CN213667591U - Miniaturized particle beam therapy device - Google Patents

Abstract

The disclosure relates to the technical field of tumor radiotherapy, and particularly provides a miniaturized particle beam therapy device. The miniaturized particle beam therapy device comprises a fixed support device, a synchrotron, a rotary support device, a first deflection magnet group, a second deflection magnet group and an irradiation head, wherein the fixed support device comprises a base and a driving rotating mechanism; the synchronous accelerator is connected with a first conveying channel; the rotary supporting device supports the synchrotron and drives the rotating mechanism to drive the rotary supporting device to rotate; the first deflection magnet group is arranged on the rotary supporting device; the second deflection magnet group is connected with the first deflection magnet group, the structures and parameters of the first deflection magnet group and the deflection magnet groups in the synchrotron are the same as the number of the deflection magnet bodies, a first deflection magnet is arranged between the first deflection magnet group and the second deflection magnet group, an irradiation head is arranged at the output 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 supporting device.

Description

Miniaturized particle beam therapy device

Technical Field

The present disclosure relates to the field of tumor radiotherapy, and more particularly, to a miniaturized particle beam therapy device.

Background

The particle accelerator can be applied to tumor radiotherapy, such as accelerating a particle beam in heavy ion therapy or proton therapy. The accelerated particle beam needs to be directed to the target tissue of the patient and often the target tissue needs to be irradiated from different directions to enhance the therapeutic effect or reduce the exposure of surrounding healthy tissue.

In some tumor radiotherapy systems, the particle beam generating device and the accelerator are fixed on the ground, and the treatment room is disposed near the accelerator, so that the particle beam emitted from the accelerator needs to be steered and guided into the treatment room, and particularly, a complex system composed of a deflection magnet and a focusing magnet is needed to guide the particle beam from the particle accelerator to a target, which is large in size and expensive to manufacture. In addition, the distance between the treatment room and the accelerator is large, and the energy loss of the particle beam occurs during the transmission process, which may cause the control precision of the irradiation dose to be reduced.

SUMMERY OF THE UTILITY MODEL

To solve the above technical problem or at least partially solve the above technical problem, the present disclosure provides a miniaturized particle beam therapy device.

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

the fixed supporting device comprises a base, wherein a driving rotating mechanism is arranged on the base and is used as a supporting foundation;

the particle beam accelerator comprises a synchrotron, a deflection magnet and a first conveying channel, wherein the synchrotron is used for accelerating a particle beam and is connected with the first conveying channel, and the first conveying channel conveys the particle beam obliquely upwards;

the rotary supporting device is used for supporting the synchrotron and is rotatably arranged on the fixed supporting device; the rotary supporting device has a rotary central line when rotating, and the rotary supporting device can rotate around the rotary central line by the power provided by the driving rotating mechanism;

the first deflection magnet group is arranged on the rotary supporting device and used for receiving and conveying the particle beam output by the first conveying channel, the first deflection magnet group is arc-shaped, and the particle beam output by the first conveying channel enters the first deflection magnet group along the tangential direction of the input end of the first deflection magnet group;

the second deflection magnet group is connected with the first deflection magnet group and used for receiving and transmitting the particle beams output by the first deflection magnet group, the structures and parameters of the first deflection magnet group and the deflection magnet groups in the synchrotron are the same, and the number of the deflection magnet bodies is the same, 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 beams deflected by the first deflection magnet enter the second deflection magnet group along the tangential 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 supporting device;

an irradiation head connected to a distal end of the second deflection magnet group, from which a particle beam is emitted to a target tissue of interest.

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

Optionally, a second transportation channel is disposed between the first deflection magnet set and the second deflection magnet set, the particle beam deflected by the first deflection magnet enters the second transportation channel, and an output end of the second transportation channel is tangent to a connection of the second deflection magnet set.

Optionally, the second conveying channel is arranged along a horizontal direction or parallel to the supporting surface of the base.

Optionally, the second conveying passage is provided with a first focusing magnet at its outer periphery.

Optionally, an included angle is formed between a plane where the first deflection magnet group is located and a plane where the second deflection magnet group is located.

Optionally, the plane of the first deflection magnet is coincident with the plane of the first deflection magnet group.

Optionally, the particle beam output by the second deflection magnet assembly is perpendicular to the rotation centerline of the rotary support device.

Optionally, the rotation center line of the rotation support device is parallel to the horizontal plane or the support plane of the base.

Optionally, the periphery of the first conveying channel is provided with a second focusing magnet.

Optionally, the second deflection magnet group and the deflection magnet groups in the synchrotron have the same structure and parameters and the number of deflection magnet bodies.

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

Optionally, both sides of the rotary supporting device are provided with an annular structure, the annular structure is coaxial with the rotary supporting device, the annular structure is rotatably disposed on the fixed supporting device, and the outer diameter of the annular structure is smaller than the radial distance at the radially farthest position of the rotary supporting device.

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 of the deflection magnet groups in the synchrotron each have a focusing edge.

