JP2010080400A - Rotary anode type x-ray tube assembly - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a rotary anode type X-ray tube assembly for reducing the power of a driving power supply 65 to supply a current to a deflecting coil 53, while reducing the current capacities of power feeders 64, 66 between the deflecting coil 53 inside a housing 11 and the driving power supply 65 outside the housing 11 and of a current supply terminal 63. <P>SOLUTION: Inside the housing 11 of the rotary anode type X-ray tube assembly, a resonance circuit 61 is formed by connecting a capacitor 62 in parallel to the deflecting coil 53, thereby: reducing the power of the driving power supply 65 for supplying a current to the deflecting coil 53; and reducing the current capacities of the power feeders 64, 66 between the deflecting coil 53 inside the housing 11 and the driving power supply 65 outside the housing 11 and of the current supply terminal 63. Although the capacitor 62 involves heat generation, the capacitor 62 is stored in the housing 11 so as to be cooled concurrently with the rotary anode type X-ray tube assembly, thereby preventing characteristic changes in use. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a rotary anode type X-ray tube apparatus that generates X-rays by colliding electrons generated from an electron generation source with a rotating anode target.

  2. Description of the Related Art Conventionally, for example, in an X-ray CT apparatus, electrons generated from an electron source of a cathode collide with a rotating anode target, and X-rays are generated from an X-ray focal point formed by the collision of electrons on the anode target. A rotary anode X-ray tube apparatus is used.

  In such an X-ray CT apparatus or the like, the X-ray focal point is arranged at different positions in the rotary anode type X-ray tube apparatus during X-ray imaging, so that the incident angle of the X-ray incident on the detector through the subject can be set. A technique is known that slightly shifts and improves the resolution characteristics of an X-ray image.

  In order to place the X-ray focal point at different positions in the rotary anode X-ray tube apparatus during X-ray imaging, it is necessary to periodically move the X-ray focal point with a cycle of 1 msec or less.

  As one of the systems for periodically moving the X-ray focal point, there is an electrostatic electron beam deflection system in which a deflection voltage is applied to a deflection electrode disposed in a vacuum vessel to electrostatically deflect the electron beam ( For example, see Patent Document 1.)

  In general, in an X-ray tube in which the voltage between the cathode and the anode exceeds 100 kV, a negative high voltage potential is supplied to at least the cathode, so a high voltage cable is adopted as the cathode voltage supply cable. However, in the electrostatic electron beam deflection method, since it is necessary to apply a deflection voltage to the deflection electrode, a conventional high voltage cable cannot be used, and a dedicated high voltage cable is required. A dedicated power supply is also required for the voltage power supply. Therefore, the upgrade of the existing X-ray CT apparatus cannot be achieved only by exchanging the rotary anode X-ray tube apparatus, resulting in a problem in terms of economy, and conversely, the electrostatic deflection type rotary anode X Because it is difficult to mount a conventional rotating anode X-ray tube device on a new X-ray CT device that employs a tube device, a dedicated high-voltage power supply and a dedicated high-voltage cable, the rotating anode X-ray tube device In some cases, it may interfere with recovery in the event of down.

  As another method for instantaneously moving the X-ray focal point minutely, there is a magnetic electron beam deflection method in which an electron beam is deflected by a deflection magnetic field generated by a magnetic pole.

  In this magnetic electron beam deflection system, there is a configuration in which a constriction portion having a small diameter is provided in a vacuum envelope located between a cathode and an anode target, and a magnetic pole for generating a deflection magnetic field is disposed there. In this configuration, since the diameter of the vacuum envelope is reduced by the constricted portion, the distance between the magnetic poles is shortened, the magnetic flux density at the electron beam position is increased, and it is possible to deflect even if the electron velocity is high. (For example, refer to Patent Documents 2 to 4.)

