JP3334747B2 - High-speed X-ray shutter - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an X-ray irradiation control apparatus for controlling the opening and closing of an X-ray beam to be irradiated, and more particularly, to reducing the amount of X-ray exposure of a patient in the imaging of a moving image of a cardiovascular system by X-rays. The present invention relates to an X-ray irradiation control device provided in the device.

[0002]

2. Description of the Related Art Conventionally, a technique of a coronary angiography apparatus (SR angiography) of a two-dimensional moving image system using synchrotron radiation has been completed by accumulating a track record through animal experiments and then applying it to clinical practice. And a sufficiently clear coronary artery image can be obtained even when a contrast medium is injected from a vein. In animal experiments, moving images are obtained by continuously irradiating the sample with X-rays, but in order to eliminate blurring of images due to heart pulsation, the imaging time per frame must be kept to about 4 msec. Must. In addition, since the imaging device and the display device which are generally used set the reading and displaying interval of the image signal to 33 msec, X-rays are unnecessarily exposed for a period of 29 msec, which is the difference between the two, for each frame photographing.

[0003] As long as the imaging apparatus for intermittently shooting frames to obtain a moving image is used, the period during which X-ray irradiation is required is limited to a part of the entire period. Are receiving unnecessary exposure. Such a situation is not limited to angiography, and is the same in an in vivo trace element detection system and the like. However, in order to use such a diagnostic device in a clinical setting for humans, it is preferable to minimize X-ray exposure of a patient.

[0004]

SUMMARY OF THE INVENTION An object of the present invention is to provide a two-dimensional moving image coronary angiography apparatus or the like using synchrotron radiation to minimize X-ray exposure of a subject. To provide an X-ray irradiation control device capable of receiving a diagnosis more safely.

[0005]

In order to solve the above-mentioned problems, an X-ray irradiation control apparatus according to the present invention rotates a rotating drum having an opening through which X-rays pass in a direction perpendicular to a rotation axis at a predetermined speed. X for a certain short period at regular intervals
A rotating drum type X-ray beam switchgear having an X-ray shutter mechanism to obtain the intermittent emission light is passed through the line, rotary Dora
X-ray opening of the system is defined by radiation from the rotation axis
It has a flared opening. In particular, the X-ray is passed through the X-ray imaging apparatus that captures the X-ray image of the subject for a time corresponding to the exposure time for capturing the X-ray image at every integral multiple of the acquisition interval of the plane image signal. Is preferable.

According to the X-ray irradiation control device of the present invention, since the irradiation X-rays are passed only for a short period of time during a certain period, the X-ray exposure of a subject such as a person can be minimized. . Further, since a trigger signal synchronized with the X-ray passage period is generated, a device for capturing an X-ray image accurately measures a necessary exposure timing by using the trigger signal to obtain a moving image required for diagnosis. Can be obtained. Note that, for example, in a normal imaging device such as a CCD camera, CR is used.
In many cases, moving pictures are taken by taking 30 frames per second in accordance with the specifications of the T display, but even in this case, the exposure time required for imaging is short and the time used for signal processing such as video signal extraction is long. .

Therefore, if the X-ray is passed through the exposure time necessary for capturing the X-ray image at every acquisition interval of the plane image signal in the X-ray imaging device or at an interval of an integral multiple of the acquisition interval, the X-ray imaging device can be used for imaging. Necessary diagnosis can be made only by receiving necessary minimum X-ray exposure. In order to obtain a smooth moving image, it is preferable to take an image every 1/30 second and display it. X-rays may be opened and closed at intervals of an integral multiple of the acquisition interval of the screen image signal of the imaging device.

The X-ray irradiation control device of the present invention can be used for capturing a moving image of a cardiovascular system using emitted light. At this time, for example, in angiography using X-rays, it is said that it is better to suppress the photographing time of one frame to about 4 msec in order to prevent image deterioration due to the heartbeat, so that exposure can be suppressed as described above. If 33ms
Unnecessary exposure of about 29 msec during ec can be eliminated.

