CN215916245U

CN215916245U - Radiotherapy target structure and radiotherapy equipment

Info

Publication number: CN215916245U
Application number: CN202121783687.2U
Authority: CN
Inventors: 贺守波; 韩卫; 刘艳芳; 文朝廷; 董守增; 王理
Original assignee: Shanghai United Imaging Healthcare Co Ltd
Current assignee: Shanghai United Imaging Healthcare Co Ltd
Priority date: 2021-08-02
Filing date: 2021-08-02
Publication date: 2022-03-01
Anticipated expiration: 2031-08-02

Abstract

The utility model relates to a radiotherapy target structure and radiotherapy equipment. This radiotherapy target structure includes: a target assembly including a support and a first target body mounted to the support; the protective shell is wrapped on the outer side of the target assembly; the protective shell comprises a first face and a second face, the first face and the second face are located on two opposite sides of the first target body, at least one part of the first face and at least one part of the second face can be penetrated by a beam, a sealed cavity is formed inside the protective shell, and the sealed cavity is used for preventing the first target body from being oxidized. When electron beams emitted by the electron generating device hit the first target body to generate heat, the oxidizing substances generated by the first target body can be reduced, the sputtering of the oxidizing substances can be avoided, the accelerating tube cannot be influenced, the use performance is ensured, the service lives of the first target body and the accelerating tube are prolonged, the output window of the accelerating tube does not need to be replaced, and the cost is reduced.

Description

Radiotherapy target structure and radiotherapy equipment

Technical Field

The utility model relates to the technical field of imaging equipment, in particular to a radiotherapy target structure and radiotherapy equipment.

Background

The in-process that the high strength electron beam that electron accelerating tube produced that radiotherapy used hits the target and produce the photon can deposit a large amount of heats on the target, and the target surface can produce quick temperature variation, and the high temperature target of work can accelerate the thermal shock damage on target surface in the air, for example leads to the target matter to sublimate after the oxidation to the deposit causes destruction, influence performance on the output window on accelerating tube. Moreover, the process of replacing the output window is very complicated, the cost is high, and the cost is increased.

SUMMERY OF THE UTILITY MODEL

In view of the above, it is necessary to provide a radiotherapy target structure and a radiotherapy apparatus capable of avoiding oxidation reaction in order to solve the problem of the oxidation deposition of the target substance on the output window.

A radiotherapy target structure comprising:

a target assembly including a support and a first target body mounted to the support; and

the protective shell is wrapped on the outer side of the target assembly; the protective shell comprises a first face and a second face, the first face and the second face are located on two opposite sides of the first target body, at least one part of the first face and at least one part of the second face can be penetrated by a beam, a sealed cavity is formed inside the protective shell, and the sealed cavity is used for preventing the first target body from being oxidized.

In one embodiment, the protective housing further includes a first window and a second window, which are disposed opposite to each other, the first window is disposed on the first surface, the second window is disposed on the second surface, and the first window and the second window are located on two sides of the first target body and are used for the beam to pass through.

In one embodiment, the radiotherapy target structure further comprises a cooling assembly passing through the protective housing and disposed at the support for cooling the first target body;

the joint of the protective shell and the cooling assembly is arranged in a sealing mode, so that the sealed cavity is formed inside the protective shell.

In one embodiment, the support comprises a target substrate having a first through hole extending in the beam direction, and a first backing plate mounted in the first through hole for mounting the first target body.

In one embodiment, a surface of the first backing plate facing the first face has a mounting groove for mounting the first target body;

and/or a concave part is arranged on the surface of the first target holder facing the second surface, and the concave part is arranged corresponding to the first target body and used for a beam to pass through.

In one embodiment, a predetermined space is present between an outer wall of the first backing plate and an inner wall of the first through hole, the predetermined space being passed through by the cooling assembly for cooling the first target body.

In one embodiment, the first through hole includes a first stepped hole and a second stepped hole which are coaxially disposed, a diameter of the first stepped hole is larger than a diameter of the second stepped hole, and after the first target holder is mounted in the first through hole, an inner wall of the first target holder abuts against an inner wall of the second stepped hole and encloses the predetermined space with the inner wall of the first stepped hole.

In one embodiment, the support further comprises a second backing plate, the target assembly further comprises a second target body, the target substrate has a second through hole extending in the beam direction, and the second backing plate is disposed in the second through hole for mounting the second target body.

In one embodiment, at least a portion of the second backing plate is sealingly coupled to the protective enclosure such that the second target body is positioned outside the sealed enclosure volume.

A radiotherapy apparatus comprising an electron generating device for generating an electron beam, an accelerating tube for accelerating the electron beam, and a radiotherapy target structure according to any one of the above technical features, wherein the radiotherapy target structure is used for converting the accelerated electron beam into X-rays.

After the technical scheme is adopted, the utility model at least has the following technical effects:

according to the radiotherapy target structure and the radiotherapy equipment, after the protective shell is additionally arranged on the outer side of the target assembly, electron beams emitted by the electron generating device of the radiotherapy equipment penetrate through the first surface of the protective shell and are emitted into the first target body, and then are converted into X rays which are emitted through the second surface. Moreover, a sealed cavity is formed in the protective shell, so that the first target body works in a sealed environment, and the existence of oxygen is reduced. Like this, when electron beam that electron generation device launched hit first target body and produce the heat, can reduce the oxidation material that first target body produced, moreover, even first target body produces oxidation material, because of the seal of protecting sheathing, can avoid oxidation material sputter protecting sheathing, the effectual problem of target material oxidation deposit at the output window of accelerating tube of solving now, can not exert an influence to the accelerating tube, guarantee performance, the life of extension first target body and accelerating tube, the output window that need not to change the accelerating tube, reduce cost.

