CN112156379A - Multi-treatment-terminal radiotherapy device - Google Patents
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- CN112156379A CN112156379A CN202011104043.6A CN202011104043A CN112156379A CN 112156379 A CN112156379 A CN 112156379A CN 202011104043 A CN202011104043 A CN 202011104043A CN 112156379 A CN112156379 A CN 112156379A
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- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
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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
- A61N5/1042—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy with spatial modulation of the radiation beam within the treatment head
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1077—Beam delivery systems
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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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
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- A—HUMAN NECESSITIES
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Abstract
The invention relates to a multi-treatment terminal radiotherapy device, which belongs to the technical field of radiotherapy and sequentially comprises an electron source, a radio frequency superconducting linear accelerator, a beam splitting component, an X-ray target and an X-ray collimator.
Description
Technical Field
The invention belongs to the technical field of radiotherapy, and particularly relates to a multi-treatment-terminal radiotherapy device.
Background
At present, the incidence of tumors in China is higher and higher, the tumors become one of the biggest killers harmful to the health of the people, and the common means for anti-tumor treatment comprise operations, radiotherapy, chemotherapy and the like. The principle of radiotherapy is that the radiation with certain energy acts on the cell to destroy the double DNA chains of tumor cell and inhibit the proliferation of tumor cell and kill tumor cell directly. Under the condition of the current radiotherapy, the irradiation range of normal tissues is reduced by improving the conformity degree of the radiation field of a radiotherapy machine and finally achieving the purpose of irradiating tumor tissues as accurately as possible. However, due to the structural particularity of human organs, normal tissues in radiotherapy must be irradiated with a certain dose of radiation, especially the normal tissues adjacent to tumor tissues. Therefore, under the current radiation treatment conditions, the irradiation dose of the tumor tissue needs to be increased, and the radiation dose of the normal tissues around the tumor needs to be reduced.
According to the literature report, by increasing the X-ray radiation dose rate to 106Gy/s to 108At Gy/s, the radiosensitivity of normal tissue can be reduced (radiation resistance occurs and toxic side effects are reduced), but tumor tissue is still sensitive to radiation, and this phenomenon is called "flash effect", and the condition for the "flash effect" is that extremely high dose rate radiation is emitted in a very short time (usually in the order of nanoseconds to hundreds of milliseconds), called "flash radiotherapy". The biological effect generated by 'flash radiation therapy' just solves the main contradiction of the development of tumor radiotherapy, and is a radiation therapy method which is possible to break through the dose-limiting toxicity of normal tissues at present. At present, the radiation dose rate of a medical accelerator is about 0.1Gy/s, the total time of complete radiation of a tumor patient is about 7.5 hours, the radiation is distributed in 1.5 months, and the existing radiotherapy device based on the medical normal-temperature linear accelerator cannot provide long-pulse high-dose-rate X-rays.
Disclosure of Invention
In order to solve the above-mentioned problems, a multi-treatment terminal radiotherapy device is proposed to overcome the defects of the prior art that the prior radiotherapy technology cannot provide long-pulse high dose rate X-rays, and meanwhile, a radio frequency superconducting linear accelerator can be used to provide a plurality of beam lines with different transmission directions, thereby improving the beam utilization rate and radiotherapy efficiency.
In order to achieve the purpose, the invention provides the following technical scheme:
a multi-treatment-terminal radiation therapy device comprising, in order:
an electron source for generating a long-pulse low-energy electron beam forming a pulse train;
the radio frequency superconducting linear accelerator is used for carrying out energy gain on the long-pulse low-energy electron beam to obtain a long-pulse high-energy electron beam, and the transmission directions of the long-pulse high-energy electron beams in the pulse train are the same;
the beam splitting assembly is used for applying different acting forces to a plurality of long-pulse high-energy electron beams with the same transmission direction in a pulse train to obtain a plurality of deflection electron beams, and the transmission directions of the plurality of deflection electron beams are different;
an X-ray target, the deflected electron beam bombarding the X-ray target and generating X-rays;
and an X-ray collimator for adjusting an irradiation area of the X-ray and irradiating the X-ray to the treatment terminal.
Further, the long-pulse low-energy electron beam is transmitted to the superconducting linear accelerator through the first beam transmission line to obtain energy gain so as to obtain a long-pulse high-energy electron beam, the long-pulse high-energy electron beam is guided into different second beam transmission lines through the beam splitting assembly and is transmitted to the X-ray target, X-rays are generated through interaction of the electron beam and the X-ray target, and then the X-rays are irradiated onto the treatment terminal through the X-ray collimator.
