JP5480117B2 - Radiation image capturing apparatus and radiation image capturing system - Google Patents

Description

  The present invention relates to a radiation image capturing apparatus configured by connecting a plurality of radiation detection units provided with a radiation conversion panel for converting radiation into a radiation image and a panel housing section for housing the radiation conversion panel at a coupling section; The present invention relates to a radiographic image capturing apparatus and a radiographic image capturing system having a control device for controlling the radiographic image capturing apparatus.

  2. Description of the Related Art In the medical field, radiation image capturing apparatuses that irradiate a subject with radiation and guide the radiation transmitted through the subject to a radiation conversion panel to capture a radiation image are widely used. As the radiation conversion panel, a conventional radiation film in which the radiation image is exposed and recorded, or radiation energy as the radiation image is accumulated in a phosphor and irradiated with excitation light, thereby stimulating the radiation image. A storage phosphor panel that can be extracted as light is known. These radiation conversion panels supply the radiation film on which the radiation image is recorded to the developing device to perform development processing, or supply the storage phosphor panel to the reading device to perform reading processing, A visible image can be obtained.

  On the other hand, in an operating room or the like, it is necessary to be able to immediately read out and display a radiation image from a radiation conversion panel after imaging in order to perform a quick and accurate treatment on a patient. As a radiation conversion panel that can meet such demands, a direct conversion type radiation conversion panel using a solid-state detection element that directly converts radiation into an electrical signal, or a scintillator that temporarily converts radiation into visible light, and the visible light. An indirect conversion type radiation conversion panel using a solid-state detection element that converts light into an electrical signal has been developed.

  And the radiation detection unit called an electronic cassette is comprised by accommodating the direct conversion type or indirect conversion type radiation conversion panel mentioned above in a panel accommodating part. The electronic cassette is more expensive than a radiation detection unit configured by housing a radiation film or a storage phosphor panel in a panel housing portion, but a high-quality radiation image can be obtained. Since image display can be performed promptly, it has become popular in recent years.

  By the way, as imaging for a subject, normal imaging in which radiation transmitted through a predetermined imaging region of the subject is converted into a radiographic image using one radiation detection unit, and long imaging that does not fit in one image. There is long imaging for obtaining a radiation image of a part (for example, the whole body of the subject) (see Patent Documents 1 to 3).

  Japanese Patent Application Laid-Open No. H10-228688 proposes to perform long photographing in a state where a plurality of stimulable phosphor sheets are partially overlapped and accommodated in a housing. Japanese Patent Application Laid-Open No. 2004-133830 proposes to perform long photographing in a state where a plurality of indirect conversion type radiation conversion panels are partially overlapped. In Patent Documents 1 and 2, a long subject image can be obtained by synthesizing the radiation images obtained by the radiation conversion panels. In Patent Document 3, in view of the fact that the electronic cassette is more expensive and thicker than other radiation detection units, one electronic cassette is moved relative to the imaging region of the subject, and at each moved position. It has been proposed to synthesize each radiographic image after imaging to obtain a single long radiographic image.

JP 2002-85392 A JP 2000-292546 A JP 2008-17965 A

  In the technique of Patent Document 1, since the thickness of the stimulable phosphor sheet is relatively thin, even if a plurality of the stimulable phosphor sheets are partially overlapped, the step of the overlapped portion (connection portion) does not increase. Therefore, there is no possibility that the thickness of the housing increases. However, in order to be able to quickly display an image of a long subject, it is desirable to take a long image using an electronic cassette.

  However, in the technique of Patent Document 2, since a part of the thick electronic cassette is overlapped, the step at the connecting portion is increased, and as a result, the thickness of the housing that accommodates the plurality of electronic cassettes is increased. There is a risk that the entire system becomes large. On the other hand, when a plurality of connected electronic cassettes are used for long shooting without being housed in a casing, the subject may feel uncomfortable with the presence of a step during shooting.

  Moreover, in the technique of Patent Document 3, since the radiation (imaging) is performed on the subject at each position where the electronic cassette is moved, the above-described step problem does not occur, but over a long period from the start of imaging to the end of imaging, The subject must maintain the same posture. Further, if body movement of the subject occurs during shooting, there is a possibility that image composition after shooting may be broken.

  The present invention has been made to solve the above-described problems, and a radiographic image that enables long imaging by connecting a plurality of radiation detection units without causing a step at the connection location. An object is to provide an imaging apparatus and a radiographic imaging system.

The present invention provides a radiation image having a radiation conversion panel capable of converting radiation into a radiation image, a plurality of radiation detection units including a panel housing portion that houses the radiation conversion panel, and a connecting portion that connects the radiation detection units. A photographing device,
Each panel accommodating portion is provided with a front surface through which the radiation can be transmitted and a back surface opposite to the front surface,
The surface of each panel housing portion is an irradiation surface irradiated with the radiation that has passed through the subject, and the irradiation region of the radiation on the irradiation surface is an imaging region that can be converted into the radiation image.
Each said panel accommodating part is the 1st panel accommodating part which has a 1st irradiation surface, and the 2nd panel accommodating part which has a 2nd irradiation surface,
By connecting the panel accommodating portions by the connecting portion so that a part of each of the radiation conversion panels overlaps and alternately repeating in order of the first irradiation surface and the second irradiation surface, The radiographic imaging apparatus including the radiographing areas is configured to maintain a radiographic imaging surface in a substantially flat shape.

In addition, the present invention includes a radiation conversion panel capable of converting radiation into a radiation image, a plurality of radiation detection units including a panel housing unit that houses the radiation conversion panel, and a connection unit that connects the radiation detection units. A radiographic imaging device;
A control device for controlling the radiographic imaging device;
A radiographic imaging system comprising:
Each panel accommodating portion is provided with a front surface through which the radiation can be transmitted and a back surface opposite to the front surface,
The surface of each panel housing portion is an irradiation surface irradiated with the radiation that has passed through the subject, and the irradiation region of the radiation on the irradiation surface is an imaging region that can be converted into the radiation image.
Each said panel accommodating part is the 1st panel accommodating part which has a 1st irradiation surface, and the 2nd panel accommodating part which has a 2nd irradiation surface,
By connecting the panel accommodating portions by the connecting portion so that a part of each of the radiation conversion panels overlaps and alternately repeating in order of the first irradiation surface and the second irradiation surface, The radiographic imaging apparatus including the radiographing areas is configured to maintain a radiographic imaging surface in a substantially flat shape.

  According to these inventions, when a plurality of two types of radiation detection units are alternately and repeatedly connected by a connecting portion to form a single radiographic image capturing apparatus, and the radiographic image capturing apparatus performs a long image capturing on a subject. In addition, the radiation detecting units are connected by the connecting portion as follows.

