JP2013085631A - Device for arthrography - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a device for arthrography, including a base for a subject to be imaged which can firmly fix an imaging target without imposing a load on a patient and which hardly causes a positional shift, slight movement or the like.SOLUTION: The device 1 for arthrography includes: a base 13 for a subject to be imaged holding the subject to be imaged in an imaging position; and a strut 17 and a base stand part 19 having an X-ray source 11 disposed above the base 13, and irradiating radiation to a joint portion of a finger that is an imaging target region of the subject to be imaged, and an X-ray detector 16 disposed below the base 13, and detecting the radiation transmitted through the joint portion. The base 13 includes: an imaging target fixing unit 33 fixing the joint portion that is an imaging target portion in a prescribed position to an X-ray irradiation direction from the X-ray source 11; and a base unit 31 to/from which the imaging target fixing unit 33 can be attached/detached, and which fixes a wrist of the subject to be imaged.

Description

  The present invention relates to a joint imaging apparatus.

The cartilage of the joints such as the hands and legs and the soft tissues around the joints cannot obtain images suitable for diagnosis by conventional X-ray imaging using the absorption contrast method. Photographed images have been used.
However, MRI imaging requires a large burden on the patient, such as mechanically restraining the patient's body position for a predetermined time, and also costs medical expenses. Therefore, an X-ray image captured using a general radiation tube is used for rheumatic diagnosis. The technology to be used is desired.

In this regard, as an imaging method replacing MRI, for example, X-ray imaging has been proposed by a phase contrast method that obtains an X-ray image with high visibility by edge enhancement using X-ray refraction during phase contrast magnification imaging ( For example, see Patent Document 1 to Patent Document 3).
In addition, as one of phase contrast imaging, a Talbot interferometer and a Talbot interferometer using the Talbot effect have been studied (for example, see Patent Document 4 to Patent Document 6). The Talbot effect is a phenomenon in which, when coherent light is transmitted through a first grating provided with slits at a certain period, the grating image is formed at a certain period in the light traveling direction. This lattice image is called a self-image, and the Talbot interferometer arranges a second grating at a position connecting the self-images, and measures interference fringes (moire) generated by slightly shifting the second grating. If an object is placed in front of the second grating, the moire is disturbed. Therefore, if X-ray imaging is performed with a Talbot interferometer, an object is placed in front of the first grating and irradiated with coherent X-rays. It is possible to obtain a reconstructed image of a subject by calculating a moire image.
Furthermore, a Fourier transform method that uses a one-dimensional or two-dimensional lattice and does not require scanning such as the Talbot method has been developed.

  X-ray imaging using such a phase contrast method can image breast tissue, articular cartilage, and soft tissue around the joint, which have a small X-ray absorption difference and are difficult to appear as an image by the absorption contrast method. Therefore, using a widely used general X-ray imaging technique, an X-ray image taken using the phase contrast method is used for diagnosis of a lesion in cartilage or soft tissue such as rheumatism. Therefore, it is expected to reduce the burden imposed on patients and medical costs.

JP 2008-023312 A JP 2007-268033 A JP 2008-18060 A JP 58-16216 A International Publication No. 2004/058070 Pamphlet Japanese Patent Application Laid-Open No. 2007-203063

  For example, when taking an image for diagnosis of rheumatoid arthritis, when the purpose is to prevent the onset of rheumatism, early detection, etc. by conducting image diagnosis for a solitary army who has not developed rheumatism, rheumatism has already developed. It may be aimed at confirming the progress of patients after the onset of symptoms (medication effectiveness, etc.).

However, when a lesion has occurred in the joint, such as when rheumatism has already developed, the lesion such as the joint, which is the region of interest to be imaged, is painful. As described above, it may be difficult to extend straight along the joint table and the like.
Moreover, even if it can be extended straight, it is very painful and it is a heavy burden on the patient to fix it to the subject table in such a state.
In addition, if there is a space between the joint part where the lesion has developed and the subject table, the subject may move due to tremors of the fingers or body movement because the lesion is originally painful. Is assumed.
Even in the Fourier transform method that does not require scanning and only one imaging is required, the irradiation time (imaging time) until the predetermined dose is irradiated becomes long. Therefore, if the subject moves during this time, the generated image is blurred. End up. In addition, although the individual photographing time itself is short, even in the Talbot (Talborough) method in which a plurality of scanning photographings are performed, if the subject moves during each scanning, the generated image is still blurred.

  Further, when imaging the joint part, the engineer needs to position the patient so that the top of the region of interest (ROI), such as the MCP joint or PIP joint, substantially coincides with the radiation irradiation axis. However, if the posture is fixed in a painful posture, the region of interest may move when the technician leaves the patient for the exposure switch operation. If the region of interest moves, re-imaging is required. However, if re-imaging is performed, the patient is wasted.

  Furthermore, depending on the purpose of imaging, the target site, and the like, there may be a case where an image superior in observation of a lesion site can be obtained by imaging with a joint or the like lightly bent rather than a flat stretched state. However, it is difficult to keep the joints and the like bent during the photographing, and there is a problem that the position shift and the shake are likely to occur.

  The present invention has been made in view of the above circumstances, and provides a joint imaging apparatus including a subject table that can firmly fix an imaging target without imposing a burden on a patient and that is unlikely to cause displacement or blurring. It is for the purpose.

In order to solve the above problem, according to the invention of claim 1,
A subject table that holds the finger of the person who is the subject in the shooting position;
Radiation generating means for irradiating a joint portion of a finger, which is an imaging target portion of the subject, and radiation detection means, which is disposed below the subject table and detects the radiation transmitted through the joint portion. An imaging unit having means;
A joint imaging device comprising:
The subject table is
An imaging target fixing unit that fixes a joint part, which is the imaging target part, at a predetermined position with respect to a radiation irradiation direction from the radiation generating unit;
A base unit configured to detachably attach the photographic subject fixing unit and fix a wrist portion of the subject;
There is provided a joint imaging apparatus comprising:

According to invention of Claim 2,
A plurality of the photographing target fixing units for fixing the joint portions of the fingers at predetermined positions different from each other;
The joint imaging apparatus according to claim 1, wherein each of the plurality of imaging target fixing units is configured to be detachable from the base unit.

According to invention of Claim 3,
2. A fringe scanning type imaging apparatus comprising a first grating and a second grating that extend in a direction orthogonal to a radiation irradiation direction from the radiation generating means and are provided with a plurality of slits at predetermined intervals. Or the joint imaging device of Claim 2 is provided.

According to invention of Claim 4,
Comprising a multi-grating arranged in the vicinity of the radiation generating means,
The joint imaging apparatus according to claim 3, which is a Talbot-Lau interferometer that moves the multi-grating relative to the first and second gratings.

According to the imaging apparatus of the present invention, in the joint imaging apparatus that captures the joint portion of a subject such as a human finger, the joint portion that is the imaging target portion from the radiation generating means is placed on the subject table that holds the subject at the imaging position. An imaging target fixing unit that fixes the imaging target fixing unit in a predetermined position with respect to the radiation irradiation direction, and a base unit that is configured to be detachable from the imaging target fixing unit and fix the wrist portion of the subject. As a result, when it is difficult to place the joint part straight on the subject table, such as when the patient has already developed rheumatism, such as when the joint part is lesioned and painful, etc. However, the subject to be imaged can be firmly fixed without imposing a burden on the patient, and shaking or shaking of the subject to be imaged during imaging can be suppressed.
In addition, since the wrist unit is fixed by the base unit and the joint part that is the imaging target part can be fixed to a predetermined position suitable for imaging by the imaging target fixing unit, the patient can straighten the joint part and the like. Even when it is not possible, the subject can be prevented from floating and can be fixed stably. For this reason, it is possible to prevent the subject from moving due to trembling of fingers or body movement, and it is possible to prevent the possibility of image blurring or re-shooting.
In addition, since it includes a plurality of imaging target fixing units that fix the joint parts of the fingers at different predetermined positions, the user is a user depending on the purpose of imaging, the imaging target region, the state of the joints of the patient's fingers, etc. The engineer can select the most suitable one. For this reason, while being able to respond | correspond to imaging | photography in various situations with one apparatus, the image suitable for a diagnosis can be obtained, reducing a patient's burden.
In addition, when a multi-grating having a plurality of slits and / or a first phase grating and a second phase grating are provided, a plurality of images of the joint portion are taken by a fringe scanning method. Since the subject can be stably held at the imaging position so that the imaging target portion does not move during this period, the X-ray absorption difference is small, and it is a soft tissue around the joint that is difficult to appear as an image depending on the absorption contrast method. In addition, it is possible to obtain an image suitable for diagnosis without artifacts associated with body movement.

1 is a schematic side view of an X-ray imaging system including a joint imaging apparatus according to the present embodiment. It is a top view of the joint imaging apparatus shown in FIG. It is a perspective view which shows the specific structure of the joint imaging apparatus shown in FIG. It is a perspective view which shows the state which isolate | separated each structure part of the joint imaging apparatus shown in FIG. It is a perspective view which shows the state which decomposed | disassembled the 1st cover unit of the joint imaging apparatus shown in FIG. It is a perspective view which shows the state which decomposed | disassembled the 2nd cover unit of the joint imaging apparatus shown in FIG. It is a perspective view which shows a mode that an X-ray detector holding | maintenance part is attached to the joint imaging apparatus shown in FIG. It is a perspective view which shows the state which attached the X-ray detector holding | maintenance part to the joint imaging apparatus shown in FIG. It is the principal part perspective view which expanded the to-be-photographed object base upper surface board of a to-be-photographed base. FIG. 10 is an enlarged cross-sectional view showing a main part in the vicinity of the center of the subject table upper surface plate of the subject table shown in FIG. 9. FIG. 3 is a perspective view showing a base unit, a first photographing target fixing unit, and a subject holding member with the first photographing target fixing unit mounted on the base unit. FIG. 4 is a perspective view showing a state in which a subject holding member having a first photographing target fixing unit mounted thereon is placed on a subject table upper surface plate of a subject table. FIG. 6 is a perspective view showing a base unit, a second photographing target fixing unit, and a subject holding member with the second photographing target fixing unit mounted on the base unit. It is a perspective view which shows the state which fixed the finger | toe to the subject holding member with which the 2nd imaging | photography target fixing unit was mounted | worn, (a) Forefinger, (b) A middle finger, (c) A ring finger, (d) A little finger It is a perspective view which shows the state which fixed. It is a perspective view which shows a base unit and a 3rd imaging | photography target fixing unit, and the to-be-photographed object holding member which attached the 3rd imaging | photography target fixing unit to the base unit. It is a perspective view which shows the state which fixed the finger | toe to the subject holding member with which the 3rd imaging | photography target fixing unit was mounted | worn. It is a perspective view which shows a base unit and a 4th imaging | photography target fixing unit, and the to-be-photographed object holding member which attached the 4th imaging | photography target fixing unit to the base unit. It is a perspective view which shows the state which fixed the finger | toe to the subject holding member with which the 4th imaging target fixing unit was mounted | worn. It is a perspective view showing a base unit, a fifth photographing target fixing unit, and a subject holding member with the fifth photographing target fixing unit attached to the base unit. It is a perspective view which shows the state which fixed the finger | toe to the to-be-photographed object holding member with which the 5th imaging | photography target fixing unit was mounted | worn. It is a figure which shows typically the main structures of the joint imaging apparatus shown in FIG. It is a perspective view of a multi lattice unit. It is a perspective view which shows the state by which the multi-grating unit was arrange | positioned under the X-ray source. It is a graph which shows the relationship between an exciting current and the displacement amount of a multi-grid. It is a top view of a multi lattice. It is a perspective view which shows the state which attached the 1st grating | lattice unit and the 2nd grating | lattice unit to the base part. It is a perspective view of a 1st lattice unit. It is a perspective view of a 1st lattice unit. It is a perspective view of a 1st lattice unit. It is a block diagram which shows the functional structure of a main-body part. It is a figure explaining the principle of a Talbot interferometer. It is a flowchart which shows the process at the time of the X-ray imaging by a joint imaging device. It is a flowchart which shows the process by a controller. It is a figure which shows the moire image obtained by imaging | photography of 5 steps. It is a graph which shows the X-ray relative intensity of the attention pixel of the moire image of each step. FIG. 4 is a perspective view showing a state in which a subject support plate is placed on a subject table upper surface plate of the subject table of the joint imaging apparatus shown in FIG. 3. It is a perspective view which shows the state which connected the auxiliary | assistant stand to the to-be-photographed object support plate of the joint imaging apparatus shown in FIG. It is a perspective view which shows a mode that the imaging | photography of the joint part of a shoulder of a to-be-photographed object is carried out using the to-be-photographed object support plate and auxiliary stand shown in FIG. It is a perspective view which shows a mode that imaging | photography of the joint part of the ankle of a to-be-photographed object is performed using the to-be-photographed object support plate and auxiliary stand shown in FIG. It is a perspective view which shows a mode that the subject's knee joint part is image | photographed using the to-be-photographed object support plate and auxiliary stand shown in FIG. FIG. 38 is a perspective view showing a state where a subject's knee joint is photographed in a reclining state using the subject support plate and auxiliary stand shown in FIG. 37. It is a perspective view which shows a mode that imaging | photography of the joint part of the ankle of a to-be-photographed object is carried out using the to-be-supported board and stretcher shown in FIG. It is explanatory drawing which shows typically the structure provided with a refractive index adjustment tank in a to-be-photographed object base.

