CN105636331A - Electronic linear accelerator - Google Patents
Electronic linear accelerator Download PDFInfo
- Publication number
- CN105636331A CN105636331A CN201410582019.1A CN201410582019A CN105636331A CN 105636331 A CN105636331 A CN 105636331A CN 201410582019 A CN201410582019 A CN 201410582019A CN 105636331 A CN105636331 A CN 105636331A
- Authority
- CN
- China
- Prior art keywords
- electron beam
- level
- imaging
- deflection system
- magnetic deflection
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Landscapes
- Radiation-Therapy Devices (AREA)
Abstract
The invention provides an electronic linear accelerator, which comprises an electron beam emitting device used for emitting a kV-level electron beam or an mV-level electron beam, a magnetic deflection system, a therapeutic target and an imaging target. The mV-level electron beam can enter the magnetic deflection system and then shoots out of the magnetic deflection system after being deflected in the magnetic deflection system. The therapeutic target is used for receiving the mV-level electron beam shot out of the magnetic deflection system. The mV-level electron beam bombards the therapeutic target to generate therapeutic rays. The imaging target is positioned between the electron beam emitting device and the magnetic deflection system and is used for receiving the kV-level electron beam. The kV-level electron beam bombards the imaging target to generate imaging rays. According to the technical scheme of the electronic linear accelerator, the design limitation of an existing homologous double-beam linear accelerator due to the existence of a deflection magnet is broken through. The kV-level electron beam will not enter the magnetic deflection system to be deflected, while the kV-level electron beam directly bombards the imaging target to generate imaging rays. The energy of the imaging rays can meet the imaging requirement, so that the utilization efficiency of the kV-level electron beam is improved. Therefore, formed images are high in quality. Meanwhile, the irradiation part can be accurately positioned and the setup error is lowered.
Description
Technical field
The present invention relates to medical instruments field, particularly to a kind of electron linear accelerator.
Background technology
Along with the development of Interesting Issues of Precise Radiation, image-guided radiotherapy (ImageGuideRadiationTherapy, IGRT) technology is gradually by clinical practice. Use IGRT technology, on the one hand before treatment patients, it is possible to use the irradiation position of patient is verified by the mode of imaging, implement treatment after location confirmation to be illuminated is errorless again and irradiate, reduce Set-up errors. On the other hand, over the course for the treatment of can the change of real-time tracing tumor, treat condition according to the change adjustment of knub position and make irradiation field tightly " follow " target area, to realize accurate treatment.
Owing to the ray for the treatment of is generally the X ray of MV level energy, but it is unintelligible again that MV level energy is made directly imaging, therefore existing a kind of linear accelerator is the design of homology two-beam, can produce the high energy MV level electron beam for treating, also can produce the mental retardation KV level electron beam for imaging. Wherein two-beam refers to that linear accelerator can export the line of different-energy rank.
In existing a kind of homology two-beam electron linear accelerator, electron gun the electron beam launched exports after the acceleration of accelerating tube, and accelerating tube adopts energy switch to regulate the energy level of output electron beam, thus respectively obtaining KV level or the electron beam of MV level. Owing to the energy of MV level electron beam is higher, the tube length of this accelerating tube is longer, therefore typically requires this accelerating tube horizontal positioned in the frame of radiotherapy apparatus. Enter magnetic deflection system after the electron beam of accelerating tube output, get to again after deflecting through the effect of deflection magnet on the target of correspondence to produce corresponding beam. Namely, MV level electron beam and KV level electron beam can pass same deflection magnet and have the vacuum track of same deflection radius, and the energy of MV level electron beam and KV level electron beam has larger difference, therefore just require that the magnetic field range of deflection magnet is very wide, to adapt to the higher-energy of MV level electron beam and the more low-yield of KV level electron beam.
But under the premise ensureing field quality, common deflection magnet is difficulty with this requirement, and therefore existing deflection magnet can only be designed for magnetic field range needed for MV level electron beam, and this magnetic field intensity is relatively low. This results in, after KV level electron beam enters deflection magnet, owing to magnetic field intensity is relatively low, enter the KV level electron beam loss in magnetic deflection system very big, very low from the line efficiency of the KV level electron beam of deflection magnet injection, less from the KV level imaging ray of imaging target emanation, cause that imaging time is longer, and the time is longer it is possible to artifact can be produced in imaging image, causing that imaging image is of low quality, image definition declines. So, irradiation position can not be accurately positioned according to the image that definition is relatively low, finally cannot complete accurate treatment.