Further, the detecting mechanism has a mechanism for adjusting a timing for detecting a state in which the X-ray is passing through the X-ray shutter mechanism, and has a delay circuit for delaying a timing at which the signal processing device outputs a trigger signal. Thus, a function of adjusting the timing of sending the trigger signal with respect to the passage of X-rays can be provided. If the trigger signal is generated after detecting that the X-ray has passed through the shutter mechanism, the control of the imaging apparatus may not be able to keep up.
For this reason, if a signal is generated at a timing earlier than the X-ray actually passes, and a trigger signal is generated at an optimum timing with an appropriate delay circuit,
The timing of the X-ray irradiation and the photographing accurately match, and a high-quality moving image can be obtained.

[0010] A rotating drum having an opening in a direction perpendicular to the rotation axis can be used as an X-ray shutter mechanism. Such an X-ray shutter mechanism can transmit X-rays at a predetermined period for a predetermined period of time very simply by constant-speed rotation, and can also be very easily rotated at a constant speed. The present invention is, X-rays pass through the opening of the rotary drum have a flared opening defined by the radiation from the axis of rotation
It is characterized by doing . The opening having such a shape rapidly changes while the distance of transmission of X-rays through the shielding material is short, so that the rising portion and the falling portion of the pulsed amount of X-ray transmission amount change. This has the effect of steepening the slope.

Further, a windshield can be provided at the opening of the rotating drum. In addition, the X-ray passage opening of the rotating drum can be covered with a substance having a high X-ray transmittance. Since the rotating drum rotates at a very high speed, the edge of the opening generates wind noise, which is not only annoying to the ear but also may give anxiety to the patient to be diagnosed. The generation of such wind noise can be suppressed by attaching a windshield to the opening or covering the opening with a substance having a high X-ray transmittance.

The diameter of the rotary drum is preferably 120 mm or more. If the pulse of the irradiation X-ray output has a steep rising and falling shape, meaningless X-ray exposure can be reduced. In the rotary drum type X-ray shutter mechanism, the pulse transition time becomes longer as the diameter of the drum is smaller. Therefore, by setting the diameter of the rotating drum to be 120 mm or more, a transition time of about 1 msec when irradiating 4 msec every 33 msec with an X-ray beam having a thickness of about 7 mm used in synchrotron radiation angiography.
It is desirable to suppress to the extent.

The X-ray beam opening / closing device preferably includes a shield covering the X-ray shutter mechanism that radiates and scatters the emitted light. In the shield covering,
A window for passing necessary intermittent radiation light is provided, and an opening / closing window for exchanging the X-ray shutter mechanism can be provided. The X-ray shutter mechanism receives radiated light including X-rays during the X-ray shielding period and generates scattered radiation. When the scattered radiation reaches a subject or an operator, X-ray exposure occurs. Therefore, the shield coating prevents the scattered radiation from leaking to the surroundings, thereby reducing unnecessary X-ray exposure. It is preferable that a sliding-type opening / closing window is attached to a part of the shield wall so that the X-ray shutter mechanism can be maintained and the drum can be replaced.

[0014]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS An X-ray irradiation control apparatus according to the present invention will be described below in detail with reference to the drawings.
FIG. 1 is a perspective view schematically showing an arrangement example when the X-ray irradiation control device of the present embodiment is used for synchrotron radiation angiography. Electrons 2 emitted from an electron injector 1 composed of an electron gun or the like are injected into an electron orbit 4 of an electron storage ring 3 and are caused to travel around the orbit by bending electromagnets 5, 5,. An insertion light source 6 such as a wiggler is interposed in a linear portion between predetermined bending electromagnets 5 in the electron storage ring 3. The electrons orbiting the electron storage ring 3 generate radiation 7 containing strong X-rays when passing through the insertion power supply 6.