  In other words, each of the radiation conversion panels is overlapped and each panel housing portion is used by using the connecting portion so that the first irradiation surface and the second irradiation surface, which are surfaces, are alternately repeated in this order. By connecting, the imaging surface of the radiographic imaging device configured to include each imaging region is maintained substantially flat without generating a step at the connection location.

  In other words, in the present invention, each irradiation surface constituting the imaging surface is in the order of the first irradiation surface → the second irradiation surface → the first irradiation surface → the second irradiation surface →. By sequentially connecting the two types of the respective radiation detection units by the connecting portion in a state of repeating alternately in the order of surface → first irradiation surface → second irradiation surface → first irradiation surface →. While suppressing the overall thickness of the radiographic image capturing device to the thickness of each radiation detection unit, no step is generated at the connection location.

  Therefore, according to the present invention, it is possible to perform long imaging by connecting a plurality of radiation detection units without causing a step at the connection location. That is, in the present invention, even if the radiation detection units are sequentially connected, it is possible to avoid an increase in the size of the radiation image capturing apparatus and to ensure that the capturing surface is flat.

  In addition, since the radiation image capturing apparatus is configured by connecting the panel housing portions by the connecting portion, it is possible to perform long-time imaging with a single irradiation of radiation to the subject, and shorten the imaging time. Can also be realized.

  Further, in the present invention, the radiation detection units are sequentially connected so as not to generate a step at the connection location. Therefore, as compared with the case where a step is generated at the connection location of each electronic cassette as in Patent Document 2. When the electronic cassettes are disconnected from each other, it is possible to avoid a problem that the electronic cassettes are broken due to an impact (for example, an impact caused by a drop) caused by a step at the connection location.

  In the present invention, for example, when the first panel housing portion and the second panel housing portion are connected by the connecting portion, the radiation conversion panel housed in the first panel housing portion is used. The first panel housing so that a part on the second panel housing part side and a part on the first panel housing part side in the radiation conversion panel housed in the second panel housing part overlap. When the unit and the second panel housing unit are connected, the respective radiographic images obtained by the respective radiation conversion panels are combined to obtain a radiographic image of one long subject. It is also possible to prevent an image from being lost at the connection location of the radiation images.

  Therefore, according to the present invention, the two types of radiation detection units are alternately connected, and the overall thickness of the radiation imaging apparatus is made the thickness of each radiation detection unit without causing a step at the connection point. Suppressing and maintaining the imaging surface in a flat shape can eliminate the sense of incongruity of the subject at the time of imaging, and also realizes a thinner radiographic imaging device compared to the prior art. It is also possible to do. In addition, since the radiographic image capturing apparatus is configured by connecting the two types of the respective radiation detection units with a connecting unit, the imaging time can be shortened.

  Note that each of the radiation detection units described above is an electronic cassette that can perform normal imaging even when each is alone, and in the present invention, each of the above-described radiation cassettes is connected by connecting the plurality of electronic cassettes at the connection portion. An effect is obtained.

  Further, a side surface of each panel housing portion is provided between an outer peripheral portion on the front surface and an outer peripheral portion on the back surface of each panel housing portion, and the connecting portion is formed on a side surface of each panel housing portion. It is desirable that the panel accommodating portions are connected by fitting the step portions.

  Thereby, each said panel accommodating part can be connected more easily.

  In this case, each panel housing portion is a substantially rectangular housing, and a part of the side portion of each housing is configured as a block that is removable from the housing, and the block is removed from the housing. Each of the step portions may be formed by detaching. Alternatively, each panel housing portion is a substantially rectangular housing, and a part of the side portion of each housing is configured as a block that can rotate with respect to the housing, and the block is configured as the housing. The step portions may be formed by rotating with respect to the body.

  As described above, since the step portion is easily formed by removing or rotating the block, the panel housing portions can be efficiently connected. In addition, when the step is formed by rotating the block, the block is not separated from the housing, so that loss of the block or the like can be prevented.

  Further, of the step portion of the first panel housing portion and the step portion of the second panel housing portion, one of the step portions is provided with a convex portion, and the other step portion is provided with a concave portion that fits into the convex portion. When provided, the panel housing portions can be reliably and easily coupled when the panel housing portions are coupled.

  In the first panel housing portion, a surface close to the step portion of the first panel housing portion is a back surface, while a surface facing the back surface and spaced apart from the step portion is the first panel housing portion. The irradiation surface (surface) may be used. In the second panel housing portion, a surface close to the stepped portion of the second panel housing portion is defined as the second irradiation surface (front surface), while facing the second irradiation surface. The surface separated from the stepped portion may be the back surface. As described above, by determining the front surface (irradiation surface) and the back surface in advance, it is possible to efficiently connect the panel housing portions.

  The radiographic imaging apparatus may further include a connection order information generation unit that detects a connection order of the panel storage units connected by the connection unit and generates a detection result as connection order information.

  As described above, each irradiation surface constituting the imaging surface is in the order of the first irradiation surface → the second irradiation surface → the first irradiation surface → the second irradiation surface →... (Or the second irradiation). Since the panel accommodating portions are sequentially connected in the order of plane → first irradiation surface → second irradiation surface → first irradiation surface →...), The radiation images are synthesized. When the image of one long subject is formed, the radiation image obtained by referring to the connection order information is an image on the first irradiation surface, or the second irradiation surface. It is possible to specify whether the image is in As a result, the one long image can be efficiently formed.

The control device includes an image processing unit that generates an image of the subject based on a radiation image obtained by each radiation conversion panel, and the image processing unit is generated by the connection order information generation unit. based on the connection order information, the after correcting the respective radiation images, by combining the radiation ray image after correction to generate an image of the subject.

  As a result, an image (long image) of the subject with uniform image quality can be obtained.

  Here, each said radiation detection unit may further have a control part which controls the said radiation conversion panel.

  In this case, the radiation conversion panel, the radiation shielding member that blocks the transmission of the radiation, and the control unit may be sequentially arranged from the front surface to the back surface in each panel housing portion. .

  Thus, by arranging the control unit behind the radiation conversion panel via the radiation shielding member, it is possible to avoid a possibility that the control unit is irradiated with the radiation.

  Moreover, if the said control part is smaller than the said radiation conversion panel by planar view, a possibility that the said radiation will be irradiated to this control part can be prevented reliably.

  Alternatively, each of the radiation detection units has a rotation mechanism that can rotate the control unit with respect to the panel housing portion, and each of the control units is moved relative to the panel housing portion by the rotation mechanism. By rotating, at the time of irradiation of the radiation, they may be arranged so as not to overlap each of the panel housing portions.

  Thereby, irradiation of the radiation with respect to each control unit can be reliably avoided.

  In this case, the thickness of each control unit is such that the control unit is substantially flush with the imaging surface when the control unit is arranged so as not to overlap each panel housing unit by the rotation mechanism. If so, even when the subject touches the control unit at the time of shooting, there is no sense of incongruity.

