JP5601832B2 - Rotating anode type X-ray apparatus and X-ray CT apparatus - Google Patents

Description

  The present invention relates to a rotary anode type X-ray apparatus and an X-ray computed tomography apparatus (X-ray Computed Tomography Apparatus). In particular, the present invention relates to a technique for suppressing vibration and noise from a target bearing portion in a rotary anode X-ray apparatus and an X-ray CT apparatus using the same.

  The rotary anode type X-ray apparatus generates a rotating magnetic field for rotating and driving a cathode (anode) that emits thermoelectrons, a target (anode) that receives the thermoelectrons to generate X-rays, and a main shaft (shaft) of the target. A stator coil is provided. The X-ray exposure is performed by applying a high voltage between the cathode and the target in a state where the target is rotated at a predetermined rotation speed, and emitting thermal electrons from the cathode.

  The rotary anode X-ray apparatus for X-ray CT apparatus is required to further increase the X-ray intensity due to clinical needs. To achieve this, the rotational speed of the target is further increased. It is hoped that However, when the target is rotated at a higher speed in the conventional target bearing structure using a ball bearing or the like, low-frequency vibrations and noise are amplified due to the influence of eccentricity of the rotational center of gravity of the target bearing. There is a possibility that the vibration propagates to the gantry (bed) of the X-ray CT apparatus.

  Therefore, Patent Document 1 describes a technique for suppressing vibration and noise of each part accompanying the rotation of the shaft by floating the shaft of the target with a magnetic force in the bearing of the cylindrical rotating anode.

Japanese Patent Laid-Open No. 2-121245

  Since the target is impacted by thermionic electrons emitted from the cathode, the target shaft becomes considerably hot. Since it is difficult to use a magnetic bearing for such a high-temperature part, it is considered difficult to realize the technique described in Patent Document 1. For this reason, the technique which suppresses the vibration and noise of each part accompanying rotation of the shaft of a target with another technique was requested | required.

  The present invention has been made in view of the above problems, and an object of the present invention is to provide a technique for suppressing vibration and noise from a target bearing portion in a rotary anode X-ray apparatus and an X-ray CT apparatus using the same. And

Internal (1) rotating anode X-ray device of one embodiment, an insert portion having a rotary anode for generating X-rays upon receiving a cathode and thermionic emitting thermal electrons therein, the insert portion And a housing part to be housed in the housing . The rotary anode type X-ray device is constructed as a magnetic working portion having a material which at least part of the outer wall of the insert part is subjected to force, further comprising a magnet support portion. The magnetic support unit is provided in the housing unit, that on the magnetic force to the magnetic action part, supports the insert portion such that the outer wall of the inner wall and the insert portion of the housing portion away from each other in a floating state in the housing unit. The magnetic support portion has an induction coil that supports the insert portion by generating a magnetic force in the axial direction of the rotation of the anode by the supplied current.
(2) A rotating anode type X-ray apparatus according to another embodiment includes an insert portion having a cathode that emits thermoelectrons and a rotating anode that generates X-rays by receiving thermoelectrons, and an insert portion inside And a housing part to be housed in the housing. In this rotary anode type X-ray apparatus, a first protrusion and a second protrusion having a material for receiving magnetic force are formed at positions that are at least a part of the outer wall of the insert portion and face each other on the outer wall. . This rotary anode type X-ray apparatus is provided in the housing part, and exerts a magnetic force in a direction orthogonal to the axial direction of the anode rotation on the first projecting part and the second projecting part, so that the inner wall of the housing part and the insert part A magnetic support portion is further provided for supporting the insert portion in a floating state in the housing portion so as to be separated from the outer wall.
(3) A rotating anode X-ray apparatus according to another embodiment includes an insert portion having a cathode that emits thermoelectrons and a rotating anode that generates X-rays by receiving thermoelectrons, and an insert portion. And a housing portion that is housed inside. In this rotary anode type X-ray apparatus, at least a part of the outer wall of the insert part is configured as a magnetic action part having a material that receives magnetic force. The housing part also has a radiation port for emitting X-rays to the outside. This rotary anode type X-ray device is provided in the housing part, and by applying a magnetic force to the magnetic action part, the insert part floats in the housing part so that the inner wall of the housing part and the outer wall of the insert part are separated from each other. And a magnetic support portion supported by The magnetic support part has an induction coil that generates a magnetic force for the magnetic action part by the supplied current, and controls the magnetic force for the magnetic action part by controlling the current supplied to the induction coil, thereby the insert part in a desired direction. Is moved to change the beam direction of X-rays emitted from the radiation port.

