X-ray tube and medical equipment

Abstract

The utility model belongs to the field of medical equipment, and particularly relates to an X-ray tube and medical equipment. The cathode assembly comprises an electron emission end, and at least the electron emission end of the cathode assembly is accommodated in the vacuum container; the anode assembly comprises an anode bar and a target material, the circumferential surface of the anode bar is provided with an annular belt area used for being connected with the vacuum container, and the annular belt area divides the anode bar into a first part and a second part; the projection of the second part on the first plane and the projection of the vacuum container on the first plane are not overlapped, and the first plane is any plane passing through the axis of the anode bar. According to the utility model, a flanging structure at the end part of the vacuum container is cancelled, so that a semi-closed cavity between the vacuum container and the fixed anode is eliminated, the second part of the anode bar is exposed outside the vacuum container, the anode bar can be in full contact with a cooling medium, and the heat conduction and heat dissipation efficiency is improved.

Description

Technical Field

[0001] The utility model belongs to the field of medical equipment, and in particular relates to an X-ray tube and medical equipment. Background Art

[0002] When an X-ray tube is operating, 99% of the energy it generates is converted into heat. Whether this heat can be conducted away promptly is a crucial factor limiting the continuous power of fixed-anode X-ray tubes. In practical applications, excessive anode temperatures often lead to cracking or melting of the target surface, sparking within the tube, and cracking of the insulating oil, all of which seriously impact product stability and service life. Utility Model Content

[0003] In view of the above-mentioned shortcomings of the prior art, the purpose of the present invention is to provide an X-ray tube and medical equipment that can improve heat dissipation performance.

[0004] To achieve the above-mentioned and other related purposes, the present invention provides an X-ray tube, comprising:

[0005] Vacuum container;

[0006] a cathode assembly, the cathode assembly comprising an electron emitting end, at least the electron emitting end of the cathode assembly being accommodated in the vacuum container;

[0007] An anode assembly comprising an anode rod and a target material. The anode rod is provided with an annular zone on its circumference for connecting to the vacuum container. The annular zone separates the anode rod into a first portion and a second portion. The vacuum container is sealed to the annular zone so that the first portion is accommodated within the vacuum container and the second portion is exposed outside the vacuum container. The target material is disposed in the first portion and is disposed opposite the electron emitting end.

[0008] A projection of the second portion on a first plane has no overlapping area with a projection of the vacuum container on the first plane, and the first plane is any plane passing through the axis of the anode rod.

[0009] In an optional embodiment of the present invention, the vacuum container includes a body made of a first material and an adapter ring made of a second material, one end of the adapter ring is connected to the body, and the other end is connected to the annular zone.

[0010] In an optional embodiment of the present invention, the first material is glass, and the second material is Kovar alloy.

[0011] In an optional embodiment of the present invention, the diameter of the main body is larger than the diameter of the anode rod, and the adapter ring includes a first mating portion for connecting the annular zone, a second mating portion for connecting the main body, and a connecting portion between the first mating portion and the second mating portion.

[0012] In an optional embodiment of the present invention, the connecting portion includes a conical structure whose diameter gradually increases from the annular zone toward the side where the first portion is located.

[0013] In an optional embodiment of the present invention, the first matching portion includes a straight cylinder parallel to the axial direction of the anode rod.

[0014] In an optional embodiment of the present invention, the first matching portion includes a cone that is flush with the connecting portion; and the annular zone is a conical surface that is adapted to the inner wall of the cone.

[0015] In an optional embodiment of the present invention, a flange is provided on a side of the annular zone away from the first portion, and the flange abuts against an end surface of the first matching portion.

[0016] In an optional embodiment of the present invention, a heat sink is provided on an end of the second part away from the first part.

[0017] To achieve the above-mentioned purpose and other related purposes, the present invention also provides a medical device including the aforementioned X-ray tube.