  Moreover, each said control part may be arrange | positioned in places other than the said imaging | photography area | region on the said surface. Even in this case, irradiation of the radiation to the control units can be avoided.

  That is, when the radiation is performed in a state where the control unit is arranged in each imaging region or the imaging surface, the control unit deteriorates due to the radiation, or the control unit adds to the radiographic image. There is an inconvenience of being reflected. Therefore, according to each configuration of the present invention described above, it is possible to prevent the occurrence of these disadvantages by avoiding the irradiation of the radiation to the respective control units.

  Moreover, the said radiographic imaging apparatus may further have a connection part which connects between each said panel accommodating part connected by the said connection part.

  In this case, the connection by the connection part includes mechanical connection, electrical connection, optical connection (optical coupling), or magnetic coupling. If the panel housing portions are mechanically connected, the panel housing portions can be reliably coupled. Further, if the electrical connection, the optical connection, or the magnetic coupling is used, signals can be transmitted and received between the panel housing units.

  In the radiographic imaging apparatus described above, each of the radiation conversion panels includes a scintillator that converts the radiation into visible light, a solid state detection element that converts the visible light into an electrical signal indicating the radiation image, and the solid state detection. In a radiation conversion panel that includes a switching element that reads out the electrical signal from an element, and a substrate on which the solid-state detection element and the switching element are formed, and is disposed at least on the radiation irradiation side, the substrate is acceptable. It is a plastic substrate having flexibility, and it is preferable that the solid-state detection element is made of an organic photoconductor, and the switching element is made of an organic semiconductor material.

  Accordingly, at least in the radiation conversion panel disposed on the radiation irradiation side, the solid-state detection element and the switching element can be formed at a low temperature on the substrate, and the radiation conversion panel and It is possible to reduce the thickness and weight of the panel housing portion that houses the radiation conversion panel. As a result, it is possible to reduce the level difference at the connection location when a plurality of panel housing portions are connected. In addition, since plastic and organic materials hardly absorb the radiation, it is possible to cause a radiation of a large dose to reach the radiation conversion panel on the distal side along the irradiation direction of the radiation.

  In addition, if all the radiation conversion panels use the above-mentioned plastic and organic materials, since any radiation detection unit will become thin, of course, it will become difficult to produce the level | step difference in a connection location.

  In this case, if the scintillator composed of the substrate, the switching element, the solid state detection element, and the CsI is arranged in this order along the radiation direction of the radiation, a high-quality radiation image and one long image are obtained. Can be obtained. In addition, usability is improved when an expensive electronic cassette (radiation detection unit) is used alone.

  According to the present invention, it is possible to perform long imaging by connecting a plurality of radiation detection units without generating a step at the connection location. That is, even if the radiation detection units are sequentially connected, it is possible to avoid an increase in the size of the radiation image capturing apparatus and to ensure that the capturing surface is flat.

It is a block diagram of the radiographic imaging system which concerns on 1st Embodiment. It is a perspective view of the radiographic imaging apparatus of FIG. It is a top view of the radiographic imaging apparatus of FIG. It is a side view which shows typically the radiographic imaging apparatus of FIG. 5A is a perspective view of one radiation detection unit, and FIG. 5B is a perspective view of another radiation detection unit different from the radiation detection unit of FIG. 5A. 6A is a perspective view showing a state where two blocks are separated from the radiation detection unit of FIG. 5A, and FIG. 6B is a perspective view showing a state where two blocks are separated from the radiation detection unit of FIG. 5B. is there. FIG. 7A is a perspective view showing a state in which the radiation detection unit of FIG. 6A and the radiation detection unit of FIG. 6B are connected, and FIG. 7B is a cross-sectional view showing a state of a connection portion of two radiation detection units. . It is the top view which fractured | ruptured and illustrated some radiation detection units of FIG. It is sectional drawing along the IX-IX line of FIG. It is sectional drawing along the XX line of FIG. It is sectional drawing which shows the inside of the radiation detection unit of FIG. 6B. It is sectional drawing which shows the inside of the radiation detection unit of FIG. 6B. It is explanatory drawing which shows typically the arrangement | sequence of the pixel in a radiation conversion panel, and the electrical connection between a pixel and a cassette control part. It is a block diagram of a panel accommodating part. It is a block diagram of a control part. It is a detailed block diagram of the radiographic imaging system of FIG. It is a flowchart for demonstrating long imaging using the radiographic imaging apparatus of FIG. It is a flowchart for demonstrating the detail of the process of step S2 of FIG. 19A and 19B are explanatory views showing other connections between the radiation detection units. It is sectional drawing which shows the other connection method between two panel accommodating parts. It is a perspective view which shows the state of the charge process with respect to the radiation detection unit of FIG. 22A and 22B are cross-sectional views showing a state in which one scintillator is housed in a housing. 23A and 23B are cross-sectional views showing a state in which two scintillators are housed in a housing. It is a block diagram of the radiographic imaging system which concerns on 2nd and 3rd embodiment. 25A is a perspective view of one radiation detection unit, and FIG. 25B is a perspective view of another radiation detection unit different from the radiation detection unit of FIG. 25A. 26A is a perspective view showing a state in which two blocks are rotated with respect to the radiation detection unit of FIG. 25A, and FIG. 26B is a diagram in which two blocks are rotated with respect to the radiation detection unit of FIG. 25B. It is a perspective view which shows a state. It is a perspective view of the radiographic imaging apparatus of FIG. 28A and 28B are perspective views of one radiation detection unit used in the radiation image capturing system according to the third embodiment. FIG. 29A is a perspective view showing a state in which four blocks are rotated with respect to one radiation detection unit, and FIG. 29B shows another radiation detection unit different from the radiation detection unit of FIG. 29A. It is a perspective view which shows the state which rotated four blocks. It is a perspective view of another radiographic imaging device. It is a side view which shows typically another radiographic imaging apparatus. It is a figure which shows roughly the structure for 3 pixels of the radiation detector which concerns on a modification. FIG. 33 is a schematic configuration diagram of a TFT and a charge storage section shown in FIG. 32.

  A preferred embodiment of a radiographic imaging apparatus and a radiographic imaging system according to the present invention will be described below in detail with reference to FIGS.

  First, a radiographic imaging system 10A according to the first embodiment will be described with reference to FIGS. 1 to 23B.

  As shown in FIG. 1, a radiographic imaging system 10A includes a radiation irradiating device 18 that irradiates a subject 16 such as a patient lying on an imaging platform 12 such as a bed with radiation 16 having a dose according to imaging conditions. The radiation image capturing device 20A that detects the radiation 16 that has passed through the subject 14 and converts it into a radiation image, the console (control device) 22 that controls the radiation irradiation device 18 and the radiation image capturing device 20A, and the radiation image are displayed. And a display device 24.