The emitted light is guided to the spectroscope, and is subjected to Bragg reflection by the spectroscopic crystal of the spectroscope 9 to become monochromatic X-rays 10, transmitted through the heart of the patient 11 and incident on the image intensifier 12. Image intensifier 1
Reference numeral 2 denotes a device for converting X-rays into visible light, and reads an image converted into visible light by a CCD camera 13 provided behind the device. The image signal output from the CCD camera 13 is recorded in the image processing device 14 and stored as a diagnostic image. The CCD camera 13 is a camera controller 17
It is configured to be able to be controlled via a. In this coronary angiography system, an X-ray irradiation control device 8 is installed between the insertion light source 6 and the spectroscope 9 in the course of the radiation light including X-rays.

In coronary angiography using synchrotron radiation, it is considered that the exposure time for taking one image is preferably about 4 msec in order to eliminate blurring of the image due to the pulsation of the heart. On the other hand, a general imaging device normally shoots 30 frames per second, and the image signal is read out during this time. Therefore, the next image cannot be captured 33 msec after the start of shooting. Therefore, in a method in which X-rays are continuously applied to a subject as in a conventional animal experiment, there is an X-ray irradiation period of 29 msec that is not useful for imaging, and X-ray exposure during this period is meaningless. X-ray irradiation control device 8 of the present invention
Is a shutter that allows X-rays to pass for an exposure time necessary for imaging, and blocks X-rays at other times. By using such a shutter device, unnecessary X-ray exposure can be minimized.

The X-ray irradiation control device 8 includes an X-ray shutter mechanism and a signal processing device 16 which detects the passage of X-rays and generates a trigger signal 15. A trigger signal 15 for starting image reading by the CCD camera 13 is provided. To the camera controller 1
Send to 7. Since the trigger signal 15 is output in synchronization with the timing at which the X-ray irradiation control device 8 allows X-rays to pass, the X-ray 10 starts passing through the X-ray irradiation control device 8 and at the same time, the image capture of the CCD camera 13 is started. The exposure is started during the time when the X-ray that has passed is irradiated to the patient, and an image signal is accumulated in each pixel. After the irradiation for the required time, the CCD camera 13 scans the screen and performs serial communication until the next image capturing timing when the X-ray 10 is blocked by the X-ray irradiation control device 8 and the X-ray exposure of the patient is controlled. It is output to the image processing device 14 as a plane image signal. The image processing device 14 records the input surface image signal in an image memory or a magnetic recording medium.

FIG. 2 is a perspective view showing the structure of the X-ray irradiation control device of the present embodiment. The X-ray irradiation control device 8 has a structure in which the X-ray passes through the X-ray transmission hole 20 for passing X-rays at a predetermined speed and passes X-rays for a certain period of time at a certain period, and a direction perpendicular to the rotation axis. A cylindrical rotary drum 21 having an opening 20 is rotatably supported by a bearing 23 fixed on a base 22, and is rotated by a drum rotating motor 24. When the X-ray transmitting hole 20 matches the optical path of the emitted light, the emitted light containing X-rays goes straight and reaches the spectroscope 9, and when the X-ray transmitting hole 20 deviates from the optical path, the emitted light is cut off and the patient is blocked. Will escape X-ray exposure. The drum rotation motor 24 is a motor whose rotation speed can be adjusted, whereby the cycle through which X-rays pass can be precisely controlled.

The timing of the passage of X-rays is detected by three detectors: an optical sensor, a proximity sensor, and an encoder, and is processed by the signal processor 16. The optical sensor and the proximity sensor detect the rotational position of the rotary drum 21 by a disk attached to the side of the rotary drum 21 and output a signal according to the actual radiation light passage timing. FIG. 3 is an enlarged perspective view showing a part of the rotary drum. Rotating drum 21
A disk 25 for the optical sensor and a disk 26 for the proximity sensor are fixed to the sides. The optical sensor disk 25 is provided with a hole 27 for detecting the passage of light passing through the axis in the radial direction. The optical sensor disk 25 is rotated so that the hole 27 is located at the same position as the X-ray transmission hole 20. It is attached to the drum 21. Also,
A notch 28 having a depth to which the proximity sensor responds is provided on the circumferential surface of the proximity sensor disk 26, and the proximity sensor disk 26 is rotated so that the notch 28 is located at the same position as the X-ray transmission hole 20. It is attached to the drum 21.