Further, the electron source comprises a driving laser, a photocathode and an anode, wherein laser emitted by the driving laser is incident on the photocathode to generate an electron beam, and an extraction electric field between the photocathode and the anode is used for extracting the electron beam from the photocathode to be incident on the first beam transmission line.
Further, the electron source is a direct-current high-voltage electron source formed by a direct-current high-voltage electron gun or a radio-frequency electron source formed by a radio-frequency electron gun, an extraction electric field formed by the direct-current high-voltage electron source is a static high-voltage electric field, and an extraction electric field formed by the radio-frequency electron source is a radio-frequency electromagnetic field.
Furthermore, the laser emitted by the driving laser is laser with adjustable pulse length so as to realize the adjustment of the pulse time length of the electron source for generating the electron beam, and the driving laser adjusts the length of the laser pulse by adjusting the length of the voltage signal.
Further, the pulse length of the long-pulse low-energy electron beam generated by the electron source is adjustable, and the adjustment range is from 10ns to 500 ms.
Further, the emittance of the long-pulse low-energy electron beam generated by the electron source is lower than 10mm x mrad.
Further, the long pulse low energy electron beam is delivered to the superconducting linear accelerator via a first beam flux transmission line.
Further, the radio frequency superconducting linear accelerator operates in a superconducting state and is driven by a radio frequency power source.
Further, the radio frequency superconducting linear accelerator comprises a radio frequency resonant cavity distributed along an axis, and the radio frequency resonant cavity is driven by a radio frequency power source.
Further, the radio frequency resonant cavity is placed in a low-temperature environment of 4K or 2K.
Further, the beam splitting assembly comprises a beam kicker, a segmentation magnet and a vacuum box, wherein the inner cavity of the vacuum box is in a vacuum environment, the beam kicker is placed at one end of the inner cavity of the vacuum box, and the segmentation magnet is placed at the other end of the inner cavity of the vacuum box.
Furthermore, the beam kicker applies a beam kicking force perpendicular to the transmission direction of the long-pulse high-energy electron beam, and the transmission direction of the long-pulse high-energy electron beam is subjected to primary deflection and is incident to the segmentation magnet, so that the transmission direction of the long-pulse high-energy electron beam is subjected to secondary deflection, and a deflected electron beam is obtained.
Furthermore, the split magnets are provided with a plurality of blocks which are arranged in a fan shape.
Further, the kickers are bar-shaped parallel electrodes comprising positive and negative plates aligned and spaced apart, with an electrostatic field between the positive and negative plates to form a kicking force.
Further, if the angle of the primary deflection of the long-pulse high-energy electron beam is alpha, then
Wherein q is the charge amount of charged particles in the long-pulse high-energy electron beam, VmIs the voltage between the positive and negative plates, W is the kinetic energy of the charged particles, d is the distance between the positive and negative plates, and L is the effective length of the positive and negative plates.
Further, the segmentation magnet is a deflection dipolar magnet which comprises a first coil and a second coil which are aligned and arranged at intervals, a separation plate is connected between the first coil and the second coil, and the long-pulse high-energy electron beam penetrates through the first coil and the second coil.
Further, the secondary deflection angle is proportional to the deflection acting force, and if the deflection acting force is set to F, F is q (v × B), where q is the charge amount of the charged particles in the long-pulse high-energy electron beam, v is the propagation speed of the long-pulse high-energy electron beam, and B is the magnetic induction intensity of the split magnet.
Further, the forces applied by the beam splitting assembly to the long pulse high energy electron beam include a kick force and a deflection force.
And further, the deflected electron beams are guided into a plurality of second beam transmission lines with different transmission directions and transmitted to the X-ray target, when the layout of the plurality of second beam transmission lines is determined, the voltage on the beam kicker is changed to control the primary deflection angle, and then the divided magnets and the second beam transmission lines are injected correspondingly, so that a plurality of long-pulse high-energy electron beams with the same transmission direction in a pulse train emitted by the radio-frequency superconducting linear accelerator are distributed to the second beam transmission lines with different transmission directions to reach different treatment terminals.
Furthermore, the number of the X-ray targets, the X-ray collimators, the splitting magnets and the treatment terminals is the same.
Further, the X-ray target comprises a high atomic number material.
