JP5405178B2 - Rotating anode type X-ray tube device - Google Patents

Description

  The present invention relates to a rotary anode type X-ray tube apparatus.

  X-ray tube devices are used in medical diagnostic equipment and the like. The X-ray tube device includes a housing, an X-ray tube accommodated in the housing, and an insulating oil filled between the X-ray tube and the inner surface of the housing. X-rays radiated from the X-ray tube are taken out from an X-ray emission port provided in the housing and used.

Of the X-rays emitted from the X-ray tube, if the X-rays emitted in directions other than the emission port are not shielded, they are emitted as X-rays that are not used outside the housing, and the human body is unnecessarily exposed. The danger of doing. For this reason, it is necessary to shield the X-rays radiated in directions other than the radiation opening inside the housing. Generally, X-ray shielding is realized by attaching a lead plate having a thickness of 1 mm to 3 mm to the inner surface of a housing (see, for example, Patent Document 1).
Moreover, the technique using the X-ray shielding material instead of lead is also disclosed (for example, refer to Patent Documents 2 to 4).

US Patent No. 70000662 US Pat. No. 6,494,618 JP 2008-73539 A JP 2007-212304 A

  Incidentally, the inner surface of the housing is composed of many curved surfaces. The work of attaching the lead plate to the inner surface of the housing without any gap is very skillful. For this reason, in the case of providing the X-ray tube apparatus at a lower cost by reducing the manufacturing cost, the above-described pasting work is the biggest bottleneck.

  In recent years, in order to avoid the risk that lead gives to the environment, lead-substitute X-ray shielding materials are becoming widespread. The X-ray shielding material is a material in which an X-ray opaque material is mixed with a plastic material intended for molding.

However, it is very difficult to mold using the X-ray shielding material instead of the lead plate. This is because, in order to obtain an X-ray shielding ability equivalent to that of a lead plate with a thickness of 1 mm to 3 mm, it is necessary to form nearly 80% by volume of the X-ray shielding material with an X-ray opaque material. In this case, the fluidity of the X-ray shielding material during mold molding is extremely deteriorated, and the structural strength of the molded X-ray shielding material is further reduced. For this reason, the lead-substituting X-ray shielding material is only applied to the manufacture of relatively small parts and sheet materials.
The present invention has been made in view of the above points, and an object thereof is to provide a rotary anode type X-ray tube apparatus capable of reducing the manufacturing cost.

In order to solve the above-described problem, a rotary anode X-ray tube apparatus according to an aspect of the present invention includes:
A cathode for emitting electrons, an anode target that emits X-rays by being collision to the emitted electron from the cathode, and the vacuum envelope which houses at least the cathode and anode target, the anode target An X-ray tube having a rotating body fixed and rotatably provided together with the anode target; and a fixing body that rotatably supports the rotating body;
A rotation driving device for rotating the rotating body;
A housing formed of a material mainly composed of a solid resin material and containing at least the vacuum envelope;
X-ray transmission that is fixed to at least one of the vacuum envelope and the housing, is located between the vacuum envelope and the housing, is provided with a gap between the vacuum envelope and the housing, and transmits the X-ray. An X-ray shield with a window;
And a coolant that fills the space between the X-ray tube and the housing, including between the vacuum envelope and the X-ray shield, and between the X-ray shield and the housing.

  According to the present invention, it is possible to provide a rotary anode type X-ray tube apparatus that can reduce the manufacturing cost.

It is a longitudinal section showing a rotating anode type X-ray tube device concerning an embodiment of the invention.

  Hereinafter, a rotary anode X-ray tube apparatus according to an embodiment of the present invention will be described in detail with reference to the drawings. FIG. 1 is a longitudinal sectional view showing an X-ray tube apparatus 10 according to an embodiment of the present invention.

  As shown in FIG. 1, the X-ray tube device 10 includes a cylindrical housing 20, an X-ray tube 30 accommodated in the housing 20, and the inside of the housing 20 filled between the X-ray tube 30 and the housing 20. The coolant 7 satisfying the above condition and a stator coil 910 as a rotational drive device are provided. The housing 20 is provided with a rubber bellows 21 to adjust the pressure of the coolant 7. The housing 20 has a radiation window 24 that emits X-rays to the outside of the housing 20.

