Radiation field collimation system and radiotherapy equipment

Abstract

The utility model discloses a radiation field collimation system and radiation treatment equipment, relates to the technical field of medical instruments for radiation diagnosis and treatment, and aims to solve the problems that a rotating part of an existing radiation field collimation system is heavy in dead weight and a pre-collimation part of the radiation field collimation system is high in material cost. The radiation field collimation system comprises a radiation source and a first collimation system. The radiation source is arranged on the base and used for emitting beams. The first collimation system comprises a primary collimation cone, the primary collimation cone is arranged on the beam outlet side of the radiation source and is fixed relative to the position of the radiation source, and in the beam outlet direction of the radiation source, the length L of the primary collimation cone is larger than or equal to 100 mm and smaller than or equal to 300 mm.

Description

Technical Field

[0001] This utility model relates to the field of medical devices for radiodiagnosis and treatment, and in particular to a radiation field collimation system and a radiotherapy device. Background Technology

[0002] The function of the radiation head in a medical linear accelerator is to provide a radiation beam that meets certain requirements for uniformity and symmetry, and to confine the radiation beam within a specific area to obtain radiation fields of different sizes required clinically. The field collimation system can precisely control and define the shape and size of the X-ray beam irradiating the patient, thereby obtaining the radiation field required clinically.

[0003] Existing collimation systems typically include a radiation source, a conical primary collimator, an aperture, and a grating. Generally, a field collimation system comprises a fixed section and a rotating section. The radiation source is located in the fixed section, while the conical primary collimator, aperture, and grating are all located in the rotating section. In existing field collimation systems, the conical primary collimator, aperture, and grating are usually arranged along the beam direction and in relatively fixed positions. This arrangement occupies a large space, resulting in a large overall weight and volume of the medical linear accelerator radiation head, making installation and subsequent maintenance and repair inconvenient. Furthermore, because the primary collimator has a large defined range and produces a significant amount of unwanted beam, additional shielding material is required to block it.

[0004] Therefore, a field collimation system is needed to solve the above problems. Utility Model Content

[0005] The purpose of this invention is to provide a field collimation system and a radiotherapy device, which aims to solve the problem of large space occupation in the existing collimation system layout.

[0006] To achieve the above objectives, the present invention adopts the following technical solution:

[0007] This invention provides a beam collimation system, including a base, a beam source, and a first collimation system. The beam source is mounted on the base and is used to emit a beam. The first collimation system includes a primary collimating cone, which is located on the beam exit side of the beam source and is fixed relative to the beam source. In the beam exit direction of the beam source, the length L of the primary collimating cone satisfies: 100mm ≤ L ≤ 300mm.

[0008] In this way, the primary collimator can be mounted on the base, thus eliminating the space occupied below the base and resolving the issue of large space requirements in the arrangement of the field collimation system. The primary collimator is fixed to the base and cannot rotate, reducing the weight and size of the rotating components.

[0009] In some embodiments of this application, the length L of the primary collimator satisfies: 200mm≤L≤240mm.

[0010] In some embodiments of this application, the primary collimator is disposed on the base and is fixed relative to the position of the radiation source.

[0011] In some embodiments of this application, the primary collimator is made of a lead-antimony alloy.

[0012] In some embodiments of this application, the primary collimator is made of lead metal.

[0013] In some embodiments of this application, a frustum-shaped collimation channel is formed within the primary collimation cone, penetrating the primary collimation cone. The collimation channel includes an inlet and an outlet disposed opposite each other, with the inlet closer to the beam exit side of the X-ray source, and the cross-sectional area of ​​the inlet being smaller than the cross-sectional area of ​​the outlet.

[0014] In some embodiments of this application, the field collimation system further includes a second collimation system, which is rotatable relative to the first collimation system and is detachable relative to the first collimation system; the second collimation system includes an aperture and / or a grating.

[0015] In some embodiments of this application, the field collimation system further includes a second collimation system, including an aperture. The second collimation system is rotatable relative to the first collimation system and is detachable relative to the first collimation system.

[0016] In some embodiments of this application, the field collimation system further includes a second collimation system, including a grating. The second collimation system is rotatable relative to the first collimation system and is detachable relative to the first collimation system.

[0017] In some embodiments of this application, the field collimation system further includes a second collimation system, comprising an aperture and a grating. The second collimation system is rotatable relative to the first collimation system and is detachable relative to the first collimation system.

