Miniaturized particle beam therapy device

Abstract

The present disclosure relates to the technical field of tumor radiotherapy, and specifically provides a miniaturized particle beam therapy device. The miniaturized particle beam therapy device includes a fixed support device, a synchrotron, a rotating support device, a first deflection magnet group, a second deflection magnet group and an irradiation head, wherein the fixed support device includes a base and a driving and rotating mechanism; the synchrotron is connected with a first conveying channel; the rotating support device supports the synchrotron, and the driving and rotating mechanism drives the rotating support device to rotate; the first deflection magnet group is arranged on the rotating support device; the second deflection magnet group is connected with the first deflection magnet group, the first deflection magnet group has the same structure and parameters as the deflection magnet group in the synchrotron, and the number of deflection magnet bodies is the same; a first deflection magnet is arranged between the first deflection magnet group and the second deflection magnet group, and an irradiation head is arranged at the output end of the second deflection magnet group, and its output end points to the rotation center line of the rotating support device.

Description

Technical Field

[0001] The present disclosure relates to the technical field of tumor radiotherapy, and in particular to a miniaturized particle beam therapy device. Background Art

[0002] Particle accelerators can be used in tumor radiotherapy, such as accelerating particle beams in heavy ion therapy or proton therapy. The accelerated particle beam needs to be guided to the patient's target tissue, and it is often necessary to irradiate the target tissue from different directions to enhance the treatment effect or reduce the radiation to surrounding healthy tissue.

[0003] In some tumor radiotherapy systems, the particle beam generator and accelerator are fixed to the ground, and the treatment room is set near the accelerator. Therefore, the particle beam emitted by the accelerator needs to be diverted and guided into the treatment room. Specifically, a complex system consisting of deflection magnets and focusing magnets is required to guide the particle beam from the particle accelerator to the target. The system is large in size and expensive to manufacture. In addition, the distance between the treatment room and the accelerator is large, and the particle beam will lose energy during transmission, which may reduce the control accuracy of the irradiation dose. Summary of the invention

[0004] In order to solve the above technical problems or at least partially solve the above technical problems, the present disclosure provides a miniaturized particle beam therapy device.

[0005] The present disclosure provides a miniaturized particle beam therapy device for emitting a particle beam to a target tissue, comprising:

[0006] A fixed support device, comprising a base, on which a driving rotation mechanism is provided, used as a support base;

[0007] A synchrotron accelerator is used to accelerate a particle beam, wherein the synchrotron accelerator has a deflection magnet and is connected to a first conveying channel, wherein the first conveying channel conveys the particle beam obliquely upward;

[0008] A rotating support device, used to support the synchrotron, the rotating support device being rotatably arranged on the fixed support device; the rotating support device has a rotating center line when rotating, and the power provided by the driving rotation mechanism can cause the rotating support device to rotate around the rotating center line;

[0009] a first deflection magnet group, arranged on the rotating support device, for receiving and conveying the particle beam outputted from the first conveying channel, the first deflection magnet group being arc-shaped, and the particle beam outputted from the first conveying channel entering into the first deflection magnet group along a tangent direction of an input end of the first deflection magnet group;

[0010] a second deflection magnet group, connected to the first deflection magnet group, and used for receiving and transmitting the particle beam output by the first deflection magnet group; the first deflection magnet group and the deflection magnet group in the synchrotron have the same structure and parameters as well as the number of deflection magnet bodies; the second deflection magnet group is arc-shaped; a first deflection magnet is arranged between the first deflection magnet group and the second deflection magnet group; the particle beam deflected by the first deflection magnet enters the second deflection magnet group along the tangent direction of the input end of the second deflection magnet group; and the output end of the second deflection magnet group points to the rotation center line of the rotation support device;

[0011] The irradiation head is connected to the end of the second deflection magnet group, and the particle beam is emitted from the irradiation head to the target tissue.

[0012] Optionally, the first deflection magnet deflects the particle beam output by the first deflection magnet group to a horizontal direction or parallel to a supporting surface of the base.

[0013] Optionally, a second transport channel is provided between the first deflection magnet group and the second deflection magnet group, the particle beam deflected by the first deflection magnet enters the second transport channel, and the output end of the second transport channel is tangent to the connection between the second deflection magnet group.

[0014] Optionally, the second conveying channel is arranged in a horizontal direction or parallel to the supporting surface of the base.

[0015] Optionally, a first focusing magnet is provided on the periphery of the second conveying channel.

[0016] Optionally, a plane where the first deflection magnet group is located forms an angle with a plane where the second deflection magnet group is located.

[0017] Optionally, the plane where the first deflection magnet is located coincides with the plane where the first deflection magnet group is located.

[0018] Optionally, the particle beam output by the second deflection magnet group is perpendicular to the rotation center line of the rotation support device.

[0019] Optionally, the rotation centerline of the rotation support device is parallel to a horizontal plane or a support surface of the base.

[0020] Optionally, a second focusing magnet is provided on the periphery of the first conveying channel.

[0021] Optionally, the second deflection magnet group has the same structure and parameters as the deflection magnet group in the synchrotron and the same number of deflection magnet bodies.

[0022] Optionally, the number of deflection magnet bodies in the first deflection magnet group and the deflection magnet group in the synchrotron is four; or the number of deflection magnet bodies in the first deflection magnet group, the second deflection magnet group and the deflection magnet group in the synchrotron is four.

[0023] Optionally, an annular structure is provided on both sides of the rotating support device, the annular structure is coaxial with the rotating support device, the annular structure is rotatably arranged on the fixed support device, and the outer diameter of the annular structure is smaller than the radial distance of the farthest radial point of the rotating support device.