[0018] The technical effects of this utility model are as follows: By eliminating the flange structure at the end of the vacuum vessel, the semi-enclosed cavity between the vacuum vessel and the fixed anode is eliminated, allowing the second portion of the anode rod to be exposed outside the vacuum vessel, allowing the anode rod to fully contact the cooling medium, thereby improving heat conduction and heat dissipation efficiency. Compared with the high-temperature zone caused by the semi-enclosed cavity in traditional fixed-anode X-ray tubes, the new design significantly improves heat dissipation performance, reduces the problem of insulating oil cracking caused by high temperature, and thus extends the service life of the X-ray tube. The second portion does not overlap with the projection of the vacuum vessel in any direction perpendicular to the anode rod axis, which means that the exposed portion of the anode rod can directly contact the surrounding high-flow cooling medium, further improving the heat dissipation effect. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] Figure 1 is a cross-sectional view of an X-ray tube provided by the first embodiment of the present utility model;

[0020] Figure 2 This is a partial cross-sectional view of an X-ray tube provided by the first embodiment of the present utility model;

[0021] Figure 3is a cross-sectional view of an X-ray tube provided by a second embodiment of the present utility model;

[0022] Figure 4 is a partial cross-sectional view of an X-ray tube provided by a second embodiment of the present utility model;

[0023] Figure 5 is a schematic diagram of a simulation of the temperature of the cooling medium around the X-ray tube provided in the comparative embodiment;

[0024] Figure 6 This is a schematic diagram of the simulation of the temperature of the cooling medium around the X-ray tube provided by the embodiment of the present utility model. DETAILED DESCRIPTION

[0025] The following describes the embodiments of the present invention through specific examples. Those skilled in the art will readily understand the other advantages and benefits of the present invention from the disclosure herein. The present invention may also be implemented or applied through various other specific embodiments, and the details in this specification may be modified or altered based on different perspectives and applications without departing from the spirit of the present invention. It should be noted that the following embodiments and features within these embodiments may be combined with one another, unless they conflict.

[0026] It should be noted that the illustrations provided in the following embodiments are merely schematic illustrations of the basic concept of the present invention. Therefore, the illustrations only show components related to the present invention and are not drawn according to the number, shape, and size of components in actual implementation. In actual implementation, the type, quantity, and proportion of each component may be changed at will, and the component layout may also be more complex.

[0027] An X-ray tube is one of the core components of medical or industrial equipment such as X-ray machines and CT (computed tomography) equipment. Its main structure includes an anode, a cathode, and a vacuum container. The main part of the anode is the target material, such as a tungsten target, which can absorb high-speed electrons and convert their energy into X-rays. The cathode mainly includes a filament and a focusing coil. The filament can be, for example, a tungsten filament. When powered, the tungsten filament will heat up and release electrons. The focusing coil is used to focus the electron beam onto a small area of ​​the anode target. The vacuum container can be, for example, a glass or ceramic shell. The anode and cathode are sealed in the vacuum container, which can prevent electrons from colliding with air molecules before hitting the anode target. When power is supplied to the cathode filament, it heats up and emits electrons. These electrons are accelerated and form a concentrated electron beam through a focusing coil. The electron beam is accelerated from the cathode to the anode by a high-voltage electric field. When the high-speed electrons hit the tungsten target at the anode, most of the energy is converted into heat and a small part is converted into X-rays. Due to the design of the X-ray tube, only a small part of the specific X-rays can be emitted through the window of the vacuum container. This part of the X-rays is used for medical imaging. The X-rays emitted from the anode target pass through the patient's body. Tissues of different densities absorb X-rays to different degrees, causing the intensity of the X-rays received by the detector to change. This information is sent to a computer for processing to generate a two-dimensional or three-dimensional tomographic image. In this way, the CT X-ray tube can efficiently and accurately generate X-rays for imaging, thereby realizing non-invasive inspection of the internal structure of the human body or industrial products. X-ray tubes are divided into two types: fixed anode and rotating anode. A fixed anode means that the relative position relationship between the anode and the cathode is fixed, and the electron beam bombards the same area of ​​the target material. A rotating anode means that the anode can rotate along its own axis, and the cathode is set eccentrically relative to the anode, so that the bombardment area of ​​the electron beam continuously changes relative to the circumference of the anode.

