CN106879158A - Medical proton linear accelerator - Google Patents
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- CN106879158A CN106879158A CN201710157738.2A CN201710157738A CN106879158A CN 106879158 A CN106879158 A CN 106879158A CN 201710157738 A CN201710157738 A CN 201710157738A CN 106879158 A CN106879158 A CN 106879158A
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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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- H—ELECTRICITY
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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
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
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- A—HUMAN NECESSITIES
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- 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 application discloses medical proton linear accelerator includes: the ECR ion source, the RFQ accelerator, the SDTL and the traveling wave proton accelerator are connected in sequence. The medical proton linear accelerator has the advantages that the intermediate energy acceleration section adopts a separated drift tube linear accelerator, namely SDTL, and the high energy acceleration section adopts a traveling wave proton accelerator, so that the medical proton linear accelerator has a more compact structure and smaller occupied space, the energy of an emergent proton beam is continuously adjustable within the range of 70-250MeV, and the requirement that the beam energy needs to be adjusted due to different tumor positions in a patient body during tumor treatment is met. In addition, the SDTL and the traveling wave proton accelerator are both of a structure formed by sequentially connecting multiple sections, can be built stage by stage and can meet the requirements of different hospitals on proton energy, and the energy can be upgraded according to the treatment requirements in the later stage.
Description
Technical field
The application is related to treatment of cancer instrument field, more particularly to a kind of medical proton linac.
Background technology
The world today, cancer has turned into the chief complaint of chief threat human life.Whole world cancer morbidity in recent years
Improve year by year, cancer has also turned into the biggest threat of influence Chinese's life and health.At present, the traditional therapy of cancer
There are drug therapy and radiotheraping method.Wherein conventional radiotheraphy method mainly has X-ray and gamma-rays, because the energy of ray is discharged with road
Footpath is successively decreased, and both radiotherapy modes are while cancer cell is killed, and the normal structure in path can also sustain damage, therefore postoperative
Badly influence the quality of life of patient.
In recent years, domestic proton and the heavy ion technology of rising had great in treating cancer compared to conventional radiotheraphy method
Advantage, when proton accelerates to about 61% light velocity via linear accelerator, forms ion irradiation and is brought out injecting human body, reaches
Before tumor focus, ray energy release is few, but after reaching focus, the ray meeting big energy of abrupt release forms Bragg bent
Wire energy discharges track, and whole therapeutic process cans be compared to " the stereotaxis explosion " for being directed to tumour, tumor focus can be entered
The strong irradiation of row, and greatly reduce the irradiation to normal surrounding tissue, realize that curative effect is maximized.Because of tumour in patient body
The difference of position, therefore the general continuously adjustabe in 70-250MeV of proton beam energy requirement required during treatment, and be
Reach larger close rate and reduce irradiation time, proton beam dutycycle needs higher.
Proton precessional magnetometer mainly includes bevatron, proton-synchrotron and proton linac.Proton
Cyclotron can provide stabilization, lasting proton beam, and line cut-out and opening speed quickly, but need to regularly replace built-in ion
Source, and beam energy is non-adjustable, needs to connect an energy tune again in order to realize proton beam energies continuously adjustabe, after cyclotron
Device processed, the beam energy reduction of the proton beam that will be accelerated through cyclotron using scattering, the proton beam energies of this intercept type
Regulative mode can produce substantial amounts of radiation, easily cause the activation of device, increase the radiation shield cost of hospital, and scattering is made
Into beam energy utilization rate it is low, the quality of beam after scattering is poor, and the efficiency that 70MeV passes through is only 2%.Proton-synchrotron
Adjustable proton beam in the range of 70-250MeV can be provided, but synchrotron is made up of injector and ring-like accelerator, takes up an area face
Product is big, and whole system framework is complicated, and the injection of synchrotron, rise can and standardization circulation need to take for a long time,
The effective time drawn corresponding to platform is very short, and the transducing time is slow, causes the futile treatment time long；It is tight after even improving
Gather type synchrotron, can not still overcome can only provide Pulsed Proton beam, average dose rate low shortcoming, it is impossible to adapt to it is quick,
The need for continuous treatment.Proton linac proton is drawn and injection is easy, it is possible to provide stabilization, lasting proton beam, proton
Beam almost free of losses in acceleration and transmitting procedure, have the advantages that ion gun can run steadily in the long term, close rate it is high, application number
To solve the problems, such as to install proton linac in limitation area of space in 201410323833.1 patent, but due to adopting
Coupler linear accelerator (CCL) is standing wave accelerator, and the proton beam energies of outgoing are fixed value, still fails to solve straight line
Machine-made energy cannot continuously adjustabe problem.