[0024] Optionally, the deflection magnet bodies in the first deflection magnet group, the deflection magnet bodies in the second deflection magnet group, and the deflection magnet bodies in the deflection magnet group in the synchrotron all have focusing edges.

[0025] Optionally, a vertical plane between the particle beam motion trajectory in the first transport channel and a plane where the particle beam motion trajectory in the synchrotron is located is perpendicular to a horizontal plane or a supporting surface of the base.

[0026] Optionally, the plane where the particle beam motion trajectory in the synchrotron is located is perpendicular to the supporting surface or horizontal plane of the base.

[0027] Compared with the prior art, the technical solution provided by the embodiments of the present disclosure has the following advantages:

[0028] Compared with the structure in which the synchrotron and the beam transport device are arranged separately, the synchrotron, the first deflection magnet group and the second deflection magnet group integrated on the rotating support device can significantly save space. The particle beam output by the synchrotron enters the first deflection magnet group along the tangent direction of the input end of the first deflection magnet group, so there is no need to set a deflection magnet and a focusing magnet at the input end of the first deflection magnet group, thereby reducing the overall height of the particle beam therapy device. The height reduction can reduce the space occupied by the particle beam therapy device, thereby saving the overall construction cost and construction difficulty of the building that accommodates the particle beam therapy device, and realizing an ultra-miniaturized synchrotron particle beam therapy device.

[0029] The deflection magnets in the first deflection magnet group and the second deflection magnet group have the same structure and parameters as the deflection magnets in the synchrotron, so basically the same control parameters can be used to control the deflection of the particle beam, thereby reducing the difficulty and complexity of the deflection control of the particle beam on the irradiation treatment path of the patient after it is drawn out from the synchrotron, and simplifying the control system. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments consistent with the present disclosure and, together with the description, serve to explain the principles of the present disclosure.

[0031] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, for ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative labor.

[0032] Figure 1 It is a schematic structural diagram of a miniaturized particle beam therapy device according to an embodiment of the present disclosure;

[0033] Figure 2 for Figure 1 The main view;

[0034] Figure 3 for Figure 1 Right view of;

[0035] Figure 4 A schematic diagram of a miniaturized particle beam therapy device with the rotating support device hidden;

[0036] Figure 5 for Figure 4 A top view of

[0037] Figure 6 A schematic diagram of a miniaturized particle beam therapy device according to an embodiment of the present disclosure having a cylinder;

[0038] Figure 7 A schematic diagram of an annular support plate being arranged on both sides of the rotating support device according to an embodiment of the present disclosure;

[0039] Figure 8 A schematic diagram of the positional relationship between the synchrotron and the first delivery channel according to an embodiment of the present disclosure;

[0040] Fig. 9 A schematic diagram of a plane where the synchrotron accelerator is located and a plane where the second deflection magnet group is located according to an embodiment of the present disclosure;

[0041] Fig.10 is a schematic diagram of the plane where the first deflection magnet group is located in an embodiment of the present disclosure;

[0042] Fig.11 It is a schematic diagram of a vertical plane between the particle beam motion trajectory described in an embodiment of the present disclosure and the plane where the particle beam motion trajectory of the synchrotron is located.

[0043] Among them, 10, the plane where the synchrotron is located; 11, the plane where the first deflection magnet group is located; 12, the plane where the second deflection magnet group is located; 13, the vertical plane; 14, the rotation center line; 100, the fixed support device; 110, the first support; 120, the second support; 200, the rotating support device; 210, the annular plate; 220, the cylinder; 230, the support rod; 240, the annular support plate; 300, the injection device; 310, the driving device; 400, the synchrotron; 410, the first deflection magnet body; 500, the first deflection magnet group; 510, the second deflection magnet body; 600, the second deflection magnet group; 610, the third deflection magnet body; 700, the support device; 800, the irradiation head; 900, the second conveying channel; 901, the first focusing magnet; 902, the first deflection magnet; 910, the first conveying channel; 911, the second focusing magnet. DETAILED DESCRIPTION

[0044] In order to more clearly understand the above-mentioned objectives, features and advantages of the present disclosure, the scheme of the present disclosure will be further described below. It should be noted that the embodiments of the present disclosure and the features in the embodiments can be combined with each other without conflict.

[0045] In the following description, many specific details are set forth to facilitate a full understanding of the present disclosure, but the present disclosure may also be implemented in other ways different from those described herein; it is obvious that the embodiments in the specification are only part of the embodiments of the present disclosure, rather than all of the embodiments.

[0046] Combination Figures 1 to 4 As shown, the miniaturized particle beam therapy device provided in the embodiment of the present application is used to emit a particle beam to a target tissue. The particle beam therapy device includes a fixed support device 100, a rotating support device 200, an injection device 300, a synchrotron 400, a first deflection magnet group 500, a second deflection magnet group 600, a support device 700, a driving device 310, an irradiation head 800 and a control device (not shown in the figure).

[0047] The fixed support device 100 is fixed on the ground as a mounting base. In some embodiments, the base of the fixed support device 100 is the ground. A driving rotation mechanism is provided on the base to serve as a support base. The injection device 300 includes a particle source, which is fixed on the rotating support device 200 and is used to generate a particle beam and inject the particle beam into the synchrotron 400 after preliminary acceleration. Specifically, it can be a proton beam, a carbon ion beam or a helium ion beam.

