Medical X-ray imaging equipment and fixing, sealing and filling device thereof

Abstract

The invention relates to the technical field of medical equipment, in particular to medical X-ray imaging equipment and a solid sealing and filling device thereof.The medical X-ray imaging equipment comprises a shell, an X-ray tube is fixedly installed in the shell, an anode target assembly and a cathode assembly are installed at the two ends of the X-ray tube respectively, and a ceramic tube is connected between the anode target assembly and the cathode assembly; the anode target assembly comprises a target material and a transmission window, the cathode assembly comprises a filament assembly, the filament assembly emits electrons to the target material in a vacuum environment, and X-rays are generated through the transmission window; a collimator and a baffle plate are fixedly mounted at the two ends of the shell corresponding to the anode target assembly and the cathode assembly respectively, a beam outlet corresponding to the transmission window is formed in the center of the collimator, and the beam outlet limits the electron radiation range. The X-ray imaging equipment is small in size, wide in application range, good in insulation effect, high in service environment tolerance, capable of bearing high voltage and excellent in radiation shielding performance.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a medical X-ray imaging device and its encapsulation and filling device. Background Art

[0002] Medical X-ray imaging systems typically include an X-ray emission source and an X-ray detector. The X-rays emitted by the X-ray imaging device pass through the human body and are received by the X-ray detector, and the X-rays transmitted through the human body are converted into electrical signals, and finally digital images are generated for medical staff as a reference for diagnosis. Currently, mobile X-ray imaging systems are usually used in non-fixed medical places such as field emergency rescue stations. However, the traditional mobile X-ray imaging systems are relatively large in shape and volume, occupy a relatively large space in the structural design of the instrument, and cannot meet the needs of social development. Therefore, the miniaturization design of the instrument must reduce the volume of the X-ray imaging device.

[0003] The core principle of the imaging system is the X-ray generating device. The X-ray tube generating device generates electrons at the cathode, accelerates them through a high-voltage electric field, and then hits the anode target surface. X-rays are generated through the bremsstrahlung mechanism. The X-ray tube is integrated with an external power supply and a high-voltage power supply to provide a high-voltage electric field as an X-ray imaging device.

[0004] In traditional systems, due to the size requirements of the X-ray tube and the high-voltage power supply, as well as the associated electrical insulation and radiation shielding requirements, the voltage of X-ray imaging devices is usually limited to below 100 KV. To solve the above problems of large-volume imaging systems, a medical X-ray imaging device and its encapsulation and filling device are specially developed, with a voltage that can load 70 KV - 180 KV and a continuous output power of 10 watts - 15 watts. Therefore, the insulation treatment of the small-volume charged part of the X-ray imaging device has become a top priority. Currently, the insulation methods used in X-ray imaging devices mainly include vacuum insulation, liquid potting insulation with insulating oil, gas filling with sulfur hexafluoride and nitrogen insulation, and insulation by placing insulating plates between high voltages. Based on the above technologies, we have integrated a medical X-ray imaging device with a small shape, small volume, high voltage, and short distance. The insulation method mainly uses solid insulating materials for insulation, and the solid insulation method has a high insulation coefficient and strong environmental tolerance. Summary of the Invention

[0005] In view of the above problems, the present invention provides a medical X-ray imaging device and its encapsulation and filling device. The X-ray imaging device is small in volume, wide in application range, good in insulation effect, strong in environmental tolerance, capable of withstanding high voltages, and has excellent radiation shielding performance.

