WO2016181715A1 - Source de rayonnement et dispositif d'imagerie par contraste de phase de rayonnement en étant doté - Google Patents

Source de rayonnement et dispositif d'imagerie par contraste de phase de rayonnement en étant doté Download PDF

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Publication number
WO2016181715A1
WO2016181715A1 PCT/JP2016/059968 JP2016059968W WO2016181715A1 WO 2016181715 A1 WO2016181715 A1 WO 2016181715A1 JP 2016059968 W JP2016059968 W JP 2016059968W WO 2016181715 A1 WO2016181715 A1 WO 2016181715A1
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Prior art keywords
slit
radiation
width
radiation source
ray
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PCT/JP2016/059968
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English (en)
Japanese (ja)
Inventor
貴弘 土岐
真悟 古井
晃一 田邊
吉牟田　利典
弘之 岸原
哲 佐野
日明 堀場
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株式会社島津製作所
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Priority to JP2017517640A priority Critical patent/JP6372614B2/ja
Publication of WO2016181715A1 publication Critical patent/WO2016181715A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/06—Diaphragms
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
    • G01N23/20—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by using diffraction of the radiation by the materials, e.g. for investigating crystal structure; by using scattering of the radiation by the materials, e.g. for investigating non-crystalline materials; by using reflection of the radiation by the materials
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05G—X-RAY TECHNIQUE
    • H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor

Definitions

  • the present invention relates to a radiation phase difference imaging apparatus capable of imaging an internal structure of an object using a phase difference of radiation transmitted through the object, and a radiation source provided therein.
  • Such a radiation imaging apparatus can only capture an object having a property of absorbing radiation to some extent. For example, living soft tissue hardly absorbs radiation. Even if such a tissue is photographed with a general device, the projection image shows almost nothing. Thus, when attempting to image the internal structure of an object that does not absorb radiation, a general radiographic apparatus has a theoretical limit.
  • a radiation phase difference imaging apparatus that images the internal structure of an object using the phase difference of transmitted radiation.
  • Such an apparatus uses Talbot interference to image the internal structure of an object.
  • the radiation source 53 shown in FIG. 14 emits radiation in phase.
  • an image of the phase grating 55 appears on a projection plane separated from the phase grating 55 by a predetermined distance (Talbot distance).
  • This image is called a self-image.
  • the self image is not simply a projection image of the phase grating 55.
  • the self-image occurs only at a position where the projection plane is separated from the phase grating 55 by the Talbot distance.
  • the self-image is composed of interference fringes generated by light interference.
  • the reason why the self-image of the phase grating 55 appears at the Talbot distance is that the phases of the radiation generated from the radiation source 53 are aligned. When the phase of radiation is disturbed, the self-image that appears in the Talbot distance is also disturbed.
  • the radiation phase contrast imaging device uses the disturbance of the self-image to image the internal structure of the object. Assume that an object is placed between the radiation source and the phase grating 55. Since this object hardly absorbs radiation, most of the radiation incident on the object is emitted to the phase grating 55 side.
  • phase of the radiation changes while passing through the object.
  • the radiation emitted from the object passes through the phase grating 55 with its phase changed.
  • this radiation is observed on the projection plane placed at the Talbot distance, the self-image of the phase grating 55 is disturbed. This degree of disturbance of the self-image represents a change in the phase of the radiation.
  • phase change The extent to which the phase of the radiation that has passed through the object is specifically changed depends on where the radiation has passed through the object. If the object has a homogeneous configuration, the change in the phase of the radiation is the same everywhere in the object. However, in general, an object has some internal structure. If radiation is transmitted through such an object, the phase change will not be the same.
  • the internal structure of the object can be known.
  • the change in phase can be known by observing the self-image of the phase grating 55 at the Talbot distance.
  • detection of a self-image is performed by a radiation detector.
  • the radiation detector has a detection surface for detecting radiation, and the radiation detector can image the self image by projecting the self image on the detection surface (see, for example, Patent Document 1).
  • Coherent radiation refers to radiation that is in phase.