Drawings

FIG. 1 is a perspective view of a radiotherapy target configuration in accordance with an embodiment of the present invention;

figure 2 is a cut-away perspective view of the radiation therapy target structure shown in figure 1;

figure 3 is a cross-sectional view of the radiation therapy target structure shown in figure 2;

figure 4 is a perspective view of a radiation therapy target construction in accordance with another embodiment of the present invention;

figure 5 is a schematic cut-away view of the radiotherapy target structure shown in figure 4;

figure 6 is a cross-sectional view of the radiation therapy target structure shown in figure 5;

fig. 7 is a perspective view of a first backing plate of the radiation therapy target structure shown in fig. 6;

FIG. 8 is a cross-sectional view of the first backing plate shown in FIG. 6;

figure 9 is a top cross-sectional view of the radiation therapy target structure shown in figure 6 with the target assembly coupled to the cooling assembly;

figure 10 is a cross-sectional view of a radiation therapy target construction in accordance with yet another embodiment of the present invention

Figure 11 is a cutaway perspective view of the radiation therapy target structure shown in figure 10;

figure 12 is a perspective view of the radiation therapy target structure shown in figure 10.

Wherein: 100. a radiotherapy target structure; 110. a target assembly; 111. a support member; 1111. a target substrate; 11111. a first through hole; 11112. a cooling channel; 1112. a first target holder; 11121. mounting grooves; 11122. a recess; 11123. a cooling tank; 11124. fixing the edge; 1113. a target holder; 1114. a second target holder; 112. a first target body; 113. a second target body; 120. a protective housing; 121. a first window; 122. a second window; 123. a first side; 124. a second face; 130. a cooling assembly; 131. cooling the inlet pipe; 132. cooling out the pipe; A. and sealing the cavity.

Detailed Description

In order to make the aforementioned objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in detail below. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present invention. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein.

In the description of the present invention, it is to be understood that the terms "central," "longitudinal," "lateral," "length," "width," "thickness," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," "counterclockwise," "axial," "radial," "circumferential," and the like are used in the orientations and positional relationships indicated in the drawings for convenience in describing the utility model and to simplify the description, and are not intended to indicate or imply that the referenced device or element must have a particular orientation, be constructed and operated in a particular orientation, and are not to be considered limiting of the utility model.

Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one such feature. In the description of the present invention, "a plurality" means at least two, e.g., two, three, etc., unless specifically limited otherwise.

In the present invention, unless otherwise expressly stated or limited, the terms "mounted," "connected," "secured," and the like are to be construed broadly and can, for example, be fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; they may be directly connected or indirectly connected through intervening media, or they may be connected internally or in any other suitable relationship, unless expressly stated otherwise. The specific meanings of the above terms in the present invention can be understood by those skilled in the art according to specific situations.

In the present invention, unless otherwise expressly stated or limited, the first feature "on" or "under" the second feature may be directly contacting the first and second features or indirectly contacting the first and second features through an intermediate. Also, a first feature "on," "over," and "above" a second feature may be directly or diagonally above the second feature, or may simply indicate that the first feature is at a higher level than the second feature. A first feature being "under," "below," and "beneath" a second feature may be directly under or obliquely under the first feature, or may simply mean that the first feature is at a lesser elevation than the second feature.

It will be understood that when an element is referred to as being "secured to" or "disposed on" another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and the like as used herein are for illustrative purposes only and do not denote a unique embodiment.

Referring to fig. 1-6, the present invention provides a radiotherapy target structure 100. The radiotherapy target structure 100 is applied to a radiotherapy apparatus (not shown) and can treat and/or image a lesion site of a patient. It is understood that the radiotherapy target structure 100 can be used in conjunction with an electron generating device of a radiotherapy apparatus, and a beam generated by the electron generating device passes through the radiotherapy target structure 100 to be converted into photons to be projected to a lesion of a patient, so as to perform radiotherapy or imaging, etc. Specifically, after an electron beam is generated by an electron generating device (not shown) of the radiotherapy apparatus, the electron beam is accelerated by an accelerating 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 an X-ray and emits the X-ray.

When the high-strength electron beam current that electron accelerating tube produced that present radiotherapy used hits target, can deposit a large amount of heats on the target, in addition with the reaction between the oxygen, can lead to the target matter to sublimate after the oxidation and deposit on the output window of accelerating tube, on the one hand can accelerate the thermal shock damage to the target surface, on the other hand leads to the fact the destruction to the output window, influences the performance of accelerating tube. Therefore, the present invention provides a novel radiotherapy target structure 100 to avoid the oxidative deposition of target material and ensure the usability of the target and the accelerating tube. The specific structure of the radiotherapy target structure 100 is described in detail below.

Referring to fig. 1-6, in one embodiment, a radiotherapy target structure 100 includes a target assembly 110 and a protective housing 120. The target assembly 110 includes a support 111 and a first target body 112 mounted to the support 111. The shield case 120 is wrapped around the outside of the target assembly 110. The protective housing 120 includes a first face 123 and a second face 124, the first face 123 and the second face 124 being located on either side of the first target body 112, and if described in connection with a radiation treatment environment, the first face 123 and the second face 124 being located on either side of the first target body 112 along a beam direction, at least a portion of the first face 123 and at least a portion of the second face 124 being capable of being traversed by the beam. The interior of the protective enclosure 120 forms a sealed volume a (shown in fig. 3) for protecting the first target body 112 from oxidation.