Except for the radiation window 24, the housing 20 is formed as follows.
The housing 20 is formed of a material mainly composed of a solid resin material. Solid resin material is at least thermosetting epoxy resin, unsaturated polyester resin, phenol resin, diallyl phthalate resin, thermoplastic epoxy resin, nylon resin, aromatic nylon resin, polybutylene terephthalate resin, polyethylene terephthalate resin, polyphenylene sulfide resin , Polyphenylene ether resin, liquid crystal polymer, and methylpentene polymer resin.

  It is more preferable that the housing 20 further includes a reinforcing fiber in addition to a solid resin material because the strength is increased. In this case, glass fiber, carbon fiber, boron fiber, alumina fiber, and aramid fiber can be selected as the reinforcing fiber.

  The thickness of the housing 20 is 3 to 10 mm. In this embodiment, the thickness of the housing 20 is 8 mm. A lead plate is not attached to the inner surface of the housing 20. The inner surface of the housing 20 is in contact with the coolant 7.

  The X-ray tube 30 includes a vacuum envelope 31. The vacuum envelope 31 includes a vacuum container 32 made of glass, a high voltage insulating member 40, and a high voltage insulating member 50. An anode 35 is indirectly attached to the high voltage insulating member 40, and a cathode 36 is indirectly attached to the high voltage insulating member 50. The cathode 36 emits electrons for irradiating the anode 35. The anode 35 and the cathode 36 are accommodated in a vacuum envelope 31.

  The anode 35 has an anode target 35a and a support 35c. The anode target 35a is formed in a disc shape. The anode target 35a has a target layer 35b provided on a part of the outer surface of the anode target. The target layer 35b emits X-rays when electrons emitted from the cathode 36 collide. The support 35c supports the anode target 35a. The support 35c is formed integrally with the anode target 35a. The anode 35 is made of a metal such as a tungsten alloy. The anode 35 can rotate around the tube axis. A relatively positive voltage is applied to the anode 35.

  A voltage supply terminal 54 is connected to the cathode 36. The voltage supply terminal 54 applies a relatively negative voltage to the cathode 36 and supplies current to a filament (not shown) of the cathode 36.

  The X-ray tube 30 includes a rotor 920, a bearing 930, a fixed body 1, and a rotating body 2. The fixed body 1 is formed in a cylindrical shape and is fixed to the high voltage insulating member 40. The fixed body 1 supports the rotating body 2 in a rotatable manner. The rotating body 2 is formed in a cylindrical shape and is provided coaxially with the fixed body 1. A rotor 920 is attached to the outer surface of the rotating body 2. A support 35 c is fixed to the rotating body 2. The rotating body 2 is rotatably provided with the anode 35.

  The high voltage insulating member 40 forms a part of the vacuum envelope 31. The high voltage insulating member 40 is formed by a cylindrical portion 46 and a bottom portion 47 that closes one end side of the cylindrical portion 46. The high voltage insulating member 40 includes an external end surface 41 exposed to the outside of the housing 20, a cooling surface 43 in contact with the coolant 7, and a mounting surface that is positioned inside the vacuum envelope 31 and to which the anode 35 is indirectly attached. 42. In this embodiment, the outer end surface 41 is a flat surface.

  Inside the high voltage insulating member 40, a voltage supply terminal 44 connected to the anode 35 and led out to the external end face 41 side is provided. In this embodiment, the voltage supply terminal 44 is a high voltage supply terminal. The voltage supply terminal 44 is provided through the outer end face 41 and supplies a high voltage to the anode 35 attached to the high voltage insulating member 40.

  The high voltage insulating member 50 forms a part of the vacuum envelope 31. The high voltage insulating member 50 is formed of a cylindrical portion 56 and a bottom portion 57 that closes one end side of the cylindrical portion 56. The high voltage insulating member 50 includes an external end surface 51 exposed to the outside of the housing 20, a cooling surface 53 in contact with the coolant 7, and a mounting surface that is located inside the vacuum envelope 31 and to which the cathode 36 is indirectly attached. 52. In this embodiment, the outer end surface 51 is a flat surface.

