A radiotherapy device, a photon flash therapy system, and an ultra-high energy electron flash therapy system

Abstract

The embodiments of this specification provide a radiotherapy device, a photon flash therapy system, and an ultra-high-energy electron flash therapy system. The radiotherapy device includes: a beam generating device, a scanning magnet, and a focusing magnet; the beam generating device is used to generate a charged particle beam; the scanning magnet is used to diverge the charged particle beam; and the focusing magnet is used to deflect the charged particle beam diverged by the scanning magnet so that it converges at the treatment center. The photon flash therapy system includes: a beam generating device, a scanning magnet, a focusing magnet, and / or an arc target and a multi-leaf collimator. The ultra-high-energy electron flash therapy system includes: a beam generating device, a scanning magnet, a focusing magnet, and / or at least one diverging magnet.

Description

Technical Field

[0001] This specification relates to the technical field of medical equipment, and in particular to a radiotherapy device, a photon flash therapy system, and an ultra-high energy electron flash therapy system. Background Art

[0002] At present, malignant tumors can usually be treated by irradiation with high-energy accelerated particle beams. When a particle beam is irradiated onto an object, energy (irradiation dose) is imparted to the object along the path of the particle beam inside the object. In the case of concentrating the irradiation dose on a restricted area (lesion) inside the object, the concentration of the irradiation dose can be improved by irradiating the charged particle beam from all directions in such a way that the particle beam and the lesion overlap. One of the common methods is to place the particle beam or particle source on a gantry that can rotate around the patient. This method requires a larger rotating mechanism and a larger working space. Another common method is to place multiple accelerators at different angles around the patient. This method requires multiple devices, which is more expensive and occupies a larger space. Therefore, there is a need for a radiotherapy device that is smaller in size and lower in cost. Summary of the Invention

[0003] One of the embodiments of this specification provides a radiotherapy device, including a beam generating device, a scanning magnet and a focusing magnet; the beam generating device is used to generate a charged particle beam; the scanning magnet is used to diverge the charged particle beam; the focusing magnet is used to deflect the charged particle beam diverged by the scanning magnet to converge on a treatment center point.

[0004] In some embodiments, the focusing magnet includes an inlet and an outlet; the focusing magnet is bent toward the outlet, and the outlet of the focusing magnet is arc-shaped.

[0005] In some embodiments, the charged particle beam is deflected by the focusing magnet and converges on the treatment center point within a range of a central angle greater than 180° with the treatment center point as the center of the circle.

[0006] In some embodiments, the radiotherapy device further includes a curved target, which is disposed at an outlet of the focusing magnet.

[0007] In some embodiments, the charged particle beam strikes the arc-shaped target within a range of a central angle greater than 180° with the treatment center point as the center to generate a photon beam.

[0008] In some embodiments, the radiotherapy device further includes a multi-leaf collimator, which is arc-shaped and disposed at an exit of the focusing magnet.

[0009] In some embodiments, at least one diverging magnet is provided at the outlet of the focusing magnet, and the at least one diverging magnet is movably provided at the outlet of the focusing magnet.

[0010] In some embodiments, the number of the focusing magnets is at least two, and the at least two focusing magnets are adjacent and / or oppositely arranged; when the at least two focusing magnets are oppositely arranged, the outlets of the focusing magnets are opposite.

[0011] One embodiment of this specification provides a photon flash therapy system, including the above-mentioned radiotherapy device, the photon flash therapy system includes: the beam generating device, the scanning magnet, the focusing magnet and / or the arc target and the multi-leaf collimator; wherein the beam generating device includes at least one of a petal accelerator and a cyclotron accelerator.