Further, in the magnetic electron beam changing method, there is a configuration in which a part of the cathode is a magnetic path made of a magnetic material and a magnetic field is generated by a deflection coil wound around the magnetic path (see, for example, Patent Document 5). In this configuration, since the deflection coil is arranged at the cathode position in the vacuum envelope, it is necessary to supply current to the deflection coil through a high voltage cable, which is a problem of the electrostatic electron beam deflection method described above. There are exactly the same problems.
U.S. Pat. No. 4,689,809 US Pat. No. 7,289,603 US Pat. No. 6,777,991 US Pat. No. 6,629,579 Japanese Patent Laid-Open No. 11-111204

  As described above, a magnetic electron beam deflection system in which a constriction is provided in a vacuum envelope positioned between a cathode and an anode target, and a magnetic pole is disposed in the constriction, in order to reliably deflect the electron trajectory. In the electrostatic electron beam deflection method and the magnetic electron beam changing method, there is an advantage that there is no problem as in the case of a configuration in which a deflection coil is wound with a part of the cathode as a magnetic path.

  However, as the constriction of the vacuum envelope is formed, it is necessary to dispose the cathode further away from the anode target in order to maintain the space insulation distance between the cathode and the vacuum envelope. As the portion is formed, the potential distribution changes so that the electron beam is less likely to be focused, and these together cause problems such as expansion, blurring, and distortion of the X-ray focus.

  As described above, the method of magnetically changing the electron beam by forming the constricted portion in the vacuum envelope involves many difficulties. The method of arranging the magnetic poles without providing the constricted portion in the vacuum envelope has a problem that the deflection power is relatively large, but the system can be configured by applying the prior art in other cases. There is a big merit.

  In the case of the magnetic electron beam deflection method, the present inventors adopt a sinusoidal motion that requires a relatively low driving voltage of the deflection coil as the motion of the beam spot on the anode target in the X-ray tube. Attention has been focused on research to realize a method that does not have a special constriction in the vacuum envelope. In the case of a device using a sinusoidal deflection current, it is generally known to use a resonance circuit in order to reduce the power of the drive power supply. In the case of the electromagnetic deflection method in which the vacuum envelope is not particularly provided with a constricted portion, it is necessary to flow a large current of several tens of A or more to the deflection coil. However, by configuring a resonance circuit, the current on the drive power supply side can be reduced. It is possible to reduce from 1/5 to 1/10. As a result, the power of the drive power source can be reduced from 1/5 to 1/10.

  In general, in order to configure a resonance circuit, a capacitor having an electrostatic capacity so as to achieve a desired resonance frequency is arranged in the drive power supply in parallel with the deflection coil.

  However, in this case, the power supply line and the terminal connecting the drive power supply and the X-ray tube require a large current capacity, and the electric resistance of the power supply line particularly affects the amplitude increase coefficient of the resonance circuit, thereby increasing the deflection power. There is a problem that will let you.

  A feed line that is as short and thick as possible is preferable. However, shortening the length has restrictions on the apparatus, and increasing the supply line to keep the electrical resistance low raises the problem of increasing the cost of the apparatus.

  The present invention has been made in view of these points, and can reduce the power of the drive power supply that supplies current to the deflection coil, and can connect the deflection coil inside the housing and the drive power supply disposed outside the housing. An object of the present invention is to provide a rotating anode type X-ray tube apparatus that can reduce current capacity of electric wires and connection terminals.

  The present invention relates to a vacuum envelope, a cathode electron generation source disposed in the vacuum envelope, a cathode support for supporting the electron generation source, and a rotatable rotation in the vacuum envelope. A rotary anode type X-ray tube having an anode target on which an X-ray focal point is formed that generates X-rays upon impact of electrons generated from the electron generation source, and a vacuum envelope of the rotary anode type X-ray tube A deflection that deflects the trajectory of electrons generated from the electron source, arranged outside the chamber at a position opposite to the trajectory where electrons generated from the electron source in the vacuum envelope move to the anode target A deflection coil that forms a magnetic field, a resonance circuit having a capacitor electrically connected in parallel with the deflection coil, the rotary anode X-ray tube, the deflection coil, and at least a capacitor of the resonance circuit are incorporated with a coolant. Howe to It is what you are and a grayed.