  Inside the high voltage insulating member 50, a voltage supply terminal 54 connected to the cathode 36 and leading to the external end face 51 side is provided. In this embodiment, the voltage supply terminal 54 is a high voltage supply terminal. The voltage supply terminal 54 is provided through the outer end face 51 and supplies a high voltage to the cathode 36 attached to the high voltage insulating member 50. The voltage supply terminal 54 is supported by a KOV member 55 that is a low expansion alloy. Between the KOV member 55 and the cathode 36 and between the KOV member 55 and the high voltage insulating member 50 are brazed.

  The high-voltage connector 100 includes a bottomed cylindrical housing 101, a cable 102 having a tip inserted into the housing 101, and the housing 101 filled with the terminal 102a of the cable 102 facing the opening side of the housing 101. And a fixed portion 103 made of an epoxy resin material and a silicone plate 104 made of a silicone resin material inserted between the fixed portion 103 and the outer end face 41 of the bottom portion 47. In this embodiment, the cable 102 is a high voltage cable. The fixing part 103 is an electrical insulating material.

  In this embodiment, the fixing portion 103 as an electrical insulating material of the high voltage connector 100 is in intimate contact with the external end surface 41 of the bottom portion 47. Note that the fixing portion 103 may be in direct contact with the outer end surface 41. The high voltage connector 100 provides a high voltage to the voltage supply terminal 44.

  The X-ray tube apparatus configured as described above is used as follows. When the high voltage connector 100 is attached to the housing 20, the silicone plate 104 is pressed so as to be in close contact with the fixing portion 103 and the external end surface 41 of the high voltage insulating member 40.

  The high voltage connector 200 includes a bottomed cylindrical housing 201, a cable 202 having a tip inserted into the housing 201, and the housing 201 filled with the terminal 202a of the cable 202 facing the opening of the housing 201. And a fixed portion 203 made of an epoxy resin material, and a silicone plate 204 made of a silicone resin material inserted between the fixed portion 203 and the outer end face 51 of the high-voltage insulating member 50. In this embodiment, cable 202 is a high voltage cable. The fixing part 203 is an electrical insulating material.

  In this embodiment, the fixing portion 203 as an electrical insulating material of the high voltage connector 200 is in intimate contact with the external end surface 51 of the high voltage insulating member 50. Note that the fixing portion 203 may be in direct contact with the outer end surface 51. The high voltage connector 200 applies a high voltage to the voltage supply terminal 54.

  The X-ray tube apparatus configured as described above is used as follows. When attaching the high voltage connector 200 to the housing 20, the silicone plates 204 are pressed so as to be in close contact with the fixing portion 203 and the external end face 51 of the high voltage insulating member 50.

  An X-ray shielding cap 300 as an X-ray shielding part is detachably attached to the housing 20 so as to cover the high voltage connector 100. An X-ray shielding cap 400 as an X-ray shielding part is detachably attached to the housing 20 so as to cover the high voltage connector 200. The X-ray shielding cap 300 and the X-ray shielding cap 400 are made of a material containing an X-ray opaque material.

  The X-ray tube apparatus 10 further includes a shielding layer 20 a that is provided on at least a part of the inner surface or the outer surface of the housing 20 and shields electromagnetic waves. In this embodiment, the shielding layer 20 a is provided on the outer surface of the housing 20. The shielding layer 20a is a shell made of metal. As a result, malfunction of peripheral devices due to electromagnetics can be prevented.

  The X-ray tube apparatus 10 further includes shielding layers 300a and 400a that are provided on at least a part of the inner surface or outer surface of the X-ray shielding caps 300 and 400 and shield electromagnetic waves. In this embodiment, the shielding layer 300 a is provided on the outer surface of the X-ray shielding cap 300. The shielding layer 400 a is provided on the outer surface of the X-ray shielding cap 400. Thereby, it is possible to further prevent malfunction of peripheral devices due to electromagnetics.