Hereinafter, an embodiment of an articulation apparatus according to the present invention will be described with reference to the drawings.
In the present embodiment, the joint photographing apparatus includes a subject base 13 that holds a human finger or the like as a subject at a photographing position, and a joint part such as a finger that is disposed above the subject base 13 and is a subject to be photographed. An X-ray source 11 as radiation generating means for irradiating radiation to the imaging unit, and an imaging unit having an X-ray detector 16 as detection means disposed below the subject table 13 and detecting radiation transmitted through the joint part. I have.

FIG. 1 schematically shows an X-ray imaging system including a joint imaging apparatus according to the present embodiment, and FIG. 2 is a plan view of the joint imaging apparatus 1 shown in FIG. 1 as viewed from above.
The X-ray imaging system includes a joint imaging apparatus 1 and a controller 5. The joint imaging apparatus 1 performs X-ray imaging with a Talbot-Lau interferometer, and the controller 5 creates a reconstructed image of the subject using the moire image obtained by the X-ray imaging.

As shown in FIG. 1, the joint imaging apparatus 1 includes an X-ray source 11, a multi-grating 12, a light irradiation field confirmation unit 6, a subject table 13, a first grating 14, a second grating 15, an X-ray detector 16, and a support column. 17, a main body 18, and a base 19.
The joint imaging apparatus 1 in the present embodiment is a vertical type, and the X-ray source 11, the multi-grating 12, the subject table 13, the first grating 14, the second grating 15, and the X-ray detector 16 are arranged in this order in the direction of gravity. They are arranged along a certain z direction (see FIG. 21).
In FIG. 1, the distance between the focal point of the X-ray source 11 and the multi-grating 12 is d1 (mm), the distance between the focal point of the X-ray source 11 and the X-ray detector 16 is d2 (mm), The distance between the 1st grating | lattice 14 is represented by d3 (mm), and the distance between the 1st grating | lattice 14 and the 2nd grating | lattice 15 is represented by d4 (mm).

The distance d1 is preferably 3 to 500 (mm), and more preferably 4 to 300 (mm).
The distance d2 is preferably at least 3000 (mm) or less since the height of the radiology room is generally about 3 (m) or less. Especially, the distance d2 is preferably 400 to 2500 (mm), and more preferably 500 to 2000 (mm).
The distance (d1 + d3) between the focal point of the X-ray source 11 and the first grating 14 is preferably 300 to 5000 (mm), and more preferably 400 to 1800 (mm).
The distance (d1 + d3 + d4) between the focal point of the X-ray source 11 and the second grating 15 is preferably 400 to 5000 (mm), more preferably 500 to 2000 (mm).
Each distance may be set by calculating an optimum distance at which the lattice image (self-image) by the first lattice 14 overlaps the second lattice 15 from the wavelength of the X-rays emitted from the X-ray source 11.

3 is a perspective view specifically showing the configuration of the joint imaging apparatus 1 shown in FIGS. 1 and 2, and FIG. 4 is a perspective view showing a state in which each component of the joint imaging apparatus 1 is separated. .
As shown in FIGS. 3 and 4, the joint imaging apparatus 1 in the present embodiment includes a column 17 that supports the X-ray source 11, a multi-grating unit 120 that includes a multi-grating 12, and a first grating that includes a first grating 14. A base unit 19 to which the unit 140, the second grid unit 150 including the second grid 15 and the X-ray detector 16 are attached, and a subject table 13 (in FIG. 4, the subject table base constituting the subject table 13) Only the portion 130 is shown.). In the present embodiment, the imaging unit is configured by the support column 17 that supports the X-ray source 11 and the base unit 19 to which the X-ray detector 16 is attached. Since the imaging unit and the subject table 13 can be separated, it is possible to prevent an impact or the like applied to the subject table 13 from a patient from affecting the imaging unit before or during imaging.

In the present embodiment, the base portion 19 is provided with a first cover unit 21 provided so as to cover the multi-grid unit 120, a first grid unit 140 and a second grid unit 150 provided so as to cover the second grid unit 150. Two cover units 22 are attached.
As will be described later, the multi-grating 12, the first grating 14, and the second grating 15 are members that require position adjustment with very high accuracy, and photographing without photographic subjects for photographing the subject and calibrating the subject. For example, when a series of photographing is performed over a plurality of times, it is desirable that the same conditions be maintained during that time.
However, in the state exposed to the atmosphere without providing any cover or the like around the multi-grid 12, the first grid 14 and the second grid 15, the change in the ambient temperature in the installed photographing room (for example, the ceiling due to the change in the air flow by the air conditioner). Temperature difference between the vicinity and the floor surface), impacts, vibrations, and the like, so that the multi-grating 12, the first grating 14, and the second grating 15 are performed during a series of imaging operations. There is a possibility that the position and orientation of the lens slightly deviate from the proper state. The first cover unit 21 and the second cover unit 22 avoid the influence of the multi-grid 12, the first grid 14 and the second grid 15 from the outside, for example, a cold air current of an air conditioner or a warm air. It is directly exposed to an air current and the like, and the thermal expansion fluctuation is partially suppressed. The imaging conditions are maintained during a series of imaging, and the multi-grating 12, the first grating 14 and the second grating, which are precision members, are maintained. This is to prevent 15 from receiving external impact or the like.

FIG. 5 is a perspective view showing a state in which the first cover unit 21 provided around the multi-grating unit 120 and the light irradiation field confirmation unit 6 is disassembled.
As shown in FIG. 5, the first cover unit 21 includes a front cover member 211 disposed so as to cover the multi-grid unit 120 and the light irradiation field confirmation unit 6 from the front side, and a joint more than the front cover member 211. An upper cover member 212 that is disposed on the back side of the imaging apparatus 1 (that is, on the support column 17 side) and covers the upper side of the multi-grating unit 120, and an upper cover member that is below the multi-grating unit 120 and the light irradiation field confirmation unit 6 And a lower cover member 213 disposed at a position corresponding to 212. The front cover member 211, the upper cover member 212, and the lower cover member 213 constituting the first cover unit 21 are formed by, for example, pressing a metal plate.
Cutout portions 211 a and 212 a are formed on the upper surfaces of the front cover member 211 and the upper cover member 212 and facing the X-ray source 11. An opening 211b is provided on the lower surface of the front cover member 211 and facing the X-ray irradiation port of the X-ray source 11. Thereby, even when the first cover unit 21 is attached, the X-ray irradiation from the X-ray source 11 is not hindered by the first cover unit 21.
Further, on the surface of the front cover member 211 facing the support column 17, a lever opening 211c is formed at a position corresponding to a movement lever 67 of the light irradiation field confirmation unit 6 described later. The lever opening 211c is a long hole extending in the x direction so as to have substantially the same length as the moving range of the moving lever 67, and the front end of the moving lever 67 extends from the lever opening 211c to the front cover. It protrudes out of the member 211. Thus, the user can operate the moving lever 67 of the light irradiation field confirmation unit 6 even when the first cover unit 21 is attached. In addition, a scale or an index indicating whether the light irradiation field confirmation unit main body 65 is in the light irradiation field confirmation position or the retraction position (described later) depending on the position of the moving lever 67 around or near the lever opening 211c. May be provided.
When attaching the first cover unit 21, the upper cover member 212 is screwed and fixed to the base 19 so as to cover the upper side of the multi-grid unit 120, and the lower cover member 213 is attached to the upper cover from the lower side of the multi-grid unit 120. The position is adjusted so as to contact the lower end of the member 212, and the base 212 is fixed with screws. Further, the front cover member 211 is fitted to the upper cover member 212 and the lower cover member 213 from the front side of the multi-grid unit 120 and fixed with screws.
The first cover unit 21 only needs to be able to block external influences on the multi-grid unit 120, and the material, shape, configuration, fixing method, and the like are not limited to those exemplified here. In addition, a heat insulating member is preferably provided on at least the inner surface side of the first cover unit 21.

FIG. 6 is a perspective view showing a state in which the second cover unit 22 provided around the first grid unit 140 and the second grid unit 150 is disassembled.
As shown in FIG. 6, the second cover unit 22 includes a first grid unit 140, a front cover member 221 disposed so as to cover the second grid unit 150 from the front side, and an upper side of the first grid unit 140. The upper cover member 222 to cover and the side surface cover member 223 arrange | positioned at the both sides of the 1st grating | lattice unit 140 and the 2nd grating | lattice unit 150 are provided. The front cover member 221, the upper cover member 222, and the side cover member 223 constituting the second cover unit are formed by, for example, pressing a metal plate.
The upper cover member 222 is a U-shaped member with a center portion cut out, and is formed on the subject placed on the subject table 13, the first lattice 14 and the second lattice 15, of the upper cover member 222. The upper surface is not covered.
When the second cover unit 22 is attached, the side cover member 223 is fixed to the base 19 so as to cover both sides of the first lattice unit 140 and the second lattice unit 150, and the front cover member 221 is attached to the first cover unit 221. The positions of the first grid unit 140 and the second grid unit 150 are adjusted so as to cover from the front side, and are fixed to the front side end of the side cover member 223 by screws. Further, the upper cover member 222 is covered from above and fixed to the base 19, the side cover member 223, and the front cover member 221 by screws.
The second cover unit 22 only needs to be able to block the external influence on the first grid unit 140 and the second grid unit 150, and its material, shape, configuration, fixing method, and the like are exemplified here. It is not limited to things. Further, it is preferable that a heat insulating member is provided on at least the inner surface side of the second cover unit 22.

Further, the periphery of the second cover unit 22 is easily subjected to an impact from the outside, for example, by a patient's foot or the like placing a hand or the like as a subject on the subject table 13. For this reason, the guard member 41 as shown in FIG.3 and FIG.5 is provided in the outer side of the 2nd cover unit 22, for example. The guard member 41 is formed of, for example, a metal plate or the like, and is detachably fixed around the second cover unit by screwing or the like as shown in FIG. In addition, the shape of the guard member 41, the fixing method to the second cover unit, and the like are not limited to those exemplified here. Further, an elastic member for absorbing shock may be provided inside the guard member 41.
By providing such a guard member 41, it is possible to prevent the impact from affecting the precision members such as the first grid 14 and the second grid 15 even if the patient's foot or the like hits the apparatus side during imaging. Highly accurate image shooting can be performed.

  The subject table 13 is used to place a patient's fingers and the like that are subjects at the time of photographing. Although the size of the subject table 13 is not particularly limited, as shown in FIG. 1, when the patient's finger or the like that is the subject at the time of imaging is placed within the X-ray irradiation range (in the imaging possible region), the elbow portion of the patient It is preferable that the arm rest portion is configured to have a length dimension so that the arm rest portion can be placed. By placing the finger to the elbow part on the subject table 13, the position and posture of the finger to be imaged can be stabilized, and camera shake or the like at the time of imaging can be prevented.

As shown in FIGS. 3 and 4, in the present embodiment, the subject table 13 includes a subject table base unit 130 having a leg 132 including casters 131, and is independent of the support column 17 and the base unit 19. . The leg portion 132 is arranged between the support column 17 and the base portion 19, and the leg portion 132 on the base portion 19 side is provided with a lock mechanism 133 that locks the caster 131. .
The configuration of the subject table 13 is not limited to the example illustrated here. For example, the lock mechanism 133 may be provided on all the leg portions 132 of the subject base 130, or the subject base 13 may be fixed to one end of the column 17 or the base 19 without providing the lock mechanism 133. May be. The subject table 13 preferably includes an impact absorbing member (not shown) that can absorb an impact when it comes into contact with the support column 17 or the base unit 19.

Further, in the present embodiment, a member locking column 132a to which the X-ray detector holding unit 25 is detachably attached is fixed substantially horizontally between the front side legs 132 of the subject table base unit 130. ing.
The X-ray detector holding unit 25 holds the X-ray detector 16 during calibration of the gain and the like of the X-ray detector 16, and as shown in FIGS. 7 and 8, the X-ray detector holding unit 25. A hook 251 for locking formed in a bowl shape is provided on one end side of the. The X-ray detector holding unit 25 holds the locking hook 251 on the member locking column 132a of the subject table 13 while holding the X-ray detector 16 on the upper surface when the X-ray detector 16 is calibrated. By being locked, it is fixed to the subject table 13.