The target assembly 110 is a main body portion of the radiation therapy target structure 100 and the protective housing 120 is the protective housing 120 of the radiation therapy target structure 100. The target assembly 110 includes a support 111 and a first target body 112. The support 111 is a bearing portion of the target assembly 110, and is used for bearing various components of the target assembly 110. The first target body 112 is disposed on the support 111, and converts the accelerated electron beam into X-rays to be emitted.

The protective housing 120 includes a first face 123 and a second face 124. Optionally, the first face 123 and the second face 124 are two oppositely disposed plates of the protective housing 120. Alternatively, the protective housing 120 is a box-like structure or a cylinder structure, etc. Of course, in other embodiments of the present invention, the first surface 123 and the second surface 124 may be surfaces of other components, and the like. The first surface 123 and the second surface 124 are disposed along the beam direction and located on both sides of the first target body 112. Here, the two sides of the first target body 112 may be understood as one surface of the first target body 112 corresponding to the first surface 123 and the other surface of the first target body 112 corresponding to the second surface 124 with the beam direction as a reference direction. Moreover, at least a portion of the first face 123 and at least a portion of the second face 124 are capable of being traversed by the beam. The beam is incident on the first target body 112 along the first surface 123, converted into X-rays by the first target body 112, and then emitted from the second surface 124.

The protective housing 120 is a sealed structure, and a sealed space is formed therein to form a sealed cavity a. The target assembly 110 is located within the protective enclosure 120 such that the target assembly 110 is in a closed environment. That is, the protective housing 120 is wrapped around the outside of the target assembly 110, and the working environment of the target assembly 110 is a closed environment sealing the cavity a. Thus, after the electron beam generated by the electron generating device irradiates the target assembly 110, the target assembly 110 is in a closed environment, i.e., the protective enclosure 120 has a low oxygen content or even an oxygen-free environment, so that the target assembly 110 is less oxidized.

If no oxygen is present in the protective enclosure 120, after the electron beam is incident on the first target body 112 of the target assembly 110, the first target body 112 will not undergo an oxidation reaction at a high temperature, and at this time, no oxidized substance will be deposited on the output window. If a small amount of oxygen exists in the protective enclosure 120, after the electron beam is irradiated into the first target body 112, the first target body 112 can generate an oxidation reaction with the oxygen at a high temperature to generate a small amount of oxidized substances. Because the amount of the oxidizing substance is small, the oxidizing substance is not sputtered on the output window of the accelerating tube, and even if the oxidizing substance is sputtered, the inner wall of the protective shell 120 can block the oxidizing substance to prevent the oxidizing substance from being deposited on the output window.

That is to say, the radiotherapy target structure 100 of the present invention employs the protective casing 120 having a closed cavity to wrap the target assembly 110, and after the electron beam is incident on the first target body 112, the first target body 112 does not undergo an oxidation reaction or generates a small amount of oxidation substances at a high temperature, and the oxidation substances of the target assembly 110 can be prevented from being deposited on the output window by the protective function of the protective casing 120, so as to ensure the safety during use.

If the first target body 112 is protected by the protective housing 120, the temperature of the first target body 112 is several hundred degrees after the beam is input into the first target body 112, and under this temperature condition, the first target body 112 and the oxygen in the air undergo an oxidation reaction, i.e., the first target body 112 is oxidized. After the protective housing 120 is adopted, the first target body 112, the support member 111 and other components are located in the sealed cavity a, so that the first target body 112 and the support member 111 are in a low-oxygen or even oxygen-free environment to prevent oxidation of the components. Moreover, when the first target body 112 is located in the protective housing 120, the possibility of oxidation can be reduced, so that the dose rate/treatment beam of the first target body 112 is high, and the treatment effect is ensured.

The radiotherapy target structure 100 of the embodiment, the inside of the protective housing 120 forms the airtight chamber, the existence of oxygen is reduced, after the outside of the target assembly 110 is wrapped by the protective housing 120, the target assembly 110 can be in the airtight environment, the reaction between the oxygen and the first target body 112 at high temperature can be reduced, the problem of the current target substance oxidized deposition at the output window is effectively solved, the accelerating tube is not affected, the service performance is ensured, the output window of the accelerating tube is not required to be replaced, and the cost is reduced.

Referring to fig. 1 to 3, in an embodiment, the protective housing 120 has a first window 121 and a second window 122 disposed opposite to each other, the first window 121 is disposed on a first surface 123, the second window 122 is disposed on a second surface 124, and the first window 121 and the second window 122 are located on two sides of the first target body 112 along the beam direction for passing through the beam.

The first target body 112 has two surfaces along the beam direction, a first window 121 is disposed on the first surface 123 and corresponding to one surface of the first target body 112, and a second window 122 is disposed on the second surface 124 and located on the other surface of the first target body 112. Also, the first window 121 can be used for beam input, and the second window 122 can be used for X-ray emission. Specifically, after the beam generated by the electron generating device is accelerated by the acceleration tube, the accelerated beam enters the first target body 112 through the first window 121, and is converted into X-rays by the first target body 112, and then exits from the second window 122.

Alternatively, a first mounting hole (not shown) is formed through the first surface 123 of the protective housing 120, a second mounting hole (not shown) is formed through the second surface 124 of the protective housing 120, the first window 121 is sealingly mounted in the first mounting hole, and the second window 122 is sealingly mounted in the second mounting hole.

Alternatively, the first window 121 is fixed in the first mounting hole by welding. Of course, the first window 121 may be fixed in the first mounting hole by a sealing method such as a sealant. Alternatively, the second window 122 is fixed in the second mounting hole by welding. Of course, the second window 122 may be fixed in the second mounting hole by sealing means such as sealant.