[0006] To solve the above problems, the technical solutions adopted by the present invention are as follows:

[0007] A medical X-ray imaging device, comprising a housing, wherein an X-ray tube is fixedly installed inside the housing, an anode target assembly and a cathode assembly are respectively installed at two ends of the X-ray tube, and a ceramic tube is connected between the anode target assembly and the cathode assembly;

[0008] The anode target assembly includes a target material and a transmission window, and the cathode assembly includes a filament assembly. The filament assembly emits electrons to the target material in a vacuum environment, and X-rays are generated through the transmission window;

[0009] Collimators and baffles are respectively fixedly installed at two ends of the housing corresponding to the anode target assembly and the cathode assembly. An exit port corresponding to the transmission window is provided at the center of the collimator, and the exit port defines the electron radiation range;

[0010] The housing is filled with silicone resin that wraps the cathode assembly, epoxy resin that wraps the tube body of the X-ray tube, and PEI resin that wraps the anode target assembly. A shielding lead sleeve is also sleeved outside the epoxy resin;

[0011] It further includes a high-voltage power supply housing fixed at the bottom of the housing. A power supply component is installed inside the high-voltage power supply housing. The bottoms of the anode target assembly and the cathode assembly are both electrically connected to the power supply component through high-voltage cables, and the high-voltage power supply housing is filled with silicone resin.

[0012] Preferably, the power supply component includes positive and negative high-voltage power supplies, which are composed of two rows of high-voltage voltage multiplier rectifier units. One row of units generates positive high voltage, and the other row of units generates negative high voltage. The negative high voltage is applied to the high-voltage cable of the cathode assembly, and the positive high voltage is applied to the high-voltage cable of the anode target assembly. The high-voltage voltage multiplier rectifier unit is a voltage multiplier rectifier.

[0013] Preferably, a filament transformer and a voltage multiplier rectifier transformer are also installed inside the high-voltage power supply housing. A controller is installed at the top of the high-voltage power supply housing. The two rows of voltage multiplier rectifiers are electrically connected to the voltage multiplier rectifier transformer, and the filament transformer and the voltage multiplier rectifier transformer are located between the two rows of voltage multiplier rectifiers.

[0014] Preferably, heat dissipation fins are installed on both sides of the housing, a temperature test paper is installed at the top of the housing, and a pair of cable ports that communicate with the high-voltage power supply housing and allow the high-voltage cables to pass through are provided at the bottom of the housing. The pair of cable ports are facing the anode target assembly and the cathode assembly.

[0015] Preferably, the arrangement direction of the two rows of high-voltage voltage multiplier rectifier units forms an angle of 25°-35° with the direction of the high-voltage power supply housing.

[0016] Preferably, the epoxy resin is mixed with a radiopaque filler, which is lead or tungsten oxide. The density of the epoxy resin is greater than that of the PEI resin. The silicone resin, epoxy resin, PEI resin, and shielding lead sleeve are automatically filled and installed using a potting filling device.

[0017] The present invention also discloses a potting filling device. The potting filling device includes a base for clamping an X-ray imaging device. A movable frame that can move along its length direction is installed on the base. A switching disk is installed on the side wall of the movable frame. A silicone resin filling mechanism, an epoxy resin filling mechanism, and a PEI resin filling mechanism are circumferentially installed on the side wall of the switching disk.

[0018] Preferably, the silicone resin filling mechanism includes a turntable installed on the side wall of the switching disk. The turntable is driven by a first motor to rotate within a range of 180°. A silicone resin injection pipe and an air pipe are fixedly connected to the side wall of the turntable. The ends of the silicone resin injection pipe and the air pipe are fixedly connected to an annular partition. An opening for a high-voltage cable to pass through is provided at the bottom of the annular partition. An annular slot extending to the opening is provided on the inner wall of the annular partition. A sealing air cushion adapted to its shape is installed in the annular slot. The air pipe is connected to the sealing air cushion. The end of the silicone resin injection pipe communicates with the side wall of the annular partition.

[0019] Preferably, the epoxy resin filling mechanism includes a clamping seat fixedly connected to the side wall of the switching disk. A clamping groove for clamping a shielding lead sleeve is provided at the front end of the clamping seat. A clamping sleeve for sealing and sleeving around the anode target assembly is fixedly installed in the clamping groove. An epoxy resin injection pipe is provided at the inner bottom of the clamping groove outside the clamping sleeve.

[0020] Preferably, the PEI resin filling mechanism includes a resisting column fixed to the side wall of the switching disk. The resisting column is used to seal the port of the shielding lead sleeve. A PEI resin injection pipe is provided on the resisting column.