[0028] Since the X-ray tube generates a lot of heat when it is working, the heat dissipation requirement is high. The common heat dissipation method is to immerse the entire X-ray tube in a cooling medium. However, due to the influence of the assembly process, the end of the vacuum container that matches the anode is generally equipped with an inward-rolled flange, such as Figure 5 As shown, this results in a semi-enclosed cavity between the vacuum vessel and the anode, significantly reducing the fluidity of the cooling medium in this area, resulting in a high-temperature zone near the target disk. Excessively high temperatures in this area can cause the insulating oil to decompose, shortening the product's service life. To address this, the present invention improves the assembly structure between the vacuum vessel and the fixed anode, eliminating the flange structure at the end of the vacuum vessel and, consequently, eliminating the semi-enclosed cavity between the vacuum vessel and the fixed anode. This allows the anode to fully engage with the cooling medium for heat exchange, improving the heat dissipation performance of the X-ray tube.

[0029] See also Figure 1-6As shown, the technical solution of the present invention is described in detail below with reference to specific embodiments:

[0030] See also Figure 1-4 As shown, an X-ray tube provided in an embodiment of the present invention includes a vacuum container 10, a cathode assembly (not shown), and an anode assembly. The X-ray tube can be used in medical equipment, especially CT equipment. The cathode assembly includes an electron emitting end, at least the electron emitting end of the cathode assembly is accommodated in the vacuum container 10. The specific structure and working principle of the cathode assembly can be implemented with reference to the existing technology and will not be repeated here. The anode assembly includes an anode rod 20 and a target material 21. An annular zone 203 for connecting to the vacuum vessel 10 is provided on the circumference of the anode rod 20. The annular zone 203 separates the anode rod 20 into a first portion 201 and a second portion 202. The vacuum vessel 10 is sealedly connected to the annular zone 203 so that the first portion 201 is contained within the vacuum vessel 10 and the second portion 202 is exposed outside the vacuum vessel 10. The target material 21 is disposed in the first portion 201 and is arranged opposite the electron emission end. The projection of the second portion 202 on a first plane does not overlap with the projection of the vacuum vessel 10 on the first plane. The first plane is any plane passing through the axis of the anode rod 20.

[0031] contrast Figure 5 、 6 As shown, the present invention eliminates the flange structure at the end of the vacuum vessel 10, eliminating the semi-enclosed cavity between the vacuum vessel 10 and the fixed anode. This allows the second portion 202 of the anode rod 20 to be exposed outside the vacuum vessel 10, allowing the anode rod 20 to fully contact the cooling medium, thereby improving heat dissipation efficiency. Compared to the high-temperature zone caused by the semi-enclosed cavity in traditional fixed-anode X-ray tubes, the new design significantly improves heat dissipation performance, reduces the problem of insulating oil cracking caused by high temperatures, and thus extends the service life of the X-ray tube. The projection of the second portion 202 on any plane passing through the axis of the anode rod 20 does not overlap with the projection of the vacuum vessel 10 on that plane. This means that the exposed portion of the anode rod 20 can directly contact the surrounding, highly fluid cooling medium, improving heat dissipation.

