treatment system, which comprises a superconducting cyclotron, a proton generator, a power supply and a power supply, wherein the superconducting cyclotron is used for generating a proton beam; a superconducting rotary treatment cabin is arranged beside the superconducting cyclotron; the superconducting rotary treatment pod includes a beam line of the rotary treatment pod. By adopting the technical scheme, the proton treatment system adopts a mode that the superconducting cyclotron is provided with the superconducting rotary treatment cabin, the system is compact in layout and small in occupied space, the weight of the equipment is greatly reduced, and the manufacturing cost is further reduced.
Description
Technical Field
The invention relates to the technical field of proton treatment, belongs to the technical field of biology (medical treatment), and particularly relates to a full-superconducting proton treatment system.
Background
At present, the incidence of cancer in China is higher and higher, and the cancer becomes one of the biggest killers harmful to the health of people in China, and common treatment modes comprise operations, gamma knife, proton/heavy ion treatment and the like.
The proton/heavy ion therapy mainly utilizes an accelerator to generate proton/heavy ion beams with certain energy, and transmits beam current to a target area through each electromagnetic element to bombard tumor cells, thereby achieving the effect of treatment. Because the proton has a sharp Bragg peak in the substance, namely the energy of the proton is lost to the canceration position to the maximum extent, the proton can kill the canceration cells and protect the normal tissues to the maximum extent, so that the proton therapy becomes one of the most advanced malignant tumor treatment means in the world at present and is also one of the treatment means popular in the world at present.
Proton treatment systems are usually composed of main subsystems such as an accelerator, an energy selection and beam transmission system, and a rotary or fixed treatment cabin. The weight of the normal temperature proton cyclotron is about 200 tons, the diameter is about 4.5 meters, and the volume of the synchrotron is larger. The weight of the superconducting cyclotron is only 50-90 tons, and the diameter is 2-3.2 meters. The normal temperature rotary therapeutic rack system is at least more than 100 tons (100 tons to 200 tons), and the superconductive rotary therapeutic cabin system is about 20 tons. Internationally, the conventional proton treatment systems have no full-superconducting proton treatment system in the modes of equipping a room temperature accelerator with a room temperature rotary treatment cabin (such as a room temperature C235 cyclotron of IBA and a room temperature Proteusplus rotary treatment cabin), equipping a superconducting accelerator with a room temperature rotary treatment cabin (such as an S2C2 superconducting synchrocyclotron of IBA and a Proteus one rotary treatment cabin, PSI/Varian superconducting cyclotron and a room temperature rotary treatment cabin), equipping a room temperature accelerator with a superconducting rotary treatment cabin (such as a room temperature heavy ion synchrotron of HIMAC-NIRS and a superconducting rotary treatment cabin of room temperature proton cyclotron and a probova SC360 superconducting rotary treatment cabin).
Taking the scheme of a PSI 250MeV superconducting cyclotron and a normal-temperature rotary treatment cabin as an example, because the accelerator adopts a superconducting coil to excite a main magnet, compared with the main magnet of the normal-temperature cyclotron, the air gap of a magnetic pole is larger, on one hand, a sufficient space is provided for installing a flow enhancement device, the flow enhancement of proton beam can be rapidly modulated, the proton enhancement treatment can be further realized, the treatment dosage of a patient can be more accurately controlled, on the other hand, the extraction efficiency of the proton beam is higher, and the beam loss is small; and the superconducting coil is used, so that the electric power (including the refrigerator power) of the main magnet is only 50kW, which is about 1/4 of the normal-temperature convolution main magnet, and the superconducting coil is energy-saving and environment-friendly. The matching of the accelerator and the rotating treatment cabin is also very important for the final performance, and in proton treatment, the advanced tumor layered fast scanning treatment technology needs the fast change of proton energy, and further needs the corresponding fast change of the magnetic field of the magnet for restraining the proton track on the rotating treatment cabin. In order to realize layered rapid scanning, the PSI adopts a normal-temperature magnet for a beam transmission line of a rotary treatment cabin to realize rapid change of a magnetic field, so that rapid proton energy change with only 100ms of switching time per 5mm of treatment depth can be realized, the PSI is a proton treatment system with the highest treatment speed in the world at present, the cost is the rotary treatment cabin weighing nearly two hundred tons, the scale of the whole proton treatment system is large, and the power consumption cannot be reduced by adopting the normal-temperature magnet treatment cabin.