The content of the invention
The application provides a kind of medical proton linac, and the proton beam that the medical proton linac is provided is steady
Fixed, lasting and beam energy continuously adjustabe.
A kind of medical proton linac that the application is provided, including：Ion gun, low energy accelerating sections draw from ion gun
Go out proton energy is accelerated to fixed energies value for the injector of proton, middle energy accelerating sections draft tube linac, RF power
Source and the traveling wave proton precessional magnetometer of high energy acceleration section, the RF power sources provide high frequency power for the traveling wave proton precessional magnetometer,
So that forming electromagnetic field of high frequency in the traveling wave proton precessional magnetometer cavity；The traveling wave proton precessional magnetometer is connected to drift tube straight line
After accelerator, accelerated by the effect of high-frequency electric field when proton beam enters the traveling wave proton precessional magnetometer cavity, pass through
Change the size of the high frequency power of input, the intensity of high-frequency electric field can be changed so that by the traveling wave proton precessional magnetometer
The proton beam energies value of outgoing after acceleration is continuously adjustable, the proton beam of different-energy value is obtained, the need for meeting treatment of cancer.
In certain embodiments, the ion gun is Electron cyclotron resonance ion source.
In certain embodiments, the traveling wave Proton emission chamber that the traveling wave proton precessional magnetometer is sequentially connected including multistage, RF
Power source has multiple, and each RF power source individually provides high frequency power, the high frequency work(of each RF power source to every section of accelerator module
Rate Independent adjustable.
In certain embodiments, the traveling wave proton precessional magnetometer also the coupling disc including periodic arrangement, the cycle
Property arrangement coupling disc be used for reduce electromagnetic field phase velocity and guarantee adjacent cells magnetic coupling.
In certain embodiments, the coupling disc is arranged at the traveling wave Proton emission chamber inside cavities, couples disc
In periodic arrangement.
In certain embodiments, the injector is radio frequency four polar field accelerator.
In certain embodiments, the medical proton linac also includes line transfers section, is arranged at described
Between ion gun and radio frequency four polar field accelerator, the proton beam for receiving the ion gun output is adjusted to match and penetrated
The suction parameter of frequency four polar field accelerator.
In certain embodiments, the draft tube linac is divergence type draft tube linac.
In certain embodiments, the medical proton linac also includes energy span line in line, is arranged at described
Between radio frequency four polar field accelerator and divergence type draft tube linac, for receiving the radio frequency four polar field accelerator output
Proton beam, adjusted the suction parameter for matching divergence type draft tube linac.
In certain embodiments, it is characterised in that the traveling wave proton precessional magnetometer is circular cylindrical cavity or square cavity.
The beneficial effect of the application is：
The medical proton linac of the application uses divergence type draft tube linac in middle energy accelerating sections, in height
Energy accelerating sections replaces CCL of the prior art using traveling wave proton precessional magnetometer so that not only structure is compacter for accelerator, occupancy
Space is smaller, and outgoing proton beam energies in the range of 70-250MeV continuously adjustabe, because of patient when can meet oncotherapy
The need for knub position difference beam energy need to be adjusted in body.
Further, since divergence type draft tube linac and traveling wave proton precessional magnetometer are the knot that multistage is sequentially connected
Structure, can sectional construction by stages, the medical proton linac of the application is suitable for demand of the Different hospital to proton energy,
Later stage carries out energy upgrading also dependent on Treatment need.
Brief description of the drawings
Fig. 1 is a kind of medical proton linac structured flowchart of the application；
A kind of SDTL structure charts that Fig. 2 is provided for the application；
One section of accelerating cavity structure chart of the traveling wave proton precessional magnetometer that Fig. 3 is provided for the application.
Fig. 4 is the schematic diagram of traveling wave proton precessional magnetometer accelerating proton.
Specific embodiment
The application is described in further detail below by specific embodiment combination accompanying drawing.
Fig. 1 is refer to, is a kind of medical proton linac that the application is provided, the medical proton linac bag
Include：Ion gun 1, injector 2, draft tube linac 3 and the traveling wave proton precessional magnetometer 4 being sequentially connected.
