Collimation assembly, radiotherapy head and medical equipment

Abstract

The embodiment of the utility model provides a collimation assembly, a radiotherapy head and medical equipment. The collimation assembly comprises a first collimation body and a second collimation body; the first collimation body and the second collimation body are arranged side by side; the side, close to the radioactive source, of the first collimation body and the side, close to the radioactive source, of the second collimation body are flush and located on the same horizontal plane. The thickness of the first collimation body is smaller than that of the second collimation body; the first collimation body is provided with a plurality of first collimation hole groups with different apertures, and each first collimation hole group comprises a plurality of first collimation holes; the second collimation body is provided with a plurality of second collimation hole groups with different apertures, and each second collimation hole group comprises a plurality of second collimation holes; the collimation assembly is provided with a working position and an avoiding position; the first collimation body and the second collimation body can move between the working position and the avoiding position, the collimation assembly can provide different collimation bodies for tumors of different positions and sizes, and therefore the situation that the actual treatment space is insufficient is reduced.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, and in particular to a collimation component, a radiotherapy head, and a medical device. Background Technology

[0002] Radiotherapy equipment can be used to treat cancer. Among them, the roller radiotherapy equipment includes a roller and a radiotherapy head. The roller can rotate around its own axis and has a treatment space inside. The radiotherapy head is installed in the roller. When the roller radiotherapy equipment is in operation, the radiotherapy head emits rays to perform radiotherapy on the patient in the treatment space.

[0003] Radiation field size refers to the area irradiated by the radiation beam during radiotherapy. Different radiation field sizes are required for tumors of different locations and sizes. For example, patients with tumors in the body generally require a large radiation field size, necessitating a larger actual treatment space; while patients with tumors in the head generally require a relatively smaller radiation field size with higher precision, requiring less actual treatment space. Generally, the radiation field size is defined by the collimation aperture on the collimator. In related technologies, drum-type radiotherapy equipment uses only one collimator in the radiotherapy head, treating tumors of different locations and sizes using the same collimator, which can easily lead to insufficient actual treatment space. Utility Model Content

[0004] The purpose of this utility model embodiment is to provide a collimation component, a radiotherapy head, and a medical device to reduce the occurrence of insufficient actual treatment space. The specific technical solution is as follows:

[0005] An embodiment of the first aspect of this application provides a collimation assembly for use in a radiotherapy head. The collimation assembly includes a first collimator and a second collimator. The first collimator and the second collimator are arranged side by side. The side of the first collimator near the radiation source is flush with the side of the second collimator near the radiation source, and they are located on the same horizontal plane. The thickness of the first collimator is less than the thickness of the second collimator. The first collimator has a plurality of first collimation hole groups with different apertures, and each first collimation hole group includes a plurality of first collimation holes. The second collimator has a plurality of second collimation hole groups with different apertures, and each second collimation hole group includes a plurality of second collimation holes. The collimation assembly has a working position and a clearance position. Both the first collimator and the second collimator are movable between the working position and the clearance position.

[0006] In some embodiments of this application, the first collimator includes at least two first sub-collimator layers stacked in its thickness direction;

[0007] Multiple first sub-holes are formed on each of the first sub-collimator layers, and the multiple first sub-holes of two adjacent first sub-collimator layers are arranged in a one-to-one correspondence to form the multiple first collimation holes.

[0008] In some embodiments of this application, the first sub-hole is a through hole.

[0009] In some embodiments of this application, the second collimator includes at least two second sub-collimator layers stacked in its thickness direction;

[0010] Multiple second sub-holes are formed on each of the second sub-collimator layers, and the multiple second sub-holes of two adjacent second sub-collimator layers are arranged in a one-to-one correspondence to form the multiple second collimation holes.

[0011] In some embodiments of this application, the second sub-hole is a through hole.

[0012] In some embodiments of this application, for the same first collimating aperture, the aperture of the first sub-aperture of the first sub-collimator layer closer to the radiation source is larger than the aperture of the first sub-aperture of the first sub-collimator layer farther from the radiation source.

[0013] In some embodiments of this application, the density of the material in the first sub-collimator layer near the radiation source is less than the density of the material in the first sub-collimator layer away from the radiation source.

[0014] In some embodiments of this application, for the same second collimating aperture, the aperture of the second sub-aperture of the second sub-collimator layer closer to the radiation source is larger than the aperture of the second sub-aperture of the second sub-collimator layer farther from the radiation source.

[0015] In some embodiments of this application, the density of the material in the second sub-collimator layer near the radiation source is less than the density of the material in the second sub-collimator layer away from the radiation source.

[0016] In some embodiments of this application, the first collimator includes: a plurality of first sub-collimators, the plurality of first sub-collimators being arranged side by side; each first sub-collimator being provided with at least one first collimation hole group; the apertures of the plurality of first collimation holes in the same first collimation hole group are the same;

[0017] And / or, the second collimator includes: a plurality of second sub-collimators, the plurality of second sub-collimators being arranged side by side; each second sub-collimator being provided with at least one second collimation hole group; the apertures of the plurality of second collimation holes in the same second collimation hole group are the same.

[0018] In some embodiments of this application, the collimation assembly has two driving members; wherein, one driving member is used to drive the first collimator to move between the working position and the avoidance position, and the other driving member is used to drive the second collimator to move between the working position and the avoidance position.

[0019] In some embodiments of this application, the collimation assembly has a driving member; the driving member is used to drive the first collimator and the second collimator to move synchronously, so that the first collimator and the second collimator can move between the working position and the avoidance position.

[0020] In some embodiments of this application, the collimation assembly further includes: two displacement sensors; wherein one displacement sensor is connected to the first collimator and is used to provide feedback on the position of the first collimator; and the other displacement sensor is connected to the second collimator and is used to provide feedback on the position of the second collimator.

[0021] An embodiment of the second aspect of this application provides a radiotherapy head, comprising: a radiation source and a collimation assembly according to any embodiment of the first aspect; the collimation assembly is used to collimate the rays emitted by the radiation source.

[0022] An embodiment of the third aspect of this application provides a medical device comprising: a roller and a radiotherapy head according to either the second aspect; the roller is rotatable about its own axis and has a treatment space therein; the radiotherapy head is mounted on the roller.