At present, the primary technical difficulty of the superconducting rotating therapeutic cabin is how to adapt to the problem of rapid change of proton energy required by a tumor layered fast scanning therapeutic technology. Because the superconducting magnet can not achieve the rapid magnetic field change like a normal-temperature magnet at present, the scanning speed of the superconducting rotating treatment cabin is low (NIRS-HIMAC), or the momentum acceptance (momentarity) of the superconducting rotating treatment cabin is increased by adopting the (achromatic deflection section) design of an achromatic deflection element group, so that protons are within the range of 0-30 cm of the human body range, when the scanning depth is changed, only a certain superconducting magnet exciting current working point needs to be set, and each working point can cover the nearby proton range without adjusting the exciting current of the superconducting magnet; only after the range exceeds the coverage range of each working point, the exciting current of the superconducting magnet is adjusted to the next working point. The latter method is well conceived, but on one hand, the momentum receptivity under a fixed magnetic field is limited to optimization, and on the other hand, the time is still limited by the excitation rate of the superconducting magnet in the working point switching process, so that the scanning speed of the currently practical superconducting rotary treatment cabin still cannot exceed the PSI normal-temperature rotary treatment cabin design. The superconducting magnet must be optimized in terms of structures or materials for preventing eddy current, quench protection and the like, so as to improve the scanning speed of the superconducting therapy cabin.
Disclosure of Invention
In view of the above technical problems, the present invention provides a solution for a full superconducting proton treatment system, which is used to increase the scanning speed of a superconducting treatment cabin and reduce the size, weight and manufacturing cost of a proton treatment device, without affecting the proton treatment effect.
In order to achieve the purpose, the invention provides the following technical scheme: a fully superconducting proton therapy system comprising:
a superconducting cyclotron to generate a proton beam;
a superconducting rotary treatment cabin is arranged beside the superconducting cyclotron;
the superconducting rotary treatment pod includes a beam line of the rotary treatment pod.
By adopting the technical scheme, the proton treatment system adopts a mode that the superconducting cyclotron is provided with the superconducting rotary treatment cabin, the system is compact in layout and small in occupied space, the weight of equipment is greatly reduced, and the manufacturing cost is further reduced. Compared with a normal-temperature cyclotron, the superconducting cyclotron and the superconducting rotating beam linear magnet are energy-saving and environment-friendly, and the operating cost is obviously reduced.
The invention is further configured to: and a beam transport system and an energy selection system are sequentially arranged in the beam output direction generated by the superconducting cyclotron and between the superconducting cyclotron and the superconducting rotary treatment cabin.
By adopting the technical scheme, the beam transport system is used for transporting the beam, and the beam enters the energy selection system for energy selection and color difference elimination, so that the quality of the beam transported to the rotary treatment cabin is improved.
The invention is further configured to: the beam transport system comprises a first quadrupole lens group and an energy degrader which are sequentially arranged.
By adopting the technical scheme, the first quadrupole lens group is used for focusing the beam led out by the superconducting cyclotron, and the focused beam then enters the energy degrader for energy adjustment.
The invention is further configured to: the energy selection system comprises a first deflection magnet, a second quadrupole lens and a second deflection magnet which are arranged in sequence.
By adopting the technical scheme, the first deflection magnet is used for deflecting the beam current led out by the superconducting cyclotron, the second quadrupole lens is used for focusing the beam current passing through the first deflection magnet, and the second deflection magnet is used for deflecting the beam current passing through the second quadrupole lens, so that energy selection and chromatic aberration elimination of the beam current are realized.
The invention is further configured to: the beam transport system further comprises a third quadrupole lens, a third deflection magnet, a fourth quadrupole lens, a fourth deflection magnet and a fifth quadrupole lens which are sequentially arranged.