  • the radiation phase difference imaging apparatus is intended to detect a change in the phase of radiation that occurs when radiation passes through a subject. Therefore, the radiation before hitting the subject must be in phase.
  • the radiation having the same phase can be generated from the radiation source 53 having a narrow radiation generation region.
  • the radiation source 53 has a drawback that the radiation output is weak.
  • a configuration using a higher output radiation source 53 is employed. If the output of the radiation source 53 is to be increased, the radiation generation area needs to be increased accordingly, and the coherency of the radiation is lost.
  • the radiation is allowed to pass through a multi-slit as shown on the left side of FIG.
  • the multi-slit is composed of a member that absorbs radiation, and is provided with a plurality of slits as shown on the right side of FIG. Radiation can pass through the multi slit only from the opening of the slit.
  • the radiation that has passed through one slit has high coherency. With this alone, the radiation output remains weak.
  • the multi slit has a plurality of slits. Therefore, the dose of radiation that passes through the multi-slit increases in accordance with the number of slits provided in the multi-slit. By this device, the dose of the radiation source 53 is high enough to be used for imaging.
  • the conventional radiation source has the following problems. That is, the radiation source of the conventional configuration can still output only a low dose of radiation. This is because, in order to maintain high coherency, it is necessary to sufficiently narrow the width of each slit constituting the multi-slit.
  • the conventional radiation source has a configuration suitable for imaging that requires high coherency by sufficiently narrowing the width of each slit constituting the multi-slit.
  • various types of imaging using a radiation source and there are some imaging that prioritizes dose over coherency.
  • the present invention has been made in view of such circumstances, and its purpose is to adjust the dose and coherency by enabling the width of each slit constituting the multi-slit to be changed. It is to provide a radiation source that can be used.
  • the present invention has the following configuration in order to solve the above-described problems. That is, in the radiation source according to the present invention, slits that transmit the radiation generated at a single generation point are arranged at a constant pitch in an orthogonal direction that is a direction orthogonal to the extending direction of the slit, and the slits are provided.
  • a multi-slit that absorbs radiation incident on the non-slit part, a shield that outputs only radiation incident on a part of the multi-slit by restricting the spread of radiation in the slit extension direction, and a radiation generation point
  • a moving part that moves the relative position between the shield and the multi-slit in the slit extending direction, and each of the slits provided in the multi-slit is provided with a narrow part and a wide part in the orthogonal direction. It is characterized by that.
  • the dose and coherency can be adjusted by changing the width of each slit constituting the multi-slit. That is, each of the slits provided in the multi-slit of the present invention is provided with a narrow portion and a wide portion. When radiation is applied to a portion where the slit width of the multi-slit is narrow, the coherency of the radiation passing through the multi-slit is high and the dose becomes small. In addition, when radiation is applied to a portion where the slit width of the multi-slit is wide, the coherency of the radiation passing through the multi-slit is low and the dose is increased. According to the present invention, by providing the moving unit, it is possible to change the portion of the multi-slit where the radiation hits, so that it is possible to adjust the radiation dose and the coherency according to the purpose of imaging.
  • the slit provided in the multi-slit has a taper shape in which the width in the orthogonal direction gradually increases from one end to the other end in the extending direction.
  • the dose and coherency can be adjusted by making it possible to change the width of each slit constituting the multi-slit. That is, each of the slits provided in the multi-slit of the present invention is provided with a narrow portion and a wide portion. According to the present invention, by providing the moving unit, it is possible to change the portion of the multi-slit where the radiation hits, so that it is possible to adjust the radiation dose and the coherency according to the purpose of imaging.
  • FIG. 1 is a functional block diagram for explaining an X-ray source according to Embodiment 1.
  • FIG. It is a top view explaining the shielding body concerning Example 1.
  • FIG. 3 is a plan view for explaining a multi-slit according to Embodiment 1.
  • FIG. 3 is a schematic diagram illustrating an X-ray beam according to Embodiment 1.
  • FIG. 6 is a schematic diagram for explaining adjustment of X-ray dose and coherency according to the first embodiment.