[0012] One embodiment of this specification provides an ultra-high energy electron flash therapy system, including the above-mentioned radiotherapy device, the ultra-high energy electron flash therapy system includes: the beam generating device, the scanning magnet, the focusing magnet and / or at least one of the diverging magnets; wherein the beam generating device includes at least one of a high gradient radio frequency tube and a cyclotron accelerator. BRIEF DESCRIPTION OF THE DRAWINGS

[0013] This specification will be further described in the form of exemplary embodiments, which will be described in detail with reference to the accompanying drawings. These embodiments are not limiting, and in these embodiments, like numbers represent like structures, wherein:

[0014] Figure 1 is a schematic structural diagram of a radiotherapy device according to some embodiments of this specification;

[0015] Figure 2 is a schematic diagram of charged particle beam deflection according to some embodiments of this specification;

[0016] Figure 3 is a schematic diagram of the positions of diverging magnets according to some embodiments of this specification;

[0017] Figure 4 is a schematic diagram of a radiotherapy device according to another structure shown in some embodiments of this specification;

[0018] Figure 5 is a schematic structural diagram of a curved target and a multi-leaf collimator according to some embodiments of this specification;

[0019] Figure 6 is a side view of a curved target and a multi-leaf collimator according to some embodiments of the present specification. DETAILED DESCRIPTION

[0020] To more clearly illustrate the technical solutions of the embodiments of this specification, the following briefly describes the drawings required for describing the embodiments. Obviously, the drawings described below are merely examples or embodiments of this specification. Those skilled in the art can apply this specification to other similar scenarios based on these drawings without inventive effort. Unless otherwise apparent from the context or otherwise noted, the same reference numerals in the figures represent the same structure or operation.

[0021] As used in this specification and claims, unless the context clearly indicates otherwise, the words "a," "an," "an," and / or "the" do not refer to the singular but also include the plural. Generally speaking, the terms "comprises" and "include" only indicate the inclusion of the steps and elements specifically identified, and these steps and elements do not constitute an exclusive list. A method or apparatus may also include other steps or elements.

[0022] Flash therapy (flash therapy) has been a hot topic in international cancer radiotherapy research in recent years. It uses ultra-high dose rates (typically greater than 100 Gy / s) to deliver the entire therapeutic dose to the target area within a very short time (1-50 milliseconds). Flash therapy produces a flash effect in the body (tumor tissue remains sensitive to radiation while normal tissue becomes resistant). This effect can provide better protection for normal tissue without reducing the effectiveness of radiotherapy on the tumor. Therefore, based on the difference in radiation sensitivity between tumor and normal tissue, flash therapy has a revolutionary advantage in tumor treatment.

[0023] In current flash therapy, in order to deliver doses to the tumor target from multiple angles, devices that can rotate around the patient are usually used, or multiple devices are set up around the patient. However, these devices have disadvantages such as large size and high cost, making them difficult to promote.

[0024] In view of this, some embodiments of the present specification provide a radiotherapy device, which deflects the charged particle beam to multiple angles through a scanning magnet, and then the charged particle beam is incident on the focusing magnet from a larger angle range, and is deflected by the focusing magnet to converge from different angles to the center of the lesion (treatment center point).

[0025] Figure 1Schematic diagram of the structure of the radiotherapy device 100 shown in some embodiments of this specification. The radiotherapy device 100 shown in some embodiments of this specification can be used in ultra-high energy electron flash radiotherapy schemes, that is, ultra-high energy electron beams obtained by accelerating electrons through an accelerator are converged to the tumor location from multiple angles after passing through the radiotherapy device 100 to achieve tumor treatment. The ultra-high energy electron range is 100MeV to 200MeV, the dose rate reaches 30Gy / s, and the treatment depth reaches about 15cm. The radiotherapy device 100 shown in some embodiments of this specification can also be used in radiotherapy schemes using other charged particles (for example, protons). In addition, the radiotherapy device 100 shown in some embodiments of this specification can also be applied to other medical schemes as needed.