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

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

Compared with the prior art, the technical scheme provided by the embodiment of the disclosure has the following advantages:

the synchrotron, the first deflection magnet group and the second deflection magnet group integrated on the rotary support device can save space significantly compared to a structure in which the synchrotron and the beam transport device are arranged separately. The particle beam output by the synchrotron enters the first deflection magnet group along the tangential direction of the input end of the first deflection magnet group, so that the deflection magnet and the focusing magnet do not need to be arranged at the input end of the first deflection magnet group, the overall height of the particle beam treatment device is reduced, the space occupied by the particle beam treatment device can be reduced due to the height reduction, the overall construction cost and the construction difficulty of a building accommodated by the particle beam treatment device are further saved, and the subminiaturized synchrotron particle beam treatment device is realized.

The deflecting magnets in the first deflecting magnet group and the second deflecting magnet group have the same structure and parameters as those of the deflecting magnets in the synchrotron, so that the deflection of the particle beam can be controlled by adopting basically the same control parameters, the difficulty and complexity of deflection control of an irradiation treatment path of a patient after the particle beam is led out of the synchrotron are reduced, and a control system can be simplified.

Drawings

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 disclosure.

In order to more clearly illustrate the embodiments or technical solutions in the prior art of the present disclosure, the drawings used in the description of the embodiments or prior art will be briefly described below, and it is obvious for those skilled in the art that other drawings can be obtained according to the drawings without inventive exercise.

Fig. 1 is a schematic structural diagram of a miniaturized particle beam therapy device according to an embodiment of the present disclosure;

FIG. 2 is a front view of FIG. 1;

FIG. 3 is a right side view of FIG. 1;

fig. 4 is a schematic view of a miniaturized particle beam therapy device with the rotating support means hidden;

FIG. 5 is a top view of FIG. 4;

fig. 6 is a schematic view of a miniaturized particle beam therapy device according to an embodiment of the present disclosure provided with a barrel;

FIG. 7 is a schematic view of two annular support plates disposed on two sides of the rotary support device according to the embodiment of the disclosure;

FIG. 8 is a schematic diagram of a positional relationship between a synchrotron and a first conveyance path according to an embodiment of the disclosure;

FIG. 9 is a schematic view of a plane of a synchrotron according to an embodiment of the present disclosure and a plane of a second deflection magnet set;

FIG. 10 is a schematic view of a plane in which the first deflection magnet assembly of the disclosed embodiment is located;

fig. 11 is a schematic diagram of a vertical plane between a particle beam trajectory and a plane in which a particle beam trajectory of a synchrotron according to an embodiment of the present disclosure is located.

10, a 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. a vertical plane; 14. a center line of rotation; 100. fixing the supporting device; 110. a first support; 120. a second support; 200. a rotation support device; 210. an annular plate; 220. a barrel; 230. a support bar; 240. an annular support plate; 300. an injection device; 310. a drive device; 400. a synchrotron; 410. a first deflection magnet body; 500. a first deflection magnet group; 510. a second deflection magnet body; 600. a second deflection magnet group; 610. a third deflection magnet body; 700. a support device; 800. irradiating a head; 900. a second conveyance path; 901. a first focusing magnet; 902. a first deflection magnet; 910. a first conveyance path; 911. a second focusing magnet.

Detailed Description

In order that the above objects, features and advantages of the present disclosure may be more clearly understood, aspects of the present disclosure will be further described below. It should be noted that the embodiments and features of the embodiments of the present disclosure may be combined with each other without conflict.

In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present disclosure, but the present disclosure may be practiced in other ways than those described herein; it is to be understood that the embodiments disclosed in the specification are only a few embodiments of the present disclosure, and not all embodiments.

As shown in fig. 1 to 4, the miniaturized particle beam therapy device provided by the embodiment of the present application is used for emitting a particle beam to a target tissue, and includes a fixed support device 100, a rotary support device 200, an implantation 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).

The fixed support 100 is fixed to the ground as a mounting base, and in some embodiments, the base of the fixed support 100 is the ground. The base is provided with a driving rotating mechanism used as a supporting foundation. The implantation apparatus 300 includes a particle source, which is fixed to the rotation support 200, for generating a particle beam and primarily accelerating the particle beam to implant the particle beam into the synchrotron 400, which may be a proton beam, a carbon ion beam, or a helium ion beam.

As shown in fig. 2, a synchrotron 400 is fixed to the rotary support 200 for receiving and accelerating the particle beam generated by the implantation device 300, and the synchrotron 400 has a deflection magnet therein. Preferably, the synchrotron 400 is fixed on the rotary supporting device 200 in an upright state, i.e. the plane 10 where the particle beam motion trajectory is located in the synchrotron 400 is perpendicular to the supporting surface or horizontal plane of the base, so as to reduce the occupied internal space of the rotary supporting device 200. In other embodiments, the synchrotron 400 may be disposed in the rotating support 200 at an angle, i.e., the plane of the synchrotron 400 is at an angle to the vertical plane, which may reduce the height of the particle beam therapy device. Referring to fig. 9 and 10, the plane 10 of the synchrotron, the plane 11 of the first deflection magnet set, the plane 12 of the second deflection magnet set, and the plane of the first deflection magnet 902, which are located at the position and below, refer to the plane where the particle beam moves in each device or the plane where the center line of the channel of the particle beam is located.

