CN115569312A - Beam control method for particle radiotherapy device and beam device - Google Patents
Beam control method for particle radiotherapy device and beam device Download PDFInfo
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- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1048—Monitoring, verifying, controlling systems and methods
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- A—HUMAN NECESSITIES
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- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1042—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
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1048—Monitoring, verifying, controlling systems and methods
- A61N5/1064—Monitoring, verifying, controlling systems and methods for adjusting radiation treatment in response to monitoring
- A61N5/1065—Beam adjustment
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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
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
- A61N2005/1087—Ions; Protons
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Abstract
The present disclosure provides a beam control method and apparatus for a particle radiotherapy apparatus, the method comprising: acquiring the length of the deflection magnet and a second horizontal distance from the edge of the deflection magnet to the target area; setting the distance from the exit point of each particle beam to a target area, the incident angle and the movement track radius of each particle beam according to the treatment requirement of the particle radiotherapy device; for each particle beam, calculating the incident point position of the particle beam according to the length of the deflection magnet, the second horizontal distance, the distance from the emergent point of the particle beam to the target area, the incident angle of the particle beam and the motion track radius of the particle beam; for each particle beam, calculating the position of an exit point of the particle beam according to the distance from the exit point of the particle beam in the magnetic field area of the bunching magnet to the target and the incident angle of the particle beam; determining the boundary of a magnetic field area of the bunching magnet according to the positions of the incident points and the positions of the emergent points of all particle beams; the corresponding magnetic field area is configured according to the boundary to control the particle beam to be introduced into the target area.
Description
Technical Field
The present disclosure relates to the field of particle therapy and proton heavy ion radiotherapy, and more particularly, to a beam control method and a beam apparatus for a particle radiotherapy apparatus.
Background
Radiotherapy, which is called radiotherapy for short, is a special method for local treatment of tumor by using the radiation effect of radiation. The radiation generally used for radiotherapy is mainly divided into two major categories, the first category is radiotherapy by utilizing natural alpha ions, beta electrons, gamma photons and the like generated by isotope decay; the second type is radiotherapy using a charged particle beam such as a photon beam, an electron beam, a proton beam, or a heavy particle beam generated by an accelerator. In order to reduce the radioactive damage of the normal tissues and organs by the charged particle beam, it is generally necessary to perform the treatment by irradiating the charged particle beam from a plurality of directions.
In a conventional beam control method, the deflection points of all particle beams in a deflection magnet are positioned at the same point, and the shape of a beam focusing magnet is designed based on the positioning. However, in practice, when a deflection electromagnet is used to deflect the high-energy particle beam, the opposite extension lines of the rays do not converge at one point, that is, the equivalent deflection starting point of the high-energy particle beam actually deflected is not at the center of the deflection electromagnet, and the shape of the effective magnetic field of the beam-focusing electromagnet designed according to the scheme to control the particle beam cannot make the charged particle beam accurately converge at the equivalent treatment central point.
In addition, in the conventional beam control method, the intensity of the beam-focusing magnet is constant, and in this case, the large-angle deflection angle orbit and the small-angle deflection orbit of the charged particles overlap, so that the large-angle deflection of the charged particles cannot be realized, that is, the irradiation of the whole azimuth can not be realized without moving the patient, and the tumor (target) deformation easily occurs when the irradiation of the whole azimuth is performed by the moving patient.
Disclosure of Invention
In view of the above technical problems, the present disclosure provides a beam control method and device for a particle radiation therapy device, which are used to at least partially solve the technical problems that the existing beam control method cannot accurately converge a charged particle beam to an equivalent therapy center point, and cannot achieve omnidirectional irradiation without moving a patient.