[0026] like Figure 1 As shown, the radiotherapy device 100 may include a beam generating device, a scanning magnet 110 and a focusing magnet 120, wherein the beam generating device can generate a charged particle beam; the scanning magnet 110 can be used to diverge the charged particle beam, and divergence means that the charged particle beam originally moving in a certain direction is deflected in multiple directions, that is, deflected at different angles, and the point where the charged particle beam starts to deflect can be set as the deflection starting point, and the deflection angle is φ; the focusing magnet 120 can be used to deflect the charged particle beam diverged by the scanning magnet 110 to converge, and convergence means that the charged particle beams injected from multiple angles are directed to the same point, which is the treatment center point, corresponding to the center point of the lesion in the patient 140, etc.

[0027] The scanning magnet 110 is used to guide the deflection of each charged particle beam. After passing through the scanning magnet 110, the irradiation field of the charged particle beam changes. For example, the irradiation field of the charged particle beam can be changed from a point shape to a strip shape, achieving uniform irradiation within a certain range and dispersing the power density of the charged particle beam.

[0028] In some embodiments, the scanning magnet 110 can sweep the charged particle beam at a certain angle in a certain direction at a certain moment (e.g., time T1), and then sweep it at a certain angle in a certain direction at a next moment (e.g., time T2). The angle corresponds to the magnetic field of the scanning magnet 110. For example, strengthening the magnetic field of the scanning magnet 110 results in a larger deflection angle. In some embodiments, the irradiation field of the charged particle beam can be controlled by controlling the magnetic field of the scanning magnet 110.

[0029] In some embodiments, the scanning magnet 110 may be a two-pole magnet or a multi-pole magnet, such as a quadrupole magnet or a sextupole magnet.

[0030] The focusing magnet 120 is used to deflect charged particle beams incident from multiple angles and converge them at the treatment center point after exiting the focusing magnet 120. The focusing magnet 120 may include an entrance and an exit, and the charged particle beam may be injected from the entrance and emitted from the exit, with the deflection angle of the charged particle beam between the entrance and the exit being θ. Specifically, the entrance of the focusing magnet 120 may be arranged toward the scanning magnet 110, and the exit of the focusing magnet 120 may be arranged toward a lesion, etc., in the patient 140. In some embodiments, the focusing magnet 120 may have an effective magnetic field region 130 that deflects the charged particle beam, and the charged particle beam passing through the effective magnetic field region 130 can converge. In some embodiments, the center line of the focusing magnet 120, the center line of the scanning magnet 110, and the center point of the lesion (treatment center point) may be located on the same straight line. Above the straight line is a first effective magnetic field region 131, and below the straight line is a second effective magnetic field region 132. The particle beam can irradiate the target from an upper angle and a lower angle respectively through the first effective magnetic field region 131 and the second effective magnetic field region 132. If only the upper angle or the lower angle needs to be irradiated, the focusing magnet 120 can also include only one of the first effective magnetic field region 131 or the second effective magnetic field region 132. In some embodiments, the range of the first effective magnetic field region 131 and the second effective magnetic field region 132 can be the same, that is, symmetrical with respect to the center line of the focusing magnet 120, and the obtained irradiation field is also symmetrical with respect to the center line of the focusing magnet 120, such as Figure 1 In addition, the ranges of the first effective magnetic field region 131 and the second effective magnetic field region 132 may also be different. The ranges of the first effective magnetic field region 131 and the second effective magnetic field region 132 may be determined by calculation and the focusing magnet 120 may be designed accordingly.

[0031] In some embodiments, the focusing magnet 120 may include but is not limited to a superconducting magnet, an electromagnet, etc. In a specific embodiment, the focusing magnet 120 may include at least one set of coil pairs, and the at least one set of coil pairs can generate an effective magnetic field region 130 by passing current through the at least one set of coil pairs.

[0032] In some embodiments, after the charged particle beam is injected into the entrance of the focusing magnet 120, it is subjected to the Lorentz force while moving in the magnetic field, causing it to change its direction of motion. When the charged particle beam enters the effective magnetic field region 130 of the focusing magnet 120, it moves in an arc, exiting the focusing magnet 120 from multiple angles and converging at the treatment center. In some embodiments, the charged particle beam is deflected by the focusing magnet 120 so that it converges at the treatment center within a range of an angle greater than 180° (e.g., within a range of 350°, 240°, 195°, etc.) with the treatment center as the center.