An X-ray CT apparatus according to an embodiment includes a rotating anode X-ray apparatus according to any one of (1) to (3) that emits X-rays, an X-ray detection unit that detects X-rays that have passed through a subject, and comprises a projection data acquisition unit for acquiring X-ray projection data on the basis of the detection signal of the X-ray detection unit is subjected to a reconstruction process in the X-ray projection data and image data generating unit for generating image data of the object Is.

  According to the present invention, in a rotary anode X-ray apparatus and an X-ray CT apparatus using the same, vibration and noise from the target bearing portion can be suppressed.

FIG. 3 is a schematic side sectional view of the rotary anode X-ray apparatus according to the first embodiment of the present invention, in which the cross section is an axis of rotation of the rotary anode from the X-ray radiation port side surface toward the opposite surface. The cross-sectional schematic diagram at the time of crossing so that it may contain. The plane cross-section schematic diagram which shows the plane cross section of the A1-A1 direction of FIG. The cross-sectional schematic diagram which shows the cross section of the B1-B1 direction of FIG. The plane cross-section schematic diagram which shows the plane cross section of the A2-A2 direction of FIG. The cross-sectional schematic diagram which shows the cross section of the B2-B2 direction of FIG. The block diagram which shows the structure of the X-ray CT apparatus in the 2nd Embodiment of this invention.

  Hereinafter, embodiments of the present invention will be described with reference to the accompanying drawings. In addition, in each figure, the same code | symbol is attached | subjected to the same element and the overlapping description is abbreviate | omitted.

[First Embodiment]
The first embodiment relates to the rotary anode X-ray apparatus 10 of the present invention.

  FIG. 1 is a schematic side sectional view of the rotary anode X-ray apparatus 10 of the present embodiment. The cross section of the rotary anode rotates from the surface on the X-ray emission port 52 side to the opposite surface. It is a side cross-sectional schematic diagram at the time of traversing so that an axis line may be included. FIG. 2 is a schematic cross-sectional view showing a cross-section in the A1-A1 direction of FIG.

  As shown in FIG. 1, the rotary anode X-ray apparatus 10 includes a control unit 18, a housing (X-ray tube container) 20 indicated by a thick line, and an insert (X-ray tube) 24 provided in the housing 20. Prepare.

  The insert 24 is supported in the housing 20 by a magnetic support mechanism so as to be separated from the inner wall of the housing 20. That is, the position of the insert 24 is controlled by this magnetic support mechanism, and the insert 24 is supported in a floating state in the housing 20. The housing 20 is filled with an insulating coolant 28, and the interior of the insert 24 is kept in a vacuum. In FIG. 1 and FIG. 2 (and FIGS. 3 to 5 described later), the portion filled with the cooling liquid 28 is shown as a pattern filled with dots.

  In the insert 24, a filament 32 that emits thermoelectrons as a cathode, a target 36 that receives thermoelectrons to generate X-rays as an anode, and a bearing mechanism 40 that rotatably supports the target 36 are provided. . The target 36 is formed in a disk shape as a rotating electrode. The bearing mechanism 40 has a structure that supports a shaft (not shown) that is a main shaft of the target 36 that rotates at a high speed by, for example, a ball bearing (rolling bearing), a radical bearing, or a thrust bearing. In addition, a stator coil 44 that generates a rotating magnetic field for rotating the shaft of the target 36 at a high speed is provided in the housing 20.