  • FIG. 6 is a schematic diagram for explaining adjustment of X-ray dose and coherency according to the first embodiment.
  • FIG. 6 is a schematic diagram for explaining adjustment of X-ray dose and coherency according to the first embodiment.
  • FIG. 6 is a schematic diagram for explaining adjustment of X-ray dose and coherency according to the first embodiment.
  • FIG. 6 is a schematic diagram for explaining adjustment of X-ray dose and coherency according to the first embodiment. It is a functional block diagram explaining the apparatus carrying the X-ray source which concerns on Example 1.
  • FIG. It is a schematic diagram explaining the apparatus carrying the X-ray source which concerns on Example 1.
  • FIG. 3 is a schematic diagram illustrating an absorption grating according to Example 1.
  • FIG. It is a schematic diagram explaining the modification which concerns on this invention.
  • It is a schematic diagram explaining the modification which concerns on this invention.
  • It is a schematic diagram explaining the modification which concerns on this invention.
  • the radiation source according to the present invention is assumed to be a radiation phase difference imaging apparatus, it can also be mounted on other apparatuses.
  • X-rays correspond to the radiation of the present invention.
  • FIG. 1 is a functional block diagram showing the configuration of the X-ray source 3 according to the present invention.
  • an X-ray source 3 according to the present invention includes an anode 3 a that collides with electrons, a shield 3 b that limits the spread of X-rays radiated from the anode 3 a, and an X that has passed through the shield 3 b. And a multi slit 3c through which a line is incident.
  • the anode 3a is an electron target, and X-rays are generated when high-speed electrons collide. X-rays occur at a single focal point p.
  • the shield 3 b is configured by a member that absorbs X-rays having a window W that allows X-rays to pass therethrough.
  • the window W is a through hole provided in the shield 3b.
  • the X-ray beam that has passed through the window W becomes a fan-shaped beam that is narrow in the vertical direction Y and wide in the horizontal direction X in FIG. This X-ray beam is a beam from the focal point p toward the depth direction Z.
  • the X-ray beam is a beam that is narrow in the vertical direction Y and wide in the paper penetration direction.
  • the shield 3b limits only the X-ray spread in the extending direction of the slit S, thereby outputting only the X-rays incident on a part of the multi-slit 3c.
  • the fan-shaped X-ray beam emitted from the shield 3b enters the multi-slit 3c.
  • the multi slit 3c is made of a material such as gold that can be easily processed, and has a thickness that does not allow X-rays to pass therethrough.
  • the multi-slit moving mechanism 3d is configured to move the multi-slit 3c in the vertical direction Y with respect to the anode 3a and the shield 3b as shown in FIG.
  • the multi-slit 3c moves with respect to the focal point on the anode 3a and the shield 3b. Will move. Then, the position where the fan-shaped X-ray beam is incident on the multi-slit 3c changes.
  • the multi-slit movement control unit 3e is configured to control the multi-slit movement mechanism 3d.
  • the operation panel 3f is configured to input an operator instruction regarding the movement of the multi slit 3c.
  • the multi-slit movement control unit 3e controls the multi-slit movement mechanism 3d to realize the movement of the multi-slit 3c instructed by the operator.
  • the multi-slit moving mechanism 3d moves the X-ray generation point and the relative position between the shield 3b and the multi-slit 3c in the extending direction (longitudinal direction Y) of the slit S.
  • the multi-slit moving mechanism 3d corresponds to the moving unit of the present invention.
  • FIG. 3 illustrates the multi slit 3c of the present invention.
  • the multi slit 3 c has a configuration in which slits S extending in the vertical direction Y are arranged in the horizontal direction X.
  • Each of the slits S is a through hole of the multi slit 3c.
  • the slits S are arranged at equal intervals in the horizontal direction X.
  • FIG. 3 shows the configuration of the multi slit 3c.
  • the multi slit 3c has a rectangular shape.
  • the slit S provided in the multi slit 3c has an elongated shape extending from the upper end to the lower end of the multi slit 3c.