[0048] like Figure 2As shown, the synchrotron 400 is fixed on the rotating support device 200, and is used to receive and accelerate the particle beam generated by the injection device 300. The synchrotron 400 has a deflection magnet. Preferably, the synchrotron 400 is fixed on the rotating support device 200 in an upright state, that is, the plane 10 where the particle beam motion trajectory in the synchrotron 400 is located is perpendicular to the support surface or horizontal plane of the base, thereby reducing the internal space occupied by the rotating support device 200. In other embodiments, the synchrotron 400 can also be tilted in the rotating support device 200, that is, the plane where the synchrotron 400 is located is at a certain angle to the vertical plane. This design can reduce the height of the particle beam therapy device. Combined with Fig. 9 and Fig.10 As shown, the plane 10 where the synchrotron is located, the plane 11 where the first deflection magnet group is located, the plane 12 where the second deflection magnet group is located, and the plane where the first deflection magnet 902 is located all refer to the plane where the trajectory of the particle beam moves in each device or the plane where the channel center line of the particle beam is located.

[0049] The particle beam passes through the first deflection magnet group 500 and the second deflection magnet group 600 to receive the accelerated particle beam in turn, and irradiates the target area through the irradiation head 800. The support device 700 is used to support the patient. The support device 700 is driven by a movable mechanical mechanism (not shown) to adjust its relative position with the irradiation head 800. The support device 700 is preferably a treatment bed, which can be moved by a mechanical arm or a roller movable seat provided at the bottom. The driving device 310 is used to drive the rotating support device 200 to rotate on the fixed support device 100. The synchrotron 400 is connected to a first conveying channel 910, and the first conveying channel 910 conveys the particle beam obliquely upward.

[0050] like Figure 4As shown, the synchrotron 400 includes four groups of deflection magnet groups and an accelerator. The number of deflection magnet bodies in each group of deflection magnet groups is multiple, and each group of deflection magnet groups includes four first deflection magnet bodies 410 in the illustrated embodiment. The accelerator may be a radio frequency accelerator. The first deflection magnet body 410 is used to deflect the particle beam through its magnetic field so that the particle beam can rotate along a circular orbit. The synchrotron 400 accelerates the particle beam to rotate in a circular manner to increase the energy or maintain it in a circular orbit. Further optimized, the first deflection magnet body 410 may also be configured to have an edge focusing effect. Among them, the number of the first deflection magnet bodies 410 in each group of deflection magnet groups shown in the figure is multiple, and the structure and parameters of the first deflection magnet bodies 410 in each group of deflection magnet groups are different. The figure is only for illustration and does not represent the actual structure of the first deflection magnet body 410. In some optional embodiments, the number of the first deflection magnet body 410 in each group of deflection magnet groups may also be one, so that the beam is rotated by 90 degrees. In other embodiments, the shape of the synchrotron 400 may also be a rounded rectangle or the like, and each rounded corner is composed of a plurality of deflection magnets, and the deflection magnets at the rounded corners can deflect the beam.

[0051] Combination Figure 1 and Figure 3 As shown, the fixed support device 100 includes a base and a driving rotation mechanism. As a preferred embodiment, the driving rotation mechanism can be a plurality of rollers and a driving device 310, the rollers are rotatably arranged on the base, the axes of the plurality of rollers are parallel, the plurality of rollers are arranged on the base along a concave arc track, and the outer peripheral surface of the roller forms a concave arc track. The driving device 310 can drive at least one roller to rotate. As an embodiment, the driving device 310 can be a motor or a motor reducer, or a reduction motor or other mechanism that can provide roller pivot rotation by electric power. The driving rotation mechanism can also be other mechanisms that can drive an object to rotate.

[0052] The rotating support device 200 is used to support the synchrotron 400, that is, the synchrotron 400 is mounted on the rotating support device 200, and the synchrotron 400 is coaxially arranged with the rotating support device 200. The rotating support device 200 is rotatably arranged on the fixed support device 100, and the rotating support device 200 has a rotation center line 14 when performing a rotational motion. The power provided by the driving rotation mechanism can make the rotating support device 200 rotate around the rotation center line 14. Preferably, the rotation center line 14 of the rotating support device 200 is arranged parallel to the horizontal plane or the support surface (that is, the upper surface of the base) to facilitate installation and control. Figures 1 to 3As shown, in some embodiments, the rotating support device 200 is an annular support, specifically including two annular plates 210, the two annular plates 210 are arranged concentrically, and the two annular plates 210 are arranged at an interval, so that a space for installing the synchrotron 400 is formed between the two annular plates 210. The outer peripheral surface of the rotating support device 200 is equal to the arc track formed by the outer edge of the roller in the fixed support device 100, and is rotatably arranged on the outer peripheral surface of the roller, and the outer peripheral surface of the roller is tangentially in contact with the outer peripheral surface of the rotating support device 200, and the rotating support device 200 can be driven to rotate when the roller rotates.

[0053] It should be understood that the shape of the rotating support device 200 and the connection method thereof with the fixed support device 100 are not limited to the above-mentioned structures, and other structures that can realize the installation and fixing of the synchrotron 400 and can rotate on the fixed support device 100 should also fall within the scope of protection claimed in the present disclosure. For example, the outer shape of the rotating support device 200 can be square, polygonal, etc., and the internal structure can adopt a hollow truss structure formed by short metal round tubes and cylinders fixedly connected to each other, which can greatly reduce the weight of the rotating support device 200.