  In the present embodiment, as will be described later, the X-ray irradiation direction of the X-ray source 11 can be changed. When the X-ray detector 16 is calibrated, the optical axis of the X-ray is the multi-grating 12, The orientation of the X-ray source 11 is adjusted until the first grating 14 and the second grating 15 are removed from the top (calibration state see FIG. 8). The X-ray detector holding unit 25 is arranged on an extension line of the optical axis of the X-ray source 11 when the X-ray irradiation direction of the X-ray source 11 is adjusted to the calibration state in a state where the X-ray detector holding unit 25 is attached to the subject table 13. The X-ray detector 16 is held on the X-ray detector holding unit 25, X-rays are emitted from the X-ray source 11, and imaging is performed, whereby the multi-grating 12, the first An image for calibration in which images of the grid 14 and the second grid 15 are not reflected can be acquired.

On the upper surface of the subject table 13 and on the upper cover member 222 of the second cover unit 22, the subject table upper surface plate 3 that holds the subject is pinned by a fixing pin (not shown). Stopped and fixed. A through hole is formed in the upper cover member 222 at a position corresponding to the fixing pin of the subject table top surface plate 3, and the subject table top surface plate 3 is attached after the second cover unit 22 is attached to the base unit 19. The upper part of the upper cover member 222 is fixed to the subject base part 130.
It is preferable that the subject table upper surface plate 3 can adjust the height for holding the subject by adjusting the fixing position of the fixing pin in the height direction in a plurality of stages, for example. Thereby, the distance between the subject held on the subject table 13 and the X-ray source 11 can be kept at a predetermined distance suitable for imaging by adjusting the fixing position of the fixing pin on the subject table top surface plate 3. it can.

A circular notch 301 is provided at substantially the center of the subject table upper surface plate 3, and a circular rotating plate 302 is rotatably attached to the notch 301. By rotating the rotating plate 302, the orientation and position of the subject holding member 30 (see FIG. 11 and the like) placed on the rotating plate 302 can be easily changed / corrected. This makes it possible to easily correct the positioning.
Further, when the joint part is imaged by the fringe scanning method as in the joint imaging apparatus 1 in the present embodiment, the multi-grating 12 and the first grid (first grid) are used to obtain a moire image in which interference fringes appear. It is necessary to appropriately adjust the direction and angle of the slits of the phase grating 14 and the second grating 15 (second phase grating) 15 and the direction and angle of the subject. In this respect, the multi-grating 12, the first grating 14, and the second grating 15 are very precisely configured, and it is difficult to maintain accuracy if they are moved and adjusted. In this regard, by configuring the portion of the subject table upper surface plate 3 on which the subject is placed so as to be rotatable, it is possible to make appropriate adjustments by moving the subject side. If the rotating plate 302 is rotated too much, a moire image cannot be obtained. For this reason, the rotating plate 302 may be configured to be rotatable within a certain range, for example, 45 degrees from a predetermined initial position.
A rotating plate fixing pin 303 for fixing the rotating plate 302 is provided on the object table upper surface plate 3 and in the vicinity of the peripheral edge of the rotating plate 302 so that the rotating plate 302 can be fixed.

A substantially circular notch 304 is provided at a position substantially corresponding to the first grating 14 and the second grating 15 in the substantially central portion of the rotating plate 302, and X-ray irradiation from the X-ray source 11 is performed. It does not interfere.
As shown in FIGS. 9 and 10, a substantially circular transparent plate member 305 made of a transparent material such as transparent acrylic or glass is attached to the notch portion 304.
As shown in FIG. 10, the transparent plate member 305 is disposed so that the upper surface thereof is slightly lower than the upper surface of the rotating plate 302 (in this embodiment, only the height difference G shown in FIG. 10 is transparent). (The upper surface of the plate member 305 is lower than the upper surface of the rotating plate 302). This prevents the subject holding member 30 from coming into contact with the surface of the transparent plate member 305 when a later-described subject holding member 30 or the like is placed and fixed on the upper surface of the rotating plate 302 of the subject table top surface plate 3. It is possible to improve durability by preventing the surface of the transparent plate member 305 from being damaged such as scratches.

  As shown in FIG. 9, elongated holes 306 formed substantially parallel to each other are provided at substantially symmetrical positions on the rotating plate 302 of the subject table top surface plate 3 with the transparent plate member 305 interposed therebetween. The elongated hole 306 is provided with a holding member fixing pin 307 for fixing the subject holding member 30 shown in FIG.

A subject holding member 30 is detachably mounted on the subject table upper surface plate 3. In the present embodiment, the same location is shot multiple times, but the subject holding member 30 holds and fixes the position of the finger so that the subject finger does not move or shift during the series of shots. belongs to.
As shown in FIGS. 11 and 13 to 20, in the present embodiment, the subject holding member 30 is configured to be detachable from the base unit 31 and supports the finger of a person who is the subject. The imaging target fixing unit 33 (the first imaging target fixing unit 33a to the fifth imaging target fixing unit 33e) for this purpose. In the following embodiments, only the left-hand subject holding member 30 is shown, but the right-hand subject holding member 30 having the same configuration is used when photographing the finger of the right hand.
The base unit 31 and the photographing target fixing unit 33 are made of, for example, polyacetal resin (POM: polyacetal, polyoxymethylene) or the like. The material for forming the base unit 31 and the photographing target fixing unit 33 is not limited to polyacetal resin, and various resins can be used. Further, in the base unit 31 and the photographing target fixing unit 33, a portion that does not overlap with a joint portion of a finger that is a photographing target when the subject is held on the subject holding member 30 may be formed of metal or the like. Moreover, it is preferable that a buffer member made of an elastic material such as silicon resin is disposed in a portion where the fingers are in direct contact. The base unit 31 and the imaging target fixing unit 33 are preferably sanitized every time the patient to be imaged changes, and the material forming the base unit 31 and the imaging target fixing unit 33 is alcohol used for disinfection or the like. It is preferable that it has tolerance with respect to.

The base unit 31 includes a photographing target fixing unit mounting portion 311 for mounting a photographing target fixing unit 33 (first photographing target fixing unit 33a to fifth photographing target fixing unit 33e) at the substantially center, and the photographing target fixing unit 33. It is the frame-shaped member comprised so that attachment or detachment was possible.
In the base unit 31, the positions corresponding to the two holding member fixing pins 307 provided on the rotating plate 302 of the subject table upper surface plate 3 respectively extend in directions substantially orthogonal to the extending direction of the long hole 306. A long hole 312 is formed.
As shown in FIG. 12, the holding member fixing pin 307 passes through the long hole 312 of the base unit 31 and the long hole 306 of the rotating plate 302, so that the subject holding member 30 is attached to the rotating plate 302 of the subject table top surface plate 3. The subject holding member 30 is fixed on the holding member after the orientation and position on the subject table top surface plate 3 are finely adjusted by adjusting the positions of the long hole 306 and the long hole 312. It is fixed by a pin 307 for use.
A wrist fixing belt 313 for fixing the wrist portion of the subject is provided in the vicinity of one end side of the photographing target fixing unit mounting portion 311 and on the wrist side of the hand supported by the photographing target fixing unit 33. It has been.

Further, the photographing target fixing unit 33 is placed near the other end side of the photographing target fixing unit mounting portion 311 and on the fingertip side of the hand supported by the photographing target fixing unit 33. It becomes the base side fixing | fixed part 314 for fixing to. The base-side fixing portion 314 has a hole 316 through which the fixing pin 333 is inserted after the imaging target fixing unit 33 is attached to the imaging target fixing unit mounting portion 311.
Further, in the vicinity of the base side fixing portion 314 in the base unit 31 and at a position corresponding to the hole 334 provided on the side surface of the fixing portion on the photographing target fixing unit 33 (fixed unit side fixing portion 331) described later. Through-holes penetrating in the horizontal direction in the base unit 31 (the horizontal direction when the subject holding member 30 is placed on the subject table top surface plate 3) from the side end surface of the base unit 31 to the inside of the subject fixing unit mounting portion 311 317 is formed. A fine adjustment screw 318 is inserted into the through-hole 317 from the side end surface of the base unit 31 toward the inside of the photographing target fixing unit mounting portion 311.
Furthermore, a hole 319 is formed in the base unit 31 in the vertical direction from the surface of the base unit 31 toward the through hole 317. An adjustment fixing screw 320 for fixing the fine adjustment screw 318 is inserted into the hole 319 from the surface of the base unit 31 toward the through hole 317.
The shape and configuration of the base unit 31 and the configuration for fixing the base unit 31 to the subject table upper surface plate 3 are not limited to those illustrated here, and can be changed as appropriate.

The imaging target fixing unit 33 fixes the joint portion of the finger that is the imaging target portion at a predetermined position with respect to the X-ray (radiation) irradiation direction from the X-ray source 11 that is the radiation generating means.
In the present embodiment, five types of shooting target fixing units 33 a to 33 e are prepared as the shooting target fixing unit 33 that can be attached to the base unit 31, as shown in FIGS. 11 and 13 to 20. In the following description, when the imaging target fixing unit 33 is simply used, all of these (imaging target fixing units 33a to 33e) are included.
In photographing, a photographing target fixing unit 33 suitable for photographing is selected according to a part to be photographed or a state of deformation of a joint of a patient's finger and attached to the base unit 31. Note that the photographing target fixing unit 33 that can be attached to the base unit 31 is not limited to the one illustrated here. Many more types may be prepared, or only a part of those listed here may be provided.

As shown in FIG. 11, the first photographing target fixing unit 33 a includes a fixing unit side fixing portion 331 for fixing to the base unit 31 and four inter-finger holding members 332.
The fixing unit side fixing portion 331 is provided with a fixing pin 333 at a position corresponding to the hole 316 of the base unit 31, and the fixing pin 333 is fixed from the fixing unit side fixing portion 331 to the base side 31 of the base unit 31. The first imaging target fixing unit 33a can be temporarily fixed to the base unit 31 by inserting the hole 316 into the hole 316 and tightening.
At a position corresponding to the through hole 317 of the base unit 31 on the side surface of the fixed unit side fixing portion 331, a hole portion 334 into which the tip of the fine adjustment screw 318 inserted through the through hole 317 is inserted is provided. ing.
The fine adjustment screw 318 is inserted into the through hole 317 of the base unit 31, and the tip end portion thereof is inserted into the hole portion 334 and appropriately pushed inward, whereby the width direction of the first shooting target fixing unit 33a (shooting target) The position in the width direction of the finger fixed to the fixing unit 33 can be finely adjusted. After adjusting the position in the width direction, the first imaging target fixing unit 33 a can be fixed to the base unit 31 by fixing the fine adjustment screw 318 from the surface of the base unit 31 with the adjustment fixing screw 320.

One end of the inter-finger holding member 332 is fixed to the fixed unit side fixing portion 331, and when the subject's fingers are fixed to the subject holding member 30, each inter-finger holding member 332 is between the five fingers of the subject's fingers. Are arranged side by side so as to be located respectively. The inter-finger holding member 332 is formed in a tapered shape that gradually increases in width from the free end side toward the fixed end side fixed to the fixed unit side fixing portion 331, and the tip of the finger of the subject is sufficiently It can be fixed in the open state.
FIG. 12 shows a state in which the first photographing target fixing unit 33a fixed to the base unit 31 is fixed on the subject table upper surface plate 3, and the user fixes his / her finger to the first photographing target fixing unit 33a. It is a figure. For example, when it is desired to photograph the second joint (PIP joint) portion of the finger, as shown in FIG. 12, the first finger is placed so that the four inter-finger holding members 332 are positioned between the five fingers. By placing the imaging target fixing unit 33a on the imaging target fixing unit 33a, it is possible to support the five fingers in a state of being spaced apart.
The shape and configuration of the first imaging target fixing unit 33a, the configuration for fixing the first imaging target fixing unit 33a to the base unit 31, and the like are not limited to those illustrated here, and can be changed as appropriate. . For example, the inter-finger holding member 332 is configured to be easily detachable with respect to the fixed unit side fixing portion 331, and a plurality of inter-finger holding members 332 having different shapes and sizes are prepared. Depending on the situation, an appropriate one may be selected and mounted as appropriate.