[0023] The collimation assembly of this application embodiment is applied to a radiotherapy head. The collimation assembly has a working position and a clearance position. The collimation assembly includes a first collimator and a second collimator, which are arranged side by side. Both the first and second collimators are movable between the working position and the clearance position, so that the collimation assembly has a first working state, a second working state, and a clearance state (i.e., a non-working state). When the first collimator is in the working position and the second collimator is in the clearance position, the collimation assembly is in the first working state, and the radiation is emitted through the first collimation aperture. When the second collimator is in the working position and the first collimator is in the clearance position, the collimation assembly is in the second working state, and the radiation is emitted through the second collimation aperture. When both the first and second collimators are in the clearance position, the collimation assembly is in the clearance state, and the radiation cannot be emitted through the collimation assembly. The collimation assembly can switch between the first working state, the second working state, and the clearance state.

[0024] When the radiotherapy head is performing treatment, in the first working state, the distance between the side of the first collimator away from the radiation source and the isocenter on the rotating shaft of the drum is 'a'. In the second working state, the distance between the side of the second collimator away from the radiation source and the isocenter is 'b'. Since the side of the first collimator close to the radiation source is flush with the side of the second collimator close to the radiation source, and the thickness of the first collimator is less than the thickness of the second collimator, the first and second collimators are collimators in the same plane but with different thicknesses, making 'a > b'. That is, during treatment, the space occupied by the first collimator is smaller than the space occupied by the second collimator.

[0025] When performing treatments requiring a large actual treatment space, such as body tumors, a first collimator is used. Compared to a second collimator, the first collimator occupies less space, providing a larger actual treatment area. When performing treatments requiring a smaller actual treatment space, such as head tumors, a second collimator can be used. Compared to the first collimator, the second collimator has a longer channel length and better field quality. Compared to related technologies that only use one collimator, the collimation assembly of this application can provide different collimators for tumors of different locations and sizes, thereby reducing the occurrence of insufficient actual treatment space.

[0026] The radiotherapy head of this application includes the collimation component of any of the above embodiments. When performing treatments requiring a large actual treatment space, such as body tumor treatment, a first collimator is used. Compared to a second collimator, the first collimator occupies less space and can provide a larger actual treatment space. When performing treatments requiring a smaller actual treatment space, such as head tumor treatment, a second collimator is used. Compared to the first collimator, the second collimator has a longer channel length and better radiation field quality. Compared to treatment heads in related technologies that only have one collimator, the radiotherapy head of this application can provide different collimators for tumors of different locations and sizes, thereby reducing the occurrence of insufficient actual treatment space.

[0027] The medical device of this application includes a radiotherapy head of any of the above embodiments. When performing treatments such as body tumor treatment that require a large actual treatment space, a first collimator is used for treatment. Compared with a second collimator, the first collimator occupies less space and can provide a larger actual treatment space. When performing treatments such as head tumor treatment that require a smaller actual treatment space, a second collimator is used for treatment. Compared with a first collimator, the second collimator has a longer channel length and better radiation field quality, thus balancing the provision of a large actual treatment space and good treatment effect.

[0028] Of course, any product implementing this utility model does not necessarily need to achieve all of the advantages described above at the same time. Attached Figure Description

[0029] To more clearly illustrate the technical solutions in the embodiments of this utility model or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this utility model. For those skilled in the art, other drawings can be obtained based on these drawings.

[0030] Figure 1 This is a schematic diagram of the structure (working state) of the medical device according to an embodiment of this application;

[0031] Figure 2 This is a diagram showing the connection relationship between the collimation component and the housing in an embodiment of this application;

[0032] Figure 3 for Figure 2 The main view;

[0033] Figure 4 This is a schematic diagram of the structure of a medical device according to an embodiment of this application (in a non-working state);

[0034] Figure 5 This is an exploded structural diagram of the first collimator and the first connector in the embodiments of this application;

[0035] Figure 6 This is an exploded structural diagram of the second collimator and the second connector in the embodiments of this application;

[0036] Figure 7 for Figure 2 AA section view;

[0037] Figure 8 for Figure 2 Top view;

[0038] Figure 9 for Figure 8 A schematic diagram of the decomposed structure;

[0039] Figure 10 This is a diagram showing the positional relationship between the driving component, the guiding structure, and the displacement sensor in the embodiments of this application;

[0040] Figure 11 for Figure 8 A magnified view of a portion of point M;

[0041] Figure 12 This is a schematic diagram of the structure of a radiotherapy head according to another embodiment of this application (collimation component avoidance state);

[0042] Figure 13 This is a schematic diagram of the structure of a radiotherapy head according to another embodiment of this application (collimation component in working state);

[0043] Figure 14 This is a diagram showing the connection relationship between the second collimator and the second connector in another embodiment of this application.

[0044] Explanation of reference numerals in the attached figures:

[0045] 1. Radiation therapy head; 2. Roller; 3. Treatment space P;

[0046] Collimation assembly 10; housing 20; limiting slide 21; radiation source 30; working position S; shielding position Q; isocenter O;

[0047] First collimator 100; First collimation hole 101; First sub-collimator layer 110; First sub-hole 111; First sub-collimator 120; First sub-section 121; Step structure 1211; Second collimator 200; Second collimator hole 201; Second sub-collimator layer 210; Second sub-hole 211; Second sub-collimator 220; Second sub-section 221; Shielding plate 230; Driving component 300; Motor 310; Transmission structure 320; Lead screw 321; Lead screw nut 322; Bearing support seat 323; Coupling 324; First connecting component 400; Installation space 410; Protrusion structure 411; Second connecting component 500; Displacement sensor 600; Limiting groove 610; Contact 620; Guide structure 700; Guide rail 710; Slider 720; Push connecting component 810; Groove 811; Limit switch 900; Operator 910. Detailed Implementation

[0048] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present utility model, and not all embodiments. Based on the embodiments of the present utility model, all other embodiments obtained by those of ordinary skill in the art based on this application are within the protection scope of the present utility model.

