CN109192644B - Medical X-ray tube with internal cooling ball bearing - Google Patents
Medical X-ray tube with internal cooling ball bearing Download PDFInfo
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- CN109192644B CN109192644B CN201810825060.5A CN201810825060A CN109192644B CN 109192644 B CN109192644 B CN 109192644B CN 201810825060 A CN201810825060 A CN 201810825060A CN 109192644 B CN109192644 B CN 109192644B
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/02—Details
- H01J35/04—Electrodes ; Mutual position thereof; Constructional adaptations therefor
- H01J35/08—Anodes; Anti cathodes
- H01J35/10—Rotary anodes; Arrangements for rotating anodes; Cooling rotary anodes
- H01J35/101—Arrangements for rotating anodes, e.g. supporting means, means for greasing, means for sealing the axle or means for shielding or protecting the driving
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/02—Details
- H01J35/04—Electrodes ; Mutual position thereof; Constructional adaptations therefor
- H01J35/08—Anodes; Anti cathodes
- H01J35/10—Rotary anodes; Arrangements for rotating anodes; Cooling rotary anodes
- H01J35/105—Cooling of rotating anodes, e.g. heat emitting layers or structures
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J35/00—X-ray tubes
- H01J35/24—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof
- H01J35/26—Tubes wherein the point of impact of the cathode ray on the anode or anticathode is movable relative to the surface thereof by rotation of the anode or anticathode
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J2235/00—X-ray tubes
- H01J2235/10—Drive means for anode (target) substrate
- H01J2235/1046—Bearings and bearing contact surfaces
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J2235/00—X-ray tubes
- H01J2235/12—Cooling
- H01J2235/1204—Cooling of the anode
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Abstract
The invention discloses an internal cooling ball bearing medical X-ray tube, which belongs to the technical field of medical detection and ray metering detection and comprises a target disc, a support ring, a rotor molybdenum rod, a rotor copper sleeve, a rotor iron seat, anode corrugated ceramic and a hollow bearing. The invention provides a solution for realizing a high heat capacity X-ray tube of 5MHU and above by combining a hollow target disc, a hollow bearing system, an anode corrugated ceramic structure and a novel internal cooling ball bearing medical X-ray tube in a target disc fixing mode; the heat of the hollow target disc is directly transmitted to the rotor copper sleeve through the cavity by the structural design of the hollow target disc; the design of the hollow shaft sleeve can directly cool the cooling oil into the shaft sleeve; the design of the anode corrugated ceramic, the heat of the rotor copper sleeve can be radiated to the anode corrugated ceramic and then is conducted to cooling oil through the anode corrugated ceramic; the design of the new anode target disk fixing mode improves the reliability of the high-speed rotation process.
Description
Technical Field
The invention belongs to the technical field of medical detection and ray metering detection, and particularly relates to an internal cooling ball bearing medical X-ray tube.
Background
The X-ray tube is mainly used for medical equipment such as an X-ray machine, a CT machine and the like, and generates X-rays under the action of external high pressure so as to be used for diagnosing or treating a patient by a doctor.
The mechanism by which X-rays are generated by an X-ray tube is generally as follows: the filament (cathode) of the X-ray tube is heated, and free electrons escape from the filament surface to form an electron cloud. Under the condition of applying high voltage (40-150 kilovolts generally) between the cathode and the anode of the X-ray tube, electrons at the filament fly to a target disc (anode) at a high speed, and X-rays are generated after striking the anode target disc and are output through a ray window. As described above, in this energy conversion process, only 1% of the kinetic energy of electrons is converted into X-rays, and the remaining 99% of the kinetic energy is converted into heat energy, which is transferred to the outside of the X-ray tube by heat radiation or heat conduction, and is carried away by the X-ray tube housing and the X-ray tube radiator. Specifically, the method comprises the following steps: (1) One part of the heat (accounting for 90% of the total heat) of the target disk is radiated to the metal shell in the middle of the X-ray tube, the other part is radiated to the outside of the X-ray tube through glass shells at two ends or other materials, and the last part is taken away through the rotor copper sleeve. Wherein the maximum amount of heat radiated to the metal shell is about 60%, the amount of heat radiated through the glass is about 20%, and the amount of heat carried away through the rotor copper sleeve is about 20%. (2) The heat of the cathode (10% of the total heat) is carried away through the cathode glass and metal casing.
In the use process, only 1% of energy of the X-ray tube is converted into X-rays, and the rest 99% is converted into heat energy, so that rapid heat dissipation is required. Therefore, the thermal management of an X-ray tube is one of the key factors affecting its reliability and lifetime.
