CN116407777A - Flash radiotherapy device and flash radiotherapy equipment - Google Patents
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Abstract
The application relates to a flash radiotherapy device and flash radiotherapy equipment, flash radiotherapy device, including high-energy electron accelerator, focusing defocusing system and scanning magnet. The high-energy electron accelerator is used for providing a first pulse electron beam current with switchable energy. The focusing and defocusing system is used for converging the first pulse electron beam current to form a beam spot at a target position. The scanning magnet is used for adjusting the position of the beam spot at the target position. The flash radiotherapy device comprises the flash radiotherapy device. The device can complete radiotherapy to a patient in millisecond-scale time. The whole treatment process adjusts the dose depth through the focusing defocusing system, ensures a smaller dose absorption percentage of the beam current on the surface, realizes that the whole flash treatment dose is injected into the target position in a very short time, and reduces the damage to normal tissues around the target position.
Description
Technical Field
The application relates to the technical field of radiotherapy, in particular to a flash radiotherapy device and flash radiotherapy equipment.
Background
Tumor therapy is an important topic of modern medical research, where radiotherapy plays an important role as an effective therapeutic tool. Along with the progress of science and technology, novel radiotherapy technology continues to appear, including adopting novel particles such as proton, heavy ion to reach accurate radiotherapy technique etc.. In addition, a novel Flash radiotherapy (Flash Radiotherapy, flash-RT) technology has been rapidly developed in recent years, and has become a new research hotspot.
Flash radiotherapy (Flash-RT, flash therapy) is a leading-edge technology and research hotspot of international tumor radiotherapy research in recent years, which uses ultra-large dose rates (typically greater than 100 Gy/s) to inject the entire radiotherapy dose into the target volume in a very short time (1-50 ms). The research shows that the composition has smaller damage to normal tissues and can reduce radiotherapy time in an order of magnitude.
The current proton treatment technology is mainly based on a cyclotron and a synchrotron, has the characteristics of slow proton energy switching or low pulse dose rate and the like, and the treatment time for completing the irradiation treatment course can not meet the technical requirements of ideal flash therapy. While the proton linear accelerator can output proton beams meeting the requirement of the dosage rate, the proton linear accelerator has high manufacturing cost and is not easy to be industrially popularized.
Disclosure of Invention
Based on the above, it is necessary to provide a flash radiotherapy device and a flash radiotherapy apparatus, aiming at the problems that in the prior art, the pulse dose rate is low and the treatment time for completing the irradiation treatment course is far from meeting the ideal flash treatment technical requirement.
A flash radiation therapy device comprising:
a high energy electron accelerator for providing a first pulsed electron beam current;
a focusing defocusing system for adjusting the first pulse electron beam to form a beam spot at a target position;
and the scanning magnet is positioned between the high-energy electron accelerator and the focusing and defocusing system or between the focusing and defocusing system and the target position and is used for adjusting the position of the beam spot at the target position.
In one embodiment, the focusing and defocusing system is a distributed focusing and defocusing magnetic element system configured to expand the first pulse electron beam, and then focus the expanded first pulse electron beam, so as to form the beam spot at the target position.
In one embodiment, the scanning magnet is used to adjust the position of the beam spot in the lateral direction.
In one embodiment, the focusing defocus system is further configured to adjust the position of the beam spot in the depth direction.
In one embodiment, the scanning magnet and the focusing and defocusing system are configured to adjust a direction of incidence of the first pulsed electron beam current to the target location.
In one embodiment, the flash radiotherapy apparatus further comprises:
the beam rapid distribution deflection system is positioned between the high-energy electron accelerator and the focusing defocusing system and is used for rapidly deflecting the first pulse electron beam to form high-energy electron beams with different energies;
the deflection magnet assembly is positioned between the beam current rapid distribution deflection system and the focusing and defocusing system, deflects and converges the high-energy electron beams with different energies to form a second pulse electron beam current, and the scanning magnet is used for adjusting the position of the second pulse electron beam current forming the beam spot at the target position.
In one embodiment, the focused defocus system is a four-stage magnet.