[0049] Radiation therapy equipment is a device that treats tumors by irradiating them with beams of radiation. Currently, radiation therapy equipment typically uses self-generated alpha, beta, and gamma rays, X-rays, electron beams, proton beams, and other particle beams to irradiate tumor cells and kill them. Roller-type radiation therapy equipment consists of a roller and a radiation therapy head. The roller can rotate around its own axis and has a treatment space inside. The radiation therapy head is mounted on the roller. When the roller-type radiation therapy equipment is in operation, the radiation therapy head emits radiation to treat the patient within the treatment space. The field size refers to the size of the area irradiated by the radiation beam during radiation therapy. Different field sizes are required for tumors of different locations and sizes. For example, patients with tumors in the body generally require a large field size and a larger actual treatment space; patients with tumors in the head generally require a relatively small field size with higher precision and a relatively lower requirement for actual treatment space. Generally, the field size is defined by a collimation aperture on the collimator. In related technologies, the roller-type radiotherapy equipment has only one collimator in its radiotherapy head. Tumors of different locations and sizes are treated using the same collimator, which can easily lead to insufficient actual treatment space.

[0050] like Figure 1 As shown, Figure 1 This is a schematic diagram (in working state) of a medical device according to an embodiment of this application. The embodiment proposes a medical device including a roller 2 and a radiotherapy head 1. The roller 2 can rotate around its own axis and has a treatment space P inside. The radiotherapy head 1 is mounted on the roller 2. The radiotherapy head 1 can be positioned circumferentially on the roller 2. The rotation of the roller 2 drives the radiotherapy head 1 to rotate around its axis. The radiation beam generated by the radiotherapy head 1 is focused onto the isocenter O of the roller 2 during rotation. The medical device may also include a treatment bed for carrying the patient. The patient is moved into the treatment space P by the movement of the treatment bed, moving the patient's tumor area to the isocenter O of the roller 2. When the radiotherapy head 1 generates radiation and rotates, the radiation can irradiate the patient's tumor area within a 360-degree range, thereby achieving the purpose of treating the patient.

[0051] like Figure 1 As shown in the embodiment of this application, a radiotherapy head 1 is proposed, including a radiation source 30 and a collimation component 10; the collimation component 10 is used to collimate the rays emitted by the radiation source 30.

[0052] Optionally, the radiotherapy head 1 may also include a housing 20, with the radiation source 30 disposed within the housing 20; the collimation assembly 10 may be connected to the housing 20. The radiation emitted by the radiation source 30 is directed to the patient's tumor area via the collimation assembly 10, thereby achieving the purpose of treating the patient.

[0053] The structures of the radiotherapy head 1 according to the embodiments of this application will be described in detail below.

[0054] like Figures 1 to 4 As shown, Figure 2 This is a diagram showing the connection relationship between the collimation component 10 and the housing 20 in an embodiment of this application. Figure 3 for Figure 2 The main view, Figure 4 This is a schematic diagram of the structure of a medical device according to an embodiment of this application (in a non-working state). This embodiment proposes a collimation component 10 applied to a radiotherapy head 1. The collimation component 10 includes a first collimator 100 and a second collimator 200. The first collimator 100 and the second collimator 200 are arranged side-by-side. The side of the first collimator 100 closest to the radiation source 30 is flush with the side of the second collimator 200 closest to the radiation source 30, located on the same horizontal plane. The thickness of the first collimator 100 is less than the thickness of the second collimator 200. The first collimator 100 has multiple first collimation hole groups with different apertures, each first collimation hole group including multiple first collimation holes 101. The second collimator 200 has multiple second collimation hole groups with different apertures, each second collimation hole group including multiple second collimation holes 201. The collimation component 10 has a working position S and a clearance position. Both the first collimator 100 and the second collimator 200 can move between the working position S and the clearance position.

[0055] It should be noted that the working position S is located on the path of the radiation emitted by the radiation source 30, and the avoidance position is located around the working position S; the first collimator 100 and the second collimator 200 can both move between the working position S and the avoidance position so that the first collimation hole 101 or the second collimation hole 201 can be selectively located on the radiation path.

[0056] The collimation assembly 10 of this application embodiment is applied to a radiotherapy head 1. The collimation assembly 10 has a working position S and a clearance position. The collimation assembly 10 includes a first collimator 100 and a second collimator 200, which are arranged side by side. Both the first collimator 100 and the second collimator 200 can move between the working position S and the clearance position, so that the collimation assembly 10 has a first working state, a second working state, and a clearance state. When the first collimator 100 is in the working position S and the second collimator 200 is in the clearance position, the collimation assembly 10 is in the first working state, and the radiation is emitted through the first collimation hole 101. Figure 1 The dashed lines indicate the positions of the first collimator 100 and the second collimator 200. When the second collimator 200 is in the working position S and the first collimator 100 is in the clearance position, the collimation assembly 10 is in the second working state, and the ray exits through the second collimation hole 201. Figure 1 The solid lines indicate the positions of the first collimator 100 and the second collimator 200. Figure 4The first collimator 100 and the second collimator 200 shown are in the collimation assembly 10 in the avoidance state (i.e., non-working state). When both the first collimator 100 and the second collimator 200 are in the avoidance position, the collimation assembly 10 is in the avoidance state, and the rays cannot be emitted through the collimation assembly 10. The collimation assembly 10 can switch between the first working state, the second working state, and the avoidance state.

[0057] like Figure 1 As shown, when the radiotherapy head 1 is performing treatment, the distance between the side of the first collimator 100 away from the radiation source 30 and the isocenter O on the rotating shaft of the roller 2 in the first working state is a. The distance between the side of the second collimator 200 away from the radiation source 30 and the isocenter O in the second working state is b. Since the side of the first collimator 100 near the radiation source 30 and the side of the second collimator 200 near the radiation source 30 are flush, and the thickness of the first collimator 100 is less than the thickness of the second collimator 200, the first collimator 100 and the second collimator 200 are collimators in the same plane but with different thicknesses, making a > b. That is, when performing treatment, the space occupied by the first collimator 100 is smaller than the space occupied by the second collimator 200.

[0058] When performing treatments requiring a large actual treatment space, such as body tumors, the first collimator 100 is used. Compared to the second collimator 200, the first collimator 100 occupies less space and can provide a larger actual treatment space. When performing treatments requiring a smaller actual treatment space, such as head tumors, the second collimator 200 can be used. Compared to the first collimator 101, the second collimator 201 has a longer channel length and better field quality. Compared to related technologies that only use one collimator, the collimation assembly 10 of this application embodiment can provide different collimators for tumors of different locations and sizes, thereby reducing the occurrence of insufficient actual treatment space.