As shown in fig. 5, in the prior art, since the temperature of the target disk can reach more than 1000 degrees during operation, the temperature of heat conducted to the shaft lever of the ball bearing is more than 500 degrees, and the shaft lever can only conduct heat to the insulating oil through the shaft sleeve, resulting in low heat dissipation efficiency.
In the prior art, the X-ray tube has the following defects in the heat dissipation process:
1. the anode has limited heat capacity;
2. the requirements on bearing materials are high;
3. the bearing life is limited;
4. in the high-speed rotation process of the target disc, the fixed position deviation and the falling risk are high.
The reasons for this conclusion are as follows:
1. in the existing X-ray tube design, the anode of the high-voltage generator is connected with the target disc through threads on the ball bearing, and the structure limits the heat dissipation efficiency of the ball bearing; meanwhile, the target disk can reach high temperature of 1100 ℃ in operation, heat is conducted to the iron seat through the molybdenum rod and then to the shaft rod, then is conducted to the outer ring of the bearing through the balls, and the outer ring is conducted to the shaft sleeve and is taken away by insulating oil. It follows that the path of heat conduction and dissipation is very long. The constraint condition leads to that the heat capacity of the anode can only be 3.5MHU or below, and is not suitable for the X-ray tube with the large heat capacity of 5MHU or above;
2. in the existing X-ray tube design, the heat of the target disk is conducted to the shaft lever, but the highest allowable working temperature of the shaft lever is not higher than 550 ℃, so that the shaft lever flange is generally made of a material with extremely low heat conductivity, and the bearing is quite high in manufacturing cost;
3. because the shaft lever works at about 500 ℃ for a long time, the working temperature of the outer ring of the bearing cannot be lower than 350 ℃ (note: the temperature difference between the inner side and the outer side of the bearing in the radial thrust structure cannot exceed 150 DEG, otherwise, the inner and outer raceways of the bearing are easy to deform to cause the clamping shaft), and the temperature of the outer ring of the bearing can only meet the most basic temperature requirement (maintained at about 350 ℃), so that the service life of the bearing is reduced;
4. in the existing X-ray tube design, the target disc fixing mode is a single-thread fixing mode, the specific structure is shown in fig. 1, and as the rotating speed of the anode target disc in operation can reach 10800RPM, the threads are possibly loosened in a high-speed working state, and the existing solution is that: (1) The target disc and the rotor copper sleeve are fixed by adopting single threads, and then are welded by adopting high-temperature solder at 1600 ℃, so that the scheme has high cost and needs to be put into electron beam welding equipment; (2) The target disc and the rotor copper sleeve are fixed by adopting molybdenum nuts, and the molybdenum nuts and the rotor copper sleeve are riveted mechanically, so that the scheme has poor reliability, the target disc is easy to fall off when rotating at a high speed, and the safety risk exists; (3) The target disc and the rotor copper sleeve are fixed by adopting molybdenum nuts, and the molybdenum nuts and the rotor copper sleeve are connected by tantalum gaskets, so that the cost is increased, and the looseness can be caused when the rotor copper sleeve rotates at a high speed, so that the image quality is affected.
Disclosure of Invention
The invention aims to: in order to overcome the defects, the invention aims to provide the medical X-ray tube with the internal cooling ball bearing, and solves the problem of heat dissipation of the X-ray tube.
The technical scheme is as follows: the utility model provides a medical X-ray tube of inside cooling ball bearing, includes target dish, support ring, rotor molybdenum stick, rotor copper sheathing, rotor iron seat, positive pole ripple pottery and hollow bearing, the target dish is connected with the support ring, the support ring is connected with the rotor molybdenum stick, the rotor molybdenum stick is connected with the rotor iron seat, the rotor copper sheathing is established on the outer wall of rotor iron seat, the outside at the rotor copper sheathing is established to positive pole ripple pottery cover, hollow bearing sets up in rotor molybdenum stick and rotor iron seat. The invention provides a solution for realizing a high heat capacity X-ray tube of 5MHU and above by combining a hollow target disc, a hollow bearing system, an anode corrugated ceramic structure and a novel internal cooling ball bearing medical X-ray tube in a target disc fixing mode; the heat of the hollow target disc is directly transmitted to the rotor copper sleeve through the cavity by the structural design of the hollow target disc; the design of the hollow shaft sleeve can directly cool the cooling oil into the shaft sleeve; the design of the anode corrugated ceramic, the heat of the rotor copper sleeve can be radiated to the anode corrugated ceramic and then is conducted to cooling oil through the anode corrugated ceramic; the design of the new anode target disk fixing mode improves the reliability of the high-speed rotation process.