Through adopting above-mentioned technical scheme, the third quadrupole lens is used for to passing through beam behind the second deflection magnet is focused on, the third deflection magnet is used for deflecting beam behind the third quadrupole lens, the fourth quadrupole lens is used for passing through beam behind the third deflection magnet is focused on, the fourth deflection magnet is used for deflecting beam behind the fourth quadrupole lens, the fifth quadrupole lens is used for passing through beam behind the fourth deflection magnet is focused on, has realized the transmission of beam and has controlled the quality of beam in transmission process from this.
The invention is further configured to: a first diagnostic element is arranged between the second deflection magnet and the third quadrupole lens.
By adopting the above technical solution, a first diagnostic element is disposed between the second deflection magnet and the third quadrupole lens. In this way, the beam current passing through the second deflection magnet can be detected by the first diagnostic element.
The invention is further configured to: the superconducting rotary treatment cabin comprises a fifth deflection magnet, a sixth quadrupole lens and a sixth deflection magnet which are sequentially arranged, and the fifth deflection magnet, the sixth quadrupole lens and the sixth deflection magnet which are sequentially arranged form a beam line of the rotary treatment cabin.
Through adopting above-mentioned technical scheme, fifth deflection magnet is used for deflecting beam current after passing through the fifth quadrupole lens, the sixth quadrupole lens is used for focusing the beam current after passing through the fifth deflection magnet, the sixth deflection magnet is used for deflecting the beam current after passing through the sixth quadrupole lens.
The invention is further configured to: a second diagnostic element is disposed between the sixth quadrupole lens and the sixth deflection magnet.
With the above configuration, a second diagnostic element is disposed between the sixth quadrupole lens and the sixth deflection magnet. In this way, the beam current passing through the sixth quadrupole lens can be detected by the second diagnostic element.
The invention is further configured to: the fifth deflection magnet, the sixth quadrupole lens and the sixth deflection magnet 16 are all superconducting magnets.
By adopting the technical scheme, the fifth deflection magnet, the sixth quadrupole lens and the sixth deflection magnet are all superconducting magnets. The superconducting magnet has high field strength, compact structure and light weight. Further improving the efficiency and stability of the beam current led out.
In conclusion, the invention has the following beneficial effects:
the occupied space and the weight of the proton treatment equipment are greatly reduced, so that the requirements of the proton treatment equipment on plant space and bearing are obviously reduced, the construction cost and the equipment operation power consumption of the proton treatment device are obviously reduced, the problems of large equipment and high requirements on plant space and bearing of the conventional proton treatment system are solved, and the conventional X-ray treatment equipment with large loading capacity can be replaced one to one by the proton treatment system scheme provided by the invention.
Drawings
Fig. 1 is a schematic diagram of the structure of the fully superconducting proton therapy system of the present invention.
Reference numerals: 1. a superconducting cyclotron; 2. a first quadrupole lens group; 3. an energy reducing device; 4. a first deflection magnet; 5. a second quadrupole lens; 6. a second deflection magnet; 7. a first diagnostic element; 8. a third quadrupole lens; 9. a third deflection magnet; 10. a fourth quadrupole lens; 11. a fourth deflecting magnet; 12. a fifth quadrupole lens; 13. a fifth deflection magnet; 14. a sixth quadrupole lens; 15. a second diagnostic element; 16. a sixth deflecting magnet; 17. a treatment head.
Detailed Description
The present invention will be described in further detail with reference to the accompanying drawings.
As shown in figure 1, the full superconducting proton treatment system comprises a superconducting cyclotron 1, a superconducting cyclotron 1 and a control unit, wherein the superconducting cyclotron 1 is used for generating beams; when the superconducting cyclotron 1 is a superconducting proton cyclotron, the superconducting cyclotron 1 is used for generating proton beams; a superconducting rotary treatment cabin is arranged beside the superconducting cyclotron 1; the superconducting rotary therapeutic cabin comprises a beam line of the rotary therapeutic cabin and a superconducting magnet thereof. The proton treatment system provided by the invention adopts a mode that the superconducting cyclotron is provided with the superconducting rotary treatment cabin, and the like, and is compact in layout, small in occupied space, and greatly reduced in equipment weight. Compared with a normal-temperature cyclotron, the superconducting cyclotron and the superconducting rotating beam linear magnet are energy-saving and environment-friendly, and the operating cost is obviously reduced.