[0059] Optionally, the aperture of the first collimation hole 101 on the first collimator 100 can be larger, so that the first collimator 100 can be used for treatment with a large field size, and the aperture of the second collimation hole 201 on the second collimator 200 can be smaller, so that the second collimator 200 can be used for treatment with a small field size.

[0060] Optionally, the diameter of all the first collimating holes 101 may be larger than the diameter of all the second collimating holes 201, or the diameter of all the first collimating holes 101 may be larger than the diameter of only some of the second collimating holes 201, or the diameter of only some of the first collimating holes 101 may be larger than the diameter of only some of the second collimating holes 201. It can be set according to actual needs, and this application does not limit it.

[0061] In some embodiments of this application, such as Figure 5 As shown, Figure 5 This is an exploded structural diagram of the first collimator 100 and the first connector 400 in an embodiment of this application. The first collimator 100 includes at least two first sub-collimator layers 110 stacked in its thickness direction. Each first sub-collimator layer 110 has multiple first sub-holes 111 formed therein. The multiple first sub-holes 111 of two adjacent first sub-collimator layers 110 are arranged in a one-to-one correspondence to form multiple first collimation holes 101. That is, the first collimation hole 101 is composed of multiple first sub-holes 111. The thickness of the first sub-collimator layer 110 is thinner than the thickness of the first collimator 100. The length of the first sub-collimator layer 111 on each layer is shorter than the length of the first collimation hole 101, which reduces the processing difficulty of the first collimation hole 101 and facilitates processing.

[0062] In some embodiments of this application, the first sub-hole 111 can be a through hole, which is easier to process than a tapered hole, thus reducing the processing difficulty.

[0063] In some embodiments of this application, such as Figure 6 As shown, Figure 6 This is an exploded structural diagram of the second collimator 200 and the second connector 500 in an embodiment of this application. The second collimator 200 includes at least two second sub-collimator layers 210 stacked in its thickness direction. Each second sub-collimator layer 210 has multiple second sub-holes 211 formed therein. The multiple second sub-holes 211 of two adjacent second sub-collimator layers 210 are arranged in a one-to-one correspondence to form multiple second collimator holes 201. That is, the second collimator hole 201 is composed of multiple second sub-holes 211. The thickness of the second sub-collimator layer 210 is thinner than the thickness of the second collimator 200. The length of the second sub-holes 211 on each layer is shorter than the length of the second collimator hole 201, which reduces the processing difficulty of the second collimator hole 201 and facilitates processing.

[0064] In some embodiments of this application, the second sub-hole 211 can be a through hole, which is easier to process than a tapered hole, thus reducing the processing difficulty.

[0065] Figure 5 and Figure 6 In the illustrated embodiment, the first collimator 100 includes two first sub-collimator layers 110, and the second collimator 200 includes two second sub-collimator layers 210. In other embodiments of this application, the number of first sub-collimator layers 110 and second sub-collimator layers 210 may also be three, four, five, or more.

[0066] In some embodiments of this application, such as Figure 7 As shown, Figure 7 for Figure 2 In the AA sectional view, some of the first collimating holes 101 can be inclined, and the inclination angle can be set as needed. For example, the angle between the axis of the first collimating hole 101 and the first perpendicular line is a non-zero angle. The first perpendicular line refers to the line passing through the focal point and perpendicular to the side of the first collimator 100 near the focal point, so as to facilitate ray focusing. The axes of multiple first collimating holes 101 intersect at the focal point, and the focal point coincides with the isocenter O. The first collimating hole 101 can be a tapered hole with a gradually decreasing aperture from the direction near the radiation source 30 to the direction away from the radiation source 30. The second collimating hole 201 can be set in the same way as the first collimating hole 101. When the first collimating hole 101 is a through hole, the second collimating hole 201 can be a through hole or a tapered hole; when the first collimating hole 101 is a tapered hole, the second collimating hole 201 can be a through hole or a tapered hole, depending on the actual needs.

[0067] In some embodiments of this application, for the same first collimating hole 101, the aperture of the first sub-hole 111 of the first sub-collimating layer 110 (upper collimating layer) closer to the radiation source 30 is larger than the aperture of the first sub-hole 111 of the first sub-collimating layer 110 (lower collimating layer) farther away from the radiation source 30; that is, from the direction closer to the radiation source 30 to the direction farther away from the radiation source 30, the apertures of multiple first sub-holes 111 of the same first collimating hole 101 gradually decrease. The aperture reduction method makes the focusing effect better, improves the radiation field quality of the focal point, and facilitates processing while achieving the focusing of radiation.

[0068] In some embodiments of this application, the density of the material of the first sub-collimator layer 110 near the radiation source 30 is less than the density of the material of the first sub-collimator layer 110 away from the radiation source 30. That is, the first sub-collimator layer 110 near the focal point uses a high-density material, while the first sub-collimator layer 110 away from the focal point uses a low-density material. Under the condition of meeting the requirements of the radiation field size, different materials are selected for different first sub-collimator layers 110, which is beneficial to reduce the amount of precious metals used, thereby reducing costs. At the same time, using a higher-density material near the focal point can make the dose decay faster and the boundary of the treatment field clearer.

[0069] As the aperture of the first collimating aperture 101 gradually decreases, the density of the material in the first sub-collimating layer 110 near the radiation source 30 is less than the density of the material in the first sub-collimating layer 110 far from the radiation source 30. This can improve the quality of the focal field while reducing costs.

[0070] In some embodiments of this application, for the same second collimating hole 201, the aperture of the second sub-hole 211 of the second sub-collimator layer 210 near the radiation source 30 is larger than the aperture of the second sub-hole 211 of the second sub-collimator layer 210 away from the radiation source 30. That is, from the direction near the radiation source 30 to the direction away from the radiation source 30, the aperture of the second sub-hole 211 of the same second collimating hole 201 gradually decreases. The aperture reduction method makes the focusing effect better, thereby improving the radiation field quality of the focal point. While achieving the focusing of the radiation, it is also convenient for processing.

[0071] In some embodiments of this application, the density of the material of the second sub-collimator layer 210 near the radiation source 30 is less than the density of the material of the second sub-collimator layer 210 away from the radiation source 30. That is, the second sub-collimator layer 210 near the focal point uses a high-density material, while the second sub-collimator layer 210 away from the focal point uses a low-density material. Under the condition of meeting the radiation field requirements, different materials are selected for different second sub-collimator layers 210, which is beneficial to reduce the amount of precious metals used, thereby reducing costs. At the same time, using a higher-density material near the focal point can make the dose decay faster and the boundary of the treatment field clearer.