Summary of the invention
The problem that this invention address that is, use the electron beam loss after deflection magnet of the existing homology two-beam electron linear accelerator KV level electron beam big, cause that imaging image definition declines, the irradiation position for the treatment of ray can not be accurately positioned according to the image that definition is relatively low, finally cannot complete accurate treatment.
For solving the problems referred to above, the present invention provides a kind of electron linear accelerator, and this electron linear accelerator includes:
Electron beam launcher, is used for launching KV level electron beam or MV level electron beam;
Magnetic deflection system, described MV level electron beam can enter magnetic deflection system injection after deflection in magnetic deflection system;
Therapeutic target, for receiving the MV level electron beam penetrated from described magnetic deflection system, MV level beam bombardment therapeutic target produces treatment ray; And,
Imaging target, between described electron beam launcher and described magnetic deflection system, is used for receiving described KV level electron beam, and described KV level beam bombardment imaging target produces imaging ray.
Alternatively, described imaging target is fixedly arranged on the round of the KV level electron beam between described electron beam launcher and described magnetic deflection system, and described imaging target is configured to be passed by described MV level electron beam.
Alternatively, described imaging target is positioned at the round cross point that described MV level electron beam enters, penetrates magnetic deflection system.
Alternatively, described imaging target and therapeutic target are sequentially located at from described magnetic deflection system on the round of the MV level electron beam of injection.
Alternatively, described imaging target has the radiating surface receiving described KV level electron beam, and described radiating surface is acute angle with the angle of the round of the MV level electron beam of injection from described magnetic deflection system, and along this round towards side, therapeutic target place;
Described in described KV level beam bombardment, radiating surface is to produce imaging ray, and described imaging ray radiates at radiating surface.
Alternatively, the density range of described imaging target is: less than or equal to 8g/cm3��
Alternatively, the material of described imaging target is rustless steel, aluminum or graphite.
Alternatively, described electron beam launcher includes:
Electron gun;
Accelerating tube between described electron gun and imaging target, described accelerating tube connects with electron gun.
Alternatively, also include:
Example of primary collimator and secondary collimator, be sequentially located at the described therapeutic target downstream along the round of the MV level electron beam from magnetic deflection system injection.
Alternatively, also include: the ionization chamber between described example of primary collimator and secondary collimator.
Compared with prior art, technical scheme has the advantage that
KV level electron beam will not enter magnetic deflection system, but when arriving imaging target, directly bombardment imaging target is to occur bremsstrahlung to react, and generates mental retardation KV level imaging ray. Therefore, the electron linear accelerator of this programme breaches in existing homology two-beam linear accelerator due to the design limitation of deflection magnet, improves the line efficiency of KV level electron beam, and the quality of image of formation is high, irradiation position can be accurately positioned, reduce Set-up errors. And, it is low that the electron linear accelerator of this programme has cost, it is easy to the advantages such as operation, has higher technical advantage and good generalization. Additionally, imaging target is positioned on the KV level electron beam round that electron beam launcher is launched, arrive in all KV level electron beams of imaging target, the electronics that bremsstrahlung is reacted is not occurred directly to beat on deflection magnet after imaging target transmission, and absorbed by the shielding construction of surrounding, substantially without beating on human body, reduce patient and extra dose produced by the electron beam of bremstrahlen is not occurring suffered by imaging process, it is to avoid patient is damaged.
Accompanying drawing explanation
Fig. 1 is the plan view of the electron linear accelerator of the specific embodiment of the invention;
Fig. 2 is the electron linear accelerator operating diagram at imaging pattern of the specific embodiment of the invention;
Fig. 3 is the electron linear accelerator operating diagram at Therapeutic mode of the specific embodiment of the invention.
Detailed description of the invention
Understandable for enabling the above-mentioned purpose of the present invention, feature and advantage to become apparent from, below in conjunction with accompanying drawing, specific embodiments of the invention are described in detail.