The invention has the beneficial effects that:
the X-ray of long pulse high dosage rate is provided by adopting the electron source and the radio frequency superconducting linear accelerator, so that the very high irradiation dosage can be given to a treatment terminal in a short time, the energy of the X-ray can be adjusted by adjusting the energy of the electron beam, the time length of the X-ray can be adjusted by adjusting the pulse length of the electron beam, and the dosage rate can be adjusted by adjusting the flow intensity of the electron beam, so that the better radiotherapy effect of the treatment terminal can be achieved.
Drawings
FIG. 1 is a schematic view of the overall structure of the present invention;
FIG. 2 is a schematic structural view of a beam splitting assembly;
FIG. 3 is a schematic view of a kicker;
FIG. 4 is a schematic view of a split magnet configuration;
fig. 5 is a schematic diagram of the evolution of a plurality of long pulsed high energy electron beams to a plurality of deflected electron beams.
In the drawings: the device comprises a 1-electron source, a 2-first beam transmission line, a 3-radio frequency superconducting linear accelerator, a 4-second beam transmission line, a 5-X-ray target, a 6-X-ray collimator, a 7-beam splitting assembly, an 8-beam kicker, a 9-split magnet, a 10-vacuum box, an 11-positive plate, a 12-negative plate, a 13-first coil, a 14-second coil 14, a 15-splitter plate, a 16-beam passing area and a 17-non-beam passing area.
Detailed Description
In order to make the technical solutions of the present invention better understood, the following description of the technical solutions of the present invention with reference to the accompanying drawings of the present invention is made clearly and completely, and other similar embodiments obtained by a person of ordinary skill in the art without any creative effort based on the embodiments in the present application shall fall within the protection scope of the present application. In addition, directional terms such as "upper", "lower", "left", "right", etc. in the following embodiments are directions with reference to the drawings only, and thus, the directional terms are used for illustrating the present invention and not for limiting the present invention.
The first embodiment is as follows:
as shown in figure 1, a multi-treatment terminal radiotherapy device comprises an electron source 1, a radio frequency superconducting linear accelerator 3, a beam splitting assembly 7, an X-ray target 5 and an X-ray collimator 6 in sequence, wherein the electron source 1 is used for generating a long-pulse low-energy electron beam to form a pulse train, the long-pulse low-energy electron beam is transmitted to the radio frequency superconducting linear accelerator 3 through a first beam transmission line 2, the radio frequency superconducting linear accelerator 3 is used for performing energy gain on the long-pulse low-energy electron beam to obtain a long-pulse high-energy electron beam, the transmission directions of a plurality of long-pulse high-energy electron beams in the pulse train are the same, the beam splitting assembly 7 is used for applying different acting forces to the plurality of long-pulse high-energy electron beams in the same transmission direction in the pulse train to obtain deflected electron beams, the transmission directions of the deflected electron beams are all different, the deflected electron beams are guided into different, the deflected electron beam bombards the X-ray target 5 and generates X-rays, and the X-ray collimator 6 adjusts the irradiation area of the X-rays and irradiates the X-rays onto the treatment terminal.
The electron source 1 generates a long-pulse low-energy electron beam BE1 with a first energy E1, the electron source 1 comprises a driving laser, a photocathode and an anode, the driving laser emits laser light to BE incident on the photocathode to generate an electron beam, and an extraction electric field between the photocathode and the anode extracts the electron beam from the photocathode to BE incident on a first beam transmission line 2. The long-pulse low-energy electron beam BE1 is generated by a driving laser through the action of a photocathode, the long-pulse low-energy electron beam BE1 and the driving laser have the same time structure, the laser emitted by the driving laser is laser with adjustable pulse length, so that the pulse time length of the long-pulse low-energy electron beam BE1 generated by the electron source 1 is adjustable, and the driving laser adjusts the length of a laser pulse by adjusting the length of a voltage signal. Meanwhile, the pulse length of the long-pulse low-energy electron beam BE1 is adjustable, the adjustment range is from 10ns to 500ms, and the emittance is lower than 10mm x mrad.
The electron source 1 is a direct-current high-voltage electron source formed by a direct-current high-voltage electron gun or a radio-frequency electron source formed by a radio-frequency electron gun, an extraction electric field formed by the direct-current high-voltage electron source is a static high-voltage electric field, and an extraction electric field formed by the radio-frequency electron source is a radio-frequency electromagnetic field.