A beam transport system and an energy selection system are sequentially arranged in the beam output direction generated by the superconducting cyclotron 1 and between the superconducting cyclotron 1 and the superconducting rotary treatment cabin. The beam transport system is used for transmitting a beam, and enabling the beam to enter the energy selection system for energy selection and color difference elimination. When the superconducting cyclotron 1 is a superconducting proton cyclotron, the beam transport system is used for transporting the proton beam, and the proton beam enters the energy selection system for energy selection and chromatic aberration elimination.
The beam transport system comprises a first quadrupole lens group 2 and an energy degrader 3 which are sequentially arranged; the first quadrupole lens group 2 is used for focusing the beam current led out by the superconducting cyclotron 1, and the focused beam current enters the energy degrader 3 for energy adjustment; the first quadrupole lens group 2 is arranged in the direction of the beam led out by the superconducting cyclotron 1; the degrader 3 is arranged in the direction of the beam after passing through the first quadrupole lens group 2.
The energy selection system comprises a first deflection magnet 4, a second quadrupole lens 5 and a second deflection magnet 6 which are arranged in sequence; the first deflection magnet 4 is used for deflecting the beam current led out by the superconducting cyclotron 1, the second quadrupole lens 5 is used for focusing the beam current after passing through the first deflection magnet 4, the second deflection magnet 6 is used for deflecting the beam current after passing through the second quadrupole lens 5, the first deflection magnet 4 is arranged in the direction of the beam current after passing through the energy degrader 3, the second quadrupole lens 5 is arranged in the direction of the beam current after passing through the first deflection magnet 4, and the second deflection magnet 6 is arranged in the direction of the beam current after passing through the second quadrupole lens 5.
The beam transport system also comprises a third quadrupole lens 8, a third deflection magnet 9, a fourth quadrupole lens 10, a fourth deflection magnet 11 and a fifth quadrupole lens 12 which are sequentially arranged; the third quadrupole lens 8 is configured to focus the beam after passing through the second deflection magnet 6, the third deflection magnet 9 is configured to deflect the beam after passing through the third quadrupole lens 8, the fourth quadrupole lens 10 is configured to focus the beam after passing through the third deflection magnet 9, the fourth deflection magnet 11 is configured to deflect the beam after passing through the fourth quadrupole lens 10, the fifth quadrupole lens 12 is configured to focus the beam after passing through the fourth deflection magnet 11, the third quadrupole lens 8 is disposed in the direction of the beam after passing through the second deflection magnet 6, the third deflection magnet 9 is disposed in the direction of the beam after passing through the third quadrupole lens 8, the fourth quadrupole lens 10 is disposed in the direction of the beam after passing through the third deflection magnet 9, the fourth deflection magnet 11 is disposed in the direction of the beam after passing through the fourth quadrupole lens 10, and the fifth quadrupole lens 12 is disposed in the direction of the beam after passing through the fourth deflection magnet 11.
A first diagnostic element 7 is arranged between the second deflection magnet 6 and the third quadrupole lens 8. This allows the beam current passing through the second deflection magnet 6 to be detected by the first diagnostic element. The first diagnostic element is a beam current detection device.
The superconducting rotary treatment cabin is arranged in the treatment room and comprises a fifth deflection magnet 13, a sixth quadrupole lens 14 and a sixth deflection magnet 16 which are sequentially arranged, and the fifth deflection magnet 13, the sixth quadrupole lens 14 and the sixth deflection magnet 16 which are sequentially arranged form a beam line of the rotary treatment cabin; the fifth deflection magnet 13 is configured to deflect the beam after passing through the fifth quadrupole lens 12, the sixth quadrupole lens 14 is configured to focus the beam after passing through the fifth deflection magnet 13, the sixth deflection magnet 16 is configured to deflect the beam after passing through the sixth quadrupole lens 14, the fifth deflection magnet 13 is disposed in the direction of the beam after passing through the fifth quadrupole lens 12, the sixth quadrupole lens 14 is disposed in the direction of the beam after passing through the fifth deflection magnet 13, the sixth deflection magnet 16 is disposed in the direction of the beam after passing through the sixth quadrupole lens 14, and the treatment head 17 is disposed in the direction of the beam after passing through the sixth deflection magnet 16.