  According to the present invention, the resonance circuit is configured by connecting a capacitor in parallel with the deflection coil inside the housing of the rotary anode X-ray tube device, thereby reducing the power of the drive power supply that supplies current to the deflection coil. In addition, the current capacity of a feeder line or a connection terminal that connects between the deflection coil inside the housing and the drive power source arranged outside the housing can be reduced. Furthermore, although a capacitor | condenser accompanies heat_generation | fever, by accommodating in a housing, it cools simultaneously with an X-ray tube and can prevent the characteristic change at the time of use.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings.

  1 to 5 show a first embodiment.

  As shown in FIGS. 2 and 3, the rotary anode X-ray tube apparatus includes a housing 11 and a grounded anode type rotary anode X-ray tube 12 disposed in the housing 11. The space between the housing 11 and the rotary anode X-ray tube 12 is filled with a water-based coolant 13, and this coolant 13 is circulated through a cooler connected to the housing 11 with a hose so as to be cooled. It is configured.

  The rotary anode type X-ray tube 12 includes a vacuum envelope 15, which is formed in a cylindrical shape having a large diameter portion 16 and small diameter portions 17 and 18 above and below the large diameter portion 16. Has been. Further, a cylindrical cathode storage portion 19 is formed on the large diameter portion 16 of the vacuum envelope 15.

  The material of the vacuum envelope 15 including the cathode housing part 19 is preferably a non-magnetic material, and is a high electrical resistance material that hardly generates eddy currents due to an alternating magnetic field. For example, nonmagnetic stainless steel, Inconel, Inconel X, titanium, conductive ceramics, nonconductive ceramics whose surface is coated with a metal thin film, or the like may be used.

  An X-ray transmission window 20 through which X-rays pass is attached to the outer peripheral surface of the large diameter portion 16 of the vacuum envelope 15 corresponding to the position of the cathode housing portion 19.

  Further, in the vacuum envelope 15, a fixed shaft 23 is disposed at the center of the vacuum envelope 15, and a rotating body 24 supported so as to be rotatable with respect to the fixed shaft 23 is disposed. . The fixed shaft 23 is configured as a rotating shaft that is the center of rotation of the rotating body 24 when viewed from the rotating body 24.

  The rotating body 24 is formed with a disk portion 25 that is rotatably disposed within the large diameter portion 16 and a rotor portion 26 that is rotatably disposed within the small diameter portion 18 on the lower side. The outer peripheral side of the upper surface of the disk portion 25 of the rotating body 24 is inclined downward at a predetermined angle so as to face the X-ray transmission window 20, and electrons collide with the inclined surface to cause X-rays. A generated anode target 27 is provided.

  A coil 28 that generates an induction electromagnetic field and rotates the rotating body 24 and the anode target 27 via the rotor portion 26 is disposed outside the small-diameter portion 18 on the lower side of the vacuum envelope 15.

  A cathode 31 disposed so as to face the anode target 27 is accommodated in the cathode accommodating portion 19 of the vacuum envelope 15. As shown in FIG. 4, the cathode 31 includes a filament 32 as an electron generation source that generates electrons, and a cathode support 33 that supports the filament 32.

  The filament 32 includes a small-focus filament 32a and a large-focus filament 32b, each formed in a shape having a long longitudinal direction and a narrow width direction perpendicular to the longitudinal direction. On the other hand, they are arranged in parallel in the direction along the width direction. The longitudinal direction of the filament 32 is arranged along the radial direction of the anode target 27, and the width direction is arranged along the rotation direction of the anode target 27.

  The cathode support 33 is supported on the vacuum envelope 15 by an insulator 35.

  As shown in FIGS. 2 and 3, the cathode housing part 19 of the vacuum envelope 15 is constituted by a cylindrical peripheral wall part 38 on the upper side and an annular recoil electron capturing structure 39 on the lower side. It is configured.