The particle beam sequentially receives the accelerated particle beam through the first deflection magnet assembly 500 and the second deflection magnet assembly 600, and irradiates a target region 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 the relative position of the support device 700 and the irradiation head 800, and the support device 700 is preferably a treatment couch, which can be moved by a robot arm or a roller moving base provided at the bottom. The driving device 310 is used for driving the rotary supporting device 200 to rotate on the fixed supporting device 100. The synchrotron 400 is connected to a first transport duct 910, and the first transport duct 910 transports the particle beam obliquely upward.

As shown in fig. 4, the synchrotron 400 includes four sets of deflection magnet sets and an accelerating device. The number of the deflection magnet bodies in each set of deflection magnet groups is plural, and each set of deflection magnet groups includes four first deflection magnet bodies 410 as in the illustrated embodiment. The accelerating means may be a radio frequency accelerator. The first deflection magnet body 410 is used to deflect the particle beam by its magnetic field so that the particle beam can orbit around a circular orbit. The synchrotron 400 cyclically rotationally accelerates the particle beam to increase energy or maintain in a cyclic orbit. Further optimally, the first deflection magnet body 410 may also be provided with an edge focusing effect. The number of the first deflection magnet bodies 410 of each deflection magnet group shown in the figure is plural, and the structures and parameters of the first deflection magnet bodies 410 of each deflection magnet group are different, and the figure is only schematic and does not represent the actual structure of the first deflection magnet bodies 410. In some alternative embodiments, the number of the first deflection magnet bodies 410 in each deflection magnet group may be one, so that the beam current turns 90 degrees. In other embodiments, the shape of the synchrotron 400 can also be a rounded rectangle, etc., each rounded corner is composed of a plurality of deflection magnets, and the deflection magnets at the rounded corners can deflect the beam current.

As shown in fig. 1 and 3, the fixed supporting device 100 includes a base and a driving rotation mechanism. Preferably, the driving rotation mechanism may be a plurality of rollers and a driving device 310, the rollers are rotatably disposed on the base, axes of the plurality of rollers are parallel, the plurality of rollers are arranged on the base along a concave arc track, and a concave arc track is formed on an outer circumferential surface of each roller. The driving device 310 may drive at least one roller to rotate. As an embodiment, the driving device 310 may be a motor or a motor reducer, or a mechanism such as a reduction motor capable of providing the roller pivot by electric power. The driving rotation mechanism can also be other mechanisms capable of driving the object to rotate.

The rotary supporting device 200 is used for supporting the synchrotron 400, that is, the synchrotron 400 is installed on the rotary supporting device 200, and the synchrotron 400 is arranged coaxially with the rotary supporting device 200. The rotary supporting device 200 is rotatably disposed on the fixed supporting device 100, the rotary supporting device 200 has a rotation center line 14 when performing a rotation motion, and the rotary supporting device 200 can rotate around the rotation center line 14 by driving a power provided by the rotation mechanism. Preferably, the rotation center line 14 of the rotary supporting device 200 is disposed in parallel with a horizontal plane or with a supporting surface (i.e., an upper surface of the base) for easy installation and control. As shown in fig. 1 to 3, in some embodiments, the rotary supporting device 200 is an annular bracket, and specifically includes two annular plates 210, the two annular plates 210 are concentrically arranged, and the two annular plates 210 are spaced apart, so that a space for installing the synchrotron 400 is formed between the two annular plates 210. The outer circumference of the rotary supporting device 200 is equal in diameter to the arc track formed by the outer edges of the rollers in the fixed supporting device 100, and is rotatably disposed on the outer circumference of the rollers, the outer circumference of the rollers is in tangential contact with the outer circumference of the rotary supporting device 200, and the rollers can drive the rotary supporting device 200 to rotate when rotating.

It should be understood that the shape of the rotary supporting device 200 and the connection manner thereof with the fixed supporting device 100 are not limited to the above-mentioned structure, and other structures capable of mounting the fixed synchrotron 400 and rotating on the fixed supporting device 100 should also fall within the protection scope of the present disclosure. For example, the external shape of the rotary supporting device 200 may be square or polygonal, and the internal structure may be a hollow truss structure formed by fixedly connecting short round tubes and cylinders made of metal, so that the weight of the rotary supporting device 200 can be greatly reduced.

The rotatable connection between the rotary supporting device 200 and the fixed supporting device 100 can be in other forms, for example, a ring structure (the ring structure can be a circular arc or a split ring with a set angle for rotating the synchrotron 400, and the central angle of the circular arc or the split ring ensures that the synchrotron 400 can rotate by a preset angle, for example, 90 ° or more, preferably, the ring structure is shown in fig. 7) can be arranged on both end faces of the rotary supporting device 200, and two fixed supporting devices 100 are arranged in a matching manner. The ring structure is coaxial with the rotation center of the rotary support device 200, the ring structure is rotatably disposed on the fixed support device 100, and the outer diameter of the ring structure is smaller than the radial distance at the radially farthest position of the rotary support device 200, at this time, the fixed support device 100 enables the radius of the ring structure to be smaller. The outer peripheral surfaces of the two ring structures are matched with the rollers on the fixed supporting device 100, and the rotating supporting device 200 is driven to rotate through the engagement or friction between the rollers and the outer peripheral surfaces of the ring structures.

