Directional proton treatment head of radiotherapy equipment

Abstract

The invention discloses a radiotherapy equipment directional proton treatment head which comprises a polymerization cover, a proton beam section control device is arranged on the polymerization cover, a plurality of directional proton emission heads are arranged in the polymerization cover, the directional proton emission heads are connected in series through a sliding rod structure, and the directional proton emission heads are arranged in the polymerization cover in a sliding mode in the length direction of the polymerization cover. The sliding rod structure is used for driving the directional proton emission head to linearly slide so as to correspond to different ray holes. The multiple ray holes are formed in the surface of the polymerization cover through the proton beam section control device, the directional proton emission head is driven by the sliding rod structure to linearly slide in the arrangement direction of the ray holes, and the purpose of adjusting the diameter of the proton beam is achieved. In addition, the device utilizes selective disconnection of the first connecting rod and the second connecting rod to form proton beams with different intensities for targeted radiation, so that the flexibility and the pertinence of the whole proton treatment head are higher.

Description

Technical Field

[0001] The present invention relates to the technical field of medical equipment, and in particular to a directional proton therapy head of radiotherapy equipment. Background Art

[0002] As an advanced radiotherapy technology, proton therapy has received extensive attention in the field of tumor treatment in recent years. Compared with traditional X-ray radiotherapy, proton therapy utilizes the Bragg Peak characteristics of the proton beam to release most of the energy in the tumor target area, thereby minimizing damage to surrounding healthy tissues.

[0003] However, the proton therapy heads of most current proton therapy devices are proton output devices with a fixed diameter. Therefore, for tumors of varying sizes, the proton beam of a fixed diameter cannot be flexibly adjusted according to the actual size of the tumor, resulting in some tumor areas not being fully covered or normal tissues being exposed to unnecessary radiation. Summary of the invention

[0004] The object of the present invention is to provide a directional proton therapy head for radiotherapy equipment to solve the technical problem in the prior art that it is difficult to adjust the output diameter of the proton beam according to the size of the tumor.

[0005] In order to solve the above technical problems, the present invention specifically provides the following technical solutions:

[0006] A directional proton therapy head of a radiotherapy device comprises a polymer cover, on which a plurality of proton beam cross-section control devices are arranged, each of which is connected to the polymer cover to form a plurality of ray holes, the plurality of ray holes are linearly arranged along the length direction of the polymer cover, and the proton beam cross-section control devices can adjust the diameter of the proton beam passing through different ray holes;

[0007] A plurality of directional proton emission heads are arranged in the polymer cover, and the plurality of directional proton emission heads are arranged in one-to-one correspondence with the plurality of proton beam cross-section control devices. The plurality of directional proton emission heads are connected in series by a sliding rod structure, and the directional proton emission heads are slidably arranged in the polymer cover along the length direction of the polymer cover, and the sliding rod structure is used to drive the directional proton emission heads to slide linearly to correspond to different ray holes.

[0008] As a preferred solution of the present invention, the polymer cover is arranged in an arc shape, and the multiple directional proton emission heads are arranged in the arc-shaped internal chamber of the polymer cover. The multiple directional proton emission heads emit proton beams through the ray holes to the same focal point on one side of the polymer cover.

[0009] As a preferred solution of the present invention, the directional proton emission heads are linearly arranged along the length direction of the polymer cover, and the directional proton emission heads are also arranged in an array along the arc contour of the polymer cover. The directional proton emission heads and the proton beam cross-section control devices are arranged in a one-to-one correspondence. A plurality of the directional proton emission heads are interconnected to form a proton emission head joint assembly, and the sliding rod structure is connected to the proton emission head joint assembly to drive the proton emission head joint assembly to slide linearly in the polymer cover.

[0010] As a preferred solution of the present invention, the sliding rod structure includes a first connecting rod and a second connecting rod, the first connecting rod is arranged in the polymer cover and fixedly connected to at least one of the directional proton emission heads, one end of the second connecting rod is arranged in the polymer cover and fixedly connected to at least one of the directional proton emission heads, and the other end is arranged outside the polymer cover and connected to a driving device, and the two ends of the first connecting rod are movably connected to the polymer cover and the second connecting rod respectively;

[0011] Wherein, when the first connecting rod is connected to the second connecting rod, the first connecting rod is disconnected from the polymer cover;

[0012] When the first connecting rod is connected to the polymer cover, the first connecting rod is disconnected from the second connecting rod.

