Radiotherapy target structure and radiotherapy equipment

Abstract

The present invention relates to a radiotherapy target structure and a radiotherapy device. The radiotherapy target structure includes: a target assembly, including a support member and a first target body mounted on the support member; and a protective housing, wrapped around the outside of the target assembly; the protective housing includes a first surface and a second surface, the first surface and the second surface are located on opposite sides of the first target body, at least a part of the first surface and at least a part of the second surface are both capable of allowing a beam to pass through, a sealed cavity is formed inside the protective housing, and the sealed cavity is used to prevent the first target body from being oxidized. When the electron beam emitted by the electron generating device hits the first target body to generate heat, it can reduce the oxidation substances generated by the first target body, can avoid the sputtering of oxidation substances, will not affect the accelerating tube, ensure the use performance, extend the service life of the first target body and the accelerating tube, do not need to replace the output window of the accelerating tube, and reduce the cost.

Description

Technical Field

[0001] The present invention relates to the technical field of imaging devices, and particularly to a radiotherapy target structure and a radiotherapy device. Background Art

[0002] During the process of generating photons by bombarding a target with a high-intensity electron beam generated by an electron acceleration tube for radiotherapy, a large amount of heat will be deposited on the target, and rapid temperature changes will occur on the target surface. A high-temperature target operating in air will accelerate the thermal shock damage on the target surface, such as causing the target material to oxidize and sublimate, and deposit on the output window of the acceleration tube, damaging the output window and affecting the performance. Moreover, the process of replacing the output window is very complicated and costly, increasing the cost. Summary of the Invention

[0003] Based on this, in view of the current problem that the target material oxidizes and deposits on the output window, it is necessary to provide a radiotherapy target structure and a radiotherapy device that can avoid oxidation reactions.

[0004] A radiotherapy target structure includes:

[0005] A target assembly including a support member and a first target body mounted on the support member; and

[0006] A protective housing wrapped around the outside of the target assembly; the protective housing includes a first surface and a second surface, the first surface and the second surface are located on opposite sides of the first target body, at least a part of the first surface and at least a part of the second surface can both allow the beam to pass through, and a sealed cavity is formed inside the protective housing, and the sealed cavity is used to prevent the first target body from being oxidized.

[0007] In one embodiment, the protective housing further includes a first window and a second window arranged opposite to each other, the first window is arranged on the first surface, the second window is arranged on the second surface, and the first window and the second window are located on both sides of the first target body for allowing the beam to pass through.

[0008] In one embodiment, the radiotherapy target structure further includes a cooling assembly, the cooling assembly passes through the protective housing and is arranged on the support member for cooling the first target body;

[0009] The connection between the protective housing and the cooling assembly is sealed to form the sealed cavity inside the protective housing.

[0010] In one embodiment, the support member includes a target substrate and a first target seat, the target substrate has a first through hole extending along the beam direction, and the first target seat is installed in the first through hole, and the first target seat is used to install the first target body.

[0011] In one embodiment, the surface of the first target seat facing the first surface has a mounting groove for mounting the first target body.

[0012] And / or, a recess is formed on the surface of the first target seat facing the second surface. The recess corresponds to the first target body and is used for the beam to pass through.

[0013] In one embodiment, there is a preset space between the outer wall of the first target seat and the inner wall of the first through hole. The preset space allows the cooling component to pass through for cooling the first target body.

[0014] In one embodiment, the first through hole includes a first stepped hole and a second stepped hole which are coaxially arranged, and the diameter of the first stepped hole is larger than that of the second stepped hole. After the first target seat is installed in the first through hole, the inner wall of the first target seat abuts against the inner wall of the second stepped hole, and a preset space is defined by the inner wall of the first target seat and the inner wall of the first stepped hole.

[0015] In one embodiment, the support member further includes a second target seat, and the target assembly further includes a second target body. The target substrate has a second through hole extending along the beam direction, and the second target seat is disposed in the second through hole for mounting the second target body.

[0016] In one embodiment, at least a part of the second target seat is hermetically connected to the protective housing so that the second target body is located outside the sealed cavity.

[0017] A radiotherapy device includes an electron generating device, an accelerating tube, and a radiotherapy target structure as described in any of the above technical features. The electron generating device is used to generate an electron beam, the accelerating tube is used to accelerate the electron beam, and the radiotherapy target structure is used to convert the accelerated electron beam into an X-ray and emit it.

[0018] After adopting the above technical solution, the present invention has at least the following technical effects:

[0019] The radiotherapy target structure and radiotherapy equipment of the present invention. After adding a protective housing outside the target assembly, the electron beam emitted by the electron generation device of the radiotherapy equipment passes through the first surface of the protective housing and enters the first target body, where it is converted into X-rays and emitted through the second surface. Moreover, since a sealed cavity is formed inside the protective housing, the first target body operates in a closed environment, reducing the presence of oxygen. In this way, when the electron beam emitted by the electron generation device hits the first target body and generates heat, the oxidation substances generated by the first target body can be reduced. Moreover, even if oxidation substances are generated by the first target body, due to the airtightness of the protective housing, the oxidation substances can be prevented from splashing out of the protective housing, effectively solving the problem that the target substance is oxidized and deposited on the output window of the accelerating tube, without affecting the accelerating tube, ensuring the use performance, extending the service life of the first target body and the accelerating tube, eliminating the need to replace the output window of the accelerating tube, and reducing costs. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] Figure 1 Stereogram of the radiotherapy target structure in an embodiment of the present invention;

[0021] Figure 2 is Figure 1 Cut-away stereogram of the radiotherapy target structure shown;

[0022] Figure 3 is Figure 2 Cross-sectional view of the radiotherapy target structure shown;

[0023] Figure 4 Stereogram of the radiotherapy target structure in another embodiment of the present invention;

[0024] Figure 5 is Figure 4 Cut-away schematic diagram of the radiotherapy target structure shown;

[0025] Figure 6 is Figure 5 Cross-sectional view of the radiotherapy target structure shown;

[0026] Figure 7 is Figure 6 Stereogram of the first target base in the radiotherapy target structure shown;

[0027] Figure 8 is Figure 6 Cross-sectional view of the first target base shown;

[0028] Figure 9 is Figure 6 Top cross-sectional view of the radiotherapy target structure shown after the target assembly and the cooling assembly are connected;

[0029] Figure 10 Cross-sectional view of the radiotherapy target structure in yet another embodiment of the present invention

[0030] Figure 11 As shown in Figure 10 the cutaway perspective view of the radiotherapy target structure;

[0031] Figure 12 As shown in Figure 10 the perspective view of the radiotherapy target structure.