The light sensor comprises a light emitter 29 and a light receiver 30 provided at the same height as the incident radiation 7, and light projected from the light emitter 29 passes through the light passage hole 27 of the optical sensor disk 25. While passing through and entering the light receiving element 30, a detection signal is output from the optical sensor. The proximity sensor 31 is also installed at the same height as the emitted light 7, and a detection signal is output from the proximity sensor 31 while detecting the cut 28 of the opposed proximity sensor disk 26. The signal processing device 16 catches the rise of these detection signals and sets them as trigger signals, and sends them to the camera device. Further, the rotating drum 21
An encoder 32 for detecting a rotation phase is provided at the tip of the rotation shaft.
Is installed. The encoder 32 is connected to the rotating drum 21
Sends a trigger signal to the camera device 13 when it comes to the rotation position where the X-ray 7 starts to pass. When the operation is stopped and the drum is stopped, a motor 33 such as a pulse motor is provided to control the rotation angle of the drum so that the rotation angle of the drum comes to the closed position with the opening being vertical. I have.

As described above, since the passing state of the radiated light is detected by the sensors having three different principles, it is possible to avoid a situation in which the operation becomes impossible even if one of the detectors breaks down. The above is the description of the X-ray irradiation control device of the present embodiment.
This is a basic concept of a method of detecting a passage of X-rays and sending a trigger signal synchronized with the detection to the camera device. However, actually, the time for the sensor to detect and the time for signal processing are not zero, and a certain time delay occurs. Therefore, the rotation position of the drum, which is a reference for outputting a trigger signal from the encoder 32, is set slightly before the position of the X-ray passage hole 20, and the light passage hole 27 of the optical sensor disk 25 and the proximity sensor disk are set. Each disk is set on the drum 21 so that the cut 28 of 26 is located slightly before the position of the X-ray passage hole 20. In this manner, the detection signal is output earlier by the delay of the trigger signal 15 reaching the camera device 13 due to signal processing or the like. If the detection signals are set to be output a little earlier, and the signals that are too early are delayed by a delay circuit provided in the signal processing device 14, the adjustment is easy.

FIG. 4 is a view showing a state in which a rotating drum used as an X-ray shutter mechanism in the present embodiment allows emitted light to pass therethrough. FIG. 4 is a cross-sectional view of a rotating drum 21 having an X-ray passage hole 20 cut along a plane perpendicular to a rotation axis along an optical path of the radiated light 7. The radiated light 7 including X-rays has a certain thickness (vertical Direction width) hb. The cross-sectional shape of the X-ray passage hole 20 has a width that allows the emitted light beam 7 to sufficiently pass at the axial position, and has a divergent fan shape defined by the radiation from the rotation axis. When the X-ray passing hole 20 having such a shape is used, the distance that the radiated light 7 transmits through the shielding material changes rapidly due to the rotation of the rotary drum 21.
The rising and falling of the pulse of the line transmission amount becomes steep. FIG. 4A shows a state where the radiation 7 has completely started to pass, and FIG.
(C) shows where the radiation 7 has begun to be blocked, and (d) shows the time when the radiation 7 has been completely blocked.

FIG. 5 is a view showing a state in which the transmitted dose of X-ray changes due to the intervention of the X-ray shutter mechanism. The horizontal axis represents time, and the vertical axis represents transmitted X-ray dose on an arbitrary scale. Transmission X
The dose has a pulse-like waveform that is repeated at regular intervals. The pulse period Tr is 33 m in accordance with the fact that the image signal read by the CCD camera 13 is performed 30 times per second.
sec. Arrows (a), (b), and (c) in the figure
(D) shows the times in the states of (a), (b), (c), and (d) in FIG. The radiation 7 starts to leak from the edge of the X-ray passage hole 20 in a state where it is completely blocked,
Eventually, the rotating drum 21 rotates by the thickness of the emitted light beam 7, and the state changes to the state (a) where the emitted light 7 completely passes through the X-ray passage hole 20. After that, during the time Te from the state (a) to the state (c), the radiated light passes without being interrupted, irradiates the patient 11, forms an X-ray transmission image on the image intensifier 12, Exposure time.
The rotating drum 21 further rotates, and the wall of the X-ray passage hole 20 blocks the emitted light beam 7 little by little to reach the state (d).
The rise time from the X-ray cutoff state to the state (a) and the time from the states (c) to (d) are the transient times T, respectively.
t.