  As shown in FIGS. 1 and 2, the rotary anode X-ray apparatus 10 includes a high voltage cable 48 that passes through a cable insertion opening (not shown) on the outer wall of the housing 20 and the insert 24. The high-voltage cable 48 has a terminal end 50 formed as a terminal portion 50 and is connected to the filament 32. The high voltage cable 48 is for applying a predetermined tube voltage between the filament 32 and the target 36.

  As shown in FIG. 1, the housing 20 is provided with a radiation port 52 for emitting X-rays above the target 36. Corresponding to the position of the radiation port 52, a radiation window 56 for emitting X-rays is provided above the target 36 on the outer wall of the insert 24.

  Here, as an example in FIGS. 1 and 2 and FIGS. 3 to 5 to be described later, the X axis, the Y axis, and the Z axis orthogonal to each other on the target 36 side along the rotation axis (not shown) of the bearing mechanism 40. The direction from the side toward the stator coil 44 is taken as the positive Z-axis direction. The direction from the radiation window 56 on the outer wall of the insert 24 toward the radiation port 52 side on the outer wall of the housing 20 is defined as the positive Y-axis direction.

  On the inner surface of the housing 20, Z-axis direction induction coils 60 and 61 are fixed on both sides of the stator coil 44 in the Y-axis direction, and on the opposite surface (the rotating shaft of the bearing mechanism 40). The Z-axis direction induction coil 62 is fixed to a portion of the Z-axis induction coil 62 that is in contact with the extension line. The Z-axis direction induction coils 60 to 62, together with the X-axis direction induction coil and the Y-axis direction induction coil described later, generate a magnetic field by supplied current and support the insert 24 by magnetic attraction generated from the magnetic field. Yes, it functions as an electromagnet. For this reason, at the position facing the Z-axis direction induction coils 60 to 62 and the later-described X-axis direction induction coil and Y-axis direction induction coil on the outer wall of the insert 24, a magnetic attractive force such as iron or nickel is strongly received. Metal is embedded. Accordingly, the insert 24 receives a magnetic attractive force generated by the Z-axis direction induction coils 60 to 62 and the like, but the position of the insert 24 is controlled by controlling the attractive force of each part. In addition, it is good also as a structure which embeds a strong permanent magnet like a neodymium magnet instead of the metal which receives a magnetic attractive force strongly, and controls the position of the insert 24 by both a magnetic attractive force and a magnetic repulsive force.

  In FIG. 1, magnetic shielding shields 64 and 66 are disposed (fixed) between the Z-axis direction induction coil 60 and the stator coil 44 and between the Z-axis direction induction coil 61 and the stator coil 44, respectively. Is done. Each of the magnetic shielding shields 64 and 66 is disposed so as to face at least the entire upper and lower surfaces of the stator coil 44 in the Y-axis direction. The magnetic shielding shields 64 and 66 prevent the magnetic field generated by the Z-axis direction induction coils 60 and 61 from affecting the rotating magnetic field of the stator coil 44. The magnetic shield shields 64 and 66 may be formed of a nonmagnetic material such as amorphous.

  In FIG. 1, the first sensor 72 is fixed on the outer wall of the insert 24 (at the lower right position of the Z-axis direction induction coil 62). Further, a second sensor 76 is fixed on the inner wall of the housing 20 at a position below the Z-axis direction induction coil 62. The first sensor 72 detects in which direction gravity is acting with respect to the insert 24 (which part of the insert 24 is at the lowest position in the vertical direction), and this is detected by, for example, ultrasonic waves or radio waves. 76. For detection of the direction of gravity, for example, a conventional technique is used in which an acceleration value is obtained by detecting a force applied to the first sensor 72 by an acceleration detection means, and the inclination of the first sensor 72 with respect to the vertical direction is calculated from the acceleration value. That's fine.

  The second sensor 76 communicates with the first sensor 72 using sound waves or the like to detect positional information relative to the first sensor 72, and based on this, the housing 20 (inner wall) and the insert 24 ( Position information relative to the outer wall. The second sensor 76 inputs relative positional information between the housing 20 and the insert 24 and information on which direction gravity is acting on the insert 24 to the control unit 18 by wiring (not shown).