[0021] The beneficial effects of the present invention are as follows:

[0022] 1. In the X-ray imaging device, the X-ray tube is installed in the housing, and the power supply component is installed in the high-voltage power supply housing. The layout is reasonable, the overall volume is small, and the weight is light. It has a wide range of applications in small volumes and is convenient for movement and carrying. Heat dissipation fins are provided on both sides of the housing, and the heat dissipation effect is good.

[0023] 2. The integrated design of the high-voltage power supply and the X-ray tube does not use a long high-voltage cable for connection, resulting in higher reliability and insulation. Two cable ports are opened at the bottom of the housing, and the positions of the two cable ports respectively correspond to the anode end and the cathode end. The high-voltage power supply leads are effectively adjusted to the shortest and most insulating positions, avoiding the risk of creepage and arcing caused by too long leads, which may lead to power supply damage. It is convenient for integration, and the safety insulation coefficient is higher.

[0024] 3. The X-ray tube selects an end-face transmission type ceramic tube, which is not only small in size but also has a high voltage. The maximum operating voltage can reach 70 KV - 180 KV, exceeding the existing 70 KV integrated power supply technology.

[0025] 4. Solid encapsulation resin filling is selected between the X-ray tube and the housing. Oxides of high atomic number elements such as lead and tungsten oxides can be used for filling. Different density fillers can be used in different regions according to different ray intensities, which is both insulating and can block radiation leakage. Specifically, silicone resin is filled around the cathode assembly, epoxy resin is filled around the X-ray tube body, PEI resin is filled at the transmission window of the anode target assembly, and a shielding lead sleeve is also sleeved outside the epoxy resin; among them, PEI resin has the advantages of low density, high temperature resistance, flame retardancy, electrical insulation performance, and radiation resistance. The low density is beneficial to the maximum transmission of X-rays; the epoxy resin is mixed with oxides such as lead and tungsten. The voltage is high and the radiation dose is the strongest around the anode target area of the X-ray tube, and the heat is concentrated. This epoxy resin can reduce the ray transmittance, has high insulation and high thermal conductivity. Adding a shielding lead sleeve outside the epoxy resin can further increase the radiation shielding amount; silicone resin is filled in the cathode end and the high-voltage power supply housing to prevent the oil leakage phenomenon that occurs when traditional insulation oil is used for potting, and also plays a heat conduction effect.

[0026] 5. Through the installation base, moving frame, switching disk, silicone resin filling mechanism, epoxy resin filling mechanism, and PEI resin filling mechanism, the X-ray imaging device is clamped on the base. The silicone resin filling mechanism is first pushed into the housing, and silicone resin is injected into the cathode end area and the high-voltage power supply housing. After curing, the shielding lead sleeve is sent into the housing through the epoxy resin filling mechanism, and epoxy resin is filled inside. Finally, the port of the shielding lead sleeve is sealed by the bottom column, and PEI resin is filled at the transmission window part of the anode end, and the solid encapsulation filling process is automatically completed in sequence. Description of the Drawings

[0027] Figure 1 is a perspective view of the present invention;

[0028] Figure 2 is a cross-sectional view of the present invention;

[0029] Figure 3 is a schematic structural diagram of the present invention with an additional high-voltage power supply;

[0030] Figure 4 is Figure 3 the internal structural schematic diagram of;

[0031] Figure 5 is a system schematic diagram of the present invention;

[0032] Figure 6 is a schematic diagram of the solid encapsulation filling device proposed by the present invention;

[0033] Figure 7 Front view of the potting filling device proposed by the present invention;

[0034] Figure 8 Schematic three-dimensional view of the annular partition proposed by the present invention;

[0035] Figure 9 Schematic sectional view of the annular partition proposed by the present invention;

[0036] Figure 10 Schematic diagram of the epoxy resin filling mechanism proposed by the present invention.