By making the X-ray passage hole 20 of the rotary drum 21 sector-shaped, the radiation 7 can transmit the X-ray shielding material of the rotary drum 21 during the transition time Tt, for example, from the state (c) to the state (d). Since the distance through which the light is transmitted rapidly increases and the state can be immediately shifted to the completely shut-off state, the irradiation X-ray dose during the transient time, which is unnecessary exposure, can be reduced. FIG. 6 is a drawing for explaining the design principle of the X-ray passage hole. X-ray passing hole 2
The shape of 0 can be determined by the following procedure. In FIG. 6, the rotation angle of the drum during the transition time Tt from the state (c) to the state (d) is the angle at which the radiation light beam on the drum outer periphery is viewed from the drum center, that is, the angle 2θb sandwiching the thickness hb of the radiation light beam. Is equivalent to On the other hand, the repetition period T
The rotation angle of the drum during r is π. Therefore, since the rotational speed of the drum is constant, the beam expected angle 2θb is expressed by the following equation from a proportional relationship. 2θb = π · Tt / Tr (1)

Also, from the geometric relationship in FIG.
The radius R of the rotating drum is expressed by the half θb of the expected beam angle and the thickness hb of the emitted light beam as follows. R = hb / 2 sin θb (2) On the other hand, the drum opening angle θo corresponds to the rotation angle from the state (a) to the state (c), and is expressed by the following equation using the expected beam angle 2θb, the exposure time Te, and the repetition period Tr. . 2θo = π · Te / Tr + 2θb (3) The opening height ho is expressed as follows from the geometrical relationship in FIG. ho = 2R · sin θo (4)

From the state (b) of FIG.
When rotated by b, the upper wall surface of the X-ray transmission hole 20 is in the state of FIG. Therefore,
The cutting angle θc that forms the wall surface of the X-ray transmission hole 20 must be an angle represented by the following equation. θc = θo−θb (5) Since the X-rays transmitted during the transition time Tt do not contribute to high-quality image formation and become noise, the transition time Tt is desired to be as short as possible. The transient time Tt is determined by the equations (1) and (2). The repetition period Tr is constant according to the standard of the imaging system, and the radiation light beam thickness hb is externally determined by the characteristics of the light source device. Therefore, referring to the equations (1) and (2), it can be seen that the drum radius R may be increased to shorten the transition time Tt.

FIGS. 7 to 10 are sectional views showing modified examples of the rotary drum 21. FIG. FIG. 7 shows a rotating drum 21 having an X-ray transmitting hole 20 having parallel walls instead of a fan-shaped passage.
It is. In such a structure, although the pulse of the transmitted X-ray dose is not easily cut, the work is significantly simplified and there is a cost advantage. FIG. 8 shows a rotating drum 21 in which projections 34 are formed before and after the opening of the X-ray transmission hole 20 to substantially increase the radius. By using such a rotating drum, the amount of transmitted X-rays during the transition time Tt from the state (c) to the state (d) in FIG. 4 can be further reduced.

FIG. 9 shows a rotating drum 21 having a structure in which the meat of the drum is cut along the wall of the X-ray transmitting hole 20. The diameter of the rotating drum 21 is determined according to the requirement of the transition time based on the equations (1) and (2). The material of the drum is made of a material having a large X-ray absorption coefficient, and the thickness of the shielding material of the drum is sufficient. When there is a large margin in the X-ray blocking performance, FIG.
By making the outer wall of the drum hollow 35 as shown in FIG. 9A or by forming the inside of the drum hollow 36 as shown in FIG. 9B, the moment of inertia of the rotary drum 21 is reduced. It is possible to reduce the required torque of the drive motor and to quickly start and stop. FIG. 10 shows a rotating drum 21 having a structure in which a lid 37 is made of a material having a high X-ray transmittance such as aluminum at the opening of the X-ray transmitting hole 20. When the rotating drum 21 rotates at a high speed, a wind noise is generated by the edge of the opening, and such abnormal noise may give a patient who is diagnosed an uneasy feeling. As shown in FIG. 10, the structure having the edge of the opening disappeared does not generate wind noise, so that the noise during operation is reduced and the patient or doctor is not discomforted.