  In the insert 24 of FIG. 1, a region indicated by a two-dot chain line so as to include the target 36 and the bearing mechanism 40 is a region as the anode portion 78, and a region indicated by a broken line so as to include the filament 32 is This is a region as the cathode portion 80.

  FIG. 3 is a schematic cross-sectional view showing a cross-section in the B1-B1 direction of FIG. As shown in FIG. 3, on the inner wall of the insert 24, a layer of a magnetic shielding shield 84 (shaded portion in FIG. 3) is formed so as to cover the region as the cathode portion 80 described above. The magnetic shielding shield 84 prevents the magnetic force from the Z-axis direction induction coils 60 to 62 and the later-described XY direction induction coil from acting on the filament 32 and emitted thermoelectrons. The magnetic shielding shield 84 may be formed of a nonmagnetic material such as amorphous. Similarly, a magnetic shielding shield layer is formed on the inner wall of the insert 24 so as to cover only the vicinity of the target 36 in the region as the anode portion 78 (the two-dot chain line portion in FIG. 1) ( Not shown). This is to prevent the magnetic force of the Z-axis direction induction coils 60 to 62 from affecting the thermionic emission trajectory and the rotating magnetic field of the stator coil 44.

  4 is a schematic cross-sectional view showing a cross-section in the A2-A2 direction of FIG. As shown in FIG. 4, both ends of the insert 24 in the X-axis direction protrude as ear portions 90. The insert 24 is supported by receiving magnetic attractive forces in the X-axis direction and the Y-axis direction through the ears 90. Therefore, these ears 90 are embedded with a metal that receives a strong magnetic attraction such as iron or nickel.

  FIG. 5 is a schematic cross-sectional view showing a cross-section in the B2-B2 direction of FIG. 1, and particularly shows a detailed structure in the vicinity of the ear portion 90. The tips of the left and right ears 90 are each formed as a flat projection 100. On the inner wall of the housing 20, X-axis direction induction coils 110, 111, 112, and 113 are respectively fixed at positions facing the protrusion 100 of the left ear portion 90 in FIG. 5 from both sides. Similarly, X-axis direction induction coils 114, 115, 116, and 117 are fixed on the inner wall of the housing 20 at positions facing the protrusion 100 of the right ear 90 in FIG. 5 from both sides. .

  Further, on the inner wall of the housing 20, Y-axis direction induction coils 130 and 131 are fixed in positions near the center of the left ear 90 from both sides, and near the center of the right ear 90 from both sides. Y-axis direction induction coils 132 and 133 are fixed at opposing positions.

  Further, on the inner wall of the housing 20 (a total of four) pedestals 150 are fixed at positions facing the root sides of the two ear portions 90, respectively. On these pedestals 150, buffer materials 152 made of, for example, rubber or sponge are fixed. Four pedestals 150 and four cushioning materials 152 are also provided on the inner wall of the housing 20 on both surfaces in the Y-axis direction (on the upper surface and the lower surface in FIG. 5). These eight pedestals 150 and cushioning materials 152 prevent the insert 24 from directly colliding with the inner wall of the housing 20 due to gravity when the control of the magnetic support mechanism is stopped by turning off the power of the rotary anode X-ray apparatus 10 or the like. Acts as a cushion.

  The above is the description regarding the structure of the rotary anode X-ray apparatus 10 of the first embodiment. Hereinafter, the position control of the insert 24 by the magnetic support mechanism, the X-ray irradiation operation, and the flying focus function are performed in this order. The function of the line device 10 will be described.

  First, the position control of the insert 24 by the magnetic support mechanism will be described.

  The control unit 18 calculates magnetic attractive forces in the X-axis, Y-axis, and Z-axis directions such that a force having the same magnitude as the gravity on the insert 24 acts on the insert 24 in a direction opposite to the gravity. At the time of this calculation, the control unit 18 uses the relative position information of the housing 20 and the insert 24 input from the second sensor 76 and information on the direction in which gravity is acting with respect to the insert 24. .