[0018] In some embodiments of this application, the second collimation system includes an aperture and a grating; wherein the aperture is located at the exit side of the collimation channel of the primary collimation cone, and includes a mounting base, and a first aperture member and a second aperture member disposed opposite to each other within the mounting base; wherein the first aperture member and the second aperture member are capable of linear movement along a first direction, the first direction being perpendicular to the beam emission direction of the X-ray source; wherein, relative to the grating, the aperture is located between the X-ray source and the grating, and the grating includes a plurality of blades disposed opposite to each other; and the grating can be independently assembled and disassembled relative to the aperture; wherein, the plurality of blades are capable of linear movement along a second direction, the second direction being perpendicular to the first direction and the beam emission direction of the X-ray source.

[0019] In some embodiments of this application, the second collimation system further includes a first driving component and a second driving component. The first driving component is distributed along a first direction outside the aperture and is used to drive the first aperture element and the second aperture element to move linearly along the first direction, respectively. The second driving component is distributed along a second direction outside the grating and is used to drive multiple blades to move linearly along the second direction.

[0020] In some embodiments of this application, the second collimation system further includes a secondary collimation cone, the position of which is fixed relative to the aperture and / or grating.

[0021] This application also provides a radiotherapy device, including any of the above-described field collimation systems.

[0022] In this way, the primary collimating cone of the radiotherapy device provided in this application can be set on the base and its position is relatively fixed with respect to the radiation source, so it will no longer occupy the space of the rotating part. This solves the problem of large space occupation in the traditional layout of the radiation field collimation system, and can also reduce the weight and volume of the rotating part. Furthermore, it can also solve the problem of high material cost of the pre-collimation part of the radiation field collimation system, thereby reducing costs. Attached Figure Description

[0023] To more clearly illustrate the technical solutions of the embodiments of this application, the drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0024] Figure 1 This is one of the schematic diagrams of a field collimation system provided in an embodiment of this application;

[0025] Figure 2 A second schematic diagram of a field collimation system provided in an embodiment of this application;

[0026] Figure 3 A third schematic diagram of a field collimation system provided in this application embodiment;

[0027] Figure 4 This is one of the schematic diagrams of a radiotherapy device provided in the embodiments of this application;

[0028] Figure 5 This is a second schematic diagram of a radiotherapy device provided in an embodiment of this application;

[0029] Figure 6 This is the third schematic diagram of a radiotherapy device provided in the embodiments of this application.

[0030] Figure label:

[0031] Fire field collimation system-100; base-1; mounting cavity-10;

[0032] X-ray source-2;

[0033] First collimation system - 300; Primary collimation cone - 3; Collimation channel - 30; Inlet - 301; Outlet - 302;

[0034] Second collimation system-4; Mounting base-40; Aperture-41; First aperture element-411; Second aperture element-412; Grating-42; Blade-420; Secondary collimation cone-43;

[0035] Rack - 500; Treatment bed - 600; Radiation source - 50; Radiation beam - 50a; Radiation delivery device - 500A; Main control system - 700; Slave control system - 800; Treatment planning system - 900; Memory - 1000;

[0036] X-ray tube-300a; detector-300b. Detailed Implementation

[0037] 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 without creative effort are within the protection scope of the present utility model.

[0038] In the description of this utility model, it should be understood that the terms "upper," "lower," "left," "right," "front," "rear," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or relative positional relationship shown in the accompanying drawings. They are used only for the convenience of describing this utility model and for simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this utility model. Unless otherwise specified, the above-mentioned orientational descriptions can be flexibly set in actual application, provided that the relative positional relationship shown in the accompanying drawings is satisfied.

[0039] The terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this utility model, unless otherwise stated, "a plurality of" means two or more.

[0040] In the description of this utility model, it should be noted that, unless otherwise explicitly specified and limited, the terms "installation," "connection," "linking," and "communication" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection. They can refer to a direct connection or an indirect connection through an intermediate medium, or a connection within two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model according to the specific circumstances.

[0041] In embodiments of this invention, the terms "comprising," "including," or any other variations thereof are intended to cover a non-exclusive inclusion, such that a process, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, article, or apparatus. Without further limitation, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, article, or apparatus that includes that element.

