CN105636331B - Electron linear accelerator - Google Patents
Electron linear accelerator Download PDFInfo
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- CN105636331B CN105636331B CN201410582019.1A CN201410582019A CN105636331B CN 105636331 B CN105636331 B CN 105636331B CN 201410582019 A CN201410582019 A CN 201410582019A CN 105636331 B CN105636331 B CN 105636331B
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Abstract
An electron linear accelerator comprising: electron beam emitting device for emitting a KV electron beam or a MV electron beam: and the MV-grade electron beams can enter the magnetic deflection system, are deflected in the magnetic deflection system and then are emitted: a treatment target for receiving the MV-grade electron beam emitted from the magnetic deflection system, the MV-grade electron beam bombarding the treatment target to generate treatment rays: and the imaging target is positioned between the electron beam emitting device and the magnetic deflection system and used for receiving the KV-level electron beam, and the KV-level electron beam bombards the imaging target to generate imaging rays. The electron linear accelerator breaks through the design limitation of a deflection magnet in the existing homologous double-beam linear accelerator, a KV-level electron beam cannot enter a magnetic deflection system to deflect but directly bombards an imaging target to generate imaging rays, the energy of the imaging rays can meet the imaging requirement, the utilization efficiency of the KV-level electron beam is improved, the formed image is high in quality, the irradiation position can be accurately positioned, and the positioning error is reduced.
Description
Technical Field
The invention relates to the field of medical instruments, in particular to an electron linear accelerator.
Background
With the development of precision radiotherapy technology, Image Guide Radiation Therapy (IGRT) technology is gradually applied clinically. By using the IGRT technology, on one hand, before the patient receives treatment, the irradiation position of the patient can be verified in an imaging mode, and after the irradiation position is confirmed to be correct, treatment irradiation is carried out, so that the positioning error is reduced. On the other hand, the change of the tumor can be tracked in real time in the treatment process, and the treatment condition is adjusted according to the change of the tumor position so that the irradiation field closely follows the target area, thereby realizing accurate treatment.
Since the therapeutic radiation is usually X-rays with MV-level energy, but the MV-level energy is directly imaged and is unclear, an existing linear accelerator is designed with a homologous dual-beam system, and can generate both high-energy MV-level electron beams for therapy and low-energy KV-level electron beams for imaging. The dual beams refer to beams of different energy levels which can be output by the linear accelerator.
In the existing homologous dual-beam electron linear accelerator, an electron beam emitted by an electron gun is accelerated by an accelerating tube and then output, and the energy level of the output electron beam is adjusted by the accelerating tube by adopting an energy switch, so that a KV-level electron beam or an MV-level electron beam is obtained respectively. Since the tube length of the accelerating tube is long due to the high energy of the MV-grade electron beam, it is usually necessary to place the accelerating tube horizontally in the gantry of the radiotherapy apparatus. The electron beam output by the accelerating tube enters a magnetic deflection system, is deflected under the action of a deflection magnet and then is irradiated onto a corresponding target to generate a corresponding ray beam. That is, the MV-grade electron beam and the KV-grade electron beam pass through the same deflection magnet and have the same deflection radius of the vacuum orbit, and the energies of the MV-grade electron beam and the KV-grade electron beam have a large difference, so that the magnetic field range of the deflection magnet is required to be wide to accommodate the higher energy of the MV-grade electron beam and the lower energy of the KV-grade electron beam.
However, on the premise of ensuring the quality of the magnetic field, the common deflection magnet is difficult to realize the requirement, so that the existing deflection magnet can only be designed for the magnetic field range required by the MV grade electron beam, and the magnetic field intensity is lower. Therefore, after the KV electron beam enters the deflection magnet, the KV electron beam entering the magnetic deflection system has a large loss due to a low magnetic field strength, the beam efficiency of the KV electron beam emitted from the deflection magnet is low, the KV imaging ray radiated from the imaging target is less, resulting in a long imaging time, which may generate an artifact in the imaging image, resulting in a low quality of the imaging image and a reduced definition of the image. Thus, the irradiation position cannot be accurately positioned according to the image with low definition, and finally, accurate treatment cannot be completed.