Based on this, a first aspect of the present disclosure provides a beam control method for a particle radiation therapy apparatus, the particle radiation therapy apparatus including a deflection magnet and a beam focusing magnet, a particle beam being introduced into a target region after being deflected twice by the deflection magnet and the beam focusing magnet, the beam control method including: acquiring the length of the deflection magnet and a second horizontal distance from the edge of the deflection magnet close to the bunching magnet to the target area; setting the distance from an exit point of each particle beam in a bunching magnet magnetic field area to a target area according to the treatment requirement of a particle radiation treatment device, the incident angle of each particle beam relative to the target area and the movement track radius of each particle beam in the magnet magnetic field area; for each particle beam, calculating the incident point position of the particle beam in the magnetic field area of the beam concentration magnet according to the length of the deflection magnet, the second horizontal distance, the distance from the emergent point of the particle beam in the magnetic field area of the beam concentration magnet to the target area, the incident angle of the particle beam relative to the target area and the motion track radius of the particle beam in the magnetic field area of the beam concentration magnet; for each particle beam, calculating the position of an exit point of the particle beam in the magnetic field area of the bunching magnet according to the distance from the exit point of the particle beam in the magnetic field area of the bunching magnet to the target and the incident angle of the particle beam relative to the target; determining the boundary of a bunching magnet magnetic field area according to a first track formed by all particle beam incidence point positions and a second track formed by all particle beam emergent point positions; and controlling the particle beam to be introduced into the target area according to the magnetic field area of the bunching magnet corresponding to the boundary configuration.
According to the embodiment of the present disclosure, the beam current control method further includes: acquiring the charge quantity and momentum of charged particles of each particle beam in the beam; for each particle beam, calculating the magnetic induction intensity required by the deflection of the particle beam in the bunching magnet according to the radius of the motion track of the particle beam in the magnetic field area of the bunching magnet and the charge quantity and momentum of the charged particles of the particle beam; and controlling the deflection tracks of the particle beams with different incidence angles not to be overlapped in the beam bunching magnet according to the magnetic induction intensity corresponding to the particle beams with different incidence angles.
According to the embodiment of the present disclosure, calculating the incident point position of the particle beam in the magnetic field area of the beam focusing magnet according to the length of the deflecting magnet, the second horizontal distance, the distance from the exit point of the particle beam in the magnetic field area of the beam focusing magnet to the target, the incident angle of the particle beam relative to the target, and the radius of the motion trajectory of the particle beam in the magnetic field area of the beam focusing magnet specifically includes: calculating the deflection angle of each particle beam in the deflection magnet according to the length of the deflection magnet, the second horizontal distance, the distance from the exit point of the particle beam in the magnetic field area of the bunching magnet to the target area, the incident angle of each particle beam relative to the target area and the movement track radius of each particle beam in the magnetic field area of the magnet; and for each particle beam, calculating the position of the incident point of the particle beam in the magnetic field area of the bunching magnet according to the distance from the emergent point of the particle beam in the magnetic field area of the bunching magnet to the target, the incident angle of the particle beam relative to the target, the motion track radius of the particle beam in the magnetic field area of the magnet and the deflection angle of the particle beam in the deflection magnet.
According to an embodiment of the present disclosure
Calculating the deflection angle of each particle beam in the deflection magnet, wherein i is the number of the particle beam, phi i For the deflection angle, R, of the i-th beam in the deflection magnet 1 For the distance, R, from the exit point of each particle beam in the magnetic field area of the magnet to the target i2 Is the track radius, L, of the ith beam in the bunching magnet i1 A first horizontal distance theta from the deflection point of the ith beam to the edge of the deflection magnet near the bunching magnet i Is the incident angle, L, of the ith beam 2 A second horizontal distance, L a length of the deflection magnet, R i Is the straight-line distance from the deflection center of the ith beam particle in the deflection magnet to the incident point of the bunching magnet.
According to an embodiment of the present disclosure
Calculating the position of the incident point of the particle beam, wherein i is the number of the particle beam, (x) i1 ，y i1 ) Is the incident point position, R, of the ith beam 1 For the distance, R, of the exit point of each particle beam to the target i2 Is the radius of motion trajectory of the ith beam of particle beam i For the deflection angle, theta, of the i-th beam in the deflection magnet i Is the incident angle of the ith beam.
According to an embodiment of the present disclosure
Calculating the position of an emergent point of the particle beam, wherein i is the number of the particle beam, (x) i2 ，y i2 ) Is the exit point position, R, of the i-th beam 1 For the distance, θ, of the exit point of each particle beam to the target i Is the incident angle of the ith beam.
According to an embodiment of the present disclosure
Calculating the magnetic induction intensity required by the deflection of the particle beams with different incident angles in the bunching magnet, wherein i is the number of the particle beams, and B i Adapted magnetic induction, R, for an i-th particle beam i2 Radius of motion trajectory of ith beam in bunching magnet i Is the momentum of the charged particles of the i-th beam, q i The charge amount of the charged particles of the ith beam.