In one embodiment, the high energy electron accelerator has at least one of the following characteristics:
the energy range of the first pulse electron beam current regulated and output by the high-energy electron accelerator is 150MeV-250MeV;
the high-energy electron accelerator outputs the average current intensity of the first pulse electron beam current to be more than 50uA;
the operating frequency range of the high-energy electron accelerator is 9-12GHz; and
the average acceleration gradient of the high-energy electron accelerator is greater than 80MV/m.
In one embodiment, the high energy electron accelerator is configured to provide the first pulsed electron beam stream with switchable energy.
In one embodiment, the high energy electron accelerator is an X-band high gradient linear accelerator tube, a racetrack accelerator, or a superconducting electron cyclotron.
A flash radiotherapy device comprises the flash radiotherapy device and a treatment bed for bearing an irradiated body.
A flash radiotherapy apparatus comprises a high-energy electron accelerator, a focusing defocusing system and a scanning magnet. The high-energy electron accelerator is used for providing a first pulse electron beam current. The focusing and defocusing system is used for converging the first pulse electron beam current to form a beam spot at a target position. The scanning magnet is positioned between the high-energy electron accelerator and the focusing and defocusing system or between the focusing and defocusing system and the target position and is used for adjusting the position of the beam spot at the target position.
The device can complete the radiotherapy of a patient in millisecond-level time, the whole treatment process adjusts the dosage depth through the focusing defocusing system, simultaneously ensures smaller dosage absorption percentage of the beam on the surface, solves the problems that the pulse dosage rate is low, the treatment time for completing the irradiation treatment course can not meet the ideal flash treatment technical requirement far, realizes the injection of all flash treatment dosages into the target position in extremely short time, and reduces the damage to normal tissues around the target position.
Drawings
In order to more clearly illustrate the technical solutions of embodiments or conventional techniques of the present application, the drawings required for the descriptions of the embodiments or conventional techniques will be briefly described below, and it is apparent that the drawings in the following description are only some embodiments of the present application, and other drawings may be obtained according to these drawings without inventive effort for a person of ordinary skill in the art.
FIG. 1 is a block diagram of a flash radiotherapy apparatus;
FIG. 2 is a second block diagram of a flash radiotherapy apparatus;
FIG. 3 is a third block diagram of a flash radiotherapy apparatus;
fig. 4 is a structural diagram of the flash radiotherapy apparatus.
Reference numerals:
a flash radiotherapy apparatus 10; a high-energy electron accelerator 100; a scanning magnet 200; a focused defocus system 300; a target location 400; beam fast distribution deflection system 500; deflection magnet assembly 600.
Detailed Description
In order to make the objects, technical solutions and advantages of the present application more apparent, the present application will be further described in detail below by way of examples with reference to the accompanying drawings. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the present application.
The numbering of the components itself, e.g. "first", "second", etc., is used herein merely to distinguish between the described objects and does not have any sequential or technical meaning. The terms "coupled" and "connected," as used herein, are intended to encompass both direct and indirect coupling (coupling), unless otherwise indicated. In the description of the present application, it should be understood that the terms "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," "counterclockwise," etc. indicate or refer to an orientation or positional relationship based on that shown in the drawings, merely for convenience of description and to simplify the description, and do not indicate or imply that the devices or elements referred to must have a specific orientation, be configured and operated in a specific orientation, and therefore should not be construed as limiting the present application.
In this application, unless expressly stated or limited otherwise, a first feature "up" or "down" a second feature may be the first and second features in direct contact, or the first and second features in indirect contact via an intervening medium. Moreover, a first feature being "above," "over" and "on" a second feature may be a first feature being directly above or obliquely above the second feature, or simply indicating that the first feature is level higher than the second feature. The first feature being "under", "below" and "beneath" the second feature may be the first feature being directly under or obliquely below the second feature, or simply indicating that the first feature is less level than the second feature.
Embodiments of the present application provide a flash radiotherapy apparatus comprising a high-energy electron accelerator 100, a focused defocus system 300, and a scan magnet 200. The high-energy electron accelerator 100 is used for providing a first pulsed electron beam current. The focusing and defocusing system 300 is used for adjusting the first pulsed electron beam to form a beam spot at the target position 400. The scanning magnet 200 is located between the high-energy electron accelerator 100 and the focusing defocus system 300, or the scanning magnet 200 is located between the focusing defocus system 300 and the target position 400 for adjusting the position of the beam spot at the target position 400.