Disclosure of Invention
The invention solves the problems that the loss of an electron beam of a KV-level electron beam of the existing homologous double-beam electron linear accelerator is large after passing through a deflection magnet, so that the definition of an imaging image is reduced, the irradiation position of a treatment ray cannot be accurately positioned according to an image with lower definition, and finally accurate treatment cannot be finished.
To solve the above problems, the present invention provides an electron linear accelerator, comprising:
the electron beam emitting device is used for emitting a KV-level electron beam or an MV-level electron beam;
the MV-grade electron beams can enter the magnetic deflection system, and are deflected in the magnetic deflection system and then emitted;
the treatment target is used for receiving the MV-grade electron beams emitted from the magnetic deflection system, and the MV-grade electron beams bombard the treatment target to generate treatment rays; and the number of the first and second groups,
and the imaging target is positioned between the electron beam emitting device and the magnetic deflection system and is used for receiving the KV electron beam, and the KV electron beam bombards the imaging target to generate imaging rays.
Optionally, the imaging target is fixed on a propagation path of the KV-grade electron beam between the electron beam emitting device and the magnetic deflection system, and the imaging target is configured to be penetrated by the MV-grade electron beam.
Optionally, the imaging target is located at the intersection of the propagation paths of the MV-grade electron beam entering and exiting the magnetic deflection system.
Optionally, the imaging target and the therapeutic target are sequentially located on a propagation path of the MV grade electron beam emitted from the magnetic deflection system.
Optionally, the imaging target has a radiation surface for receiving the KV-grade electron beam, an included angle between the radiation surface and a propagation path of the MV-grade electron beam emitted from the magnetic deflection system is an acute angle, and the radiation surface faces the side of the treatment target along the propagation path;
the KV-level electron beams bombard the radiation surface to generate imaging rays, and the imaging rays are radiated on the radiation surface.
Optionally, the density range of the imaging target is: less than or equal to 8g/cm3。
Optionally, the material of the imaging target is stainless steel, aluminum or graphite.
Optionally, the electron beam emitting device includes:
an electron gun;
and the accelerating tube is positioned between the electron gun and the imaging target and is communicated with the electron gun.
Optionally, the method further comprises:
and the primary collimator and the secondary collimator are sequentially positioned downstream of the treatment target along the propagation path of the MV-grade electron beam emitted from the magnetic deflection system.
Optionally, the method further comprises: an ionization chamber located between the primary collimator and the secondary collimator.
Compared with the prior art, the technical scheme of the invention has the following advantages:
the KV-level electron beam does not enter the magnetic deflection system, but directly bombards the imaging target to generate bremsstrahlung reaction when reaching the imaging target, so as to generate low-energy KV-level imaging rays. Therefore, the electron linear accelerator breaks through the design limitation of the deflection magnet in the existing homologous double-beam linear accelerator, improves the beam efficiency of the KV electron beam, forms high-quality images, can accurately position the irradiation position, and reduces the positioning error. In addition, the electronic linear accelerator has the advantages of low cost, easiness in operation and the like, and has high technical advantages and good popularization. In addition, the imaging target is positioned on a KV-level electron beam propagation line emitted by the electron beam emitting device, all KV-level electron beams reaching the imaging target are transmitted by the imaging target, electrons which do not generate bremsstrahlung reaction directly hit the deflection magnet and are absorbed by surrounding shielding structures, and basically do not hit a human body, so that extra dose generated by the electron beams which do not generate bremsstrahlung radiation and applied to a patient in the imaging process is reduced, and the patient is prevented from being injured.