[0072] As the aperture of the second collimating aperture 201 gradually decreases, the density of the material in the second sub-collimating layer 210 near the radiation source 30 is less than the density of the material in the second sub-collimating layer 210 far from the radiation source 30. This can improve the quality of the focal field while reducing costs.

[0073] Optionally, the materials of the first sub-collimator layer 110 and the second sub-collimator layer 210 near the radiation source 30 can be steel, while the materials of the first sub-collimator layer 110 and the second sub-collimator layer 210 away from the radiation source 30 can be tungsten or lead.

[0074] In some embodiments of this application, such as Figure 8 As shown, Figure 8 for Figure 2 In the top view, the first collimator 100 includes a plurality of first sub-collimators 120 arranged side by side; each first sub-collimator 120 is provided with at least one first collimation hole group, and the apertures of the plurality of first collimation holes 101 in the same first collimation hole group are the same; and / or, the second collimator 200 includes a plurality of second sub-collimators 220 arranged side by side; each second sub-collimator 220 is provided with at least one second collimation hole group, and the apertures of the plurality of second collimation holes 201 in the same second collimation hole group are the same, so that the number of collimation holes on each sub-collimator is small, thereby reducing the processing difficulty and facilitating processing.

[0075] It is understood that the diameters of the first collimation holes 101 located on different first sub-collimators 120 can be the same or different, and the diameters of the second collimation holes 102 located on different second sub-collimators 220 can be the same or different. This application does not limit this.

[0076] The distribution of the collimating hole groups on each sub-collimator is consistent with the arrangement of the radiation source 30. The collimator can be formed by combining sub-collimators including collimating holes of different diameters. Each field size corresponds to one collimating hole. By setting multiple sub-collimators with different collimating hole diameters, multiple field sizes can be provided. At the same time, the accuracy requirements of collimating holes of different diameters are different, and different equipment can be used for processing. This reduces the time occupied by a single processing equipment and reduces the dependence on relatively special equipment such as five-axis cutting, which helps to improve production efficiency, shorten delivery cycle, and reduce scrap rate and cost.

[0077] Optionally, the diameter of the collimating hole can be, for example, 3mm, 4mm, 5mm, 6mm, 8mm, 10mm, 12mm, 16mm, 20mm, 25mm, 35mm, etc., and can be selected according to the requirements. Among them, the diameter of the first collimating hole 101 can be greater than or equal to 15mm, and the diameter of the second collimating hole 201 can be less than 15mm.

[0078] It should be noted that when the collimation assembly 10 is in the first working state, any one of the plurality of first sub-collimators 120 is located in the working position S, and the remaining first sub-collimators 120 are located in the avoidance position, so that the ray only passes through the first sub-collimator 120 located in the working position S to provide a ray field size; when the collimation assembly 10 is in the second working state, any one of the plurality of second sub-collimators 220 is located in the working position S, and the remaining second sub-collimators 220 are located in the avoidance position, so that the ray only passes through the second sub-collimator 220 located in the working position S to provide a ray field size.

[0079] like Figure 8 As shown, there are four first sub-collimators 120 and three second sub-collimators 220. When the collimation assembly 10 is in the first working state, any one of the four first sub-collimators 120 is located at working position S, and the other three first sub-collimators 120 are located at clearance positions, so that the rays only pass through the first sub-collimator 120 located at working position S to provide a radiation field size. When the collimation assembly 10 is in the second working state, any one of the three second sub-collimators 220 is located at working position S, and the other two second sub-collimators 220 are located at clearance positions, so that the rays only pass through the second sub-collimators 220 located at working position S to provide a radiation field size. Compared with the related technologies that can only provide 3-4 radiation field sizes, the collimation assembly 10 of this application embodiment can provide at least 7 radiation field sizes even when the treatment space P of the roller 2 is limited.

[0080] In some embodiments of this application, reference is returned. Figures 5 to 7 The first collimator 100 can be divided into multiple first sub-parts 121 in its thickness direction. Multiple first sub-parts 121 located in the same layer constitute a first sub-collimator layer 110 as described above. Different first sub-parts 121 are provided with first sub-holes 111 of different diameters. Compared with the first sub-collimator layer 110 or the first sub-collimator 120 as the smallest unit constituting the first collimator 100, the first sub-part 121 as the smallest unit has a smaller volume and is easier to process. Figure 5 In the embodiment shown, there are 4 first sub-collimators 120, and each first sub-collimator 120 includes two first sub-parts 121, with a total of 8 first sub-parts 121 forming two layers of first sub-collimator layers 110.

[0081] Similarly, the second collimator 200 can also be divided into multiple second sub-parts 221 in its thickness direction. Multiple second sub-parts 221 located in the same layer constitute the second sub-collimator layer 210 mentioned above. Different second sub-parts 221 are provided with second sub-holes 211 of different diameters. Figure 6 In the embodiment shown, there are 3 second sub-collimators 220, and each second sub-collimator 220 includes two second sub-parts 221, with a total of 6 second sub-parts 221 forming two layers of second sub-collimator layers 210.

[0082] The above-mentioned methods of dividing the collimator into upper and lower layers or dividing it into multiple layers according to the size of the collimating hole can reduce the difficulty of processing and manufacturing, reduce reliance on special equipment, shorten the construction period, and thus reduce costs.

[0083] In some embodiments of this application, such as Figure 8 and Figure 9 As shown, Figure 9 for Figure 8 The exploded structural diagram shows that the collimation assembly 10 has two driving members 300; one driving member 300 is used to drive the first collimator 100 to move between the working position S and the avoidance position, and the other driving member 300 is used to drive the second collimator 200 to move between the working position S and the avoidance position. The two driving members 300 drive the first collimator 100 and the second collimator 200 to move respectively, thereby realizing the independent movement of the two collimators.