The radio frequency superconducting linear accelerator 3 comprises radio frequency resonant cavities distributed along an axis, the radio frequency resonant cavities are driven by a radio frequency power source, and the radio frequency resonant cavities are placed in a 4K or 2K low-temperature environment to ensure that the radio frequency superconducting linear accelerator 3 runs in a superconducting state. The radio frequency resonant cavity is soaked in liquid helium with gas phase and liquid phase for cooling, and the working temperature is the boiling temperature of the liquid helium. The boiling temperature of liquid helium at one atmosphere is 4.2K and at 30mBar is 2K. Pumping helium gas through a pump set of the cryogenic system, and controlling the surface gas pressure of the liquid helium so as to control the temperature of the liquid helium. The long-pulse low-energy electron beam BE1 passes through the radio-frequency superconducting linear accelerator 3 to obtain the energy gain Delta E, and becomes a long-pulse high-energy electron beam BE 2. Meanwhile, the Δ E is determined by the scale and performance of the radio frequency superconducting linear accelerator 3, and the larger the number of radio frequency resonant cavities is, the larger the field gradient is, and the larger the energy gain Δ E is. In theory, Δ E can range from a few MeV to a few GeV or even to infinity.
For radiotherapy devices, the energy gain Δ E does not need to be particularly large, and is in an energy interval suitable for human radiotherapy, generally 4-18 MeV. Under the premise of determining the type and the number of the radio frequency resonant cavities, the energy gain delta E can be adjusted by adjusting the intensity of the radio frequency resonant cavities so as to meet the X-ray energy requirements required by different radiotherapy. The strength of the radio frequency resonant cavity is positively correlated with the feed-in power of the power source, and the field gradient of the radio frequency resonant cavity is correspondingly changed by adjusting the power of the power source.
The electron source 1 and the radio frequency superconducting linear accelerator 3 are adopted to provide long-pulse high-dose-rate X rays for radiotherapy, so that very high irradiation dose can be given to a treatment terminal in a short time, the energy of the X rays can be adjusted by adjusting the energy of an electron beam, the time length of the X rays can be adjusted by adjusting the pulse length of the electron beam, and the dose rate can be adjusted by adjusting the flow intensity of the electron beam, so that better radiotherapy effect of the treatment terminal can be achieved.
As shown in fig. 2, the beam splitting assembly 7 includes a beam kicker 8, a dividing magnet 9 and a vacuum box 10, an inner cavity of the vacuum box 10 is in a vacuum environment, the beam kicker 8 is placed at one end of the inner cavity, the dividing magnet 9 is placed at the other end of the inner cavity, the dividing magnet 9 is provided with a plurality of blocks, and the plurality of blocks of dividing magnets 9 are arranged in a fan shape. Specifically, the beam kicker 8 applies a kicking force perpendicular to the transmission direction of the long-pulse high-energy electron beam, and the transmission direction of the long-pulse high-energy electron beam is subjected to primary deflection and is incident on the split magnet 9, so that the transmission direction of the long-pulse high-energy electron beam is subjected to secondary deflection, and a deflected electron beam is obtained.
As shown in fig. 3, the kickers 8 are bar-shaped parallel electrodes including positive plates 11 and positive plates 11 aligned and spaced apartAnd the negative plate 12, and an electrostatic field exists between the positive plate 11 and the negative plate 12 to form kicking force. When an electrostatic field exists between the positive electrode plate 11 and the negative electrode plate 12, that is, when the positive electrode plate 11 and the negative electrode plate 12 are respectively connected to the positive electrode and the negative electrode of the pulse high-voltage power supply, a pulse high-voltage electric field is formed between the positive electrode plate 11 and the negative electrode plate 12, and when a long-pulse high-energy electron beam passes through between the positive electrode plate 11 and the negative electrode plate 12, a primary deflection angle is α, a primary deflection occurs
Wherein q is the charge amount of charged particles in the long-pulse high-energy electron beam, VmIs the voltage between the positive and negative plates, W is the kinetic energy of the charged particles, d is the distance between the positive and negative plates, and L is the effective length of the positive and negative plates. In general, the primary deflection angle is a very small angle, and tg α ≈ α.
As shown in fig. 4, the split magnet 9 is a deflection dipole magnet, and includes a first coil 13 and a second coil 14 which are aligned and spaced, the long-pulse high-energy electron beam passes through the first coil 13 and the second coil 14, and a separation plate 15 is connected between the first coil 13 and the second coil 14 to change the magnetic field distribution, specifically, to improve the uniformity of the magnetic field in the beam passing region 16 and to reduce the stray field in the non-beam passing region 17 as much as possible. The secondary deflection angle is proportional to the deflection acting force, and if the deflection acting force is set to F, F is q (v × B), where q is the charge amount of the charged particles in the long-pulse high-energy electron beam, v is the propagation speed of the long-pulse high-energy electron beam, and B is the magnetic induction intensity of the split magnet 9. Because the magnetic induction intensity of the beam passing area 16 is large, even 1T magnitude can be achieved, and therefore a large secondary deflection angle exists after the long-pulse high-energy electron beam passes through the beam passing area 16.