[0013] As a preferred solution of the present invention, the first connecting rod is hollow inside, and the two end surfaces of the first connecting rod are respectively provided with a first straight groove and a second straight groove, the first straight groove and the second straight groove are respectively arranged perpendicular to each other, a rotating column is coaxially arranged inside the first connecting rod, and the two end surfaces of the rotating column are respectively provided with clamping limit members, the clamping limit members include clamping gaps, the clamping gaps at both ends of the rotating column are aligned, and the first cross pin and the second cross pin are respectively arranged in the clamping gaps at both ends of the rotating column, the first cross pin is rotatably installed on the inner wall of the polymer cover through a connecting shaft, and the second cross pin is fixedly installed on the end of the second connecting rod through a connecting shaft.

[0014] Compared with the prior art, the present invention has the following beneficial effects:

[0015] The present invention forms a plurality of ray holes on the surface of the polymer cover through a proton beam cross-section control device, and drives the directional proton emission head to slide linearly along the arrangement direction of the ray holes through a sliding rod structure, so that the proton beam can pass through different ray holes to form a cross-section change, thereby achieving the purpose of adjusting the proton beam diameter. In addition, through the structural design of the sliding rod structure in the present device, the selective disconnection of the first connecting rod and the second connecting rod is utilized, so that when the overall device faces tumors of different sizes, the sliding rod structure can selectively apply different numbers of directional proton emission heads to form proton beams of different intensities for targeted radiation, making the overall proton therapy head more flexible and targeted, while improving the overall energy efficiency of the equipment and reducing operating costs. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] In order to more clearly illustrate the implementation methods of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for the implementation methods or the description of the prior art. Obviously, the drawings in the following description are only exemplary, and for ordinary technicians in this field, other implementation drawings can be derived from the provided drawings without creative work.

[0017] Figure 1 It is a front cutaway schematic diagram of the present invention;

[0018] Figure 2 It is a schematic diagram of the overall structure of the present invention;

[0019] Figure 3 It is one of the schematic diagrams of the side section structure of the present invention;

[0020] Figure 4 This is the second schematic diagram of the side cutaway structure of the present invention;

[0021] Figure 5 For the present invention Figure 4 The enlarged view of point A in the middle;

[0022] Figure 6 is a schematic cross-sectional view of the end portion of the first connecting rod of the present invention;

[0023] Figure 7 It is a schematic structural diagram of two end surfaces of the first connecting rod of the present invention;

[0024] Figure 8 This is a diagram showing the use process of the first connecting rod of the present invention.

[0025] The numbers in the figure represent the following:

[0026] 1. Polymer cover; 2. Proton beam cross-section control device; 3. Ray hole; 4. Directional proton emitter; 5. Proton emitter joint assembly; 6. First connecting rod; 7. Second connecting rod; 8. First straight groove; 9. Second straight groove; 10. Rotating column; 11. Clamping limiter; 12. Clamping gap; 13. First cross pin; 14. Second cross pin. DETAILED DESCRIPTION

[0027] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0028] like Figures 1 to 8 As shown, the present invention provides a directional proton therapy head of a radiotherapy device, comprising a polymer cover 1, on which a plurality of proton beam cross-section control devices 2 are arranged, such as Figure 1 , Figure 2 and Figure 3 As shown, the proton beam cross-section control device 2 is composed of a plurality of independent control parts capable of adjusting the diameter of the proton beam. Each independent control part is tilted toward the focal point on one side of the polymer cover 1, and the proton beams emitted by each independent control part converge at one point for targeted therapy. Each independent control part can control the proton beam to form different diameters such as 2mm, 4mm, 8mm, and 16mm. Each proton beam cross-section control device 2 is connected to the polymer cover 1 to form a plurality of ray holes 3. The plurality of ray holes 3 are perforations formed by connecting a plurality of independent control parts to the polymer cover 1. The plurality of ray holes 3 are linearly arranged along the length direction of the polymer cover 1. When the proton beam emitted by the directional proton emission head 4 passes through the independent control part, the diameter of the proton beam is changed. The proton beam cross-section control device 2 can adjust the diameter of the proton beam emitted from different ray holes 3.