[0042] In this embodiment of the invention, the terms "exemplary" or "for example" are used to indicate that something is an example, illustration, or description. Any embodiment or design described as "exemplary" or "for example" in this embodiment of the invention should not be construed as being more preferred or advantageous than other embodiments or designs. Specifically, the use of the terms "exemplary" or "for example" is intended to present the relevant concepts in a specific manner.

[0043] To provide a more precise radiation range to meet treatment needs, radiotherapy equipment also includes a beam collimation system, which is used to constrain the radiation beam. However, the existing beam collimation system layout occupies a large amount of space, and its structure needs to be optimized.

[0044] To address the issue of the large weight and volume of rotating parts caused by the existing layout of the field collimation system, this application provides a field collimation system.

[0045] like Figure 1 As shown, the radiation field collimation system 100 provided in this application includes a base 1, a radiation source 2, and a first collimation system 300;

[0046] Among them, the radiation source 2 is set on the base 1, and the radiation source 2 is used to emit a beam;

[0047] The first collimation system 300 includes a primary collimation cone 3, which is located on the beam exit side of the X-ray source 2, and the positions of the primary collimation cone 3 and the X-ray source 2 are relatively fixed.

[0048] The length L of the primary collimating cone also satisfies: 100mm≤L≤300mm.

[0049] In this way, the relatively fixed position of the primary collimator 3 and the radiation source 2 ensures that the primary collimator 3 stably constrains the beam emitted from the radiation source 2. The primary collimator 3 is fixed in position relative to the base 1 and cannot rotate. That is, the primary collimator 3 does not rotate with the rotating part, thus eliminating the need for the primary collimator 3 to rotate when the rotating part rotates. This reduces the weight and volume of the rotating part, solving the problems of large space occupation, large volume, and heavy weight in existing radiation field collimation systems.

[0050] In this application, the radiation source 2 can be cobalt-60, a proton beam, or X-rays, for example, a X-ray tube.

[0051] In this application, the fixing method between the radiation source 2 and the base 1 can be conventional and is not limited in this application.

[0052] In this application, the primary collimating cone 3 only needs to be relatively fixed in position with the base 1, and the method of relatively fixing the position is not particularly limited in this application.

[0053] In some embodiments of this application, the primary collimator 3 is disposed on the base 1, and the positions of the primary collimator 3 and the radiation source 2 are relatively fixed. This ensures that the primary collimator 3 stably conforms to the beam emitted from the radiation source.

[0054] In one possible embodiment, such as Figure 2 As shown, the base 1 has a mounting cavity 10. This allows the primary collimating cone 3 to be housed within the mounting cavity 10 of the base 1, preventing it from occupying space below the base 1 and overcoming the problem of large space requirements in existing field collimation systems. Furthermore, since the primary collimating cone 3 is housed within the mounting cavity 10 of the base 1, i.e., fixed to the base 1, the weight of the rotary table in the field collimation system is reduced. In addition, the base 1 also provides shielding, reducing radiation leakage.

[0055] In some embodiments of this application, the length L of the primary collimating cone preferably satisfies: 200mm ≤ L ≤ 240mm. More preferably, the length of the primary collimating cone 3 also satisfies 200mm ≤ L ≤ 240mm. It should be noted that during diagnosis and treatment, the beam emitted by the X-ray source 2 needs to be conformed by the radiation field collimation system before being projected onto the target area of ​​the object for treatment. In the radiation field collimation system, the effective treatment beam refers to the portion of the beam emitted through the collimation channel of the primary collimating cone 3. When the beam emitted by the X-ray source passes through the collimation channel, only a portion penetrates the collimation channel, while the rest is blocked by the inner wall of the collimation channel of the primary collimating cone. Therefore, the existing primary collimating cone 3 is usually made of a material with shielding properties.

[0056] Furthermore, the longer the primary collimator cone, the lower the risk of leakage; however, an excessively long primary collimator cone will occupy too much space. Therefore, considering the conformal effect, shielding effect, and size of the field collimation system, the length of the primary collimator cone 3 in this application is calculated based on the type of shielding material, shielding attenuation efficiency, and the highest leakage radiation attenuation rate around the outside of the field collimation system of commonly used primary collimators. This achieves both ensuring the shielding effect and minimizing the overall space occupied by the collimation system, as well as low radiation levels in the environment surrounding the outside of the field collimation system, thus meeting safety requirements.