The second aspect of the present disclosure also provides a beam control device for a particle radiotherapy device, the particle radiotherapy device includes a deflection magnet and a beam focusing magnet, a particle beam is deflected twice by the deflection magnet and the beam focusing magnet and then introduced into a target region, the beam control device includes: the first acquisition module is used for acquiring the length of the deflection magnet and a second horizontal distance from the edge of the deflection magnet close to the beam bunching magnet to the target area; the setting module is used for setting the distance from an exit point of each particle beam in the beam-focusing magnet magnetic field area to the target area, the incident angle of each particle beam relative to the target area and the motion track radius of each particle beam in the magnet magnetic field area according to the treatment requirement of the particle radiation treatment device; the first calculation module is used for calculating the incident point position of the particle beam in the magnetic field area of the bunching magnet according to the length of the deflection magnet, the second horizontal distance, the distance from the emergent point of the particle beam in the magnetic field area of the bunching magnet to the target area, the incident angle of the particle beam relative to the target area and the motion track radius of the particle beam in the magnetic field area of the bunching magnet for each particle beam; the second calculation module is used for calculating the position of an exit point of the particle beam in the magnetic field area of the bunching magnet according to the distance from the exit point of the particle beam in the magnetic field area of the bunching magnet to the target and the incident angle of the particle beam relative to the target for each particle beam; the determining module is used for determining the boundary of the magnetic field area of the bunching magnet according to first tracks formed by the positions of all particle beam incidence points and first tracks formed by the positions of all particle beam exit points; and the first control module is used for controlling the particle beam to be introduced into the target area according to the magnetic field area corresponding to the boundary configuration.
According to the embodiment of the present disclosure, the beam control apparatus further includes: the second acquisition module is used for acquiring the charge quantity and momentum of the charged particles of each particle beam in the beam; the third calculation module is used for calculating the magnetic induction intensity required by the deflection of the particle beam in the bunching magnet according to the motion track radius of the particle beam in the magnetic field area of the bunching magnet and the charge quantity and momentum of the charged particles of the particle beam; and the second control module is used for controlling the deflection tracks of the particle beams with different incidence angles in the beam bunching magnet not to be overlapped according to the magnetic induction intensities corresponding to the particle beams with different incidence angles.
Drawings
The above and other objects, features and advantages of the present disclosure will become more apparent from the following description of the embodiments of the present disclosure with reference to the accompanying drawings, in which:
fig. 1 schematically shows a structural view of a particle radiation therapy device provided by an embodiment of the present disclosure.
Fig. 2 schematically illustrates a beam current control method for a particle radiation therapy device according to an embodiment of the present disclosure.
Fig. 3 schematically shows a specific flowchart of operation S203 provided by the embodiment of the present disclosure.
Fig. 4 schematically illustrates a diagram of a motion trajectory of charged particles in a deflecting magnet provided by an embodiment of the present disclosure.
Fig. 5 schematically illustrates a deflection trajectory diagram of charged particles in a particle beam therapy device provided by an embodiment of the present disclosure.
Fig. 6 schematically shows a flow chart of a beam current control method for a particle radiation therapy device according to another embodiment of the present disclosure.
Fig. 7 schematically shows a block diagram of a beam current control apparatus for a particle radiation therapy apparatus according to an embodiment of the present disclosure.
Fig. 8 schematically shows a block diagram of a beam control apparatus for a particle radiation therapy apparatus according to another embodiment of the present disclosure.
Detailed Description
To make the objects, technical solutions and advantages of the present disclosure more apparent, the present disclosure will be described in further detail below with reference to specific embodiments and the accompanying drawings. It is to be understood that the described embodiments are only a few, and not all, of the disclosed embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments disclosed herein without making any creative effort, shall fall within the protection scope of the present disclosure.
The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the disclosure. The terms "comprises," "comprising," and the like, as used herein, specify the presence of stated features, steps, operations, and/or components, but do not preclude the presence or addition of one or more other features, steps, operations, or components.
In the present disclosure, unless otherwise expressly stated or limited, the terms "mounted," "connected," "secured," and the like are to be construed broadly and can, for example, be fixedly connected, detachably connected, or integral; can be mechanically connected, electrically connected or can communicate with each other; either directly or indirectly through intervening media, either internally or in any other suitable relationship. The specific meaning of the above terms in the present disclosure can be understood by those of ordinary skill in the art as appropriate.