[0032] Wherein: 100, radiotherapy target structure; 110, target assembly; 111, support member; 1111, target substrate; 11111, first through hole; 11112, cooling channel; 1112, first target seat; 11121, mounting groove; 11122, recess; 11123, cooling groove; 11124, fixed edge; 1113, target holder; 1114, second target seat; 112, first target body; 113, second target body; 120, protective housing; 121, first window; 122, second window; 123, first surface; 124, second surface; 130, cooling assembly; 131, cooling inlet pipe; 132, cooling outlet pipe; A, sealed cavity. Detailed implementation manners

[0033] To make the above objects, features, and advantages of the present invention more obvious and understandable, the following will describe the detailed implementation manners of the present invention with reference to the accompanying drawings. Many specific details are set forth in the following description to fully understand the present invention. However, the present invention can be implemented in many other ways different from those described herein, and those skilled in the art can make similar improvements without departing from the connotation of the present invention. Therefore, the present invention is not limited by the specific embodiments disclosed below.

[0034] In the description of the present invention, it should be understood that the terms "center", "longitudinal", "transverse", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential", etc. indicate the orientation or positional relationship based on the orientation or positional relationship shown in the drawings, and are only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and thus should not be construed as a limitation of the present invention.

[0035] In addition, the terms "first" and "second" are only used for descriptive purposes and cannot be understood as indicating or implying relative importance or implicitly specifying the quantity of the indicated technical features. Thus, the features defined with "first" and "second" may explicitly or implicitly include at least one of such features. In the description of the present invention, "a plurality of" means at least two, such as two, three, etc., unless otherwise specifically defined.

[0036] In the present invention, unless otherwise clearly specified or limited, terms such as "installed", "connected", "coupled", "fixed", etc. shall be construed in a broad sense. For example, it may be a fixed connection, a detachable connection, or integrated; it may be a mechanical connection or an electrical connection; it may be directly connected or indirectly connected through an intermediate medium, and it may be the internal communication of two components or the interaction relationship between two components, unless otherwise clearly limited. For those of ordinary skill in the art, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

[0037] In the present invention, unless otherwise clearly specified or limited, the first feature being "on" or "under" the second feature may be that the first and second features are in direct contact, or the first and second features are indirectly in contact through an intermediate medium. Moreover, the first feature being "above", "over" and "on top of" the second feature may be that the first feature is directly above or obliquely above the second feature, or merely indicates that the first feature has a higher horizontal height than the second feature. The first feature being "under", "beneath" and "underneath" the second feature may be that the first feature is directly below or obliquely below the second feature, or merely indicates that the first feature has a lower horizontal height than the second feature.

[0038] It should be noted that when an element is referred to as "fixed to" or "disposed on" another element, it can be directly on the other element or there may also be an intermediate element. When an element is considered to be "connected" to another element, it can be directly connected to the other element or there may be an intermediate element at the same time. The terms "vertical", "horizontal", "up", "down", "left", "right" and similar expressions used herein are only for the purpose of illustration and do not represent the only implementation.

[0039] See Figures 1 to 6 , the present invention provides a radiotherapy target structure 100. The radiotherapy target structure 100 is applied in a radiotherapy device (not shown) and can treat and / or image the lesion site of a patient. It can be understood that the radiotherapy target structure 100 can be used in cooperation with the electron generation device of the radiotherapy device. The beam generated by the electron generation device passes through the radiotherapy target structure 100 and is converted into photons and projected onto the lesion site of the patient to achieve radiotherapy or imaging, etc. Specifically, after the electron generation device (not shown) of the radiotherapy device generates an electron beam, the electron beam is accelerated by an acceleration tube (not shown). The accelerated electron beam enters the radiotherapy target structure 100, and the radiotherapy target structure 100 converts the beam of the electron beam into X-rays and emits them.

[0040] When the high-intensity electron beam generated by the current electron accelerating tube for radiotherapy hits the target, a large amount of heat will be deposited on the target. Coupled with the reaction with oxygen, it will cause the target material to oxidize, sublimate and deposit on the output window of the accelerating tube. On the one hand, it will accelerate the thermal shock damage to the target surface, and on the other hand, it will damage the output window, affecting the service performance of the accelerating tube. For this reason, the present invention provides a new radiotherapy target structure 100 to avoid the oxidation and deposition of the target material and ensure the service performance of the target and the accelerating tube. The following details the specific structure of the radiotherapy target structure 100.

[0041] See Figures 1 to 6 , in one embodiment, the radiotherapy target structure 100 includes a target assembly 110 and a protective housing 120. The target assembly 110 includes a support member 111 and a first target body 112 mounted on the support member 111. The protective housing 120 is wrapped around the outside of the target assembly 110. The protective housing 120 includes a first surface 123 and a second surface 124. The first surface 123 and the second surface 124 are located on both sides of the first target body 112. If described in combination with the radiotherapy environment, the first surface 123 and the second surface 124 are located on both sides of the first target body 112 along the beam direction, and at least a part of the first surface 123 and at least a part of the second surface 124 can both allow the beam to pass through. A sealed cavity A (as Figure 3 shown) is formed inside the protective housing 120, and the sealed cavity A is used to prevent the first target body 112 from being oxidized.