[0057] For example, if the primary collimator is made of tungsten, the length of the primary collimator made of tungsten can be calculated using the attenuation efficiency of tungsten for rays and the standard attenuation rate of the highest leakage radiation around the outer edge of the collimation system. Typically, the attenuation rate of the highest leakage radiation around the outer edge of the collimation system is attenuated to below 0.0005. It should be noted that this application selected the length range of the primary collimator 3 based on the above principles. The length of the primary collimator determined by the above principles should be within the protection scope of this application, and this application will not elaborate further on this point.

[0058] Furthermore, the primary collimator 3 provided in this application is made of a lead-antimony alloy or of lead metal.

[0059] The primary collimating cone 3 provided in this application can be manufactured by casting. When the primary collimating cone 3 is manufactured by casting, the collimating channel 30 does not require post-processing.

[0060] It should be noted that the melting points of lead-antimony alloys and lead metal are lower than those of tungsten alloys commonly used in existing collimators. Collimators made of tungsten alloys are typically manufactured using slow wire EDM or other cutting processes, which are time-consuming, difficult, and result in low material utilization. Consequently, the length of the primary collimator is usually short, leading to large dimensions and weight in the rotating parts and other structures. This application uses economical materials such as lead-antimony alloys or lead metal to manufacture the primary collimator, resulting in low manufacturing costs and high material utilization. Compared to existing tungsten alloy primary collimators, material utilization is increased by more than 50%, while the cost is only 10%. Furthermore, since this application uses a casting process, cutting is eliminated, significantly shortening the manufacturing period and reducing costs. In addition, the length of the primary collimator in this application can be as long as possible, for example, 100-300 mm, with a preference for longer dimensions. This results in smaller dimensions and lighter weight for the rotating parts.

[0061] like Figure 2As shown, a frustum-shaped collimation channel 30 is formed within the primary collimation cone 3, penetrating the primary collimation cone. The collimation channel 30 includes an inlet 301 and an outlet 302 disposed opposite to each other. The inlet 301 is closer to the beam exit side of the X-ray source 2, and the cross-sectional area of ​​the inlet 301 is smaller than the cross-sectional area of ​​the outlet 302. This collimation channel 30 allows the beam emitted from the X-ray source 2 to pass through.

[0062] It should be noted that the beam emitted from X-ray source 2, after passing through the frustum-shaped collimation channel 30, has an approximately rectangular illumination range. If the collimation channel 30 were a conical channel, the illumination range would be approximately circular. When the illumination range is approximately circular, this increases the difficulty of conformal fitting of the grating and aperture behind the optical path. For example, the conical primary collimator used in the prior art, in addition to the difficulty of conformal fitting, also increases the difficulty of shielding the surrounding area of ​​the collimation system. The shielding on the outside of the collimator needs to be very thick to meet the shielding requirements, which increases the weight of the primary collimator. In addition, additional shielding material is required for blocking. In contrast, the primary collimator of this application preferentially adopts a square cone channel, which constrains the maximum radiation field to be square. The protective pressure of the primary collimator is low, and the weight of the primary collimator can be effectively reduced without reducing the shielding effect.

[0063] like Figure 3 As shown, the field collimation system provided in this application also includes a second collimation system 4, which is capable of rotating relative to the first collimation system 300, and is detachable relative to the first collimation system 300.

[0064] In some embodiments of this application, the second collimation system 4 includes an aperture 41 and / or a grating 42.

[0065] In some specific embodiments, the second collimation system 4 may include an aperture 41. When the second collimation system 4 rotates relative to the first collimation system, the aperture 41 can further block and constrain the beam emitted by the radiation source 2, thereby adjusting the shape and size of the beam irradiation range. This allows for more precise radiation therapy to the target area of ​​the object, avoiding unnecessary radiation damage to the healthy tissue around the target area.

[0066] In the case where the second collimation system 4 includes an aperture 41, the aperture 41 is located on the exit side of the collimation channel of the primary collimation cone 3. The aperture 41 includes a mounting base 40, and a first aperture element 411 and a second aperture element 412 (aperture 41 includes a first aperture element 411 and a second aperture element 412) disposed opposite each other within the mounting base 40. The first aperture element 411 and the second aperture element 412 are capable of linear movement along a first direction X. It should be noted that the first direction X is perpendicular to the beam emission direction Z of the X-ray source 2.

[0067] In this way, the first aperture 411 and the second aperture 412 can move in a straight line perpendicular to the beam output direction to further adjust and constrain the illumination range of the beam.