Further, the medical X-ray tube with the internal cooling ball bearing comprises target disc graphite, TZM and a rhenium tungsten layer, wherein the inside of the target disc graphite, the TZM and the rhenium tungsten layer are of hollow structures, the TZM and the rhenium tungsten layer are arranged on the left end face of the target disc graphite, the left end face of the supporting ring is attached to the right end face of the TZM and the rhenium tungsten layer, and the left end part of the supporting ring is arranged in an inner cavity of the target disc graphite. TZM, graphite and holding ring pass through high temperature welding mode and connect, and the holding ring passes through screw and rotor connection, and the target disc heat can only be through holding ring heat conduction to the rotor when not considering the radiation like this, and the bearing can not directly bear the high temperature of target disc, can improve bearing reliability effectively.
Further, the medical X-ray tube with the internal cooling ball bearing comprises a hollow shaft sleeve, a bearing outer ring, a bearing middle ring, a bearing outer ring and a shaft rod, wherein one end of the shaft rod is arranged in the hollow shaft sleeve, the bearing outer ring, the bearing middle ring and the bearing outer ring are arranged between the outer wall of the shaft rod and the inner wall of the hollow shaft sleeve, the bearing middle ring is arranged between the bearing outer ring and the bearing outer ring, and a transition ring is arranged between the bearing middle ring and the bearing outer ring. The heat of the target disk is less conducted to the shaft lever and then conducted to the shaft sleeve, and the heat is taken away by cooling oil, so that the reliability of the bearing can be improved.
Furthermore, the medical X-ray tube with the internal cooling ball bearing is characterized in that a cavity is arranged at one end, far away from the shaft rod, of the hollow bearing. The cooling liquid can enter the cavity, so that the heat dissipation performance is improved.
Furthermore, in the medical X-ray tube with the internal cooling ball bearing, the end part of the shaft rod, which is close to the target disc, is provided with the bearing flange. And a bearing flange is arranged to connect the hollow bearing with the rotor molybdenum rod.
Furthermore, in the internal cooling ball bearing medical X-ray tube, a group of ceramic waves are arranged on the outer wall of the anode corrugated ceramic. The surface area of the anode ceramic is increased, the heat radiation capacity of the anode ceramic is improved, the heat radiated to the anode ceramic by the rotor copper sleeve can be rapidly conducted to cooling oil through the anode corrugated ceramic, so that a part of the heat of the target disc is conducted to the cooling oil through the metal shell, and a part of the heat is conducted to the cooling oil through the anode ceramic, and the heat of the bearing can be overcome during operation.
Further, in the internal cooling ball bearing medical X-ray tube, the end part of the anode corrugated ceramic, which is close to the target disc, is provided with the anode kovar, and the end part of the anode corrugated ceramic, which is far away from the target disc, is provided with the anode kovar. The anode large kovar and the anode small kovar are welded with the anode corrugated ceramic end seal, and the corrugated ceramic and end seal structure can ensure the coaxiality of the whole pipe, reduce the mechanical stress between the insulating material and the metal and strengthen the mechanical strength.
Furthermore, in the medical X-ray tube with the internal cooling ball bearing, the target disc, the supporting ring and the rotor copper sleeve are connected through 3-6 screws.
Furthermore, the internal cooling ball bearing medical X-ray tube is characterized in that the rotor copper sleeve and the hollow bearing are fixed through 6-12 screws.
Further, in the internal cooling ball bearing medical X-ray tube, the screw is made of stainless steel material and is fixed through fusion spot welding. The novel anode target plate fixing mode is adopted, the single thread fixing mode in the prior art can be improved through the fixation of a plurality of screws, wherein 3-6 screws are adopted for fixing the target plate, the supporting ring and the rotor copper sleeve, 6-12 screws are adopted for fixing the rotor copper sleeve and the hollow bearing, argon arc welding fusion spot welding is adopted, no other process is needed for realizing high-speed rotation 10800rpm of the target plate, and the reliability is extremely high.