Optionally, the first window 121 is made of beryllium or other material through which the beam can pass. Optionally, second window 122 is made of beryllium, stainless steel, titanium, copper, or other material capable of passing X-rays.

Alternatively, the first window 121 is disposed coaxially with the second window 122. This ensures that the beam after being converted into X-rays can exit through the second window 122. Of course, in other embodiments of the present invention, the axis of the first window 121 and the axis of the second window 122 may also be arranged in parallel, and the first window 121 and the second window 122 at least partially correspond in the beam direction. This ensures that the beam after being converted into X-rays can exit through the second window 122.

In one embodiment, the material of the first window 121 and the second window 122 is the same as or different from the material of the rest of the protective housing 120. That is, it may be that the material of the first window 121 is the same as the material of the rest of the protective housing 120; it may be that the material of the first window 121 is different from the material of the rest of the protective housing 120; it may be that the material of the second window 122 is the same as the material of the rest of the shield casing 120; it may be that the material of the second window 122 is different from the material of the rest of the shield case 120.

When the first and

second windows

121 and 122 are the same material as the rest of the shield case 120, the entire shield case 120 is made of a material through which the radiation passes. That is, the entire protective housing 120 is transparent to radiation. In actual use, the output window of the acceleration tube is directly aligned with the first target body 112. Such that the beam passes through the shield shell 120 and is accurately projected into the first target body 112.

Referring to fig. 1 to 6, in an embodiment, the radiotherapy target structure 100 further includes a cooling assembly 130, and the cooling assembly 130 passes through the protective housing 120 and is disposed on the support 111 for cooling the first target body 112. The joint of the protective casing 120 and the cooling assembly 130 is hermetically arranged, so that the inner wall of the protective casing 120 forms the sealed cavity a.

The cooling assembly 130 is partially located inside the protective housing 120 and partially located outside the protective housing 120. The part of the cooling assembly 130 outside the protective casing 120 can be connected to an external cold source, and the external cold source supplies cooling liquid to the cooling assembly 130. A portion of the cooling assembly 130 in the shield case 120 is disposed on the supporter 111 and is disposed corresponding to the first target body 112, and the first target body 112 is cooled by the cooling liquid in the cooling assembly 130. The cooled cooling liquid can be discharged to an external cold source through the cooling assembly 130, so that the cyclic utilization of the cooling liquid is realized; of course, the cooling fluid may also be exhausted directly through the cooling assembly 130 to the external environment. Alternatively, the cooling fluid is water or other medium capable of achieving cooling, such as liquid helium or the like.

Furthermore, the junction of the cooling assembly 130 and the protective housing 120 is hermetically sealed. This enables the interior of the protective housing 120 to form a sealed cavity a, which prevents air from entering the protective housing 120. Optionally, the joint of the cooling assembly 130 and the protective housing 120 is provided by welding, sealant or other sealing components to ensure the sealing property.

Optionally, the cooling assembly 130 supports the support 111 in the protective housing 120. That is, the support 111 is not in contact with the inner wall of the protective housing 120, and the cooling assembly 130 can connect the protective housing 120 and the support 111, respectively, such that the support 111 is suspended in the protective housing 120. Of course, in other embodiments of the present invention, after the cooling assembly 130 supports the support 111, at least one surface of the support 111 is in contact with or connected to the protective housing 120.

Referring to fig. 2, 9 and 12, optionally, the support 111 has a cooling channel 11112 therein, and a portion of the cooling assembly 130 within the shield shell 120 is located in the cooling channel 11112 to cool the first target body 112. Alternatively, the cooling passage 11112 communicates with the position where the first target body 112 is located, or a part of the cooling passage 11112 is surrounded on the circumferential side of the first target body 112 or the first backing plate 1112. The cooling passage 11112 has an inlet and an outlet, and the cooling module 130 is connected to the inlet and the outlet, respectively.

Optionally, the cooling assembly 130 includes a cooling inlet pipe 131 and a cooling outlet pipe 132, and the cooling inlet pipe 131 and the cooling outlet pipe 132 are respectively disposed in the cooling channel 11112. One end of the cooling inlet pipe 131 is connected with an output end of an external cold source, one end of the cooling outlet pipe 132 is connected with an input end of the external cold source, the other end of the cooling inlet pipe 131 is arranged at an inlet of the cooling channel 11112 and is communicated with the cooling channel 11112, and the other end of the cooling outlet pipe 132 is arranged at an outlet of the cooling channel 11112 and is communicated with the cooling channel 11112.

The output end of the external cold source delivers the cooling fluid into the cooling inlet pipe 131, and then into the cooling channel 11112 through the cooling inlet pipe 131. The cooling liquid in the cooling channel 11112 cools the first target body 112, and then the cooling liquid absorbing heat enters the cooling outlet pipe 132 through the cooling channel 11112 and is conveyed to the external cold source through the input end through the cooling outlet pipe 132. The cooling liquid is cooled by an external cold source, so that the cyclic utilization of the cooling liquid is realized.

Of course, in other embodiments of the present invention, the cooling assembly 130 includes a cooling tube having an inlet end and an outlet end, the cooling tube is disposed in the cooling channel 11112 and located at the periphery of the first target body 112 or the first target holder 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.

It should be noted that the cooling tube and the cooling inlet tube 131 and the cooling outlet tube 132 in the above embodiments are different only in structural arrangement, and the principle of cooling the first target body 112 is substantially the same, which is not repeated herein.

In one embodiment, the protective housing 120 is provided with a vent (not shown) that is connected to an external vacuum pump. The vacuum pump can evacuate the interior of the protective housing 120 through the vent hole, so that the interior of the protective housing 120 is kept in a vacuum state. Thus, during actual use, the interior of the protective casing 120 is in a vacuum environment, so that the first target body 112 is in an oxygen-free working state, oxidation reaction cannot occur at a high temperature, and usability is ensured.