Note that when the shielding layers 20a, 300a, and 400a are provided on the inner surface of the housing 20, the shielding layer may be corroded by the coolant, so that these shielding layers are formed on the outer surface of the housing 20 and the X-ray shielding caps 300 and 400. It is preferable to provide on the outer surface.
The shielding layers 20a, 300a, and 400a may be formed by a coating process such as a plating process.

  The X-ray shield 80 is fixed to at least one of the vacuum envelope 31 and the housing 20. Here, the X-ray shield 80 is indirectly fixed to the housing 20. The X-ray shield 80 is located between the vacuum vessel 32 and the housing 20. The X-ray shield 80 is provided with a gap between the vacuum vessel 32 and the housing 20. The X-ray shield 80 is positioned to face at least the anode target 35a in the direction perpendicular to the rotation axis of the anode target 35a.

  The X-ray shield 80 is made of a material containing an X-ray opaque material. The radiopaque material is a metal composed of at least one of tungsten, tantalum, molybdenum, barium, bismuth, rare earth metal and lead, or a compound of tungsten, tantalum, molybdenum, barium, bismuth, rare earth metal and lead. At least one is contained as a main material.

  The X-ray shield 80 is formed in a cylindrical shape. In this embodiment, the X-ray shield 80 is formed of a lead cylinder. The surface of the lead cylinder is formed with metal plating or resin coating of tin, silver, copper, nickel or the like for protection against corrosion.

The X-ray shield 80 has an X-ray transmission window 81 that transmits X-rays. The X-ray transmission window 81 faces the radiation window 24. Here, the X-ray transmission window 81 is an opening in which a part of the X-ray shield 80 is opened.
The X-ray shield 80 shields X-rays emitted in directions other than the X-ray transmission window 81.

  The protective body 70 is fixed to at least one of the vacuum envelope 31 and the housing 20. Here, the protective body 70 is fixed to the housing 20. The protective body 70 is located between the vacuum vessel 32 and the housing 20. The protective body 70 is provided with a gap between the vacuum vessel 32 and the housing 20. The protective body 70 is located at least facing the anode target 35a in the direction perpendicular to the rotation axis of the anode target 35a.

  The protective body 70 is formed in a cylindrical shape made of a ductile material such as a stainless steel plate. In this embodiment, the protective body 70 and the X-ray shield 80 are integrally formed. The protective body 70 is located between the vacuum vessel 32 and the X-ray shield 80. The X-ray shield 80 is formed by attaching a lead plate to the outer surface of the protective body 70.

  The protective body 70 has an X-ray transmission window 71 that transmits X-rays. The X-ray transmission window 71 faces the radiation window 24 and the X-ray transmission window 81. Here, the X-ray transmission window 71 is an opening in which a part of the protective body 70 is opened.

  The protective body 70 protects the collision of the fragments of the anode target 35a, which is scattered in a state having high kinetic energy, with the housing 20 when the anode target 35a is broken during high-speed rotation.

  Even if a fragment of the anode target 35a collides with the protective body 70, the protective body 70 can absorb kinetic energy by causing sufficient deformation. Since the protective body 70 (X-ray shield 80) and the housing 20 are located with a gap, even if the protective body 70 is deformed, the deformation of the housing 20 itself can be prevented. Thereby, the crack which may arise in the housing 20 can be prevented.

  The thickness of the protective body 70 is 0.5 to 3 mm. In this embodiment, the thickness of the protective body 70 is 1 mm. The thickness of the X-ray shield 80 is 1 to 3 mm. In this embodiment, the thickness of the X-ray shield 80 is 2.5 mm. In the direction perpendicular to the rotation axis of the anode target 35a, the gap between the vacuum vessel 32 and the housing 20 is 3 to 12 mm. In this embodiment, the gap between the vacuum vessel 32 and the housing 20 is 8 mm.

The coolant 7 is filled in the housing 20 and fills the space between the X-ray tube 30 and the housing 20. The coolant 7 also fills a region including the space between the vacuum envelope 31 and the protective body 70 and the space between the X-ray shield 80 and the housing 20.
As the coolant 7, insulating oil or an aqueous coolant can be used. In this embodiment, an aqueous coolant is used as the coolant 7.