As shown in FIG. 13 and FIGS. 14A to 14D, the second photographing target fixing unit 33b includes a fixing unit side fixing portion 331 for fixing to the base unit 31, and a finger other than a finger to be photographed. A gripping portion 335 for supporting fingers, four finger holding members 338 for holding fingers to be photographed one by one, and a support member 336 for supporting the finger holding members 338 are provided.
Since the configuration of the fixed unit side fixing portion 331 is the same as that of the first photographing target fixing unit 33a, the description thereof is omitted.
The gripping portion 335 is a cylindrical member that is erected substantially perpendicular to a horizontal plane (a surface that is horizontal to the subject table upper surface plate 3) when the subject holding member 30 is fixed to the object table upper surface plate 3. . The gripping portion 335 is formed in a size and shape that can be easily grasped with a hand. The gripping portion 335 may be coated with a non-slip resin or a cloth or the like so that the patient can easily grip it. Further, a groove along the finger may be formed on the surface of the hand placement portion 349.
The support member 336 is a plate-like member that is erected almost vertically in the vicinity of the grip portion 335. The support member 336 is formed with four rail portions 337 respectively corresponding to the four finger holding members 338 along the extending direction of the fingers when the fingers are fixed to the subject holding member 30.
The four finger holding members 338 are sheath-like members configured so that the fingertips of the fingers to be photographed can be placed, and are respectively slidably engaged with the four rail portions 337 of the support member 336. Yes. The finger holding member 338 slides along the rail part 337 when placing the fingertip, and fixes the finger at a position corresponding to the length of each finger.

In this embodiment, when photographing the joint part of the index finger, as shown in FIG. 14A, the hand is stabilized by grasping the grip portion 335 with a hand other than the index finger, and the index finger is moved along the support member 336. The fingertip is placed on the finger holding member 338 that is extended and positioned at the top. Further, when photographing the joint portion of the middle finger, as shown in FIG. 14B, the gripping portion 335 is held with a hand other than the middle finger to stabilize the hand, and the middle finger is extended along the support member 336. The fingertip is placed on the finger holding member 338 located at the second position. Further, when photographing the joint part of the ring finger, as shown in FIG. 14C, the hand is stabilized by grasping the gripping part 335 with a hand other than the ring finger, and the ring finger is extended along the support member 336. The fingertip is placed on the finger holding member 338 located third. When photographing the joint portion of the little finger, as shown in FIG. 14D, the hand is stabilized by grasping the grip portion 335 with a hand other than the little finger, and the little finger is extended along the support member 336. The fingertip is placed on the finger holding member 338 located at the bottom.
For example, when the second joint (PIP joint) portion of the finger or the like is to be photographed, the subject holding member 30 with the second photographing target fixing unit 33b fixed to the base unit 31 is fixed on the subject table top surface plate 3. By placing the fingers to be photographed one by one on the finger holding member 338 of the second photographing target fixing unit 33b, the fingers can be supported in an extended state.
Note that the shape, configuration, and the like of the second imaging target fixing unit 33b are not limited to those illustrated here, and can be changed as appropriate. When photographing the second joint (PIP joint) portion or the like of the finger, it is preferable that the finger is slightly warped toward the back of the hand. Therefore, for example, the support member 336 is moved outward (ie, away from the gripping portion 335). A curved shape may be used, and the finger holding member 338 may be provided near the end. In addition, it is not essential to have the gripping portion 335, and it is possible to provide a partition plate or the like that can position the fingers one by one so that the fingers can be held one by one against the back of the hand. Good.

As shown in FIGS. 15 and 16, the third shooting target fixing unit 33 c is inclined to the fixing unit side fixing portion 331 for fixing to the base unit 31 and the fingertip of the finger to be shot. And a finger position restricting member 341 for restricting the position and angle of the fingers so that a gap between the thumb and the fingers other than the thumb is increased.
Since the configuration of the fixed unit side fixing portion 331 is the same as that of the first photographing target fixing unit 33a, the description thereof is omitted.
The stepped portion 340 is integrated with the fixed unit side fixed portion 331, and is constituted by an overhang portion that protrudes from one end of the fixed unit side fixed portion 331. The step portion 340 is, for example, about 10 mm to 15 mm higher than the subject table upper surface plate 3 on which the palm portion is placed. Thus, the fingertip can be warped upward. Note that the shape, height, and the like of the stepped portion 340 are not limited to those illustrated here. For example, the stepped portion 340 may be made higher than the fixed unit side fixed portion 331 so that the fingertip can be warped higher. Further, the stepped portion 340 may be inclined so as to increase in height toward the fingertip side.
One end of the finger position regulating member 341 is fixed to the fixed unit side fixing portion 331, and is positioned between the thumb and the index finger when the subject finger is fixed to the subject holding member 30. The finger position regulating member 341 is formed in a tapered shape that gradually increases in width from the free end side toward the fixed end side fixed to the fixed unit side fixing portion 331, and the finger other than the thumb and the thumb of the subject. Fingers other than the thumb (forefinger to little finger) are restricted in a direction away from the thumb so that the gap between the index finger and the little finger is widened. The shape, size, etc. of the finger position regulating member 341 are not particularly limited. For example, the finger position restricting member 341 has such a shape that the fixed end side is wide enough to open between the thumb and a finger other than the thumb to almost 90 degrees. Is preferred. In addition, a plurality of types of finger position regulating members 341 having different shapes and sizes are prepared according to the size of the user's hand, the shape of the finger, the region to be photographed, etc., and the most suitable one is used according to the situation. It is good also as composition to do.
As described above, in this embodiment, the subject holding member 30 that fixes the third imaging target fixing unit 33c to the base unit 31 is fixed on the subject table upper surface plate 3, and the finger that is the subject is attached to the subject holding member 30. When fixed, the fingertips of the fingers from the index finger to the little finger to be photographed are pushed upward by the step portion 340 and further regulated by the finger position regulating member 341 in a direction away from the thumb. For this reason, for example, when photographing the joint portion of the base of the thumb or the like, the gap between the thumb and other fingers can be widened and the thumb can be fixed in a lying state.
Note that the shape, configuration, and the like of the third imaging target fixing unit 33c are not limited to those illustrated here, and can be changed as appropriate.

As shown in FIGS. 17 and 18, the fourth imaging target fixing unit 33d includes a fixing unit side fixing portion 331 for fixing to the base unit 31, and four fingers for holding one finger to be imaged one by one. A holding member 345 and a guide member 343 for guiding the finger holding member 345 along the extending direction of the fingers are provided.
Since the configuration of the fixed unit side fixing portion 331 is the same as that of the first photographing target fixing unit 33a, the description thereof is omitted.
One end of the guide member 343 is fixed to the fixed unit side fixing portion 331, and a finger holding member 345 is attached to each guide member 343 so as to be slidable along the extending direction of the fingers.
In the finger holding member 345, the portion on which the fingertip is placed is an inclined surface that is inclined upward so that the height increases as it goes to the tip side of the finger. Thus, when the finger is placed on the finger holding member 345, the fingertip is pushed up by the inclined surface and fixed in a state of warping upward.
The finger holding member 345 slides along the guide member 343 when placing the fingertip, and fixes the finger at a position corresponding to the length of each finger, as shown in FIG.
Note that the shape, configuration, and the like of the fourth imaging target fixing unit 33d are not limited to those illustrated here.

As shown in FIGS. 19 and 20, the fifth imaging target fixing unit 33 e includes a fixing unit side fixing unit 348 for fixing to the base unit 31 and a hand placement unit 349 on which a finger to be imaged can be placed. And.
One end of the fixed unit side fixing portion 348 is fixed to the hand placement portion 349 and is formed in a rod shape. A fixing screw 348 for fixing the fifth photographing target fixing unit 33e to the base unit 31 is provided at the free end side of the fixing unit side fixing portion 348. In the base unit 31, a hole (not shown) is formed in the vicinity of the wrist fixing belt 313, and the fifth photographing target fixing unit 33 e is screwed into this hole on the base unit 31 side by a fixing screw 348. It is fixed to the base unit 31 by being stopped.
The hand placement portion 349 is a hemispherical member, and as shown in FIG. 20, the finger is fixed by placing it on the hand placement portion 349 with the finger to be imaged lightly bent. Yes. As a result, in cases where the joint part cannot be extended due to the onset of rheumatism, etc., or when it is preferable to take a picture with the hot water part slightly bent, the burden is placed on the patient with a relatively easy posture. The position and angle of the finger can be stabilized without being applied, and the displacement or shaking of the finger during photographing can be suppressed.
Note that the shape, configuration, and the like of the fifth imaging target fixing unit 33e are not limited to those illustrated here. For example, an anti-slip resin may be applied to the surface of the hand placement unit 349 so that the patient can easily grasp it. Further, a groove along the finger may be formed on the surface of the hand placement portion 349. Further, as the fifth imaging target fixing unit 33e, a plurality of units different in the length of the fixed unit side fixing part 348 and the size, shape, height, etc. of the hand placing part 349 are prepared, and the shape of the patient's hand Alternatively, the one suitable for the size and the like may be used for photographing.

FIG. 21 schematically shows a main configuration of the joint imaging apparatus 1 in the present embodiment.
In the present embodiment, the joint imaging apparatus 1 includes an X-ray source 11, a multi-grating 12, a light irradiation field confirmation unit main body 65, a subject holding member 30 on the subject table 13, a first grating 14, a second grating 15, and an X-ray detector. 16 are arranged in this order along the z direction (see FIG. 1), which is the direction of gravity.

A fixing member 111 formed in a substantially U shape is attached to the X-ray source 11 via an attachment arm 112. In the present embodiment, the support column 17 has a quadrangular prism shape, and the fixing member 111 is attached and fixed to the support column 17 so as to sandwich the support column 17 from the side surface.
A buffer member 17a (see FIG. 1) is provided on a part of the mounting arm 112, and the X-ray source 11 is held via the buffer member 17a. Any material may be used for the buffer member 17a as long as it can absorb shocks and vibrations, and examples thereof include an elastomer. Since the X-ray source 11 generates heat upon irradiation with X-rays, the buffer member 17a on the X-ray source 11 side is preferably a heat insulating material in addition to a material that can absorb shock and vibration.

The X-ray source 11 includes an X-ray tube, generates X-rays by the X-ray tube, and irradiates the X-rays in the gravity direction (z direction). As the X-ray tube, for example, a Coolidge X-ray tube or a rotary anode X-ray tube widely used in the medical field can be used. As the anode, tungsten or molybdenum can be used.
The X-ray focal diameter is preferably 0.03 to 3 (mm), more preferably 0.1 to 1 (mm).

In this embodiment, as shown in FIGS. 5 and 6 and the like, the X-ray source 11 is a multi-unit whose parallelism and relative distance are adjusted by bending a part of the mounting arm 112 approximately 90 degrees. The mounting direction of the X-ray source 11 is configured to be rotatable by approximately 90 degrees with respect to the slit directions of the grating 12, the first grating 14, and the second grating 15.
In the present embodiment, the focal shape of the X-ray tube of the X-ray source 11 is not a perfect circle, but is slightly elliptical. In some cases, an appropriate moire image can be obtained by changing. For this reason, by rotating the X-ray source 11 by approximately 90 degrees, it is possible to eliminate the problems caused by the focal shape of the X-ray tube.
In addition, the structure which enables the X-ray source 11 to change the attachment direction with respect to the slit direction of the multi grating | lattice 12, the 1st grating | lattice 14, and the 2nd grating | lattice 15 is not limited to what was illustrated here. For example, the attachment direction of the X-ray source 11 may be changed by changing the attachment position of the fixing member 111. Further, the change in the mounting direction of the X-ray source 11 is not limited to 90 degrees, and the angle may be set more finely.

Furthermore, in this embodiment, as shown in FIG. 8, the X-ray source 11 is configured such that the end of the mounting arm 112 on the fixed side of the X-ray source 11 is rotatable, and is irradiated from the X-ray source 11. From the state in which the optical axis of the X-ray is substantially parallel to the support column 17 and the X-ray is irradiated onto the multi-grating 12, the first grating 14, and the second grating 15 (see the imaging state FIG. 7), The X-ray irradiation direction of the X-ray source 11 can be changed up to a state (see FIG. 8 in the calibration state) that is out of the multi-grating 12, the first grating 14, and the second grating 15.
Note that the X-ray irradiation direction of the X-ray source 11 at the time of calibration may be any direction in which the optical axis of the X-ray is in a state in which the X-ray optical axis deviates from above the multi-grating 12, the first grating 14, and the second grating 15. It is not limited to what was illustrated to. When the X-ray irradiation direction of the X-ray source 11 at the time of calibration is another direction, the X-ray detector holding unit 25 is attached so as to be disposed on the extension line of the optical axis of the X-ray source 11. The position is adjusted.

An irradiation field stop 113 and a filter 114 are provided directly below the X-ray source 11 and below the multi-grating 12 described later.
The irradiation field stop 113 narrows the X-ray irradiation field irradiated from the X-ray source 11 to a predetermined range.
The filter 114 separates a light beam having an unnecessary wavelength from the light beam irradiated from the X-ray source 11, and an AL addition filter or the like is applied, for example.