  Between the console 22, the radiation irradiation device 18, the radiation image capturing device 20A, and the display device 24, for example, UWB (Ultra Wide Band), IEEE802.11. Signals are transmitted and received by wireless communication using a wireless LAN (Local Area Network) such as a / g / n or millimeter waves. It goes without saying that signals may be transmitted and received by wired communication using a cable.

  The console 22 is connected to a radiology information system (RIS) 26 for comprehensively managing radiographic images and other information handled in the radiology department in the hospital, and the RIS 26 has medical information in the hospital. Is connected to a medical information system (HIS) 28 for overall management.

  The radiographic image capturing apparatus 20A is disposed between the imaging table 12 and the subject 14, and includes three radiation detection units 30a to 30c and two electrical and mechanical connections between the radiation detection units 30a to 30c. And a connector (connection portion) 32.

  As shown in FIGS. 1 to 7A, the radiation detection units 30a to 30c have two radiation detection units 30a and 30c having the same shape and the same thickness, and have the same shape as the radiation detection units 30a and 30c. By providing two types of electronic cassettes with one radiation detection unit 30b having a thickness, alternately connecting different types of electronic cassettes along one row, and electrically and mechanically connecting them by two connectors 32 One radiographic image capturing apparatus 20A is configured.

  Here, each radiation detection unit 30a-30c is demonstrated in detail.

  The radiation detection units 30a to 30c have substantially rectangular casings (panel housing portions) 34a to 34c, respectively (see FIGS. 5A and 5B). The casings 34a to 34c are capable of transmitting the radiation 16 and contain radiation conversion panels 172a to 172c capable of converting the radiation 16 into a radiation image (see FIG. 4). And the panel parts 198a-198c are comprised by components other than the below-mentioned control parts 196a-196c (refer FIGS. 9-11) in the housing | casing 34a-34c.

  Guide lines 38a to 38c indicating the shooting positions of the subject 14 are formed on the surfaces 36a to 36c of the casings 34a to 34c, respectively. The outer frames of the guide lines 38a to 38c become imaging regions 40a to 40c indicating the irradiation field (irradiation range) of the radiation 16 on the surfaces 36a to 36c. The center positions of the guide lines 38a to 38c (intersection points of the two guide lines 38a to 38c intersecting in a cross shape) are the center positions of the imaging areas 40a to 40c.

  In these radiation detection units 30a to 30c, guide lines and imaging regions are not provided on the back surfaces 42a to 42c facing the front surfaces 36a to 36c. That is, the radiation detection units 30a to 30c are electronic cassettes that are capable of converting the radiation 16 into a radiation image by being irradiated with the radiation 16 only from the outside to the surfaces 36a to 36c.

  2 and 3, even if the radiation detection units 30a to 30c are connected, the guide lines 38a to 38c do not overlap, while the radiation conversion panels 172a to 172 accommodated in the casings 34a to 34c. 172c partially overlaps (see FIG. 4).

Further, the surfaces 36a to 36c have substantially the same area as each other, and the irradiation field of the radiation 16 is originally substantially the same size. However, the housing 34a, 34c of the side portions of the rear surface 42a, 42c side blocks 58a, 58c, 60a, housing 34a as 60c, separated from each 34c, to form stepped portions 120a, 120c, and 122a, 122 c (See FIG. 6A) and the side surface 36b side of the housing 34b can be separated from the housing 34b as blocks 58b and 60b to form stepped portions 120b and 122b (see FIG. 6). 6B), at the time of photographing, the area of the surface 36b (second irradiation surface) is smaller than the areas of the surfaces 36a and 36c (first irradiation surface). Accordingly, the guide line 38b and the imaging region 40b are displayed only in the region that is not separated from the housing 34b in the surface 36b.

  That is, in each case 34a, 34c (first panel housing portion), the surfaces close to (connected) to the stepped portions 120a, 120c, 122a, 122c are the back surfaces 42a, 42c, while the back surfaces 42a, 42c The surfaces that face each other and are separated from the stepped portions 120a, 120c, 122a, and 122c are the surfaces 36a and 36c (irradiated surfaces 148a and 148c). On the other hand, in the housing 34b (second panel housing portion), the surface close to (connected to) the stepped portions 120b and 122b is the surface 36b (irradiated surface 148b), while facing the surface 36b and the stepped portion 120b. , 122b is a back surface 42b.

  Furthermore, in the casings 34a to 34c, the outer peripheral portions of the front surfaces 36a to 36c and the outer peripheral portions of the rear surfaces 42a to 42c are connected by four side surfaces 50a to 50c, 52a to 52c, 54a to 54c, and 56a to 56c, respectively. Has been. In this case, blocks 58a to 58c that are separable from the casings 34a to 34c are respectively provided on the side surfaces 54a to 54c of the casings 34a to 34c, and on the side surfaces 56a to 56c that face the side surfaces 54a to 54c. Are provided with blocks 60a to 60c that are separable from the casings 34a to 34c, respectively. In addition, the full length of these blocks 58a-58c and 60a-60c is set to the distance between the side surfaces 50a-50c and the side surfaces 52a-52c facing the side surfaces 50a-50c.

  Concave portions 70a to 70c are respectively provided on the side surfaces 50a to 50c of the blocks 58a to 58c, and manual operation portions 72a to 72c are disposed in the concave portions 70a to 70c. Further, concave portions 74a to 74c having the same shape as the concave portions 70a to 70b are respectively provided on the side surfaces 52a to 52c of the blocks 58a to 58c, and manual operation portions 76a to 76c are disposed in the concave portions 74a to 74c, respectively. On the other hand, the blocks 60a to 60c are also provided with recesses 78a to 78c and 82a to 82c so as to face the recesses 70a to 70c and 74a to 74c, respectively. 80c and 84a to 84c are arranged.

  On the housings 34a to 34c side of the blocks 58a to 58c, claw members 90a to 90c connected to the manual operation portions 72a to 72c are respectively disposed through the holes 92a to 92c, and the housings 34a to 34c. Hole portions 94a to 94c that can be engaged with the claw members 90a to 90c are formed at positions facing the hole portions 92a to 92c (see FIGS. 6A and 6B). Similarly to the above-described claw members 90a to 90c, claw members 96a to 96c connected to the manual operation portions 76a to 76c pass through the holes 98a to 98c on the housings 34a to 34c side of the blocks 58a to 58c. Thus, holes 100a to 100c that can be engaged with the claw members 96a to 96c are formed at locations facing the holes 98a to 98c in the casings 34a to 34c, respectively.