  The recoil electron capturing structure 39 captures recoil electrons from the anode target 27, and a circular opening 40 through which electrons generated from the filament 32 pass is formed at the center, and the filament 32 Are arranged so as to surround the trajectory in which the electrons generated from the target move to the anode target 27. The surface of the recoil electron capturing structure 39 facing the cathode 31 is formed as a concave surface, the surface facing the anode target 27 is formed as a flat surface, and the outer peripheral surface is formed as a cylindrical side surface.

  The material of the recoil electron capture structure 39 is preferably a non-magnetic material and a high thermal conductivity material, for example, a copper, copper alloy, reinforced copper such as GLID-COP, a metal material such as molybdenum or molybdenum alloy, etc. In addition, a ceramic surface having a high thermal conductivity such as SiC, AlN, or BeO coated with a metal thin film may be used.

  Although not shown, the recoil electron capture structure 39 has a cooling structure, and as this cooling structure, for example, a coolant flow path in which the coolant circulates inside the recoil electron capture structure 39 is formed. The coolant in the coolant channel is circulated through the cooler to cool the recoil electron capturing structure 39.

  Further, as shown in FIGS. 2 and 5, a deflection magnetic field is formed outside the cathode housing portion 19 of the vacuum envelope 15 to form a deflection AC magnetic field that periodically deflects the trajectory of electrons generated from the filament 32. Means 51 are arranged. The deflection magnetic field forming means 51 is a dipole having a substantially U-shaped yoke 52 and deflection coils 53 wound around both ends of the yoke 52, and a pair of magnetic poles 54 formed at both ends of the yoke 52. It is configured. The deflection coil 53 is formed by winding one winding, and includes a coil part 53a wound around one end of the yoke 52 and a coil part 53b wound around the other end of the yoke 52. The parts 53a and 53b are connected. The pair of magnetic poles 54 are arranged to face each other in the rotation direction of the anode target 27 and in the direction along the width direction of the filament 32.

  The main material constituting the yoke 52 is a soft magnetic material and a high electrical resistance material in which an eddy current is hardly generated by an AC magnetic field. For example, an Fe—Si alloy (silicon steel), an Fe—Al alloy, an electromagnetic stainless steel, etc. A thin plate made of Fe-Ni high magnetic permeability alloy such as steel, permalloy, Ni-Cr alloy, Fe-Ni-Cr alloy, Fe-Ni-Co alloy, Fe-Cr alloy, etc. was laminated with an electric insulating film interposed therebetween. Laminated bodies, aggregates in which wires made of these materials are covered with an electric insulating film and then bundled and hardened, or these materials are made into fine powder of about 1 μm and the surface is covered with an electric insulating film, and then compression molding The formed molded body may be used. Soft ferrite is also an optimal material.

  Then, as shown in FIG. 2, when the cathode support 33 and the anode target 27 face each other, the length of the magnetic pole 54 is Y, and the surface of the cathode support 33 facing the anode target 27 and the magnetic pole When the distance from the center position in the direction is X, there is a relationship of Y> X.

  More specifically, when the negative side is the negative side with respect to the surface of the cathode support 33 facing the anode target 27, the relationship Y> X> -Y is more preferable. Has a relationship of 0.5Y> X> −0.5Y.

  In the anode grounded rotary anode X-ray tube 12, not only the anode but also the recoil electron capturing structure 39 and the metal part of the vacuum envelope 15 are at the ground potential.

  Further, as shown in FIG. 3, the housing 11 is provided with an X-ray transmission window 11 a that transmits X-rays facing the X-ray transmission window 20 of the vacuum envelope 15.

  FIG. 1 is a schematic diagram showing a deflection-type power feeding system.

  Inside the housing 11, there is a rotating anode X-ray tube 12, a deflection coil 53, a capacitor 62 that is connected in parallel with the deflection coil 53 to form a resonance circuit 61, and a current supply that is a connection terminal provided in the housing 11. A power supply line 64 that connects the terminal 63 to the deflection coil 53 and the capacitor 62 is incorporated. All the electrically exposed portions of the devices and components built in these housings 11 are subjected to an insulation coating process on the coolant 13.

