Medical x-ray imaging apparatus and its hermetic filling device

Abstract

The application relates to the technical field of medical equipment, and particularly provides a medical X-ray imaging device and a solid sealing and filling device thereof. The X-ray imaging device comprises a shell, an X-ray tube is fixedly arranged in the shell, an anode target assembly and a cathode assembly are respectively arranged at two ends of the X-ray tube, and a ceramic tube is arranged 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 are respectively fixedly arranged at two ends of the shell and correspond to the anode target assembly and the cathode assembly, a beam outlet corresponding to the transmission window is arranged at the center of the collimator, and the beam outlet limits the electron radiation range. The X-ray imaging device has the advantages of small volume, wide application range, good insulation effect, strong use environment tolerance, high voltage bearing capacity and excellent radiation shielding performance.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of medical equipment, in particular to a medical X-ray imaging device and a solid sealing and filling device thereof. BACKGROUND

[0002] A medical X-ray imaging system generally comprises an X-ray emitting source and an X-ray detector. After being transmitted through a human body, the X-rays emitted by the X-ray imaging device are received by the X-ray detector and converted into electrical signals, and finally a digital image is generated for medical personnel to use as a reference for diagnosis. Currently, non-fixed medical sites such as field emergency rescue stations often use mobile X-ray imaging systems. However, the traditional mobile X-ray imaging system has a large shape and volume, and occupies a large space in the structural design of the instrument, which 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 generates electrons from the cathode, which are accelerated by a high-voltage electric field to hit the anode target. X-rays are generated through the impact 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 the traditional system, the voltage of the X-ray imaging device is usually limited to below 100KV 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. To solve the problem of the large imaging system, a medical X-ray imaging device and a solid sealing and filling device thereof are developed, which can load a voltage of 70KV-180KV and continuously output a power of 10-15 watts. Therefore, the insulation treatment of the small-volume charged part of the X-ray imaging device becomes a top priority. Currently, the main insulation methods for X-ray imaging devices include vacuum insulation, liquid filling insulation oil insulation, gas filling sulfur hexafluoride and nitrogen insulation, and insulation between high voltages through insulation boards. Based on the above technologies, we integrate a medical X-ray imaging device with a small shape and volume, high voltage, and short distance. The main insulation method is to fill solid insulation materials for insulation. The solid insulation method has high insulation coefficient and strong environmental tolerance. SUMMARY

[0005] To solve the above problems, the present application provides a medical X-ray imaging device and a solid sealing and filling device thereof. The X-ray imaging device has a small volume, a wide application range, a good insulation effect, a strong environmental tolerance, can withstand high voltage, and has excellent radiation shielding performance.

[0006] To solve the above problems, the technical solution adopted by the present application is:

[0007] The utility model provides a kind of medical X-ray imaging equipment, including shell, X-ray tube is fixedly installed in the shell, both ends of the X-ray tube are installed anode target assembly and cathode component respectively, ceramic tube is connected between the anode target assembly and cathode component;

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

[0009] The shell is fixedly installed collimator and baffle at both ends respectively corresponding anode target assembly and cathode component, the center of the collimator is provided with beam exit corresponding transmission window, and the beam exit limits electron radiation range.

[0010] The shell is filled with silicon resin wrapping cathode component, epoxy resin wrapping X-ray tube body, and PEI resin wrapping anode target assembly, and the periphery of the epoxy resin is further provided with shielding lead sleeve.

[0011] Further comprising high-voltage power supply shell fixed at the bottom of the shell, the power supply assembly is installed in the high-voltage power supply shell, the bottom of the anode target assembly and the cathode component are electrically connected with the power supply assembly through high-voltage cable, and the high-voltage power supply shell is filled with silicon resin.

[0012] Preferably, the power supply assembly includes positive and negative high-voltage power supply, which is composed of two rows of high-voltage voltage doubler 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 component, and the positive high-voltage is applied to the high-voltage cable of the anode target assembly, and the high-voltage voltage doubler rectifier unit is a voltage doubler rectifier.

[0013] Preferably, the high-voltage power supply shell is further provided with filament transformer and voltage doubler rectifier transformer, and the controller is installed at the top of the high-voltage power supply shell, the two rows of voltage doubler rectifiers are electrically connected with the voltage doubler rectifier transformer, and the filament transformer and the voltage doubler rectifier transformer are located between the two rows of voltage doubler rectifiers.