  Also on the housings 34a to 34c side of the blocks 60a to 60c, like the above-described claw members 90a to 90c, the claw members 102a to 102c connected to the manual operation units 80a to 80c pass through the holes 104a to 104c. Hole portions 106a to 106c that can be engaged with the claw members 102a to 102c are formed at locations that are respectively disposed and face the hole portions 104a to 104c in the casings 34a to 34c. Similarly to the above-described claw members 96a to 96c, claw members 108a to 108c connected to the manual operation units 84a to 84c pass through the holes 110a to 110c on the housings 34a to 34c side of the blocks 60a to 60c. Thus, holes 112a to 112c that can be engaged with the claw members 108a to 108c are formed at locations of the casings 34a to 34c facing the holes 110a to 110c, respectively.

  Therefore, when the doctor or engineer displaces the manual operation units 72a to 72c and 76a to 76c in the directions close to each other in the state shown in FIGS. 5A and 5B, the nail interlocked with the manual operation units 72a to 72c and 76a to 76c. The members 90a to 90c and 96a to 96c move, and as a result, the engagement state between the claw members 90a to 90c and 96a to 96c and the holes 94a to 94c and 100a to 100c is released, and the housings 34a to 34c are released. Blocks 58a-58c can be separated (see FIGS. 6A and 6B). Further, when the doctor or engineer displaces the manual operation units 80a to 80c and 84a to 84c in directions close to each other, the claw members 102a to 102c and 108a to 108c interlocked with the manual operation units 80a to 80c and 84a to 84c are provided. As a result, the claw members 102a to 102c, 108a to 108c are disengaged from the holes 106a to 106c and 112a to 112c, and the blocks 60a to 60c are separated from the casings 34a to 34c. it can.

  By separating the blocks 58a to 58c and 60a to 60c from the housings 34a to 34c, the side surfaces 54a to 54c and 56a to 56c of the housings 34a to 34c have stepped portions (connecting portions) 120a to 120c, 122a to 122c are respectively formed, and the irradiation surface 148b (the imaging region thereof) having a smaller area than the irradiation surfaces 148a and 148c (imaging regions 40a and 40c thereof) of the housings 34a and 34c is formed on the surface 36b of the housing 34b. 40b) is formed.

  Concave portions 370a and 370c are respectively formed in the stepped portions 120a and 120c along the longitudinal direction of the blocks 58a and 58c. Convex portions 372a and 372c that can be fitted into the concave portions 370a and 370c are respectively formed in the blocks 58a and 58c. Is formed. On the other hand, in the stepped portions 122a and 122c, concave portions 374a and 374c having the same shape as the concave portions 370a and 370c are formed along the longitudinal direction of the blocks 60a and 60c, respectively, and the concave portions 374a and 374c are formed in the blocks 60a and 60c, respectively. Protrusions 376a and 376c that can be fitted are formed.

  Further, the step portion 120b is formed with a convex portion 378b having the same shape as the convex portions 376a and 376c along the longitudinal direction of the block 58b, and the block 58b is formed with a concave portion 380b that can be fitted to the convex portion 378b. Has been. On the other hand, convex portions 382b having the same shape as the convex portions 376a and 376c are formed in the stepped portion 122b along the longitudinal direction of the block 60b, and a concave portion 384c that can be fitted to the convex portion 382b is formed in the block 60b. Has been.

  Connection terminals 124a to 124c that can be fitted to the connector 32 are disposed at the positions on the side of the step portions 120a to 120c on the side surfaces 50a to 50c, respectively. In addition, connection terminals 126a to 126c having the same shape as the connection terminals 124a to 124c are also disposed at the positions on the side of the stepped portions 122a to 122c on the side surfaces 50a to 50c.

  Further, concave portions 130a to 130c are formed in the central portions of the side surfaces 50a to 50c, respectively, and handle portions 132a to 132c are disposed in the concave portions 130a to 130c. Shaft portions 134a to 134c that enter the housings 34a to 34c are provided at one end portions of the handle portions 132a to 132c, and shaft portions 136a to 136c that are coaxial with the shaft portions 134a to 134c are also provided at the other end portions. It is provided in a state of entering the bodies 34a to 34c (see FIG. 5A). Therefore, a doctor or an engineer can grip the handle portions 132a to 132c by rotating the handle portions 132a to 132c around the shaft portions 134a to 134c, 136a to 136c.

  In addition, concave portions 140a to 140c and handle portions 142a to 142c having the same shapes as the concave portions 130a to 130c and the handle portions 132a to 132c described above are also provided in the central portions of the side surfaces 52a to 52c, respectively. Shaft portions 144a to 144c that enter the housings 34a to 34c are provided at one end, and shaft portions 146a to 146c that are coaxial with the shaft portions 144a to 144c are also provided in the housings 34a to 34c at the other end portion. It is provided in an approached state (see FIG. 5B).

  Therefore, the doctor or engineer can grip the handle portions 142a to 142c by rotating the handle portions 142a to 142c around the shaft portions 144a to 144c and 146a to 146c. Accordingly, the doctor or engineer can also carry the radiation detection units 30a to 30c while holding the handle portions 132a to 132c and 142a to 142c.

  Here, when three radiation detection units 30a to 30c are connected to constitute one radiation image capturing apparatus 20A, a doctor or an engineer performs assembly work of the radiation image capturing apparatus 20A as follows.

  First, the blocks 58a to 58c and 60a to 60c are separated from the casings 34a to 34c to form stepped portions 120a to 120c and 122a to 122c (see FIGS. 6A and 6B). In this state, the doctor or engineer fits the stepped portion 122a of the housing 34a and the stepped portion 120b of the housing 34b, and fits the stepped portion 122b of the housing 34b and the stepped portion 120c of the housing 34c. (See FIGS. 7A and 7B).

  In this case, by fitting the concave portion 374a on the housing 34a side and the convex portion 378b on the housing 34b side, the stepped portion 122a and the stepped portion 120b are securely fitted without any gaps while being positioned with respect to each other. The Further, by fitting the convex portion 382b on the housing 34b side and the concave portion 370c on the housing 34c side, the stepped portion 122b and the stepped portion 120c are securely fitted with no gap in a state of being positioned with respect to each other. .

  Next, the doctor or engineer fits the substantially U-shaped connector 32 to the connection terminals 126a and 124b on the stepped portions 122a and 120b, and also connects the other connection terminals 126b and 124c on the stepped portions 122b and 120c. The connector 32 is fitted.

  By assembling in this way, in the radiographic imaging apparatus 20A, different types of electronic cassettes are arranged in the order of the radiation detection unit 30a → the radiation detection unit 30b → the radiation detection unit 30c from the left side to the right side of FIGS. Alternately connected. Therefore, the upper surface of the radiographic imaging device 20A is in the order of the surface 36a (first irradiation surface) → the surface 36b (second irradiation surface) → the surface 36c (first irradiation surface), and irradiation surfaces having different areas are arranged. They are connected alternately along one direction.