[0054] The rotatable connection between the rotating support device 200 and the fixed support device 100 may also be in other forms, such as a ring structure may be provided on both end surfaces of the rotating support device 200 (the ring structure may be an arc shape or an open ring that can rotate the synchrotron 400 at a set angle, and the center angle of the arc or ring ensures that the synchrotron 400 can rotate at a preset angle, for example, greater than or equal to 90°. Preferably, it is a ring structure, such as Figure 7 As shown), two fixed support devices 100 are provided in a matching manner. The annular structure is coaxial with the rotation center of the rotating support device 200, and the annular structure is rotatably provided on the fixed support device 100, and the outer diameter of the annular structure is smaller than the radial distance of the farthest radial position of the rotating support device 200. At this time, the fixed support device 100 allows the radius of the annular structure to be smaller. The outer circumferences of the two annular structures cooperate with the rollers on the fixed support device 100, and the rotating support device 200 is driven to rotate by the meshing or friction between the rollers and the outer circumferences of the annular structures.

[0055] Specifically, Figure 7As shown, a plurality of support rods 230 are provided on both sides of the rotating support device 200, and the annular structure is an annular support plate 240, which is arranged at the end of the support rod 230, and then the two annular support plates 240 are fixedly supported on both sides of the rotating support device 200 by the support rod 230. The outer circumference of the annular support plate 240 cooperates with the roller on the fixed support device 100, and the annular support plate 240 is driven to rotate by the rotation of the roller. That is, rollers are provided on both sides of the rotating support device 200, and the rollers are rotatably arranged on the base, and the axes of the plurality of rollers are parallel, and the plurality of rollers are arranged on the base along a concave arc track, and the outer circumference of the roller forms a concave arc track and is tangent to the outer edge of the annular support plate 240. The driving device 310 can drive at least one roller to rotate. By supporting the annular support plate 240 by the roller groups on both sides, it can be ensured that the rotating support device 200 is supported and rotated more stably. Preferably, the rotating support device 200 is provided with a mechanism that can ensure that the rotating support device 200 does not tilt when rotating. The mechanism can be arranged inside the roller frame, on the base, or on the top or both side walls of the building body that contains the particle beam therapy device. For example, a roller or ball mechanism is arranged inside the roller frame, and the roller or ball is against the surface of the rotating support device 200. Preferably, the support rod 230 is perpendicular to the plane where the rotating support device 200 is located, and the center line of the annular support plate 240 coincides with the rotation center line 14 of the rotating support device 200, so that the rotating support device 200 is driven to rotate along its center line by the rotation of the annular support plate 240. Further optimized, the diameter of the annular support plate 240 is reduced as much as possible to ensure that the particle beam therapy device does not interfere when rotating. For example, first ensure that the part of the rotating support device 200 with the largest radial distance does not interfere with the base during the rotation of the set angle. This design method can further reduce the overall height of the particle beam therapy device.

[0056] In other embodiments, the method of driving the rotating support device to rotate can be through gear transmission, a driving device is provided on the base, and a first gear is connected to the driving device, and the driving device can drive the first gear to rotate. Accordingly, a second gear meshing with the first gear is provided on the outer periphery of the annular plate 210 or the annular support plate 240, and then the annular plate 210 or the annular support plate 240 is driven to rotate by the rotation of the first gear. It can be seen that the specific matching method of the fixed support device 100 and the rotating support device 200 is not limited, and it is only necessary to satisfy that the fixed support device 100 drives the rotating support device 200 to rotate around its rotation center line 14.

[0057] Combination Figures 1 to 5As shown, the first deflection magnet group 500 is arranged on the rotating support device 200, and is used to receive and transport the particle beam output by the first transport channel 910. The first deflection magnet group 500 is arc-shaped, and the particle beam output through the first transport channel 910 enters the first deflection magnet group 500 along the tangent direction of the input end of the first deflection magnet group 500. Specifically, the first transport channel 910 is tangent to the connection position of the input end of the first deflection magnet group 500, that is, the tangent direction of the input end of the first deflection magnet group 500 coincides with the transport direction of the particle beam output by the synchrotron 400. The first deflection magnet group 500 can be arranged on the rotating support device 200 through a connecting member, and can also be arranged on the rotating support device 200 through the first transport channel 910. Specifically, the first deflection magnet group 500 includes a plurality of deflection magnets, wherein the first deflection magnet group 500 can also include one deflection magnet. As shown in the embodiment, the first deflection magnet group 500 includes four second deflection magnet bodies 510, and the four second deflection magnet bodies 510 are used to deflect the particle beam through their magnetic field, so that the particle beam is output from the first deflection magnet group 500 according to the set direction. Of course, the second deflection magnet bodies 510 can also be other numbers, such as the number of the second deflection magnet bodies 510 can also be one, and the center angle of the second deflection magnet body 510 at the corresponding position in the second deflection magnet group 500 can be the same as or different from the center angle of the first deflection magnet body 410 at the corresponding position in the deflection magnet group of the synchrotron 400, which is designed according to specific needs. Among them, the center angle is the center angle of the arc formed by the beam motion trajectory on the surface where the deflection magnet body or the deflection magnet group is located.

[0058] It is worth noting that the tangent in the above and below texts refers to the tangent to the trajectory formed by the direction of movement of the particle beam.