[0084] Optionally, such as Figures 8 to 10 As shown, Figure 10This is a positional relationship diagram of the drive unit 300, guide structure 700, and displacement sensor 600 in the embodiments of this application. The two drive units 300 can be located on both sides of the first collimator 100 and the second collimator 200, respectively. The drive unit 300 may include a motor 310 and a transmission structure 320. The transmission structure 320 is used to convert the rotational motion of the motor 310 into the linear motion of the first collimator 100 or the second collimator 200, so that the first collimator 100 or the second collimator 200 can move between the working position S and the avoidance position. The transmission structure 320 may include a lead screw 321, a lead screw nut 322, a bearing support seat 323, and a coupling 324. A bearing support seat 323 is provided at each end of the lead screw 321. One end of the lead screw 321 is connected to the motor 310 through the coupling 324. The lead screw nut 322 is sleeved on the lead screw 321 and connected to the first collimator 100 or the second collimator 200, so that the lead screw nut 322 can drive the first collimator 100 or the second collimator 200 to move under the drive of the motor 310.

[0085] Optionally, such as Figure 8 and Figure 9 As shown, the housing 20 may also be provided with a limiting groove 21, and the lead screw nut 322 is disposed in the limiting groove 21. When the lead screw nut 322 moves to the limit position, it can abut against the end of the limiting groove 21 to limit the movement of the lead screw nut 322.

[0086] In other embodiments of this application, the collimation assembly 10 may also have only one drive member 300. The drive member 300 is used to drive the first collimator 100 and the second collimator 200 to move synchronously, so that the first collimator 100 and the second collimator 200 can move between the working position S and the avoidance position. Setting only one drive member 300 can also meet the switching of the state of the collimation assembly 10. Compared with setting two drive members 300, setting one drive member 300 is simpler. Specifically, the first collimator 100 and the second collimator 200 can be connected to the lead screw nut 322 of the drive member 300 through a connection structure (not shown in the figure), so that the lead screw nut 322 can drive the first collimator 100 and the second collimator 200 to move synchronously under the drive of the motor 310.

[0087] In some embodiments of this application, such as Figures 7 to 9As shown, the collimation assembly 10 has a first connector 400 and a second connector 500. The first connector 400 is connected to a first collimator 100 and a drive member 300, respectively. The second connector 500 is connected to a second collimator 200 and another drive member 300, respectively. The collimator is connected to the drive member 300 through the connectors. The shape of the connectors is adapted to both the collimator and the drive member 300, so that the shape of the collimator does not need to be adapted to the shape of the drive member 300, and the shape of the collimator can be more regular, thereby reducing the processing difficulty of the collimator. Optionally, the first connector 400 and the second connector 500 can be connected to corresponding lead screw nuts 322.

[0088] Return to reference Figures 5 to 7 The first connector 400 has a through-hole mounting space 410 in the middle. The inner wall of the mounting space 410 is provided with a protrusion structure 411, which is used to support the first sub-part 121. The first sub-part 121 of the first collimator 100 is provided with a step structure 1211. When the first sub-part 121 is installed in the mounting space 410, the step structure 1211 of the first sub-part 121 near the housing 20 abuts against the corresponding protrusion structure 411, and the step structure 1211 of the first sub-part 121 away from the housing 20 abuts against the end face of the first connector 400. The first sub-part 121 and the first connector 400 can be fixedly connected by fasteners.

[0089] Optionally, the structure of the second connector 500 and its connection with the second collimator 200 can be referenced to the structure of the first connector 400 and the connection between the first connector 400 and the first collimator 100, and will not be repeated here.

[0090] In some embodiments of this application, such as Figures 7 to 10 As shown, the collimation assembly 10 also includes two guide structures 700, which are disposed in the housing 20. Both guide structures 700 are used to guide the movement of the first collimator 100 and the second collimator 200. The guide structure 700 includes a guide rail 710 and a slider 720. The guide rail 710 is arranged parallel to the lead screw 321, and the slider 720 is slidably connected to the guide rail 710. There can be multiple sliders 720, some of which are fixedly connected to the first collimator 100, and others are fixedly connected to the second collimator 200.

[0091] Specifically, the slider 720 can be connected to the first collimator 100 via the first connector 400, and to the second collimator 200 via the second connector 500. Two guide rails 710 can be respectively set on both sides of the lead screw 321. Each guide rail 710 can be equipped with four sliders 720. Two adjacent sliders 720 are connected to the first connector 400, and the remaining two sliders 720 are connected to the second connector 500. One end of the first connector 400 is connected to two sliders 720 of one guide structure 700, and the other end is connected to two sliders 720 of another guide structure 700. Similarly, one end of the second connector 500 is connected to two sliders 720 of one guide structure 700, and the other end is connected to two sliders 720 of another guide structure 700. Each connector is fixed at four points, and the four fixed points can be distributed in the vertices of a rectangle, making the connection more stable and the movement more stable.

[0092] In some embodiments of this application, such as Figures 8 to 10 As shown, the collimation assembly 10 also includes two displacement sensors 600; one displacement sensor 600 is connected to the first collimator 100 and is used to provide feedback on the position of the first collimator 100; the other displacement sensor 600 is connected to the second collimator 200 and is used to provide feedback on the position of the second collimator 200. The displacement sensors 600 have the function of position feedback, so that the position of the corresponding collimator can be determined more accurately.

[0093] Optionally, such as Figure 10 and Figure 11 As shown, Figure 11 for Figure 8 The enlarged schematic diagram at point M shows that the displacement sensor 600 can be a brushless, waterproof, and dustproof displacement sensor, including a limiting groove 610 and a contact 620. The contact 620 is disposed in the limiting groove 610. Position feedback is achieved by the change in the relative position of the contact 620 and the limiting groove 610. The brushless, waterproof, and dustproof displacement sensor has the advantages of high precision, long life, and high stability. A push connector 810 can be provided on the lead screw nut 322. The push connector 810 drives the contact 620 to move synchronously with the first collimator 100 or the second collimator 200 in the limiting groove 610. Specifically, the push connector 810 can be provided with a groove 811, and the lead screw nut 322 is disposed in the groove 811.

[0094] In some embodiments of this application, such as Figure 10 and Figure 11As shown, the collimation assembly 10 may further include a limit switch 900. The lead screw nut 322 triggers a disc-shaped actuator 910 on the limit switch 900. The limit switch 900 is used to limit the movement of the lead screw nut 322. Optionally, each drive structure is provided with two limit switches 900, and the two limit switches 900 are spaced apart in the extension direction of the lead screw 321.