[0037] In the figure: 1 housing, 2 temperature test paper, 3 collimator, 301 beam outlet, 4 heat dissipation fins, 5 baffle, 6 X-ray tube, 601 anode target assembly, 602 cathode assembly, 7 silicone resin, 8 epoxy resin, 9 shielding lead sleeve, 10 PEI resin, 11 cable port, 12 high-voltage power supply housing, 13 controller, 14 filament transformer, 15 voltage multiplier rectifier, 16 voltage multiplier rectifier transformer, 17 base, 18 installation groove, 19 clamping plate, 20 threaded rod, 21 second motor, 22 moving frame, 23 switching disk, 24 clamping seat, 25 ferrule, 26 PEI resin injection pipe, 27 abutting post, 28 silicone resin injection pipe, 29 air pipe, 30 turntable, 31 annular partition, 32 annular slot, 33 sealing air cushion, 34 opening, 35 epoxy resin injection pipe, 36 card slot, 37 double-headed cylinder, 38 first motor. Specific embodiments

[0038] In order to make the above objects, features and advantages of the present invention more obvious and understandable, the specific embodiments of the present invention will be described in detail below with reference to the accompanying drawings. Many specific details are set forth in the following description in order to provide a thorough understanding of 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.

[0039] It should be noted that when an element is referred to as being "fixed to" 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", "left", "right" and similar expressions used herein are for illustrative purposes only and do not represent the only embodiments.

[0040] Refer to Figures 1 - 5A medical X-ray imaging device includes a shell 1, in which an X-ray tube 6 is fixedly installed, and an anode target assembly 601 and a cathode assembly 602 are respectively installed at both ends of the X-ray tube 6, a ceramic tube is connected between the anode target assembly 601 and the cathode assembly 602, the anode target assembly 601 includes a target material and a transmission window, the cathode assembly includes a filament assembly, and the filament assembly emits electrons to the target material in a vacuum environment to generate X-rays through the transmission window.

[0041] A collimator 3 and a baffle 5 are fixedly installed at both ends of the shell 1 corresponding to the anode target assembly 601 and the cathode assembly 602, respectively. A beam outlet 301 corresponding to the transmission window is provided at the center of the collimator 3. The beam outlet 301 limits the electron radiation range so as to protect normal objects outside the target area from being irradiated. The effective radiation angle can reach an ultra-wide-angle beam outlet angle of 70 degrees to 100 degrees.

[0042] The shell 1 is filled with silicone resin 7 wrapping the cathode assembly 602, filled with epoxy resin 8 wrapping the X-ray tube 6 body, and filled with PEI resin 10 (amorphous polyetherimide resin) wrapping the anode target assembly 601. A shielding lead sheath 9 is also sheathed around the epoxy resin 8. Oxides of high atomic number elements, such as lead, tungsten and other oxides can be used for filling. Different densities of fillers can be used for different areas of different radiation intensities, which can both insulate and block radiation leakage.

[0043] The X-ray tube 6 and the power supply are enclosed in a conductive shell maintained at a reference ground potential, which forms an equipotential surface around the X-ray tube and the power supply. Since the cathode and anode ends of the X-ray tube 6 are at high voltage relative to the shell, the area surrounding the entire X-ray tube 6 is designed to be filled with an electrical insulating material to prevent high voltage breakdown between the tube electrode and the adjacent shell. The electrical insulating material can be a solid packaging material, such as silicone, polyurethane, epoxy resin, etc.; liquid insulating materials include transformer oil or gas insulation, such as sulfur hexafluoride, dry nitrogen, etc. Silicone resin 7 and epoxy resin 8 are the most mechanically stable solid packaging materials, so they can be preferred. In addition, the solid packaging material can be mixed with non-radioactive fillers to provide enhanced X-ray shielding near the X-ray tube. Such non-radioactive fillers can be selected from oxides of high atomic number elements, such as oxides containing lead, tungsten, etc. And the non-radioactive fillers do not need to be evenly distributed in the packaging material. In some cases, it is advantageous to allocate fillers with different concentrations for different voltages in different regions.