[0014] Preferably, the shell is provided with heat dissipation fins on both sides, and the shell is provided with temperature test paper at the top, and the shell is provided with a pair of cable ports at the bottom, which are in communication with the high-voltage power supply shell and allow high-voltage cables to pass through, and the pair of cable ports are opposite to the anode target assembly and the cathode component.

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

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

[0017] The application also discloses a solid sealing filling device, which comprises a base for clamping an X-ray imaging equipment, a movable frame movably arranged on the base, a switching disc arranged on the side wall of the movable frame, and a silicone resin filling mechanism, an epoxy resin filling mechanism and a PEI resin filling mechanism arranged on the side wall of the switching disc.

[0018] Preferably, the silicone resin filling mechanism comprises a rotating disc arranged on the side wall of the switching disc, the rotating disc is driven to rotate within a range of 180 degrees by a first motor, the side wall of the rotating disc is fixedly connected with a silicone resin injection pipe and an air pipe, the ends of the silicone resin injection pipe and the air pipe are fixedly connected with a ring-shaped partition plate, the bottom of the ring-shaped partition plate is provided with an opening for a high-voltage cable to pass through, the inner wall of the ring-shaped partition plate is provided with a ring-shaped slot extending to the opening, the ring-shaped slot is arranged with a sealing air cushion matched with the shape of the ring-shaped slot, the air pipe is connected with the sealing air cushion, and the end of the silicone resin injection pipe is in communication with the side wall of the ring-shaped partition plate.

[0019] Preferably, the epoxy resin filling mechanism comprises a clamping seat fixedly connected with the side wall of the switching disc, the front end of the clamping seat is provided with a clamping groove for clamping the shielding lead sleeve, the clamping groove is fixedly arranged with a clamping sleeve for sealing the clamping sleeve around the anode target assembly, and the inner bottom of the clamping groove outside the clamping sleeve is provided with an epoxy resin injection pipe.

[0020] Preferably, the PEI resin filling mechanism comprises a resisting column fixedly arranged on the side wall of the switching disc, the resisting column is used for sealing the port of the shielding lead sleeve, and the resisting column is provided with a PEI resin injection pipe.

[0021] The application has the following beneficial effects:

[0022] 1. The X-ray imaging equipment installs the X-ray tube in the shell and installs the power supply assembly in the high-voltage power supply shell, the layout is reasonable, the overall volume is small, the weight is light, the small volume is widely applied, and the X-ray imaging equipment is convenient to move and carry; the heat dissipation fins are arranged on the two sides of the shell, and the heat dissipation effect is good.

[0023] 2. The high-voltage power supply and the X-ray tube are designed in an integrated manner, a long high-voltage cable is not used, the reliability and insulation are higher; two cable openings are formed in the bottom of the shell, and the positions of the two cable openings correspond to the anode end and the cathode end, respectively. The high-voltage power supply lead is effectively adjusted to be the shortest and the most beneficial to insulation, the risk of power supply damage caused by long lead and easy creeping arc is avoided, the X-ray imaging equipment is convenient to integrate, and the safety insulation factor is higher.

[0024] 3. The X-ray tube is selected to have an end face transmission type ceramic tube, which not only has a small volume, but also has a high voltage, and the highest working voltage can reach 70KV-180KV, which exceeds the existing technology of 70KV power supply.

[0025] 4. The X-ray tube and the shell are filled with solid packaging resin, which can be filled with oxides of high atomic number elements, such as lead, tungsten and the like, and can be filled with different densities in different regions according to different radiation intensities, which is not only insulated but also blocks radiation leakage. Specifically, the outer periphery of the cathode assembly is filled with silicone resin, the outer periphery of the X-ray tube is filled with epoxy resin, the transmission window of the anode target assembly is filled with PEI resin, and a shielding lead sleeve is additionally provided outside the epoxy resin. The 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 maximization of X-ray transmission. The epoxy resin mixed with lead, tungsten and other oxides has high voltage and strong radiation intensity around the anode target area of the X-ray tube, and the heat is concentrated. The epoxy resin can reduce the radiation transmission rate and has high insulation and high thermal conductivity. The shielding lead sleeve outside the epoxy resin can further increase the radiation shielding amount. The cathode end and the high-voltage power supply shell are filled with silicone resin to prevent oil leakage caused by traditional oil filling, and also have the effect of heat conduction.