Specifically, as shown in fig. 7, a plurality of support rods 230 are disposed on both sides of the rotary support device 200, the annular structure is an annular support plate 240, the annular support plate 240 is disposed at an end of each support rod 230, and then the two annular support plates 240 are fixedly supported on both sides of the rotary support device 200 through the support rods 230. The outer peripheral surface of the annular supporting plate 240 is engaged with the roller on the fixed supporting device 100, and the rotation of the roller drives the annular supporting plate 240 to rotate. That is, rollers are disposed on both sides of the rotary supporting device 200, the rollers are rotatably disposed on the base, the axes of the rollers are parallel, the rollers are arranged on the base along a concave arc track, and the outer peripheral surfaces of the rollers form a concave arc track and are tangent to the outer edge of the annular supporting plate 240. The driving device 310 may drive at least one roller to rotate. The annular support plate 240 is supported by the roller sets on both sides, so that the rotary support device 200 can be supported and rotated more stably. Preferably, the rotation support device 200 is provided with a mechanism for preventing the rotation support device 200 from tilting during rotation, and the mechanism may be disposed inside the roller frame, on the base, or on the top or two side walls of the building where the particle beam therapy device is accommodated. For example, a roller or ball mechanism is mounted within the roller frame and the roller or ball mechanism is pressed against the surface of the rotary support device 200. Preferably, the supporting rod 230 is perpendicular to the plane of the rotary supporting device 200, and the center line of the ring-shaped supporting plate 240 coincides with the rotation center line 14 of the rotary supporting device 200, so that the rotary supporting device 200 is rotated along the center line thereof by the rotation of the ring-shaped supporting plate 240. Further optimally, the diameter of the annular support plate 240 is reduced as much as possible, so that the particle beam therapy device can be ensured not to interfere with each other when rotating. For example, it is first ensured that the portion of the rotary support device 200 having the largest radial distance does not interfere with the base during the rotation of the set angle. This design enables a further reduction of the overall height of the particle beam therapy device.

In other embodiments, the manner of driving the rotary supporting device to rotate may be through gear transmission, a driving device is provided on the base, the driving device is provided with a first gear in a connected manner, the driving device can drive the first gear to rotate, correspondingly, a second gear engaged with the first gear is provided on the periphery of the annular plate 210 or the annular supporting plate 240, and the annular plate 210 or the annular supporting plate 240 is driven to rotate through the rotation of the first gear. It can be seen that the specific matching manner of the fixed supporting device 100 and the rotary supporting device 200 is not limited, and it is only required that the fixed supporting device 100 drives the rotary supporting device 200 to rotate around the rotation center line 14.

As shown in fig. 1 to 5, the first deflection magnet assembly 500 is disposed on the rotary support device 200 for receiving and transporting the particle beam output from the first transporting channel 910, the first deflection magnet assembly 500 is arc-shaped, and the particle beam output from the first transporting channel 910 enters the first deflection magnet assembly 500 along a tangential direction of the input end of the first deflection magnet assembly 500. Specifically, the first transportation channel 910 is tangent to the connection point of the input end of the first deflection magnet assembly 500, i.e. the tangential direction of the input end of the first deflection magnet assembly 500 coincides with the transportation direction of the particle beam output by the synchrotron 400. The first deflecting magnet assembly 500 may be disposed on the rotary supporting device 200 through a connecting member, and may also be disposed on the rotary supporting device 200 through the first conveying passage 910. Specifically, the first deflection magnet group 500 includes a plurality of deflection magnets, wherein the first deflection magnet group 500 may also include one deflection magnet. The first deflection magnet group 500 includes four second deflection magnet bodies 510 in the illustrated embodiment, and the four second deflection magnet bodies 510 are used to deflect the particle beam by their magnetic fields such that the particle beam is output from the first deflection magnet group 500 in a set direction. Of course, the number of the second deflecting magnet bodies 510 may be other, for example, the number of the second deflecting magnet bodies 510 may also be one, and the central angle of the second deflecting magnet body 510 at the corresponding position in the second deflecting magnet group 500 may be the same as or different from the central angle of the first deflecting magnet body 410 at the corresponding position in the deflecting magnet group of the synchrotron 400, which is designed according to specific requirements. The central angle is the central angle of an arc formed by the motion tracks of the beams on the surface of the deflection magnet body or the deflection magnet group.

It is to be noted that tangent in the above and in the following is to be understood as being tangent to the trajectory formed by the direction of motion of the particle beam.