As shown in FIGS. 3, 5, and the like, the light irradiation field confirmation unit 6 is mounted on a substantially L-shaped base attaching part 61 attached to the base part 19 and the base attaching part 61. A light irradiation field confirmation unit main body 65. The base mounting portion 61 is fixed to the base portion 19 with screws or the like (not shown).
A guide 63 for moving the light irradiation field confirmation unit main body 65 in the x direction is provided on a surface of the base mounting part 61 that is disposed substantially horizontally with respect to the floor surface. The main body 65 can be moved manually or automatically along the guide 63.
The light irradiation field confirmation unit 6 illuminates the same region as the X-ray irradiation field with visible light in order to confirm the X-ray irradiation field irradiated from the X-ray source 11 in advance. 65 is provided with a light source (not shown) capable of emitting visible light.
Further, the light irradiation field confirmation unit main body 65 is provided with a moving lever 67 that protrudes substantially horizontally with respect to the floor surface from the back side (that is, the support column 17 side) to the front side of the joint photographing apparatus 1. The moving lever 67 is a lever for manually moving the light irradiation field confirming unit main body 65 in the x direction along the guide 63. As described above, the first cover unit 21 is attached to the joint photographing apparatus 1. In the attached state, the tip end portion projects out of the front cover member 211 from the lever opening 211c.

In the present embodiment, the light irradiation field confirmation unit main body 65 confirms the light irradiation field by matching the optical axis of the light emitted from the light source with the optical axis of the X-ray emitted from the X-ray source 11. And a retracted position that does not interfere with the X-rays emitted from the X-ray source 11 can be taken. During normal use, such as when shooting, the light irradiation field confirmation unit main body 65 is located at the retracted position (position indicated by a solid line in FIG. 21) so as not to interfere with shooting. When confirming the light irradiation field, the user appropriately operates the moving lever 67 so that the optical axis of light emitted from the light source of the light irradiation field confirmation unit main body 65 is irradiated from the X-ray source 11. The position of the light irradiation field confirmation unit main body 65 is moved to a light irradiation field confirmation position (a position indicated by a broken line in FIG. 21) that coincides with the optical axis of the X-ray. The light irradiation field confirmation unit main body 65 may be configured to automatically move in the x direction by a motor or the like.
In the present embodiment, since there is nothing that blocks the light from the light irradiation field confirmation unit main body 65 and the first grating 14 and the second grating 15, the light irradiation field can be confirmed accurately.

The multi-grating unit 120, the first grating unit 140, the second grating unit 150, and the X-ray detector 16 are held on the same base 19 and the positional relationship in the z direction is fixed. The multi-grating unit 120, the first grating unit 140, and the second grating unit 150 are extended in a direction orthogonal to the gravitational direction (z direction), and can be attached to and detached from the base unit 19 with screws or the like. It is attached.
The light irradiation field confirmation unit 6 is mounted on the base portion 19 and in the vicinity immediately below the multi-grating unit 120.
Further, the X-ray detector 16 is placed on a detector support base 191 provided on the base 19 via a buffer member 192.
The base unit 19 may be configured to be movable in the z direction with respect to the support column 17.

FIG. 22 is a perspective view of the multi-grid unit 120.
As shown in FIG. 22, the multi-grid unit 120 includes a substantially L-shaped base attachment portion 121 attached to the base portion 19 and a multi-grid unit main body 122 placed on the base attachment portion 121. I have.
A linear guide 123 for moving the multi-grid unit main body 122 in the x direction is provided on a surface of the base mounting portion 121 that is disposed substantially horizontally with respect to the floor surface.
The base mounting part 121 is capable of adjusting the relative distance between the multi-grating 12 and the first grid 14 or the second grid 15 by adjusting the mounting position on the base part 19. The multi-grating unit main body 122 is provided with a relative distance fine adjustment mechanism portion 127. The relative distance fine adjustment mechanism 127 adjusts the position of the multi-grid 12 in the gravitational direction (vertical direction) by changing the length in the gravitational direction (vertical direction). In the present embodiment, the base mounting portion 121 and the relative distance fine adjustment mechanism portion 127 constitute a relative distance adjustment mechanism that adjusts the relative distance between the multi lattice 12 and the first lattice 14 or the second lattice 15. Is done.
From the viewpoints of workability and safety when handling a multi-grid unit that is relatively heavy, and ease of position adjustment, it is preferable to separate the former and latter functions, and the mounting position is Temporarily fixed with positioning pins (not adjustable) and screwed (fixed) to the base 19 with screws or the like. After the fixing is completed, the operator can freely use both hands in the multi-grid unit main body 122. It is preferable that the relative distance be finely adjusted by the provided relative distance fine adjustment mechanism 127.

The multi-grating unit body 122 supports the multi-grating 12 and, as a multi-grating driving unit 125 for moving the multi-grating 12, the x-direction moving motor 125a and the multi-grating 12 are rotated in the x direction. Θx rotating motor 125b, a θy rotating motor 125c for rotating the multi-grating 12 in the y direction, and a θz rotating motor 125d for rotating the multi-grating 12 in the z direction are provided.
In the present embodiment, as shown in FIG. 23, the multi-grating 12 is inserted into the X-ray source 11 from below the X-ray source 11 and is arranged in the immediate vicinity of the focal position of the X-ray tube. It has become.

The x-direction movement motor 125a is a drive source that is energized and is configured by a motor that can perform highly accurate operation control, such as a stepping motor (pulse motor) that operates in synchronization with a pulse signal accurately. ing. As the stepping motor applied to the x-direction moving motor 125a, for example, a 5-phase stepping motor such as a 5-phase stepping motor (model: PX533MH-B) manufactured by Oriental Motor Co., Ltd. is desirable, and a high-resolution type is also available for 5 phases. preferable. That is, in general, the basic step angle is 0.72 °, but in the high resolution type, the basic step angle is 0.36 °, and such a motor is preferably used. Furthermore, it is preferable to perform control by microsteps that can subdivide the number of steps.
In the present embodiment, when the x-direction movement motor 125a that is a driving source is driven, the transmission system that transmits the output of the driving source to the main body of the multi-grid unit 120 including the multi-grid 12 that is a driven part is illustrated. The main body of the multi-grating unit 120 including the multi-grating 12 is guided by the linear guide 123 and moves in the x direction.
The moving unit of the multi-grid unit 120 is configured by the x-direction moving motor 125a as the driving source and the ball screw and linear guide as the transmission system, and the moving unit moves in a direction orthogonal to the gravitational direction (z direction). It is comprised only by the moving element to do.

  In this embodiment, when the multi-grid 12 is moved, the output of the x-direction moving motor 125a is maximized, but at the time of X-ray irradiation, the multi-grid driving unit 125 is moved to the x-direction moving motor 125a. The energizing current value to the x-direction moving motor 125a is adjusted so that the energizing current becomes a current value that is 50% or less of the displacement generated in the multi-grid 12 when the output of the motor is maximized. It is like that.

When photographing a plurality of times while moving the multi-grating 12, in order to maintain the position of the multi-grating 12 with high accuracy, the position is maintained by its self-holding force by exciting the x-direction moving motor 125a with current. Must be fixed. In addition, when shooting a plurality of times while moving the multi-grid 12, the multi-grid 12 is sequentially moved using the current position of the multi-grid 12 as a base point for the next movement, but the power supply is stopped. Otherwise, the current position of the multi-grid 12 cannot be fed back at the next movement. For this reason, even when the multi-grating 12 is not moved (that is, during X-ray irradiation), it is necessary to continue to apply current to the x-direction moving motor 125a until a predetermined plurality of times of imaging are completed. .
On the other hand, if the current value of the current applied to the x-direction movement motor 125a during excitation is high, the x-direction movement motor 125a generates heat and causes slight vibration, which is transmitted to the ball screw. This causes a minute displacement at the position.

In FIG. 24, the horizontal axis represents time (min) and the vertical axis represents the displacement (μm) and temperature change (° C.) of the multi-grid 12, and the excitation current value, temperature change, and displacement of the multi-grid 12 are shown. It is the graph which showed the relationship.
In FIG. 24, the amount of displacement of the multi-grating 12 indicates how much the multi-grating 12 is displaced in the moving direction (x direction) due to the excitation current value and temperature change when the position of the multi-grating 12 in the initial state is zero. It is measured. Further, the temperature rise value is obtained by measuring the temperature change of the x-direction moving motor 125a when the exciting current of each current value is applied.
As shown in FIG. 24, when the exciting current value is about 90% when the output of the motor is maximized, the temperature of the x-direction moving motor 125a rises as time passes, and the multi-grid 12 The amount of displacement also increases, and the amount of displacement exceeds 1.4 μm. On the other hand, if the exciting current value is about 27% of the maximum output of the motor, the temperature of the x-direction moving motor 125a does not rise so much even if time passes, and the displacement of the multi-grid 12 The amount also stops at about 0.3 μm. Even when the excitation current value is about 50% of the maximum output of the motor, the temperature increase of the x-direction moving motor 125a with time is not so large, and the displacement amount of the multi-grid 12 is also zero. It stops at about 45μm.

Here, in order to obtain an appropriate moire image, the lattice feed accuracy of the multi-grid 12 by the x-direction moving motor 125a needs to be 1/10 or less of the lattice feed amount. For example, when a moiré image is obtained by moving the multi-grating 12 five times and photographing five times, the multi-grating 12 is moved by 1/5 of the grating pitch. Further, when a moiré image is obtained by moving the multi-grating 12 three times and photographing three times, the multi-grating 12 is moved by 1/3 of the grating pitch. Therefore, for example, when the lattice pitch is 22.8 μm and the lattice feed amount is 5.7 μm, the required accuracy (lattice relative position) is ± 0.23 μm (PP: 0.46 μm).
In this embodiment, if the exciting current value is about 50% or less when the output of the motor is maximized, the required accuracy (lattice relative position) is satisfied, and the current is supplied to the x-direction moving motor 125a. It can be said that it does not affect the generation of the moire image.

  It should be noted that how much the excitation current value applied to the x-direction moving motor 125a affects the generation of the moire image, that is, “the energization current to the x-direction moving motor 125a maximizes the output of the motor. The degree of the “current value that is 50% or less of the amount of displacement generated in the multi-grid 12” depends on the type of motor. For this reason, it is preferable to set the excitation current value at the time of X-ray irradiation suitably according to the motor to apply.

  The θx rotation motor 125b, the θy rotation motor 125c, and the θz rotation motor 125d are goniostages that incorporate an actuator or the like serving as a drive source, for example, and are arranged between the multi-grid 12, the first grating 14, and the second grating 15. It functions as a turning adjustment mechanism that can adjust the parallelism.

  The multi-grating 12 provided in the multi-grating unit 120 is a diffraction grating, and a plurality of slits are provided at predetermined intervals in the x direction as shown in FIG. The multi-lattice 12 is formed on a substrate having a low X-ray absorption rate, such as silicon or glass, with a material having a high X-ray shielding power, that is, a high X-ray absorption rate, such as tungsten, lead, or gold. For example, the resist layer is masked in a slit shape by photolithography, and UV is irradiated to transfer the slit pattern to the resist layer. A slit structure having the same shape as the pattern is obtained by exposure, and a metal is embedded between the slit structures by electroforming to form a multi-grating 12.

The slit period of the multi-grating 12 is 1 to 60 (μm). As shown in FIG. 25, the slit period is defined as a period between adjacent slits. The width (length in the x direction) of the slit is 1 to 60 (%) of the slit period, and more preferably 10 to 40 (%). The height (length in the z direction) of the slit is 1 to 500 (μm), preferably 1 to 150 (μm).
When the slit period of the multi-grating 12 is w0 (μm) and the slit period of the first grating 14 is w1 (μm), the slit period w0 can be obtained by the following equation.
w0 = w1 · (d3 + d4) / d4
By determining the slit period w0 so as to satisfy the above equation, the self-images formed by the X-rays that have passed through the slits of the multi-grating 12 and the first grating 14 overlap each other on the second grating 15, so to speak. Can be in a suitable state.

  The first grating 14 is a diffraction grating provided with a plurality of slits in the x direction, like the multi-grating 12. The first grating 14 can be formed by photolithography using UV as in the case of the multi-grating 12, or a silicon substrate is deep-digged with fine fine lines by a so-called ICP method to form a grating structure only with silicon. It is good as well. The slit period of the first grating 14 is 1 to 20 (μm). The width of the slit is 20 to 70 (%) of the slit period, and preferably 35 to 60 (%). The height of the slit is 1 to 100 (μm).

  When a phase type is used as the first grating 14, the height of the slit (length in the z direction) is a phase difference (X between the materials of the X-ray transmitting part and the X-ray shielding part, that is, two kinds of materials forming the slit period. The height of the phase difference between the lines is π / 8 to 15 × π / 8. The height is preferably π / 4 to 3 × π / 4. When an absorption type is used as the first grating 14, the height of the slit is set to a height at which X-rays are sufficiently absorbed by the X-ray shielding part.