Drawings
FIG. 1 is a plan view of an electron linear accelerator in accordance with an embodiment of the invention;
FIG. 2 is a schematic diagram of an electron linear accelerator according to an embodiment of the present invention operating in an imaging mode;
fig. 3 is a schematic diagram of the operation of the electron linac in the treatment mode according to an embodiment of the present invention.
Detailed Description
In order to make the aforementioned objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in detail below.
Referring to fig. 1, the homologous dual-beam IGRT medical electron linear accelerator of the present embodiment includes:
a fixed frame 1; a rotating frame 2 positioned at one side of the fixed frame 1; a treatment bed 3, wherein a patient lies on the treatment bed 3 to be treated; an irradiation head 4 is connected to the top of the rotating gantry 2, opposite to the couch 3, and the imaging radiation and the treatment radiation emitted from the irradiation head 4 can be irradiated on the patient. The rotating frame 2 can rotate around the central axis of the fixed frame 1 in a reciprocating way along the direction A, and the treatment bed 3 can also rotate around the axis of the base along the direction B so as to adjust the position of the irradiation head 4 relative to the human body and adjust the distribution of rays irradiated on the human body.
With combined reference to fig. 2 and 3, the irradiation head 4 comprises a shielding chamber (not shown), inside which are disposed:
the electron beam emitting device 41 comprises an electron gun 410 and an accelerating tube 411 communicated with the electron gun 410, wherein the central axis of the accelerating tube 411 is perpendicular to the linear direction of the irradiation head 4 pointing to the treatment couch 3, the electron gun 410 is used for generating electron beams, the electron beams are accelerated in the accelerating tube 411 to the required speed so that the energy of the electron beams emitted by the accelerating tube 411 meets the requirement, namely the accelerating tube 411 can accelerate the electron beams to the KV energy level required by imaging and the MV energy level required by treatment;
the magnetic deflection system 42 is positioned at the downstream of the propagation direction of the electron beam emitted by the accelerating tube 411, the MV-grade electron beam can enter the magnetic deflection system 42 and is emitted after being deflected in the magnetic deflection system 42, the deflection angle of the MV-grade electron beam is 270 degrees or other angles, and the propagation route of the deflected MV-grade electron beam is parallel to the linear direction of the irradiation head 4 pointing to the treatment couch 3;
a treatment target 43 for receiving the MV-grade electron beam emitted from the magnetic deflection system 42, the MV-grade electron beam bombarding the treatment target 43 to generate treatment radiation; and the number of the first and second groups,
and an imaging target 44 located between the electron beam emitting device 41 and the magnetic deflection system 42 for receiving a KV electron beam, which bombards the imaging target 44 to generate imaging rays. The imaging rays pass through the body of the patient and obtain an image of the part of the patient to be treated on the display screen, and arrows in fig. 2 represent the propagation direction of the KV-level electron beam and the propagation direction of the KV-level imaging rays.
In the prior art, the imaging target is a transmission anode target, and the imaging mechanism is as follows: the KV electron beam irradiates the transmission anode target and then is excited in the transmission anode target, KV rays are transmitted from the anode target and then image a patient, therefore, the imaging target is arranged below the deflection magnet, and the KV electron beam is deflected by the deflection magnet, then strikes the upper surface of the imaging target and is transmitted from the lower surface to reach the patient. Compared with the prior art, the KV-grade electron beam of the present embodiment does not enter the magnetic deflection system 42, but directly bombards the imaging target 44 to generate bremsstrahlung reaction to generate KV-grade low-energy imaging rays when reaching the imaging target 44. Therefore, the electron linear accelerator breaks through the design limitation of the deflection magnet in the existing homologous double-beam linear accelerator, the beam loss caused by the fact that the KV electron beam passes through the deflection magnet is reduced, the imaging ray energy can meet the imaging requirement, the formed image quality is high, the irradiation position can be accurately positioned, and the positioning error is reduced. Moreover, the electronic linear accelerator of the embodiment has the advantages of low cost, easiness in operation and the like, and has higher technical advantages and good popularization. In addition, the imaging target in the prior art is positioned on a propagation path of a KV electron beam emitted from the magnetic deflection system, and electrons which do not generate bremsstrahlung reaction in the imaging target are transmitted from the imaging target and then hit a human body, so that the human body is damaged. Compared with the above, in the present embodiment, the imaging target 44 is located on the electron beam propagation path emitted by the electron beam emitting device 41, and of all the electron beams reaching the imaging target 44, electrons that do not undergo bremsstrahlung reaction are transmitted from the imaging target 44, and then directly hit the deflection magnet, and are absorbed by the surrounding shielding structure, and will not hit the human body, so that the harm of the electron beams to the patient during the imaging process is reduced.