That is, the forces applied by the beam splitting assembly to the long pulse high energy electron beam include kick and deflection forces. The deflected electron beams are led into a plurality of second beam transmission lines 4 with different transmission directions and transmitted to an X-ray target 5, when the layout of the plurality of second beam transmission lines 4 is determined, the voltage on a beam kicker 8 is changed to control the primary deflection angle, and then the divided magnets 9 and the second beam transmission lines 4 are injected correspondingly, so far, a plurality of long-pulse high-energy electron beams with the same transmission direction in a pulse train emitted by the radio-frequency superconducting linear accelerator 3 are distributed to the second beam transmission lines 4 with different transmission directions to reach different treatment terminals.
In order to intuitively express the inventive concept of the inventor, the process of evolving from a plurality of long-pulse high-energy electron beams with the same transmission direction to a plurality of deflected electron beams with different transmission directions is illustrated in fig. 5 as an example: the second beam transmission lines 4 are provided with 4, the pulse train emitted by the radio frequency superconducting linear accelerator 3 contains 4 long pulse high-energy electron beams with the same transmission direction and are respectively represented by A, B, C, D, the 4 long pulse high-energy electron beams are transmitted to the beam splitting assembly 7 to form 4 deflection electron beams which are respectively represented by A ', B', C 'and D', and meanwhile, the 4 deflection electron beams are respectively led into the second beam transmission lines 4 with different transmission directions.
The core component of the X-ray target 5 is a high Z material (i.e., a high atomic number material) that generates X-rays by the interaction of a deflected electron beam and the high Z material. The X-ray target 5 is made of a high-Z material having a hard texture, a high heat transfer rate, and a high melting point, and generally made of tungsten or tantalum. Meanwhile, the X-ray target 5 should have a cooling function to prevent the energy of the deflected electron beam deposition from burning out the X-ray target 5. The X-ray is irradiated to the treatment terminal via the X-ray collimator 6, and the X-ray collimator 6 filters the X-ray outside the treatment terminal area to adjust the distribution of the X-ray. The number of the X-ray targets 5, the X-ray collimators 6, and the split magnets 9 is the same as the number of the treatment terminals.
To sum up, the electron source 1 generates a pulse train formed by a long-pulse low-energy electron beam, the long-pulse low-energy electron beam is transmitted to the radio frequency superconducting linear accelerator 3 through the first beam transmission line 2 to obtain energy gain, and then transmitted to the beam splitting assembly 7 to form a plurality of deflection electron beams, the deflection electron beams are transmitted to the X-ray target 5 through the second beam transmission line 4, and X-rays are generated through interaction between the deflection electron beams and the X-ray target 5. Part of energy of the deflected electron beams is converted into energy of X rays, the other part of energy is deposited on an X ray target 5 in the form of heat energy, an X ray collimator 6 irradiates the X rays to a treatment terminal, and the function that one radio frequency superconducting linear accelerator 3 supplies beams to a plurality of treatment terminals at the same time is achieved.
Example two:
parts of this embodiment that are the same as those of the first embodiment are not described again, except that:
the electron source 1 adopts a direct-current high-voltage electron gun, the direct-current high-voltage electron gun generates a long-pulse low-energy electron beam BE1 with the energy of about 300kV, an induced electric field of the direct-current high-voltage electron gun is a static high-voltage electric field formed between a photocathode and an anode by a direct-current high-voltage power supply, and the long-pulse low-energy electron beam and the driving laser have the same time distribution which is less than 10 ps.
The radio frequency resonant cavity uses 2 4-unit TESLA cavity types with 1.3GHz, the field gradient adjustment range is 0-10 MV/m, the effective acceleration length is 1m, the electron beam energy gain adjustment interval is 0-10 MeV, and the long-pulse high-energy electron beam energy is 6-8 MeV.
The X-ray target 5 is a tungsten target and is a rotating target, namely the X-ray target 5 rotates ceaselessly, so that deflected electron beams are made to hit different parts, and the phenomenon that the X-ray target 5 is burnt out due to too concentrated heat is avoided. In other embodiments, water pipes may be laid in the X-ray target 5, and cooling water may be introduced to dissipate heat.