[0095] This application also provides a radiotherapy head 1, including the collimation component 10 of any of the above embodiments. When performing treatments requiring a large actual treatment space, such as body tumor treatment, a first collimator 100 is used. Compared to a second collimator 200, the first collimator 100 occupies less space and can provide a larger actual treatment space. When performing treatments requiring a smaller actual treatment space, such as head tumor treatment, a second collimator 200 is used. Compared to a first collimation aperture 101, the second collimation aperture 201 has a longer channel length and better radiation field quality. Compared to treatment heads in related technologies that only have one collimator, the radiotherapy head 1 of this application embodiment can provide different collimators for tumors of different locations and sizes, thereby reducing the occurrence of insufficient actual treatment space.

[0096] Meanwhile, a large actual treatment space usually requires a sufficiently large distance between the lower end face of the collimation component 10 and the isocenter O. Correspondingly, the distance from the radiation source 30 to the isocenter O needs to be increased. The farther the radiation source 30 is from the isocenter O, the more source activity and quantity are required to obtain the same focal dose rate, which increases the cost and size of the equipment. The radiotherapy head 1 of this application embodiment, by using the above-mentioned collimation component 10, forms different actual treatment spaces for treating patients with head and body tumors. It provides a larger actual treatment space for the treatment of body tumors and other tumors that require a larger actual treatment space, obtains a larger treatment range, and provides patients with a better treatment experience. It does not require increasing the distance between the radiation source 30 and the isocenter O, the number of radiation sources, or the source activity, which is conducive to the miniaturization of the equipment and the reduction of costs.

[0097] This application also provides a medical device, including a radiotherapy head 1 of any of the above embodiments. When performing treatments such as body tumor treatment that require a large actual treatment space, a first collimator 100 is used for treatment. Compared with a second collimator 200, the first collimator 100 occupies less space and can provide a larger actual treatment space. When performing treatments such as head tumor treatment that require a smaller actual treatment space, a second collimator 200 is used for treatment. Compared with a first collimator 101, a second collimator 201 has a longer channel length and better radiation field quality, thus balancing the provision of a large actual treatment space and good treatment effect.

[0098] This application also proposes another embodiment of the collimation component 10, such as Figure 12 and Figure 13 As shown, Figure 12 This is a schematic diagram of the structure of a radiotherapy head 1 according to another embodiment of this application (collimation component 10 in a avoidance state). Figure 13 This is a schematic diagram of the structure of a radiotherapy head 1 according to another embodiment of this application (collimation assembly 10 in working state). Figure 12 and Figure 13 In the collimation component 10 shown in the embodiment, the first collimator 100 and the second collimator 200 are not arranged horizontally side by side, but are arranged in upper and lower layers.

[0099] In another embodiment of this application, such as Figure 12 and Figure 13 As shown, the collimation assembly 10 includes a first collimator 100 and a second collimator 200; the first collimator 100 can move to the side of the second collimator 200 away from the radiation source; the first collimator 100 is provided with a plurality of first collimation holes 101, and the second collimator 200 is provided with a plurality of second collimation holes 201, at least some of the first collimation holes 101 having a smaller aperture than at least some of the second collimation holes 201; the collimation assembly 10 has a working position S located on the emission path of the radiation emitted by the radiation source, and a clearance position located around the working position S; both the first collimator 100 and the second collimator 200 can move between the working position S and the clearance position, so that the first collimation hole 101 or the second collimation hole 201 can be selectively located on the emission path.

[0100] The above configuration allows the collimation component 10 to have a first working state, a second working state, and an avoidance state. When the second collimator 200 is in the working position S and the first collimator 100 is in the avoidance position, the collimation component 10 is in the first working state, and the ray exits through the second collimation hole 201. When the second collimator 200 is in the working position S and the first collimator 100 is also in the working position S, the collimation component 10 is in the second working state, and the ray exits through the second collimation hole 201 and the first collimation hole 101 in sequence. When both the first collimator 100 and the second collimator 200 are in the avoidance position, the collimation component 10 is in the avoidance state (i.e., non-working state), and the ray cannot exit through the collimation component 10. The collimation component 10 can switch between the first working state, the second working state, and the avoidance state.

[0101] When performing treatments requiring a large actual treatment space, such as body tumor treatment, the collimation assembly is in its first working state, i.e., using only the second collimator 200 for large-field treatment, which provides a larger actual treatment space. When performing treatments requiring a smaller actual treatment space, such as head tumor treatment, the collimator is in its second working state, i.e., using both the first collimator 100 and the second collimator 200 for small-field treatment. Based on the collimation of the rays by the second collimation aperture 201, the first collimation aperture 101 with a smaller aperture is also used to collimate the rays, which can improve the quality of the radiation field.

[0102] like Figure 12 and Figure 13 As shown, the collimation assembly 10 also includes two driving members 300. These two driving members 300 are used to drive the first collimator 100 and the second collimator 200 to move between the working position S and the clearance position, respectively. The structure of the driving member 300 can refer to the driving member 300 described above, using a motor 310 and a lead screw 321, which will not be repeated here. The driving member 300 can be connected to the first collimator 100 via a first connecting member 400 and to the second collimator 200 via a second connecting member 500. The first connecting member 400 and the second connecting member 500 serve as a collimator mounting frame.

[0103] like Figure 12 As shown, the number of the first collimator 100 and the second collimator 200 is one. In some other embodiments of this application, the number of the first collimator 100 and the second collimator 200 may also be two. This application does not limit this.

[0104] like Figure 14 As shown, Figure 14 This diagram illustrates the connection relationship between the second collimator 200 and the second connector 500 in another embodiment of this application. The second collimator 200 may include multiple second sub-collimators 220, arranged side-by-side. Different second sub-collimators 220 have second collimation holes 201 with different diameters to provide multiple firing field sizes. The connection method of the second sub-collimators 220 can refer to the connection method between the second sub-collimator 220 and the second connector 500 described above, and will not be repeated here. Similarly, the first collimator 100 may also include multiple first sub-collimators 120 arranged side-by-side. Both the first collimator 100 and the second collimator 200 may be provided with at least one set of collimation holes. By providing multiple sets of collimation holes on the first collimator 100 and the second collimator 200, the selectable firing field sizes are greatly increased.