As shown in fig. 4, the second deflection magnet assembly 600 is connected to the first deflection magnet assembly 500 for receiving and transmitting the particle beam output from the first deflection magnet assembly 500, the structures and parameters of the deflection magnet assemblies and the number of deflection magnet bodies in the first deflection magnet assembly 500 and the synchrotron 400 are the same, and further, optimally, the structures and parameters of the deflection magnet assemblies and the number of deflection magnet bodies in the second deflection magnet assembly 600 and the synchrotron 400 are the same. The design mode can adopt 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 irradiation treatment path of the patient after the particle beam is led out from the synchrotron 400 and simplifying the control system. The second deflection magnet group 600 is arc-shaped, the first deflection magnet 902 is disposed 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 deflection magnet group 600 along the tangential direction of the input end of the second deflection magnet group 600, i.e., the transport direction of the particle beam deflected by the first deflection magnet 902 is parallel to the tangential direction of the input end of the second deflection magnet group 600. The output end of the second deflection magnet assembly 600 is directed toward the rotation center line 14 of the rotary support device 200. The second deflection magnet group 600 includes a plurality of deflection magnets, and there may be one deflection magnet in the second deflection magnet group 600. In some preferred embodiments, the second deflection magnet assembly 600 includes four third deflection magnet bodies 610 as in the illustrated embodiment, the four third deflection magnet bodies 610 being configured to deflect the particle beam by their magnetic fields such that the particle beam is output toward the rotational centerline 14 of the rotary support device 200. This design is such that the number of the second and third deflecting magnet bodies 510 and 610 is the same as the number of the first deflecting magnet bodies 410 of each set of deflecting magnet groups in the synchrotron 400, and further optimally, the radius of curvature of the deflecting portion constituted by the deflecting magnets in the first and second deflecting magnet groups 500 and 600 is the same as the radius of curvature of the deflecting portion constituted by the deflecting magnets in the synchrotron 400, and the number of the deflecting magnet bodies is four. Therefore, the first deflection magnet assembly 500 and the second deflection magnet assembly 600 can directly employ the deflection magnet assemblies in the synchrotron 400, so that the design and installation of the particle beam therapy apparatus as a whole are more convenient. And the deflection of the beam can be controlled by adopting basically the same control parameters, thereby reducing the difficulty and complexity of deflection control of the irradiation treatment path of the patient after the beam is led out from the synchrotron 400, and simplifying a control system.

Preferably, the synchrotron 400, the first deflection magnet group 500 and the second deflection magnet group 600 are each composed of a plurality of deflection magnet bodies having a focusing edge, and have a focusing function while achieving deflection of the particle beam, and an individual focusing magnet may be omitted, so that the overall volume and weight of the particle therapy apparatus can be greatly reduced, and when the vertically arranged particle beam therapy apparatus is rotated, the rotational driving is simpler and more powerful rotational driving is not required, and the accuracy control of the rotational movement is facilitated. It should be noted that the first deflection magnet assembly 500 and the second deflection magnet assembly 600 may also use magnets without edge focusing function, and cooperate with a separate focusing magnet for focusing.

The irradiation head 800 is attached to the end of the second deflection magnet assembly 600, and a particle beam is emitted from the irradiation head 800 to a target tissue of interest. Further optimally, a focusing magnet may be disposed between the irradiation head 800 and the second deflection magnet set 600. In other embodiments, the number of the first deflection magnet bodies 410 of each deflection magnet group in the synchrotron 400 may be one, and in this case, the number of the second deflection magnet bodies 510 and the number of the third deflection magnet bodies 610 should also be one, for convenience of design and installation. Specifically, one deflection magnet body achieves a 90 ° deflection, wherein the synchrotron requires 4 first deflection magnet bodies 410 to complete one beam revolution. Or one deflection magnet body to achieve 60 deg. deflection, the synchrotron needs 6 first deflection magnet bodies 410 to complete one beam revolution. Therefore, the deflection angle of the deflection magnet body is not limited, only the deflection requirement is met, and the number of the deflection magnet bodies in the synchrotron is required to enable the beam to rotate for one circle. It should be noted that, in this embodiment, separate focusing magnets are required to be disposed before and after each deflection magnet body, so as to avoid beam divergence.

The synchrotron 400, the first deflection magnet group 500, and the second deflection magnet group 600 integrated on the rotary support device 200 can significantly save space with respect to the structure in which the synchrotron 400 and the beam transport device are separately arranged. The particle beam outputted from the synchrotron 400 enters the first deflection magnet group 500 along the tangential direction of the input end of the first deflection magnet group 500, and therefore, there is no need to set a deflection magnet and a focusing magnet at the input end of the first deflection magnet group 500, so that the overall height of the particle beam therapy apparatus is reduced, the space occupied by the particle beam therapy apparatus can be reduced due to the height reduction, the overall construction cost and the construction difficulty of the particle beam therapy apparatus for accommodating buildings are further saved, and the microminiaturized synchrotron 400 particle beam therapy apparatus is realized. Among them, the particle beam therapy system is required to be housed in a building and to have a shielding function, and the thicker the wall used, the higher the height, and the more the construction cost and the construction difficulty are rapidly raised.

The deflecting magnets in the first deflecting magnet group 500 and the second deflecting magnet group 600 have the same structure and parameters as those of the deflecting magnets in the synchrotron 400, so that the deflection of the particle beam can be controlled by adopting basically the same control parameters, thereby reducing the difficulty and complexity of deflection control of the irradiation treatment path of the patient after the particle beam is led out of the synchrotron 400, and simplifying the control system.