[0044] It also includes a high-voltage power supply housing 12 fixed to the bottom of the housing 1. A power supply component is installed inside the high-voltage power supply housing 12. The bottoms of the anode target assembly 601 and the cathode assembly 602 are electrically connected to the power supply component through high-voltage cables. The high-voltage power supply housing 12 is filled with silicone resin 7. The power supply component includes positive and negative high-voltage power supplies, which are composed of two rows of high-voltage voltage multiplier rectifier units. One row of units generates positive high voltage, and the other row of units generates negative high voltage. The negative high voltage is applied to the high-voltage cable of the cathode assembly 602, and the positive high voltage is applied to the high-voltage cable of the anode target assembly 601. The high-voltage voltage multiplier rectifier unit is a voltage multiplier rectifier 15. A filament transformer 14 and a voltage multiplier rectifier transformer 16 are also installed inside the high-voltage power supply housing 12. A controller 13 is installed on the top of the high-voltage power supply housing 12. The two rows of voltage multiplier rectifiers 15 are electrically connected to the voltage multiplier rectifier transformer 16. The filament transformer 14 and the voltage multiplier rectifier transformer 16 are located between the two rows of voltage multiplier rectifiers 15. The power supply is enclosed in a conductive housing maintained at a reference ground potential, and this conductive housing forms an equipotential surface around the X-ray power supply.

[0045] Further, heat dissipation fins 4 are installed on both sides of the housing 1. A temperature test paper 2 is installed on the top of the housing 1. A pair of cable ports 11 communicating with the high-voltage power supply housing 12 and allowing the high-voltage cables to pass through are provided at the bottom of the housing 1. The pair of cable ports 11 are opposite to the anode target assembly 601 and the cathode assembly 602, effectively adjusting the high-voltage power supply leads to the shortest and most insulating position, avoiding the risk that too long leads are prone to creepage and arcing, resulting in power supply damage, facilitating integration, and having a higher safety insulation factor.

[0046] Further, the setting direction of the two rows of high-voltage voltage multiplier rectifier units forms an angle of 25° - 35° with the direction of the high-voltage power supply housing 12, so that the two rows of high-voltage voltage multiplier rectifier units are far from the housing and bear high voltage.

[0047] An X-ray-impermeable filler is mixed in the epoxy resin 8. The filler is lead and tungsten oxide. The density of the epoxy resin 8 is greater than the density of the PEI resin 10. The silicone resin 7, the epoxy resin 8, the PEI resin 10, and the shielding lead sleeve 9 are automatically filled and installed by a potting filling device.

[0048] It may be very important for X-ray imaging equipment to minimize the overall size and weight of the source. Therefore, it is necessary to operate at a voltage of up to 70KV-180KV and have an X-ray imaging equipment configuration that is consistent with the small size and low weight that may be expected for portable and handheld applications. This application can be used for hospital diagnosis, on-site first aid, and facilitate rapid X-ray examination of patients and accurate diagnosis; handheld or security inspection equipment can be used for security inspections in airports, stations, subways, etc., and can detect contraband hidden in luggage and parcels; border security inspections perform X-ray inspections on vehicle cargo to prevent cross-border transportation of non-articles. Various phenomena of social development show that small portable X-ray analyzers and handheld X-ray imaging equipment used randomly in the field are indispensable.

[0049] Reference Figures 6 - 10 The present invention also provides a solid sealing filling device, which includes a base 17 for clamping the X-ray imaging device, a movable frame 22 that can move along its length direction is installed on the base 17, a switching disk 23 is installed on the side wall of the movable frame 22, and a silicone resin filling mechanism, an epoxy resin filling mechanism and a PEI resin filling mechanism are circumferentially installed on the side wall of the switching disk 23. The silicone resin filling mechanism is first pushed into the shell, and silicone resin 7 is injected into the cathode end area and the high-voltage power supply shell. After curing, the shielding lead sleeve 9 is sent into the shell through the epoxy resin filling mechanism, and the epoxy resin 8 is filled inside. Finally, the port of the shielding lead sleeve 9 is sealed through the bottom column, and the transmission window part of the anode end is filled with PEI resin 10, and the solid sealing filling process is automatically completed in sequence.