[0059] like Figure 4As shown, the second deflection magnet group 600 is connected to the first deflection magnet group 500, and is used to receive and transmit the particle beam output by the first deflection magnet group 500. The structure and parameters of the first deflection magnet group 500 and the number of deflection magnet bodies are the same as those of the deflection magnet group in the synchrotron 400. Further optimized, the structure and parameters of the second deflection magnet group 600 and the number of deflection magnet bodies are the same as those of the deflection magnet group in the synchrotron 400. This design method can use basically the same control parameters to control the deflection of the particle beam, thereby reducing the difficulty and complexity of the deflection control of the particle beam after it is drawn out from the synchrotron 400 to irradiate the patient for treatment, and can simplify the control system. The second deflection magnet group 600 is arc-shaped, and a first deflection magnet 902 is provided between the first deflection magnet group 500 and the second deflection magnet group 600. The particle beam deflected by the first deflection magnet 902 enters the second deflection magnet group 600 along the tangent direction of the input end of the second deflection magnet group 600, that is, the transport direction of the particle beam deflected by the first deflection magnet 902 is parallel to the tangent direction of the input end of the second deflection magnet group 600. The output end of the second deflection magnet group 600 points to the rotation center line 14 of the rotating support device 200. The second deflection magnet group 600 includes a plurality of deflection magnets, and the deflection magnet in the second deflection magnet group 600 may also be one. In some preferred embodiments, as shown in the illustrated embodiment, the second deflection magnet group 600 includes four third deflection magnet bodies 610, and the four third deflection magnet bodies 610 are used to deflect the particle beam through its magnetic field so that the particle beam is output toward the rotation center line 14 of the rotating support device 200. This design method makes the number of the second deflection magnet bodies 510 and the number of the third deflection magnet bodies 610 the same as the number of the first deflection magnet bodies 410 of each deflection magnet group in the synchrotron 400. Further optimized, the curvature radius of the deflection part formed by the deflection magnets in the first deflection magnet group 500 and the second deflection magnet group 600 is the same as the curvature radius of the deflection part formed by the deflection magnets in the synchrotron 400, and the number of the deflection magnet bodies is four. Therefore, the first deflection magnet group 500 and the second deflection magnet group 600 can directly adopt the deflection magnet group in the synchrotron 400, making the overall design and installation of the particle beam therapy device more convenient. In addition, substantially the same control parameters can be used to control the deflection of the beam, thereby reducing the difficulty and complexity of deflection control of the beam path for irradiating the patient after the beam is drawn out from the synchrotron 400, and simplifying the control system.

[0060] Preferably, the synchrotron 400, the first deflection magnet group 500 and the second deflection magnet group 600 are all composed of a plurality of deflection magnet bodies with focusing edges, which have a focusing function while realizing particle beam deflection, and can omit a separate focusing magnet, thereby greatly reducing the overall volume and weight of the particle therapy device, making it easier to rotate the vertically arranged particle beam therapy device when it rotates, without requiring a higher-power rotation drive, and at the same time facilitating the precision control of the rotation motion. It is worth noting that the first deflection magnet group 500 and the second deflection magnet group 600 can also use magnets without edge focusing function, and cooperate with a separate focusing magnet for focusing.

[0061] The irradiation head 800 is connected to the end of the second deflection magnet group 600, and the particle beam is emitted from the irradiation head 800 to the target target tissue. Further optimized, a focusing magnet can be set between the irradiation head 800 and the second deflection magnet group 600. In other embodiments, the number of the first deflection magnet body 410 of each deflection magnet group in the synchrotron 400 can be one, in which case the number of the second deflection magnet body 510 and the number of the third deflection magnet body 610 should also be one, which is convenient for design and installation. Specifically, one deflection magnet body realizes a 90° deflection, wherein the synchrotron requires 4 first deflection magnet bodies 410 to complete one beam rotation. Or one deflection magnet body realizes a 60° deflection, and the synchrotron requires 6 first deflection magnet bodies 410 to complete one beam rotation. It can be seen that the deflection angle of the deflection magnet body is not limited, as long as it meets the deflection requirements, and the number of deflection magnet bodies in the synchrotron should be such that the beam can rotate once. It should be noted that each deflection magnet body in this embodiment needs to be provided with a separate focusing magnet before and after to avoid beam divergence.

[0062] Compared with the structure in which the synchrotron 400 and the beam transport device are arranged separately, the synchrotron 400, the first deflection magnet group 500 and the second deflection magnet group 600 integrated on the rotating support device 200 can significantly save space. The particle beam output by the synchrotron 400 enters the first deflection magnet group 500 along the tangent direction of the input end of the first deflection magnet group 500. Therefore, it is not necessary to set a deflection magnet and a focusing magnet at the input end of the first deflection magnet group 500, thereby reducing the overall height of the particle beam therapy device. The height reduction can reduce the space occupied by the particle beam therapy device, thereby saving the overall construction cost and construction difficulty of the building that accommodates the particle beam therapy device, and realizing an ultra-miniaturized synchrotron 400 particle beam therapy device. Among them, the particle beam therapy device accommodates the building and needs to have a shielding function. The thicker the wall used and the higher the height, the sharper the construction cost and construction difficulty.

[0063] The deflection magnets in the first deflection magnet group 500 and the second deflection magnet group 600 have the same structure and parameters as the deflection magnets in the synchrotron 400, so basically the same control parameters can be used to control the deflection of the particle beam, thereby reducing the difficulty and complexity of the deflection control of the particle beam for irradiating the patient after it is drawn out from the synchrotron 400, and simplifying the control system.