[0042] The target assembly 110 is the main part of the radiotherapy target structure 100, and the protective housing 120 is the protective housing 120 of the radiotherapy target structure 100. The target assembly 110 includes a support member 111 and a first target body 112. The support member 111 is the bearing part of the target assembly 110, which plays a bearing role and is used to bear the various components of the target assembly 110. The first target body 112 is arranged on the support member 111 and is used to convert the accelerated electron beam into X-rays and emit them.

[0043] The protective housing 120 includes a first surface 123 and a second surface 124. Optionally, the first surface 123 and the second surface 124 are two oppositely arranged plate bodies of the protective housing 120. Optionally, the protective housing 120 is in a box-like structure or a columnar structure, etc. Of course, in other embodiments of the present invention, the first surface 123 and the second surface 124 may also be the surfaces of other components, etc. Moreover, the first surface 123 and the second surface 124 are arranged along the beam direction and are respectively located on both sides of the first target body 112. Here, being located on both sides of the first target body 112 can be understood as that with the beam direction as the reference direction, one surface of the first target body 112 corresponds to the first surface 123, and the other surface of the first target body 112 corresponds to the second surface 124. Furthermore, at least a part of the first surface 123 and at least a part of the second surface 124 can allow the beam to pass through. The beam enters the first target body 112 along the first surface 123, and after being converted into X-rays by the first target body 112, it exits from the second surface 124.

[0044] The protective housing 120 is a sealed structure, and the inside thereof is a closed space to form a sealed cavity A. The target assembly 110 is located inside the protective housing 120, so that the target assembly 110 is in a closed environment. That is to say, the protective housing 120 is wrapped around the outside of the target assembly 110, and the working environment of the target assembly 110 is the closed environment of the sealed cavity A. In this way, after the electron beam generated by the electron generating device irradiates the target assembly 110, since the target assembly 110 is in a closed environment, that is, the oxygen content in the protective housing 120 is relatively low or even an oxygen-free environment, the situation of oxidation of the target assembly 110 is reduced.

[0045] If there is no oxygen in the protective housing 120, after the electron beam enters the first target body 112 of the target assembly 110, the first target body 112 will not undergo an oxidation reaction at high temperature. At this time, there will be no situation where oxidation substances are deposited on the output window. If there is a small amount of oxygen in the protective housing 120, after the electron beam enters the first target body 112, the first target body 112 can undergo an oxidation reaction with oxygen at high temperature to generate a small amount of oxidation substances. Because the amount of oxidation substances is relatively small, they will not sputter on the output window of the acceleration tube. Moreover, even if the oxidation substances sputter, the inner wall of the protective housing 120 will block the oxidation substances to prevent the oxidation substances from being deposited on the output window.

[0046] That is to say, the radiotherapy target structure 100 of the present invention uses a protective housing 120 with a sealed cavity to wrap the target assembly 110. After the electron beam enters the first target body 112, the first target body 112 will not undergo an oxidation reaction at high temperature or generate a small amount of oxidation substances. Through the protection of the protective housing 120, it can prevent the oxidation substances of the target assembly 110 from being deposited on the output window and ensure the safety during use.

[0047] When the first target body 112 is protected by the protective housing 120, after the beam enters the first target body 112, the temperature of the first target body 112 is several hundred degrees. Under this temperature condition, the first target body 112 undergoes an oxidation reaction with oxygen in the air, that is, the first target body 112 is oxidized. When the protective housing 120 is adopted, each component such as the first target body 112 and the support member 111 is located in the sealed cavity A, so that the first target body 112 and the support member 111 are in an environment with low oxygen or even no oxygen, preventing the oxidation of each component. Moreover, when the first target body 112 is located in the protective housing 120, the possibility of oxidation can be reduced, thereby making the dose rate / therapy beam of the first target body 112 high and ensuring the treatment effect.

[0048] For the radiotherapy target structure 100 of the above embodiment, a sealed cavity is formed inside the protective housing 120 to reduce the presence of oxygen. After the protective housing 120 is wrapped around the outside of the target assembly 110, the target assembly 110 can be in a sealed environment, which can reduce the reaction between oxygen and the first target body 112 at high temperatures, effectively solve the problem that the target material is oxidized and deposited on the output window at present, will not affect the accelerating tube, ensure the service performance, do not need to replace the output window of the accelerating tube, and reduce the cost.

[0049] See Figures 1 to 3 , in one embodiment, the protective housing 120 has a first window 121 and a second window 122 which are oppositely arranged. The first window 121 is arranged on the first surface 123, the second window 122 is arranged on the second surface 124, and the first window 121 and the second window 122 are located on both sides of the first target body 112 along the beam direction for the beam to pass through.

[0050] The first target body 112 has two surfaces along the beam direction. The first window 121 is arranged on the first surface 123 and corresponds to one surface of the first target body 112. The second window 122 is arranged on the second surface 124 and is located on the other surface of the first target body 112. Moreover, the first window 121 can allow the beam to enter, and the second window 122 can allow X-rays to exit. Specifically, the beam generated by the electron generating device is accelerated by the accelerating tube. After acceleration, the beam enters the first target body 112 through the first window 121, and after being converted into X-rays by the first target body 112, it exits through the second window 122.

[0051] Optionally, a through first mounting hole (not shown) is opened on the first surface 123 of the protective housing 120, and a through second mounting hole (not shown) is opened on the second surface 124 of the protective housing 120. The first window 121 is installed in the first mounting hole by a sealing method, and the second window 122 is installed in the second mounting hole by a sealing method.

[0052] Optionally, the first form 121 is fixed in the first mounting hole by welding. Of course, the first form 121 can also be fixed in the first mounting hole by sealing means such as sealant. Optionally, the second form 122 is fixed in the second mounting hole by welding. Of course, the second form 122 can also be fixed in the second mounting hole by sealing means such as sealant.

[0053] Optionally, the first form 121 is made of beryllium material or other materials that can allow the beam to pass through. Optionally, the second form 122 is made of beryllium, stainless steel, titanium, copper or other materials that can allow X-rays to pass through.