[0026] 5. By installing the base, the moving frame, the switching disc, the silicone resin filling mechanism, the epoxy resin filling mechanism and the PEI resin filling mechanism, the X-ray imaging equipment is clamped on the base, the silicone resin filling mechanism is first pushed into the shell, the silicone resin is injected into the cathode end area and the high-voltage power supply shell, and after solidification, the shielding lead sleeve is sent into the shell by the epoxy resin filling mechanism, the epoxy resin is filled into the interior, and finally the port of the shielding lead sleeve is sealed by the bottom column, the PEI resin is filled into the transmission window part of the anode end, and the filling process of solid sealing is automatically completed in sequence. BRIEF DESCRIPTION OF DRAWINGS

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

[0028] Figure 2 is a sectional view of the present application;

[0029] Figure 3 is a structure diagram of the present application with a high-voltage power supply;

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

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

[0032] Figure 6 is a solid sealing and filling device diagram proposed by the present application;

[0033] Figure 7 Front view of the solid sealing filling device according to the present application;

[0034] Figure 8 Schematic perspective view of the annular partition according to the present application;

[0035] Figure 9 Schematic sectional view of the annular partition according to the present application;

[0036] Figure 10 Schematic view of the epoxy resin filling mechanism according to the present application.

[0037] In the figure: 1 housing, 2 temperature test paper, 3 collimator, 301 beam outlet, 4 heat dissipation fin, 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 shell, 13 controller, 14 filament transformer, 15 voltage multiplier rectifier, 16 voltage multiplier rectifier transformer, 17 base, 18 mounting groove, 19 clamping plate, 20 threaded rod, 21 second motor, 22 moving frame, 23 switching disc, 24 clamping seat, 25 clamping sleeve, 26 PEI resin injection pipe, 27 abutment column, 28 silicone resin injection pipe, 29 air pipe, 30 rotary disc, 31 annular partition, 32 annular slot, 33 sealed air cushion, 34 opening, 35 epoxy resin injection pipe, 36 clamping groove, 37 double-head air cylinder, 38 first motor. DETAILED DESCRIPTION

[0038] In order to make the above objectives, features and advantages of the present application more apparent, specific embodiments of the present application will be described in detail below with reference to the accompanying drawings. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present application. However, the present application can be practiced in a number of different ways beyond the specific details disclosed herein. Thus, the present application is not intended to be limited to the following disclosed specific embodiments.

[0039] It should be noted that when an element is referred to as being "on" another element, it can be directly on the other element or intervening elements can also be present. When an element is referred to as being "connected" or "coupled" to another element, it can be directly connected or coupled to the other element or intervening elements can also be present. The terms "vertical", "horizontal", "left", "right" and similar expressions as used herein are for illustrative purposes only and are not intended to be limiting.

[0040] REFERENCE Figures 1-5The utility model provides a medical X -ray imaging equipment, including the shell 1, the X -ray tube 6 is fixedly installed in the shell 1, and the both ends of X -ray tube 6 are installed anode target assembly 601 and cathode assembly 602 respectively, and the ceramic tube is connected between anode target assembly 601 and cathode assembly 602, and anode target assembly 601 includes target material and transmission window, and cathode assembly includes filament assembly, and filament assembly emits electron to target material under vacuum environment, and X -ray is generated through transmission window.

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

[0042] The shell 1 is filled with the silicon resin 7 wrapped cathode assembly 602, is filled with the epoxy resin 8 wrapped X -ray tube 6 pipe body, is filled with the PEI resin 10 (amorphous polyetherimide resin) wrapped anode target assembly 601, and the periphery of epoxy resin 8 is also set with shielding lead sleeve 9, and can select the oxide of high atomic number element, such as lead, tungsten oxide filling, and can use different density fillers in different radiation intensity regions, which is insulation and also blocks radiation leakage.

[0043] The X -ray tube 6 and power supply are surrounded in the conductive shell kept at reference ground potential, and the conductive shell forms equipotential surface around the X -ray tube and power supply. Since the cathode and anode ends of X -ray tube 6 are at high voltage relative to the shell, the region surrounding the entire X -ray tube 6 is designed to be filled with an electrically insulating material to prevent high voltage breakdown between the tube electrodes and the adjacent shell. The electrically insulating material can be a solid encapsulant material, such as: silicone, polyurethane, epoxy, etc. The liquid insulation material has transformer oil or gas insulation, such as sulfur hexafluoride, dry nitrogen, etc. The silicone 7 and epoxy 8 are the most stable in mechanical properties among the solid encapsulant materials, and can be preferred. In addition, the solid encapsulant material can be mixed with a radiopaque filler to provide enhanced X -ray shielding in the vicinity of the X -ray tube. Such a radiopaque filler can be selected from the oxide of a high atomic number element, such as lead, tungsten oxide. And the radiopaque filler does not need to be uniformly distributed in the encapsulant material. In some cases, it is advantageous to adjust the filler with different concentrations in different regions with different voltages.