The target location 400 may be in the vicinity of the isocenter of the flash radiotherapy apparatus. The size of the target position 400 may be set according to the accuracy requirement of radiotherapy, for example, a sphere with an isocenter as a center and a radius of 1 mm may be used. In radiation therapy, a tumor target region may be placed at the target location 400. In one embodiment, the high-energy electron accelerator 100 is capable of providing the first pulsed electron beam current at different energies, thereby enabling treatment of tumors of different depths. The focusing and defocusing system 300 expands and focuses the first pulsed electron beam to make the first pulsed electron beam converge into the beam spot at the target position 400. The focusing and defocusing system 300 ensures that the first pulsed electron beam stream forms a focal spot with a small longitudinal length that reduces rapidly in lateral dimension to a small focal spot incident on the tumor target area, thereby focusing more energy on the tumor target area and reducing damage to surrounding healthy tissue. Moreover, the focusing and defocusing system can reduce the absorption of surface dose under the condition of certain electron beam energy, and concentrate the energy at different depths so as to adapt to tumor target areas with different depths. For example, the position of the beam spot in the depth direction may be adjusted by changing parameters of the focusing defocus system. The depth direction may refer to a direction of the electron beam current.
Referring to fig. 1, the scan magnet 200 is positioned between the high-energy electron accelerator 100 and the focusing defocus system 300. The scanning magnet 200 may generate different magnetic fields, the first pulse electron beam output by the high-energy electron accelerator 100 enters the scanning magnet 200 and may deflect in a direction, the deflected first pulse electron beam enters the focusing and defocusing system 300, and the energy of the electron beam is focused on the tumor target area after being regulated by the focusing and defocusing system 300. Accordingly, the first pulsed electron beam may be deflected at a position where the beam spot is generated after passing through the scan magnet 200 and the focusing defocus system 300. The first pulsed electron beam may be passed through the scanning magnet 200 and the focusing defocus system 300 to scan the target location 400 through a range of scan positions. The scanning magnet 200 may adjust the position of the beam spot in the lateral direction. The lateral direction may refer to a direction perpendicular to the electron beam current. For example, the scanning magnet 200 may deflect in a direction perpendicular to the electron beam, so as to achieve a transverse scanning of the electron beam in a plane perpendicular to the depth direction. The first pulse electron beam is deflected to different positions of the tumor target area by controlling the magnetic field distribution of the scanning magnet 200, so that the effect similar to the effect of irradiating a large beam spot to the tumor target area is realized by the electron beams with different directions entering the tumor target area, and the curative effect is improved. Alternatively, the scanning magnet may be an electromagnet, whereby the magnetic field distribution is controlled by varying the current to achieve different positions of incidence of the electron beam on the tumor target.
In an embodiment, the scanning magnet 200 and the focusing and defocusing system 300 may be used to adjust the direction of the first pulsed electron beam incident on the target position, so as to form a plurality of converging beam spots incident on the target position 400, thereby improving the radiation treatment effect. With continued reference to fig. 1, the position of the first pulsed electron beam is adjusted by the scanning magnet 200, and the focusing and defocusing system 300 can adjust the converging direction of the electron beam while defocusing and refocusing the first pulsed electron beam after the position adjustment, so that the electron beam converges toward the isocenter, thereby realizing that a plurality of electron beams in different directions are incident to the target position 400, and better focusing energy on the tumor target area, and further improving the effect of radiotherapy.
In the embodiment of fig. 1, the scanning magnet 200 is disposed between the high energy electron accelerator 100 and the focusing defocus system 300. In this position, the beam spot of the first pulsed electron beam entering the scan magnet 200 is small and the incident angle deviation is small, and thus the scan magnet 200 can deflect the position of the first pulsed electron beam more easily. Moreover, the first pulsed electron beam current may be further adjusted by the subsequent focusing defocus system 300 to focus energy at the tumor target volume.
Referring to fig. 2, the scanning magnet 200 is positioned between the focusing defocus system 300 and the target location 400. The scanning magnet 200 may generate different magnetic fields, the first pulsed electron beam may pass through the focused first pulsed electron beam formed by the focusing defocus system 300, and the focused first pulsed electron beam may be deflected in a direction passing through the scanning magnetic fields, which may cause the position of the beam spot formed at the target position 400 to be moved within a certain range, thereby implementing a certain range of scanning of the target position 400.