In the description of the present disclosure, it is to be understood that the terms "longitudinal," "length," "circumferential," "front," "rear," "left," "right," "top," "bottom," "inner," "outer," and the like are used in the orientation or positional relationship indicated in the drawings for convenience in describing the present disclosure and for simplicity in description, and are not intended to indicate or imply that the referenced subsystems or elements must have a particular orientation, be constructed and operated in a particular orientation, and thus, are not to be construed as limiting the present disclosure.
Throughout the drawings, like elements are represented by like or similar reference numerals. Conventional structures or constructions will be omitted when they may obscure the understanding of the present disclosure. And the shapes, sizes and positional relationships of the components in the drawings do not reflect the actual sizes, proportions and actual positional relationships. Furthermore, in the claims, any reference signs placed between parentheses shall not be construed as limiting the claim.
Similarly, in the above description of exemplary embodiments of the disclosure, various features of the disclosure are sometimes grouped together in a single embodiment, figure, or description thereof for the purpose of streamlining the disclosure and aiding in the understanding of one or more of the various disclosed aspects. Reference to the description of the terms "one embodiment," "some embodiments," "an example," "a specific example," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the disclosure. In this specification, the schematic representations of the terms used above do not necessarily refer to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples.
Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of the present disclosure, "a plurality" means at least two, e.g., two, three, etc., unless explicitly defined otherwise.
Fig. 1 schematically shows a structural view of a particle radiation therapy device provided by an embodiment of the present disclosure.
As shown in fig. 1, the particle radiotherapy apparatus may include, for example, a deflection magnet a and a beam focusing magnet B. After the high-energy charged particle beams pass through the deflection magnet A, the tracks deflect and enter the beam bunching magnet B after passing through the linear tracks, and after the tracks deflect again, the charged particle beams are introduced to the center (treatment central point) of a tumor target area. The deflection angle phi of the charged particle beam can be controlled by designing the magnetic field area boundary of the beam-focusing magnet B and controlling the field intensity of the magnetic field of the deflection magnet A and the magnetic induction of the beam-focusing magnet B i And further controlling the irradiation angle theta i To realize radiotherapy by irradiation of charged particle beams in all azimuth angles.
Fig. 2 schematically illustrates a flow chart of a beam current control method for a particle radiation therapy device according to an embodiment of the present disclosure.
As shown in fig. 2, the beam control method for the particle radiotherapy apparatus may include, for example, operations S201 to S205.
In operation S201, a length of the deflection magnet, a second horizontal distance from the deflection magnet to the target area near an edge of the bunching magnet, is obtained.
In operation S202, the distance from the exit point of each particle beam in the magnetic field area of the beam focusing magnet to the target, the incident angle of each particle beam with respect to the target, and the radius of the motion trajectory of each particle beam in the magnetic field area of the beam focusing magnet are set according to the treatment requirements of the particle radiation treatment apparatus.
In operation S203, for each particle beam, an incident point position of the particle beam in the magnetic field region of the beam focusing magnet is calculated according to the length of the deflection magnet, the second horizontal distance, the distance from the exit point of the particle beam in the magnetic field region of the beam focusing magnet to the target, the incident angle of the particle beam with respect to the target, and the radius of the motion trajectory of the particle beam in the magnetic field region of the beam focusing magnet.
In operation S204, for each particle beam, an exit point position of the particle beam in the magnetic field area of the bunching magnet is calculated according to a distance from the exit point of the particle beam in the magnetic field area of the bunching magnet to the target and an incident angle of the particle beam relative to the target.
In operation S205, the boundaries of the bunching magnet magnetic field regions are determined according to the first trajectories formed at all the particle beam incident point positions and the second trajectories formed at all the particle beam exit point positions, and the corresponding bunching magnet magnetic field regions are configured according to the boundaries to control the introduction of the particle beam into the target region.
According to the beam control method for the particle beam treatment device, provided by the embodiment of the disclosure, the actual physical parameters of the deflection magnet and the bunching magnet are obtained, the incident angle, the movement track radius and the distance from the exit point to the center of the target area of each particle beam are set according to treatment requirements, the boundary of the magnetic field area of the bunching magnet is determined according to the incident point position and the exit point position of each particle beam in the magnetic field area of the bunching magnet calculated according to the parameters, and errors caused by setting the magnetic field boundary by equivalently setting the deflection points of all the particle beams as the same deflection point are corrected. Thereby improving the combing control precision of the particle radiotherapy device and improving the treatment effect.