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

[0045] Further, heat dissipation fins 4 are installed on both sides of the shell 1. A temperature test paper 2 is installed at the top of the shell 1. A pair of cable ports 11 is provided at the bottom of the shell 1, which communicates with the high-voltage power supply shell 12 and allows high-voltage cables to pass through. The pair of cable ports 11 is opposite to the anode target assembly 601 and the cathode assembly 602, effectively adjusting the high-voltage power supply lead to the shortest and most beneficial position for insulation, avoiding the risk of power supply damage caused by long lead and easy creepage arc. It is convenient for integrated and has higher safety insulation factor.

[0046] Further, the direction of the two rows of high-voltage voltage doubler rectifier units is at an angle of 25°-35° with the direction of the high-voltage power supply shell 12, so that the two rows of high-voltage voltage doubler rectifier units are away from the shell and withstand high voltage.

[0047] The epoxy resin 8 contains a radiopaque filler, which is lead or tungsten oxide. The density of the epoxy resin 8 is greater than that of the PEI resin 10. The silicone 7, the epoxy resin 8, the PEI resin 10, and the shielding lead sleeve 9 are automatically filled and installed by a solid sealing filling device.

[0048] It can be very important for the X-ray imaging device to minimize the overall size and weight of the source, therefore, the X-ray imaging device configuration that needs to operate at a voltage up to 70KV-180KV and is consistent with the small size and low weight that can be expected for portable and handheld applications, can be used for hospital diagnosis, on-site first aid, convenient for patients to have a quick X-ray examination, accurate diagnosis; handheld or security check equipment can be used for airport, station, subway and other security checks, which can detect contraband hidden in luggage, packages; border security checks X-ray examination of vehicle goods to prevent non-physical cross-border transportation. Various phenomena in social development show that small portable X-ray analyzers and handheld X-ray imaging devices used randomly in the field are indispensable.

[0049] Referring to Figures 6-10 The application also provides a solid sealing filling device, which comprises a base 17 for clamping the X-ray imaging device, a moving frame 22 movably arranged on the base 17, a switching disc 23 arranged on the side wall of the moving frame 22, a silicon resin filling mechanism, an epoxy resin filling mechanism and a PEI resin filling mechanism arranged on the side wall of the switching disc 23 in a circumferential direction, wherein the silicon resin filling mechanism is firstly pushed into the shell, the silicon resin 7 is injected into the cathode end area and the high-voltage power supply shell, after solidification, the shielding lead sleeve 9 is sent into the shell by the epoxy resin filling mechanism, the epoxy resin 8 is filled into the interior, finally, the port of the shielding lead sleeve 9 is sealed by the bottom column, the PEI resin 10 is filled into the transmission window part of the anode end, and the solid sealing filling process is automatically completed in sequence.

[0050] Specifically, the silicon resin filling mechanism comprises a rotating disc 30 arranged on the side wall of the switching disc 23, the rotating disc 30 is driven to rotate within a range of 180° by a first motor 38, the side wall of the rotating disc 30 is fixedly connected with a silicon resin injection pipe 28 and an air pipe 29, the distal end of the silicon resin injection pipe 28 and the air pipe 29 is fixedly connected with an annular partition plate 31, the bottom of the annular partition plate 31 is provided with an opening 34 for the high-voltage cable to pass through, the inner wall of the annular partition plate 31 is provided with an annular slot 32 extending to the opening 34, the annular slot 32 is arranged with a sealing air cushion 33 matched with the shape thereof, the air pipe 29 is connected with the sealing air cushion 33, the distal end of the silicon resin injection pipe 28 is in communication with the side wall of the annular partition plate 31, the annular partition plate 31 is pushed into the shell 1, the annular partition plate 31 passes through the anode target assembly 601 with a larger diameter first, 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, finally, the annular partition plate 31 moves to the front side of the cathode assembly 602, the first motor 38 is started to drive the rotating disc 30 to rotate by 180°, the opening 34 is turned to the upper side, the air pipe 29 is used to inflate the sealing air cushion 33, the sealing air cushion 33 inflates to abut against the outer wall of the ceramic tube and close the opening 34, so that the separation and sealing are realized, and the silicon resin 7 is filled into the periphery of the cathode assembly 602 through the silicon resin injection pipe 28.