  The control unit 18 controls the X-axis direction induction coils 110 to 117 and the Y-axis direction induction coils 130 to 133 so that the magnetic attraction in the X-axis, Y-axis, and Z-axis directions calculated as described above acts on the insert. The current supplied to the Z-axis direction induction coils 60 to 62 is controlled by wiring (not shown). In this way, the control unit 18 supports the insert 24 against gravity by the magnetic attraction in the X-axis direction, the Y-axis direction, and the Z-axis direction, and the inner wall of the housing 20 and the outer wall of the insert 24 come into contact with each other. The position of the insert 24 is controlled so as not to occur.

  For example, when gravity acts in the negative X-axis direction, the X-axis positive induction magnetic coils 111, 113, 114, 116 shown in FIG. The insert 24 is supported by exerting. Further, when gravity is acting in the negative Y-axis direction, the Y-axis direction induction coils 131 and 133 shown in FIG. 5 exert a magnetic attractive force in the positive Y-axis direction that is equivalent to gravity on the ear portion 90. Thus, the insert 24 is supported. In addition, when gravity is acting in the negative Z-axis direction, the Z-axis induction coils 60 and 61 shown in FIG. 1 exert a magnetic attractive force in the positive Z-axis direction that is equivalent to the gravity on the insert 24. Then, the insert 24 is supported.

  During these controls, relative position information between the housing 20 and the insert 24 is input from the second sensor 76 to the control unit 18 at a predetermined short time interval, and the control unit 18 determines the position of the latest insert 24. Based on the information, the magnetic support mechanism is controlled so that the inner wall of the housing 20 and the outer wall of the insert 24 do not contact each other.

  Next, an X-ray irradiation operation will be described. The control unit 18 supplies a predetermined electric power to the stator coil 44 through a wiring (not shown), and generates a rotating magnetic field for rotationally driving a shaft (not shown) in the bearing mechanism 40. As a result, in a state where the target 36 is rotated at a predetermined rotational speed, the control unit 18 applies a predetermined tube voltage between the filament 32 and the target 36 by the high voltage cable 48 or the like, and emits thermoelectrons from the filament 32. Release. The thermoelectrons collide with the target 36 to generate X-rays, and the X-rays are irradiated onto a subject or the like outside the apparatus via the radiation window 56 and the radiation port 52. Since the principle of X-ray generation is the same as in the prior art, further explanation is omitted.

  Next, the flying focus function will be described. The control unit 18 includes a group of operation buttons (not shown) for changing the X-ray beam direction. The control unit 18 calculates how the beam direction specified by the input is given when the relative positional relationship between the radiation port 52 and the insert 24 is changed. The input function of the operation button group of the control unit 18 is configured so that the beam direction that can be specified by input is only the beam direction corresponding to the range in which the inner wall of the housing 20 and the insert 24 do not contact each other.

  Next, the control unit 18 calculates in which direction and how wide the position of the insert 24 should be moved in order to give the calculated relative positional relationship between the radiation port 52 and the insert 24. And the control part 18 controls the electric current supplied to the X-axis direction induction coils 110-117, the Y-axis direction induction coils 130-136, and the Z-axis direction induction coils 60-62, so that the X-axis direction, the Y-axis direction, The magnetic attraction in the Z-axis direction is controlled, the insert 24 is moved with the calculated movement direction and movement width, and the insert 24 is controlled to be stationary in that state.

  For example, when the insert 24 is moved in the X-axis negative direction in a state where gravity is acting in the Y-axis negative direction and the insert 24 is stationary by controlling each part, the X-axis direction induction coils 110, 112, 115 in FIG. 117, the current flowing in the X-axis direction induction coils 111, 113, 114, 116 is made larger than the current flowing in the X-axis direction induction coils 111, 113, 114, 116, and the magnetic attractive force in the X-axis negative direction is increased. Move.

  Here, since the magnetic attractive force increases in proportion to the reciprocal of the square of the distance between the two objects, if the current value of each part is left as it is, the insert 24 moves in the negative direction of the X axis as the insert 24 moves in the negative direction of the X axis. The magnetic attractive force increases, and the protrusion 100 collides with the X-axis direction induction coil 110 or the like. Therefore, the control unit 18 has the calculated movement width of the insert 24 based on the latest relative position information of the housing 20 and the insert 24 input from the second sensor 76 at a predetermined short time interval. Control by the magnetic support mechanism is performed so that the insert 24 stops at the time.