[0033] In some embodiments, the scanning magnet 110 and the focusing magnet 120 may be configured according to requirements of the effective magnetic field region 130 . Figure 2 FIG. 1 is a schematic diagram of charged particle beam deflection according to some embodiments of this specification. Figure 2 As shown, the distance between the deflection starting point of the scanning magnet 110 and the entrance can be set as L, and the distance between the deflection starting point of the scanning magnet 110 and the treatment center point can be set as S; the scanning magnet 110 and the focusing magnet 120 satisfy the relationship:

[0034] In some embodiments, the focusing magnet 120 can be set to bend toward the outlet according to the requirements of the effective magnetic field area 130, and the outlet of the focusing magnet 120 can be in an arc shape, which can be an approximate arc shape rather than a strict arc shape. The arc can be centered at the treatment center point, and the corresponding central angle is greater than 180°. Within the arc range, the charged particle beam can be emitted from the focusing magnet 120 from any position of the arc outlet after being deflected by the focusing magnet 120, and then converge at the treatment center point, thereby performing multi-angle surrounding irradiation on the lesion. In some embodiments, the central angle can be the angle between the two particle beams closest to the two ends of the focusing magnet 120 in the rays emitted from the outlet. Since the particle beam will pass through the human body surface during treatment and cause certain damage to the body surface, maximizing the range of passing through the body surface under a given dose rate can effectively reduce the damage to the body surface per unit area. In some embodiments, after a period of treatment, the patient 140 (bed) can be swapped head to tail ( Figure 1 360° treatment can be easily achieved by switching the direction of the lens facing inward and the direction facing outward from the paper.

[0035] In some embodiments, the central angle of the arc of the outlet of the focusing magnet 120 may be 180°-360°. For example, the central angle of the arc of the outlet of the focusing magnet 120 may be 300°. For another example, the central angle of the arc of the outlet of the focusing magnet 120 may be 280°. For another example, the central angle of the arc of the outlet of the focusing magnet 120 may be 240°.

[0036] In some embodiments, the beam generating device may include an accelerator. An accelerator is a device for accelerating a charged particle beam, which uses a certain form of electromagnetic field to accelerate charged particles such as positrons, electrons, protons, and heavy ions to a certain energy. In some embodiments, the beam generating device may include but is not limited to a linear accelerator, a cyclotron, an electrostatic accelerator, a synchrotron, a voltage multiplier, a high-gradient radio frequency tube, and the like. Among them, cyclotrons are mostly used in proton and heavy ion therapy. In some embodiments of the present specification, the use of scanning magnets in conjunction with focusing magnets allows the power density of the charged particle beam to be dispersed and irradiated from multiple angles and over as large an area as possible, enabling the cyclotron to be used in ultra-high energy electron flash therapy.

[0037] Figure 3 Schematic diagram of the position of the diverging magnet 150 according to some embodiments of this specification. In some embodiments, the outlet of the focusing magnet 120 is movably provided with one or more diverging magnets 150, such as Figure 3 As shown, it is used to diverge the charged particle beam passing through the focusing magnet 120.

[0038] The diverging magnet 150 is used to guide the charged particle beam to form a predetermined trajectory, causing the charged particle beam to diverge. The diverging area can cover a designated area, such as the tumor area, thereby achieving full coverage of the tumor area without moving the patient bed. In some embodiments, a diverging magnet 150 can be a pair of dipole magnets or a multi-pole magnet combination capable of deflecting the charged particle beam. For example, a diverging magnet 150 can be a pair of dipole electromagnets with orthogonal deflection directions.