The technical scheme can be seen that the invention has the following beneficial effects: the internal cooling ball bearing medical X-ray tube has the following advantages:
1. the reliability of the X-ray tube in the high-speed rotation state is improved: the support ring is connected with the 6 screws of the rotor copper bush and the bearing is connected with the 6 screws of the rotor copper bush, so that a single fixing mode is avoided, and the loosening risk of the target disc during high-speed rotation is reduced;
2. the service life of the bearing and the reliability of the product are improved: the heat of the target disk is not directly conducted to the bearing, so that the bearing can work at low temperature and cannot be overheated and deformed;
3. increasing the insulation strength: the corrugated ceramic structure is adopted, so that the creepage distance of the surface can be increased, namely the insulation strength is increased;
4. increase the mechanical strength of the whole pipe: the corrugated ceramic and the end sealing structure are adopted, so that the coaxiality of the whole pipe can be ensured, the mechanical stress between the insulating material and the metal is reduced, and the mechanical strength is increased;
5. improving the capability of bearing secondary electron bombardment: ceramics can withstand 1400 degrees of high temperature and can withstand secondary electron bombardment much more than glass, thus improving the life of the X-ray tube.
In summary, the technical solution of the X-ray tube can effectively improve the heat dissipation capability of the target disc, improve the bearing reliability, and enable the heat capacity of the anode to be 5MHU or more.
Drawings
FIG. 1 is a schematic view of the structure of an internally cooled ball bearing medical X-ray tube according to the present invention;
FIG. 2 is a schematic view of the structure of a hollow target disk according to the present invention;
FIG. 3 is a schematic view of a hollow bearing according to the present invention;
FIG. 4 is a schematic structural view of an anode corrugated ceramic according to the present invention;
fig. 5 is a schematic view of a prior art X-ray tube according to the present invention;
FIG. 6 is a schematic view of a heat sink structure of a target disk and hollow bearing according to the present invention;
fig. 7 is a partial enlarged view of fig. 6.
In the figure: target disk 1, support ring 2, rotor molybdenum rod 3, rotor copper sleeve 4, rotor iron seat 5, anode corrugated ceramic 6, hollow bearing 7, target disk graphite 8, TZM and rhenium tungsten layer 9, hollow shaft sleeve 10, bearing outer ring 11, bearing middle ring 12, bearing outer ring lower 13, shaft rod 14, cavity 15, bearing flange 16, ceramic corrugation 17, anode large kovar 18, anode small kovar 19, screw 20, transition ring 21, target disk one 101, anode glass shell one 102, rotor copper sleeve one 103, bearing sleeve one 104, shaft rod one 105, shaft sleeve thread one 106.
Detailed Description
Embodiments of the present invention are described in detail below, examples of which are illustrated in the accompanying drawings, wherein like or similar reference numerals refer to like or similar elements or elements having like or similar functions throughout. The embodiments described below by referring to the drawings are illustrative and intended to explain the present invention and should not be construed as limiting the invention.
In the description of the present invention, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "clockwise", "counterclockwise", etc. indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings are merely for convenience in describing the present invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, be configured and operated in a specific orientation, and thus should not be construed as limiting the present invention.
Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include one or more such feature. In the description of the present invention, unless otherwise specified, the meaning of "a plurality" is two or more, unless otherwise clearly defined.
In the present invention, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly and may be, for example, fixedly connected, detachably connected, or integrally connected; can be mechanically or electrically connected; can be directly connected or indirectly connected through an intermediate medium, and can be communication between two elements. The specific meaning of the above terms in the present invention can be understood by those of ordinary skill in the art according to the specific circumstances.
In the present invention, unless expressly stated or limited otherwise, a first feature "above" or "below" a second feature may include both the first and second features being in direct contact, as well as the first and second features not being in direct contact but being in contact with each other through additional features therebetween. Moreover, a first feature being "above," "over" and "on" a second feature includes the first feature being directly above and obliquely above the second feature, or simply indicating that the first feature is higher in level than the second feature. The first feature being "under", "below" and "beneath" the second feature includes the first feature being directly under and obliquely below the second feature, or simply means that the first feature is less level than the second feature.
Examples
The medical X-ray tube with the internal cooling ball bearing comprises a target disc 1, a supporting ring 2, a rotor molybdenum rod 3, a rotor copper sleeve 4, a rotor iron seat 5, anode corrugated ceramics 6 and a hollow bearing 7, wherein the target disc 1 is connected with the supporting ring 2, the supporting ring 2 is connected with the rotor molybdenum rod 3, the rotor molybdenum rod 3 is connected with the rotor iron seat 5, the rotor copper sleeve 4 is sleeved on the outer wall of the rotor iron seat 5, the anode corrugated ceramics 6 is sleeved outside the rotor copper sleeve 4, and the hollow bearing 7 is arranged in the rotor molybdenum rod 3 and the rotor iron seat 5.