  Further, for example, when the insert 24 is moved in the negative Z-axis direction in a state where gravity is acting in the negative Y-axis direction and the insert 24 is stationary by the control of each part, it flows in the Z-axis induction coil 62 in FIG. Control such as temporarily increasing the current is performed to move the insert 24 while temporarily increasing the magnetic attractive force in the negative Z-axis direction.

  This completes the description of the function of the rotary anode X-ray apparatus 10.

  Thus, in the first embodiment, the inner wall of the housing 20 and the insert 24 are separated by the magnetic support mechanism. For this reason, the vibration accompanying the high speed rotation of the target 36 and its shaft in the insert 24 does not propagate to the housing 20. Therefore, even if the rotary anode X-ray apparatus 10 of the present embodiment is used in an X-ray CT apparatus and the target is rotated at a higher speed than before, there has been no problem that has been concerned about the oscillating platform. As a result, the rotational speed of the target 36 can be made higher than before, and the X-ray intensity can be made higher than before.

  In addition, since the bearing mechanism 40 in the insert 24 serving as a noise source and the housing 20 are physically separated from each other, noise can be significantly reduced as compared with the conventional case.

  Further, as shown in FIG. 5, a pedestal 150 and a cushion 152 are provided on the inner wall of the housing 20. For this reason, the insert 24 can be protected regardless of which surface of the rotary anode X-ray apparatus 10 is placed downward in the vertical direction in a state where the control by the magnetic support mechanism does not work when the power is turned off, for example, during transportation. .

  Further, a magnetic shielding shield 84 layer is formed on the inner wall of the insert 24 so as to cover a region as the cathode portion 80. Therefore, the magnetic field generated by the X-axis direction induction coils 110 to 117, the Y-axis direction induction coils 130 to 133, and the Z-axis direction induction coils 60 to 62 causes a magnetic force to act on the filament 32 and emitted thermoelectrons. This is prevented.

  Furthermore, the beam direction of the X-rays emitted from the radiation port 52 can be controlled by controlling the relative positional relationship between the radiation port 52 and the insert 24 by the magnetic support mechanism. That is, if the rotary anode X-ray apparatus 10 of this embodiment is used in, for example, an X-ray CT apparatus, a flying focus function (a function of performing scanning while gradually shifting the focal position of the X-ray tube) is easily realized. be able to.

[Second Embodiment]
The second embodiment relates to an X-ray CT apparatus, and is mainly characterized by mounting the rotary anode X-ray apparatus 10 of the first embodiment.

  FIG. 6 is a block diagram showing the configuration of the X-ray CT apparatus 200 in the second embodiment.

  As shown in FIG. 6, the X-ray CT apparatus 200 includes a rotary anode X-ray apparatus 10, a rotation unit 212, a gantry 216, an X-ray detector 220, a high voltage generator 224, and a rotation drive unit 228. A gantry control unit 232, a data acquisition system (hereinafter referred to as DAS) 236, an image data generation / storage unit 240, a system control unit 244, an input unit 248, and a display unit 252.

  The input unit 248 includes an input device such as a display panel and a selection button, and the operator inputs information on the subject P, projection data collection conditions, and reconstruction conditions in the input unit 248 prior to collection of projection data. The image display conditions are set. The condition set in this way is input to the system control unit 244.

  The system control unit 244 controls each unit of the X-ray CT apparatus 200 according to various setting conditions input from the input unit 248. The system control unit 244 is connected to the control unit 18 of the rotary anode X-ray apparatus 10 and controls X-ray irradiation by the rotary anode X-ray apparatus 10 and imaging based on the flying focus mechanism.

  The gantry 216 is inserted into an opening (not shown) provided at the center of the rotating unit 212, and the subject P is placed on the gantry 216.

  In the rotation unit 212, the radiation port 52 (see FIG. 1) of the rotary anode X-ray apparatus 10 and the X-ray detector 220 are arranged to face each other with the subject P in between.