[0039] In some embodiments, one or more diverging magnets 150 can be moved along the outlet of the focusing magnet 120. For example, one or more diverging magnets 150 can be moved along the arc-shaped extension direction of the focusing magnet 120. In some embodiments, one or more diverging magnets 150 can remain stationary during the radiation treatment process, and after a stage of treatment is completed, they can be moved to change position and then continue to the next stage of treatment. In other embodiments, one or more diverging magnets 150 can be moved according to the treatment plan during the radiation treatment process, so that the charged particle beam can be irradiated to a designated area according to the treatment plan to complete the treatment.

[0040] In some embodiments, one or more diverging magnets 150 can be fixedly arranged. For example, one or more diverging magnets 150 can be arranged at both ends and / or in the middle of the outlet of the focusing magnet 120. In a specific embodiment, two fixed diverging magnets 150 can be arranged at the outlet of the focusing magnet 120; wherein, one diverging magnet 150 can be located on the same straight line as the center positions of the scanning magnet 110 and the focusing magnet 120, and the other diverging magnet 150 can be arranged at one end of the outlet of the focusing magnet 120, and the line connecting the diverging magnet 150 and the treatment center point is perpendicular to the straight line where the centers of the scanning magnet 110 and the focusing magnet 120 are located. In another specific embodiment, the two diverging magnets 150 can be fixedly arranged at both ends of the outlet of the focusing magnet 120, and the line connecting the two can be perpendicular to the straight line where the centers of the scanning magnet 110 and the focusing magnet 120 are located.

[0041] In some embodiments, there can be at least two focusing magnets 120, with at least two focusing magnets 120 positioned adjacent to and / or opposite to each other. When at least two focusing magnets 120 are positioned opposite to each other, the outlets of the focusing magnets 120 are positioned opposite to each other. In a specific embodiment, the outlets of the two focusing magnets 120 can be positioned strictly opposite to each other (e.g., the centerlines of the two focusing magnets 120 are collinear) or roughly opposite to each other (e.g., the centerlines of the two focusing magnets 120 are 140°, 150°, etc.), as long as the particle beam can be emitted from the outlet of the focusing magnet 120 to cover a 360° range, thereby achieving 360° irradiation therapy for the patient 140. In some embodiments, more than two focusing magnets 120 can be used, positioned around the patient 140, with the outlets of the focusing magnets 120 all facing the patient 140, thereby achieving 360° irradiation therapy for the patient 140. In some embodiments, each focusing magnet 120 can be configured with a corresponding beam generating device and a scanning magnet 110, so that the particle beam generated by the corresponding beam generating device is emitted from the focusing magnet 120. In some embodiments, two or more focusing magnets 120 may share the same beam generating device and scanning magnet 110 , as long as the particle beam can be emitted from the outlets of the two or more focusing magnets 120 and cover the required range.

[0042] Figure 4 This is a schematic diagram of a radiotherapy device 200 according to another embodiment of this specification. The radiotherapy device 200 according to another embodiment of this specification can be used in photon flash radiotherapy, which treats tumors through photon irradiation. The photon energy range is 6 MV to 15 MV, the dose rate reaches 30 Gy / s, and the treatment depth reaches approximately 15 cm. The radiotherapy device 200 according to another embodiment of this specification can also be used in other particle radiotherapy regimens or other medical treatments as needed, without limitation.

[0043] like Figure 4 As shown, the radiotherapy device 200 may include a beam generating device, a scanning magnet 110 and a focusing magnet 120, wherein the structures and functions of the scanning magnet 110 and the focusing magnet 120 are the same as those in the radiotherapy device 100 and will not be repeated here. The beam generating device may be a petal accelerator, a linear accelerator, a cyclotron accelerator, an electrostatic accelerator, a synchrotron accelerator, a voltage multiplier accelerator, etc. Among them, cyclotron accelerators are mostly used in proton and heavy ion therapy; petal accelerators are rarely used in radiotherapy due to their high power. In some embodiments of the present specification, the power density of the charged particle beam is dispersed and irradiated from multiple angles and as much area as possible by using a scanning magnet in combination with a focusing magnet, thereby eliminating the limitation that high-power petal accelerators are difficult to use for radiotherapy. The radiotherapy device 200 may also include an arc target and a multi-leaf collimator 220. For more information about the arc target and the multi-leaf collimator 220, please refer to Figure 5 and Figure 6 Related description.