  Further, a cooler, that is, a cooler unit 22 is connected to the housing 20. The cooler unit 22 includes a circulation pump 22a and a heat exchanger 22b. For this reason, the coolant 7 is cooled by the heat exchanger 22b. The circulation pump 22a circulates the coolant 7 and creates a flow of the coolant 7. The coolant 7 is also circulated between the vacuum envelope 31 and the protective body 70 and between the X-ray shield 80 and the housing 20 through the opened X-ray transmission windows 71 and 81. Thereby, the heat generated in the X-ray tube device 10 is released to the outside of the housing 20 through the coolant 7.

  In the X-ray tube apparatus 10 configured as described above, when a predetermined current is applied to the stator coil 910, the rotor 920 rotates and the anode target 35a (anode 35) rotates. Next, a predetermined high voltage is applied to the high voltage connectors 100 and 200.

  The high voltage applied to the high voltage connector 100 is supplied to the anode target 35 a of the anode 35 through the voltage supply terminal 44, the fixed body 1, the bearing 930 and the rotating body 2. The high voltage applied to the high voltage connector 200 is supplied to the cathode 36 via the voltage supply terminal 54.

  As a result, an electron beam is emitted from the cathode 36 to the target layer 35b of the anode target 35a, and X-rays are emitted from the anode target 35a, and the X-rays pass through the vacuum vessel 32, the X-ray transmission windows 71 and 81, and the emission window 24. It is transmitted through and radiated to the outside.

  According to the rotary anode X-ray tube apparatus configured as described above, the rotary anode X-ray tube apparatus includes the cathode 36, the anode target 35a, the vacuum envelope 31, the rotary body 2, and the fixed body. 1, a stator coil 910, a housing 20, a protective body 70, an X-ray shield 80, and a coolant 7 filling between the X-ray tube 30 and the housing 20. Yes.

  The housing 20 is formed of a material mainly composed of a solid resin material. For this reason, when the housing 20 is injection-molded, excellent fluidity of the material (resin) forming the housing 20 can be obtained.

  The X-ray shield 80 is made of a material containing an X-ray opaque material. Since the X-ray shield 80 can shield X-rays in directions other than the X-ray transmission window 81, for example, when the X-ray tube device is mounted on a medical diagnostic device, unnecessary radiation (exposure to the human body) ) Can be prevented.

The X-ray shield 80 is fixed to at least one of the vacuum envelope 31 and the housing 20. The X-ray shield 80 is provided with a gap between the vacuum envelope 31 and the housing 20. The X-ray shield 80 is located between the vacuum envelope 31 and the housing 20. Here, the X-ray shield 80 is formed by attaching a lead plate to the outer surface of the protective body 70. The X-ray shield 80 is fixed to the housing 20 together with the protective body 70.
Since it is not necessary to attach a lead plate to the inner surface of the housing 20 or replace the lead plate with an X-ray shielding material instead of lead, the manufacturing cost can be reduced.

  The protective body 70 is fixed to at least one of the vacuum envelope 31 and the housing 20. The protector 70 is provided with a gap between the vacuum envelope 31 and the housing 20. The protective body 70 is located between the vacuum envelope 31 and the housing 20.

  The protective body 70 protects the collision of the fragments of the anode target 35a, which is scattered in a state having high kinetic energy, with the housing 20 when the anode target 35a is broken during high-speed rotation. Even if a fragment of the anode target 35a collides with the protective body 70, the protective body 70 can absorb kinetic energy by causing sufficient deformation.

  Thereby, the crack which may arise in the housing 20 can be prevented. For example, when a rotating anode type X-ray tube device is mounted on a medical diagnostic instrument, the risk that the high-temperature coolant 7 may be applied to an object to be inspected (for example, a human body) can be eliminated.

  Further, X-ray shielding caps 300 and 400 are provided so as to cover the high voltage connectors 100 and 200. Since X-rays transmitted through the high-voltage connectors 100 and 200 can be shielded by the X-ray shielding caps 300 and 400, unnecessary radiation (exposure) to the human body can be further prevented.