When the first grating 14 is a phase type, the distance d4 between the first grating 14 and the second grating 15 needs to substantially satisfy the following condition.
d4 = (m + (1/2)). w12 / λ
Note that m is an integer, and λ is the wavelength of X-rays.

  Similar to the multi-grating 12 and the first grating 14, the second grating 15 is a diffraction grating provided with a plurality of slits in the x direction. The second grating 15 can also be formed by photolithography. The slit period of the second grating 15 is 1 to 20 (μm). The width of the slit is 30 to 70 (%) of the slit cycle, and preferably 35 to 60 (%). The height of the slit is 1 to 100 (μm).

  In this embodiment, each of the first grating 14 and the second grating 15 has a grating plane perpendicular to the z direction (parallel in the xy plane), and the slit arrangement direction of the first grating and the slits of the second grating. The arrangement direction is arranged so as to be inclined by a predetermined angle in the xy plane, but both may be arranged in parallel.

The first grating 14 and the second grating 15 are respectively provided in the first grating unit 140 and the second grating unit 150 having substantially the same configuration.
FIG. 26 is an enlarged perspective view of a mounting portion of the first grid unit 140 and the second grid unit 150 in the base unit 19. As shown in FIG. 26, the second grating unit 150 is arranged so that the second grating 15 is located immediately above the X-ray detector 16. The first grating unit 140 is arranged so that the first grating 14 is positioned above the second grating 15.

  27 and 28 are perspective views of the first lattice unit 140 as viewed from above, and FIG. 29 is a perspective view of the first lattice unit 140 as viewed obliquely from above. Since the second grid unit 150 has the same configuration as the first grid unit 140, illustration and description thereof are omitted.

As shown in FIGS. 27 to 29, the first grid unit 140 includes a substantially L-shaped base mounting part 141 and a first grid unit main body 142 that are attached to the base part 19. The first lattice unit main body 142 is placed on a surface of the base mounting portion 141 that is disposed substantially horizontally with respect to the floor surface.
The base mounting portion 141 adjusts the mounting position on the base portion 19 to adjust the relative distance between the first grid 14 and the second grid 15 or the multi grid 12. Function as.
A linear guide 143 for moving the first grid 14 in the x direction is provided on the upper side surface of the first grid unit main body 142.

  The first lattice unit main body 142 is provided with the first lattice 14 supported by the support portion 14a, and as the first lattice driving portion 145 for moving the first lattice 14, an x direction moving motor 145a. A θx rotation motor 145b for rotating the first grating 14 in the x direction is provided.

The x-direction movement motor 145a is a drive source that is energized and driven, for example, a stepping motor (pulse motor) that operates in synchronization with the pulse signal accurately, as with the x-direction movement motor 125a of the multi-grid unit 120. The motor is configured to perform highly accurate operation control.
In this embodiment, when the x-direction moving motor 145a that is a driving source is driven, a ball screw that constitutes a transmission system that transmits the output of the driving source to the support portion 14a that supports the first grid 14 that is the driven portion. 144 rotates, and the first grating 14 supported by the support portion 14a is guided by the linear guide 143 to move in the x direction.
The moving unit of the first lattice unit 140 is configured by the x-direction moving motor 145a that is the driving source, the ball screw and the linear guide that are the transmission system, and this moving unit is in a direction orthogonal to the gravitational direction (z direction). It consists only of moving elements that move.

Here, in order to obtain an appropriate moire image, the lattice feed accuracy of the first lattice 14 by the x-direction moving motor 145a needs to be 1/10 or less of the lattice feed amount, as in the case of the multi-grid 12. There is. For example, when a moire image is obtained by moving the first grating 14 five times and photographing five times, the first grating 14 is moved by 1/5 of the grating pitch, and the first grating 14 is moved three times. When the moire image is obtained by photographing three times, the first grating 14 is moved by 1/3 of the grating pitch. Therefore, for example, when the lattice pitch is 5.3 μm and the lattice feed amount is 1.33 μm, the required accuracy (lattice relative position) is ± 0.05 μm (PP: 0.10 μm).
Then, when an electric current is applied to the x-direction moving motor 145a, the temperature of the motor rises as in the case of the x-direction moving motor 125a and induces thermal expansion of peripheral components. Precise feed cannot be achieved, resulting in static misalignment between the lattices, or slight vibration of the motor, and this vibration propagates to the peripheral parts. As a result, the first lattice 14 cannot be held at the precise feed position. , Dynamic lattice misalignment (indefinite) will occur.

For this reason, the x-direction moving motor 145a also maximizes the output of the x-direction moving motor 145a when moving the first grid 14 as in the case of the x-direction moving motor 125a. At the time of irradiation, the first grid driving unit 145 is such that the current applied to the x-direction moving motor 145a is 50% or less of the displacement generated in the first grid 14 when the output of the motor is maximized. The energization current value to the x-direction moving motor 145a is adjusted so as to be a value.
Note that the energization current value (excitation current value) to the x-direction movement motor 145a during X-ray irradiation is preferably set as appropriate according to the motor to be applied, as in the case of the x-direction movement motor 125a.

  The θx rotation motor 145b is a goniometer stage that incorporates an actuator or the like serving as a drive source, for example, and functions as a tilt adjustment mechanism that can adjust the parallelism among the multi-grating 12, the first grating 14, and the second grating 15. To do. As in the case of the multi-grid unit 120, a θy rotation motor and a θz rotation motor may be provided as the turning adjustment mechanism.

The second grid unit main body 152 is provided with the second grid 15 supported by the support section, and the second grid drive section 155 for moving the second grid 15 includes an x-direction moving motor, A θx rotation motor (none of which is shown) for rotating the two grids 15 in the x direction is provided.
As described above, with respect to the point of adjusting the energization current value (excitation current value) at the time of X-ray irradiation, the x-direction moving motor of the second grid driving unit 155 of the second grid 15 is also multi-grid. This is the same as the x-direction moving motor 125a of the unit 120 and the x-direction moving motor 145a of the first lattice unit 140.

The multi-grating 12, the first grating 14, and the second grating 15 can be configured as follows, for example.
Focal diameter of X-ray tube of X-ray source 11: 300 (μm), tube voltage: 40 (kVp), additional filter: aluminum 1.6 (mm)
Distance d1: 40 (mm) from the focal point of the X-ray source 11 to the multi-grating 12
Distance d3: 1110 (mm) from the multi-grating 12 to the first grating 14
Distance d3 + d4: 1370 (mm) from the multi-grating 12 to the second grating 15
Multi-grating 12 size: 10 (mm square), slit period: 22.8 (μm)
Size of the first grating 14: 50 (mm square), slit period: 4.3 (μm)
Size of the second grating 15: 50 (mm square), slit period: 5.3 (μm)

The X-ray detector 16 has two-dimensionally arranged conversion elements that generate electric signals in accordance with the irradiated X-rays, and reads the electric signals generated by the conversion elements as image signals.
The pixel size of the X-ray detector 16 is 10 to 300 (μm), more preferably 50 to 200 (μm).

The position of the X-ray detector 16 is preferably fixed to the base portion 19 so as to abut on the second grating 15. This is because the moire image obtained by the X-ray detector 16 becomes blurred as the distance between the second grating 15 and the X-ray detector 16 increases.
As the X-ray detector 16, an FPD (Flat Panel Detector) can be used. The FPD includes an indirect conversion type in which X-rays are converted into electric signals by a photoelectric conversion element via a scintillator, and a direct conversion type in which X-rays are directly converted into electric signals, either of which may be used.

  In the indirect conversion type, each pixel is configured by two-dimensionally arranging photoelectric conversion elements together with TFTs (thin film transistors) under a scintillator plate such as CsI, Gd2O3, or Gd2O2S. When the X-rays incident on the X-ray detector 16 are absorbed by the scintillator plate, the scintillator plate emits light. Charges are accumulated in each photoelectric conversion element by the emitted light, and the accumulated charges are read as an image signal.

In the direct conversion type, an amorphous selenium film having a thickness of 100 to 1000 (μm) is formed on a glass by thermal vapor deposition of amorphous selenium, and the amorphous selenium film and electrodes are arranged on a two-dimensionally arranged TFT array. Vapor deposited. When the amorphous selenium film absorbs X-rays, carriers are released into the substance in the form of electron-hole pairs, and the voltage signal between the electrodes is read by the TFT.
Note that an imaging unit such as a CCD (Charge Coupled Device) or an X-ray camera may be used as the X-ray detector 16.

A series of processing by the FPD at the time of X-ray imaging will be described.
First, the FPD is reset to remove unnecessary charges remaining after the previous photographing (reading). Thereafter, charges are accumulated at the timing when the X-ray irradiation starts, and the charges accumulated at the timing when the X-ray irradiation ends are read as an image signal. In addition, immediately after resetting or after reading an image signal, dark reading is performed to detect the voltage value of the accumulated charge, and the correction value is calculated from the voltage value of the charge accumulated after X-ray irradiation using the voltage value as a correction value. The subtracted voltage value may be output as an image signal. Thereby, so-called offset correction can be performed on the image signal.

As shown in FIG. 30, the main unit 18 includes a control unit 181, an operation unit 182, a display unit 183, a communication unit 184, a storage unit 185, a multi-grid drive unit 125, a first grid drive unit 145, and a second grid drive unit. 155.
The control unit 181 includes a CPU (Central Processing Unit), a RAM (Random Access Memory), and the like, and executes various processes in cooperation with a program stored in the storage unit 185. For example, the control unit 181 controls the timing of X-ray irradiation from the X-ray source 11, the reading timing of the image signal by the X-ray detector 16, and the like according to the imaging condition setting information input from the controller 5.

The operation unit 182 includes a touch panel configured integrally with the display of the display unit 183 in addition to a key group used for input operations such as an exposure switch and an imaging condition, and generates an operation signal corresponding to these operations to generate a control unit. It outputs to 181.
The display unit 183 displays the operation screen, the operation status of the joint photographing apparatus 1 and the like on the display according to the display control of the control unit 181.

The communication unit 184 includes a communication interface and communicates with the controller 5 on the network. For example, the communication unit 184 transmits the moire image read by the X-ray detector 16 and stored in the storage unit 185 to the controller 5.
The storage unit 185 stores a program executed by the control unit 181 and data necessary for executing the program. The storage unit 185 stores the moire image obtained by the X-ray detector 16.

  The multi-grid drive unit 125, the first grid drive unit 145, and the second grid drive unit 155 operate the drive sources (motors) of the multi-grid unit 120, the first grid unit 140, and the second grid unit 150. .

  The controller 5 controls the photographing operation of the joint photographing apparatus 1 in accordance with an operation by the operator, and creates a reconstructed image of the subject using the moire image obtained by the joint photographing apparatus 1. In the present embodiment, an example in which the controller 5 is used as an image processing apparatus that creates a reconstructed image of a subject will be described. However, a dedicated image processing apparatus that performs various image processing on an X-ray image is connected to the joint imaging apparatus 1. The reconstructed image may be created by the image processing apparatus.

An X-ray imaging method using the Talbot-Lau interferometer of the joint imaging apparatus 1 will be described.
As shown in FIG. 31, when X-rays irradiated from the X-ray source 11 pass through the first grating 14, the transmitted X-rays form an image at a constant interval in the z direction. This image is called a self-image, and the phenomenon in which a self-image is formed is called the Talbot effect. The second grating 15 is arranged in parallel at a position connecting the self-images, and the second grating 15 is slightly tilted from a position parallel to the grating direction of the first grating 14, and therefore the second grating 15. A moire image M is obtained by the X-rays transmitted through. When the subject H exists between the X-ray source 11 and the first grating 14, the phase of the X-ray is shifted by the subject H, so that the interference fringes on the moire image M are bounded by the edge of the subject H as shown in FIG. 31. Disturbed (distorted). This disturbance (distortion) of the interference fringes can be detected by processing the moire image M, and the subject image can be imaged. This is the principle of the Talbot interferometer.

  In the joint imaging apparatus 1, the multi-grating 12 is disposed near the X-ray source 11 between the X-ray source 11 and the first grating 14, and X-ray imaging using a Talbot-Lau interferometer is performed. The Talbot interferometer is based on the premise that the X-ray source 11 is an ideal point source. However, since a focus having a large focal diameter is used for actual imaging, it is as if a plurality of point sources are connected by the multi-grating 12. Multiple light sources are used as if they were irradiated with X-rays. This is an X-ray imaging method using a Talbot-Lau interferometer, and a Talbot effect similar to that of a Talbot interferometer can be obtained even when the focal diameter is somewhat large.