[0054] Optionally, the first form 121 and the second form 122 are coaxially arranged. This can ensure that the beam can pass through the second form 122 after being converted into X-rays. Of course, in other embodiments of the present invention, the axis of the first form 121 and the axis of the second form 122 can also be arranged in parallel, and at least part of the first form 121 and the second form 122 correspond along the beam direction. This can ensure that the beam can pass through the second form 122 after being converted into X-rays.

[0055] In one embodiment, the materials of the first form 121 and the second form 122 are the same as or different from the materials of the rest of the protective shell 120. That is to say, the material of the first form 121 can be the same as the material of the rest of the protective shell 120; the material of the first form 121 can be different from the material of the rest of the protective shell 120; the material of the second form 122 can be the same as the material of the rest of the protective shell 120; the material of the second form 122 can be different from the material of the rest of the protective shell 120.

[0056] When the materials of the first form 121 and the second form 122 are the same as the materials of the rest of the protective shell 120, the entire protective shell 120 is made of materials that can allow rays to pass through. That is to say, the entire protective shell 120 can allow rays to pass through. In actual use, the output window of the acceleration tube is directly aligned with the first target body 112. In this way, the beam can accurately enter the first target body 112 after passing through the protective shell 120.

[0057] See Figures 1 to 6 , in one embodiment, the radiotherapy target structure 100 further includes a cooling component 130. The cooling component 130 passes through the protective shell 120 and is arranged on the support member 111 for cooling the first target body 112. The connection between the protective shell 120 and the cooling component 130 is sealed, so that the inner wall of the protective shell 120 forms the sealed cavity A.

[0058] A part of the cooling component 130 is located inside the protective housing 120, and a part is located outside the protective housing 120. The part of the cooling component 130 outside the protective housing 120 can be connected to an external cold source, and the external cold source transports coolant into the cooling component 130. The part of the cooling component 130 inside the protective housing 120 is arranged on the support member 111 and is correspondingly arranged opposite to the first target body 112, and the first target body 112 is cooled by the coolant in the cooling component 130. The cooled coolant can be discharged to the external cold source through the cooling component 130 to realize the recycling of the coolant; of course, the coolant can also be directly discharged to the external environment through the cooling component 130. Optionally, the coolant is water or other media capable of realizing cooling, such as liquid helium, etc.

[0059] Moreover, the connection between the cooling component 130 and the protective housing 120 is sealed. This can form a sealed cavity A inside the protective housing 120 and prevent air in the outside world from entering the protective housing 120. Optionally, the connection between the cooling component 130 and the protective housing 120 is set by welding, sealant or other components capable of realizing sealing to ensure the sealing performance.

[0060] Optionally, the cooling component 130 supports the support member 111 in the protective housing 120. That is to say, there is no contact between the support member 111 and the inner wall of the protective housing 120, and the cooling component 130 can be respectively connected to the protective housing 120 and the support member 111, so that the support member 111 is suspended in the protective housing 120. Of course, in other embodiments of the present invention, after the cooling component 130 supports the support member 111, at least one surface of the support member 111 is in contact with or connected to the protective housing 120.

[0061] See Figure 2 、 Figure 9 and Figure 12 , optionally, the support member 111 has a cooling channel 11112, and the part of the cooling component 130 inside the protective housing 120 is located in the cooling channel 11112 to cool the first target body 112. Optionally, the cooling channel 11112 is communicated with the position where the first target body 112 is located, or part of the cooling channel 11112 surrounds the circumference of the first target body 112 or the first target seat 1112. The cooling channel 11112 has an inlet and an outlet, and the cooling component 130 is respectively connected to the inlet and the outlet.

[0062] Optionally, the cooling assembly 130 includes a cooling inlet pipe 131 and a cooling outlet pipe 132, which are respectively arranged in the cooling channel 11112. One end of the cooling inlet pipe 131 is connected to the output end of an external cold source, and one end of the cooling outlet pipe 132 is connected to the input end of the external cold source. The other end of the cooling inlet pipe 131 is arranged at the entrance of the cooling channel 11112 and is in communication with the cooling channel 11112. The other end of the cooling outlet pipe 132 is arranged at the exit of the cooling channel 11112 and is in communication with the cooling channel 11112.

[0063] The output end of the external cold source transports the coolant into the cooling inlet pipe 131 and then transports it into the cooling channel 11112 through the cooling inlet pipe 131. The coolant in the cooling channel 11112 cools the first target body 112, and then the heat-absorbed coolant enters the cooling outlet pipe 132 through the cooling channel 11112 and is transported to the external cold source through the cooling outlet pipe 132 and enters through the input end. The coolant is cooled by the external cold source to realize the recycling of the coolant.

[0064] Of course, in other embodiments of the present invention, the cooling assembly 130 includes a cooling pipe, which has an inlet end and an outlet end. The cooling pipe is arranged in the cooling channel 11112 and is located on the periphery of the first target body 112 or the first target base 1112. The inlet end is connected to the output end of the external cold source, and the outlet end is connected to the input end of the external cold source.

[0065] It should be noted that the cooling pipe only differs from the cooling inlet pipe 131 and the cooling outlet pipe 132 in the above embodiment in terms of structural arrangement, and the principle of cooling the first target body 112 is essentially the same, so details will not be elaborated here.

[0066] In one embodiment, a ventilation hole (not shown) is opened on the protective housing 120, and the ventilation hole is connected to an external vacuum pump. The vacuum pump can evacuate the inside of the protective housing 120 through the ventilation hole, so that the inside of the protective housing 120 remains in a vacuum state. In this way, during actual use, the inside of the protective housing 120 is a vacuum environment, so that the first target body 112 is in an oxygen-free working state and will not undergo an oxidation reaction at high temperatures, ensuring the use performance.

[0067] Optionally, the protective housing 120 and the target assembly 110, the cooling assembly 130 can also be welded or other sealing operations in a vacuum environment (such as in a vacuum furnace), so that the closed cavity inside the protective housing 120 is a vacuum environment. That is to say, no ventilation hole is provided on the protective housing 120, and the installation of the radiotherapy target structure 100 is directly realized through a vacuum assembly method.