Optionally, the protective housing 120, the target assembly 110 and the cooling assembly 130 may be welded or otherwise sealed under a vacuum environment (e.g., a vacuum furnace), so that the sealed cavity inside the protective housing 120 is a vacuum environment. That is, the protective casing 120 is not provided with a vent hole, and the radiotherapy target structure 100 is directly mounted by means of vacuum assembly.

Of course, in other embodiments of the present invention, the protective housing 120 may be connected to an inert gas source or the like through a vent. After the vent hole is connected with the inert gas source, the inert gas source can introduce inert gas into the protective shell 120 through the vent hole so that the interior of the protective shell 120 is filled with the inert gas, thus the first target body 112 can be in an oxygen-free working state, oxidation reaction can not occur at a high temperature state, and the use performance is ensured.

Referring to fig. 1 to 6, in an embodiment, the support 111 includes a target substrate 1111 and a first target holder 1112, the target substrate 1111 has a first through hole 11111 (as shown in fig. 9) extending along the beam direction, the first target holder 1112 is installed in the first through hole 11111, and the first target holder 1112 is used for installing the first target body 112. The target substrate 1111 is a carrier plate of the support 111 for carrying components of the target assembly 110, and the first backing plate 1112 also plays a role of carrying for mounting the first target body 112.

Alternatively, at least one surface of the target substrate 1111 is fixedly disposed in the shield case 120, and a certain space exists between the remaining surface of the target substrate 1111 and the inner wall of the shield case 120. This enables the target substrate 1111 to be securely fixed in the shield case 120, avoiding the play of the target assembly 110. Alternatively, the target substrate 1111 is supported by a metal material. Since the target substrate 1111 is located in the sealed cavity, it is possible to prevent the target substrate 1111 from being oxidized.

The target substrate 1111 has a first through hole 11111 formed therethrough, and the first backing plate 1112 and the first target body 112 mounted thereon are mounted in the first through hole 11111. In operation, after passing through the first window 121, the beam enters the first target body 112, and after the beam is converted into X-rays by the first target body 112, the X-rays exit through the second window 122. The target substrate 1111 is fixed behind the shield casing 120, so that the first target body 112 is in the sealed environment of the shield casing 120, which can reduce the oxidation of the substance generated by the first target body 112 and ensure the usability.

In one embodiment, first backing plate 1112 is removably attached to target substrate 1111. This facilitates replacement of first backing plate 1112 and first target body 112 thereon, and facilitates ease of use. Alternatively, the first target holder 1112 and the target substrate 1111 are fixed by welding or the like, and when replacement is required, the welded object is removed. In other embodiments of the present invention, the first backing plate 1112 and the target substrate 1111 may be detachably connected by other methods.

In one embodiment, first backing plate 1112 is integral with target substrate 1111. That is, first backing plate 1112 and target substrate 1111 are not detachable, for example, first backing plate 1112 and target substrate 1111 may be formed by integral molding. When the first target body 112 is replaced, the first target body 112 can be directly detached from the first backing plate 1112.

Referring to fig. 1 to 6, in an embodiment, a surface of the first backing plate 1112 facing the first window 121 is provided with a mounting groove 11121, and the first target body 112 is disposed in the mounting groove 11121. First backing plate 1112 is load bearing for bearing first target body 112. The first target body 112 can be reliably installed through the installation groove 11121, the position of the first target body 112 is prevented from moving, and the beam can be accurately shot into the first target body 112.

It is to be understood that the depth of the mounting groove 11121 is not limited in principle as long as the mounting of the first target body 112 can be achieved. Optionally, the depth of the mounting 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 mounting groove 11121 may be less than or equal to the height of the first target body 112. Optionally, the first backing plate 1112 is fixed to the first through hole 11111 of the target substrate 1111 by welding to ensure reliable fixing. Meanwhile, the welding mode does not affect the first target body 112, and the first target body 112 can convert the beam into the X-ray. Of course, in other embodiments of the present invention, the first target body 112 can also be directly fixed on the end of the first backing plate 1112 facing the first window 121.

Referring to fig. 2 and 3, in an embodiment, the support 111 further includes a backing plate 1113, the backing plate 1113 is disposed on the first backing plate 1112, and the backing plate 1113 is configured to mount the first target body 112. Specifically, the target holder 1113 is disposed at an end portion of the first target holder 1112 facing the first window 121, and further, the target holder 1113 may be disposed in the mounting groove 11121, and the first target body 112 is carried by the target holder 1113, thereby ensuring that the first target body 112 is reliably fixed in the mounting groove 11121. In addition, when the first target body 112 needs to be replaced, the target holder 1113 may be removed, which facilitates replacement of the first target body 112.

Referring to fig. 2 and 3, in one embodiment, a surface of the first backing plate 1112 facing away from the first target body 112 defines a recess 11122, and the recess 11122 is disposed corresponding to the first target body 112 for passing radiation therethrough. That is, a recess 11122 is formed in the end surface of the first backing plate 1112 facing the second window 122. The first target body 112 is fitted through the recess 11122, ensuring the usability of the first target body 112. Optionally, the recess 11122 is frustoconical. Of course, in other embodiments of the present invention, the recess 11122 may also have a cylindrical shape, a trapezoidal cross-section, and the like. Alternatively, the recess 11122 is provided coaxially with the mounting groove 11121.