  As the coolant 7, an aqueous coolant having the highest heat transfer coefficient and containing water as a main component can be used. For this reason, the coolant 7 can most effectively remove the heat transmitted to the high voltage insulating members 40 and 50. Further, since the water-based coolant has a larger specific heat than the insulating oil (about twice that of the insulating oil), the temperature rise of the coolant due to the heat radiation of the X-ray tube 30 is suppressed to a low level.

  In addition, since the high voltage insulating members 40 and 50 are in contact with the coolant 7, heat from the anode 35 and the cathode 36 can be effectively dissipated into the coolant 7, and the high voltage connector connected to the high voltage insulators 40 and 50. The temperature of 100, 200 can be lowered, and the insulation of the high voltage connectors 100, 200 can be ensured over a long period of time.

  From the above, it is possible to obtain a rotary anode X-ray tube apparatus that can reduce manufacturing costs. Furthermore, the housing 20 can be prevented from being damaged, and further, the heat release characteristics can be improved, so that a highly reliable rotary anode X-ray tube apparatus can be obtained over a long period of time.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the components without departing from the scope of the invention in the implementation stage. Various inventions can be formed by appropriately combining a plurality of constituent elements disclosed in the embodiments. For example, some components may be deleted from all the components shown in the embodiment.

  The protective body 70 only needs to be formed of a material that can absorb the kinetic energy of the fragments of the anode target 35a, and it is only necessary to prevent cracks that may occur in the housing 20. The protective body 70 is not limited to stainless steel, and can be formed of metal, resin, ceramics, or the like. Since the protective body 70 is best insulated from the high voltage potential, it is preferable to form the protective body 70 from an insulating material such as resin or ceramics.

  The X-ray shield 80 may be formed of a material containing an insulating material as a main component and containing an X-ray opaque material. The radiopaque material includes at least metal fine particles made of any one of tungsten, tantalum, molybdenum, barium, bismuth, rare earth metal and lead, or tungsten, tantalum, molybdenum, barium, bismuth, rare earth metal and lead. It is sufficient if at least one of the compound fine particles is contained as a main material.

  When the anode 35 is formed of molybdenum or a molybdenum alloy, the anode 35 can shield X-rays. In this case, the X-ray tube apparatus 10 needs to be provided with the X-ray shielding cap 400, but the X-ray shielding cap 300 may not be provided.

  The vacuum vessel 32 is formed of glass, but is not limited to this, and can be formed of various materials. For example, the vacuum container 32 may be formed of a ductile material such as metal. In this case, the rotary anode X-ray tube device can be formed without the protective body 70.

The protective body 70 may be located between the X-ray shield 80 and the housing 20. In this case, the X-ray shield 80 may be formed by attaching a lead plate to the inner surface of the protective body 70.
The present invention can be applied not only to the rotary anode X-ray tube apparatus but also to various rotary anode X-ray tube apparatuses.

  DESCRIPTION OF SYMBOLS 1 ... Fixed body, 2 ... Rotating body, 7 ... Coolant, 10 ... Rotary anode type X-ray tube apparatus, 20 ... Housing, 20a ... Shielding layer, 30 ... X-ray tube, 31 ... Vacuum envelope, 32 ... Vacuum Container, 35 ... Anode, 35a ... Anode target, 35b ... Target layer, 35c ... Support, 36 ... Cathode, 40 ... High voltage insulating member, 41 ... External end surface, 42 ... Mounting surface, 43 ... Cooling surface, 44 ... Voltage Supply terminal 50 ... High voltage insulating member 51 ... External end face 52 ... Mounting surface 53 ... Cooling surface 54 ... Voltage supply terminal 70 ... Protective body 71 ... X-ray transmission window 80 ... X-ray shield 81 ... X-ray transmission window, 100 ... High voltage connector, 103 ... Fixed part, 200 ... High voltage connector, 203 ... Fixed part, 300 ... X-ray shielding cap, 300a ... Shielding layer, 400 ... X-ray shielding cap, 400a ... Shielding layer, 910 ... stator coil Le.