[0029] A plurality of directional proton emission heads 4 are arranged in the polymer cover 1. The plurality of directional proton emission heads 4 are arranged in one-to-one correspondence with a plurality of proton beam cross-section control devices 2 (each proton beam cross-section control device 2 includes a plurality of independent control parts with different diameters). The plurality of directional proton emission heads 4 are connected in series by a sliding rod structure. The directional proton emission heads 4 are slidingly arranged in the polymer cover 1 along the length direction of the polymer cover 1. The sliding rod structure is used to drive the proton emission heads to slide linearly to correspond to different ray holes 3.

[0030] The arc-shaped arrangement of the aggregate cover 1 can more conveniently concentrate the proton beams emitted by multiple directional proton emission heads 4 at the same focus. The multiple directional proton emission heads 4 are arranged in the arc-shaped internal chamber of the aggregate cover 1. The multiple directional proton emission heads 4 emit proton beams to the same focus on one side of the aggregate cover 1 through the ray holes 3 to treat the target area.

[0031] In practical application, this device can be used as Figure 1 As shown, a plurality of directional proton emission heads 4 are provided, and a proton beam formed by the combination of the plurality of directional proton emission heads 4 has a higher intensity of energy for targeted therapy. The plurality of directional proton emission heads 4 are linearly arranged along the length direction of the polymer cover 1, and the plurality of directional proton emission heads 4 are also arranged in an array along the arc contour of the polymer cover 1. The directional proton emission heads 4 are arranged in a one-to-one correspondence with the proton beam cross-section control device 2. Each directional proton emission head 4 forms a proton beam of unequal diameter through a proton beam cross-section control device 2. The plurality of directional proton emission heads 4 are interconnected to form a proton emission head joint assembly 5. The sliding rod structure is connected to the proton emission head joint assembly 5 to drive the proton emission head joint assembly 5 to slide linearly in the polymer cover 1.

[0032] Furthermore, when targeting tumors of different sizes, by adjusting the number of directional proton emitters 4 used, the energy intensity of the proton beam acting on the target area can be adjusted to adapt to tumors of different sizes, thereby reducing damage to surrounding cells and reducing the occurrence of side effects. Figure 4 As shown, the sliding rod structure includes a first connecting rod 6 and a second connecting rod 7. The first connecting rod 6 is arranged in the polymer cover 1 and fixedly connected to at least one directional proton emission head 4. One end of the second connecting rod 7 is arranged in the polymer cover 1 and fixedly connected to at least one directional proton emission head 4, and the other end is arranged outside the polymer cover 1 and connected to a driving device. The two ends of the first connecting rod 6 are movably connected to the polymer cover 1 and the second connecting rod 7 respectively. When the first connecting rod 6 is connected to the second connecting rod 7, the first connecting rod 6 is disconnected from the polymer cover 1. When the first connecting rod 6 is connected to the polymer cover 1, the first connecting rod 6 is disconnected from the second connecting rod 7.

[0033] Firstly, the linear movement of the second connecting rod 7 can drive the movement of the entire proton emission head joint assembly 5 to change the diameter of the proton beam.

[0034] Secondly, by disconnecting the first connecting rod 6 from the second connecting rod 7, the first connecting rod 6 can be idle when the second connecting rod 7 moves, so that only the directional proton emitting head 4 connected to the first connecting rod 6 is moved, while the directional proton emitting head 4 connected to the second connecting rod 7 is idle and does not work, thereby changing the number of directional proton emitting heads 4 that need to be used. Specifically, when applied to a tumor of smaller size, first, when the first connecting rod 6 is connected to the second connecting rod 7, the second connecting rod 7 is slid to drive the overall proton emitting head joint assembly 5 to move, and move to a position where the directional proton emitting head 4 abuts against the polymer cover 1 and is not aligned with the ray hole 3. At this time, the directional proton emitting head 4 connected to the first connecting rod 6 cannot emit a proton beam, and then the first connecting rod 6 is disconnected from the second connecting rod 7, so that by moving the second connecting rod 7 and aligning it with the ray hole 3, a proton beam can be formed for treatment, thereby achieving the purpose of reducing the number of directional proton therapy heads used to change the proton beam output intensity, thereby coping with tumors of different sizes.