Ion gun 1 is preferably electron cyclotron resonace (ECR) ion gun, ecr ion that continuous line is larger, proton ratio is higher
Source produces the proton beam of continuous-stable and its energy is accelerated into 30keV, and proton beam dutycycle is higher.
Injector 2 is preferably radio frequency four polar field (RFQ) accelerator, and rfq accelerator is used as a kind of high current low energy ion straight line
Accelerator, it is dexterously by effects such as the matchings longitudinally, laterally and acceleration and focusing of line all with an accelerating cavity
Single rf electric field is achieved, and is widely used as the low energy high current injector of proton precessional magnetometer, is suitable to accelerate low energy region proton.
Specifically, after the proton beam of energy 30keV is drawn from ion gun 1, by rfq accelerator, beam energy is accelerated to 3~
5MeV。
In certain embodiments, line transfers section (LEBT) are additionally provided between ion gun 1 and rfq accelerator
12, the proton beam for receiving the output of ion gun 1 is adjusted the suction parameter for matching rfq accelerator.
The energy accelerating sections in of draft tube linac (DLT) 3, is suitable to accelerate several megavolts to tens megavolts of proton.
Because high-frequency work frequency is higher, accelerating cavity radial dimension is smaller, if magnet focusing device is installed in DLT3 inside, can cause structure
More complicated, size is difficult to reduce.Therefore, the draft tube linac 3 of the application uses divergence type drift tube linear accelerating
Device (SDTL), with reference to Fig. 2, SDTL includes multiple short cavities, and drift tube 31 is placed in chamber, and magnet focusing is free of in drift tube 31
Device 33 so that the external diameter of drift tube 3 is smaller, magnet focusing device 33 is arranged between adjacent chambers, and vacuum is passed through between adjacent chambers
Beam current tube 32 is connected SDTL due to multiple short cavities and magnet focusing device 33 thus can be so that proton beam is laterally obtained
Focus on.The center of drift tube 31 is beam channel 311, and proton beam is along the axis positive movement of beam channel 311, adjacent drift pipe 31
Between be acceleration gap, it is high when proton movement is between two drift tubes full of high frequency between drift tube and chamber, in acceleration gap
Frequency longitudinal electric field makes Proton emission, and when electric field is reverse, proton is just moved in drift tube 31, is shielded.At some
In embodiment, proton beam is by after SDTL acceleration, beam energy reaches 70MeV.Divergence type draft tube linac (SDTL)
Power consumption can be reduced, the advantages of accelerating gradient is high, compact conformation, easy processing are installed.
In certain embodiments, energy span line (MEBT) 12 in line is additionally provided between rfq accelerator and SDTL, is used
In the proton beam for receiving rfq accelerator output, the suction parameter for matching SDTL is adjusted.
Above-mentioned rfq accelerator, draft tube linac 3 and traveling wave proton precessional magnetometer 4 are by RF power sources (not shown) point
High frequency power is indescribably supplied, RF power sources have multiple, and high frequency power is transmitted separately to above-mentioned each accelerator by RF networks.
Traveling wave proton precessional magnetometer 4 is connected to after draft tube linac 3, used as high energy acceleration section.Due to RF power
Source provides high frequency power so that electromagnetic field of high frequency is formed in traveling wave proton precessional magnetometer cavity, when proton beam adds into proton
The cavity of fast device 4, will be acted on by high-frequency electric field.With reference to Fig. 4, if proton velocity Vp is asynchronous with high-frequency electric field phase velocity Vmw
Or difference is too big, over time, proton can fall into the negative value area of high-frequency electric field curve, and proton cannot effectively accelerate very
To being decelerated.Therefore, in order to normal accelerating proton, it is necessary to make the phase velocity of high-frequency electric field synchronous with proton velocity, i.e., two
Relative velocity between person is very small.