[0050] Specifically, the silicone filling mechanism includes a turntable 30 mounted on the side wall of the switching disk 23, the turntable 30 is driven by the first motor 38 to rotate within a range of 180 degrees, the side wall of the turntable 30 is fixedly connected with a silicone injection pipe 28 and an air pipe 29, the ends of the silicone injection pipe 28 and the air pipe 29 are fixedly connected with an annular partition 31, the bottom of the annular partition 31 is provided with an opening 34 for the high-voltage cable to pass through, the inner wall of the annular partition 31 is provided with an annular groove 32 extending to the opening 34, a sealing air cushion 33 adapted to its shape is installed in the annular groove 32, the air pipe 29 is connected to the sealing air cushion 33, the silicone injection pipe 28 is fixedly connected to the end of the air pipe 29, and the silicone injection pipe 28 is fixedly connected to the end of the air pipe 29. The end is connected with the side wall of the annular partition 31, and the annular partition 31 is pushed into the shell 1. The annular partition 31 first passes through the anode target assembly 601 with a larger diameter, and then passes through the ceramic tube. In this process, the opening 34 is located at the bottom for the high-voltage cable to pass through, and finally moves to the front side of the cathode assembly 602. The first motor 38 is started to drive the turntable 30 to rotate 180°, and the opening 34 is turned upward. The sealing air cushion 33 is inflated through the air pipe 29. The sealing air cushion 33 is inflated and expands, against the outer wall of the ceramic tube, and the opening 34 is closed to achieve separation and sealing. The silicone resin 7 is filled into the periphery of the cathode assembly 602 through the silicone resin injection tube 28.

[0051] The epoxy resin filling mechanism includes a clamping seat 24 fixedly connected to the side wall of the switching disk 23. A clamping groove 36 for clamping the shielding lead sleeve 9 is provided at the front end of the clamping seat 24. A clamping sleeve 25 for hermetically sleeving around the anode target assembly 601 is fixedly installed in the clamping groove 36. An epoxy resin injection pipe 35 is provided at the inner bottom of the clamping groove 36 outside the clamping sleeve 25. The shielding lead sleeve 9 is clamped in the clamping groove 36 and pushed into the housing 1. The clamping sleeve 25 is sleeved around the anode target assembly 601 to achieve separation. Epoxy resin 8 is injected into the shielding lead sleeve 9 through the epoxy resin injection pipe 35 and fills the corresponding cable opening 11 and the bottom gap along the strip-shaped opening at the bottom of the shielding lead sleeve 9.

[0052] The PEI resin filling mechanism includes a resisting column 27 fixed to the side wall of the switching disk 23. The resisting column 27 is used to seal the port of the shielding lead sleeve 9. A PEI resin injection pipe 26 is provided on the resisting column 27. After the epoxy resin 8 is cured, the resisting column 27 is pushed to the port of the shielding lead sleeve 9, and PEI resin 10 is injected into the transmission end of the anode target assembly 601 through the PEI resin injection pipe 26.

[0053] To achieve the clamping of the X-ray imaging device, an installation groove 18 is opened on the base 17. A double-headed cylinder 37 is installed in the installation groove 18. Clamping plates 19 are fixed to both telescopic ends of the double-headed cylinder 37. A pair of clamping plates 19 clamp the high-voltage power supply housing 12. The double-headed cylinder 37 is started to drive a pair of clamping plates 19 to clamp the high-voltage power supply housing 12, thereby fixing the position of the housing 1.

[0054] To achieve the movement of the moving frame 22, a moving groove is opened on the base 17. A threaded rod 20 is rotatably connected in the moving groove. A second motor 21 capable of driving the threaded rod 20 to rotate is installed at the end of the base 17. The bottom of the moving frame 22 is threadedly connected to the threaded rod 20. The second motor 21 is started to drive the threaded rod 20 to rotate, and then the switching disk 23 is driven to move through the moving frame 22.