[0044] Figure 5 2 is a schematic structural diagram of a curved target 210 and a multi-leaf collimator 220 according to some embodiments of this specification. Figure 6 FIG. 2 is a side view of a curved target 210 and a multi-leaf collimator 220 according to some embodiments of the present disclosure.

[0045] In some embodiments, the radiotherapy device 200 may include a target. A charged particle beam (e.g., an electron beam) impacting the target can generate photons. The target can have various shapes, such as straight or curved. The target shape needs to coordinate with the beam direction of the particle beam, for example, so that the beam strikes the target perpendicular to the target surface to achieve optimal results. In some embodiments, the radiotherapy device 200 may include a curved target 210. The curved target 210 may include a metal target, such as a tungsten target. In some embodiments, the curved target 210 may be positioned at the exit of the focusing magnet 120. After exiting the focusing magnet 120, the electron beam strikes the curved target 210, thereby generating photons. Due to the curved target surface, the focal spot of the charged particle beam on the curved target 210 is not fixed. Furthermore, the curved target surface has a relatively larger area than a straight target surface, which reduces the heat per unit area. Therefore, the curved target surface design facilitates heat dissipation and extends the target's service life.

[0046] In some embodiments, the charged particle beam can strike the arc target 210 with the treatment center point as the center within a range of a central angle greater than 180° (e.g., 190°, 240°, 330°, 350°, etc.) to generate a photon beam. In some embodiments, the arc target 210 can be placed close to the outlet of the focusing magnet 120 and have an angle and length greater than or equal to the outlet of the focusing magnet 120, such as Figure 5 As shown, the electron beam exiting the focusing magnet 120 can all bombard the curved target 210. In some embodiments, the central angle corresponding to the curved edge of the curved target 210 can be greater than 180°. In a specific embodiment, the central angle corresponding to the curved edge of the curved target 210 can be 240°. In this case, the central angle corresponding to the curved edge of the focusing magnet 120 outlet can also be 240°.

[0047] In some embodiments, the radiotherapy apparatus 200 further includes a multi-leaf collimator 220, such as Figure 5 As shown. The multi-leaf collimator 220 is a device for generating a conformal radiation field. In some embodiments, the multi-leaf collimator 220 can be set at the exit of the focusing magnet 120 to conform the photon radiation field so that the radiation field contour is as consistent as possible with the tumor shape to reduce radiation damage to non-tumor areas. Figure 6 shown.

[0048] In some embodiments, the multi-leaf collimator 220 is arc-shaped. The multi-leaf collimator 220 can be disposed close to the arc-shaped target 210 and can have substantially the same angle and length as the arc-shaped target 210 so as to better conform to the shape.

[0049] In some embodiments, the arc target 210 is disposed between the outlet of the focusing magnet 120 and the multi-leaf collimator 220. Figure 5 The electron beam first hits the arc-shaped target 210 to generate photons, which then pass through the multi-leaf collimator 220 to achieve conformal alignment.

[0050] In some embodiments, the curved target 210 and the multi-leaf collimator 220 are removable devices, that is, when photon flash therapy is not needed, the curved target 210 and the multi-leaf collimator 220 can be removed to allow irradiation therapy with a charged particle beam.

[0051] In some embodiments of the radiotherapy device, a driving device can be provided to enable the bed carrying the patient 140 to perform translation, rotation, and other movements. The movement of the bed can be performed after a period of treatment has been implemented, and the bed can also be continuously moved during the treatment process to achieve 360° all-round treatment of the patient 140.