[0064] like Figure 2 As shown, the first delivery channel 910 extends from the middle of the synchrotron 400 and extends obliquely upward, thereby allowing the particle beam to be transported obliquely upward. The connection between the first deflection magnet group 500 and the second deflection magnet group 600 is located above the rotation centerline 14 of the rotating support device 200, and the output end of the second deflection magnet group 600 points to the rotation centerline 14 of the rotating support device 200, which is convenient for emitting the particle beam from top to bottom. Further optimized, the first deflection magnet 902 deflects the particle beam output by the first deflection magnet group 500 to the horizontal direction or parallel to the support surface of the base. This design method makes the tangent direction of the input end of the second deflection magnet group 600 parallel to the horizontal direction or the support surface of the base, thereby making the particle beam output by the second deflection magnet group 600 perpendicular to the rotation centerline 14 of the rotating support device 200. In the embodiment where the input end of the second deflection magnet group 600 is horizontal and the output end is vertical, the second deflection magnet group 600 can directly adopt the same deflection magnet group as the synchrotron 400, that is, the structure, parameters and number of deflection magnet bodies are the same, simplifying the control system. This method can make the particle beam substantially perpendicular to the support surface of the patient lying flat and the virtual central axis where the torso is located. The central axis can be set to pass through the patient's tumor position and the rotation center line 14, preferably colinear with the rotation center line 14. After the synchrotron 400 is rotated, the beam can be rotated on a vertical plane perpendicular to the support surface and the virtual central axis where the patient's torso is located.

[0065] In other embodiments, a second delivery channel 900 is provided between the first deflection magnet group 500 and the second deflection magnet group 600, and the particle beam deflected by the first deflection magnet 902 enters the second delivery channel 900, and the output end of the second delivery channel 900 is tangent to the connection of the second deflection magnet group 600. Specifically, the first deflection magnet 902 is provided at the output end of the first deflection magnet group 500, so that the particle beam deflected by the first deflection magnet 902 enters the second delivery channel 900, and the output direction of the particle beam deflected by the first deflection magnet 902 is the same as the beam delivery direction of the second delivery channel 900. The length of the second delivery channel 900 is designed according to specific requirements, so that the output end of the second deflection magnet group 600 points to the rotation center line 14 of the rotating support device 200. Further optimized, the direction of the second transport channel 900 can ensure that its beam transport direction is set in the horizontal direction or parallel to the supporting surface of the base, that is, this design makes the particle beam output by the second deflection magnet group 600 perpendicular to the rotation centerline 14 of the rotating support device 200.

[0066] Further optimized, the outer periphery of the second delivery channel 900 is provided with a first focusing magnet 901, and the number of the first focusing magnets 901 is preferably one or two. Of course, the number of the first focusing magnets 901 can also be multiple, but this will increase the length of the second delivery channel 900. By providing the first deflection magnet 902 and the first focusing magnet 901, the length of the second delivery channel 900 can be shortened, which plays a role in reducing the axial length of the particle beam therapy device. If the radiation of the accelerator and the injection device is too large during treatment, it is necessary to control the distance between the accelerator and the patient not to be too small, and to add a shielding device. At this time, the length of the second delivery channel 900 is adjusted as needed.

[0067] The axial direction mentioned above and below refers to the length direction of the rotation center line 14 of the rotation support device 200 .

[0068] like Figure 5As shown, the plane where the first deflection magnet group 500 is located forms an angle with the plane where the second deflection magnet group 600 is located. The second deflection magnet group 600 can thus deflect the particle beam downward. At the same time, because the plane where the first deflection magnet group 500 is located has a certain angle with the plane where the second deflection magnet group 600 is located, in order to avoid the particle beam from diverging, a plurality of first focusing magnets 901 are arranged between the first deflection magnet group 500 and the second deflection magnet group 600. Specifically, since the first deflection magnet group 500 and the second deflection magnet group 600 are connected through the second delivery channel 900, the first focusing magnet 901 is arranged on the periphery of the second delivery channel 900, wherein the first focusing magnet 901 may be one, two or more, and is designed according to the length of the second delivery channel 900. Of course, under the premise of ensuring that beam focusing can be achieved, and during treatment, the radiation of the synchrotron 400, the injection device 300, etc. itself is not too large or can be reduced to an allowable range after shielding by necessary radiation shielding devices, in order to reduce the length of the second delivery channel 900, the number of the first focusing magnet 901 is as small as possible. In the scheme of some embodiments of the present patent, the radiation of the synchrotron 400, the injection device 300, etc. itself is within the allowable range, or can be reduced to the allowable range after shielding.

[0069] The first deflection magnet group 500 deflects the particle beam from the delivery direction of the first delivery channel 910 to the set direction, the first deflection magnet 902 turns the direction of the particle beam output from the first delivery channel 910 to the horizontal direction, and the second deflection magnet group 600 can turn the particle beam from the horizontal direction to the vertical direction, which can simplify the structure of the particle beam therapy device and facilitate installation, and avoid the angle between the second delivery channel 900 and the reference object cannot be accurately positioned during installation, resulting in installation errors, and then causing treatment accidents during treatment by the particle beam therapy device. And this design method reduces the height of the first deflection magnet group 500 and the second deflection magnet group 600, thereby reducing the height of the overall particle beam therapy device, and further saving the volume of the building that accommodates the particle beam therapy device. It is worth noting that this design method should meet the requirements that the irradiation head 800 is above the rotation center line 14 of the rotating support device 200, and there is a certain distance between the irradiation head 800 and the rotation center line 14 of the rotating support device 200, so as to accommodate patients.