[0055] The high-voltage power supply housing 12 is placed on the base 17, and the double-headed cylinder 37 is started to drive a pair of clamps 19 to clamp the high-voltage power supply housing 12, thereby fixing the position of the housing 1, and the second motor 21 is started to drive the threaded rod 20 to rotate, and then the switching disk 23 is driven to move through the moving frame 22, and the annular partition 31 is first pushed into the housing 1, and the annular partition 31 first passes through the anode target assembly 601 with a larger diameter, and then passes through the ceramic tube. In this process, the opening 34 is located at the bottom for the high-voltage cable to pass through, and finally moves to the front side of the cathode assembly 602, and the first motor 38 is started to drive the turntable 30 to rotate 180°, and the opening 34 is turned to the top, and the sealing air cushion 33 is inflated through the air pipe 29. The sealing air cushion 33 is inflated and expanded to resist the outer wall of the ceramic tube, and the opening 34 is closed to achieve separation and sealing, and silicone resin 7 is filled into the periphery of the cathode assembly 602 through the silicone resin injection tube 28, and flows into the high-voltage power supply housing 12 through the corresponding cable port 11, and the silicone resin 7 is filled. After it is cured, the annular partition 31 is pulled out.

[0056] The switching disk 23 rotates to turn the epoxy resin filling mechanism to the position corresponding to the shell 1. At this time, the shielding lead sleeve 9 is clamped in the clamping groove 36 and pushed into the shell 1. The clamping sleeve 25 is sleeved on the outer periphery of the anode target assembly 601 to achieve separation. The epoxy resin 8 is injected into the shielding lead sleeve 9 through the epoxy resin injection tube 35, and the corresponding cable port 11 and the bottom gap are filled along the strip port at the bottom of the shielding lead sleeve 9; after the epoxy resin 8 is cured, the support column 27 is pushed to the port of the shielding lead sleeve 9, and the PEI resin 10 is injected into the transmission end of the anode target assembly 601 through the PEI resin injection tube 26, and the sealing process can be automatically completed in sequence.

[0057] The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principle of the present invention should be included in the protection scope of the present invention.

Claims

1. A medical X-ray imaging device, comprising a housing (1), characterized in that: An X-ray tube (6) is fixedly installed in the shell (1), an anode target assembly (601) and a cathode assembly (602) are respectively installed at two ends of the X-ray tube (6), and a ceramic tube is connected between the anode target assembly (601) and the cathode assembly (602); The anode target assembly (601) comprises a target material and a transmission window, and the cathode assembly (602) comprises a filament assembly, wherein the filament assembly emits electrons to the target material in a vacuum environment and generates X-rays through the transmission window; A collimator (3) and a baffle (5) are fixedly mounted on the two ends of the shell (1) corresponding to the anode target assembly (601) and the cathode assembly (602), respectively; a beam outlet (301) corresponding to the transmission window is provided at the center of the collimator (3); and the beam outlet (301) limits the electron radiation range; The shell (1) is filled with silicone resin (7) wrapping the cathode assembly (602), epoxy resin (8) wrapping the tube body of the X-ray tube (6), and PEI resin (10) wrapping the anode target assembly (601), and a shielding lead sleeve (9) is also provided around the epoxy resin (8); It also includes a high-voltage power supply housing (12) fixed to the bottom of the shell (1), a power supply component is installed in the high-voltage power supply housing (12), the bottoms of the anode target assembly (601) and the cathode assembly (602) are electrically connected to the power supply component via high-voltage cables, and the high-voltage power supply housing (12) is filled with silicone resin (7).

2. A medical X-ray imaging device according to claim 1, characterized in that: The power supply assembly includes positive and negative high-voltage power supplies, which are composed of two rows of high-voltage voltage-doubling rectifier units. One row of units generates positive high voltage, and the other row of units generates negative high voltage. The negative high voltage is applied to the high-voltage cable of the cathode assembly (602), and the positive high voltage is applied to the high-voltage cable of the anode target assembly (601). The high-voltage voltage-doubling rectifier unit is a voltage-doubling rectifier (15).