In this embodimentReferring to fig. 2 and 3, the imaging target 44 and the therapeutic target 43 are sequentially located on the propagation path of the MV-grade electron beam emitted from the magnetic deflection system 42. The imaging target 44 has a radiation surface 440 for receiving the electron beam of KV class, and the radiation surface 440 forms an acute angle with the propagation path of the electron beam of MV class emitted from the magnetic deflection system 42. In the imaging mode, when the electron beam in KV level reaches the radiation surface 440, it strikes the radiation surface 440 to generate imaging rays, which can be radiated outside at the radiation surface 440. By adjusting the included angle between the radiation surface 440 and the propagation path of the KV-grade electron beam, most of the imaging rays radiated from the radiation surface 440 can be emitted toward the ray exit port of the shielding chamber and irradiated on the human body to obtain a clearer image; in the treatment mode, the MV grade electron beam emitted by the electron emission device 41 can pass through the imaging target 44 and enter the magnetic deflection system 42, and then is deflected to be emitted, and then passes through the imaging target 44 again to reach the treatment target 43, and bombards the treatment target 43 to generate MV grade treatment rays. In order to allow transmission of the MV-level electron beam from the imaging target 44, the imaging target 44 is made of a low-density metal or alloy material, and the density of the imaging target 44 is 8g/cm or less3The upper limit value corresponds approximately to the density of stainless steel. Thus, the KV-level electron beam having a lower energy is greatly obstructed when reaching the imaging target 44 and instantaneously decelerates to generate KV-level imaging rays, while the MV-level electron beam having a higher energy can be transmitted through the imaging target 44 without being greatly attenuated in energy. To meet the density requirements described above, the material of the imaging target 44 may be stainless steel, graphite, or aluminum. In the embodiment, the imaging target 44 is made of graphite, the KV-grade electron beam strikes the imaging target 44 made of graphite, and the transmission amount is small, so that most of the KV-grade electron beam is used for exciting the KV-grade imaging ray, and the KV-grade imaging ray can sufficiently meet the imaging requirement.
In imaging mode, the location of the imaging target 44 can affect the positional accuracy of the tumor location. In view of this, in the present embodiment, since the MV-grade electron beam can directly pass through the imaging target 44, the imaging target 44 can be fixedly disposed on the propagation path of the KV-grade electron beam between the electron beam emitting device 41 and the magnetic deflection yoke 42. This ensures that the imaging target 44 does not need to be moved repeatedly during each imaging positioning, and the fixed position of the imaging target 44 can effectively reduce the large movement error caused by the movement of the target, so as to realize the accurate positioning of the tumor position. Specifically, in this embodiment, the imaging target 44 is fixed at the intersection of the propagation paths of the MV-grade electron beam entering and exiting the magnetic deflection system 42, so that both the imaging radiation and the therapeutic radiation can exit from the same radiation exit port of the shielded room.
In addition, as a modification, there may be: the imaging target is arranged on the movable target holder, and the imaging target is moved to the position with the minimum imaging error when imaging and positioning are carried out each time.