The present invention has been described in detail, and it should be understood that the detailed description and specific examples, while indicating the preferred embodiment of the invention, are intended for purposes of illustration only and are not intended to limit the scope of the invention.
Claims (9)
1. A multi-treatment terminal radiotherapy device is characterized by sequentially comprising:
an electron source for generating a long-pulse low-energy electron beam forming a pulse train;
the radio frequency superconducting linear accelerator is used for carrying out energy gain on the long-pulse low-energy electron beam to obtain a long-pulse high-energy electron beam, and the transmission directions of the long-pulse high-energy electron beams in the pulse train are the same;
the beam splitting assembly is used for applying different acting forces to a plurality of long-pulse high-energy electron beams with the same transmission direction in a pulse train to obtain a plurality of deflection electron beams, and the transmission directions of the plurality of deflection electron beams are different;
an X-ray target, the deflected electron beam bombarding the X-ray target and generating X-rays;
and an X-ray collimator for adjusting an irradiation area of the X-ray and irradiating the X-ray to the treatment terminal.
2. The multi-treatment terminal radiotherapy device of claim 1, wherein the beam splitting assembly comprises a kicker, a splitting magnet, and a vacuum box, the vacuum box having a cavity in a vacuum environment, the kicker being disposed at one end of the cavity, and the splitting magnet being disposed at the other end of the cavity.
3. The multi-treatment terminal radiotherapy device according to claim 2, wherein the kicker applies a kicking force perpendicular to a transmission direction of the long-pulse high-energy electron beam to the long-pulse high-energy electron beam, and the transmission direction of the long-pulse high-energy electron beam is primarily deflected and incident to the dividing magnet, so that the transmission direction of the long-pulse high-energy electron beam is secondarily deflected to obtain a deflected electron beam.
4. The multi-treatment terminal radiotherapy device of claim 3, wherein the split magnet is provided in a plurality of pieces, and the plurality of split magnets are arranged in a fan shape.
5. A multi-treatment terminal radiotherapeutic apparatus according to any one of claims 2 to 4, wherein the kickers are bar-shaped parallel electrodes comprising positive and negative plates in aligned spaced apart relationship with an electrostatic field therebetween to generate a kicking force.
6. The multi-treatment terminal radiation therapy device of claim 5, wherein the angle at which the long-pulse high-energy electron beam is deflected is a, then
Wherein q is the charge amount of charged particles in the long-pulse high-energy electron beam, VmIs the voltage between the positive and negative plates, W is the kinetic energy of the charged particles, d is the distance between the positive and negative plates, and L is the effective length of the positive and negative plates.
7. The multi-treatment terminal radiotherapy device of claim 6, wherein the split magnet is a deflection dipole magnet comprising a first coil and a second coil aligned and spaced apart with a separation plate connected therebetween, and the long-pulse high-energy electron beam passes through the first coil and the second coil.
8. The multi-treatment terminal radiotherapy device according to claim 7, wherein the secondary deflection angle is proportional to the deflection acting force, and if the deflection acting force is set to be F, then F is q (v × B), where q is the charge amount of the charged particles in the long-pulse high-energy electron beam, v is the transmission speed of the long-pulse high-energy electron beam, and B is the magnetic induction of the split magnet.
9. The multi-treatment terminal radiotherapy device of claim 8, wherein the number of the X-ray targets, the X-ray collimators, the split magnets and the treatment terminals is the same.
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| CN202011104043.6A CN112156379A (en) | 2020-10-15 | 2020-10-15 | Multi-treatment-terminal radiotherapy device |
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113616938A (en) * | 2021-08-05 | 2021-11-09 | 中国科学院近代物理研究所 | Compact electronic linear accelerator system for FLASH radiotherapy |
| CN114867181A (en) * | 2022-04-22 | 2022-08-05 | 西北核技术研究所 | Low-frequency kick cavity device for multi-pulse compression and manufacturing method thereof |
-
2020
- 2020-10-15 CN CN202011104043.6A patent/CN112156379A/en active Pending
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113616938A (en) * | 2021-08-05 | 2021-11-09 | 中国科学院近代物理研究所 | Compact electronic linear accelerator system for FLASH radiotherapy |
| CN113616938B (en) * | 2021-08-05 | 2024-03-15 | 中国科学院近代物理研究所 | Compact electronic linac system for FLASH radiotherapy |
| CN114867181A (en) * | 2022-04-22 | 2022-08-05 | 西北核技术研究所 | Low-frequency kick cavity device for multi-pulse compression and manufacturing method thereof |
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