With reference to Fig. 1, the homology two-beam IGRT medical electronic linear accelerator of the present embodiment includes:
Fixed frame 1; It is positioned at the rotary frame 2 of fixed frame 1 side; Therapeutic bed 3, patient lies in and accepts treatment on therapeutic bed 3; It is connected to the irradiation head 4 at rotary frame 2 top, relative with therapeutic bed 3, can be radiated at patient from the imaging ray of irradiation head 4 outgoing and treatment ray. Wherein rotary frame 2 can along the direction A axis reciprocating rotary around fixed frame 1, and therapeutic bed 3 also can rotate along direction B around the axis of base, to adjust the position of the relative human body of irradiation head 4, makes adjustment be radiated at the radiation profile on human body.
In conjunction with reference to Fig. 2, Fig. 3, irradiation head 4 includes a screened room (not shown), is provided with in screened room:
Electron beam launcher 41, including the accelerating tube 411 that electron gun 410 connects with electron gun 410, the axis of accelerating tube 411 is perpendicular to irradiation head 4 and points to the rectilinear direction of therapeutic bed 3, electron gun 410 is used for producing electron beam, electron beam accelerates to required speed in accelerating tube 411 so that the beam energy that accelerating tube 411 is launched meets requirement, and namely electron beam can be accelerated to the KV energy level needed for imaging and the MV energy level needed for treatment by accelerating tube 411;
Magnetic deflection system 42, it is positioned at the downstream of the electron beam direction of propagation that accelerating tube 411 is launched, MV level electron beam can enter magnetic deflection system 42, and injection after deflection in magnetic deflection system 42, usual MV level deflection of a beam of electrons angle is 270 �� or other angles, and the round of the MV level electron beam after deflection is parallel to irradiation head 4 and points to the rectilinear direction of therapeutic bed 3;
Therapeutic target 43, for receiving the MV level electron beam of injection from magnetic deflection system 42, MV level beam bombardment therapeutic target 43 is to produce treatment ray; And,
Imaging target 44, between electron beam launcher 41 and magnetic deflection system 42, is used for receiving KV level electron beam, and this KV level beam bombardment imaging target 44 is to produce imaging ray. Imaging ray is through patient body the image obtaining patient position to be treated on a display screen, and in Fig. 2, arrow represents the direction of propagation of KV level electron beam and the direction of propagation of KV level imaging ray.
In the prior art, imaging target is transmission anode target, its imaging mechanism is: KV level electron beam irradiation completes excitation therein after transmission anode target, KV level ray go out from plate target transmission after to imaging patients, therefore imaging target is arranged on the lower section of deflection magnet, and KV level electron beam must be played at imaging target upper surface face transmission from the table below after deflection magnet deflects and go out to arrive patient. Compared with prior art, the KV level electron beam of the present embodiment will not enter magnetic deflection system 42, but when arriving imaging target 44, directly bombardment imaging target 44 is to occur bremsstrahlung to react, and generates KV level mental retardation imaging ray. Therefore, the electron linear accelerator of the present embodiment breaches in existing homology two-beam linear accelerator due to the design limitation of deflection magnet, decrease the beam loss that KV level electron beam causes through deflection magnet, imaging ray energy can meet imaging demand, the quality of image formed is high, irradiation position can be accurately positioned, reduce Set-up errors. And, it is low that the electron linear accelerator of the present embodiment has cost, it is easy to the advantages such as operation, has higher technical advantage and good generalization. It addition, the imaging target of prior art is positioned at from the round of the KV level electron beam of magnetic deflection system injection, does not occur the electronics that bremsstrahlung is reacted can beat on human body after imaging target transmission in imaging target, and then human body is damaged. By comparison, in the present embodiment, imaging target 44 is positioned on the electron beam round that electron beam launcher 41 is launched, arrive in all electron beams of imaging target 44, the electronics that bremsstrahlung is reacted is not occurred directly to beat on deflection magnet after imaging target 44 transmission, and absorbed by the shielding construction of surrounding, will not beat on human body, reduce patient and injure at electron beam suffered by imaging process.