In addition to the above structure, the electron linear accelerator of the present embodiment further includes: a primary collimator and a secondary collimator (not shown) are located in turn downstream of the treatment target 43 along the propagation path of the MV-grade electron beam emitted from the magnetic deflection system 42. The primary collimator and the secondary collimator work together to generate a radiation field with a certain shape and contour, and the contour of the therapeutic ray emitted from the irradiation head is adjusted to enable the range contour of the ray irradiated on the tumor to be basically the same as the shape of the tumor. The primary collimator is used for adjusting the range of the radiation field and providing the maximum radiation field range, and the secondary collimator is used for adjusting the shape profile of the radiation field.
In addition, an ionization chamber is arranged between the primary collimator and the secondary collimator and is used for measuring the dosage of the imaging rays emitted from the primary collimator so as to ensure the imaging quality or measuring the energy of the treatment rays so as to ensure effective and accurate treatment.
Although the present invention is disclosed above, the present invention is not limited thereto. Various changes and modifications may be effected therein by one skilled in the art without departing from the spirit and scope of the invention as defined in the appended claims.
Claims (10)
1. An electron linear accelerator, comprising:
the electron beam emitting device is used for emitting a KV-level electron beam or an MV-level electron beam;
the MV-grade electron beams can enter the magnetic deflection system, and are deflected in the magnetic deflection system and then emitted;
the treatment target is used for receiving the MV-grade electron beams emitted from the magnetic deflection system, and the MV-grade electron beams bombard the treatment target to generate treatment rays; and the number of the first and second groups,
the imaging target is positioned on a propagation path of a KV-grade electron beam between the electron beam emitting device and the magnetic deflection system and used for receiving the KV-grade electron beam, the KV-grade electron beam bombards the imaging target to generate imaging rays, and the imaging target is configured to be penetrated by the MV-grade electron beam.
2. The electron linear accelerator of claim 1, wherein the imaging target is fixed on a propagation path of the KV-grade electron beam between the electron beam emitting device and the magnetic deflection system, and the imaging target is configured to be passed through by the MV-grade electron beam.
3. The electron linear accelerator of claim 2, wherein the imaging target is located at the intersection of the propagation paths of the MV grade electron beam into and out of the magnetic deflection system.
4. The electron linac of claim 2, wherein said imaging target and therapeutic target are sequentially located on the propagation path of the MV grade electron beam emerging from said magnetic deflection system.
5. The electron linear accelerator of claim 4, wherein the imaging target has a radiation surface for receiving the electron beam of KV level, the radiation surface forms an acute angle with the propagation path of the electron beam of MV level emitted from the magnetic deflection system, and the propagation path is toward the side of the therapeutic target;
the KV-level electron beams bombard the radiation surface to generate imaging rays, and the imaging rays are radiated on the radiation surface.
6. The electron linac of claim 1, wherein the density range of the imaging target is: less than or equal to 8g/cm 3.
7. The electron linear accelerator of claim 6, wherein the material of the imaging target is stainless steel, aluminum, or graphite.
8. The electron linear accelerator of claim 2, wherein the electron beam emitting means comprises: an electron gun;
and the accelerating tube is positioned between the electron gun and the imaging target and is communicated with the electron gun.
9. The electron linac of claim 8, further comprising:
and the primary collimator and the secondary collimator are sequentially positioned downstream of the treatment target along the propagation path of the MV-grade electron beam emitted from the magnetic deflection system.
10. The electron linear accelerator of claim 9, further comprising: an ionization chamber located between the primary collimator and the secondary collimator.
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| CN108478941B (en) * | 2018-04-28 | 2021-04-27 | 西安大医集团股份有限公司 | Radiotherapy device |
| 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 |
| AU2020318462A1 (en) * | 2019-07-19 | 2022-02-17 | Shine Technologies, Llc | Gas jet deflection in pressurized systems |
| DE102020212200B3 (en) * | 2020-09-28 | 2022-03-17 | Siemens Healthcare Gmbh | Method for electron beam deflection using a magnet unit of a linear accelerator system, linear accelerator system, MeV radiation device and computer program product for carrying out the method |
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