Fig. 3 schematically shows a specific flowchart of operation S203 provided by the embodiment of the present disclosure.
As shown in fig. 3, operation S203 may include, for example, operations S301 to S302.
In operation S301, a deflection angle of each particle beam in the deflection magnet is calculated according to the length of the deflection magnet, the second horizontal distance, the distance from the exit point of each particle beam in the magnetic field region of the beam focusing magnet to the target, the incident angle of each particle beam with respect to the target, and the radius of the motion trajectory of each particle beam in the magnetic field region of the magnet.
In operation S302, for each particle beam, an incident point position of the particle beam in the magnetic field area of the bunching magnet is calculated according to a distance from an exit point of the particle beam in the magnetic field area of the bunching magnet to the target, an incident angle of the particle beam with respect to the target, a moving track radius of the particle beam in the magnetic field area of the magnet, and a deflection angle of the particle beam in the deflection magnet.
The following further introduces the three-dimensional execution principle of the beam control method according to the embodiment of the present disclosure, specifically as follows:
fig. 4 schematically illustrates a diagram of a motion trajectory of charged particles in a deflecting magnet provided by an embodiment of the present disclosure.
As shown in FIG. 4, when the deflection magnet A deflects the high-energy particle beam, the deflection point Q corresponding to the particle beam deflected at different angles i Different position, deflection point Q i The first horizontal distance to the edge of the deflection magnet is also changed, and the deflection points Q corresponding to the particle beams with different angles are deflected i A first horizontal distance L from the edge of the deflection magnet i1 Angle phi with respect to the deflection i Satisfies the following relationship:
where i denotes the number of the particle beam at different deflection angles, [ phi ] i L is the deflection angle of the ith beam, and L is the length of the deflection magnet.
Fig. 5 schematically illustrates a diagram of deflection trajectories of charged particles in a particle beam therapy device provided by an embodiment of the present disclosure.
As shown in fig. 5, the particle beam is transported to the deflection magnet a, deflected by the deflection magnet a, reaches the beam focusing magnet along different paths, deflected by the focusing magnet B, and enters the isocenter O, i.e., the equivalent patient target, in different directions. Arrival of the energetic charged particle beam at P 1 Point, entering bunching magnetFrom P after being deflected by Lorentz force 2 Spot-emitting the bunching magnet B. P corresponding to particle beams incident at all different angles 1 、P 2 The point tracks are respectively the boundaries of the left and inner effective magnetic fields of the bunching magnet B, the boundary of the right effective magnetic field of the bunching magnet can contain the rightmost charged ion beam track, and the shape does not need other special requirements, therefore, the point tracks can be determined according to the requirements
Calculating the deflection angle of each particle beam in the deflection magnet, wherein i is the number of the particle beam, phi i For the deflection angle, R, of the i-th beam in the deflection magnet 1 For the distance from the exit point of each particle beam in the magnetic field area of the magnet to the target, i.e. the distance from the exit point of each particle beam to the target, R is the same i2 Is the radius of the trajectory of the ith beam in the bunching magnet, L i1 A first horizontal distance theta from the deflection point of the ith beam to the edge of the deflection magnet near the bunching magnet i Is the incident angle, L, of the ith beam 2 A second horizontal distance, L a length of the deflection magnet, R i The linear distance from the deflection center of the ith beam particle in the deflection magnet to the incident point of the beam bunching magnet
Then according to
Calculating the position of the incident point of the particle beam, wherein i is the number of the particle beam, (x) i1 ，y i1 ) Is the incident point position, R, of the ith particle beam 1 For the distance, R, of the exit point of each particle beam to the target i2 Is the trajectory radius of the ith beam, phi i Is the deflection angle, theta, of the i-th beam i The angle of incidence of the ith beam.
Then according to
Calculating the position of the incident point of the particle beam, wherein i is the number of the particle beam, (x) i2 ，y i2 ) Is the exit point position, R, of the i-th beam 1 For the distance, theta, from the exit point of each particle beam to the target i Is the incident angle of the ith beam.