[0068] Of course, in other embodiments of the present invention, the protective housing 120 can also be connected to devices such as an inert gas source through ventilation holes. After the ventilation holes are connected to the inert gas source, the inert gas source can introduce inert gas into the protective housing 120 through the ventilation holes, so that the protective housing 120 is filled with inert gas, which can also make the first target body 112 in an oxygen-free working state and prevent oxidation reactions from occurring at high temperatures, ensuring the performance.

[0069] See Figures 1 to 6 , in one embodiment, the support member 111 includes a target substrate 1111 and a first target base 1112. The target substrate 1111 has a first through hole 11111 extending along the beam direction (as Figure 9 shown), and the first target base 1112 is installed in the first through hole 11111. The first target base 1112 is used to install the first target body 112. The target substrate 1111 is the carrier plate of the support member 111 and is used to carry the various components of the target assembly 110. The first target base 1112 also plays a supporting role and is used to realize the installation of the first target body 112.

[0070] Optionally, at least one surface of the target substrate 1111 is fixedly arranged in the protective housing 120, and there is a certain space between the remaining surfaces of the target substrate 1111 and the inner wall of the protective housing 120. This can make the target substrate 1111 be reliably fixed in the protective housing 120 and prevent the target assembly 110 from moving. Optionally, the target substrate 1111 is supported by a metal material. Since the target substrate 1111 is located in the sealed cavity, this can prevent the target substrate 1111 from being oxidized.

[0071] The target substrate 1111 has a first through hole 11111 that penetrates through it, and the first target base 1112 and the first target body 112 thereon are installed in the first through hole 11111. During operation, after the beam passes through the first window 121, it enters the first target body 112. After the beam is converted into X-rays by the first target body 112, the X-rays are emitted through the second window 122. After the target substrate 1111 is fixed in the protective housing 120, the first target body 112 is in the sealed environment of the protective housing 120, which can reduce the oxidation of the substances generated by the first target body 112 and ensure the performance.

[0072] In one embodiment, the first target base 1112 and the target substrate 1111 are detachably connected. This can facilitate the replacement of the first target base 1112 and the first target body 112 thereon and is convenient for use. Optionally, the first target base 1112 and the target substrate 1111 are fixed by welding or other means. When replacement is needed, the welded part can be removed. In other embodiments of the present invention, the first target base 1112 and the target substrate 1111 can also be detachably connected by other means.

[0073] In one embodiment, the first target base 1112 and the target substrate 1111 are of an integral structure. That is to say, the first target base 1112 and the target substrate 1111 are non-detachable structures. For example, the first target base 1112 and the target substrate 1111 can be processed by an integral molding method. When replacing the first target body 112, the first target body 112 can be directly detached from the first target base 1112.

[0074] See Figures 1 to 6 , in one embodiment, an installation groove 11121 is formed on the surface of the first target base 1112 facing the first window 121, and the first target body 112 is disposed in the installation groove 11121. The first target base 1112 functions as a carrier for carrying the first target body 112. The first target body 112 can be reliably installed through the installation groove 11121, preventing the position of the first target body 112 from shifting and ensuring that the beam can accurately enter the first target body 112.

[0075] It can be understood that the depth of the installation groove 11121 is not limited in principle as long as the installation of the first target body 112 can be achieved. Optionally, the depth of the installation groove 11121 is slightly greater than the height of the first target body 112. Of course, in other embodiments of the present invention, the depth of the installation groove 11121 can also be less than or equal to the height of the first target body 112. Optionally, the first target base 1112 is fixed in the first through hole 11111 of the target substrate 1111 by welding to ensure reliable fixation. At the same time, the welding method will not affect the first target body 112, ensuring that the first target body 112 can convert the beam into X-rays. Of course, in other embodiments of the present invention, the first target body 112 can also be directly fixed to the end of the first target base 1112 facing the first window 121.

[0076] See Figure 2 and Figure 3 , in one embodiment, the support member 111 further includes a target holder 1113, and the target holder 1113 is disposed on the first target base 1112 for installing the first target body 112. Specifically, the target holder 1113 is disposed at the end of the first target base 1112 facing the first window 121. Further, the target holder 1113 can be disposed in the installation groove 11121. The first target body 112 is carried by the target holder 1113 to ensure that the first target body 112 is reliably fixed in the installation groove 11121. Moreover, when the first target body 112 needs to be replaced, the target holder 1113 can be removed, facilitating the replacement of the first target body 112.

[0077] See Figure 2 and Figure 3, in one embodiment, a recess 11122 is formed on the surface of the first target base 1112 facing away from the first target body 112. The recess 11122 is arranged corresponding to the first target body 112 and is used for the ray to pass through. That is to say, the recess 11122 is formed on the end face of the first target base 1112 aligned with the second window 122. By adapting the recess 11122 to the first target body 112, the service performance of the first target body 112 is ensured. Optionally, the recess 11122 is frustum-shaped. Of course, in other embodiments of the present invention, the recess 11122 may also be cylindrical, trapezoidal in cross-section, etc. Optionally, the recess 11122 is coaxially arranged with the mounting groove 11121.

[0078] Optionally, the cross-sectional area of the first window 121 is smaller than that of the second window 122. That is to say, the cross-sectional area of the first window 121 is small, and the cross-sectional area of the second window 122 is large. After the beam enters the first target body 112 and is converted into X-rays by the first target body 112, since the X-rays are divergent, the larger cross-sectional area of the first window 121 can ensure that the X-rays accurately exit through the second window 122 and avoid blocking the rays.

[0079] As Figures 1 to 3 , Figure 9 As shown in the figure, in one embodiment of the present invention, there is a preset space between the outer wall of the first target base 1112 and the inner wall of the first through hole 11111. The preset space is for the cooling component 130 to pass through and is used to cool the first target body 112. This preset space can facilitate the cooling component 130 to effectively cool the first target body 112. It can be understood that the cooling component 130 can be directly located in the preset space, or the coolant can be introduced into the preset space. The corresponding layout of the cooling method for the cooling component 130 has been described in detail at the specific structure of the cooling component 130 above and will not be elaborated here one by one.