In certain embodiments, traveling wave proton precessional magnetometer 4 is circular cylindrical cavity or square cavity, including multistage is sequentially communicated
Traveling wave Proton emission chamber 40.It is one section of schematic diagram of traveling wave Proton emission chamber 40 that the application is provided, traveling wave proton with reference to Fig. 3
The inside cavities of accelerating cavity 40 are provided with the coupling disc 41 of periodic arrangement, and coupling disc 41 is metal material, is provided with footpath
To passage, coupling the radial passage of disc 41 is used to ensure the magnetic coupling between adjacent acceleration gap, is transmitted as high frequency power
Passage simultaneously can play a part of to strengthen cavity anti-interference, and the periodic arrangement for coupling disc 41 determines the height of adjacent acceleration gap
Frequency electric field phase shift.Wherein, between adjacent coupled disc 41 be acceleration gap, proton beam along the axis of traveling wave Proton emission chamber 40 just
During to motion, proton beam is accelerated full of positive high-frequency electric field in acceleration gap, coupling disc 41 isolates reverse high-frequency electric field so that
Proton beam is not decelerated.Determined by energy when entering traveling wave Proton emission chamber 40 for the interval between coupling disc 41, if
Want to accelerate the proton of 70MeV energy, the phase shift of adjacent acceleration gap high-frequency electric field is 5/6 π, into traveling wave Proton emission chamber
Proton velocity factor-beta is 0.367, and coupling disc 41 need to be spaced the distance (c is the light velocity, and f is RF power source frequency) of 0.153c/f,
If entering the proton energy in traveling wave Proton emission chamber for 80MeV, the interval 41 for coupling disc need to accordingly adjust.
Every section of traveling wave Proton emission chamber 40 is connected to a RF power source, and each RF power source is individually to every section of traveling wave
Proton emission chamber 40 provides high frequency power, forms electromagnetic field of high frequency, each RF work(in every section of traveling wave Proton emission chamber 40 respectively
The high frequency power Independent adjustable in rate source.Change the performance number of the corresponding RF power sources in traveling wave Proton emission chamber 40, you can changing should
The intensity of section accelerating cavity electric field, so as to change the energy value that proton beam is obtained after this section of accelerating cavity accelerates.Every section of traveling wave matter
Sub- accelerating cavity 40 all has certain energy acceleration area, when proton beam enters each section of traveling wave Proton emission chamber 40, every section of row
The high-frequency electric field phase velocity passed through in ripple Proton emission chamber 40 in the presence of the coupling disc 41 of periodic arrangement respectively with work as
When proton beam speed sync, when proton beam is by after the acceleration in the multistage traveling wave Proton emission chamber 40 being sequentially communicated, proton
Beam will obtain desired oncotherapy needs beam energy.In general, the need for according to oncotherapy, beam energy needs
The continuously adjustabe in the range of 70-250MeV, when 70-250MeV energy is interval, the change of its velocity factor β is by 0.367 for proton
Rise to 0.61.Therefore, traveling wave proton precessional magnetometer 4 need to ensure that the high-frequency electric field phase velocity that it passes through is interval in 0.367-0.61,
Further, need to be in the work of the coupling disc 41 of periodic arrangement by every section of high-frequency electric field phase velocity in traveling wave Proton emission chamber 40
Under, it is ensured that in one section of smaller interval, smaller interval and every section of energy acceleration area phase in traveling wave Proton emission chamber 40
Correspondence.For example, 70MeV-250MeV energy interval is divided into 12 sections, then phase velocity interval 0.367-0.61 is also divided into 12
Section, every section corresponds to a traveling wave Proton emission chamber 40 respectively.
Will be by high-frequency electrical after the proton beam of the outgoing of draft tube linac 3 enters the cavity of traveling wave proton precessional magnetometer 4
Effect and accelerate, by change input RF power sources be input into high frequency power, you can change high-frequency electric field intensity, make
The proton beam of different-energy value by the proton beam energies value continuously adjustabe of outgoing after acceleration, must be obtained, oncotherapy is met
Need.
Specifically, after energy enters traveling wave proton precessional magnetometer 4 for the proton beam of 70MeV, due to coupling the work of disc 41
With proton beam enters every section of traveling wave Proton emission chamber 40, phase velocity and the proton speed of the high frequency electric field of traveling wave Proton emission chamber 40
Degree is suitable, and proton beam is moved along the cavity axis of traveling wave proton precessional magnetometer 4, by high-frequency electrical in each traveling wave Proton emission chamber 40
The effect of field is constantly accelerated.According to actual needs, by the high frequency of each corresponding RF power source in traveling wave Proton emission chamber 40
Power setting is different performance numbers or zero, proton beam is obtained the different beam energies of desired oncotherapy needs, is realized
Proton beam energies value continuously adjustabe.