[0032] See also Figure 1-4As shown, in an optional embodiment of the present application, the vacuum container 10 comprises a body 11 made of a first material, and an adapter ring 12 made of a second material, one end of the adapter ring 12 is connected with the body 11, and the other end is connected with the ring belt area 203. It should be understood that the vacuum container 10 and the anode rod 20 have different physical performance requirements for the material, so they are made of different materials, for example, the anode rod 20 can be made of a metal material with high melting point and high thermal conductivity, and the vacuum container 10 can be made of a material with good mechanical strength, high temperature resistance and air tightness, such as glass, ceramic, quartz and the like, which leads to different thermal expansion coefficients of the vacuum container 10 and the anode rod 20, so that the direct connection of the two will cause internal stress or looseness at the connection position during the working process, and further cause damage to the X-ray tube. Therefore, the adapter ring 12 is arranged between the body 11 of the vacuum container 10 and the anode rod 20, the adapter ring 12 can be made of a material with physical properties between the body 11 and the anode rod 20, to ensure that the adapter ring 12 can be reliably connected with the body 11 and the anode rod 20 at the same time.

[0033] In an optional embodiment of the present invention, the first material is glass, and the second material is Kovar alloy. Glass has excellent thermal stability and can withstand large temperature fluctuations without cracking or deformation, which is crucial for maintaining the structural integrity of the X-ray tube during heating and cooling. Glass can be precisely welded and sealed, ensuring the vacuum vessel 10 is airtight. Glass has good light transmittance, allowing operators to directly observe the heating of the filament and the formation of the electron beam, facilitating commissioning and maintenance. Glass can be precisely machined and complexly formed, making it suitable for manufacturing vacuum vessels 10 of various shapes and sizes. Compared to some metal and ceramic materials, glass is generally less expensive and has a relatively simple processing process, which helps reduce the overall manufacturing cost of the X-ray tube. Glass has excellent chemical resistance and is not easily affected by ionizing radiation and chemicals generated by electron bombardment, thereby extending the service life of the vacuum vessel 10. Glass is an electrically insulating material that effectively isolates the anode and cathode, preventing electrical breakdown and short circuits, thereby improving the safety and reliability of the X-ray tube. Kovar is a nickel-iron alloy whose main components include iron (Fe), nickel (Ni) and cobalt (Co). The thermal expansion coefficient of Kovar is close to that of glass, which means that during heating and cooling, the thermal stress between glass and Kovar is small. This matching helps to ensure the sealing of the seal and reduce cracks or seal failure caused by thermal expansion mismatch. Kovar has good machinability and weldability and can form a highly airtight seal with glass. Kovar has high mechanical strength and hardness and can withstand the stress between the anode rod 20 and the vacuum vessel 10, ensuring the structural stability and durability of the seal. Kovar can maintain its mechanical properties and sealing performance at higher temperatures. Kovar has good corrosion resistance and can resist the effects of ion radiation and chemicals generated by electron bombardment, thereby extending the service life of the X-ray tube. Kovar is easy to process and seal, which simplifies the assembly process between the vacuum vessel 10 and the anode rod 20 and improves production efficiency and product consistency.

[0034] In some other alternative embodiments, glass can be replaced by ceramic, quartz, sapphire and other materials, and Kovar alloy can be replaced by other alloys, such as cobalt-based alloys, stainless steel, titanium alloys, copper-nickel alloys, nickel-based alloys, etc. It should be understood that the material selection of the main body 11 and the adapter ring 12 is not limited to the parts listed above. As long as their physical properties meet the requirements of the X-ray tube, they can be used as materials for making the main body 11 and the adapter ring 12. The specific material can be selected based on factors such as thermal expansion coefficient, mechanical strength, corrosion resistance, processability, weldability, and cost. For example, ensure that the thermal expansion coefficient of the alternative material matches that of the glass or other sealing material to maintain good sealing performance; the alternative material should have sufficient mechanical strength to withstand internal stress and the influence of the external environment; the alternative material should have good corrosion resistance to resist the influence of electron bombardment and other chemicals; the alternative material should be easy to process and weld to simplify the manufacturing process; the cost of the alternative material should meet the economic requirements of the application, etc.