[0068] In some specific embodiments, the second collimation system 4 may include a grating 42. Thus, when the second collimation system 4 rotates relative to the first collimation system 300, the grating 42 can further obstruct and constrain the beam emitted from the radiation source 2, thereby adjusting the shape and size of the beam's irradiation range. This allows for more precise radiation therapy of the target area, avoiding unnecessary radiation damage to surrounding healthy tissues.

[0069] like Figure 3 As shown, in the case where the second collimation system 4 includes a grating 42, the grating 42 is located on the exit side of the primary collimation cone 3. The grating 42 includes a plurality of blades 420. These blades 420 are capable of linear motion along a second direction Y, which is perpendicular to the first direction X and the beam exit direction Z of the radiation source 2.

[0070] In this way, the multiple blades 420 of the grating 42 can further constrain the beam emitted by the radiation source 2 and make more precise adjustments to the illumination range.

[0071] In some specific embodiments, the second collimation system 4 described above may also include an aperture 41 and a grating 42, with the aperture 41 and the grating 42 arranged along the beam output direction Z.

[0072] The aperture 41 is located on the exit side of the collimation channel of the primary collimating cone 3, and includes a mounting base 40, and a first aperture element 411 and a second aperture element 412 (aperture 41 includes the first aperture element 411 and the second aperture element 412) disposed opposite each other within the mounting base 40. The first aperture element 411 and the second aperture element 412 are capable of linear movement along a first direction X. It should be noted that the first direction X is perpendicular to the beam emission direction Z of the X-ray source 2.

[0073] Among them, relative to the grating 42, the aperture 41 is located between the radiation source 2 and the grating 42. The grating 42 includes multiple blades 420 arranged opposite to each other; and the grating 42 can be independently assembled and disassembled relative to the aperture 41.

[0074] Among them, multiple blades 420 can move in a straight line along the second direction Y, which is perpendicular to the first direction X and the beam emission direction Z of the ray source 2.

[0075] In the specific embodiments described above, the aperture 41 and the grating 42 work together to more precisely constrain the beam emitted by the radiation source 2, obtain a more accurate irradiation range, and adjust the shape and size of the beam irradiation range. This allows for more precise radiation therapy of the target area of ​​the object, avoiding unnecessary radiation damage to the healthy tissues around the target area.

[0076] Based on this, the second collimation system 4 also includes a first driving component, which is distributed on the outside of the aperture 41 along the first direction. The first driving component is used to drive the first aperture element 411 and the second aperture element 412 of the aperture 41 to move linearly along the first direction, respectively.

[0077] In this way, the first aperture 411 and the second aperture 412 can be moved along the first direction by the first driving component.

[0078] The second collimation system 4 also includes a second driving component, which is distributed on the outside of the grating 42 along the second direction. The second driving component is used to drive the multiple blades 420 to move linearly along the second direction.

[0079] In this way, the second drive assembly can achieve the purpose of moving multiple blades 420 along the second direction.

[0080] In some embodiments of this application, the second collimation system 4 may further include a secondary collimation cone 43, the secondary collimation cone 43 being fixed in position relative to the aperture 41 and / or the grating 42.

[0081] For example, the secondary collimator 43 can be positioned between the primary collimator 3 and the aperture 41. The beam, constrained by the primary collimator, then enters the secondary collimator 43, where it is collimated and constrained again before exiting. Further constraining and adjustment by the aperture 41 and / or the grating 42 then achieves a more precise projection range to meet treatment needs.

[0082] like Figure 3 As shown, in some embodiments of this application, the second collimation system 4 may further include a secondary collimation cone 43, the secondary collimation cone 43 and the aperture 41 being relatively fixed in position.

[0083] In some embodiments of this application, the second collimation system 4 may further include a secondary collimation cone 43, the secondary collimation cone 43 being fixed in position relative to the grating 42.

[0084] In some embodiments of this application, the second collimation system 4 may further include a secondary collimation cone 43, the secondary collimation cone 43 being fixed in position relative to the aperture 41 and the grating 42.

[0085] This application provides a radiotherapy device, which includes any of the aforementioned field collimation systems.