As shown in fig. 2, the first transport channel 910 extends from the middle of the synchrotron 400 and extends obliquely upward, thereby transporting the particle beam obliquely upward. The junction of the first deflection magnet assembly 500 and the second deflection magnet assembly 600 is above the rotation centerline 14 of the rotary support device 200 and such that the output end of the second deflection magnet assembly 600 is directed toward the rotation centerline 14 of the rotary support device 200 to facilitate the emission of the particle beam from the top down. Further optimally, the first deflection magnet 902 deflects the particle beam output by the first deflection magnet set 500 to a horizontal direction or parallel to the support surface of the base. This design allows the tangential direction of the input end of the second deflection magnet assembly 600 to be parallel to the horizontal direction or the supporting surface of the base, so that the particle beam output by the second deflection magnet assembly 600 is perpendicular to the rotation center line 14 of the rotary support device 200. With the embodiment in which the input end of the second deflection magnet assembly 600 is horizontal and the output end is vertical, the second deflection magnet assembly 600 may directly employ the same deflection magnet assembly as the synchrotron 400, i.e., the structure, parameters, and number of deflection magnet bodies are the same, which simplifies the control system. This way the particle beam can be made substantially perpendicular to the virtual central axis of the support surface of the lying patient and of the torso thereof, which central axis can be set through the patient's tumor position and through the rotation center line 14, preferably in line with the rotation center line 14. When the synchrotron accelerator 400 is rotated, the beam can be rotated on a vertical plane perpendicular to the support plane and the virtual central axis on which the trunk of the patient is located.

In other embodiments, a second transportation channel 900 is disposed 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 transportation channel 900, and the output end of the second transportation channel 900 is tangent to the connection point of the second deflection magnet group 600. Specifically, the first deflection magnet 902 is disposed 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 transportation channel 900, and the output direction of the particle beam deflected by the first deflection magnet 902 is the same as the beam transportation direction of the second transportation channel 900. The length of the second conveying passage 900 is designed according to specific requirements such that the output end of the second deflection magnet assembly 600 is directed toward the rotation center line 14 of the rotary support device 200. Preferably, the second transportation channel 900 is oriented to ensure that the beam transportation direction is arranged along the horizontal direction or parallel to the supporting surface of the base, i.e. the second deflection magnet assembly 600 is designed to output the particle beam perpendicular to the rotation center line 14 of the rotation supporting device 200.

Further optimally, the outer periphery of the second conveying passage 900 is provided with the first focusing magnets 901, the number of the first focusing magnets 901 is preferably one or two, and of course, the number of the first focusing magnets 901 can also be multiple, but this will increase the length of the second conveying passage 900. By arranging the first deflecting magnet 902 and the first focusing magnet 901, the length of the second transporting channel 900 can be shortened, which can reduce the axial length of the particle beam therapy device, and if the radiation of the accelerator and the injection device is too large during the therapy, the distance between the accelerator and the patient needs to be controlled not to be too small, and a shielding device is added. At this time, the length of the second conveyance path 900 is adjusted as necessary.

The above and below axial directions refer to the longitudinal direction of the rotation center line 14 of the rotation support device 200.

As shown in fig. 5, the first deflection magnet assembly 500 is positioned at an angle to the plane of the second deflection magnet assembly 600. The second deflection magnet assembly 600 is thus able to deflect the particle beam downwards, while a plurality of first focusing magnets 901 are arranged between the first deflection magnet assembly 500 and the second deflection magnet assembly 600 in order to avoid divergence of the particle beam, since the plane in which the first deflection magnet assembly 500 is located is at an angle to the plane in which the second deflection magnet assembly 600 is located. Specifically, since the first deflection magnet group 500 and the second deflection magnet group 600 are connected by the second conveying path 900, the first focusing magnets 901 are disposed on the periphery of the second conveying path 900, wherein the number of the first focusing magnets 901 may be one, two or more, and the first focusing magnets 901 are designed according to the length of the second conveying path 900, and certainly, on the premise that beam focusing can be achieved, and during treatment, the radiation of the synchrotron 400, the injection device 300, and the like is not too large or can be reduced to an allowable range after being shielded by a necessary radiation shielding device, in order to reduce the length of the second conveying path 900, the number of the first focusing magnets 901 is preferably smaller. In some embodiments of the present disclosure, the radiation of the synchrotron 400, the injection device 300, etc. may be within a tolerable range, or may be reduced to a tolerable range by shielding.

The first deflection magnet group 500 deflects the particle beam from the transport direction of the first transport channel 910 to a set direction, the first deflection magnet 902 deflects the particle beam output from the first transport channel 910 to a horizontal direction, and the second deflection magnet group 600 can deflect the particle beam from the horizontal direction to a vertical direction, so that the structure of the particle beam therapy apparatus can be simplified, the installation is convenient, and the phenomenon that an included angle between the second transport channel 900 and a reference object cannot be accurately positioned during the installation, so that the installation error occurs, and further, a therapy accident occurs during the therapy of the particle beam therapy apparatus is avoided. And the design mode enables the heights of the first deflection magnet group 500 and the second deflection magnet group 600 to be reduced, so that the height of the whole particle beam therapy device is reduced, and the volume of a building for accommodating the particle beam therapy device is further saved. It should be noted that the irradiation head 800 is designed to be above the rotation center line 14 of the rotary supporting device 200, and the irradiation head 800 is spaced from the rotation center line 14 of the rotary supporting device 200 by a certain distance to accommodate the patient.

In other embodiments, the output end of the first deflection magnet assembly 500 is tilted obliquely upward in the event that there is insufficient space between the illumination head 800 and the rotational centerline 14 of the rotational support apparatus 200 to accommodate the patient. Specifically, as shown in fig. 8, by changing the included angle between the first conveying channel 910 and the plane where the synchrotron 400 is located, or under the condition that the plane of the first deflection magnet assembly 500 is kept unchanged relative to the synchrotron 400, the central angle of the particle beam trajectory of the first deflection magnet assembly 500 is increased, the beam direction at the output end of the first deflection magnet assembly 500 is changed, and thus the output end of the first deflection magnet assembly 500 is inclined upward. Meanwhile, the direction of the particle beam outputted from the first deflection magnet group 500 is still turned to the horizontal direction by the first deflection magnet 902.