[0080] Specifically, taking the example that the cooling component 130 conveys the coolant into the preset space, after the cooling channel 11112 of the target substrate 1111 is connected to the first through hole 11111, the cooling component 130 can make the coolant be located in the first through hole 11111, and cool the first target base 1112 through the coolant in the first through hole 11111 to cool the first target body 112 and reduce the temperature of the first target body 112, ensuring the service performance of the first target body 112.

[0081] See Figures 1 to 3 , in one embodiment of the present invention, the first through hole 11111 includes a first stepped hole and a second stepped hole arranged coaxially, and the diameter of the first stepped hole is larger than that of the second stepped hole. After the first target base 1112 is installed in the first through hole 11111, the inner wall of the first target base 1112 abuts against the inner wall of the second stepped hole and encloses a preset space with the inner wall of the first stepped hole.

[0082] The diameter of the second stepped hole is adapted to the diameter of the first target seat 1112. After the first target seat 1112 is installed in the first through hole 11111, the outer wall of the first target seat 1112 is combined with the inner wall of the second stepped hole to ensure tightness and prevent the beam from passing through. At the same time, an annular preset space is formed between the outer wall of the first target seat 1112 and the inner wall of the first stepped hole, and this preset space is used to install the cooling component 130. Moreover, the preset space is close to the position of the first target body 112 along the beam direction and is relatively close to the first target body 112, so that the cooling component 130 can better cool the first target body 112 and ensure the heat dissipation of the first target body 112.

[0083] Certainly, in other embodiments of the present invention, the first through hole 11111 is a cylindrical hole, and an avoidance groove is provided on the inner wall of the first through hole 11111. The avoidance groove is recessed along the radial direction of the first through hole 11111 to form a preset space for installing the cooling component 130. In other embodiments of the present invention, the first target seat 1112 is provided in a stepped shape, and the outer wall of the first target seat 1112 and the inner wall of the first through hole 11111 enclose a preset space; of course, both the first target seat 1112 and the first through hole 11111 can be in a stepped shape and cooperate to form a preset space.

[0084] See Figures 4 to 9 , in another embodiment of the present invention, a cooling groove 11123 is provided on the outer wall of the first target seat 1112. The cooling groove 11123 communicates with the installation groove 11121, and the cooling groove 11123 is used for the cooling component 130 to pass through to cool the first target body 112. That is to say, a cooling groove 11123 is provided on the outer wall of the first target seat 1112. One end of the cooling groove 11123 communicates with the installation groove 11121, and the other end communicates with the cooling channel 11112. The cooling component 130 cools the first target body 112 in the installation groove 11121 through the cooling groove 11123 to ensure the normal operation of the first target body 112.

[0085] See Figures 1 to 3, in one embodiment, the first target seat 1112 has a fixed edge 11124 which protrudes along the radial direction of the first through hole 11111, making the first target seat 1112 in a stepped shape. The first through hole 11111 further includes a fixing groove located at the edge of the target substrate 1111 for installing the fixed edge 11124. The fixed edge 11124 protrudes along the radial direction from the outer wall of the first target seat 1112. That is to say, the fixed edge 11124 and the main body part of the first target seat 1112 form a stepped structure. During installation, after the fixed edge 11124 is installed in the fixing groove, the first target seat 1112 is located in the first through hole 11111. Through the cooperation and limitation between the fixed edge 11124 and the fixing groove, the first target seat 1112 can be prevented from slipping out of the first through hole 11111, facilitating the installation and fixation of the first target seat 1112.

[0086] See Figures 1 to 6 , in one embodiment, the support member 111 further includes a second target seat 1114, and the target assembly 110 further includes a second target body 113. The target substrate 1111 has a second through hole (not shown) along the beam direction. The second target seat 1114 is disposed in the second through hole for installing the second target body 113; the second target seat 1114 is located inside or outside the protective housing 120. The second target body 113 has a different structure from the first target body 112 and there are also certain differences in their functions. The second target body 113 is used to increase the usage range of the radiotherapy target structure 100. When the first target body 112 needs to be used, the beam passes through the first target body 112; when the second target body 113 needs to be used, the beam passes through the second target body 113.

[0087] See Figures 1 to 3 , optionally, the second target body 113 is located inside the protective housing 120. That is to say, the second target body 113 is also in the sealed cavity A inside the protective housing 120. At this time, a window is provided at the position corresponding to the second target body 113 on the protective housing 120 to facilitate the beam to pass through. When the second target body 113 is located behind the protective housing 120, the second target body 113 can be prevented from oxidation. Of course, in other embodiments of the present invention, the second target body 113 is located outside the protective housing 120, which is convenient for the replacement and installation of the second target body 113. For example, see Figures 4 to 6 .

[0088] It is worth noting that when two targets are provided on the target substrate 1111, namely the first target body 112 and the second target body 113, among which, the first target body 112 is the treatment target and the second target body 113 is the imaging target. The X-rays converted by the beam passing through the first target body 112 can be used to treat the diseased part of the patient, and the X-rays converted by the beam passing through the second target body 113 can be used to image the diseased position of the patient.

[0089] The first target body 112 is a high-energy target, such as a tungsten target. After the beam enters the tungsten target, a large amount of heat is generated, causing the temperature of the tungsten target to rise. At high temperatures, the reaction between tungsten and oxygen is accelerated. Therefore, the first target body 112 is placed in the protective housing 120 to ensure the performance of the first target body 112 and reduce the occurrence of oxidation reaction of the first target body 112.