[0052] In some embodiments, a driving device can be provided to drive the radiotherapy device 100 (200) to move, for example, to rotate around the patient, thereby achieving 360° all-round treatment of the patient 140. In some embodiments, the driving device can drive the radiotherapy device 100 (200) to move while outputting, thereby achieving irradiation of the particle beam from one beam angle to another.

[0053] Since the tumor is three-dimensional, different areas of the tumor require different treatment doses, and the dose distribution is uneven. When using the radiotherapy device 100 (200) shown in some embodiments of this specification, the irradiation angle of the radiotherapy device 100 (200) can also be fixed to remain unchanged, and the dose intensity in the irradiation field can be adjusted. For example, by adjusting the number of pulses of the particle beam per unit time, the dose rate of the beam can be adjusted. In some embodiments, different weights can be assigned to the particle beam according to the three-dimensional shape of the lesion and the anatomical relationship with the relevant endangered organ, so that an optimized, uneven intensity distribution is generated in the same irradiation field, so that the beam flux through the endangered organ is reduced, while the beam flux in other parts is increased.

[0054] The beneficial effects that may be brought about by the radiotherapy device provided in some embodiments of this specification include but are not limited to: (1) The radiotherapy device includes a scanning magnet and a focusing magnet, which has a simple structure, a compact structure, a small size and a low cost; (2) By designing the focusing magnet, the particle beam converges at an angle exceeding 180° in the lesion area, thereby reducing the beam dose received by the human body per unit area, thereby reducing the damage to the human body. In addition, since the beam can contact the human body over a larger area, the device does not need to rotate around the patient during treatment, thereby reducing the space required for the device to work; (3) By designing a larger arc-shaped target, the heat dissipation and life problems of the target under high-power electron beams are solved; (4) By designing an arc-shaped multi-leaf collimator, it is convenient to conform to the shape, so that the beam irradiation area is consistent with the lesion area, thereby reducing the damage to the human body. It should be noted that different embodiments may produce different beneficial effects. In different embodiments, the beneficial effects that may be produced may be any one or a combination of the above, or any other possible beneficial effects.

[0055] While the basic concepts have been described above, it will be apparent to those skilled in the art that the detailed disclosure is merely illustrative and does not limit this specification. Although not explicitly stated herein, various modifications, improvements, and revisions to this specification may be made by those skilled in the art. Such modifications, improvements, and revisions are suggested in this specification and remain within the spirit and scope of the exemplary embodiments of this specification.

[0056] This specification also uses specific terms to describe the embodiments of this specification. For example, "one embodiment," "an embodiment," and / or "some embodiments" refer to a feature, structure, or characteristic associated with at least one embodiment of this specification. Therefore, it should be emphasized and noted that references to "one embodiment," "an embodiment," or "an alternative embodiment" two or more times in different locations in this specification do not necessarily refer to the same embodiment. Furthermore, certain features, structures, or characteristics of one or more embodiments of this specification may be appropriately combined.

[0057] In addition, unless explicitly stated in the claims, the order of the processing elements and sequences, the use of alphanumeric characters, or the use of other names described in this specification are not intended to limit the order of the processes and methods of this specification. Although the above disclosure discusses some currently considered useful embodiments through various examples, it should be understood that such details are only for illustrative purposes, and the appended claims are not limited to the disclosed embodiments. On the contrary, the claims are intended to cover all modifications and equivalent combinations that are consistent with the spirit and scope of the embodiments of this specification.

[0058] Similarly, it should be noted that, in order to simplify the description of this specification and facilitate understanding of one or more embodiments, the foregoing description of the embodiments of this specification sometimes combines multiple features into a single embodiment, figure, or description thereof. However, this disclosure method does not mean that the subject matter of this specification requires more features than those recited in the claims. In fact, the features of an embodiment may be fewer than all the features of the individual embodiments disclosed above.