3. A medical X-ray imaging device according to claim 2, characterized in that: A filament transformer (14) and a voltage-doubling rectifier transformer (16) are also installed in the high-voltage power supply housing (12); a controller (13) is installed on the top of the high-voltage power supply housing (12); the two rows of voltage-doubling rectifiers (15) are electrically connected to the voltage-doubling rectifier transformer (16); and the filament transformer (14) and the voltage-doubling rectifier transformer (16) are located between the two rows of voltage-doubling rectifiers (15).

4. The medical X-ray imaging device according to claim 1, characterized in that: Heat dissipation fins (4) are installed on both sides of the shell (1), a temperature test paper (2) is installed on the top of the shell (1), and a pair of cable openings (11) are provided at the bottom of the shell (1) that are connected to the high-voltage power supply housing (12) and for high-voltage cables to pass through, and the pair of cable openings (11) are directly opposite to the anode target assembly (601) and the cathode assembly (602).

5. The medical X-ray imaging device according to claim 1, characterized in that: The arrangement direction of the two rows of high-voltage voltage-doubling rectifier units forms an angle of 25°-35° with the direction of the high-voltage power supply housing (12).

6. The medical X-ray imaging device according to claim 1, characterized in that: The epoxy resin (8) is mixed with a radiopaque filler, which is lead and tungsten oxide. The density of the epoxy resin (8) is greater than the density of the PEI resin (10). The silicone resin (7), epoxy resin (8), PEI resin (10) and shielding lead sleeve (9) are automatically filled and installed using a fixed sealing filling device.

7. A sealing and filling device for medical X-ray imaging equipment according to any one of claims 1 to 6, characterized in that: The invention comprises a base (17) for clamping an X-ray imaging device, wherein a movable frame (22) movable along its length direction is mounted on the base (17), a switching disk (23) is mounted on the side wall of the movable frame (22), and a silicone resin filling mechanism, an epoxy resin filling mechanism and a PEI resin filling mechanism are mounted on the side wall of the switching disk (23) in a circumferential direction.

8. The sealing and filling device for medical X-ray imaging equipment according to claim 7, characterized in that: The silicone filling mechanism comprises a rotating disk (30) mounted on the side wall of the switching disk (23); the rotating disk (30) is driven by a first motor (38) to rotate within a range of 180 degrees; a silicone injection tube (28) and an air tube (29) are fixedly connected to the side wall of the rotating disk (30); the ends of the silicone injection tube (28) and the air tube (29) are fixedly connected to an annular partition (31); an opening (34) for a high-voltage cable to pass through is provided at the bottom of the annular partition (31); an annular groove (32) extending to the opening (34) is provided on the inner wall of the annular partition (31); a sealing air cushion (33) adapted to the shape of the annular groove (32) is installed in the annular groove (32); the air tube (29) is connected to the sealing air cushion (33); and the end of the silicone injection tube (28) is communicated with the side wall of the annular partition (31).

9. The sealing and filling device for medical X-ray imaging equipment according to claim 7, characterized in that: The epoxy resin filling mechanism comprises a clamping seat (24) fixedly connected to the side wall of the switching disk (23); a clamping groove (36) for clamping the shielding lead sleeve (9) is provided at the front end of the clamping seat (24); a clamping sleeve (25) for sealing the clamping sleeve on the periphery of the anode target assembly (601) is fixedly installed in the clamping groove (36); and an epoxy resin injection pipe (35) is provided at the inner bottom of the clamping groove (36) located outside the clamping sleeve (25).

10. The sealing and filling device for medical X-ray imaging equipment according to claim 7, characterized in that: The PEI resin filling mechanism comprises a support column (27) fixed on the side wall of the switching disk (23), the support column (27) is used to seal the port of the shielding lead sleeve (9), and a PEI resin injection pipe (26) is provided on the support column (27).

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