Alternatively, the cross-sectional area of the first window 121 is smaller than that of the second window 122. That is, the cross-sectional area of the first window 121 is small and the cross-sectional area of the second window 122 is large. When the beam enters the first target body 112, the beam is converted into X-rays by the first target body 112, and since the X-rays are divergent, the cross-sectional area of the first window 121 is large, so that the X-rays can be ensured to be accurately emitted through the second window 122, and blocking of the rays is avoided.

As shown in fig. 1 to 3 and 9, in an embodiment of the present invention, a predetermined space is formed between an outer wall of the first backing plate 1112 and an inner wall of the first through hole 11111, and the predetermined space is passed by the cooling assembly 130 for cooling the first target body 112. The predetermined space can facilitate the cooling assembly 130 to effectively cool the first target body 112. It can be understood that the cooling assembly 130 may be directly located in the preset space, or the cooling liquid may be introduced into the preset space, so that the layout of the cooling assembly 130 corresponding to the cooling manner has been described in detail at the specific structure of the cooling assembly 130, and is not described herein again.

Specifically, taking the example that the cooling assembly 130 delivers the cooling liquid into the predetermined space as an example, after the cooling channel 11112 of the target substrate 1111 is communicated with the first through hole 11111, the cooling assembly 130 can position the cooling liquid in the first through hole 11111, and the first target holder 1112 is cooled in the first through hole 11111 by the cooling liquid, so as to cool the first target body 112, reduce the temperature of the first target body 112, and ensure the usability of the first target body 112.

Referring to fig. 1 to 3, in an embodiment of the utility model, the first through hole 11111 includes a first stepped hole and a second stepped hole coaxially disposed, and a diameter of the first stepped hole is larger than a diameter of the second stepped hole, after the first backing plate 1112 is installed in the first through hole 11111, an inner wall of the first backing plate 1112 abuts against an inner wall of the second stepped hole and encloses a predetermined space with the inner wall of the first stepped hole.

The diameter of second step hole and the diameter looks adaptation of first target holder 1112, first target holder 1112 install in first through-hole 11111 back, and the outer wall of first target holder 1112 combines together with the inner wall in second step hole, guarantees the leakproofness, avoids the pencil to pass through. Meanwhile, an annular predetermined space for installing the cooling assembly 130 is formed between the outer wall of the first backing plate 1112 and the inner wall of the first stepped hole. Moreover, the preset space is closer to the first target body 112 along the beam direction and closer to the first target body 112, so that the cooling assembly 130 can better cool the first target body 112, and the heat dissipation of the first target body 112 is ensured.

Of course, in other embodiments of the present invention, the first through hole 11111 is a cylindrical hole, and a clearance groove is formed on an inner wall of the first through hole 11111, and the clearance groove is recessed along a radial direction of the first through hole 11111 to form a predetermined space for installing the cooling module 130. In another embodiment of the present invention, the first backing plate 1112 is disposed in a step shape, and the outer wall of the first backing plate 1112 and the inner wall of the first through hole 11111 enclose a predetermined space; of course, the first backing plate 1112 and the first through hole 11111 may be stepped and cooperate to form a predetermined space.

Referring to fig. 4 to 9, in another embodiment of the present invention, the outer wall of the first backing plate 1112 is formed with a cooling groove 11123, the cooling groove 11123 is communicated with the mounting groove 11121, and the cooling groove 11123 is used for the cooling assembly 130 to pass through to cool the first target body 112. That is, the outer wall of the first backing plate 1112 is opened with a cooling groove 11123, and one end of the cooling groove 11123 is communicated with the mounting groove 11121 and the other end is communicated with the cooling passage 11112. The cooling assembly 130 cools the first target body 112 in the mounting groove 11121 through the cooling groove 11123, ensuring that the first target body 112 can work normally.

Referring to fig. 1 to 3, in an embodiment, first backing plate 1112 has a fixing edge 11124, fixing edge 11124 is protruded along a radial direction of first through hole 11111 to make first backing plate 1112 have a step shape, and first through hole 11111 further includes a fixing groove formed at an edge of backing plate 1111 for receiving fixing edge 11124. Retaining edge 11124 protrudes radially beyond the outer wall of first backing plate 1112, i.e., retaining edge 11124 forms a step structure with the main body portion of first backing plate 1112. When installed, the securing edge 11124 fits behind the securing groove and the first backing plate 1112 is positioned within the first aperture 11111. Through the cooperation of fixed limit 11124 with the fixed slot spacing, can avoid first target holder 1112 slippage from first through-hole 11111, be convenient for first target holder 1112's installation fixed.

Referring to fig. 1 to 6, in an embodiment, the support 111 further includes a second backing plate 1114, the target assembly 110 further includes a second target body 113, the target substrate 1111 has a second through hole (not shown) in the beam direction, the second backing plate 1114 is disposed in the second through hole for mounting the second target body 113; the second backing plate 1114 is located inside or outside the protective housing 120. The second target body 113 is structurally different from the first target body 112, and has a certain difference in function. The second target body 113 is used to increase the range of use of the radiotherapy target structure 100. When it is desired to use the first target body 112, the beam passes through the first target body 112; when it is desired to use the second target body 113, the beam passes through the second target body 113.

Referring to fig. 1-3, optionally, the second target body 113 is located inside the protective enclosure 120. That is, the second target body 113 is also in the sealed volume a within the protective enclosure 120. At this time, a window is provided on the shield case 120 at a position corresponding to the second target body 113 to facilitate the beam to pass through. When the second target body 113 is positioned in the shield shell 120, the second target body 113 can be prevented from being oxidized. Of course, in other embodiments of the present invention, the second target body 113 is located outside the protective shell 120, which facilitates replacement and installation of the second target body 113, for example, see fig. 4-6.