In the present embodiment, with reference to Fig. 2, Fig. 3, imaging target 44 and therapeutic target 43 are sequentially located at from magnetic deflection system 42 on the round of the MV level electron beam of injection. Imaging target 44 has the radiating surface 440 receiving KV level electron beam, and this radiating surface 440 is acute angle with the angle of the round of the MV level electron beam of injection from magnetic deflection system 42. Under imaging pattern, when KV level electron beam arrives radiating surface 440, impact radiation face 440 is to produce imaging ray, and this imaging ray can at radiating surface 440 to external radiation. By adjusting the angle of radiating surface 440 and the round of KV level electron beam, it may be achieved penetrate from the imaging ray major part of radiating surface 440 radiation towards the ray exit portal of screened room, and be radiated on human body, to obtain image comparatively clearly; In the therapeutic mode, the MV level electron beam that electron emitting device 41 is launched can pass imaging target 44 and enter magnetic deflection system 42, and after deflection, injection, again passes through imaging target 44 and arrive therapeutic target 43, and bombardment treatment target 43 is to produce MV level treatment ray. For enable MV level electron beam from imaging target 44 transmission and go out, imaging target 44 selects low density material metal or alloy material to make, and the density range of imaging target 44 is less than or equal to 8g/cm3, its higher limit is roughly equivalent to stainless density. So, there is more low-energy KV level electron beam and suffer bigger obstruction when arriving imaging target 44, and moment deceleration is to produce KV level imaging ray, and the MV level electron beam with higher-energy can go out from imaging target 44 transmission, and its energy will not obtain greater attenuation. For meeting above-mentioned density requirements, the material of imaging target 44 can be rustless steel, graphite or aluminum. In the present embodiment, the material of imaging target 44 is graphite, and KV level electron beam is beaten and is formed as on target 44 at graphite, and transmission amount is few and makes overwhelming majority KV level electron beam for exciting KV level imaging ray, and KV level imaging ray can meet imaging requirements completely.
Under imaging pattern, the position of imaging target 44 can affect the Position location accuracy of knub position. In consideration of it, in the present embodiment, owing to MV level electron beam can directly through imaging target 44, therefore imaging target 44 can be fixedly arranged on the round of the KV level electron beam between electron beam launcher 41 and magnetic deflection system 42. This can ensure that when each imaging positions, it is not necessary to repeats mobile imaging target 44, and the fixed position of imaging target 44 can effectively reduce causes bigger displacement error due to moving of target, to realize being accurately positioned knub position. Specifically, in the present embodiment, imaging target 44 is installed in the cross point that MV level electron beam enters, penetrates the round of magnetic deflection system 42, such imaging ray and treatment ray and all can penetrate from the same ray exit portal of screened room.
In addition, as variation, it is also possible to be: imaging target is located on mobile target stand, when each imaging positions, mobile imaging target is to the minimum position of image error.
Outside divided by upper structure, the electron linear accelerator of the present embodiment also includes: example of primary collimator and secondary collimator (not shown), is sequentially located at the therapeutic target 43 downstream along the round of the MV level electron beam penetrated from magnetic deflection system 42. Example of primary collimator and secondary collimator combined effect, to produce the radiation field size of definite shape profile, regulate the profile treating ray from the injection of irradiation head so that it is the radiation range profile being irradiated in tumor is essentially identical with tumor shape. Wherein, example of primary collimator is used for regulating radiation field size scope, it is possible to provide greatest irradiation open country scope, secondary collimator is for regulating the shape profile of radiation field size.
It addition, be additionally provided with an ionization chamber between example of primary collimator and secondary collimator, ionization chamber is for measuring the dosage of the imaging ray from example of primary collimator outgoing, to ensure image quality, or measures the energy treating ray, to ensure effectively and accurate treatment.
Although present disclosure is as above, but the present invention is not limited to this. Any those skilled in the art, without departing from the spirit and scope of the present invention, all can make various changes or modifications, and therefore protection scope of the present invention should be as the criterion with claim limited range.
Claims (10)
1. an electron linear accelerator, it is characterised in that including:
Electron beam launcher, is used for launching KV level electron beam or MV level electron beam;
Magnetic deflection system, described MV level electron beam can enter magnetic deflection system injection after deflection in magnetic deflection system;
Therapeutic target, for receiving the MV level electron beam penetrated from described magnetic deflection system, MV level beam bombardment therapeutic target produces treatment ray; And,
Imaging target, between described electron beam launcher and described magnetic deflection system, is used for receiving described KV level electron beam, and described KV level beam bombardment imaging target produces imaging ray.