  In the conventional Talbot-Lau interferometer, the multi-grating 12 is used for the purpose of increasing the number of light sources and increasing the irradiation dose as described above. In order to obtain a moire image by the fringe scanning method, the first grating 14 or the second grating 15 is used. Were moved relative to each other. However, in the present embodiment, the first grating 14 or the second grating 15 is not moved relatively, but the positions of the first grating 14 and the second grating 15 are fixed and the first grating 14 and the second grating 15 are fixed. On the other hand, a plurality of moire images having a constant periodic interval are obtained by moving the multi-grating.

FIG. 32 is a flowchart showing the flow of X-ray imaging performed by the joint imaging apparatus 1.
The above-mentioned X-ray imaging method using the Talbot-Lau interferometer is used for X-ray imaging, and the fringe scanning method is used for reconstruction of the subject image. In the joint imaging apparatus 1, the multi-grid 12 is moved by a plurality of steps at equal intervals, and imaging is performed for each step, and a moire image at each step is obtained.

  The number of steps is 2 to 20, more preferably 3 to 10. From the viewpoint of obtaining a reconstructed image with high visibility in a short time, 5 steps are preferable (Reference Document (1) K. Hibino, BF Oreb and DI Farrant, Phase shifting for nonsinusoidal waves). with phase-shift errors, J. Opt.Soc.Am, A, Vol.12, 761-768 (1995), reference (2) A. Momose, W. Yashiro, Y. Takeda, Y. Suzuki and T. Hattori, Phase Tomography by X-ray Talbot Interferometry for bioimaging, Jpn., J. Appl. ., Vol.45, 5254-5262 (2006)).

As shown in FIG. 32, when the exposure switch is turned on by the operator (step S1; Y), the multi-grid 12 is moved by the x-direction moving motor 125a, and a plurality of steps of imaging are executed, and the moire image is displayed. Is generated (step S2).
First, X-ray irradiation by the X-ray source 11 is started with the multi-grating 12 stopped. After the reset, the X-ray detector 16 accumulates charges in accordance with the timing of X-ray irradiation, and reads the accumulated charges as image signals in accordance with the timing of X-ray irradiation stop. This is one step of shooting. The movement of the multi-grating 12 is started at the timing when the photographing for one step is completed, and is stopped when the predetermined amount is moved, and the photographing of the next step is performed. In this way, the movement and stop of the multi-grating 12 are repeated for a predetermined number of steps, and when the multi-grating 12 stops, X-ray irradiation and image signal reading are performed. The read image signal is output to the main body 18 as a moire image.

  For example, it is assumed that the slit period of the multi-grating 12 is 22.8 (μm) and five-step imaging is performed in 10 seconds. Photographing is performed every time the multi-grating 12 moves and stops 4.56 (μm) corresponding to 1/5 of the slit period. In terms of shooting time, shooting is performed 2, 4, 6, 8, 10 seconds after the explosion switch is turned on.

  When the second grating 15 (or the first grating 14) is moved relative to the first grating 14 (or the second grating 15) as in the prior art, the slit period of the second grating 15 is relatively small, and each step moves. Although the amount is small, the slit period of the multi-grating 12 is relatively larger than that of the second grating 15, and the movement amount of each step is also large. For example, the amount of movement of the second grating 15 with a slit period of 5.3 (μm) per step is 1.06 (μm), whereas the amount of movement of the multi-grating 12 with a slit period of 22.8 (μm) is It is 4.56 (μm), about four times as large. When the same drive transmission system (including a drive source and a deceleration transmission system) is used, and when photographing at each step, starting and stopping the x-direction movement motor 125a are repeated, a moving pulse motor ( The ratio of the movement amount error due to the influence of the backlash of the x-direction moving motor 125a at the time of start and stop in the actual movement amount corresponding to the control amount (drive pulse number) of the drive source) Thus, the method of moving the multi-grating 12 becomes smaller. This indicates that it is easy to obtain a moire image along a sine curve, which will be described later, and that a high-definition reconstructed image can be obtained even after repeated activation and stoppage. Alternatively, if the image based on the conventional method is sufficiently suitable for diagnosis, the accuracy of the entire drive transmission system including the motor (drive source) (especially, start characteristics and stop characteristics) is relaxed, and the components of the drive transmission system are reduced. This shows that the cost can be reduced.

  When the photographing at each step is completed, the moire image at each step is transmitted from the main body 18 to the controller 5 (step S3). The main body 18 may send the image to the controller 5 one by one each time the shooting of each step is completed, or after the shooting of each step is completed and all the moire images are obtained, the images are collected. It is good also as transmitting.

FIG. 33 is a flowchart showing the flow of processing of the controller 5 after receiving the moire image.
As shown in FIG. 33, first, a moire image is analyzed (step S11), and it is determined whether or not it can be used to create a reconstructed image (step S12). When the multi-grating 12 can be moved with a constant feeding amount with ideal feeding accuracy, five moire images corresponding to one slit period of the multi-grating 12 are obtained by photographing in five steps as shown in FIG. Since the moire image of each step is a result of stripe scanning at fixed intervals of 0.2 cycles, when attention is paid to any one pixel of each moire image, the X-ray relative intensity obtained by normalizing the signal value Draws a sine curve as shown in FIG. Therefore, the controller 5 obtains the X-ray relative intensity by paying attention to the pixel having the moire image obtained in each step. If the X-ray relative intensity obtained from each moire image forms a sine curve as shown in FIG. 35, it is determined that a moire image having a constant periodic interval has been obtained and can be used to create a reconstructed image. be able to.
Note that the sine curve shape depends on the multi-grating aperture width, the phase grating period, and the inter-grating distance of the phase grating, and in the case of coherent light such as radiated light, it becomes a triangular wave shape. Since X-rays act as quasi-coherent light due to the effect, a sine curve is drawn.

If there is a moiré image in which a sine curve cannot be formed in the moiré image at each step, it is determined that it cannot be used to create a reconstructed image (step S12; N), and an instruction is given to change the shooting timing and reshoot. Control information is transmitted from the controller 5 to the joint imaging apparatus 1 (step S13). For example, as shown in FIG. 27, if the third step is originally 0.4 period, and the period is shifted and a moire image with 0.35 period is obtained, the feeding accuracy of the x-direction moving motor 125a is obtained. This is considered to be caused by a decrease in noise (for example, noise superposition on the drive pulse of the pulse motor). Therefore, it suffices to instruct to re-shoot only the third step by advancing the shooting timing by 0.05 cycles. Alternatively, it may be instructed to re-photograph all five steps and to advance the photographing time for 0.05 cycles only at the third step. When the moire images of all five steps are deviated from the sine curve by a predetermined amount, it may be instructed to increase or decrease the number of drive pulses from the start to the stop of the x-direction moving motor 125a.
In the joint imaging apparatus 1, the imaging timing is adjusted according to the control information, and the X-ray imaging process shown in FIG. 32 is executed again.

  On the other hand, when it is determined that a moiré image can be used to create a reconstructed image (step S12; Y), the moiré image is processed by the controller 5, and a reconstructed image of the subject is created (step S14). Specifically, an intensity change (change in signal value) for each step is calculated for each pixel of five moiré images, and a differential phase is calculated from the intensity change. If necessary, a phase connection (phase unwrapping) is performed to determine the phase of the entire step. An optical path difference in the z direction (optical path difference caused by a refractive index difference) is calculated from the phase, and a reconstructed image representing the shape of the subject is created (the above-mentioned references (1) and (2)). Since the created reconstructed image is displayed on the controller 5, the operator can confirm the reconstructed image.

As described above, according to the present embodiment, the joint photographing apparatus 1 photographs the joint part of a subject such as a human finger, and the subject table 13 uses the joint part that is the photographing target part as X. An imaging target fixing unit 33 that fixes the X-ray irradiation direction from the radiation source 11 at a predetermined position, and a base unit 31 that is configured to be detachable and to fix the wrist portion of the subject. ing. As a result, it is difficult to place the joint part straight on the subject table 13 when the patient has developed a lesion such as when rheumatism has already occurred, or when there is a pain in the joint part or the like. Even in this case, the subject to be imaged can be firmly fixed without imposing a burden on the patient, and shaking or shaking of the subject to be imaged during photographing can be suppressed.
In addition, after fixing the wrist by the wrist fixing belt 313 provided in the base unit 31, the imaging target fixing unit 33 can fix the joint portion which is the imaging target portion at a predetermined position suitable for imaging. Therefore, even when the patient cannot extend the joint part or the like straight, the subject can be prevented from floating from the subject holding member 30, and can be stably fixed. For this reason, it is possible to prevent the subject from moving due to trembling of fingers or body movement, and it is possible to prevent the possibility of image blurring or re-shooting.
In addition, since the first to-be-photographed object fixing unit 33a to the fifth to-be-photographed object-fixing unit 33e are provided as the to-be-photographed object fixing unit 33, depending on the purpose of imaging, the imaging object part, the state of the joints of the patient's fingers, etc. The engineer who is the user can select the most suitable one. For this reason, an image suitable for diagnosis can be obtained while reducing the burden on the patient.
In addition, since a multi-grating having a plurality of slits and / or a first phase grating and a second phase grating are provided and a moire image can be formed, the joint portion can be imaged by a fringe scanning method. Thus, it is possible to obtain an image suitable for diagnosis of articular cartilage and soft tissue around the joint, which has a small X-ray absorption difference and is difficult to appear as an image by the absorption contrast method.

In addition, the said embodiment is a suitable example of this invention, and the scope of the present invention is not limited to this.
For example, in the present embodiment, five types of the first photographing target fixing unit 33a to the fifth photographing target fixing unit 33e are prepared as the photographing target fixing unit 33 constituting the subject holding member 30, and any of these is arbitrarily selected. Although an example of selecting and mounting the base unit 31 is shown, the type and number of the imaging target fixing units 33 are not limited to this.
For example, only one of these may be provided, or a photographing target fixing unit 33 having another shape may be further provided.

Further, in the present embodiment, the case where the joint portion of the finger is photographed by the joint photographing apparatus 1 is described, and the subject holding member 30 is also described that holds and fixes the photographing target portion of the finger, but the joint photographing apparatus 1 The parts that can be photographed by the method are not limited to the joint parts of the fingers, and for example, joint parts such as the shoulder, ankle, and knee can be photographed.
In this case, it is necessary to place a patient's leg or the like on the subject table 13 in order to position the joints such as the shoulder, ankle, and knee in the light irradiation field of the X-ray source 11. For this reason, for example, FIG. 36 shows that the load on the main body of the subject table 13 and the first and second grids located below the subject table 13 are not loaded or affected even when the patient's weight is applied. A subject support plate 7 is disposed on the subject table top surface plate 3 of the subject table 13 as shown. The subject support plate 7 is composed of, for example, a support plate main body 71 and legs 72 provided on the back side thereof, and a portion of the support plate main body 71 corresponding to the transparent plate member 305 of the subject table upper surface plate 3 is X. An opening 73 is provided so as not to disturb the X-rays emitted from the radiation source 11. The leg portion 72 of the subject support plate 7 is placed on the upper end surface of the guard member 41 provided so as to surround the subject table 13. In this way, by supporting the subject support plate 7 with the upper end surface of the guard member 41, the guard member 41 absorbs the load and impact applied to the subject support plate 7, and the subject table 13, the first grid, the second grid, and the like. It is possible to prevent an impact or the like from being applied.

Also, when the patient needs to take a picture of the whole body, such as when photographing a joint part such as a shoulder, an ankle, or a knee, the auxiliary table 8 is appropriately attached to the subject table 13 or as shown in FIG. It may be connected to the subject support plate 7.
For example, the auxiliary base 8 includes an auxiliary base base 81 having a caster 83 and an auxiliary base upper surface plate 82. It is preferable that a lock mechanism (not shown) for locking the caster 83 is provided on the caster 83 of the auxiliary base base portion 81 so that the auxiliary base 8 is stabilized when the patient gets on the auxiliary base 8. Each auxiliary base 8 is configured to be mutually connectable with other auxiliary base 8 and subject base 13 (or subject support plate 7), and a mechanism for locking each other so that no rattling occurs when connected. Is preferably provided. The auxiliary table 8 is used by being connected as many as necessary according to the height of the patient, the imaging region, and the like. Thus, by freely connecting and using, it becomes possible to respond flexibly to various imaging | photography with the one joint imaging device 1. FIG.