The flash radiotherapy device can complete radiotherapy to a patient in millisecond-scale time. The whole treatment process adjusts the dose depth through the focusing defocusing system 300, ensures a smaller dose absorption percentage of the beam current on the surface, realizes the injection of the whole radiotherapy dose into the target position 400 in a very short time, and reduces the damage to normal tissues around the target position 400.
In one embodiment, the focusing and defocusing system 300 is a distributed focusing and defocusing magnetic element system configured to expand the first pulsed electron beam, refocus the expanded first pulsed electron beam, and form the beam spot at the target location 400.
The focusing defocusing magnetic element system is also called a beam energy adjusting magnet system. In an embodiment, the focusing defocusing magnetic element system may gradually average the first pulsed electron beam current having a lateral dimension within 10mm to a current envelope having a lateral dimension greater than 150 mm. In order to realize rapid focusing of electron beam, the last magnetic element of the focusing and defocusing magnetic element system is a strong focusing magnetic element, the transverse size of the beam envelope can be rapidly reduced on a small longitudinal length by the strong focusing magnetic element, and a focal spot with a small transverse size is formed to be incident to the tumor target area, so that space can be saved.
Modulating the first pulsed electron beam by the beam energy modulating magnet system may concentrate a majority of the dose of the first pulsed electron beam at a tumor target. At this time, the dose of the first pulsed electron beam is rarely absorbed near the superficial layer of the skin. The focusing defocusing magnetic element system can adjust the focal length of the first pulse electron beam, can reduce the absorption of surface dose under the condition of certain electron beam energy, and concentrate the energy at different depths so as to adapt to tumor target areas with different depths.
In one embodiment, the flash radiotherapy apparatus further comprises a beam fast distribution deflection system 500 and a deflection magnet assembly 600. The beam fast distribution deflection system 500 is located between the high energy electron accelerator 100 and the focusing defocus system 300. The beam fast distribution deflection system 500 is configured to fast deflect the first pulsed electron beam to form high energy electron beams with different energies. The deflection magnet assembly 600 is positioned between the beam fast distribution deflection system 500 and the focusing defocus system 300. The deflection magnet assembly 600 deflects and converges the high-energy electron beams with different energies to form a second pulsed electron beam current. The scanning magnet 200 is used to adjust the position of the second pulsed electron beam at the target location 400 where the beam spot is formed.
The beam fast distribution deflection system 500 may be a diode magnet with a time resolution on the order of milliseconds. The beam fast distribution deflection system 500 may also be a radio frequency cavity driven by microwaves. The beam fast distribution deflection system 500 may accomplish beam deflection on the order of microseconds.
The deflection magnet assembly 600 includes a plurality of oppositely disposed deflection magnets, and deflects and converges the high-energy electron beams with different energies after passing through the plurality of oppositely disposed deflection magnets to form a second pulsed electron beam current.
The rf cavity may establish an orthogonal microwave electromagnetic field under the microwave feed-in condition, so as to rapidly deflect the first pulsed electron beam output by the high-energy electron accelerator 100. When the first pulsed electron beam passes through the beam rapid distribution deflection system 500, the deflection directions of the high-energy electron beams with different energies are different, and the first pulsed electron beam passes through the beam rapid distribution deflection system 500 to form the high-energy electron beams with different energies and different directions. The high-energy electron beams with different directions and different energies enter the deflection magnet assembly 600 to deflect, and the high-energy electron beams with different energies are converged again to form the second pulse electron beam current after passing through the deflection magnet assembly 600.
The energy of the first pulse electron beam current is the same as that of the second pulse electron beam current. And a certain included angle exists between the direction of the first pulse electron beam and the direction of the second pulse electron beam. The included angle may be 90 degrees.
Referring to fig. 3, when the scan magnet 200 is located between the deflection magnet assembly 600 and the focusing and defocusing system 300, the second pulsed electron beam enters the scan magnet 200 and then enters the focusing and defocusing system 300. The focusing and defocusing system 300 expands the second pulse electron beam, focuses the expanded second pulse electron beam, forms the beam spot at the target position 400, and the scanning magnet 200 adjusts the direction of the second pulse electron beam, so that the position of the beam spot formed at the target position 400 can move within a certain range.