[0051] The epoxy resin filling mechanism comprises a clamping seat 24 fixedly connected to the side wall of the switching disc 23, a clamping groove 36 for clamping the shielding lead sleeve 9 is arranged at the front end of the clamping seat 24, a clamping sleeve 25 for sealing the clamping sleeve outside the anode target assembly 601 is fixedly arranged in the clamping groove 36, an epoxy resin injection pipe 35 is arranged 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 shell 1, the clamping sleeve 25 is sleeved outside the anode target assembly 601 to realize separation, the epoxy resin 8 is injected into the shielding lead sleeve 9 through the epoxy resin injection pipe 35, and the shielding lead sleeve 9 fills the corresponding cable port 11 and the bottom gap through the strip-shaped port at the bottom.

[0052] The PEI resin filling mechanism comprises a resisting column 27 fixedly connected to the side wall of the switching disc 23, the resisting column 27 is used for sealing the port of the shielding lead sleeve 9, and a PEI resin injection pipe 26 is arranged 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 the PEI resin 10 is injected into the transmission end of the anode target assembly 601 through the PEI resin injection pipe 26.

[0053] In order to realize clamping of the X-ray imaging device, a mounting groove 18 is arranged on the base 17, a double-head cylinder 37 is arranged in the mounting groove 18, clamping plates 19 are fixedly arranged at the two telescopic ends of the double-head cylinder 37, and a pair of clamping plates 19 clamp the high-voltage power supply shell 12, the double-head cylinder 37 is started to drive the pair of clamping plates 19 to clamp the high-voltage power supply shell 12, and then the position of the shell 1 is fixed.

[0054] In order to realize movement of the moving frame 22, a moving groove is arranged 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 arranged at the end of the base 17, the bottom of the moving frame 22 is screw-connected with the threaded rod 20, the second motor 21 is started to drive the threaded rod 20 to rotate, and then the moving frame 22 drives the switching disc 23 to move.

[0055] The high-voltage power shell 12 is placed on the base 17, the double-head cylinder 37 is started to drive a pair of clamping plates 19 to clamp the high-voltage power shell 12, and then the position of the shell 1 is fixed, the second motor 21 is started to drive the threaded rod 20 to rotate, and then the moving frame 22 drives the switching disc 23 to move, the annular partition plate 31 is first pushed into the shell 1, the annular partition plate 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 rotating disc 30 to rotate by 180°, the opening 34 is turned to the upper side, the air pipe 29 is used to fill the air in the sealing air cushion 33, the sealing air cushion 33 is inflated to resist the outer wall of the ceramic tube, and the opening 34 is closed, the separation and sealing are realized, the silicon resin 7 is filled to the periphery of the cathode assembly 602 through the silicon resin injection pipe 28, and flows into the high-voltage power shell 12 through the corresponding cable port 11, the silicon resin 7 is filled, and after the silicon resin 7 is solidified, the annular partition plate 31 is pulled out.

[0056] The switching disc 23 is rotated, the epoxy resin filling mechanism is turned to the position of the shell 1, at this time, the shielding lead sleeve 9 is clamped in the clamping groove 36, is pushed into the shell 1, the sleeve 25 is sleeved on the periphery of the anode target assembly 601, the separation is realized, the epoxy resin 8 is injected into the shielding lead sleeve 9 through the epoxy resin injection pipe 35, and the corresponding cable port 11 and the bottom gap are filled through the strip-shaped port at the bottom of the shielding lead sleeve 9; after the epoxy resin 8 is solidified, the abutting column 27 is pushed to the port of the shielding lead sleeve 9, the PEI resin 10 is injected into the transmission end of the anode target assembly 601 through the PEI resin injection pipe 26, and the solid sealing process can be automatically completed in sequence.

[0057] The above only describes the preferred embodiments of the present application and does not limit the present application, and any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present application shall be included in the protection scope of the present application.