2. electron linear accelerator as claimed in claim 1, it is characterized in that, described imaging target is fixedly arranged on the round of the KV level electron beam between described electron beam launcher and described magnetic deflection system, and described imaging target is configured to be passed by described MV level electron beam.
3. electron linear accelerator as claimed in claim 2, it is characterised in that described imaging target is positioned at the round cross point that described MV level electron beam enters, penetrates magnetic deflection system.
4. electron linear accelerator as claimed in claim 2, it is characterised in that described imaging target and therapeutic target are sequentially located at from described magnetic deflection system on the round of the MV level electron beam of injection.
5. electron linear accelerator as claimed in claim 4, it is characterized in that, described imaging target has the radiating surface receiving described KV level electron beam, described radiating surface is acute angle with the angle of the round of the MV level electron beam of injection from described magnetic deflection system, and along this round towards side, therapeutic target place;
Described in described KV level beam bombardment, radiating surface is to produce imaging ray, and described imaging ray radiates at radiating surface.
6. electron linear accelerator as claimed in claim 1, it is characterised in that the density range of described imaging target is: less than or equal to 8g/cm3��
7. electron linear accelerator as claimed in claim 6, it is characterised in that the material of described imaging target is rustless steel, aluminum or graphite.
8. electron linear accelerator as claimed in claim 2, it is characterised in that described electron beam launcher includes: electron gun;
Accelerating tube between described electron gun and imaging target, described accelerating tube connects with electron gun.
9. electron linear accelerator as claimed in claim 8, it is characterised in that also include:
Example of primary collimator and secondary collimator, be sequentially located at the described therapeutic target downstream along the round of the MV level electron beam from magnetic deflection system injection.
10. electron linear accelerator as claimed in claim 9, it is characterised in that also include: the ionization chamber between described example of primary collimator and secondary collimator.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201410582019.1A CN105636331B (en) | 2014-10-27 | 2014-10-27 | Electron linear accelerator |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201410582019.1A CN105636331B (en) | 2014-10-27 | 2014-10-27 | Electron linear accelerator |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN105636331A true CN105636331A (en) | 2016-06-01 |
| CN105636331B CN105636331B (en) | 2020-06-02 |
Family
ID=56050658
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201410582019.1A Active CN105636331B (en) | 2014-10-27 | 2014-10-27 | Electron linear accelerator |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN105636331B (en) |
Cited By (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105555007A (en) * | 2016-03-07 | 2016-05-04 | 苏州雷泰医疗科技有限公司 | Homologous dual-energy accelerator and accelerator therapy device |
| CN106132058A (en) * | 2016-08-23 | 2016-11-16 | 苏州雷泰医疗科技有限公司 | A kind of homology multipotency accelerator and accelerator therapy device |
| CN106535457A (en) * | 2016-10-28 | 2017-03-22 | 中广核中科海维科技发展有限公司 | Back-bombardment-preventing electron linear accelerator |
| CN107320858A (en) * | 2017-06-16 | 2017-11-07 | 苏州雷泰医疗科技有限公司 | A kind of dual intensity accelerator therapy device and its control method |
| CN107789749A (en) * | 2017-11-23 | 2018-03-13 | 上海联影医疗科技有限公司 | Charged particle beam deflection device and treatment system |