A second diagnostic element 15 is disposed between the sixth quadrupole lens 14 and the sixth deflection magnet 16. In this way, the beam current passing through the sixth quadrupole lens 14 can be detected by the second diagnostic element. And the second diagnosis element is a beam current detection device.
The fifth deflection magnet 13, the sixth quadrupole lens 14 and the sixth deflection magnet 16 are all superconducting magnets. The superconducting magnet has high field strength, compact structure and light weight.
The beam current led out from the superconducting proton accelerator 1 is then transmitted in a beam current transmission system, is firstly focused by a first quadrupole lens group 2, is subjected to energy adjustment by using an energy degrader 3, is then subjected to energy selection and chromatic aberration elimination by using a first deflection magnet 4, a second deflection magnet 6 and a second quadrupole lens 5, is transmitted to a rotary treatment room by a third quadrupole lens 8, a fourth quadrupole lens 10, a fifth quadrupole lens 12, a third deflection magnet 9 and a fourth deflection magnet 11, and is finally transmitted to a treatment head by combining a beam current line of a rotary treatment cabin formed by a fifth deflection magnet 13, a sixth deflection magnet 16 and a sixth quadrupole lens 14. The full superconducting system reduces the whole size and weight of the equipment and improves the efficiency and stability of the beam led out by the accelerator.
Compared with the normal-temperature cyclotron, the weight of the superconducting cyclotron is about 1/2 of the normal-temperature cyclotron, the diameter of the superconducting cyclotron is about 2/3 or even 1/2 of the diameter of the normal-temperature cyclotron, the volume and the weight of the superconducting cyclotron are greatly reduced, in addition, the superconducting cyclotron adopts superconducting coils, air gaps between magnetic poles are large, installation and maintenance of devices such as a high-frequency cavity, beam diagnosis and an extraction system are facilitated, the reliability is high, and the extraction efficiency is higher than that of the normal-temperature cyclotron.
Compared with the normal temperature rotary treatment cabin, the weight of the superconducting rotary treatment cabin can be 1/10 the weight of the normal temperature rotary treatment cabin, the diameter and the length are reduced compared with the normal temperature rotary treatment cabin, and the superconducting rotary treatment cabin is extremely favorable for hospitals. And different from the existing superconducting rotary treatment cabin design of the normal-temperature quadrupole magnet and the superconducting deflection magnet, the superconducting rotary treatment cabin is designed in a full-superconducting rotary treatment cabin, namely, the quadrupole magnet for focusing and the dipolar magnet for deflection are designed by the superconducting magnet.
In addition, the tumor layered scanning requires rapid energy change, and further requires corresponding rapid change of the magnetic field of the magnet on the rotating treatment cabin, when the magnetic field of the superconducting magnet changes rapidly, an induced voltage is applied to the low-temperature system end of the magnet, and the induced voltage is loaded on the low-temperature end metal structure, such as a cold shield and a liquid helium tank, so as to generate eddy current, and this part of energy can cause structural damage (cold shield distortion, and further generate conduction heat crossing the cold shield temperature and the liquid helium temperature) of the low-temperature system and low-temperature end resistive heat load (eddy current heat generation), so as to cause low-temperature failure, and further cause coil quench. To solve this problem, a structure for blocking the eddy current may be used, or a material having a higher resistivity may be used to reduce the eddy current. Under the condition that L is the inductance value of the superconducting coil, i is the current passing through the superconducting coil, and t is the moment of the current i passing through the superconducting coil, the superconducting magnet is usually connected with two ends of the coil in series in a quench protection mode after a plurality of cold diode groups connected in parallel back to back are connected in series in the field of MRI superconducting magnets, the change speed of the superconducting magnet magnetic field is severely limited, and the tumor layered scanning speed is further influenced. To solve this problem, quench protection can be performed in a manner such as high copper-to-superconducting coils without adding additional cold diodes. Therefore, the superconducting magnet quench protection circuit on the rotary bracket is reasonably selected, so that the voltage at two ends of the coil generated by the rapidly-changing magnetic field can be contained, and the highest temperature of the coil is not too high. The scanning speed of the superconducting therapy cabin is improved.