[0035] See also Figure 1-4 As shown, in an optional embodiment of the present invention, the diameter of the main body 11 is larger than the diameter of the anode rod 20, and the adapter ring 12 includes a first mating portion 121 for connecting to the annular zone 203, a second mating portion 122 for connecting to the main body 11, and a connecting portion 123 between the first mating portion 121 and the second mating portion 122. The larger diameter of the main body 11 than the diameter of the anode rod 20 provides greater space and flexibility, facilitating installation and removal. This design also helps reduce environmental impacts on the anode rod 20, such as vibration and impact. The design of the first mating portion 121 and the second mating portion 122 simplifies the assembly process and improves production efficiency.

[0036] See also Figure 1-4As shown, in an optional embodiment of the present invention, the connecting portion 123 includes a conical structure with a diameter that gradually increases from the annular zone 203 toward the side where the first portion 201 is located. The conical design reduces the retention and dead zones of the cooling medium, ensuring that the cooling medium can be more evenly distributed throughout the cooling system. This design helps to avoid the accumulation of cooling medium in certain areas and reduce the formation of hot spots. By using the conical structure, the connecting portion 123 forms a tapered guide surface, which helps guide the cooling medium to flow smoothly toward the second portion 202, improving the fluidity of the cooling medium on the surface of the anode rod 20. The conical structure can generate a turbulent effect during the fluid flow, which helps to mix the cooling medium and transfer heat. The turbulent effect enhances the heat exchange efficiency between the cooling medium and the high-temperature components, ensuring that heat can be removed more quickly and evenly. The cooling medium can more effectively cover the high-temperature components, reducing local hot spots, thereby improving the cooling effect. In some other alternative embodiments, the connecting portion 123 can also be a planar structure perpendicular to the axis of the anode rod 20.

[0037] See also Figure 1 、 2 As shown, in an optional embodiment of the present invention, the first mating portion 121 comprises a straight cylinder parallel to the axis of the anode rod 20. The straight cylinder structure design provides stable support parallel to the axis of the anode rod 20, enhancing the connection stability between the anode rod 20 and the first mating portion 121. This design reduces the risk of loosening or failure of the connection due to torsional or bending forces. The straight cylinder structure simplifies the assembly process of the anode rod 20 and the first mating portion 121. Since the straight cylinder is parallel to the axis of the anode rod 20, assembly only requires insertion along the axis, reducing complex alignment and adjustment steps and improving assembly efficiency. The straight cylinder structure design helps to evenly distribute stress, reducing the risk of fatigue and fracture caused by local stress concentration, and improving the reliability and service life of the system.

[0038] See also Figure 3 、 4 As shown, in another optional embodiment of the present invention, the first mating portion 121 comprises a conical cylinder flush with the connecting portion 123; the annular zone 203 is a conical surface that mates with the inner wall of the conical cylinder. The design of the conical cylinder and conical surface structure optimizes the flow path of the cooling medium. The conical cylinder design forms a tapered guide surface during the flow of the cooling medium, reducing flow resistance and improving the fluidity and uniformity of the cooling medium. The design of the conical cylinder and conical surface structure also helps to evenly distribute heat and reduce local hot spots.

[0039] See also Figure 2 、 4As shown, in an optional embodiment of the present invention, a flange 22 is provided on a side of the annular region 203 away from the first portion 201, and the flange 22 abuts against the end surface of the first mating portion 121. The design of the flange 22 abutting against the end surface helps ensure accurate alignment of the annular region 203 and the first mating portion 121, thereby reducing assembly errors.

[0040] See also Figure 1-4 As shown, in an optional embodiment of the present invention, a heat sink 30 is provided on the end of the second portion 202 away from the first portion 201. The design of the heat sink 30 enhances heat exchange efficiency, allowing the system to more effectively transfer heat to the surrounding environment. The larger heat dissipation area enables heat exchange with more cooling medium, thereby improving overall heat dissipation performance.