FIG. 11 is a perspective view showing a shield covering attached to the X-ray beam opening / closing device, and FIG. 12 is a sectional view thereof. The radiation light beam 7 incident on the rotating drum 21 is reflected or scattered by the rotating drum 21 for irradiation in various directions except for the transmission time. When the scattered radiation including the X-ray reaches the subject or the operator, X-ray exposure occurs. Therefore, it is preferable to reduce the meaningless X-ray exposure by covering the X-ray shutter mechanism and the accessory parts with the shield coating so that the scattered radiation does not leak to the surroundings. In the figure, reference numeral 40 is a scattered radiation shield main body, and 41 is X
A honeycomb base supporting a linear shutter mechanism or the like; 42, a duct for introducing a radiated light beam; 43, an emission duct for a radiated light beam intermittently transmitted; 44, a sliding opening / closing window;
Is a rail, and 46 is a cable cover.

The scattered radiation shield body 40 is a lid made of a material that sufficiently shields X-rays and the like, and covers the rotating drum 21 and other components shown in FIG.
And radiated light scattered by the rotating drum 21 or the like is prevented from leaking outside. Preferably, the inner wall structure and shape are as simple as possible so that unintended scattering is unlikely to occur. The radiation light beam introduction duct 42 and the emission duct 43 have a cross-sectional shape through which the radiation light beam 7 can pass, and are installed at the optical path position to prevent leakage of scattered radiation. These ducts are structured so that they can be removed from the scattered radiation shield main body 40 for convenience of installing the X-ray beam opening / closing device.

An opening / closing window 44 is provided on a part of the shield wall so that the X-ray shutter can be maintained and the rotating drum can be replaced.
Is provided. The opening / closing window 44 slides laterally on a rail 45 to open and close. When closed, seal tightly so that there is no leakage of synchrotron radiation. Further, a U-shaped cable cover 46 is also provided at a hole portion for taking out a cable of a power line or a signal line, thereby preventing leakage of scattered radiation. Cable cover 46
Is attached to the scattered radiation shield main body 40 via ears or the like to prevent projections from being present inside the shield to prevent extra scattering.

[0032]

As described in detail above, the X-ray irradiation control apparatus of the present invention can significantly reduce the X-ray exposure to be given to a subject or the like in a diagnostic apparatus using radiation such as angiography. it can.

[Brief description of the drawings]

FIG. 1 is a perspective view schematically showing an arrangement example when an X-ray irradiation control device according to an embodiment of the present invention is used for synchrotron radiation angiography.

FIG. 2 is a perspective view showing the structure of the X-ray irradiation control device of the present embodiment.

FIG. 3 is a partially enlarged perspective view of an X-ray shutter mechanism in the embodiment.

FIG. 4 is a view showing a state in which an X-ray shutter mechanism in the present embodiment allows emitted light to pass.

FIG. 5 is a view showing a change in an X-ray transmitted dose in the present embodiment.

FIG. 6 is a diagram illustrating the shape of an X-ray passage hole in the present embodiment.

FIG. 7 is a cross-sectional view showing a first modification of the X-ray shutter mechanism in the embodiment.

FIG. 8 is a sectional view showing a second modification of the X-ray shutter mechanism according to the embodiment.

FIG. 9 is a sectional view showing a third modification of the X-ray shutter mechanism according to the embodiment.

FIG. 10 is a sectional view showing a fourth modification of the X-ray shutter mechanism according to the embodiment.

FIG. 11 is a perspective view illustrating a shield covering attached to the X-ray beam opening / closing device in the present embodiment.