[0086] like Figures 4-6 As shown, the radiotherapy device provided in this application also includes a gantry 500, a treatment head, and a treatment bed 600; wherein, the treatment bed 600 is used to support and move the patient; the treatment head includes a radiation source 50 and a collimator, the radiation source 50 emits a radiation beam 50a toward the target area, and the collimator guides the radiation beam 50a to the target area to form a preset radiation field of a specific shape, so that the radiation irradiated on the patient site is adapted to the tumor; the gantry 500 installs various radiotherapy components and drives the treatment head to rotate around the gantry rotation axis 500b to emit radiation beams 50a from different angles.

[0087] For example, such as Figure 4 As shown, the radiation delivery device 500A consists of a gantry 500, a treatment head, and a treatment bed 600; the radiotherapy equipment also includes a main control system 700, a slave control system 800, a treatment planning system 900, and a memory 1000.

[0088] In some embodiments, the radiation delivery device 500A, the master control system 700, the slave control system 800, the treatment planning system 900, and the memory 1000 may be connected to and / or communicate with each other via wireless connection (e.g., network connection), wired connection, or a combination thereof.

[0089] In some embodiments, the main control system 700 may be used to generate control commands for one or more components of the radiotherapy device (e.g., slave control system 800, treatment planning system 900, memory 1000).

[0090] In some embodiments, the slave control system 800 may be used to control the radiation delivery device 500A to perform corresponding actions in response to control commands generated by the master control system 700.

[0091] In some embodiments, the treatment planning system 900 is configured to determine a treatment plan based on a patient's planning image (which is an image acquired by the patient using an imaging device prior to treatment) and / or based on at least a portion of an object (e.g., a tumor) represented in an image acquired by an imaging system.

[0092] The memory 1000 may store data, instructions, and / or any other information. In some embodiments, the memory 1000 may store data obtained from the treatment planning system 900. In some embodiments, the memory 1000 may store data and / or instructions used by the main control system 700 to perform the exemplary methods described in this application.

[0093] Radiation source 50 is capable of generating or emitting radiation beam 50a. There can be one or more radiation sources 50. The radiation source can be an X-ray radiation source, a gamma-ray radiation source, or other sources such as electrons, protons, or heavy ions. This application does not limit the type of radiation source; an X-ray radiation source is used as an example for illustration. The position of radiation source 50 relative to the patient and the orientation of radiation beam 50a relative to the patient can be achieved by controlling the movement of the gantry 500 and / or the treatment bed 600.

[0094] Treatment bed 600 is used to carry patient P, and treatment bed 600 can be used in three orthogonal directions (in Figure 1 The treatment bed 600 can translate in one or more of the X, Y, and Z axes. In some embodiments, the treatment bed 600 can also rotate about any one or more of the X, Y, and Z axes.

[0095] The gantry 500 is used to support the treatment head and can drive the treatment head to rotate around the gantry rotation axis 500b. The gantry rotation axis 500b and the central axis of the radiation beam 50a intersect at the isocenter point O.

[0096] The frame 500 includes C-shaped frames, roller frames, etc., and this application uses a roller frame 500 as an example. Figure 5 and Figure 6 As shown, a treatment space 500a is formed on the gantry 500. The treatment bed 600 enters the treatment space 500a and treats the patient on the treatment bed 600 through various radiotherapy components on the gantry 500.

[0097] For example, in one embodiment provided by this application, the treatment bed 600 and the gantry 500 can be relatively deflected to create different angles between them, allowing the radiation beam 50a to be emitted from different angles for coplanar and non-coplanar irradiation, providing a flexible field irradiation scheme and enabling patients to obtain better treatment results. Furthermore, during treatment, the gantry 500 can also rotate along the gantry rotation axis 500b, so that the formed preset radiation field is directed towards the target area from different directions.

[0098] In some embodiments, an imaging system is also provided on the gantry 500 for precise radiotherapy. The imaging system includes an X-ray tube 300a and a detector 300b. The X-ray tube 300a emits an imaging beam that passes through the patient and is received by the detector 300b. By acquiring patient images, it can provide information on the shape, volume, and location of the tumor and critical organs, and register these images with the treatment plan images to verify whether the patient has moved or been accurately positioned. Based on the image registration verification results, the patient can be adjusted, treatment stopped, or the treatment plan adjusted. Images from some image-guided systems can also be used to develop treatment plans. Continuous dynamic images are used to observe and assess changes in the morphology and location of tumors and organs caused by physiological movement. In some embodiments, the imaging system can be, for example, a CT scanner, a cone-beam CT scanner, a PET scanner, a volumetric CT scanner, an MRI scanner, or a combination thereof.