  A drive power supply 65 is disposed outside the housing 11, and the drive power supply 65 and the current supply terminal 63 are connected by a power supply line 66. The drive power supply 65 is controlled to a desired output by the controller 67.

  The deflection coil 53 has, for example, 70 turns, an inductance of 1.1 mH, and a capacitor 62 connected in parallel with the deflection coil 53 has a resonance frequency of 4.3 kHz with 1.25 μF. In order to obtain a desired electron beam deflection amount, the maximum current supplied to the deflection coil 53 is 28 Arms. However, since the capacitor 62 is housed in the housing 11, the amplitude increase coefficient of the resonance circuit 61 can be increased. The current supplied from the drive power supply 65 is about 3.5 Arms. The drive power supply 65 may be operated at a constant voltage or a constant current. This effect is the same in any of the following embodiments.

  Thus, at the time of X-ray imaging, in the rotating anode X-ray tube apparatus, the rotating body 24 and the anode target 27 rotate, and electrons generated from the filament 32 of the cathode 31 collide with the anode target 27, An X-ray focal point corresponding to the shape is formed, and X-rays generated from the X-ray focal point of the anode target 27 are irradiated to the outside through the X-ray transmission window 20 of the vacuum envelope 15 and the X-ray transmission window 11a of the housing 11. The

  Here, the X-ray focal point means not an actual focal point but an effective focal point.

  Recoil electrons from the anode target 27 are captured by the recoil electron capture structure 39.

  Further, as shown in FIG. 5, a deflection magnetic field that periodically changes is generated by energization of the deflection coil 53 of the deflection magnetic field forming means 51, and this deflection magnetic field causes electrons from the filament 32 to the anode target 27 to be anodes. The X-ray focal point deflected in the radial direction of the target 27 (longitudinal direction of the filament 32) and formed on the anode target 27 periodically moves minutely in the radial direction of the anode target 27 (longitudinal direction of the X-ray focal point).

  At this time, the magnetic pole 54 has a relationship of Y> X, preferably a relationship of Y> X> −Y, more preferably a relationship of 0.5Y> X> −0.5Y with respect to the cathode support 33. Since the deflection magnetic field is generated at a position close to the filament 32, the electron trajectory can be reliably deflected while the velocity of the electrons moving from the filament 32 to the anode target 27 is relatively low.

  If the magnetic pole 54 is not in a relationship of Y> X, more preferably 0.5Y> X, with respect to the cathode support 33, the magnetic pole 54 is separated from the cathode support 33 in the direction of the anode target 27, Since the electron trajectory is deflected at a position where the velocity of the electrons moving from the filament 32 to the anode target 27 is high, it becomes difficult to deflect the electrons, and the magnetic field strength is increased by reducing the distance between the magnetic poles as in the past. There is a need to increase it. On the other hand, if the relationship X> −Y, more preferably X> −0.5Y is not satisfied, the magnetic pole 54 is too close to the cathode support 33 side, so that the electrons moving from the filament 32 to the anode target 27 are not affected. As a result, the deflection magnetic field generated by the magnetic pole 54 becomes weak and it becomes difficult to deflect electrons.

  Therefore, it is not necessary to provide a constricted portion in the vacuum envelope and shorten the distance between the magnetic poles to increase the magnetic flux density as in the conventional case, so that the occurrence of expansion, blurring, distortion, etc. of the X-ray focal point can be reduced. .

  In addition, the current to the deflection coil 53 for generating the alternating magnetic field can be reduced, and the deflection magnetic field forming means 51 with less heat generation and high efficiency can be realized.

  Next, FIG. 6 shows a second embodiment.

  The pair of magnetic poles 54 of the deflection magnetic field forming means 51 are arranged opposite to each other at a position shifted by a predetermined angle α with respect to the rotation direction of the anode target 27 and along the width direction of the filament 32.

  The X-ray focal point can be moved simultaneously in the radial direction (the length direction of the X-ray focal point) and the rotation direction (the width direction of the X-ray focal point) of the anode target 27 by the deflection magnetic field generated by the pair of magnetic poles 54. .