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, a manner of adjusting the length of the first conveying channel 910 may also be adopted, and of course, the length of the first conveying channel 910 should not be too short or too long, and should be within a design range, and accordingly, the angle of the center of the first deflection magnet group 500, the angle of the center of the second deflection magnet group 600, and the length of the first conveying pipe need to be adjusted according to the beam direction of the output end of the second deflection magnet group 600, so as 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 central angle is the central angle of an arc formed by the motion tracks of the beams on the surface of the deflection magnet body or the deflection magnet group.

The plane of the particle beam deflected by the first deflection magnet 902 coincides with the plane of the first deflection magnet set 500, i.e. one of the planes of the particle beam deflected by the first deflection magnet 902 coincides with the plane of the movement trajectory of the particle beam in the first deflection magnet set 500. This design allows a better deflection of the particle beam.

As shown in fig. 11, the synchrotron 400 is connected with a first transportation channel 910, a vertical plane 13 between a particle beam motion trajectory and a plane where the particle beam motion trajectory of the synchrotron 400 is located is tangent to the particle beam trajectory before being led out from the synchrotron 400, and the vertical plane 13 between the particle beam motion trajectory in the first transportation channel 910 and the plane where the particle beam motion trajectory of the synchrotron 400 is located is perpendicular to a horizontal plane or a supporting plane of a base, so that the particle beam can enter the first transportation channel 910. As shown in fig. 1 and 3, the output end of the first conveying passage 910 extends obliquely upward, the input end of the first deflection magnet assembly 500 is connected to the first conveying passage 910, and the first conveying passage 910 is tangent to the connection of the first deflection magnet assembly 500. Wherein the output end of the first conveying passage 910 is inclined obliquely upward such that the particle beam output through the first deflection magnet assembly 500 is above the rotation center line 14 of the rotary support device 200. Further optimally, the periphery of the first conveying channel 910 is provided with a second focusing magnet 911.

As shown in fig. 6, in this embodiment, the particle beam therapy apparatus further includes a cylinder 220, the cylinder 220 is a cylinder and is coaxially fixed with the rotation support device 200, the first deflection magnet assembly 500, the second transportation channel 900 and a part of the second deflection magnet assembly 600 are located outside the cylinder 220, an output end of the second deflection magnet assembly 600 passes through a sidewall of the cylinder 220 and is inserted into an interior of the cylinder 220, and the second deflection magnet assembly 600 is fixedly connected with the cylinder 220, so as to enhance the stability of the second deflection magnet assembly 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 apparatus during the rotation process, a connecting arm or a connecting frame may be disposed on the outer periphery of the barrel 220, and the first deflection magnet assembly 500, the second deflection magnet assembly 600, the first transportation channel 910, the second transportation channel 900, the irradiation head 800, and the plurality of focusing magnets may be fixedly connected by the connecting arm or the connecting frame.

In other embodiments, when the axial length of the particle beam therapy device is small, the cylinder 220 is not required, and in this case, the first deflection magnet assembly 500, the second deflection magnet assembly 600, the first transportation channel 910, the second transportation channel 900, the irradiation head 800, and the plurality of focusing magnets need to be fixedly connected through a fixed connection device, so as to increase the stability of the rotation process. Wherein, the fixed connecting device can also be a connecting arm or a connecting frame. Because linking arm and link are all comparatively common among the prior art, and its mode of setting is diversified, it only need play connect fixed action can, consequently, do not do too much description in this embodiment.

The rotary supporting device 200 and the cylinder 220 are commonly supported by the first support 110 and the second support 120. In some alternative embodiments, the cylinder 220 may be a square cylinder, an elliptical cylinder, or a prism cylinder, although the cylinder 220 with these shapes may also be provided with a cylindrical fitting portion adapted to the circular arc orbit of the first support 110 and the second support 120.

It should be noted that in this patent, the particle beam motion trajectory in the deflecting magnet body or deflecting magnet set or synchrotron 400 or transport channel does not necessarily remain constant. In addition, when the number of the deflecting magnet bodies in the synchrotron 400 and the first or second deflecting magnet groups 500 or 600 is plural, the movement locus of the beam in the connecting channel between the deflecting magnet bodies is not necessarily an arc, so the central angle of the deflecting magnet group mentioned in this patent is the central angle of a virtual arc, and the arc is formed by fitting the movement locus of the beam in each deflecting magnet body in the deflecting magnet group.

In this document, relational terms such as "first" and "second," and the like, may be used solely to distinguish one entity or action from another entity or action without necessarily requiring or implying any actual such relationship or order between such entities or actions. Also, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. Without further limitation, an element defined by the phrase "comprising an … …" does not exclude the presence of other identical elements in a process, method, article, or apparatus that comprises the element.

The foregoing are merely exemplary embodiments of the present disclosure, which enable those skilled in the art to understand or practice the present disclosure. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other embodiments without departing from the spirit or scope of the disclosure. Thus, the present disclosure is not intended to be limited to the embodiments shown herein but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.