[0035] Finally, in order to prevent the first connecting rod 6 from being disconnected from the second connecting rod 7 and the second connecting rod 7 from accidentally sliding in the polymer cover 1, the present device allows the first connecting rod 6 to be connected to the polymer cover 1 when the first connecting rod 6 is disconnected from the second connecting rod 7, thereby limiting the movement of the first connecting rod 6. When the first connecting rod 6 and the second connecting rod 7 are connected to form an integral structure, the second connecting rod 7 is disconnected from the polymer cover 1, thereby enabling the overall proton emitter joint assembly 5 to be moved.

[0036] Specifically, Figure 5 As shown, the first connecting rod 6 is hollow inside, and the two end surfaces of the first connecting rod 6 are respectively provided with a first straight groove 8 and a second straight groove 9, the first straight groove 8 and the second straight groove 9 are arranged perpendicular to each other, and a rotating column 10 is coaxially rotatably arranged inside the first connecting rod 6, and the two end surfaces of the rotating column 10 are respectively provided with clamping limit members 11, and the clamping limit members 11 include clamping gaps 12, and the clamping gaps 12 at both ends of the rotating column 10 are aligned, and the first cross pin 13 and the second cross pin 14 are respectively arranged in the clamping gaps 12 at both ends of the rotating column 10, the first cross pin 13 is rotatably installed on the inner wall of the polymer cover 1 through a connecting shaft, and the second cross pin 14 is fixedly installed on the end of the second connecting rod 7 through a connecting shaft.

[0037] like Figure 8 The diagram shows the first connecting rod 6 in four states when in use, wherein: Figure 8 The first group of pictures from top to bottom shows the initial state of the first connecting rod 6, with the first transverse pin 13 and the second transverse pin 14 inserted into the clamping gap 12. Afterwards, the second connecting rod 7 is rotated 90 degrees, which drives the second transverse pin 14 to rotate 90 degrees, and at the same time drives the first transverse pin 13 to rotate through the rotating column 10, as shown in FIG. Figure 8As shown in the second group of figures, at this time, the second transverse pin 14 is misaligned with the second straight slot 9, the second connecting rod 7 is connected to the first connecting rod 6 (as shown in the right figure), and the first transverse pin 13 is in the same position as the first straight slot 8. Therefore, at this time, the first connecting rod 6 and the second connecting rod 7 are connected to each other, and the first connecting rod 6 is disconnected from the polymer cover 1 (as shown in the left figure), so that all the directional proton emission heads 4 of the whole can be driven to move through the second connecting rod 7.

[0038] Further, when only a small number of directional proton emitters 4 are needed, the sliding rod structure is moved to sleeve the first straight slot 8 and the first cross pin 13 in the same position, and then the second connecting rod 7 is rotated 90 degrees, as shown in FIG. Figure 8 As shown in the third group of figures, at this time, the first transverse pin 13 is misaligned with the first straight groove 8, so that the first connecting rod 6 is connected to the polymer cover 1 (as shown in the left figure), and at this time the second transverse pin 14 is in the same position as the second straight groove 9. At this time, pulling out the second connecting rod 7 can drive the directional proton emission head 44 connected only to the second connecting rod 7 to move, thereby reducing the number of applications of the directional proton emission head 4.

[0039] Further, the second transverse pin 14 is inserted into the second straight slot 9 correspondingly, and rotated 90 degrees, as shown in FIG. Figure 8 As shown in the fourth group of figures, the first connecting rod 6 and the second connecting rod 7 are connected (as shown in the right figure), and the first connecting rod 6 is disconnected from the polymer cover 1 (as shown in the left figure), so that it can be used repeatedly.

[0040] The rotating column 10 can be connected to the first connecting rod 6 with a certain connection force through a magnetic attraction part, so as to prevent the vibration from causing the rotation dislocation, making it difficult for the cross pin to be inserted into the straight groove.