The present embodiment is only for explaining the present invention, and it is not limited to the present invention, and those skilled in the art can make modifications of the present embodiment without inventive contribution as needed after reading the present specification, but all of them are protected by patent law within the scope of the claims of the present invention.
Claims (6)
1. A fully superconducting proton therapy system, comprising: the device comprises a superconducting cyclotron (1), a control unit and a control unit, wherein the superconducting cyclotron (1) is used for generating proton beams; a superconducting rotary treatment cabin capable of adapting to the rapid change of a superconducting magnet magnetic field on the rotary treatment cabin is arranged beside the superconducting cyclotron (1);
the superconducting rotary treatment cabin comprises a beam streamline of the rotary treatment cabin; the superconducting rotary treatment cabin comprises a fifth deflection magnet (13), a sixth quadrupole lens (14) and a sixth deflection magnet (16) which are sequentially arranged, and the fifth deflection magnet (13), the sixth quadrupole lens (14) and the sixth deflection magnet (16) which are sequentially arranged form a beam line of the rotary treatment cabin; the fifth deflection magnet (13), the sixth quadrupole lens (14) and the sixth deflection magnet (16) are all superconducting magnets;
the superconducting rotary treatment cabin adopts a structure for blocking eddy current or adopts a component made of a material with higher resistivity to reduce the eddy current, so as to solve the problem that the eddy current on a low-temperature system generates heat and further causes quench due to the rapid change of current; the superconducting rotary treatment cabin also adopts a high-copper-to-superconducting coil to solve the problem that the voltage between the superconducting coils can be increased due to the rapid change of current, so that a cold diode cannot be adopted for quench protection.
2. The fully superconducting proton therapy system according to claim 1, wherein: a beam transport system and an energy selection system are sequentially arranged in the beam output direction generated by the superconducting cyclotron (1) and between the superconducting cyclotron (1) and the superconducting rotary therapy cabin.
3. The fully superconducting proton therapy system according to claim 2, wherein: the beam transport system comprises a first quadrupole lens group (2) and an energy degrader (3) which are sequentially arranged.
4. The fully superconducting proton therapy system according to claim 2, wherein: the energy selection system comprises a first deflection magnet (4), a second quadrupole lens (5) and a second deflection magnet (6) which are arranged in sequence; the beam transport system further comprises a third quadrupole lens (8), a third deflection magnet (9), a fourth quadrupole lens (10), a fourth deflection magnet (11) and a fifth quadrupole lens (12) which are sequentially arranged.
5. The fully superconducting proton therapy system according to claim 4, wherein: a first diagnostic element is arranged between the second deflection magnet (6) and the third quadrupole lens (8).
6. The fully superconducting proton therapy system according to claim 1, wherein: a second diagnostic element (15) is arranged between the sixth quadrupole lens (14) and the sixth deflection magnet (16).
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| CN111790063A (en) * | 2020-07-07 | 2020-10-20 | 北京大学 | Superconducting rotating frame for laser accelerating proton cancer treatment device |
| CN111773559A (en) * | 2020-07-07 | 2020-10-16 | 北京大学 | Superconducting rotating frame for proton cancer treatment device |
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| CN115413105B (en) * | 2022-09-19 | 2023-05-12 | 中国科学院近代物理研究所 | 360 capable of realizing multi-terminal distribution o Superconductive rotary harness |
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| CN105658278A (en) * | 2013-10-17 | 2016-06-08 | 皇家飞利浦有限公司 | Medical apparatus with a radiation therapy device and a radiation detection system |
| CN106178287A (en) * | 2016-07-06 | 2016-12-07 | 合肥中科离子医学技术装备有限公司 | A kind of high temperature/low-temperature superconducting mixing rotary frame being applicable to proton precessional magnetometer |
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