Based on the calculation process, the incident points P corresponding to the particle beams with different deflection angles can be obtained 1 And an exit point P 2 Based on the position of the point of incidence P 1 And a point of departure P 2 The trajectory of the position of the bunching magnet can then determine the boundaries of the effective magnetic field of the bunching magnet, and based on the determined boundaries of the effective magnetic field, accurate control of different particle beams can be achieved.
On the basis of the above embodiments, the embodiments of the present disclosure also provide beam current control for a particle radiation therapy apparatus.
Fig. 6 schematically shows a flow chart of a beam current control method for a particle radiation therapy device according to another embodiment of the present disclosure.
As shown in fig. 6, the beam control method for the particle radiotherapy apparatus may further include, for example, operations S601 to S603.
In operation S601, a charge amount and momentum of charged particles of each particle beam in the beam are acquired.
In operation S602, for each particle beam, a magnetic induction required for deflecting the particle beam in the bunching magnet is calculated according to a radius of a motion trajectory of the particle beam in a magnetic field region of the bunching magnet and a charge amount and an momentum of charged particles of the particle beam.
In operation S603, the deflection trajectories of the particle beams at different incident angles are controlled not to overlap in the bunching magnet according to the magnetic induction intensities corresponding to the particle beams at different incident angles.
In the disclosed embodiment, can be according to
Calculating the magnetic induction intensity required by the deflection of particle beams with different incident angles in the bunching magnet, wherein i is the number of the particle beams, and B i For matched magnetic induction, R, of the ith beam i2 Radius of motion of the ith beam in the bunching magnet, P i Is the momentum of the charged particles of the i-th beam, q i The charge amount of the charged particles of the ith beam.
According to the embodiment of the disclosure, on the basis of the setting of the effective boundary magnetic field, the particle beams with different incident angles are further matched with corresponding magnetic induction intensities to control that the deflection tracks of different particle beams in the beam converging magnet are not overlapped and are not influenced mutually, so that 360-degree omnibearing charged particle beam irradiation treatment on a target area can be realized, the movement of a patient is reduced, and the risk of target deformation caused by moving the patient is further reduced.
Based on the same inventive concept, the embodiment of the disclosure also provides a beam control device for a particle radiation therapy device.
Fig. 7 schematically illustrates a block diagram of a beam control apparatus for a particle radiation therapy apparatus according to an embodiment of the present disclosure.
As shown in fig. 7, the beam current control apparatus 700 may include, for example, a first obtaining module 710, a setting module 720, a first calculating module 730, a second calculating module 740, a determining module 750, and a first control module 760.
And the first acquisition module is used for acquiring the length of the deflection magnet and the second horizontal distance from the edge of the deflection magnet close to the beam bunching magnet to the target area.
And the setting module is used for setting the distance from the exit point of each particle beam in the beam-focusing magnet magnetic field area to the target area, the incident angle of each particle beam relative to the target area and the motion track radius of each particle beam in the magnet magnetic field area according to the treatment requirement of the particle radiation treatment device.
And the first calculation module is used for calculating the position of the incident point of the particle beam in the magnetic field area of the bunching magnet according to the length of the deflection magnet, the second horizontal distance, the distance from the emergent point of the particle beam in the magnetic field area of the bunching magnet to the target area, the incident angle of the particle beam relative to the target area and the motion track radius of the particle beam in the magnetic field area of the bunching magnet.
And the second calculation module is used for calculating the position of the emergent point of the particle beam in the magnetic field area of the bunching magnet according to the distance from the emergent point of the particle beam in the magnetic field area of the bunching magnet to the target and the incident angle of the particle beam relative to the target for each particle beam.
And the determining module is used for determining the boundary of the magnetic field area of the bunching magnet according to a first track formed by the positions of all particle beam incident points and a second track formed by the positions of all particle beam emergent points.
And the first control module is used for controlling the particle beam to be introduced into the target area according to the magnetic field area of the bunching magnet corresponding to the boundary configuration.
Fig. 8 schematically shows a block diagram of a beam control apparatus for a particle radiation therapy apparatus according to another embodiment of the present disclosure.
As shown in fig. 8, the beam current control apparatus 700 may further include, for example, a second obtaining module 770, a third calculating module 780, and a second control module 790.
And the second acquisition module is used for acquiring the charge quantity and momentum of the charged particles of each particle beam in the beam.