  Further, as described above, since the casings 34a to 34c have the same thickness, when the radiation image capturing device 20A is configured by connecting the radiation detection units 30a to 30c, the connecting portions of the casings 34a to 34c are connected. The thickness of the radiographic imaging device 20A is generated without generating a step at the fitting positions of the stepped portions 122a and 120b and the fitting locations of the stepped portions 122b and 120c on the upper surface of the radiographic imaging device 20A. Can be made to have the same thickness as each of the radiation detection units 30a to 30c, and the upper surface of the radiographic image capturing apparatus 20A can be substantially planar (see FIGS. 1 to 4).

  Furthermore, when the radiation 16 is irradiated on the upper surface of the radiographic imaging apparatus 20A on which the subject 14 is lying (see FIGS. 1 and 2), the surfaces 36a to 36c become irradiation surfaces 148a to 148c to which the radiation 16 is irradiated. At the same time, an irradiation range of the radiation 16 (an irradiation field including the imaging regions 40a to 40c) is configured as an imaging surface (imaging region) 156 of the radiographic image capturing device 20A.

  As shown in FIG. 4, scintillators 150 a to 150 c and photoelectric conversion layers 152 a to 152 c are provided in wide portions where the stepped portions 120 a to 120 c and 122 a to 122 c are not formed inside the casings 34 a to 34 c, In addition, radiation conversion panels 172a to 172c that convert the radiation 16 into a radiation image are accommodated. In this case, in each case 34a, 34b, a part of the radiation conversion panel 172b on the radiation conversion panel 172b side and a part of the radiation conversion panel 172b on the radiation conversion panel 172a side overlap (in plan view). The step portion 122a and the step portion 120b are fitted, and the concave portion 374a and the convex portion 378b are fitted. Also, in each of the cases 34b and 34c, a part of the radiation conversion panel 172c side of the radiation conversion panel 172b and a part of the radiation conversion panel 172c on the side of the radiation conversion panel 172b are overlapped (in a plan view). The step portion 122b and the step portion 120c are fitted, and the concave portion 370c and the convex portion 382b are fitted.

  Further, when each of the radiation detection units 30a to 30c is used alone as one electronic cassette, the radiation regions 16 are irradiated to the imaging regions 40a to 40c. On the other hand, in the radiographic imaging apparatus 20A configured by sequentially connecting the radiation detection units 30a to 30c, as described above, the radiation 16 is applied to the imaging surface 156 including these imaging areas 40a to 40c. Is done. As shown in FIG. 8, the imaging regions 40a and 40c substantially coincide with the scintillators 150a and 150c (and the photoelectric conversion layers 152a and 152c) in plan view.

  As shown in FIGS. 2, 5A, and 6A to 7A, side surfaces 50a to 50c include AC adapter input terminals 160a to 160c for charging the radiation detection units 30a to 30c from an external power source. USB (Universal Serial Bus) terminals 162a to 162c as interface means capable of transmitting and receiving information to and from external devices, card slots 166a to 166c for loading memory cards 164 such as PC cards, and radiation detection Power switches 168a to 168c for starting the units 30a to 30c are provided, respectively.

  As shown in FIGS. 8 to 10, in the radiation detection units 30a and 30c, the batteries that supply power to the respective parts in the radiation detection units 30a and 30c to the narrow back surfaces 42a and 42c in the casings 34a and 34c. And the like, and the console 22 can wirelessly transmit and receive signals between the power supply units 190a and 190c and the cassette control units 192a and 192c for controlling the radiation conversion panels 172a and 172c. Communication units 194a and 194c capable of transmitting and receiving signals to and from the radiation detection unit are arranged. The power supply units 190a to 190c, the cassette control units 192a to 192c, and the communication units 194a to 194c constitute control units 196a and 196c.

  In addition, radiation shielding members 400a and 400c such as lead plates that block the transmission of radiation 16 are arranged above the control units 196a and 196c in contact with the radiation conversion panels 172a and 172c. Radiation conversion panels 172a and 172c and impact absorbing members 174a and 174c are sequentially stacked from the radiation shielding members 400a and 400c toward the surfaces 36a and 36c. Note that the control units 196a and 196c described above are smaller than the radiation shielding members 400a and 400c (in plan view).

  When a load is applied from the subject 14 to the surfaces 36a and 36c, the shock absorbing members 174a and 174c absorb (relax) the shock caused by the load.

  In the radiation conversion panels 172a to 172c, light transmissive and radiation transmissive substrates 178a and 178c such as glass substrates and transparent electrodes are formed from the radiation shielding members 400a and 400c toward the shock absorbing members 174a and 174c. The transparent TFT layers 176a and 176c, the photoelectric conversion layers 152a and 152c, and the scintillators 150a and 150c are stacked in this order.

  The scintillators 150a and 150c once convert the radiation 16 irradiated from the surfaces 36a and 36c through the shock absorbing members 174a and 174c into visible light.

  The scintillators 150a and 150c are made of, for example, cesium iodide (CsI) or gadolinium oxide sulfide (GOS). In addition, when performing long imaging with respect to the subject 14 using the radiographic imaging device 20A, a scintillator 150a of a radiation detection unit that captures a specific site to be noted among long imaging sites (the entire body of the subject 14), 150c may be composed of CsI, and the scintillators 150a and 150c of other radiation detection units may be composed of GOS.

  The photoelectric conversion layers 152a and 152c use the solid detection elements (hereinafter referred to as pixels) 200a and 200c (see FIG. 13) made of a substance such as amorphous silicon (a-Si) to convert the visible light into an electric signal that is a signal charge. Convert to signal.

  The TFT layers 176a and 176c are thin film transistors (TFTs) in which signal lines 204a and 204c or signal lines 206a and 206c (see FIG. 14) are connected to one signal electrode, and gate lines 202a and 202c are connected to gate electrodes. 210a and 210c are arranged in a matrix and can transmit the radiation 16 and the visible light.

  Further, as shown in FIGS. 11 and 12, in the radiation detection unit 30b, a power supply unit 190b such as a battery that supplies power to each part in the radiation detection unit 30b on the wide back surface 42b side in the housing 34b; The console control unit 192b for controlling the radiation conversion panel 172b and the console 22 can transmit and receive signals wirelessly, and can also transmit and receive signals to and from other radiation detection units via the connector 32. The communication unit 194b is arranged. Even in this case, the power supply unit 190b, the cassette control unit 192b, and the communication unit 194b constitute the control unit 196b.

  In addition, a radiation shielding member 400b such as a lead plate that blocks transmission of the radiation 16 is disposed above the control unit 196b in contact with the radiation conversion panel 172b. A radiation conversion panel 172b and an impact absorbing member 174b are sequentially stacked from the radiation shielding member 400b toward the surface 36b. The control unit 196b described above is smaller than the radiation shielding member 400b (in plan view).