  • the shape of the slit S is characteristic. That is, the lateral width of the slit S is gradually increased from the upper end to the lower end of the multi slit 3c, and the slit S is tapered as a whole. More specifically, the slit S has a symmetrical trapezoidal shape about a central axis C extending in the vertical direction Y. All of the slits S provided in the multi slit 3c have the same shape, and the upper side is narrow and the lower side is wide.
  • Each of the slits S provided in the multi slit 3c is arranged in the horizontal direction X.
  • the central axis C of the slits S is separated by a certain arrangement pitch D. Therefore, the arrangement pitch of the slits S is constant. Further, when considering a line segment crossing each slit S, the horizontal width of each slit S on the line segment is the same. This horizontal width relationship holds regardless of where the line segment is set.
  • FIG. 3 shows a state in which the fan-shaped X-ray beam emitted from the shield 3b enters the multi slit 3c.
  • the fan-shaped X-ray beam is incident only on a partial region of the multi slit 3c.
  • the fan-shaped X-ray beam is absorbed by the multi slit 3c. Since the multi slit 3c is provided with the slit S, only the X-rays that can pass through the slit S can be emitted from the multi slit 3c. Therefore, the fan-shaped X-ray beam emitted from the shield 3b passes through the multi slit 3c and is divided into a plurality of fragments as shown in FIG.
  • the separation distance of each piece is the arrangement pitch D of the slits S.
  • the multi-slit 3c of the present invention has an orthogonal direction (lateral direction X) in which the slit S that transmits X-rays generated at a single generation point is orthogonal to the extending direction (longitudinal direction Y) of the slit S. ) At a constant pitch, and absorbs X-rays incident on the portion where the slit S is not provided.
  • Each of the slits S provided in the multi slit 3c is provided with a narrow portion and a wide portion in the orthogonal direction (lateral direction X).
  • the slit S provided in the multi-slit 3c has a taper shape in which the width in the orthogonal direction (lateral direction X) gradually increases from one end to the other end in the extending direction (vertical direction Y).
  • the region on the multi-slit 3c where the fan-shaped X-ray beam is incident is moved up and down accordingly.
  • the region on the multi-slit 3c where the fan-shaped X-ray beam is incident moves downward.
  • the region on the multi-slit 3c where the fan-shaped X-ray beam is incident moves upward.
  • FIG. 5 shows a state where the fan-shaped X-ray beam emitted from the shield 3b is incident on the upper end of the multi-slit 3c by moving the multi-slit 3c.
  • the X-ray beam passes through the narrow slit S, the dose of the X-ray beam emitted from the multi slit 3c becomes small.
  • this X-ray beam passes through a narrow slit, it has high coherency.
  • FIG. 6 shows the X-ray beam that has passed through the multi-slit 3c when the fan-shaped X-ray beam emitted from the multi-slit 3c and the shield 3b has the positional relationship described with reference to FIG.
  • the X-ray beam is fragmented by the multi slit 3c.
  • the width of each fragment is narrow.
  • the separation distance between the pieces remains the arrangement pitch D of the slits S.
  • FIG. 7 shows a state where the fan-shaped X-ray beam emitted from the shield 3b is incident on the lower end of the multi-slit 3c by moving the multi-slit 3c.
  • the X-ray beam passes through the wide slit S, the dose of the X-ray beam emitted from the multi slit 3c increases.
  • this X-ray beam is transmitted through a wide slit, the coherency is low.
  • FIG. 8 shows the X-ray beam that has passed through the multi-slit 3c when the fan-shaped X-ray beam emitted from the multi-slit 3c and the shield 3b has the positional relationship described in FIG.
  • the X-ray beam is fragmented by the multi slit 3c.
  • the width of each fragment is wide.
  • the separation distance between the pieces remains the arrangement pitch D of the slits S.
  • the dose and coherence of the X-rays passing through the multi-slit 3c change, and the separation distance of each fragment of the fragmented X-ray beam does not change.
  • FIG. 9 shows the overall configuration of the photographing apparatus 1 according to the present invention.
  • the imaging apparatus 1 is generated from a mounting table 2 on which a subject M is mounted, an X-ray source 3 that is provided on the mounting table 2 and that emits an X-ray beam, and an X-ray source 3.