Claims

1. A sealing and filling device for medical X-ray imaging equipment, the sealing and filling device being used for sealing and filling the following X-ray imaging equipment, the X-ray imaging equipment comprising a housing (1), characterized in that: The shell (1) is fixedly installed with an X-ray tube (6), both ends of the X-ray tube (6) are respectively installed with an anode target assembly (601) and a cathode assembly (602), and the anode target assembly (601) and the cathode assembly (602) are connected with a ceramic tube; The anode target assembly (601) comprises a target material and a transmission window, the cathode assembly (602) 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; Both ends of the shell (1) are respectively fixedly installed with a collimator (3) and a baffle (5) corresponding to the anode target assembly (601) and the cathode assembly (602), the center of the collimator (3) is provided with a beam exit (301) corresponding to the transmission window, and the beam exit (301) limits the electron radiation range; The shell (1) is filled with silicon resin (7) wrapping the cathode assembly (602), epoxy resin (8) wrapping the X-ray tube (6) tube body, and PEI resin (10) wrapping the anode target assembly (601), and the epoxy resin (8) is further sleeved with a shielding lead sleeve (9) on the periphery; A high-voltage power supply shell (12) is further fixed at the bottom of the shell (1), a power supply assembly is installed in the high-voltage power supply shell (12), the bottoms of the anode target assembly (601) and the cathode assembly (602) are electrically connected with the power supply assembly through high-voltage cables, and the high-voltage power supply shell (12) is filled with silicon resin (7); The medical X-ray imaging equipment is filled by using a sealing and filling device, which comprises a base (17) for clamping the X-ray imaging equipment, a movable frame (22) movably arranged on the base (17), a switching disc (23) arranged on the side wall of the movable frame (22), and a silicon resin filling mechanism, an epoxy resin filling mechanism and a PEI resin filling mechanism arranged on the side wall of the switching disc (23) in a circumferential direction; The epoxy resin filling mechanism comprises a clamping seat (24) fixedly connected to the side wall of the switching disc (23), a clamping groove (36) for clamping the shielding lead sleeve (9) is arranged at the front end of the clamping seat (24), a clamping sleeve (25) for sealing the clamping sleeve around the anode target assembly (601) is fixedly installed in the clamping groove (36), and an epoxy resin injection pipe (35) is arranged at the inner bottom of the clamping groove (36) outside the clamping sleeve (25).

2. The medical X-ray imaging apparatus according to claim 1, wherein The power supply assembly comprises 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), and the high-voltage voltage doubling rectifier unit is a voltage doubler rectifier (15).

3. The medical X-ray imaging apparatus according to claim 2, wherein The high-voltage power shell (12) is also provided with a filament transformer (14) and a voltage-boosting rectifier transformer (16), and a controller (13) is installed on the top of the high-voltage power shell (12), the two rows of voltage-boosting rectifiers (15) are electrically connected to the voltage-boosting rectifier transformer (16), and the filament transformer (14) and the voltage-boosting rectifier transformer (16) are located between the two rows of voltage-boosting rectifiers (15).

4. The medical X-ray imaging apparatus according to claim 1, wherein The shell (1) is provided with heat dissipation fins (4) on both sides, and a temperature test paper (2) is installed on the top of the shell (1), and a pair of cable ports (11) are arranged on the bottom of the shell (1) and are in communication with the high-voltage power shell (12) and are used for passing high-voltage cables, and the cable ports (11) are opposite to the anode target assembly (601) and the cathode assembly (602).

5. The medical X-ray imaging apparatus according to claim 2, wherein The two rows of high-voltage voltage-boosting rectifier units are arranged at an angle of 25°-35° with the direction of the high-voltage power shell (12).

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

7. The medical X-ray imaging apparatus according to claim 1, wherein The silicon resin filling mechanism comprises a rotating disc (30) installed on the side wall of the switching disc (23), the rotating disc (30) is driven to rotate within a range of 180° by a first motor (38), the side wall of the rotating disc (30) is fixedly connected with a silicon resin injection pipe (28) and an air pipe (29), the ends of the silicon resin injection pipe (28) and the air pipe (29) are fixedly connected with an annular partition plate (31), the bottom of the annular partition plate (31) is provided with an opening (34) for passing high-voltage cables, and the inner wall of the annular partition plate (31) is provided with an annular slot (32) extending to the opening (34), the annular slot (32) is provided with a sealing air cushion (33) matched with the shape of the annular slot (32), the air pipe (29) is connected with the sealing air cushion (33), and the end of the silicon resin injection pipe (28) is in communication with the side wall of the annular partition plate (31).

8. The medical X-ray imaging apparatus according to claim 1, wherein The PEI resin filling mechanism comprises a resisting column (27) fixed on the side wall of the switching disc (23), the resisting column (27) is used for sealing the port of the shielding lead sleeve (9), and the resisting column (27) is provided with a PEI resin injection pipe (26).

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