FIG. 12 is a cross-sectional view illustrating the shield covering of FIG.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Electron injector 2 Electron 3 Electron storage ring 4 Electron orbit 5 Deflection electromagnet 6 Insertion light source 7 Emission light 8 X-ray irradiation control device 9 Spectroscope 10 X-ray 11 Patient 12 Image intensifier 13 CCD camera 14 Image processing device 15 Trigger signal 16 Signal processing device 17 Camera controller 20 X-ray transmission hole 21 Rotating drum 22 Base 23 Bearing 24 Drum rotation motor 25 Optical sensor disk 26 Proximity sensor disk 27 Light passage detection hole 28 Cutout 29 Projector 30 Photodetector 31 Proximity sensor 32 Encoder 33 Drum positioning motor 34 Projection 35 Depression 36 Hollow part 37 Cover 40 Scattered ray shield main body 41 Honeycomb table 42 Radiation light beam introduction duct 43 Radiation light beam emission duct 44 Sliding opening / closing window 45 Rail 46 Cable cable Over

──────────────────────────────────────────────────続 き Continuation of the front page (72) Inventor Shigetomo Nakagawa 118 Futatsuka, Noda-shi, Chiba Examiner, Noda Plant, Kawasaki Heavy Industries, Ltd. Examiner Oka ▲ Saki ▼ Teruo Oka (56) JP-A-4-308700 (JP, A) JP-A-54-107389 (JP, A) JP-A-60-222036 (JP, A) JP-A-7-55997 (JP, A) 8-130682 (JP, A) JP-A-60-194934 (JP, A) JP-A-5-38592 (JP, A) JP-A-6-18999 (JP, U) JP-A-56-175999 (JP, A) U) (58) Field surveyed (Int. Cl. ⁷ , DB name) G21K 1/04 A61B 6/00 300 G21K 5/02

Claims (8)

(57) [Claims] An intermittent radiant light is produced by rotating a rotating drum having an opening through which X-rays pass in a direction perpendicular to a rotation axis at a predetermined speed and passing X-rays for a predetermined short period of time at regular intervals. rotary drum X having an X-ray shutter Organization to obtain
X-ray passage opening / closing device for the rotary drum
The mouth has a divergent opening defined by the radiation from the rotating shaft.
An X-ray irradiation control device having a mouth . Wherein X-ray irradiation control unit according to claim 1, characterized in that a windshield plate in the opening of the rotary drum. Wherein X-ray irradiation control unit according to claim 1 or 2, characterized in that the X-ray passage opening of the rotary drum is covered with a high X-ray transmittance material. 4. The X-ray beam opening / closing device further includes a shield cover surrounding the X-ray shutter mechanism to shield a part other than necessary intermittent radiation light, and the shield cover replaces the X-ray shutter mechanism. The X-ray irradiation control device according to any one of claims 1 to 3, wherein an opening / closing window for performing the operation is provided on one surface. 5. The method according to claim 1, wherein the predetermined period is an integral multiple of an acquisition interval of a plane image signal in an X-ray imaging apparatus that captures an X-ray image transmitted by irradiating the X-ray, and the predetermined short time is shorter than the predetermined time. The X according to any one of claims 1 to 4, wherein the time corresponds to an exposure time for capturing an image.
Line irradiation control device. 6. A trigger signal synchronized with the passage of X-rays.
A signal processing device for generating
X-ray beam opening and closing device is further passing X-rays
Claims characterized by comprising a detection mechanism for confirming the state.
6. The X-ray irradiation control device according to any one of 1 to 5. 7. A delay circuit for adjusting a timing of detecting a state where X-rays are passing through the X-ray shutter mechanism, wherein the signal processing device delays a timing at which the signal processing device outputs a trigger signal. 7. The X-ray irradiation control device according to claim 6, further comprising a function of adjusting a timing of sending a trigger signal with respect to passage of X-rays. 8. An X-ray irradiation control device according to claim 6, which is provided between a radiation light generating device and a spectroscope for selecting X-rays, sending the trigger signal to an X-ray detection system and passing X-rays. Coronary angiography device using synchrotron radiation for capturing a moving image of the cardiovascular system by capturing a moving image in synchronization with the image.