[0090] The second target body 113 is a low-power and low-energy target, generally a copper target, an aluminum target, a graphite target, etc. The second target body 113 will also undergo an oxidation reaction at high temperatures. However, since the second target body 113 is an imaging target and the dose rate during imaging is low, its degree of oxidation is within an acceptable range. That is, when the second target body 113 undergoes an oxidation reaction at high temperatures, less oxidation substances are generated, which will not be deposited on the output window and will not affect the performance of the output window. Of course, in other embodiments of the present invention, the second target body 113 can also be a treatment target.

[0091] Optionally, the second target seat 1114 is fixed on the target substrate 1111 by means of welding, interference fit, snap connection, etc. Of course, in other embodiments of the present invention, the second target seat 1114 and the target substrate 1111 can also be an integral structure.

[0092] See Figures 10 to 12 , at least a part of the second target seat 1114 is hermetically connected to the protective housing 120 so that the second target body 113 is located outside the sealed cavity A. In this way, the second target body 113 can be located outside the protective housing 120, which is convenient for replacing the second target body 113 and can also prevent the first target body 112 from being oxidized.

[0093] See Figures 10 to 12 , in one embodiment, the support member 111 further includes a hollow second target seat 1114. The target assembly 110 further includes a second target body 113. The target substrate 1111 has a second through hole along the beam direction. The first surface 123 has a first hole, and the second surface 124 has a second hole. The first hole and the second hole are located on both sides of the second through hole along the beam direction and are coaxially arranged. The second target seat 1114 is installed in the first hole and the second hole by a sealing method and is in contact connection with the second through hole. The second target seat 1114 is used to install the second target body 113.

[0094] That is to say, in this embodiment, although the target substrate 1111 where the second target body 113 is located is between the first surface 123 and the second surface 124 of the protective housing 120, through the isolation of the second target seat 1114, the second target body 113 can be exposed outside the protective housing 120 for the convenience of replacing the second target body 113.

[0095] Specifically, the second target base 1114 is provided in a hollow manner, and the second target body 113 is installed inside the second target base 1114. Moreover, a first hole is formed on the first surface 123 of the protective housing 120, a second hole is formed on the second surface 124, the target substrate 1111 has a second through hole, and the axes of the first hole, the second through hole, and the second hole coincide. Also, the first hole and the second hole are respectively located on both sides of the second through hole. At this time, the first hole, the second through hole, and the second hole are arranged corresponding to each other along the beam direction to achieve the installation of the second target base 1114.

[0096] The second target base 1114 is installed in the first hole and the second hole in a sealed manner, that is, the outer wall of the second target base 1114 can be in sealed contact with the inner walls of the first hole and the second hole. That is to say, after the second target base 1114 is installed on the protective housing 120 and the target substrate 1111, the protective housing 120 and the second target base 1114 can enclose a sealed cavity A. The second target body 113 is located in the second target base 1114 and exposes the protective housing 120, and can be in contact with the outside air.

[0097] By setting in this way, on the one hand, it isolates the outside air from entering the protective housing 120 and reduces the occurrence of oxidation of the first target body 112. On the other hand, it is convenient to replace the second target body 113 and improves the replacement efficiency. Moreover, the second target base 1114 is in contact connection with the target substrate 1111, which can ensure the heat transfer effect, and the cooling assembly 130 cools down the second target base 1114 and the second target body 113.

[0098] Optionally, the protective housing 120 further includes a window body, and the window body covers the two ends of the second target base 1114 at the first hole and the second hole to protect the second target body 113 and prevent the second target body 113 from being oxidized. Of course, in other embodiments of the present invention, the second target body 113 can also be directly exposed outside the protective housing 120.

[0099] Optionally, a placement groove is formed in the second target base 1114, and the second target body 113 is disposed in the placement groove. Optionally, the second target base 1114 is cylindrically arranged and is adapted to the shape of the second through hole. Of course, in other embodiments of the present invention, the second target base 1114 may also be conical. In one embodiment, the support member 111 further includes a third target base (not shown), the target assembly 110 further includes a third target body (not shown), the target substrate 1111 has a third through hole along the beam direction, and the third target base is disposed in the third through hole for mounting the third target body; the third target base is located inside or outside the protective housing 120. The third target body is different in structure from the second target body 113 and the first target body 112, and there are also certain differences in its functions. After the second target body 113 and the third target body are disposed on the target substrate 1111, the usage range of the radiotherapy target structure 100 can be increased. When the first target body 112 is needed, the beam passes through the first target body 112; when the second target body 113 is needed, the ray passes through the first target body 112; when the third target body is needed, the ray passes through the third target body.

[0100] Optionally, the third target body is located inside the protective housing 120. That is to say, the third target body is also in the sealed cavity A inside the protective housing 120. At this time, a window is provided at the position corresponding to the third target body on the protective housing 120 to facilitate the beam to pass through. When the third target body is located behind the protective housing 120, oxidation of the third target body can be prevented. Of course, in other embodiments of the present invention, the third target body is located outside the protective housing 120, which is convenient for replacement and installation of the third target body.

[0101] It should be noted that when three targets are provided on the target substrate 1111, they are the first target body 112, the second target body 113, and the third target body respectively. Among them, the first target body 112 is a treatment target, the second target body 113 is an imaging target, the third target body is a treatment target, the first target body 112 is a high-energy target, and the second target body 113 and the third target body are low-energy targets. The X-rays converted by the beam passing through the first target body 112 can be used to treat the lesion site of the patient, the X-rays converted by the beam passing through the second target body 113 can image the lesion position of the patient, and the X-rays converted by the beam passing through the third target body can be used to treat the lesion position of the patient.

[0102] Of course, in other embodiments of the present invention, the second target body 113 and the third target body may both be treatment targets, or both be imaging targets, or the second target body 113 is a treatment target and the third target body is an imaging target. In the present invention, the case where the second target body 113 is an imaging target and the third target body is a treatment target is taken as an example for description.

[0103] The first target body 112 is a high-energy target, specifically a tungsten target. When the beam enters the tungsten target, a large amount of heat will be generated, causing the temperature of the tungsten target to rise. At high temperatures, the reaction between tungsten and oxygen is accelerated. Therefore, the first target body 112 is arranged in the protective housing 120 to ensure the service performance of the first target body 112 and prevent the first target body 112 from undergoing an oxidation reaction.