  The angle α is set in accordance with the ratio of the movement distance of the anode target 27 in the radial direction (the length direction of the X-ray focus) and the movement distance in the rotation direction (the width direction of the X-ray focus) of the X-ray focus.

  In order to move the X-ray focus by the same distance in the length direction and the width direction of the X-ray focus, the angle α is set equal to the inclination angle of the anode target 27.

  Next, FIG. 7 shows a third embodiment.

  The deflection magnetic field forming means 51 includes two sets of dipoles.

  The magnetic poles 54 of the two pairs of dipoles are opposed to each other at a position shifted by a predetermined angle α to the opposite side to the direction along the width direction of the filament 32 in the rotational direction of the anode target 27. Arrange.

  The X-ray focal point is in the radial direction (length direction of the X-ray focal point) and the rotational direction (width direction of the X-ray focal point) of the anode target 27 by the deflection magnetic field generated by the magnetic poles 54 of two pairs of dipoles. Can move at the same time.

  The ratio of the moving distance of the X-ray focal point in the radial direction (the length direction of the X-ray focal point) and the moving distance in the rotational direction (the width direction of the X-ray focal point) of each of the two sets of dipoles. By changing the ratio of the magnetic fields, it can be freely changed in the range between 0 and tanα.

  Next, FIG. 8 shows a fourth embodiment.

  As the deflecting magnetic field forming means 51, a dipole having a pair of magnetic poles 54 formed by combining individual yokes 52 and deflection coils 53 is used, and these pairs of magnetic poles 54 are arranged in the rotational direction of the anode target 27 and are filaments. Arranged in the direction along the 32 width direction.

  The X-ray focal point can be moved in the radial direction of the anode target 27 (the length direction of the X-ray focal point) by the deflection magnetic field generated by the pair of magnetic poles 54.

  Next, FIG. 9 shows a fifth embodiment.

  The magnetic poles 54 of the pair of dipoles of the deflection magnetic field forming means 51 are opposed to each other at a position shifted by a predetermined angle α with respect to the direction of rotation of the anode target 27 and along the width direction of the filament 32. Arrange.

  The X-ray focal point can be moved simultaneously in the radial direction (the length direction of the X-ray focal point) and the rotation direction (the width direction of the X-ray focal point) of the anode target 27 by the deflection magnetic field generated by the pair of magnetic poles 54. .

  The angle α is set in accordance with the ratio of the movement distance of the anode target 27 in the radial direction (the length direction of the X-ray focus) and the movement distance in the rotation direction (the width direction of the X-ray focus) of the X-ray focus.

  In order to move the X-ray focus by the same distance in the length direction and the width direction of the X-ray focus, the angle α is set equal to the inclination angle of the anode target 27.

  Next, FIG. 10 shows a sixth embodiment.

  As the deflection magnetic field forming means 51, two sets of dipoles are provided.

  The pair of magnetic poles 54 of the two pairs of dipoles are opposed to each other at a position shifted by a predetermined angle α to the opposite side to the direction along the width direction of the filament 32 in the rotational direction of the anode target 27. And place it.

  The X-ray focus is in the radial direction of the anode target 27 (the length direction of the X-ray focus) and the rotation direction (the width direction of the X-ray focus) due to the deflection magnetic field generated by the pair of magnetic poles 54 of the two dipoles. Can move simultaneously.

  The ratio of the movement distance of the X-ray focal point in the radial direction (the length direction of the X-ray focal point) and the movement distance in the rotational direction (the width direction of the X-ray focal point) of each of the two pairs of dipoles By changing the ratio of the magnetic field, it can be freely changed in the range between 0 and tanα.

  Next, FIG. 11 shows a seventh embodiment.

  The deflecting magnetic field forming means 51 includes two dipoles having magnetic poles 54 formed at both ends.

  The magnetic poles 54 at both ends of the two dipoles are arranged at positions shifted by a predetermined angle β toward the opposite side to the direction along the width direction of the filament 32 in the rotational direction of the anode target 27.