[0105] The second sub-collimator 220 serves as the smallest unit comprising the second collimator 200. Multiple second collimators 220 with different apertures 201 provide different field sizes. Multiple second sub-collimators 220 are machined separately and then assembled. The second sub-collimators 220 can be fixed to the second connector 500 with screws. All second sub-collimators 220 are driven by a single drive unit 300. Different second collimators 201 can be machined in different ways, increasing the variety of available equipment, reducing reliance on specialized equipment, and allowing different second sub-collimators 220 to be machined simultaneously on multiple machines. This reduces manufacturing difficulty, shortens the lead time, and lowers the risk of scrap and manufacturing costs.

[0106] like Figure 14 As shown, a shielding plate 230 can be provided between any two adjacent second sub-collimators 220 to form a shielding position Q. The shielding plate 230 is used to shield the radiation source 30 to ensure the safety of the equipment in the off-source state, that is, when the equipment is in the off-source state, the shielding plate 230 is located in the working position S.

[0107] Furthermore, the first collimator 100 may include at least two stacked first sub-collimator layers, each with a first sub-hole, and the upper and lower first sub-holes are correspondingly arranged to form a first collimator hole 101; and / or, the second collimator 200 may include at least two stacked second sub-collimator layers, each with a second sub-hole, and the upper and lower second sub-holes are correspondingly arranged to form a second collimator hole 201. This arrangement facilitates increasing the length of the collimator hole, thereby improving the quality of the firing field; the relatively thin thickness of each sub-collimator layer reduces manufacturing difficulty and processing ease, thus reducing the risk of scrap and manufacturing costs. Sub-collimator layers can be processed simultaneously on different devices, thereby shortening the construction period.

[0108] The above description is merely a preferred embodiment of this utility model and is not intended to limit the scope of protection of this utility model. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this utility model are included within the scope of protection of this utility model.

Claims

1. A collimation component, characterized in that, For use in a radiotherapy head, the collimation assembly includes: a first collimator (100) and a second collimator (200); The first collimator (100) and the second collimator (200) are arranged side by side; the side of the first collimator (100) near the radiation source (30) and the side of the second collimator (200) near the radiation source (30) are arranged at the same level. The thickness of the first collimator (100) is less than the thickness of the second collimator (200); The first collimator (100) is provided with a plurality of first collimating hole groups with different apertures, each first collimating hole group including a plurality of first collimating holes (101); the second collimator (200) is provided with a plurality of second collimating hole groups with different apertures, each second collimating hole group including a plurality of second collimating holes (201); The collimation assembly has a working position (S) and a clearance position; both the first collimator (100) and the second collimator (200) are movable between the working position (S) and the clearance position.

2. The collimation assembly according to claim 1, characterized in that, The first collimator (100) includes at least two first sub-collimator layers (110) stacked in its thickness direction; Each of the first sub-collimator layers (110) has a plurality of first sub-holes (111), and the plurality of first sub-holes (111) of two adjacent first sub-collimator layers (110) are arranged in a one-to-one correspondence to form the plurality of first collimation holes (101).

3. The collimation component according to claim 2, characterized in that, The first sub-hole (111) is a through hole.

4. The collimation component according to any one of claims 1-3, characterized in that, The second collimator (200) includes at least two second sub-collimator layers (210) stacked in its thickness direction; Each of the second sub-collimator layers (210) has a plurality of second sub-holes (211), and the plurality of second sub-holes (211) of two adjacent second sub-collimator layers (210) are arranged in a one-to-one correspondence to form the plurality of second collimator holes (201).

5. The collimation assembly according to claim 4, characterized in that, The second sub-hole (211) is a through hole.

6. The collimation assembly according to claim 2, characterized in that, For the same first collimation hole (101), the aperture of the first sub-hole (111) of the first sub-collimator layer (110) closer to the radiation source (30) is larger than the aperture of the first sub-hole (111) of the first sub-collimator layer (110) farther away from the radiation source (30).

7. The collimation assembly according to claim 2, characterized in that, The density of the material in the first sub-collimator layer (110) near the radiation source (30) is less than the density of the material in the first sub-collimator layer (110) away from the radiation source (30).

8. The collimation assembly according to claim 3, characterized in that, For the same second collimation aperture (201), the aperture of the second sub-aperture (211) of the second sub-collimator layer (210) closer to the radiation source (30) is larger than the aperture of the second sub-aperture (211) of the second sub-collimator layer (210) farther from the radiation source (30).

9. The collimation assembly according to claim 3, characterized in that, The density of the material in the second sub-collimator layer (210) near the radiation source (30) is less than the density of the material in the second sub-collimator layer (210) away from the radiation source (30).

10. The collimation assembly according to claim 1, characterized in that, The first collimator (100) includes: a plurality of first sub-collimators (120), the plurality of first sub-collimators (120) are arranged side by side; each first sub-collimator (120) is provided with at least one first collimation hole group; the apertures of the plurality of first collimation holes (101) in the same first collimation hole group are the same; And / or, the second collimator (200) includes: a plurality of second sub-collimators (220), the plurality of second sub-collimators (220) being arranged side by side; each second sub-collimator (220) is provided with at least one second collimation hole group; the apertures of the plurality of second collimation holes (201) in the same second collimation hole group are the same.

11. The collimation assembly according to claim 1, characterized in that, The collimation assembly has two drive members (300); wherein one drive member (300) is used to drive the first collimator (100) to move between the working position (S) and the avoidance position, and the other drive member (300) is used to drive the second collimator (200) to move between the working position (S) and the avoidance position.

12. The collimation assembly according to claim 1, characterized in that, The collimation assembly has a drive member (300); the drive member (300) is used to drive the first collimator (100) and the second collimator (200) to move synchronously, so that the first collimator (100) and the second collimator (200) can move between the working position (S) and the avoidance position.

13. The collimation assembly according to claim 1, characterized in that, The collimation assembly further includes two displacement sensors (600); one of the displacement sensors (600) is connected to the first collimator (100) and is used to provide feedback on the position of the first collimator (100); the other displacement sensor (600) is connected to the second collimator (200) and is used to provide feedback on the position of the second collimator (200).

14. A radiotherapy head, characterized in that, include: The radioactive source (30) and the collimation assembly according to any one of claims 1-13; The collimation assembly is used to collimate the rays emitted by the radiation source (30).

15. A medical device, characterized in that, include: The roller (2) and the radiotherapy head as described in claim 14; The roller (2) is rotatable about its own axis and has a treatment space (P) inside; The radiotherapy head is mounted on the roller (2).

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