And the third calculation module is used for calculating the magnetic induction intensity required by the deflection of the particle beam in the bunching magnet according to the motion track radius of the particle beam in the magnetic field area of the bunching magnet and the charge quantity and momentum of the charged particles of the particle beam.
And the second control module is used for controlling the deflection tracks of the particle beams with different incidence angles in the beam bunching magnet not to be overlapped according to the magnetic induction intensities corresponding to the particle beams with different incidence angles.
It should be noted that the beam control apparatus portion for a particle radiation therapy apparatus of the present disclosure corresponds to the beam control method portion for a particle radiation therapy apparatus in the embodiments of the present disclosure, and the specific implementation details and the technical effects thereof are also the same, and are not described herein again.
The above-mentioned embodiments are intended to illustrate the objects, aspects and advantages of the present disclosure in further detail, and it should be understood that the above-mentioned embodiments are only illustrative of the present disclosure and are not intended to limit the present disclosure, and any modifications, equivalents, improvements and the like made within the spirit and principle of the present disclosure should be included in the scope of the present disclosure.
Claims (9)
1. A beam control method for a particle radiation therapy device, the particle radiation therapy device comprising a deflection magnet and a beam focusing magnet, the particle beam being introduced into a target region after being deflected twice by the deflection magnet and the beam focusing magnet, the beam control method comprising:
acquiring the length of the deflection magnet and a second horizontal distance from the edge of the deflection magnet close to the bunching magnet to the target area;
setting the distance from the exit point of each particle beam in the magnetic field area of the beam-focusing magnet to the target area, the incident angle of each particle beam relative to the target area and the motion track radius of each particle beam in the magnetic field area of the magnet according to the treatment requirement of the particle radiation treatment device;
for each particle beam, calculating the incident point position of the particle beam in the magnetic field area of the bunching magnet according to the length of the deflection magnet, the second horizontal distance, the distance from the emergent point of the particle beam in the magnetic field area of the bunching magnet to the target area, the incident angle of the particle beam relative to the target area and the motion track radius of the particle beam in the magnetic field area of the bunching magnet;
for each particle beam, calculating the position of an exit point of the particle beam in the magnetic field area of the bunching magnet according to the distance from the exit point of the particle beam in the magnetic field area of the bunching magnet to the target and the incident angle of the particle beam relative to the target;
determining the boundary of the magnetic field area of the bunching magnet according to a first track formed by the positions of all particle beam incidence points and a second track formed by the positions of all particle beam emergent points;
and controlling the particle beam to be introduced into the target area according to the magnetic field area of the bunching magnet corresponding to the boundary configuration.
2. The beam control method for a particle radiation therapy apparatus according to claim 1, characterized in that said beam control method further comprises:
acquiring the charge quantity and momentum of charged particles of each particle beam in the beam;
for each particle beam, calculating the magnetic induction intensity required by the deflection of the particle beam in the bunching magnet according to the radius of the motion track of the particle beam in the magnetic field area of the bunching magnet and the charge quantity and momentum of the charged particles of the particle beam;
and controlling the deflection tracks of the particle beams with different incidence angles not to be overlapped in the beam bunching magnet according to the magnetic induction intensity corresponding to the particle beams with different incidence angles.
3. The beam control method for the particle beam radiotherapy device according to claim 1 or 2, wherein the calculating of the incident point position of the particle beam in the magnetic field area of the bunching magnet according to the length of the deflection magnet, the second horizontal distance, the distance from the exit point of the particle beam in the magnetic field area of the bunching magnet to the target, the incident angle of the particle beam relative to the target and the moving track radius of the particle beam in the magnetic field area of the bunching magnet specifically comprises:
calculating the deflection angle of each particle beam in the deflection magnet according to the length of the deflection magnet, the second horizontal distance, the distance from the exit point of each particle beam in the magnetic field area of the beam-focusing magnet to the target area, the incident angle of each particle beam relative to the target area and the motion track radius of each particle beam in the magnetic field area of the magnet;
and for each particle beam, calculating the position of the incident point of the particle beam in the magnetic field area of the bunching magnet according to the distance from the emergent point of the particle beam in the magnetic field area of the bunching magnet to the target area, the incident angle of the particle beam relative to the target area, the motion track radius of the particle beam in the magnetic field area of the bunching magnet and the deflection angle of the particle beam in the deflection magnet.