Referring to fig. 4, when the scanning magnet 200 is located between the focusing and defocusing system 300 and the target position 400, the second pulsed electron beam enters the focusing and defocusing system 300 and then enters the scanning magnet 200. The focusing and defocusing system 300 expands the second pulse electron beam and focuses the expanded second pulse electron beam. The second pulse electron beam after focusing may be deflected in a direction through the scanning magnetic field, so that the position of the beam spot formed at the target position 400 may be moved within a certain range, thereby implementing a certain range of scanning on the target position 400.
In one embodiment, the focused defocus system 300 is a four-stage magnet.
In one embodiment, the quaternary magnets may be electromagnets.
In this embodiment, by adjusting the current of the quadrupole magnet in the focusing and defocusing system 300, the concentration degree of the first pulse electron beam or the second pulse electron beam is changed, which is equivalent to changing the focal length of the first pulse electron beam or the second pulse electron beam, so as to increase the dose percentage of the first pulse electron beam or the second pulse electron beam at the target position 400.
In one embodiment, when the tumor target is treated by flash radiation, the focal length of the first pulse electron beam or the second pulse electron beam can be adjusted by adjusting the current of the quadrupole magnet in the focusing defocusing system 300, so that the first pulse electron beam or the second pulse electron beam forms a focal spot with a small longitudinal length and a transverse size which is rapidly reduced to a small size, and the focal spot is incident on the tumor target, thereby focusing more energy on the tumor target and reducing damage to surrounding healthy tissues.
The focusing defocus system 300 can also be a focusing coil.
In one embodiment, adjusting the current of the focusing coil in the focusing defocus system 300 changes the concentration of the first pulsed electron beam or the second pulsed electron beam, which is equivalent to changing the focal length of the first pulsed electron beam or the second pulsed electron beam, and increases the dose absorption percentage of the first pulsed electron beam or the second pulsed electron beam at the target location 400.
In one embodiment, when the tumor target area is treated by flash radiation, the focal length of the first pulse electron beam or the second pulse electron beam can be adjusted by adjusting the current of the focusing coil in the focusing defocusing system 300, so that the first pulse electron beam or the second pulse electron beam forms a focal spot with a small transverse size and rapidly reduces to a small size in a small longitudinal length to be incident on the tumor target area, thereby focusing more energy on the tumor target area and reducing damage to surrounding healthy tissues.
In one embodiment, the high energy electron accelerator 100 has one or more characteristics. Optionally, the energy of the first pulsed electron beam current output by the high-energy electron accelerator 100 is adjusted to be in the range of 150MeV to 250MeV.
The range of the first pulsed electron beam energy of the high energy electron accelerator 100 modulation output includes 150MeV and 250MeV. The high-energy electron accelerator 100 rapidly switches the energy of the first pulsed electron beam in the range of 150MeV-250MeV, so as to meet the requirement of rapid energy switching in flash treatment.
In one embodiment, the high energy electron accelerator 100 outputs an average current of the first pulsed electron beam current greater than 50uA.
The high-energy electron accelerator 100 outputs the first pulsed electron beam with an average current greater than 50uA, ensuring that the entire flash dose is injected into the target site 400 in a short time.
In one embodiment, the high energy electron accelerator 100 operates at a frequency in the range of 9-12GHz.
In one embodiment, the average acceleration gradient of the high energy electron accelerator 100 is greater than 80MV/m.
In one embodiment, the high energy electron accelerator is configured to provide the first pulsed electron beam stream with switchable energy.
In one embodiment, the high-energy electron accelerator 100 is configured to provide the first pulsed electron beam with switchable energy, thereby providing the first pulsed electron beam with different energy, and providing more degrees of freedom for treatment planning, thereby improving the quality of radiation treatment planning.
In one embodiment, the high-energy electron accelerator 100 is an X-band high-gradient linear accelerator tube. The X-band high-gradient linear acceleration tube can be composed of an X-band high-gradient linear acceleration tube with the length smaller than 5 m. The X-band high-gradient linear acceleration tube can be driven by a klystron. The number of the klystrons is at least one. In one embodiment, the x-band linac may adjust the microwave energy of the x-band linac by varying the output power of the x-band klystron to achieve fast switching of the first pulsed electron beam energy.