Claims (17)

1. A miniaturized particle beam therapy device for emitting a particle beam toward a target tissue, comprising:

the fixed supporting device (100) comprises a base, wherein a driving rotating mechanism is arranged on the base and used as a supporting foundation;

the particle beam accelerator comprises a synchrotron (400) and a particle beam detector, wherein the synchrotron (400) is provided with a deflection magnet, a first conveying channel (910) is connected to the synchrotron (400), and the first conveying channel (910) conveys the particle beam obliquely upwards;

a rotary supporting device (200) for supporting the synchrotron (400), wherein the rotary supporting device (200) is rotatably arranged on the fixed supporting device (100); the rotary supporting device (200) has a rotary central line (14) when in rotary motion, and the rotary supporting device (200) can rotate around the rotary central line (14) by the power provided by the driving and rotating mechanism;

a first deflection magnet assembly (500) disposed on the rotary support device (200) for receiving and transporting the particle beam output from the first transport channel (910), wherein the first deflection magnet assembly (500) is arc-shaped, and the particle beam output from the first transport channel (910) enters the first deflection magnet assembly (500) along a tangential direction of an input end of the first deflection magnet assembly (500);

a second deflection magnet group (600) connected with the first deflection magnet group (500), for receiving and transmitting the particle beams output by the first set of deflection magnets (500), the first set of deflection magnets (500) being identical in structure and parameters as well as in number of deflection magnet bodies in the synchrotron (400), the second deflection magnet group (600) is arc-shaped, a first deflection magnet (902) is arranged 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 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 rotary supporting device (200);

an irradiation head (800) connected to a distal end of the second deflection magnet group (600), from which irradiation head (800) a particle beam is emitted to a target tissue of interest.

2. The miniaturized particle beam therapy device of claim 1, wherein the first deflection magnet (902) deflects the particle beams output by the first deflection magnet set (500) to a horizontal direction or parallel to a support surface of the base.

3. The miniaturized particle beam therapy device of claim 1, wherein a second transportation channel (900) is provided between the first deflection magnet set (500) and the second deflection magnet set (600), the particle beam deflected by the first deflection magnet (902) enters the second transportation channel (900), and the output end of the second transportation channel (900) is tangential to the connection of the second deflection magnet set (600).

4. A miniaturized particle beam therapy device according to claim 3, characterized in that the second transportation channel (900) is arranged in a horizontal direction or parallel to the support surface of the base.

5. A miniaturized particle beam therapy device according to claim 3, characterized in that the outer circumference of the second transportation channel (900) is provided with first focusing magnets (901).

6. The miniaturized particle beam therapy device of claim 1, wherein a plane in which the first deflection magnet assembly (500) is located forms an angle with a plane in which the second deflection magnet assembly (600) is located.

7. The miniaturized particle beam therapy device of claim 1, wherein the first deflection magnet (902) is located in a plane that coincides with a plane in which the first deflection magnet set (500) is located.

8. The miniaturized particle beam therapy device of claim 1, wherein the particle beam output by the second deflection magnet assembly (600) is perpendicular to a rotation centerline (14) of the rotary support device (200).

9. The miniaturized particle beam therapy device of claim 1, wherein a rotation centerline (14) of the rotational support device (200) is parallel to a horizontal plane or a support plane of the base.

10. The miniaturized particle beam therapy device of claim 1, wherein the outer circumference of the first transportation channel (910) is provided with a second focusing magnet (911).

11. The miniaturized particle beam therapy device of claim 1, wherein the second deflection magnet assembly (600) is identical to the deflection magnet assembly of the synchrotron (400) in structure and parameters and the number of deflection magnet bodies.

12. The miniaturized particle beam therapy device of claim 1 or 11, wherein the number of deflection magnet bodies of the first deflection magnet assembly (500) and the deflection magnet assemblies within the synchrotron (400) is four each.

13. The miniaturized particle beam therapy device of claim 1 or 11, wherein the number of deflection magnet bodies of the first deflection magnet assembly (500), the second deflection magnet assembly (600) and the deflection magnet assembly within the synchrotron (400) is four.

14. The miniaturized particle beam therapy device according to claim 1, wherein said rotating support means (200) is provided with a ring structure on both sides, said ring structure being coaxial with said rotating support means (200), said ring structure being rotatably arranged on said stationary support means (100), and said ring structure having an outer diameter smaller than the radial distance at which said rotating support means (200) is radially farthest.

15. The miniaturized particle beam therapy device of claim 1, wherein the deflection magnet bodies within the first deflection magnet set (500), the deflection magnet bodies within the second deflection magnet set (600), and the deflection magnet bodies of the deflection magnet sets within the synchrotron (400) each have a focusing edge.

16. The miniaturized particle beam therapy device of claim 1, wherein a vertical plane (13) between the trajectory of the particle beam in the first transportation channel (910) and a plane in which the trajectory of the particle beam in the synchrotron (400) lies is perpendicular to a horizontal plane or to a supporting plane of the base.

17. The miniaturized particle beam therapy device of claim 1, wherein a plane (10) of the particle beam trajectory in the synchrotron (400) is perpendicular to a support or horizontal plane of the base.

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