  • An FPD (flat panel detector) 4 that detects X-rays transmitted through the subject M on the mounting table 2 is provided.
  • a phase grating 5 that causes Talbot interference is provided at a position between the FPD 4 and the mounting table 2.
  • the X-ray beam irradiated from the X-ray source 3 is an X-ray beam after passing through the multi slit 3c as described with reference to FIG.
  • the imaging apparatus 1 is a radiation imaging apparatus using Talbot interference. Therefore, the X-ray source 3 is configured to output an X-ray beam having the same phase.
  • the distance between the phase grating 5 and the FPD 4 is set to the Talbot distance. With this setting, the self-image of the phase grating 5 appears on the detection surface for detecting the X-rays of the FPD 4.
  • the separation distance of the X-ray beam fragments described in FIG. 4 is one of the factors that determine the Talbot distance. According to the present invention, even if the multi slit 3c is moved, the separation distance of the fragments does not change. Therefore, even if the dose and coherency of the X-ray source 3 are adjusted by moving the multi slit 3c, the Talbot distance does not fluctuate.
  • the imaging system moving mechanism 13 is configured to move the X-ray source 3, the FPD 4, and the phase grating 5 with respect to the mounting table 2 while maintaining the mutual positional relationship as shown in FIG.
  • the X-ray source 3, the FPD 4, and the phase grating 5 can be moved in a direction parallel to the mounting table 2 by the imaging system moving mechanism 13.
  • the imaging system moving mechanism 13 is configured so that the projection of the subject M moves linearly on the detection surface of the FPD 4 while the positional relationship between the X-ray source 3, the phase grating 5, and the FPD 4 is maintained. And the relative position of the subject M is changed.
  • the imaging systems 3, 4, and 5 have a phase in which an X-ray source 3 that irradiates X-rays and an absorption line 5 a that extends in one direction that absorbs radiation as shown in FIG. 11 are arranged in a direction orthogonal to one direction. It comprises a grating 5 and an FPD 4 that detects a self-image of the phase grating 5 generated by Talbot interference on a detection surface in which detection elements for detecting radiation are arranged vertically and horizontally.
  • the direction in which the absorption line 5a of the phase grating 5 shown in FIG. 11 extends coincides with the direction in which the slit S of the multi-slit 3c of the X-ray source 3 extends.
  • the relative position of the subject M with respect to the imaging systems 3, 4, and 5 is changed by moving the imaging systems 3, 4, and 5 without moving the subject M.
  • the imaging system movement control unit 14 is provided for the purpose of controlling the imaging system movement mechanism 13.
  • the X-ray source control unit 6 is provided for the purpose of controlling the X-ray source 3. During imaging, the X-ray source control unit 6 controls the X-ray source 3 so as to repeatedly output the X-ray beam in a pulse shape. Each time the X-ray source 3 outputs an X-ray beam, the FPD 4 detects X-rays that have passed through the subject M and the phase grating 5 on the mounting table 2 and sends detection data to the self-image generation unit 11. As described above, the apparatus of the present invention is configured to generate a self-image by continuously shooting X-ray imaging.
  • X-ray imaging continuous shooting is realized by the X-ray source control unit 6 and the imaging system movement control unit 14 cooperating with each other.
  • the results of continuous X-ray imaging are sent to the self-image generation unit 11 where they are joined together to form a single self-image.
  • the fluoroscopic image generation unit 12 generates a fluoroscopic image in which the phase difference of X-rays generated in the subject M is imaged based on the self-image generated by the self-image generation unit 11.
  • the priority can be given to the X-ray dose.
  • the quality of X-rays can be made suitable for the purpose of imaging.
  • the main control unit 21 shown in FIG. 9 is provided for the purpose of comprehensively controlling the units 6, 11, 12, and 14.
  • the main control unit 21 is constituted by a CPU, and realizes each unit by executing various programs. In addition, each of these units may be divided and executed by an arithmetic device in charge of them. Each unit can access the storage unit 27 as necessary.
  • the console 25 is provided for the purpose of inputting operator instructions.