  The shock absorbing member 174b is a thick member disposed on the narrow surface 36b side inside the housing 34b. When a load is applied from the subject 14 to the surface 36b, the shock due to the load is applied. Is absorbed (relaxed).

  The radiation conversion panel 172b includes a light transmissive TFT layer 176b on which a light transmissive and radiation transmissive substrate 178b such as a glass substrate, a transparent electrode, and the like are formed from the radiation shielding member 400b toward the shock absorbing member 174b. The photoelectric conversion layer 152b and the scintillator 150b are stacked in this order.

  The scintillator 150b has the same function as the scintillators 150a and 150c. Therefore, the scintillator 150b may also be composed of CsI or GOS. Further, if a specific part to be noticed is photographed, the scintillator 150b may be made of CsI. The photoelectric conversion layer 152b has the same function as the photoelectric conversion layers 152a and 152c, and the TFT layer 176b has the same function as the TFT layers 176a and 176c.

  As described above, the radiation 16 transmitted through the subject 14 is temporarily converted into visible light by a scintillator, and the converted visible light is converted into an electrical signal by a solid-state detection element (pixel) (radiation detection panel). There are a surface reading type radiation detector and a back side reading type radiation detector. Among these, a radiation detector of an ISS (Irradiation Side Sampling) method that is a surface reading method has a configuration in which a solid detection element and a scintillator are sequentially arranged along the irradiation direction of the radiation 16. In addition, a PSS (Penetration Side Sampling) type radiation detector which is a back side reading system has a configuration in which a scintillator and a solid state detection element are sequentially arranged along the irradiation direction of the radiation 16.

  The indirect conversion type radiation conversion panels 172a to 172c shown in FIGS. 8 to 12 sequentially arrange scintillators 150a to 150c and photoelectric conversion layers 152a to 152c using pixels 200a to 200c with respect to the surfaces 36a to 36b. It is configured as a PSS radiation detector.

  8 to 12 show indirect conversion type radiation conversion panels 172a to 172c, the dose of the radiation 16 is converted into an electric signal by a solid-state detection element made of a substance such as amorphous selenium (a-Se). It is also possible to employ a direct conversion type radiation conversion panel for direct conversion.

  The substrates 178a to 178c are larger than other members constituting the radiation conversion panels 172a to 172c (in plan view) (see FIGS. 8 to 12), and the side surfaces 50a to 50c of the substrates 178a to 178c are exposed to radiation. Drive circuit units 182a to 182c for driving the conversion panels 172a to 172c are arranged, and on the side surfaces 54a to 54c side of the substrates 178a to 178c, a read circuit unit 184a for reading electric signals from the radiation conversion panels 172a to 172c. To 184c, and read circuit portions 186a to 186c for reading out electrical signals are arranged on the side surfaces 56a to 56c of the substrates 178a to 178c. The radiation conversion panels 172a to 172c, the drive circuit units 182a to 182c, and the readout circuit units 184a to 184c and 186a to 186c constitute panel units 198a to 198c that convert the radiation 16 into a radiation image and output it.

  The cassette control units 192a to 192c described above control the radiation conversion panels 172a to 172c via the drive circuit units 182a to 182c and the read circuit units 184a to 184c and 186a to 186c. Further, as described above, the control units 196a to 196c are arranged in regions other than the panel units 198a to 198c to which the radiation 16 is irradiated by blocking the transmission of the radiation 16 by the radiation shielding members 400a to 400c. It will be.

  As schematically shown in FIG. 13, in each of the radiation detection units 30 a to 30 c, in the radiation conversion panels 172 a to 172 c, as described above, a large number of pixels 200 a to 200 c include TFT layers 176 a to 176 c (FIG. 9 to FIG. 9). 12) and a plurality of gate lines 202a to 202c for supplying control signals from the drive circuit units 182a to 182c to the pixels 200a to 200c, and a plurality of pixels. The electrical signals (signal charges) output from the signals 200a to 200c are read and output to the read circuit units 184a to 184c, and the electrical signals output from the pixels 200a to 200c are read and read. A large number of signal lines 206a to 206c output to the circuit units 186a to 186c are arranged. To have.

  From the upper side to the lower side of FIG. 13, the electric signals of the odd-numbered pixels 200a to 200c are output to the readout circuit portions 184a to 184c via the signal lines 204a to 204c, while the even-numbered pixels 200a. The electric signals of .about.200c are output to the reading circuit portions 186a to 186c through the signal lines 206a to 206c.

  Next, a circuit configuration and a block diagram of the radiographic image capturing apparatus 20A will be described in detail with reference to FIGS.

  The radiation conversion panels 172a to 172c are a matrix of photoelectric conversion layers 152a to 152c (see FIGS. 9 to 12) in which the respective pixels 200a to 200b made of a material such as a-Si that converts visible light into electric signals are formed. The TFTs 210a to 210c are arranged on an array. In this case, in each of the pixels 200a to 200c to which a bias voltage is supplied from the bias circuit 214 that configures the drive circuit units 182a to 182c, charges generated by converting visible light into an electric signal (analog signal) are accumulated. The charges can be read out as an image signal by sequentially turning on the TFTs 210a to 210c for each column.

  Among the TFTs 210a to 210c connected to the pixels 200a to 200c, the TFTs 210a to 210c arranged in odd rows from the top to the bottom in FIG. 14 include gate lines 202a to 202c extending in parallel to the column direction and rows It is connected to signal lines 204a to 204c extending in parallel with the direction. The TFTs 210a to 210c arranged in even rows are connected to the gate lines 202a to 202c and signal lines 206a to 206c extending in parallel to the row direction.

  In this case, each of the gate lines 202a to 202c is connected to the gate drive circuit 212, and a control signal for controlling on / off of the TFTs 210a to 210c arranged in the column direction is supplied from the gate drive circuit 212 to the gate lines 202a to 202c. The In this case, the gate drive circuit 212 is supplied with an address signal from the cassette control units 192a to 192c.

  The charges held in the pixels 200a to 200c flow out to the signal lines 204a to 204c and 206a to 206c through the TFTs 210a to 210c arranged in the row direction. The electric charges are amplified by the amplifiers 220a to 220c and 230a to 230c, respectively. Multiplexers 223a to 223c and 233a to 233c are connected to the amplifiers 220a to 220c and 230a to 230c via sample hold circuits 222a to 222c and 232a to 232c, respectively. The multiplexers 223a to 223c and 233a to 233c turn on the FET (field effect transistor) switches 224a to 224c and 234a to 234c for switching the signal lines 204a to 204c and 206a to 206c, and one FET switch 224a to 224c, 234a to 234c. Multiplexer driving circuits 226a to 226c and 236a to 236c for outputting selection signals to be respectively provided. Address signals are supplied from the cassette control units 192a to 192c (see FIGS. 11 and 13) to the multiplexer driving circuits 226a to 226c and 236a to 236c. A / D converters 228a to 228c and 238a to 238c are connected to the FET switches 224a to 224c and 234a to 234c, and radiation images converted into digital signals by the A / D converters 228a to 228c and 238a to 238c It is supplied to the cassette control units 192a to 192c.