[0104] The second target body 113 is a low-power and low-energy target, generally a copper target, an aluminum target, a graphite target, etc. The second target body 113 will also undergo an oxidation reaction at high temperatures. However, since the second target body 113 is an imaging target and has a low dose rate during imaging, its degree of oxidation is within an acceptable range. That is, when the second target body 113 undergoes an oxidation reaction at high temperatures, less oxidation products are generated, which will not deposit on the output window and will not affect the service performance of the output window.

[0105] The third target body is a low-power and low-energy target, generally a copper target, an aluminum target, a graphite target, etc. The third target body will also undergo an oxidation reaction at high temperatures. However, since the third target body is a treatment target and has a low dose rate during treatment, its degree of oxidation is within an acceptable range. That is, when the third target body undergoes an oxidation reaction at high temperatures, less oxidation products are generated, which will not deposit on the output window and will not affect the service performance of the output window.

[0106] Optionally, the third target seat is provided with a receiving groove, and the third target body is arranged in the receiving groove. Optionally, the third target seat is cylindrical and is adapted to the shape of the third through hole. Optionally, the third target seat is fixed on the target substrate 1111 by welding or other means. Of course, in other embodiments of the present invention, the third target seat and the target substrate 1111 may also be an integral structure.

[0107] Of course, in other embodiments of the present invention, the target assembly 110 may further include more target bodies, such as four, five, etc.

[0108] In the radiotherapy device of the present invention, by arranging the high-energy first target body 112 in the protective housing 120 which is a sealed cavity A, the contact between the first target body 112 and oxygen is reduced. When the beam passes through the first target body 112, the first target body 112 will generate a large amount of heat. Since the protective housing 120 is in a sealed cavity A, the oxidation products of the first target body 112 will not deposit on the output window of the electron generating device, and there is no need to replace the output window, reducing the use cost.

[0109] The present invention further provides a radiotherapy device, which includes an electron generating device, an accelerating tube, and the radiotherapy target structure 100 in the above embodiment. The electron generating device is used to generate an electron beam, the accelerating tube is used to accelerate the electron beam, and the radiotherapy target structure 100 is used to convert the accelerated electron beam into X-rays and emit them. After adopting the radiotherapy target structure 100 of the above embodiment, while ensuring the use performance, oxidation of the first target body 112 is avoided, and further, the oxidation substances of the first target body 112 are prevented from depositing on the output window, thus ensuring the use performance.

[0110] The technical features of the above embodiments can be combined arbitrarily. For the sake of brevity of description, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, it should be considered as the scope described in this specification.

[0111] The above embodiments only represent several implementation manners of the present invention. The description is relatively specific and detailed, but it should not be construed as a limitation on the scope of the invention patent. It should be noted that for those of ordinary skill in the art, without departing from the concept of the present invention, several modifications and improvements can still be made, and these all belong to the protection scope of the present invention. Therefore, the protection scope of the invention patent should be subject to the appended claims.

Claims

1. A radiotherapy target structure, characterized in that, Comprising: A target assembly, including a support member and a first target body mounted on the support member; And A protective housing, wrapped around the outside of the target assembly; the protective housing includes a first surface and a second surface, the first surface and the second surface are located on opposite sides of the first target body, at least a part of the first surface and at least a part of the second surface can both allow the beam to pass through, and a sealed cavity is formed inside the protective housing, and the sealed cavity is used to prevent the first target body from being oxidized; Wherein, the radiotherapy target structure further includes a cooling assembly, the cooling assembly passes through the protective housing and is arranged on the support member for cooling the first target body, and the cooling assembly supports and suspends the support member in the protective housing.

2. The radiotherapy target structure according to claim 1, characterized in that, The protective housing further includes a first window and a second window arranged opposite to each other, the first window is arranged on the first surface, the second window is arranged on the second surface, and the first window and the second window are located on both sides of the first target body for allowing the beam to pass through.

3. The radiotherapy target structure according to claim 1, wherein The connection between the protective housing and the cooling assembly is sealed to form the sealed cavity inside the protective housing.

4. The radiotherapy target structure according to claim 3, wherein The support member includes a target substrate and a first target seat, the target substrate has a first through hole extending along the beam direction, and the first target seat is mounted in the first through hole, and the first target seat is used for mounting the first target body.

5. The radiotherapy target structure according to claim 4, wherein, The surface of the first target seat facing the first surface has a mounting groove for mounting the first target body; And / or, a recess is formed on the surface of the first target seat facing the second surface, the recess is arranged corresponding to the first target body for allowing the beam to pass through.

6. The radiotherapy target structure according to claim 4, characterized in that, There is a preset space between the outer wall of the first target seat and the inner wall of the first through hole, and the preset space allows the cooling assembly to pass through for cooling the first target body.

7. The radiotherapy target structure according to claim 6, wherein The first through hole includes a first stepped hole and a second stepped hole arranged coaxially, and the diameter of the first stepped hole is larger than that of the second stepped hole. After the first target seat is mounted in the first through hole, the inner wall of the first target seat abuts against the inner wall of the second stepped hole and encloses the preset space with the inner wall of the first stepped hole.

8. The radiotherapy target structure according to claim 4, wherein, The support member further includes a second target seat, the target assembly further includes a second target body, the target substrate has a second through hole extending along the beam direction, and the second target seat is arranged in the second through hole for mounting the second target body.

9. The radiotherapy target structure according to claim 8, characterized in that, At least a part of the second target seat is hermetically connected to the protective housing so that the second target body is located outside the sealed cavity.

10. A radiotherapy device, characterized in that, Including an electron generating device, an accelerating tube, and the radiotherapy target structure according to any one of claims 1 to 9, the electron generating device is used to generate an electron beam, the accelerating tube is used to accelerate the electron beam, and the radiotherapy target structure is used to convert the accelerated electron beam into X-rays and emit them.

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