The target disk 1 shown in fig. 2 comprises target disk graphite 8, TZM and a rhenium tungsten layer 9, wherein the interiors of the target disk graphite 8, the TZM and the rhenium tungsten layer 9 are hollow structures, the TZM and the rhenium tungsten layer 9 are arranged on the left end face of the target disk graphite 8, the left end face of the support ring 2 is attached to the right end face of the TZM and the rhenium tungsten layer 9, and the left end part of the support ring 2 is arranged in an inner cavity of the target disk graphite 8. The hollow target plate structure is designed: TZM of the rhenium tungsten layer, graphite and the supporting ring are integrated through a high-temperature welding process, and molybdenum or TZM is adopted as a supporting ring material.
The hollow bearing 7 shown in fig. 3 comprises a hollow shaft sleeve 10, a bearing outer ring 11, a bearing middle ring 12, a bearing outer ring lower 13 and a shaft rod 14, wherein one end of the shaft rod 14 is arranged in the hollow shaft sleeve 10, the bearing outer ring 11, the bearing middle ring 12 and the bearing outer ring lower 13 are arranged between the outer wall of the shaft rod 14 and the inner wall of the hollow shaft sleeve 10, the bearing middle ring 12 is arranged between the bearing outer ring 11 and the bearing outer ring lower 13, and a transition ring 21 is arranged between the bearing middle ring 12 and the bearing outer ring lower 13. A cavity 15 is arranged at the end of the hollow bearing 7 away from the shaft lever 14. The end of the shaft 14 near the target disk 1 is provided with a bearing flange 16. The design scheme of the hollow bearing is as follows: mainly, the hollow shaft sleeve 10 is designed, the specific design structure is shown in fig. 3, and the cooling oil can be directly cooled to the shaft sleeve.
The design of the above-mentioned target disk 1 and hollow bearing 7 as shown in fig. 6 and 7 makes the path of heat generated by the target disk 1 transferred to the hollow bearing 7 and shaft 14 longer, and can effectively reduce the temperature at the hollow bearing 7 and shaft 14, and its specific heat dissipation principle is: the target disk 1 generates heat, because the target disk 1 is a hollow target disk, the target disk 1 and the rotor molybdenum rod 3 are of a non-fitting structure, therefore, the heat can only be transferred to the rotor molybdenum rod 3 along the target disk 1 until the screw at the joint of the target disk 1 and the rotor molybdenum rod 3 transfers heat to the rotor molybdenum rod 3 along the rotor molybdenum rod 3 towards the direction close to the target disk 1, the heat reaches the joint screw of the rotor molybdenum rod 3 and the hollow bearing 7, and the heat is transferred to the hollow bearing 7 through the screw, the heat transfer path of the structure is greatly prolonged, and the outer wall of the hollow shaft sleeve 10 is directly contacted with cooling oil, so that the temperature is greatly reduced when the heat is transferred to the hollow bearing 7, the structure has a good cooling effect, and the normal use of the hollow bearing 7 can be ensured, and the service life is prolonged.
The outer wall of the anode corrugated ceramic 6 as shown in fig. 4 is provided with a set of ceramic corrugations 17. The end of the anode corrugated ceramic 6, which is close to the target disc 1, is provided with an anode large kovar 18, and the end of the anode corrugated ceramic 6, which is far away from the target disc 1, is provided with an anode small kovar 19. Anode corrugated ceramic design: the anode adopts corrugated ceramic, the ceramic adopts 95%, 97% and 99% alumina industrial ceramic, any shape corrugation or transverse groove is opened on the inner and outer surfaces of the ceramic, the sealing structure of the corrugated ceramic and the kovar adopts end sealing, flat sealing, sleeve sealing and clamping sealing, wherein the clamping sealing can be metal or ceramic.
The anode target plate is fixed by a plurality of screws: the target disk 1, the support ring 2 and the rotor copper sleeve 4 are connected through 3-6 screws 20. The rotor copper bush 4 and the hollow bearing 7 are fixed by 6-12 screws 20. The screw 20 is made of stainless steel material and is fixed by fusion spot welding. Anode target plate several screw fixing modes: the anode target disk is connected with a rotor copper sleeve through 6-12 screws, the rotor copper sleeve is connected with a bearing through 3-6 screws, and all fixing screws are made of stainless steel materials in a fusion spot welding mode.