4. The beam control method for a particle radiation therapy device according to claim 3, characterized in that the beam control method is based on
Calculating the deflection angle of each particle beam in the deflection magnet, wherein i is the number of the particle beam, phi i For the deflection angle, R, of the ith beam in said deflection magnet 1 For the distance, R, from the exit point of each particle beam in the magnetic field area of the magnet to the target i2 Is the radius of the trajectory of the ith beam in the bunching magnet, L i1 A first horizontal distance, θ, from a deflection point of the ith beam to an edge of the deflection magnet near the bunching magnet i Is the incident angle, L, of the ith beam 2 For said second horizontal distance, L is the length of the deflecting magnet, R i The linear distance from the deflection center of the ith beam particle in the deflection magnet to the incident point of the beam bunching magnet.
5. The beam control method for a particle radiation therapy device according to claim 3, characterized in that the beam control method is based on
Calculating the position of the incident point of the particle beam, wherein i is the number of the particle beam, (x) i1 ，y i1 ) Is the incident point position, R, of the ith beam 1 For the distance, R, of the exit point of each particle beam to the target i2 Is the radius of the motion trajectory of the ith beam of particles, phi i Is the deflection angle, theta, of the ith beam in the deflection magnet i The angle of incidence of the ith beam.
6. The beam control method for a particle radiation therapy device according to claim 3, characterized in that the beam control method is based on
Calculating the position of an emergent point of the particle beam, wherein i is the number of the particle beam, (x) i2 ，y i2 ) For the position of the exit point of the i-th beam, a ruler 1 For the distance, θ, of the exit point of each particle beam to the target i Is the incident angle of the ith beam.
7. The beam control method for a particle radiation therapy device according to claim 2, characterized in that the beam control method is based on
Calculating the magnetic induction intensity required by the deflection of the particle beams with different incident angles in the bunching magnet, wherein i is the number of the particle beams, and B i For matched magnetic induction, R, of the ith beam i2 Radius of motion trajectory of ith beam in bunching magnet i Is the momentum of the charged particles of the ith beam, q i The charge amount of the charged particles of the ith beam.
8. A beam control apparatus for a particle radiation therapy apparatus, the particle radiation therapy apparatus including a deflection magnet and a beam focusing magnet, the particle beam being introduced into a target region after being deflected twice by the deflection magnet and the beam focusing magnet, the beam control apparatus comprising:
the first acquisition module is used for acquiring the length of the deflection magnet and a second horizontal distance from the edge of the deflection magnet close to the beam bunching magnet to the target area;
the setting module is used for setting the distance from the exit point of each particle beam in the beam-focusing magnet magnetic field area to the target area, the incident angle of each particle beam relative to the target area and the motion track radius of each particle beam in the magnet magnetic field area according to the treatment requirement of the particle radiation treatment device;
a first calculating module, configured to calculate, for each particle beam, an incident point position of the particle beam in the magnetic field area of the beam focusing magnet according to the length of the deflection magnet, the second horizontal distance, a distance from an exit point of the particle beam in the magnetic field area of the beam focusing magnet to the target, an incident angle of the particle beam with respect to the target, and a motion trajectory radius of the particle beam in the magnetic field area of the beam focusing magnet;
the second calculation module is used for calculating the position of an exit point of the particle beam in the magnetic field area of the bunching magnet according to the distance from the exit point of the particle beam in the magnetic field area of the bunching magnet to the target and the incident angle of the particle beam relative to the target for each particle beam;
the determining module is used for determining the boundary of the bunching magnet magnetic field area according to a first track formed by all particle beam incidence point positions and a second track formed by all particle beam emergent point positions;
and the first control module is used for controlling the particle beam to be introduced into the target area according to the magnetic field area of the bunching magnet corresponding to the boundary configuration.
9. The beam control apparatus for a particle radiation therapy apparatus according to claim 8, further comprising:
the second acquisition module is used for acquiring the charge quantity and momentum of the charged particles of each particle beam in the beam;
the third calculation module is used for calculating the magnetic induction intensity required by the deflection of the particle beam in the bunching magnet according to the motion track radius of the particle beam in the magnetic field area of the bunching magnet and the charge quantity and momentum of the charged particles of the particle beam;
and the second control module is used for controlling the deflection tracks of the particle beams with different incident angles in the beam bunching magnet not to be overlapped according to the magnetic induction intensities corresponding to the particle beams with different incident angles.
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