For example, 70MeV-250MeV energy interval is divided into 12 sections, every section corresponds to a traveling wave Proton emission chamber respectively
40, and by 12 adjustable RF power source supplies powers of independence, each available proton energy in traveling wave Proton emission chamber 40
Growth interval is 0-15MeV.If necessary to the proton of 150MeV energy, preceding 6 traveling wave proton precessional magnetometers only need to be opened, its
His energy can be by that analogy.
As can be seen here, through the application medical proton linac obtain the big I of proton beam energies by adjusting RF
Power source changes, the different beam energy grades of different RF power sources performance numbers correspondences, and specific corresponding to relation is searching
The form storage of table or concordance list.
Existing proton linac frequently be RFQ-DTL-CCL structures, the CCL that its high energy acceleration section is used will
To design energy, the problem that such as standing wave accelerator as 250MeV, but CCL brings is the energy of outgoing proton beam to Proton emission
Not continuously adjustable, its energy is fixed value.The advantage of traveling wave proton precessional magnetometer 4 is, (1) with accelerating gradient very high, such as
Up to 50MV/m, much larger than the 30MV/m of conventional CCL, therefore traveling wave proton precessional magnetometer can accomplish very compact to average accelerating gradient；
(2) energy of proton beam after accelerating can be adjusted by changing the high frequency power of input, so as to meet different energy during oncotherapy
The demand of amount.It should be noted that if the instrument of scientific research can based on the traveling wave proton precessional magnetometer 4 of this programme use
Basic scientific research Gao Liuqiang can not met, (Existential Space is electric during the beam acceleration of Gao Liuqiang for the requirement of quality of beam high
Lotus effect, complicated many when accelerating than low-intensity beam stream), such as the linear accelerator in CSNS project is used
It is DTL, with standing wave accelerated mode, it is not necessary to which energy can adjust, beam burst stream is about by force 30mA, line dutycycle is about
1.05%, but medical proton linac and Gao Liuqiang is not needed, the proton beam that general curative is used is about tens
The nA magnitudes of nA to hundreds of, the beam acceleration time space charge effect of this magnitude can be ignored substantially, the conduct of traveling wave proton precessional magnetometer 4
The accelerator of continuously adjustable outgoing beam energy meets the demand to beam energy for cancer well.
In sum, the application is characterized by and has used divergence type draft tube linac in middle energy accelerating sections
(SDTL), and high energy acceleration section replaces CCL of the prior art using traveling wave proton precessional magnetometer so that whole medical proton linear
Not only structure is compacter for accelerator, it is smaller to take up room, and the proton beam energies of outgoing are continuous in the range of 70-250MeV
It is adjustable, when meeting oncotherapy because in patient body knub position difference beam energy need to adjust the need for.In addition, the application
Medical proton linac H+implantation and extraction are easy, due to divergence type draft tube linac and traveling wave Proton emission
Device is the structure that multistage is sequentially connected, can sectional construction by stages, be suitable for demand of the Different hospital to proton energy, later stage
Energy upgrading is carried out also dependent on Treatment need.
Above content is to combine the further description that specific embodiment is made to the application, it is impossible to assert this Shen
Specific implementation please is confined to these explanations.For the application person of an ordinary skill in the technical field, do not taking off
On the premise of conceiving from the present application, some simple deduction or replace can also be made.
Claims (10)
1. a kind of medical proton linac, including：Ion gun, low energy accelerating sections draw the injector of proton from ion gun
With the draft tube linac that proton energy is accelerated to middle energy accelerating sections fixed energies value；Characterized in that, also including:RF
The traveling wave proton precessional magnetometer of power source and high energy acceleration section, the RF power sources provide high frequency work(for the traveling wave proton precessional magnetometer
Rate so that electromagnetic field of high frequency is formed in the traveling wave proton precessional magnetometer cavity；The traveling wave proton precessional magnetometer is connected to drift tube
After linear accelerator, accelerated by the effect of high-frequency electric field when proton beam enters the traveling wave proton precessional magnetometer cavity,
By changing the size of the high frequency power of input, the intensity of high-frequency electric field can be changed so that add by the traveling wave proton
The proton beam energies value of outgoing is continuously adjustable after fast device acceleration, obtains the proton beam of different-energy value, meets treatment of cancer
Need.
2. medical proton linac as claimed in claim 1, it is characterised in that the ion gun is electron cyclotron resonace
Ion gun.