The embodiments of the present invention compared to the prior art are as follows:
the invention mainly adopts a hollow target disc structure, and the specific implementation scheme is as follows: high-temperature welding of a hollow target disc, twice welding of a rotor copper sleeve, integrated assembly of a bearing, assembly of the hollow target disc and the rotor copper sleeve, integrated assembly of the bearing, dynamic balance and corrugated ceramic argon arc welding; high-temperature brazing and argon arc welding processes of a vacuum furnace are needed.
The foregoing is merely a preferred embodiment of the invention, and it should be noted that modifications could be made by those skilled in the art without departing from the principles of the invention, which modifications would also be considered to be within the scope of the invention.
Claims (6)
1. An internally cooled ball bearing medical X-ray tube, characterized by: the novel high-efficiency high-voltage power supply comprises a target disc (1), a supporting ring (2), a rotor molybdenum rod (3), a rotor copper sleeve (4), a rotor iron seat (5), anode corrugated ceramics (6) and a hollow bearing (7), wherein the target disc (1) is connected with the supporting ring (2), the supporting ring (2) is connected with the rotor molybdenum rod (3), the rotor molybdenum rod (3) is connected with the rotor iron seat (5), the rotor copper sleeve (4) is sleeved on the outer wall of the rotor iron seat (5), the anode corrugated ceramics (6) is sleeved outside the rotor copper sleeve (4), and the hollow bearing (7) is arranged in the rotor molybdenum rod (3) and the rotor iron seat (5);
the target disc (1) is a hollow target disc, and the target disc (1) is connected with the support ring (2) and the rotor copper sleeve (4) through 3-6 screws (20); the rotor copper sleeve (4) and the hollow bearing (7) are fixed through 6-12 screws (20);
the hollow bearing (7) comprises a hollow shaft sleeve (10), a bearing outer ring (11), a bearing middle ring (12), a lower bearing outer ring (13) and a shaft rod (14), one end of the shaft rod (14) is arranged in the hollow shaft sleeve (10), the bearing outer ring (11), the bearing middle ring (12) and the lower bearing outer ring (13) are arranged between the outer wall of the shaft rod (14) and the inner wall of the hollow shaft sleeve (10), the bearing middle ring (12) is arranged between the bearing outer ring (11) and the lower bearing outer ring (13), and a transition ring (21) is arranged between the bearing middle ring (12) and the lower bearing outer ring (13); one end of the hollow bearing (7) far away from the shaft lever (14) is provided with a cavity (15).
2. The internally cooled ball bearing medical X-ray tube according to claim 1, wherein: target dish (1) are including target dish graphite (8) and TZM and rhenium tungsten layer (9), the inside hollow structure that is of target dish graphite (8) and TZM and rhenium tungsten layer (9), TZM and rhenium tungsten layer (9) set up on the left end face of target dish graphite (8), the left end face of support ring (2) is laminated with the right-hand member face on TZM and rhenium tungsten layer (9) to in the inner cavity of target dish graphite (8) is arranged in to the left end portion of support ring (2).
3. The internally cooled ball bearing medical X-ray tube according to claim 1, wherein: the end of the shaft lever (14) close to the target disc (1) is provided with a bearing flange (16).
4. The internally cooled ball bearing medical X-ray tube according to claim 1, wherein: the outer wall of the anode corrugated ceramic (6) is provided with a group of ceramic corrugations (17).
5. The internally cooled ball bearing medical X-ray tube according to claim 4, wherein: the end of the anode corrugated ceramic (6) close to the target disc (1) is provided with an anode big kovar (18), and the end of the anode corrugated ceramic (6) far away from the target disc (1) is provided with an anode small kovar (19).
6. The internally cooled ball bearing medical X-ray tube according to claim 1, wherein: the screw (20) is made of stainless steel material and is fixed through fusion spot welding.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
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| CN201810825060.5A CN109192644B (en) | 2018-07-25 | 2018-07-25 | Medical X-ray tube with internal cooling ball bearing |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201810825060.5A CN109192644B (en) | 2018-07-25 | 2018-07-25 | Medical X-ray tube with internal cooling ball bearing |
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| CN109192644A CN109192644A (en) | 2019-01-11 |
| CN109192644B true CN109192644B (en) | 2023-09-01 |
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| CN112582242A (en) * | 2020-12-28 | 2021-03-30 | 思柯拉特医疗科技（苏州）有限公司 | Liquid metal bearing medical X-ray tube |
| CN113001002A (en) * | 2021-03-30 | 2021-06-22 | 杭州凯龙医疗器械有限公司 | Fixing method for CT tube target disc and rotor copper sleeve |
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