[0041] The above embodiments are only exemplary embodiments of the present application and are not intended to limit the present application. The protection scope of the present application is defined by the claims. Those skilled in the art may make various modifications or equivalent substitutions to the present application within the essence and protection scope of the present application, and such modifications or equivalent substitutions shall also be deemed to fall within the protection scope of the present application.

Claims

1. A directional proton therapy head for radiotherapy equipment, characterized in that: The invention comprises a polymer cover (1), wherein a plurality of proton beam cross-section control devices (2) are arranged on the polymer cover (1), each of the proton beam cross-section control devices (2) is connected to the polymer cover (1) to form a plurality of ray holes (3), the plurality of ray holes (3) are linearly arranged along the length direction of the polymer cover (1), and the proton beam cross-section control devices (2) are capable of adjusting the diameter of the proton beams passing through different ray holes (3); A plurality of directional proton emission heads (4) are arranged in the polymer cover (1), the plurality of directional proton emission heads (4) are arranged in one-to-one correspondence with the plurality of proton beam cross-section control devices (2), the plurality of directional proton emission heads (4) are connected in series by a slide bar structure, the directional proton emission heads (4) are slidably arranged in the polymer cover (1) along the length direction of the polymer cover (1), and the slide bar structure is used to drive the directional proton emission heads (4) to slide linearly to correspond to different ray holes (3).

2. A directional proton therapy head for radiotherapy equipment according to claim 1, characterized in that: The polymer cover (1) is arranged in an arc shape, and a plurality of directional proton emission heads (4) are arranged in the arc-shaped internal chamber of the polymer cover (1). The plurality of directional proton emission heads (4) emit proton beams through the ray holes (3) toward the same focal point on one side of the polymer cover (1).

3. A directional proton therapy head for radiotherapy equipment according to claim 2, characterized in that: The directional proton emission heads (4) are linearly arranged along the length direction of the polymer cover (1); the directional proton emission heads (4) are also arranged in an array along the arc-shaped contour of the polymer cover (1); the directional proton emission heads (4) and the proton beam cross-section control device (2) are arranged in a one-to-one correspondence; a plurality of the directional proton emission heads (4) are interconnected to form a proton emission head joint assembly (5); and the sliding rod structure is connected to the proton emission head joint assembly (5) to drive the proton emission head joint assembly (5) to slide linearly in the polymer cover (1).

4. A directional proton therapy head for radiotherapy equipment according to claim 1, characterized in that: The sliding rod structure comprises a first connecting rod (6) and a second connecting rod (7); the first connecting rod (6) is arranged in the polymer cover (1) and fixedly connected to at least one of the directional proton emission heads (4); one end of the second connecting rod (7) is arranged in the polymer cover (1) and fixedly connected to at least one of the directional proton emission heads (4); the other end of the second connecting rod (7) is arranged outside the polymer cover (1) and connected to a driving device; the two ends of the first connecting rod (6) are movably connected to the polymer cover (1) and the second connecting rod (7) respectively; Wherein, when the first connecting rod (6) is connected to the second connecting rod (7), the first connecting rod (6) is disconnected from the polymer cover (1); When the first connecting rod (6) is connected to the polymer cover (1), the first connecting rod (6) is disconnected from the second connecting rod (7).

5. A directional proton therapy head for radiotherapy equipment according to claim 4, characterized in that: The first connecting rod (6) is hollow inside, and the two end surfaces of the first connecting rod (6) are respectively provided with a first straight groove (8) and a second straight groove (9), and the first straight groove (8) and the second straight groove (9) are arranged perpendicular to each other. A rotating column (10) is coaxially arranged inside the first connecting rod (6), and the two end surfaces of the rotating column (10) are respectively provided with clamping limit members (11), and the clamping limit members (11) include clamping gaps (12). The clamping gaps (12) at both ends of the rotating column (10) are arranged in alignment, and the clamping gaps (12) at both ends of the rotating column (10) are respectively provided with a first cross pin (13) and a second cross pin (14), and the first cross pin (13) is rotatably mounted on the inner wall of the polymer cover (1) through a connecting shaft, and the second cross pin (14) is fixedly mounted on the end of the second connecting rod (7) through a connecting shaft.

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