It should be noted that, when two targets are disposed on the target substrate 1111, they are respectively the first target body 112 and the second target body 113, wherein the first target body 112 is a therapeutic target, and the second target body 113 is an imaging target. The X-ray of the beam transformed by the first target body 112 can realize the treatment of the lesion site of the patient, and the X-ray of the beam transformed by the second target body 113 can image the lesion site of the patient.

The first target body 112 is a high energy target, such as a tungsten target. After the beam is injected into the tungsten target, a large amount of heat is generated to raise the temperature of the tungsten target, and the reaction between tungsten and oxygen is accelerated at high temperature, so that the first target body 112 is placed in the protective shell 120, thereby ensuring the usability of the first target body 112 and reducing the oxidation reaction of the first target body 112.

The second target body 113 is a low power, low energy target, typically a copper target, an aluminum target, a graphite target, etc., and the second target body 113 is also subject to oxidation at high temperatures, but since the second target body 113 is an imaging target, the dose rate is low when imaging, and thus the degree of oxidation is within an acceptable range. That is, when the second target body 113 is oxidized at a high temperature, less oxidized substances are generated, and are not deposited on the output window, thereby not affecting the usability of the output window. Of course, in other embodiments of the present invention, the second target body 113 may also be a therapeutic target.

Alternatively, the second backing plate 1114 is secured to the target substrate 1111 by welding, interference fit, snap fit, or the like. Of course, in other embodiments of the present invention, the second target holder 1114 and the target substrate 1111 may be of a unitary structure.

Referring to fig. 10-12, at least a portion of second backing plate 1114 is sealingly connected to shield shell 120 such that second target body 113 is outside sealed volume a. Thus, the second target body 113 can be positioned outside the shield shell 120, facilitating replacement of the second target body 113 while avoiding oxidation of the first target body 112.

Referring to fig. 10 to 12, in an embodiment, the support 111 further includes a hollow second backing plate 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 face 123 has a first hole, the second face 124 has a second hole, the first hole and the second hole are located at two sides of the second through hole along the beam direction and are coaxially arranged, the second backing plate 1114 is installed in the first hole and the second hole in a sealing manner and is in contact connection with the second through hole, and the second backing plate 1114 is used for installing the second target body 113.

That is, in the present embodiment, although the target substrate 1111 on which the second target body 113 is located between the first surface 123 and the second surface 124 of the shield case 120, the second target body 113 can be exposed outside the shield case 120 by the isolation of the second target holder 1114, so as to facilitate the replacement of the second target body 113.

Specifically, the second backing plate 1114 is hollow, and the second target body 113 is mounted inside the second backing plate 1114. Moreover, the first face 123 of the protective housing 120 is provided with a first hole, the second face 124 is provided with a second hole, the target substrate 1111 has a second through hole, the axes of the first hole, the second through hole and the second hole coincide, and the first hole and the second hole are respectively located at two sides of the second through hole, at this time, the first hole, the second through hole and the second hole are correspondingly arranged along the beam direction, so that the second target base 1114 is mounted.

Second backing plate 1114 is mounted in the first hole and the second hole in a sealed manner, i.e., the outer wall of second backing plate 1114 is capable of sealing contact with the inner wall of the first hole and the inner wall of the second hole. That is to say, after the second target holder 1114 is installed on the protective casing 120 and the target substrate 1111, the protective casing 120 can be enclosed with the second target holder 1114 to form a sealed cavity a, the second target body 113 is located in the second target holder 1114, and the protective casing 120 is exposed, and can be in contact with the outside air.

Through this kind of mode setting, isolated external air enters into protective housing 120 on the one hand, reduces the condition emergence that first target body 112 took place the oxidation, and on the other hand, the change of second target body 113 of can being convenient for improves and changes efficiency. Moreover, second target holder 1114 is connected with target substrate 1111 in a contacting manner, so that the heat transfer effect can be ensured, and second target holder 1114 and second target body 113 are cooled by cooling assembly 130.

Optionally, the protective housing 120 further includes a window disposed at two ends of the second target holder 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 may also be directly exposed to the outside of the protective housing 120.

Optionally, the second backing plate 1114 has a placement groove, and the second target body 113 is disposed in the placement groove. Optionally, second backing plate 1114 is cylindrically configured and is shaped to fit into the second through-hole. Of course, in other embodiments of the present invention, the second backing plate 1114 may also be tapered. In one embodiment, the support 111 further includes a third backing plate (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 backing plate is disposed in the third through hole for mounting the third target body; the third backing plate is located inside or outside the protective housing 120. The third target body is different from the second target body 113 and the first target body 112 in structure, and has a certain difference in function. The second target body 113 and the third target body are provided on the target substrate 1111, so that the range of use of the radiotherapy target structure 100 can be increased. When it is desired to use the first target body 112, the beam passes through the first target body 112; when it is desired to use the second target body 113, the radiation passes through the first target body 112; when it is desired to use the third target body, the radiation passes through the third target body.

Optionally, a third target body is located inside the protective enclosure 120. That is, the third target body is also in the sealed volume a within the protective enclosure 120. At this time, a window is provided on the shield case 120 at a position corresponding to the third target body so that the beam passes through. When the third target body is positioned in the shield shell 120, the third target body can be prevented from being oxidized. Of course, in other embodiments of the present invention, the third target body is located outside the protective housing 120, which facilitates the replacement and installation of the third target body.