  The X-ray detector 220 has a configuration in which multi-channel detection elements are arranged in an arc shape, and detects X-rays irradiated from the rotary anode X-ray apparatus 10 and transmitted through the subject P.

  The rotation drive unit 228 drives the rotation unit 212 based on the drive control signal input from the system control unit 244, and the rotation anode type X-ray apparatus 10 and the X-ray detector 220 supported by the rotation unit 212 are examined. Rotate continuously around P.

  The gantry control unit 232 controls the position of the gantry 216 based on the gantry control signal input from the system control unit 244.

  The high voltage generator 224 is connected to the high voltage cable 48 of the rotary anode X-ray apparatus 10 through a slip ring (not shown). The high voltage generator 224 supplies a predetermined tube current and tube voltage to the rotary anode X-ray apparatus 10 based on the X-ray control signal supplied from the system control unit 244.

  The DAS 236 is an integrator that integrates the output from each detection element of the X-ray detector 220 with time, a multiplexer that captures the output of the integrator in a high-speed and serial manner in units of channels, and an A that converts the output signal of the multiplexer into a digital signal. / D converter etc. The DAS 236 collects projection data reflecting the X-ray transmittance for each X-ray path detected by the X-ray detector 220 based on the data acquisition control signal input from the system control unit 244, and this is collected as image data. Input to the generation storage unit 240.

  The image data generation storage unit 240 stores projection data collected for a plurality of slice planes of the subject P. Further, the image data generation storage unit 240 generates volume data by performing reconstruction processing on the projection data on a plurality of slice planes, and performs rendering processing on the volume data to generate three-dimensional image data, which is stored. To do. Then, the image data generation storage unit 240 inputs the three-dimensional image data to the display unit 252 in accordance with a command from the system control unit 244.

  The display unit 252 adds display information such as patient information to the three-dimensional image data to generate display data, thereby displaying an X-ray CT image on a monitor (not shown).

  As described above, in the X-ray CT apparatus 200 of the second embodiment, since the rotary anode X-ray apparatus 10 of the first embodiment is used as an X-ray source, vibration is applied to the gantry 216 even if the rotation speed of the target 36 is increased. It does not propagate and noise is significantly reduced compared to the prior art. Therefore, high-power X-ray imaging can be performed without making the patient feel uncomfortable. Further, since the rotary anode X-ray apparatus 10 of the first embodiment is used, the flying focus function can be easily realized.

[Additional matters of the present invention]
In the first embodiment, the example in which the magnetic attracting force is applied to the outer wall of the insert 24 (the portion in which iron or nickel is embedded) to control the position of the insert 24 has been described. The present invention is not limited to such an embodiment. For example, an induction coil that functions as an electromagnet may be disposed on both the outer wall of the insert 24 and the inner wall of the housing 20, and the position of the insert 24 may be controlled by both magnetic attraction and magnetic repulsion.

  Finally, the correspondence between the terms of the claims and the embodiments will be described. In addition, the correspondence shown below is one interpretation shown for reference, and does not limit the present invention.

  A portion facing the X-axis direction induction coils 110 to 117, the Y-axis direction induction coils 130 to 133, and the Z-axis direction induction coils 60 to 62 on the outer wall of the insert 24, that is, a metal that strongly receives magnetic force such as iron or nickel is embedded. This part is an example of the magnetic action part described in the claims.

  An X-axis direction induction coil 110-117, a Y-axis direction induction coil 130-133, a Z-axis direction induction coil 60-62, and an insert so that the inner wall of the housing 20 and the insert 24 are separated from each other by controlling the current supplied thereto. The function of the control unit 18 that supports 24 is an example of the magnetic support unit described in the claims.

  The insert 24 is moved in the X axis direction, the Y axis direction, or the Z axis direction by controlling the current supplied to the X axis direction induction coils 110 to 117, the Y axis direction induction coils 130 to 133, and the Z axis direction induction coils 60 to 62. Thus, the function of the control unit 18 that changes the beam direction of the X-rays emitted from the radiation port 52 is also an example of the magnetic support unit.