| CN109663220A (en) * | 2017-10-13 | 2019-04-23 | 苏州雷泰医疗科技有限公司 | A kind of method and apparatus and accelerator therapy device that MV imaging data is converted to KV imaging data |
| CN110213877A (en) * | 2019-06-21 | 2019-09-06 | 中国科学院近代物理研究所 | Bundle device is split for the ion beam of beam simultaneously for a kind of multiple terminals |
| WO2019205924A1 (en) * | 2018-04-28 | 2019-10-31 | 西安大医集团有限公司 | Radiation therapy head and radiation therapy apparatus |
| CN114145078A (en) * | 2019-07-19 | 2022-03-04 | 凤凰有限责任公司 | Gas jet deflection in pressurized systems |
| CN114286492A (en) * | 2020-09-28 | 2022-04-05 | 西门子医疗有限公司 | Linear accelerator system with magnet unit for electron beam deflection |
Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0060771A1 (en) * | 1981-03-13 | 1982-09-22 | C.G.R. MeV | X-ray photography device utilizing a charged-particles accelerator from a radiotherapy apparatus, and a radiotherapy apparatus equipped with such a device |
| JPH08206103A (en) * | 1994-10-06 | 1996-08-13 | Varian Assoc Inc | Radioactive ray medical treatment device with low dose stereostatic and x-ray source for portal imaging |
| CN1997256A (en) * | 2005-12-31 | 2007-07-11 | 清华大学 | A high and low power X ray output device |
| CN201441756U (en) * | 2009-06-23 | 2010-04-28 | 山东新华医疗器械股份有限公司 | Translation target KV/MV coaxial double-beam ray source device |
| CN102256434A (en) * | 2011-06-23 | 2011-11-23 | 山东新华医疗器械股份有限公司 | Same-source double-energy medical electron linear accelerator for image guided radiation therapy (IGRT) |
| US20120041251A1 (en) * | 2008-07-14 | 2012-02-16 | Dr. Vladimir Balakin | Charged particle cancer therapy x-ray method and apparatus |
| CN102647849A (en) * | 2012-05-04 | 2012-08-22 | 哈尔滨工程大学 | Electron linear accelerator having dual purposes and dual-purpose method of electron linear accelerator |
| CN103889135A (en) * | 2014-02-18 | 2014-06-25 | 宫良平 | Medical linear accelerator KV/MV coaxial X ray image system |
| CN203788541U (en) * | 2014-03-05 | 2014-08-20 | 上海联影医疗科技有限公司 | Medical electronic linear accelerator radiation head |
-
2014
- 2014-10-27 CN CN201410582019.1A patent/CN105636331B/en active Active
Patent Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0060771A1 (en) * | 1981-03-13 | 1982-09-22 | C.G.R. MeV | X-ray photography device utilizing a charged-particles accelerator from a radiotherapy apparatus, and a radiotherapy apparatus equipped with such a device |
| JPH08206103A (en) * | 1994-10-06 | 1996-08-13 | Varian Assoc Inc | Radioactive ray medical treatment device with low dose stereostatic and x-ray source for portal imaging |
| CN1997256A (en) * | 2005-12-31 | 2007-07-11 | 清华大学 | A high and low power X ray output device |
| US20120041251A1 (en) * | 2008-07-14 | 2012-02-16 | Dr. Vladimir Balakin | Charged particle cancer therapy x-ray method and apparatus |
| CN201441756U (en) * | 2009-06-23 | 2010-04-28 | 山东新华医疗器械股份有限公司 | Translation target KV/MV coaxial double-beam ray source device |
| CN102256434A (en) * | 2011-06-23 | 2011-11-23 | 山东新华医疗器械股份有限公司 | Same-source double-energy medical electron linear accelerator for image guided radiation therapy (IGRT) |
| CN102647849A (en) * | 2012-05-04 | 2012-08-22 | 哈尔滨工程大学 | Electron linear accelerator having dual purposes and dual-purpose method of electron linear accelerator |
| CN103889135A (en) * | 2014-02-18 | 2014-06-25 | 宫良平 | Medical linear accelerator KV/MV coaxial X ray image system |
| CN203788541U (en) * | 2014-03-05 | 2014-08-20 | 上海联影医疗科技有限公司 | Medical electronic linear accelerator radiation head |
Cited By (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105555007B (en) * | 2016-03-07 | 2019-06-18 | 苏州雷泰医疗科技有限公司 | A kind of homologous dual intensity accelerator and accelerator therapy device |