[0041] In summary, the present invention eliminates the flange structure at the end of the vacuum vessel 10, eliminating the semi-enclosed cavity between the vacuum vessel 10 and the fixed anode. This allows the second portion 202 of the anode rod 20 to be exposed outside the vacuum vessel 10, allowing the anode rod 20 to fully contact the cooling medium, thereby improving heat conduction and heat dissipation efficiency. Compared to the high-temperature zone caused by the semi-enclosed cavity in traditional fixed-anode X-ray tubes, the new design significantly improves heat dissipation performance, reduces the problem of insulating oil cracking caused by high temperatures, and thus extends the service life of the X-ray tube. The second portion 202 does not overlap with the vacuum vessel 10 in any direction perpendicular to the axis of the anode rod 20. This means that the exposed portion of the anode rod 20 can directly contact the surrounding, highly fluid cooling medium, further enhancing the heat dissipation effect.

[0042] The above embodiments are merely illustrative of the principles and effects of the present invention and are not intended to limit the present invention. Anyone skilled in the art may modify or alter the above embodiments without departing from the spirit and scope of the present invention. Therefore, all equivalent modifications or alterations made by one of ordinary skill in the art without departing from the spirit and technical principles disclosed in the present invention are intended to be covered by the claims of the present invention.

[0043] In the description herein, many specific details, such as examples of components and / or methods, are provided to provide a complete understanding of the embodiments of the present invention. However, those skilled in the art will recognize that embodiments of the present invention can be practiced without one or more of the specific details or with other devices, systems, components, methods, components, materials, parts, etc. In other cases, well-known structures, materials, or operations are not specifically shown or described in detail to avoid obscuring aspects of the embodiments of the present invention.

Claims

1. An X-ray tube, characterized in that: include: Vacuum container; a cathode assembly, the cathode assembly comprising an electron emitting end, at least the electron emitting end of the cathode assembly being accommodated in the vacuum container; An anode assembly comprising an anode rod and a target material. The anode rod is provided with an annular zone on its circumference for connecting to the vacuum container. The annular zone separates the anode rod into a first portion and a second portion. The vacuum container is sealed to the annular zone so that the first portion is accommodated within the vacuum container and the second portion is exposed outside the vacuum container. The target material is disposed in the first portion and is disposed opposite the electron emitting end. A projection of the second portion on a first plane has no overlapping area with a projection of the vacuum container on the first plane, and the first plane is any plane passing through the axis of the anode rod.

2. The X-ray tube according to claim 1, wherein The vacuum container includes a body made of a first material and an adapter ring made of a second material. One end of the adapter ring is connected to the body, and the other end is connected to the annular zone.

3. The X-ray tube according to claim 2, wherein The first material is glass, and the second material is Kovar alloy.

4. The X-ray tube according to claim 2, wherein The diameter of the body is greater than the diameter of the anode rod. The adapter ring includes a first matching portion for connecting to the annular zone, a second matching portion for connecting to the body, and a connecting portion between the first matching portion and the second matching portion.

5. The X-ray tube according to claim 4, characterized in that The connecting portion includes a conical structure with a diameter gradually increasing from the annular zone toward the side where the first portion is located.

6. The X-ray tube according to claim 5, wherein The first matching portion includes a straight cylinder parallel to the axis direction of the anode rod.

7. The X-ray tube according to claim 5, wherein The first matching portion includes a cone that is flush with the connecting portion; and the annular zone is a conical surface that is adapted to the inner wall of the cone.

8. The X-ray tube according to claim 6 or 7, characterized in that A flange is provided on a side of the annular zone away from the first portion, and the flange abuts against an end surface of the first matching portion.

9. The X-ray tube according to claim 1, wherein A heat sink is provided on an end of the second part away from the first part.

10. A medical device, characterized in that: An X-ray tube comprising the X-ray tube according to any one of claims 1 to 9.

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