In one embodiment, the high energy electron accelerator 100 is a racetrack accelerator or a superconducting electron cyclotron.
The racetrack accelerator consists of three parts, including a deflection part, an acceleration part, an injection and extraction part. The deflection part can be composed of two magnets or four magnets. The accelerating part is arranged on a connecting line between the two magnets and is used for periodically accelerating the electron beam current. The injection and extraction parts mainly comprise an electrostatic field electrode plate and a multipolar magnet.
In an embodiment, the racetrack accelerator and the superconducting electron cyclotron can implement fast switching of the first pulsed electron beam energy through a mechanical energy changer.
In particular, the mechanical energy changer is mainly composed of a multi-layer graphite or an attenuation sheet of a low atomic number material. When the energy of the first pulse electron beam is required to be reduced, the energy of the first pulse electron beam is reduced by rapidly inserting an attenuation sheet on the first pulse electron beam path.
The embodiment of the application provides a flash radiotherapy device, which comprises the flash radiotherapy device and a treatment bed for bearing an irradiated body.
The flash radiotherapy apparatus may comprise a treatment couch, a stationary gantry and a rotating gantry. The treatment couch is for carrying an irradiated body, such as a patient. In radiotherapy, the rotating gantry rotates the electron beam stream at least 360 degrees about a horizontal axis (the rotating gantry axis of rotation) to achieve radiation from different angles to the tumor target.
Referring to fig. 1 and 2, the high-energy electron accelerator 100, the focusing defocus system 300, and the scan magnet 200 are positioned on the rotating gantry in one embodiment of the present application. The rotating frame drives the treatment head to rotate around the horizontal axis, so that the multi-angle treatment of the tumor target area is realized.
In one embodiment, during flash radiotherapy, the patient is lying horizontally on the treatment couch, and the high-energy electron accelerator 100, the focusing defocus system 300, and the scan magnet 200 are vertically placed on a rotating gantry. When the rotating frame drives the treatment head to rotate around the horizontal axis, the first pulse electron beam passing through the focusing defocusing system 300 and the scanning magnet 200 is vertically incident to the tumor target area, and forms the beam spot in the tumor target area.
Referring to fig. 3 and 4, the scan magnet 200, the focusing defocus system 300, the beam fast distribution deflection system 500, and the deflection magnet assembly 600 are positioned on the rotating gantry in one embodiment of the present application. The rotating frame drives the electron beam current to rotate around a horizontal axis, so that the multi-angle treatment of the tumor target area is realized. Alternatively, the beam fast distribution deflection system 500 may not be disposed on the rotating gantry, and only needs to rapidly distribute the electron beam to the deflection magnet assemblies 600 at different gantry angles when the deflection magnet assemblies 600 are rotated to different gantry angles.
In one embodiment, the high-energy electron accelerator 100 is horizontally disposed, and outputs the first pulsed electron beam in a horizontal direction, and the high-energy electron accelerator 100 does not need to be disposed on the rotating gantry. In the flash radiotherapy process, the included angle between the second pulse electron beam and the first pulse electron beam is 90 degrees, and the second pulse electron beam is vertically incident to the tumor target area. When the rotating frame drives the electron beam to rotate around the horizontal axis, the second pulse electron beam passing through the focusing defocusing system 300 and the scanning magnet 200 vertically enters the tumor target area and forms the beam spot in the tumor target area, thereby realizing the treatment of the tumor target area from different angles. In one embodiment, the flash irradiation device may also perform non-coplanar treatment. Moreover, the pulsed electron beam current is not limited to normal incidence to the tumor target. For example, the second pulsed electron beam may be at a non-90 degree angle to the surface of the patient being treated.
In an embodiment, the flash radiotherapy apparatus may not comprise the rotating gantry described above. A plurality of beam adjustment channels may be configured, each of which may be configured with the deflection magnet assembly 600, the scanning magnet 200, and the focusing and defocusing system 300 described above, to achieve treatment of different angles of the tumor target.
The technical features of the above-described embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above-described embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.