| CN105555007A (en) * | 2016-03-07 | 2016-05-04 | 苏州雷泰医疗科技有限公司 | Homologous dual-energy accelerator and accelerator therapy device |
| CN106132058A (en) * | 2016-08-23 | 2016-11-16 | 苏州雷泰医疗科技有限公司 | A kind of homology multipotency accelerator and accelerator therapy device |
| CN106535457A (en) * | 2016-10-28 | 2017-03-22 | 中广核中科海维科技发展有限公司 | Back-bombardment-preventing electron linear accelerator |
| CN107320858A (en) * | 2017-06-16 | 2017-11-07 | 苏州雷泰医疗科技有限公司 | A kind of dual intensity accelerator therapy device and its control method |
| CN107320858B (en) * | 2017-06-16 | 2024-02-23 | 苏州雷泰医疗科技有限公司 | Dual-energy accelerator treatment device and control method thereof |
| CN109663220A (en) * | 2017-10-13 | 2019-04-23 | 苏州雷泰医疗科技有限公司 | A kind of method and apparatus and accelerator therapy device that MV imaging data is converted to KV imaging data |
| CN109663220B (en) * | 2017-10-13 | 2020-12-15 | 苏州雷泰医疗科技有限公司 | Data conversion method and device and accelerator treatment device |
| CN107789749A (en) * | 2017-11-23 | 2018-03-13 | 上海联影医疗科技有限公司 | Charged particle beam deflection device and treatment system |
| CN107789749B (en) * | 2017-11-23 | 2020-02-11 | 上海联影医疗科技有限公司 | Charged particle beam deflection device and treatment system |
| WO2019205924A1 (en) * | 2018-04-28 | 2019-10-31 | 西安大医集团有限公司 | Radiation therapy head and radiation therapy apparatus |
| CN110213877A (en) * | 2019-06-21 | 2019-09-06 | 中国科学院近代物理研究所 | Bundle device is split for the ion beam of beam simultaneously for a kind of multiple terminals |
| CN114145078A (en) * | 2019-07-19 | 2022-03-04 | 凤凰有限责任公司 | Gas jet deflection in pressurized systems |
| CN114286492A (en) * | 2020-09-28 | 2022-04-05 | 西门子医疗有限公司 | Linear accelerator system with magnet unit for electron beam deflection |
Also Published As
| Publication number | Publication date |
|---|---|
| CN105636331B (en) | 2020-06-02 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN105636331A (en) | Electronic linear accelerator | |
| JP6773841B2 (en) | Supply of charged hadron beams | |
| US7645994B2 (en) | Device for outputting high and/or low energy X-rays | |
| JP7041158B2 (en) | High speed energy switching | |
| CN107648749B (en) | Radiotherapy system, beam control device thereof and beam collimation method | |
| WO2019205924A1 (en) | Radiation therapy head and radiation therapy apparatus | |
| JP2008173184A (en) | Radiation treatment system | |
| CN108883299B (en) | Moving body tracking device and radiation irradiation system | |
| EP3765152B1 (en) | Particle beam guiding system and method and related radiotherapy system | |
| JP2016106756A (en) | Radiotherapy system | |
| US20230263489A1 (en) | Imaging system for a radiotherapy device | |
| JP5701396B2 (en) | Particle beam therapy system | |
| CN208756809U (en) | Radiotherapy unit | |
| WO2020001375A1 (en) | Radiotherapy apparatus | |
| JP2013138774A (en) | Radiotherapy system | |
| CN112439131B (en) | X-ray pencil beam scanning intensity modulated therapeutic linear accelerator device | |
| Lim et al. | Design of a radiotherapy machine using the 6-MeV C-band standing-wave accelerator | |
| JP4228017B2 (en) | Radiation therapy system | |
| JP2008173181A (en) | Radiotherapy system | |
| WO2016113906A1 (en) | Radiation irradiation apparatus | |
| JPS63270066A (en) | Radiation therapy apparatus | |
| ITLT20010014A1 (en) | THERAROBOT SCAN X-RAY RADIOTHERAPY EQUIPMENT |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant | ||
| CP01 | Change in the name or title of a patent holder | ||
| CP01 | Change in the name or title of a patent holder |
Address after: 201807 Shanghai city Jiading District Industrial Zone Jiading Road No. 2258 Patentee after: Shanghai Lianying Medical Technology Co., Ltd Address before: 201807 Shanghai city Jiading District Industrial Zone Jiading Road No. 2258 Patentee before: SHANGHAI UNITED IMAGING HEALTHCARE Co.,Ltd. |