[0070] In other embodiments, if the space between the irradiation head 800 and the rotation center line 14 of the rotation support device 200 is insufficient to accommodate the patient, the output end of the first deflection magnet group 500 is tilted upward. Figure 8As shown, the beam direction at the output end of the first deflection magnet group 500 can be changed by changing the angle between the first delivery channel 910 and the plane where the synchrotron 400 is located, or by increasing the center angle of the particle beam trajectory of the first deflection magnet group 500 while keeping the plane of the first deflection magnet group 500 relative to the synchrotron 400 unchanged, thereby making the output end of the first deflection magnet group 500 tilt upward. At the same time, the direction of the particle beam output by the first deflection magnet group 500 still needs to be turned into a horizontal direction by the first deflection magnet 902.

[0071] In other embodiments, in order to increase the distance between the irradiation head 800 and the rotation center line 14 of the rotation support device 200, the length of the first delivery channel 910 may also be adjusted. Of course, the length of the first delivery channel 910 should not be too short or too long, and should be within the design range. Accordingly, the center angle of the first deflection magnet group 500, the center angle of the second deflection magnet group 600 and the length of the first delivery channel need to be adjusted according to the beam direction of the output end of the second deflection magnet group 600 to ensure that the output end of the second deflection magnet group 600 points to the rotation center line 14 of the rotation support device 200. The center angle is the center angle of the arc formed by the beam motion trajectory on the surface where the deflection magnet body or the deflection magnet group is located.

[0072] The plane where the particle beam deflected by the first deflection magnet 902 is located coincides with the plane where the first deflection magnet group 500 is located, that is, one of the planes where the particle beam deflected by the first deflection magnet 902 is located coincides with the plane where the particle beam motion track in the first deflection magnet group 500 is located. This design can better deflect the particle beam.

[0073] like Fig.11 As shown, the synchrotron 400 is connected to a first delivery channel 910, and the vertical plane 13 between the particle beam motion trajectory and the plane where the particle beam motion trajectory of the synchrotron 400 is located is tangent to the particle beam trajectory before being drawn out from the synchrotron 400, and the vertical plane 13 between the particle beam motion trajectory in the first delivery channel 910 and the plane where the particle beam motion trajectory in the synchrotron 400 is located is perpendicular to the horizontal plane or the supporting surface of the base, so that the particle beam can enter the first delivery channel 910. Figure 1 and Figure 3As shown, the output end of the first delivery channel 910 extends obliquely upward, the input end of the first deflection magnet group 500 is connected to the first delivery channel 910, and the connection between the first delivery channel 910 and the first deflection magnet group 500 is tangent. Among them, the output end of the first delivery channel 910 is inclined upward, so that the particle beam output by the first deflection magnet group 500 is above the rotation center line 14 of the rotating support device 200. Further optimized, the periphery of the first delivery channel 910 is provided with a second focusing magnet 911.

[0074] like Figure 6 As shown, in this embodiment, the particle beam therapy device further includes a cylinder 220, which is a cylinder and is coaxially fixed with the rotating support device 200. The first deflection magnet group 500, the second delivery channel 900 and part of the second deflection magnet group 600 are located outside the cylinder 220, and the output end of the second deflection magnet group 600 passes through the side wall of the cylinder 220 and is inserted into the inside of the cylinder 220. The second deflection magnet group 600 is fixedly connected to the cylinder 220, thereby enhancing the stability of the second deflection magnet group 600, and the cylinder 220 also plays a role of physical isolation. In order to increase the stability of each device of the particle beam therapy device during the rotation process, a connecting arm or a connecting frame can be set on the outer periphery of the cylinder 220, and the first deflection magnet group 500, the second deflection magnet group 600, the first delivery channel 910, the second delivery channel 900, the irradiation head 800 and a plurality of focusing magnets are connected and fixed by the connecting arm or the connecting frame.

[0075] In other embodiments, when the axial length of the particle beam therapy device is small, it is not necessary to set the cylinder 220. In this case, the first deflection magnet group 500, the second deflection magnet group 600, the first delivery channel 910, the second delivery channel 900, the irradiation head 800 and the multiple focusing magnets need to be fixedly connected by a fixed connection device to increase the stability of the rotation process. The fixed connection device can also be a connecting arm or a connecting frame. Since the connecting arm and the connecting frame are both common in the prior art and their setting methods are diverse, they only need to be able to play a connecting and fixing role, so they are not described in detail in this embodiment.

[0076] The rotating support device 200 and the cylinder 220 are supported by the first support 110 and the second support 120. In some optional embodiments, the cylinder 220 can be a square cylinder, an elliptical cylinder or a prismatic cylinder. Of course, the cylinders 220 of these shapes will also be provided with cylindrical matching parts adapted to the arc tracks of the first support 110 and the second support 120.

[0077] It should be noted that, in this patent, the particle beam motion trajectory in the deflection magnet body or the deflection magnet group or the synchrotron 400 or the transport channel does not necessarily remain unchanged. In addition, when there are multiple deflection magnet bodies in the synchrotron 400 and the first deflection magnet group 500 or the second deflection magnet group 600, the beam motion trajectory in the connecting channel between the deflection magnet bodies is not necessarily an arc, so the center angle of the deflection magnet group mentioned in this patent is the center angle of a virtual arc, which is fitted by the motion trajectory of the beam in each deflection magnet body in the deflection magnet group.

[0078] In this article, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Moreover, the terms "comprises", "comprising" or any other variants thereof are intended to cover non-exclusive inclusion, so that a process, method, article or device including a series of elements includes not only those elements, but also other elements not explicitly listed, or also includes elements inherent to such process, method, article or device. In the absence of further restrictions, an element defined by the statement "comprising a ..." does not exclude the presence of other identical elements in the process, method, article or device including the element.