  • the display unit 26 is provided for the purpose of displaying a fluoroscopic image.
  • the dose and coherency can be adjusted by making it possible to change the width of each slit S constituting the multi-slit 3c. That is, each of the slits S provided in the multi slit 3c of the present invention is provided with a narrow portion and a wide portion.
  • the coherence of X-rays passing through the multi-slit 3c is high and the dose is reduced.
  • the coherence of the X-rays passing through the multi-slit 3c is low and the dose is increased.
  • the moving unit by providing the moving unit, it is possible to change the portion of the multi-slit 3c that is irradiated with X-rays. Therefore, the X-ray dose and coherency can be adjusted according to the purpose of imaging.
  • the X-ray dose and coherence can be adjusted steplessly.
  • the present invention is not limited to the configuration described above, and can be modified as follows.
  • the slit S provided in the multi slit 3c is tapered, but the present invention is not limited to this configuration.
  • the slit S may be composed of a plurality of regions R1, R2, and R3.
  • the width of the slit S in the region R1 is constant at a narrow width
  • the width of the slit S in the region R2 is constant at an intermediate width
  • the width of the slit S in the region R3 is wide. It is constant.
  • the vertical width of the fan-shaped X-ray beam emitted from the shield 3b is smaller than the vertical width of the regions R1, R2, and R3. That is, the multi-slit 3c has a region R1 in which the width of the slit S is a narrow width and a region R3 in which the width of the slit is a wide width.
  • the fan-shaped X-ray beam emitted from the shield 3b can be incident only on the region R1, or can be incident only on the region R2.
  • a fan-shaped X-ray beam emitted from the shield 3b can be incident only on the region R3.
  • the width of the slit S is constant. Therefore, if the fan-shaped X-ray beam emitted from the shield 3b is incident only on the region R1, the X-ray beam passes through a slit having a certain width. Then, the coherent property of the X-ray beam that has passed through the multi-slit 3c is partially uniform and constant. Similarly, the dose of the X-ray beam that has passed through the multi-slit 3c is partially uniform and constant. Such a situation is the same when the fan-shaped X-ray beam emitted from the shield 3b is applied to the regions R2 and R3.
  • FIG. 12 has three regions with different slit widths, but the number of regions can be freely adjusted.
  • the shield 3b is disposed at a position between the anode 3a and the multi slit 3c, but the present invention is not limited to this configuration.
  • the multi slit 3c may be arranged at a position where the anode 3a and the shield 3b are sandwiched.
  • the multi-slit 3c moves with respect to the anode 3a and the shield 3b.
  • the anode 3a and the shield 3b move with respect to the multi-slit 3c. It is good also as a structure which does.
  • an absorption grating may be disposed so as to cover the incident surface.
  • the absorption grating has the same shape as the phase grating 5 described with reference to FIG. 11, and has a configuration in which absorption lines are arranged in parallel at a predetermined pitch.
  • the present invention is suitable for the medical field.

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Abstract

L'invention concerne une source de rayonnement avec laquelle la dose et la cohérence peuvent être ajustées par modification de la largeur des fentes constituant une configuration à multiples fentes. Des fentes individuelles (S) apportées à ladite configuration à multiples fentes sont dotées de sections (3c) qui sont étroites et de sections qui sont larges. Selon la présente invention, par la fourniture d'une partie mobile, les sections qui sont frappées par les rayons X dans la configuration à multiples fentes (3c) peuvent être modifiées, ce qui permet d'ajuster la dose et la cohérence des rayons X selon l'effet d'imagerie souhaité.
PCT/JP2016/059968 2015-05-12 2016-03-28 Source de rayonnement et dispositif d'imagerie par contraste de phase de rayonnement en étant doté WO2016181715A1 (fr)

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JP2017517640A JP6372614B2 (ja) 2015-05-12 2016-03-28 放射線源およびそれを備えた放射線位相差撮影装置

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Citations (6)

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JPH0432800A (ja) * 1990-05-30 1992-02-04 Hitachi Ltd Ｃｔ装置及び透過装置並びにｘ線発生装置
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