Both the ear | edge parts 100 (refer FIG. 5) are examples of the 1st protrusion part and the 2nd protrusion part of a claim.
The DAS 236 is an example of a projection data collection unit described in the claims.
The image data generation storage unit 240 is an example of an image data generation unit described in claims.

DESCRIPTION OF SYMBOLS 10 Rotating anode type X-ray apparatus 18 Control part 20 Housing 24 Insert 28 Coolant 32 Filament 36 Target 40 Bearing mechanism 44 Stator coil 48 High voltage cable 50 Terminal part 52 Radiation port 56 Radiation window 60, 61, 62 Z-axis direction induction coil 64, 66 Magnetic shield shield 72 First sensor 76 Second sensor 78 Anode portion 80 Cathode portion 84 Magnetic shield shield 90 Ear portion 100 Protrusions 110, 111, 112, 113, 114, 115, 116, 117 X-axis direction induction coil 130 131, 132, 133 Y-axis direction induction coil 150 Pedestal 152 Buffer material 200 X-ray CT apparatus 212 Rotating unit 216 Mounting unit 220 X-ray detector 224 High voltage generator 228 Rotating drive unit 232 Mounting control unit 236 DAS
240 Image data generation storage unit 244 System control unit 248 Input unit 252 Display unit P Subject

Claims (4)

A rotary anode type X-ray apparatus comprising: a cathode portion that emits thermoelectrons; an insert portion that includes a rotary anode that receives the thermoelectrons to generate X-rays; and a housing portion that houses the insert portion. There,
At least a part of the outer wall of the insert part is configured as a magnetic action part having a material that receives a magnetic force,
The insert portion is provided in the housing portion, and supports the insert portion in a floating state in the housing portion so that the inner wall of the housing portion and the outer wall of the insert portion are separated from each other by exerting a magnetic force on the magnetic action portion. further comprising a magnet support portion which,
The rotary anode type X-ray apparatus , wherein the magnetic support portion has an induction coil that supports the insert portion by generating a magnetic force in the axial direction of rotation of the anode by a supplied current . A rotary anode type X-ray apparatus comprising: a cathode portion that emits thermoelectrons; an insert portion that includes a rotary anode that receives the thermoelectrons to generate X-rays; and a housing portion that houses the insert portion. There,
A first protrusion and a second protrusion having a material that receives magnetic force are formed at positions that are at least a part of the outer wall of the insert portion and face each other on the outer wall,
The inner wall of the housing part and the outer wall of the insert part are provided in the housing part and exert a magnetic force in a direction orthogonal to the axial direction of rotation of the anode on the first protrusion part and the second protrusion part. Further comprising a magnetic support portion that supports the insert portion in a floating state in the housing portion so as to be separated from each other
A rotary anode X-ray apparatus characterized by the above . A rotary anode type X-ray apparatus comprising: a cathode portion that emits thermoelectrons; an insert portion that includes a rotary anode that receives the thermoelectrons to generate X-rays; and a housing portion that houses the insert portion. There,
The housing part has a radiation port for emitting the X-ray to the outside,
At least a part of the outer wall of the insert part is configured as a magnetic action part having a material that receives a magnetic force,
The insert portion is provided in the housing portion, and supports the insert portion in a floating state in the housing portion so that the inner wall of the housing portion and the outer wall of the insert portion are separated from each other by exerting a magnetic force on the magnetic action portion. A magnetic support that
The magnetic support portion has an induction coil that generates a magnetic force for the magnetic action portion by a supplied current, and controls the magnetic force for the magnetic action portion by controlling the current supplied to the induction coil, thereby The beam direction of the X-rays emitted from the radiation port is changed by moving the insert portion in the direction.
A rotary anode X-ray apparatus characterized by the above . The rotary anode X-ray apparatus according to any one of claims 1 to 3, which emits X-rays;
An X-ray detector for detecting X-rays transmitted through the subject;
A projection data collection unit that collects X-ray projection data based on a detection signal of the X-ray detection unit;
An image data generation unit that performs reconstruction processing on the X-ray projection data and generates image data of the subject;
An X-ray CT apparatus comprising:

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