[0059] In some embodiments, numbers are used to describe the quantity of components and attributes. It should be understood that such numbers used in the description of the embodiments are modified by the modifiers "about", "approximately" or "substantially" in some examples. Unless otherwise stated, "about", "approximately" or "substantially" indicate that the numbers are allowed to vary by ±20%. Accordingly, in some embodiments, the numerical parameters used in the description and claims are approximate values, which may change according to the required characteristics of individual embodiments. In some embodiments, the numerical parameters should take into account the specified significant digits and adopt the general method of retaining digits. Although the numerical domains and parameters used to confirm the breadth of their range in some embodiments of this specification are approximate values, in specific embodiments, the settings of such numerical values ​​are as accurate as possible within the feasible range.

[0060] Each patent, patent application, patent application publication, and other materials, such as articles, books, specifications, publications, and documents, cited in this specification is hereby incorporated by reference in its entirety. This includes application history documents that are inconsistent with or conflict with the content of this specification, as well as documents (currently or subsequently attached to this specification) that limit the broadest scope of the claims of this specification. It should be noted that if the descriptions, definitions, and / or terminology used in the accompanying materials are inconsistent or conflicting with the content of this specification, the descriptions, definitions, and / or terminology used in this specification will control.

[0061] Finally, it should be understood that the embodiments described in this specification are intended only to illustrate the principles of the embodiments of this specification. Other variations may also fall within the scope of this specification. Therefore, by way of example and not limitation, alternative configurations of the embodiments of this specification may be considered consistent with the teachings of this specification. Accordingly, the embodiments of this specification are not limited to the embodiments explicitly described and illustrated in this specification.

Claims

1. A radiotherapy device, characterized in that: It includes a beam generating device, a scanning magnet (110) and a focusing magnet (120); The beam generating device is used to generate a charged particle beam; The scanning magnet (110) is used to diverge the charged particle beam; The focusing magnet (120) is used to deflect the charged particle beam diverged by the scanning magnet (110) and emit it from an arc-shaped outlet of the focusing magnet (120), wherein the arc has the treatment center point as the center of the circle; the charged particle beam is deflected by the focusing magnet (120) and can converge at the treatment center point within a range of a central angle greater than 180° with the treatment center point as the center of the circle; an arc-shaped target (210), the arc-shaped target (210) being arranged close to the outlet of the focusing magnet (120); the charged particle beam impacting the arc-shaped target (210) in a direction perpendicular to the target surface to generate photons, and the focal spot of the charged particle beam on the arc-shaped target (210) is non-fixed; A multi-leaf collimator (220) is arc-shaped and is arranged close to the arc-shaped target (210); the photons pass through the multi-leaf collimator (220) to complete conformal alignment.

2. The radiotherapy apparatus according to claim 1, wherein The focusing magnet (120) comprises an inlet and an outlet, the focusing magnet (120) is bent toward the outlet, and the outlet of the focusing magnet (120) is arc-shaped.

3. The radiotherapy apparatus according to claim 1, wherein The charged particle beam takes the treatment center point as the center of the circle and strikes the arc-shaped target (210) within a range where the center angle is greater than 180 degrees to generate a photon beam.

4. The radiotherapy apparatus according to claim 1 or 2, characterized in that: At least one diverging magnet (150) is provided at the outlet of the focusing magnet (120), and the at least one diverging magnet (150) is movably provided at the outlet of the focusing magnet (120).

5. The radiotherapy apparatus according to claim 1, wherein: The number of the focusing magnets (120) is at least two, and the at least two focusing magnets (120) are adjacently and / or oppositely arranged; when the at least two focusing magnets (120) are oppositely arranged, the outlets of the focusing magnets (120) are opposite to each other.

6. A photon flash therapy system, characterized in that: The radiotherapy device according to any one of claims 1 to 5, wherein the photon flash therapy system comprises: The beam generating device, the scanning magnet (110), the focusing magnet (120) and / or The arc-shaped target (210) and the multi-leaf collimator (220); Wherein, the beam generating device includes at least one of a petal accelerator and a cyclotron accelerator.

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