3. medical proton linac as claimed in claim 1, it is characterised in that the traveling wave proton precessional magnetometer includes many
The traveling wave Proton emission chamber that section is sequentially connected, RF power sources have multiple, and each RF power source individually provides high to every section of accelerating cavity
Frequency power, the high frequency power Independent adjustable of each RF power source.
4. medical proton linac as claimed in claim 1, it is characterised in that the traveling wave proton precessional magnetometer also includes
The coupling disc of periodic arrangement, the periodic arrangement coupling disc is used to reduce the phase velocity of high-frequency electric field and ensures adjacent
The high frequency magnetic field coupling of unit.
5. medical proton linac as claimed in claim 4, it is characterised in that the coupling disc is arranged at the row
Ripple Proton emission chamber inside cavities, coupling disc is in periodic arrangement.
6. medical proton linac as claimed in claim 1, it is characterised in that the injector adds for radio frequency four polar field
Fast device.
7. medical proton linac as claimed in claim 6, it is characterised in that the medical proton linac is also
Including line transfers section, it is arranged between the ion gun and radio frequency four polar field accelerator, for receiving the ion gun
The proton beam of output, is adjusted the suction parameter for matching radio frequency four polar field accelerator.
8. medical proton linac as claimed in claim 1, it is characterised in that the draft tube linac for point
Release draft tube linac.
9. medical proton linac as claimed in claim 8, it is characterised in that the medical proton linac is also
Including energy span line in line, it is arranged between the radio frequency four polar field accelerator and divergence type draft tube linac, uses
In the proton beam for receiving the radio frequency four polar field accelerator output, adjusted and matched divergence type draft tube linac
Suction parameter.
10. medical proton linac as claimed in any one of claims 1-9 wherein, it is characterised in that the traveling wave proton
Accelerator is circular cylindrical cavity or square cavity.
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| CN201710157738.2A CN106879158B (en) | 2017-03-16 | 2017-03-16 | Medical proton linear accelerator |
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| CN201710157738.2A CN106879158B (en) | 2017-03-16 | 2017-03-16 | Medical proton linear accelerator |
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Cited By (15)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
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| CN109041399A (en) * | 2018-08-28 | 2018-12-18 | 中国科学院上海应用物理研究所 | Charged particle accelerator |
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| CN109513118B (en) * | 2018-11-06 | 2021-05-18 | 吴秋文 | Photon energy synthesis method and system of medical linear accelerator |
| CN109819577B (en) * | 2019-04-01 | 2021-03-19 | 北京航天广通科技有限公司 | Synchrotron control method and system based on second harmonic |
| CN109819577A (en) * | 2019-04-01 | 2019-05-28 | 北京航天广通科技有限公司 | Synchrotron control method and system based on second harmonic |
| CN110225644A (en) * | 2019-06-10 | 2019-09-10 | 中国科学院近代物理研究所 | A kind of linear accelerator and its application that energy is continuously adjustable |
| CN110223796A (en) * | 2019-06-10 | 2019-09-10 | 中国科学院近代物理研究所 | A kind of Isotope production equipment |
| CN111741589A (en) * | 2020-07-09 | 2020-10-02 | 中国科学院近代物理研究所 | Bidirectional acceleration device and bidirectional acceleration method |
| CN112704818A (en) * | 2020-12-15 | 2021-04-27 | 中国科学院近代物理研究所 | Popular type light ion tumor treatment device |
| CN112804811A (en) * | 2020-12-30 | 2021-05-14 | 中国科学院近代物理研究所 | Compact high-frequency linear accelerator system and application thereof |
| CN112870559A (en) * | 2020-12-30 | 2021-06-01 | 兰州科近泰基新技术有限责任公司 | Compact proton tumor treatment device and application thereof |
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| CN112657072B (en) * | 2021-01-05 | 2022-09-16 | 中国科学院上海高等研究院 | Ultrahigh-dose-rate proton treatment device based on linear accelerator and scanning method |
| CN116489864A (en) * | 2023-01-09 | 2023-07-25 | 中国科学院近代物理研究所 | Compact strong current H 2+ Superconducting cyclotron |
| CN116489864B (en) * | 2023-01-09 | 2024-01-30 | 中国科学院近代物理研究所 | Compact strong current H 2+ Superconducting cyclotron |
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