[0079] The above description is only a specific embodiment of the present disclosure, so that those skilled in the art can understand or implement the present disclosure. Various modifications to these embodiments will be apparent to those skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the present disclosure. Therefore, the present disclosure will not be limited to the embodiments described herein, but will conform to the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. A miniaturized particle beam therapy device for emitting a particle beam to a target tissue, characterized in that: include: A fixed support device (100) comprises a base, on which a driving rotation mechanism is provided, and is used as a support base; A synchrotron (400) is used to accelerate a particle beam, wherein the synchrotron (400) has a deflection magnet, and the synchrotron (400) is connected to a first transport channel (910), wherein the first transport channel (910) transports the particle beam obliquely upward; A rotating support device (200) is used to support the synchrotron (400), and the rotating support device (200) is rotatably arranged on the fixed support device (100); when the rotating support device (200) performs a rotating motion, it has a rotating center line (14), and the power provided by the driving rotation mechanism can cause the rotating support device (200) to rotate around the rotating center line (14); A first deflection magnet group (500) is arranged on the rotating support device (200) and is used to receive and transport the particle beam output from the first transport channel (910); the first deflection magnet group (500) is arc-shaped, and the particle beam output through the first transport channel (910) enters the first deflection magnet group (500) along a tangent direction of an input end of the first deflection magnet group (500); The second deflection magnet group (600) is connected to the first deflection magnet group (500) and is used to receive and transmit the particle beam output by the first deflection magnet group (500). The first deflection magnet group (500) and the deflection magnet group in the synchrotron (400) have the same structure and parameters as well as the number of deflection magnet bodies. The second deflection magnet group (600) is arc-shaped. A first deflection magnet (902) is provided between the first deflection magnet group (500) and the second deflection magnet group (600). The particle beam deflected by the deflection magnet (902) enters the second deflection magnet group (600) along a tangential direction of the input end of the second deflection magnet group (600), the output end of the second deflection magnet group (600) points to the rotation center line (14) of the rotating support device (200), and the deflection magnet body in the first deflection magnet group (500), the deflection magnet body in the second deflection magnet group (600) and the deflection magnet body of the deflection magnet group in the synchrotron (400) all have focusing edges; A second transport channel (900) is provided between the first deflection magnet group (500) and the second deflection magnet group (600), the particle beam deflected by the first deflection magnet (902) enters the second transport channel (900), and the output end of the second transport channel (900) is tangent to the connection point of the second deflection magnet group (600); An irradiation head (800) is connected to the end of the second deflection magnet group (600), and a particle beam is emitted from the irradiation head (800) to a target tissue.

2. The miniaturized particle beam therapy device according to claim 1, characterized in that: The first deflection magnet (902) deflects the particle beam output by the first deflection magnet group (500) to a horizontal direction or parallel to a supporting surface of the base.

3. The miniaturized particle beam therapy device according to claim 1, characterized in that: The second conveying channel (900) is arranged in a horizontal direction or parallel to the supporting surface of the base.

4. The miniaturized particle beam therapy device according to claim 1, characterized in that: A first focusing magnet (901) is provided on the outer periphery of the second transport channel (900).

5. The miniaturized particle beam therapy device according to claim 1, characterized in that: The plane where the first deflection magnet group (500) is located forms an angle with the plane where the second deflection magnet group (600) is located.

6. The miniaturized particle beam therapy device according to claim 1, characterized in that: The plane where the first deflection magnet (902) is located coincides with the plane where the first deflection magnet group (500) is located.

7. The miniaturized particle beam therapy device according to claim 1, characterized in that: The particle beam outputted by the second deflection magnet group (600) is perpendicular to the rotation center line (14) of the rotation support device (200).

8. The miniaturized particle beam therapy device according to claim 1, characterized in that: The rotation center line (14) of the rotation support device (200) is parallel to a horizontal plane or a support surface of the base.

9. The miniaturized particle beam therapy device according to claim 1, characterized in that: A second focusing magnet (911) is provided on the outer periphery of the first transport channel (910).

10. The miniaturized particle beam therapy device according to claim 1, characterized in that: The second deflection magnet group (600) has the same structure and parameters as the deflection magnet group in the synchrotron (400), as well as the same number of deflection magnet bodies.

11. The miniaturized particle beam therapy device according to claim 1 or 10, characterized in that: The number of deflection magnet bodies in the first deflection magnet group (500) and the deflection magnet group in the synchrotron (400) are both four.

12. The miniaturized particle beam therapy device according to claim 1 or 10, characterized in that: The number of deflection magnet bodies in the first deflection magnet group (500), the second deflection magnet group (600) and the deflection magnet group in the synchrotron (400) are all four.

13. The miniaturized particle beam therapy device according to claim 1, characterized in that: An annular structure is provided on both sides of the rotating support device (200), the annular structure is coaxial with the rotating support device (200), the annular structure is rotatably arranged on the fixed support device (100), and the outer diameter of the annular structure is smaller than the radial distance of the farthest radial point of the rotating support device (200).

14. The miniaturized particle beam therapy device according to claim 1, characterized in that: A vertical plane (13) between the particle beam motion trajectory in the first delivery channel (910) and the plane where the particle beam motion trajectory in the synchrotron (400) is located is perpendicular to a horizontal plane or a supporting surface of the base.

15. The miniaturized particle beam therapy device according to claim 1, characterized in that: The plane (10) where the particle beam motion trajectory in the synchrotron (400) is located is perpendicular to the supporting surface or horizontal plane of the base.

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