FIG. 38 shows an example in which imaging is performed by connecting two auxiliary platforms 8 on the patient's head side and two lower body sides when imaging the patient's left shoulder joint. When it is necessary to take an image of the body at an angle, an auxiliary member such as a cushion (not shown) is appropriately arranged below the patient's body for adjustment.
FIG. 39 shows an example in which imaging is performed with one auxiliary base 8 connected to the patient's head and one lower body when the patient's right ankle joint is imaged. is there. FIG. 39 shows a case where an auxiliary member 75 such as a cushion is placed under the toe portion for adjustment in order to keep the ankle angle constant.
Further, FIG. 40 shows one auxiliary table on the patient's head side and one auxiliary body on the lower body side, similar to the case of photographing the ankle shown in FIG. 39, when photographing the joint part of the patient's right knee. 8 shows an example in which shooting is performed with 8 connected. FIG. 40 shows a case where an auxiliary member 75 such as a cushion is placed under the knee for adjustment in order to keep the knee angle constant.
Further, FIG. 41 shows a case where the joint portion of the patient's left knee is photographed from the back side, as in the case of photographing the ankle shown in FIG. 39, one on the patient's head side and one on the lower body side. An example is shown in which two auxiliary bases 8 are connected and an auxiliary plate 85 inclined so that the patient's head side becomes higher is disposed on the auxiliary base 8 that is arranged on the patient's head side. When such an auxiliary plate 85 is used, for example, as shown in FIG. 41, it is possible to perform photographing while maintaining a posture in which the patient warps the upper body. The auxiliary plate 85 is not limited to the case where it is separate from the auxiliary table 8. For example, the auxiliary plate 85 is provided integrally with the auxiliary table 8, for example, by providing a reclining mechanism on the auxiliary table upper surface plate 82. Also good. In this case, it is preferable that reclining is possible at a plurality of angles. In this case, a reclining mechanism may be provided on all the auxiliary bases 8 or only a part of the auxiliary bases 8 may be provided with a reclining mechanism so that the auxiliary base 8 provided with the reclining mechanism and the auxiliary base 8 not provided are appropriately provided. You may make it use it combining.
Further, as shown in FIG. 42, the legs are placed on the support plate main body 71 of the subject support plate 7 while the patient is on the commercially available stretcher (stretcher) 9 without using the auxiliary table 8. You may take a picture.
37 to 41 exemplify the case where photographing is performed using a plurality of connectable auxiliary bases 8, but a bed-type subject holding base in which the subject support plate 7 and the auxiliary base 8 are integrated ( You may perform imaging | photography using (not shown). In this case, for example, the leg portion of the subject holding base is provided at a position where it does not interfere with the subject base 13 of the joint photographing apparatus 1, and the subject holding base on which the patient is placed is laid from the front side of the joint photographing apparatus 1 to photograph the patient. Imaging is performed by arranging the target portion so as to be located in the light irradiation field of the joint imaging apparatus 1.
Note that the subject support plate 7, the auxiliary stand 8, and the like may be any one that can appropriately hold and fix the joints of each part to be imaged in the light irradiation field of the X-ray source 11 during imaging. It is not limited to what you did. The shape, configuration, and the like can be changed as appropriate according to the region to be imaged.

  In the above embodiment, the height of the subject table upper surface plate 3 is provided with a function for adjusting the height. However, a mechanism for adjusting the height is provided on the leg portion 132 of the subject table 13 so that the subject table 13 itself is provided. You may make it adjust the height of.

  In a reconstructed image acquired using a Talbot interferometer and a Talbot-low interferometer, the larger the difference in the X-ray refractive index from the surroundings, the larger the signal value appears. Therefore, when imaging is performed using a structure inside the subject (for example, a soft tissue peripheral part) as a region of interest, if there is a shape change (for example, a skin wrinkle) on the subject surface, the subject surface and the surrounding air Since the X-ray refractive index difference between and is relatively large, a signal value indicating a change in the shape of the surface of the subject appears large, and is superimposed on a small change in the signal value indicating the structure of the region of interest. Visibility deteriorates.

If the skin surface (including wrinkles) on the surface of the subject and the region of interest inside the subject (soft tissue periphery) do not overlap in the z direction, the region of interest (soft tissue periphery) can be visually recognized even in air. However, it is difficult to grasp the relative positional relationship of the region of interest inside the subject with respect to the subject surface structure before photographing.
Therefore, as shown in FIG. 43, a refractive index adjustment tank 51 that holds a liquid material 511 that reduces the difference in X-ray refractive index between the subject surface and the surroundings is provided in the subject table 13, and this liquid material is used during photographing. The subject (here, a hand) may be put in 511 for shooting.
The liquid material 511 that reduces the X-ray refractive index difference between the subject surface and the surroundings is, for example, water. Water has an X-ray refractive index closer to the subject surface than air. If the hand is put in the water, the subject surface is covered with water, and the water is brought into close contact with the subject surface by water pressure. Therefore, the difference in X-ray refractive index between the subject surface and its surroundings is reduced.
As the liquid material 511 that covers the subject, water is the simplest, cheap, and safe and preferable, but water added with a fragrance, a disinfectant, a pigment, etc. is used to increase the patient's sense of security. May be. Moreover, it is a preferable aspect to use the liquid material 511 which is not water but is closer to human flesh or body fluid. For example, a hyaluronic acid solution, a gelatin solution, a glycerin solution, a mannose solution, a rice juice, a starch powder, or the like can be used alone or in a solution with water.

  In addition, when imaging using a Talbot interferometer or a Talbot-Lau interferometer, a plurality of moire images are captured, so the imaging time is expected to be longer than that of a conventional simple X-ray imaging system. Minute level). During this time, the subject may move. In this respect, if a subject (here, a hand) is placed in the refractive index adjustment tank 51 holding the liquid material 511 and photographing is performed, the subject can be pressed and fixed by water pressure. For example, as shown in FIG. 43, the refractive index adjusting tank 51 preferably has a floating cover 512 and is connected to the sub tank 514 via a pipe 513. By performing imaging using the refractive index adjustment tank 51 having such a configuration, it is possible to suppress movement of the subject in the z direction, particularly in the X-ray tube direction, by pressing and pressing the subject. The diagnostic accuracy of the reconstructed image can be improved. In order to make the subject more stable, the subject table 13 preferably has a length that can hold from the elbow to the fingertip. This allows the patient to deposit the load (weight) in the periphery of the imaging target on the subject table, and therefore the probability that the finger that is the region of interest moves unexpectedly can be made extremely low.

In the above embodiment, the X-ray source 11, the multi-grating 12, the subject table 13, the first grating 14, the second grating 15, and the X-ray detector 16 are arranged in this order (hereinafter referred to as the first arrangement). However, the arrangement of the X-ray source 11, the multi-grating 12, the first grating 14, the subject table 13, the second grating 15, and the X-ray detector 16 (hereinafter referred to as the second arrangement) A reconstructed image can be obtained by moving the multi-grating 12 while the second grid 15 is fixed.
In the second arrangement, the subject center and the first grid 14 are separated from each other by the thickness of the subject, which is slightly inferior in sensitivity compared to the above-described embodiment. In consideration of dose reduction, the arrangement effectively uses X-rays by the amount of X-ray absorption in the first grating 14.
The effective spatial resolution at the subject position depends on the focal diameter of the X-ray, the spatial resolution of the detector, the magnification of the subject, the thickness of the subject, and the like. When the resolution is 120 μm (Gauss half width) or less, the effective spatial resolution is smaller in the second arrangement than in the first arrangement.
It is preferable to determine the order of arrangement of the first grating 14 and the object table 13 in consideration of sensitivity, spatial resolution, the amount of X-ray absorption in the first grating 14, and the like.

In this embodiment, the joint imaging apparatus using the Talbot-Lau interferometer including the multi-grating, the first grating, and the second grating is described as an example of the fringe scanning method. The present invention is not limited to the Talbot-Lau interferometer, and the present invention can also be applied to a joint imaging apparatus using a Talbot interferometer having a first grating and a second grating as a fringe scanning method.
Furthermore, the joint imaging apparatus is not limited to the one using the fringe scanning method. For example, the present invention may be applied to a joint imaging apparatus that performs imaging using a one-dimensional grating or a two-dimensional grating, which does not require fringe scanning, or a normal phase-contrast imaging method. This can be reduced and is preferable.

In the present embodiment, the subject table 13 is described as an example of a completely separate configuration. However, the subject table 13 may be fixed to the base 19 or the like. In this case, a buffer member or the like is provided between the subject table 13 and the base unit 19 so that the impact or vibration applied to the subject table 13 is not transmitted to the base unit 19 as much as possible.
The height of the subject table 13 may be adjusted according to the patient's body shape and the like.

  In the present embodiment, the case where the multi-grid unit 120, the first lattice unit 140, and the second lattice unit 150 are provided with the turn adjustment mechanism and the relative distance adjustment mechanism is described as an example. The relative distance adjustment mechanism does not need to be provided in all of the multi-grating unit 120, the first grating unit 140, and the second grating unit 150, and may be provided in at least one of them.

  In the present embodiment, the case where the moire image is generated by moving the multi-grating 12 has been described as an example. However, the grid to be moved to generate the moire image is not limited to the multi-grating 12, and the first grating 14 is used. The second grating 15 may be used.

  Further, as the X-ray detector 16, a cableless cassette type FPD that incorporates a battery and outputs an image signal to the main body 18 by radio may be used. According to the cassette type FPD, cables connected to the main body 18 can be eliminated, and a further space around the X-ray detector 16 can be reduced. By reducing the space, the subject's feet can be configured wider, and the patient can be more difficult to touch.

Further, the controller of the controller 5 may perform a reconstructed image creation process by a Fourier transform method in addition to a reconstructed image creation process by a fringe scanning method (in this case, the first grid and the first grid of the joint imaging apparatus). It is necessary to change the apparatus setting so that only the relative angle with the two gratings is increased compared to the case of the fringe scanning method.
For example, the reconstructed image creation process by the Fourier transform method is performed as follows.
First, a moire image with a subject and a moire image without a subject are acquired, and corrections such as offset correction processing and gain correction processing are performed for each. Thereafter, each of the corrected moire image with the subject and the moire image without the subject is subjected to Fourier transform (two-dimensional Fourier transform). When a single moire image is subjected to Fourier transform, a low frequency component (referred to as a 0th order component) and a component near the interference fringe frequency (referred to as a primary component), or a high frequency component (in addition to the 0th order component and the primary component) ( Side-by-side (depending on the coherence of the joint imaging apparatus 1).
Next, in the image obtained by Fourier transform (each with and without the subject), the zero-order component is cut out by the Hanning window. By cutting out with the Hanning window, the peripheral portion of the Hanning window is dropped to 0, and the central portion of the Hanning window is passed as it is.
Next, in the image obtained by Fourier transform, the primary component is shifted by the carrier frequency (= moire frequency) and cut out by the Hanning window. The cutting window function is not limited to the Hanning window, and a Hamming window, a Gaussian window, or the like may be used depending on the application.
Next, each of the extracted 0th-order component and 1st-order component is subjected to inverse Fourier transform.
When the inverse Fourier transform ends, the reconstructed images with and without the subject are created using the zeroth-order component and the first-order component subjected to the inverse Fourier transform. Specifically, an absorption image is created from the amplitude of the zeroth order component. A phase image is created from the phase of the primary component. Further, a small angle scattered image is created from the amplitude ratio (= Visibility) of the zeroth order component and the first order component.
Next, using the reconstructed image without the subject, the phase of the interference fringes is removed from the reconstructed image with the subject, and correction processing for removing image unevenness (artifact) is performed. Then, the reconstructed image creation process by the Fourier transform method ends.

  In addition, it cannot be overemphasized that this invention is not limited to this embodiment, and can be changed suitably.

DESCRIPTION OF SYMBOLS 1 Joint imaging apparatus 5 Controller 11 X-ray source 12 Multi grating | lattice 13 Subject stand 14 1st grating | lattice 15 2nd grating | lattice 16 X-ray detector 17 Support | pillar 17a Buffer member 18 Main body part 19 Base part 21 1st cover unit 22 2nd Cover unit 30 subject holding member 31 base unit 33 photographing target fixing unit 41 guard member

Claims (4)

A subject table that holds the finger of the person who is the subject in the shooting position;
Radiation generating means for irradiating a joint portion of a finger, which is an imaging target portion of the subject, and radiation detection means, which is disposed below the subject table and detects the radiation transmitted through the joint portion. An imaging unit having means;
A joint imaging device comprising:
The subject table is
An imaging target fixing unit that fixes a joint part, which is the imaging target part, at a predetermined position with respect to a radiation irradiation direction from the radiation generating unit;
A base unit configured to detachably attach the photographic subject fixing unit and fix a wrist portion of the subject;
A joint photographing apparatus comprising: A plurality of the photographing target fixing units for fixing the joint portions of the fingers at predetermined positions different from each other;
The joint imaging apparatus according to claim 1, wherein each of the plurality of imaging target fixing units is configured to be detachable from the base unit.   It is a fringe scanning type photographing apparatus including a first grating and a second grating that are provided in a plurality of slits extending in a direction orthogonal to the direction of irradiation of radiation from the radiation generating means. The joint imaging apparatus according to claim 1 or 2. Comprising a multi-grating arranged in the vicinity of the radiation generating means,
The joint imaging apparatus according to claim 3, wherein the multi-grating is a Talbot-Lau interferometer that moves the multi-grating relative to the first and second gratings.

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