It should be noted that, when three targets are disposed on the target substrate 1111, they are respectively a first target body 112, a second target body 113 and a third target body, wherein the first target body 112 is a therapeutic target, the second target body 113 is an imaging target, the third target body is a therapeutic 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-ray of the beam converted by the first target body 112 can realize the treatment of the lesion position of the patient, the X-ray of the beam converted by the second target body 113 can image the lesion position of the patient, and the X-ray of the beam converted by the third target body can treat the lesion position of the patient.

Of course, in other embodiments of the present invention, the second target body 113 and the third target body may be both the therapeutic target or both the imaging target, or the second target body 113 is the therapeutic target and the third target body is the imaging target. In the present invention, the second target body 113 is taken as an imaging target, and the third target body is taken as a therapeutic target.

The first target body 112 is a high energy target, specifically a tungsten target. After the beam is injected into the tungsten target, a large amount of heat is generated to raise the temperature of the tungsten target, and the reaction between tungsten and oxygen is accelerated at high temperature, so that the first target body 112 is disposed in the protective housing 120, thereby ensuring the usability of the first target body 112 and preventing the first target body 112 from oxidation reaction.

The second target body 113 is a low power, low energy target, typically a copper target, an aluminum target, a graphite target, etc., and the second target body 113 is also subject to oxidation at high temperatures, but since the second target body 113 is an imaging target, the dose rate is low when imaging, and thus the degree of oxidation is within an acceptable range. That is, when the second target body 113 is oxidized at a high temperature, less oxidized substances are generated, and are not deposited on the output window, thereby not affecting the usability of the output window.

The third target body is a low power, low energy target, typically a copper target, an aluminum target, a graphite target, etc., and the third target body also undergoes an oxidation reaction at high temperatures, but since the third target body is a therapeutic target, the dose rate is low during therapy, and thus the degree of oxidation is within an acceptable range. Namely, when the third target body is subjected to oxidation reaction at high temperature, less oxidation substances are generated, and the third target body cannot be deposited on the output window and cannot influence the service performance of the output window.

Optionally, the third target holder is provided with an accommodating groove, and the third target body is arranged in the accommodating groove. Optionally, the third backing plate is cylindrically configured and is adapted to the shape of the third through hole. Alternatively, the third backing plate is fixed to the target substrate 1111 by soldering or the like. Of course, in other embodiments of the present invention, the third backing plate and the target substrate 1111 may be an integral structure.

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

The radiotherapy apparatus of the present invention reduces the contact of the first target body 112 with oxygen by disposing the high-energy first target body 112 in the protective enclosure 120, which is a sealed chamber a. When the beam passes through the first target body 112, the first target body 112 generates a large amount of heat, and since the sealed cavity a is located in the protective housing 120, the oxidized substance of the first target body 112 is not deposited on the output window of the electron generating apparatus, and the output window does not need to be replaced, thereby reducing the use cost.

The present invention also provides a radiotherapy apparatus, which comprises an electron generating device, an accelerating tube and the radiotherapy target structure 100 in the above embodiment, wherein the electron generating device is used for generating an electron beam, the accelerating tube is used for accelerating the electron beam, and the radiotherapy target structure 100 is used for converting the accelerated electron beam into X-rays to be emitted. After the radiotherapy target structure 100 of the above embodiment is adopted, the first target body 112 is prevented from being oxidized while the use performance is ensured, and further, the oxidized substance of the first target body 112 is prevented from being deposited on the output window, so that the use performance is ensured.

The technical features of the embodiments described above may be arbitrarily combined, and for the sake of brevity, all possible combinations of the technical features in the embodiments described above are not described, but should be considered as being within the scope of the present specification as long as there is no contradiction between the combinations of the technical features.

The above-mentioned embodiments only express several embodiments of the present invention, and the description thereof is more specific and detailed, but not construed as limiting the scope of the utility model. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the inventive concept, which falls within the scope of the present invention. Therefore, the protection scope of the present patent shall be subject to the appended claims.

Claims

1. A radiotherapy target structure, comprising:

2. The radiotherapy target structure of claim 1, wherein the protective housing further comprises a first window and a second window oppositely disposed, the first window is disposed on the first surface, the second window is disposed on the second surface, and the first window and the second window are located on two sides of the first target body for the beam to pass through.

3. The radiotherapy target structure of claim 1, further comprising a cooling assembly passing through the protective enclosure and disposed to the support for cooling the first target body;

4. Radiotherapy target structure according to claim 3, characterized in that the support comprises a target base plate with a first through hole extending in the beam direction and a first backing plate mounted in the first through hole for mounting the first target body.

5. The radiotherapy target structure of claim 4, wherein the surface of the first target holder facing the first face has a mounting groove for mounting the first target body;

6. Radiotherapy target structure according to claim 4, characterized in that between the outer wall of the first target holder and the inner wall of the first through hole there is a pre-set space for the cooling assembly to pass through for cooling the first target body.

7. The radiotherapy target structure of claim 6, wherein the first through hole comprises a first stepped hole and a second stepped hole coaxially arranged, the diameter of the first stepped hole is larger than that of the second stepped hole, the first target holder is mounted on the first through hole, and the inner wall of the first target holder 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. Radiotherapy target structure according to claim 4, characterized in that said support further comprises a second backing plate, said target assembly further comprises a second target body, said target base plate having a second through hole extending in the beam direction, said second backing plate being arranged in said second through hole for mounting said second target body.

9. The radiotherapy target structure of claim 8, wherein at least a portion of the second target holder is sealingly connected with the protective enclosure such that the second target body is located outside the sealed volume.

10. A radiotherapy apparatus comprising electron generating means for generating an electron beam, an accelerating tube for accelerating the electron beam, and a radiotherapy target structure according to any one of claims 1 to 9 for converting the accelerated electron beam into X-rays for emission.