Claims (17)

A cathode for emitting electrons, an anode target that emits X-rays by being collision to the emitted electron from the cathode, and the vacuum envelope which houses at least the cathode and anode target, the anode target An X-ray tube having a rotating body fixed and rotatably provided together with the anode target; and a fixing body that rotatably supports the rotating body;
A rotation driving device for rotating the rotating body;
A housing formed of a material mainly composed of a solid resin material and containing at least the vacuum envelope;
X-ray transmission that is fixed to at least one of the vacuum envelope and the housing, is located between the vacuum envelope and the housing, is provided with a gap between the vacuum envelope and the housing, and transmits the X-ray. An X-ray shield with a window;
A rotary anode X-ray tube device comprising: a cooling liquid that fills between the X-ray tube and the housing including the vacuum envelope and the X-ray shield, and between the X-ray shield and the housing.   The rotary anode type X-ray tube apparatus according to claim 1, wherein the X-ray shield is made of a material containing an X-ray opaque material.   The radiopaque material contains, as a main material, at least one of metal fine particles composed of any one of tungsten, tantalum, molybdenum, barium, bismuth, rare earth metal, and lead, or fine particles of these compounds. Item 3. The rotating anode X-ray tube device according to Item 2.   The rotary anode X-ray tube device according to claim 1, wherein the X-ray shield is formed in a cylindrical shape. The vacuum envelope is formed of glass;
The rotary anode type X-ray tube device according to claim 1, wherein the X-ray shield is capable of absorbing kinetic energy of fragments of the anode target. The vacuum envelope is formed of glass;
The rotary anode type X-ray tube apparatus according to claim 2, wherein the X-ray shield is made of a material mainly composed of an insulating material. X-ray transmission that is fixed to at least one of the vacuum envelope and the housing, is located between the vacuum envelope and the housing, is provided with a gap between the vacuum envelope and the housing, and transmits the X-ray. A protective body having a window and capable of absorbing the kinetic energy of the fragments of the anode target;
The X-ray transmissive window of the protective body and the X-ray transmissive window of the X-ray shield are located facing each other,
The rotary anode X-ray tube device according to claim 1, wherein the vacuum envelope is made of glass.   The rotary anode type X-ray tube device according to claim 7, wherein the protective body is positioned to face the anode target in a direction perpendicular to a rotation axis of the anode target.   The rotary anode type X-ray tube device according to claim 7, wherein the protective body is made of a ductile material.   The rotary anode type X-ray tube device according to claim 7, wherein the protective body is formed in a cylindrical shape. The rotary anode X-ray tube apparatus according to claim 7, wherein the protective body is located between the vacuum envelope and the X- ray shield.   The solid resin material is thermosetting epoxy resin, unsaturated polyester resin, phenol resin, diallyl phthalate resin, thermoplastic epoxy resin, nylon resin, aromatic nylon resin, polybutylene terephthalate resin, polyethylene terephthalate resin, polyphenylene sulfide resin. The rotary anode X-ray tube apparatus according to claim 1, comprising any one of a polyphenylene ether resin, a liquid crystal polymer, and a methylpentene polymer resin.   The rotary anode type X-ray tube apparatus according to claim 1, further comprising a shielding layer that is provided on at least a part of an inner surface or an outer surface of the housing and shields electromagnetism. A part of the vacuum envelope, an external end surface exposed to the outside of the housing, a cooling surface in contact with the coolant, and a mounting surface to which the anode target or cathode is directly or indirectly attached; A high voltage insulating member having
A voltage supply terminal provided through the external end face and electrically connected to the anode target or the cathode attached to the high voltage insulating member;
2. The rotary anode type X according to claim 1, further comprising: a high voltage connector having an electrical insulating material which is directly or indirectly adhered to the external end face and electrically connected to the voltage supply terminal. Tube device.   The rotary anode type X-ray tube apparatus according to claim 14, wherein the outer end surface is a flat surface.   The rotary anode type X according to claim 14, further comprising an X-ray shielding part that is detachably attached to the high-voltage connector so as to cover the high-voltage connector and is formed of a material containing an X-ray opaque material. Tube device.   The rotary anode X-ray tube apparatus according to claim 1, wherein the coolant is an aqueous coolant.

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