The above examples only represent a few embodiments of the present application, which are described in more detail and are not to be construed as limiting the scope of the patent. It should be noted that it would be apparent to those skilled in the art that various modifications and improvements could be made without departing from the spirit of the present application, which would be within the scope of the present application. Accordingly, the scope of protection of the present application is to be determined by the claims appended hereto.
Claims (10)
1. A flash radiation therapy device, comprising:
a high energy electron accelerator (100) for providing a first pulsed electron beam current;
a focused defocus system (300) for adjusting the first pulsed electron beam stream to form a beam spot at a target location (400);
-a scanning magnet (200), the scanning magnet (200) being located between the high energy electron accelerator (100) and the focusing and defocusing system (300), or the scanning magnet (200) being located between the focusing and defocusing system and the target position (400), for adjusting the position of the beam spot at the target position (400).
2. The flash radiation therapy device of claim 1, wherein the flash radiation therapy device comprises,
the focusing and defocusing system (300) is a distributed focusing and defocusing magnetic element system and is configured to firstly expand the first pulse electron beam, then focus the expanded first pulse electron beam, and form the beam spot at the target position (400).
3. Flash radiotherapy device according to claim 1, characterized in that the scanning magnet (200) is used to adjust the position of the beam spot in the lateral direction.
4. Flash radiotherapy apparatus according to claim 1, characterized in that the focusing defocus system (300) is also used to adjust the position of the beam spot in the depth direction.
5. The flash radiotherapy apparatus of claim 1 in which the scanning magnet (200) and the focusing defocus system (300) are used to adjust the direction of incidence of the first pulsed electron beam stream to the target location (400).
6. The flash radiation therapy device of claim 2, further comprising:
a beam fast distribution deflection system (500) located between the high-energy electron accelerator (100) and the focusing defocus system (300), the beam fast distribution deflection system (500) being configured to fast deflect the first pulsed electron beam to form high-energy electron beams of different energies;
and the deflection magnet assembly (600) is positioned between the beam rapid distribution deflection system (500) and the focusing and defocusing system (300), the deflection magnet assembly (600) deflects and converges the high-energy electron beams with different energies to form a second pulse electron beam, and the scanning magnet (200) is used for adjusting the position of the second pulse electron beam forming the beam spot at the target position (400).
7. Flash radiotherapy device according to claim 1, characterized in that the high-energy electron accelerator (100) has at least one of the following characteristics:
the energy of the first pulse electron beam output by the high-energy electron accelerator (100) is in the range of 150MeV-250MeV;
the high-energy electron accelerator (100) outputs an average current of the first pulsed electron beam current greater than 50uA;
the operating frequency range of the high-energy electron accelerator (100) is 9-12GHz; and
the high-energy electron accelerator (100) has an average acceleration gradient of greater than 80MV/m.
8. Flash radiotherapy apparatus according to claim 1, characterized in that the high-energy electron accelerator (100) is adapted to provide the first pulsed electron beam current with switchable energy.
9. Flash radiotherapy apparatus according to claim 1, characterized in that the high-energy electron accelerator (100) is an X-band high-gradient linear accelerator tube, a racetrack accelerator or a superconducting electron cyclotron.
10. Flash radiotherapy apparatus comprising a flash radiotherapy device according to any one of claims 1 to 9 and a treatment couch for carrying an irradiated body.
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| CN202111652906.8A CN116407777A (en) | 2021-12-30 | 2021-12-30 | Flash radiotherapy device and flash radiotherapy equipment |
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN117065231A (en) * | 2023-07-28 | 2023-11-17 | 华中科技大学 | Dose optimizing device for high-energy electron radiotherapy |
| CN117731966A (en) * | 2023-12-19 | 2024-03-22 | 中山大学 | Nested saddle-shaped scanning magnet for flash-discharge treatment |
-
2021
- 2021-12-30 CN CN202111652906.8A patent/CN116407777A/en active Pending
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN117065231A (en) * | 2023-07-28 | 2023-11-17 | 华中科技大学 | Dose optimizing device for high-energy electron radiotherapy |
| CN117065231B (en) * | 2023-07-28 | 2024-02-02 | 华中科技大学 | Dose optimizing device for high-energy electron radiotherapy |
| CN117731966A (en) * | 2023-12-19 | 2024-03-22 | 中山大学 | Nested saddle-shaped scanning magnet for flash-discharge treatment |
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