[0099] The imaging system may include one X-ray tube 300a and one detector 300b, or it may include two X-ray tubes 300a and two detectors 300b, that is, it includes a first imaging system and a second imaging system, and the rays of the first imaging system and the second imaging system intersect.

[0100] When the system has both a primary and a secondary imaging system, the dual imaging setup allows for 3D imaging of the target area using a single 500-phase array on a single gantry, enabling real-time monitoring of lesion location. Simultaneous image data acquisition reduces the time required, improving image-guided imaging efficiency.

[0101] In the embodiments provided in this application, the field collimation system is used to guide the radiation beam 50a to the target area into a preset field of a specific shape. After the electrons generate rays upon hitting the target, they pass through a primary collimation cone to initially shape the radiation beam 50a emitted by the radiation source 50 into a square cone shape, which can effectively reduce the difficulty of constraining the subsequent aperture 41 and / or grating 42.

[0102] For example, during radiation field irradiation, conformal radiation fields are generally selected for large tumors in the body, while focused radiation fields offer higher precision for small tumors. To provide more flexible irradiation schemes for clinical applications, the radiation field collimation system provided in this application solves the problem of large space occupation in traditional radiation field collimation systems, reduces the weight and volume of the rotating parts, achieves precise conformal irradiation, and addresses the issue of high material costs for the pre-collimation components of radiation field collimation systems.

[0103] In the description of this specification, specific features, structures, materials, or characteristics may be combined in any suitable manner in one or more embodiments or examples.

[0104] The above are merely specific embodiments of this utility model, but the protection scope of this utility model is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the technical scope disclosed in this utility model should be included within the protection scope of this utility model. Therefore, the protection scope of this utility model should be determined by the scope of the claims.

Claims

1. A field collimation system, characterized by, include: A radiation source, mounted on a base, is used to emit a beam; The first collimation system includes a primary collimation cone, which is located on the beam exit side of the X-ray source and is fixed relative to the position of the X-ray source. In the beam exit direction of the X-ray source, the length L of the primary collimating cone satisfies: 100mm ≤ L ≤ 300mm.

2. The field collimating system of claim 1, wherein, The length L of the primary collimating cone satisfies: 200mm≤L≤240mm.

3. The field collimation system according to claim 1, characterized in that, The primary collimating cone is disposed on the base and is fixed relative to the position of the radiation source.

4. The field collimation system according to claim 1, characterized in that, The primary collimator is made of a lead-antimony alloy, or the primary collimator is made of lead metal.

5. The field collimating system of claim 1, wherein, A frustum-shaped collimation channel is formed inside the primary collimation cone; The collimation channel includes an inlet and an outlet arranged opposite to each other. The inlet is close to the beam exit side of the X-ray source, and the cross-sectional area of ​​the inlet is smaller than the cross-sectional area of ​​the outlet.

6. The field collimating system of claim 1, wherein, The field collimation system also includes: The second collimation system is rotatable relative to the first collimation system and is detachable relative to the first collimation system, and includes: an aperture and / or a grating.

7. The field collimating system of claim 6, wherein, The second collimation system includes an aperture stop and a grating; The aperture is located on the exit side of the collimation channel of the primary collimating cone, and includes: a mounting base, and a first aperture element and a second aperture element disposed opposite to each other within the mounting base; The first aperture and the second aperture can move linearly along a first direction, which is perpendicular to the beam emission direction of the X-ray source. The aperture is located between the ray source and the grating, and the grating includes a plurality of blades arranged opposite each other; and the grating can be independently assembled and disassembled as a whole relative to the aperture. The multiple blades are capable of linear motion along a second direction, which is perpendicular to the first direction and the beam emission direction of the ray source.

8. The field collimating system of claim 7, wherein, The second collimation system also includes: A first driving component is distributed on the outside of the aperture along the first direction, and is used to drive the first aperture component and the second aperture component to move linearly along the first direction respectively; Alternatively, a second drive assembly is distributed on the outside of the grating along the second direction to drive the plurality of blades to move linearly along the second direction.

9. The field collimating system of claim 6, wherein, The second collimation system further includes a secondary collimation cone, the secondary collimation cone being fixed in position relative to the aperture and / or the grating.

10. A radiotherapy device, characterized in that, Includes the field collimation system as described in any one of claims 1-9.

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