  The X-ray focal point can be moved in the radial direction of the anode target 27 (the length direction of the X-ray focal point) by the deflection magnetic field generated by the magnetic poles 54 of the two dipoles.

  Next, FIG. 12 shows an eighth embodiment.

  As the deflection magnetic field forming means 51, two sets of dipoles are provided.

  The pair of magnetic poles 54 of the two pairs of dipoles are mutually spaced at equal intervals, for example, 45 ° shifted to opposite directions with respect to the direction of rotation of the anode target 27 along the width direction of the filament 32. Place them facing each other.

  The X-ray focus is in the radial direction of the anode target 27 (the length direction of the X-ray focus) and the rotation direction (the width direction of the X-ray focus) due to the deflection magnetic field generated by the pair of magnetic poles 54 of the two dipoles. Can move simultaneously.

It is a schematic diagram of the electric power feeding system of the deflection | deviation system of the rotating anode type | mold X-ray tube apparatus which shows the 1st Embodiment of this invention. It is sectional drawing of a rotary anode type X-ray tube apparatus same as the above. It is sectional drawing of a 90-degree different direction with respect to FIG. 1 of a rotary anode type X-ray tube apparatus same as the above. The cathode of a rotating anode type X-ray tube apparatus is shown, (a) is sectional drawing of a cathode, (b) is a bottom view of a cathode. It is a top view which shows arrangement | positioning of the deflection magnetic field formation means in a rotary anode type X-ray tube apparatus same as the above. It is a top view which shows arrangement | positioning of the deflection magnetic field formation means in the rotary anode type | mold X-ray tube apparatus which shows the 2nd Embodiment of this invention. FIG. 6 is a plan view showing the arrangement of deflection magnetic field forming means in a rotary anode X-ray tube apparatus showing a third embodiment of the present invention. FIG. 6 is a plan view showing the arrangement of deflection magnetic field forming means in a rotary anode X-ray tube apparatus showing a fourth embodiment of the present invention. FIG. 10 is a plan view showing the arrangement of deflection magnetic field forming means in a rotary anode X-ray tube apparatus showing a fifth embodiment of the present invention. FIG. 10 is a plan view showing the arrangement of deflection magnetic field forming means in a rotary anode X-ray tube apparatus showing a sixth embodiment of the present invention. FIG. 10 is a plan view showing the arrangement of deflection magnetic field forming means in a rotary anode X-ray tube apparatus showing a seventh embodiment of the present invention. It is a top view which shows arrangement | positioning of the deflection magnetic field formation means in the rotary anode type | mold X-ray tube apparatus which shows the 8th Embodiment of this invention.

Explanation of symbols

11 Housing
12 Rotating anode X-ray tube
13 Coolant
15 Vacuum envelope
27 Anode target
31 Cathode
32 Filament as electron source
33 Cathode support
53 Deflection coil
61 Resonant circuit
62 capacitors

Claims (3)

A vacuum envelope, a cathode electron source disposed in the vacuum envelope, a cathode support for supporting the electron source, and a rotatable rotation in the vacuum envelope, the electron A rotating anode type X-ray tube having an anode target on which an X-ray focal point for generating X-rays upon impact of electrons generated from a generation source is formed;
Outside the vacuum envelope of the rotary anode X-ray tube, the electron generated from the electron generation source in the vacuum envelope is disposed at a position facing a trajectory moving to the anode target, and generating the electrons A deflection coil that forms a deflection magnetic field that deflects the trajectory of electrons generated from the source;
A resonant circuit having a capacitor electrically connected in parallel with the deflection coil;
A rotary anode X-ray tube device, comprising: the rotary anode X-ray tube; the deflection coil; and a housing containing at least a capacitor of the resonance circuit together with a coolant. The rotary anode X-ray tube apparatus according to claim 1, wherein the cooling liquid is an aqueous cooling liquid, and at least an electrically exposed portion of the resonance circuit is covered with an insulation coating with respect to the cooling liquid. The rotary anode X-ray tube apparatus according to claim 2, wherein the cooling liquid is an aqueous glycol solution.

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