  Note that the TFTs 210a to 210c functioning as switching elements may be realized in combination with another imaging element such as a CMOS (Complementary Metal-Oxide Semiconductor) image sensor. Furthermore, it can be replaced with a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting them with a shift pulse corresponding to a gate signal referred to as a TFT.

  As shown in FIG. 15, the cassette control units 192a to 192c include image memories 240a to 240c, address signal generation units 242a to 242c, cassette ID memories 244a to 244c, synchronization control units 248a to 248c, and connection order information. Generators 250a to 250c.

  The image memories 240a to 240c store the radiation images detected by the radiation conversion panels 172a to 172c.

  The address signal generators 242a to 242c supply address signals to the gate driving circuit 212 and the multiplexer driving circuits 226a to 226c and 236a to 236c. The cassette ID memories 244a to 244c store cassette ID information for specifying the radiation detection units 30a to 30c.

  The synchronization control units 248a to 248c transmit and receive synchronization control signals to and from other radiation detection units via the communication units 194a to 194c and the connector 32, so that each of the radiation detection units 30a to 30c at the time of imaging is transmitted. Take synchronization. Specifically, when the radiation 16 is irradiated from the radiation irradiation device 18 to the imaging surface 156 via the subject 14 at the timing indicated by the synchronization control signal, the synchronization control units 248a to 248c convert the radiation before the timing. The radiation conversion panels 172a to 172c are controlled so that charges can be accumulated in the pixels 200a to 200c of the panels 172a to 172c.

  The connection order information generation units 250a to 250c transmit and receive cassette ID information to and from the adjacent radiation detection units via the communication units 194a to 194c and the connector 32, whereby each radiation detection unit in the radiographic imaging apparatus 20A. The connection order of 30a to 30c is specified (detected), and connection order information indicating the specified connection order and the cassette ID information of each radiation detection unit in the connection order is generated.

  As shown in FIG. 16, the console 22 includes a communication unit 280, a control unit 282, an imaging condition setting unit 284, an ID memory 286, an image processing unit 288, an image memory 290, a synchronization processing unit 292, a connection order information management unit 294, It has a SID (distance between source image reception) management unit 296 and an operation unit 298. In FIG. 16, the radiographic image capturing apparatus 20A is schematically illustrated.

  The communication unit 280 transmits and receives signals to and from the radiographic image capturing device 20A, the display device 24, the RIS 26, and the HIS 28. The control unit 282 controls the console 22 as a whole.

  In this case, the control unit 282 stores the imaging order information acquired from the RIS 26 in the imaging condition setting unit 284. Further, the control unit 282 stores in the imaging condition setting unit 284 long imaging conditions for the subject 14 acquired from the RIS 26 or set by the doctor or engineer by operating the operation unit 298 such as a keyboard or a mouse. .

  Note that the order information is created by a doctor using the RIS 26, and in addition to subject information for specifying the subject 14, such as the name, age, and sex of the subject 14, a photographing device used for photographing, photographing The site and imaging conditions are included. The imaging conditions are conditions for determining the amount of radiation irradiated to the subject 14 such as, for example, the tube voltage of the radiation source 264 constituting the radiation irradiation apparatus 18, the tube current, the irradiation time of the radiation 16, and the like.

  The ID memory 286 stores cassette ID information of each of the radiation detection units 30a to 30c. The synchronization processing unit 292 generates a synchronization control signal and transmits the synchronization control signal to the radiation irradiation device 18 and the radiation image capturing device 20A via the communication unit 280. The connection order information management unit 294 stores (manages) the connection order information received from the radiographic image capturing apparatus 20A via the communication unit 280. The SID management unit 296 stores (manages) the distance (SID) between the radiation source 264 and the radiographic imaging device 20A (each of the radiation conversion panels 172a to 172c) based on the imaging conditions.

  The image processing unit 288 synthesizes the radiation images of the radiation detection units 30a to 30c received from the radiation image capturing apparatus 20A via the communication unit 280, and according to the long imaging part of the subject 14 after the image synthesis. The image memory (290) stores the image (long-length photographed image) and each radiographic image used for the image composition.

  As described above, the distances of the radiation conversion panels 172a to 172c with respect to the radiation source 264 are different from each other, and adjacent radiation conversion panels partially overlap each other. For this reason, even if image synthesis is performed in which the radiation images are sequentially connected in accordance with the connection order of the radiation detection units 30a to 30c, the resultant composite image may be an image whose image quality is not uniformized.

  Therefore, the image processing unit 288 first refers to the connection order information stored in the connection order information management unit 294 and the cassette ID information stored in the ID memory 286 to connect the radiation detection units 30a to 30c. While grasping the order, the SID management unit 296 is referred to, and the SID between the radiation source 264 and each of the radiation conversion panels 172a to 172c is specified.

  Next, in view of the fact that the attenuation rate of the radiation 16 differs according to the SID, the image processing unit 288 performs an image correction process considering the attenuation rate of the radiation 16 on each radiation image, and then performs the connection. Image composition for sequentially connecting the radiation images is performed according to the order information. As described above, the guide lines of the adjacent housings do not overlap with each other, but the portions between the adjacent radiation conversion panels overlap with each other. However, by performing the above-described image correction processing in advance, it is possible to obtain a composite image (a long image of the subject 14 corresponding to the long image) with uniform image quality.

  The long captured image thus obtained and each radiographic image used for image composition are both stored in the image memory 290.

  The control unit 282 transmits the long captured image stored in the image memory 290 to the display device 24 via the communication unit 280, and the display device 24 displays the received long captured image.

  On the other hand, the radiation irradiation apparatus 18 includes a communication unit 260, a control unit 262, a radiation source 264, a collimator 266, an irradiation field lamp 268, a mirror 270, and an SID detection unit 276.

  The communication unit 260 transmits and receives signals to and from the communication unit 280. The control unit 262 controls each unit of the radiation irradiation apparatus 18 in accordance with an instruction from the console 22. When a synchronization control signal is transmitted from the console 22 to the control unit 262 via the communication units 280 and 260, the radiation source 264 outputs the radiation 16 at the timing indicated by the synchronization control signal. The collimator 266 controls the irradiation range of the radiation 16 by adjusting the diaphragm according to the control from the control unit 262.

  The irradiation field lamp 268 outputs irradiation light (not shown) before the radiation 16 is output from the radiation source 264. The irradiation light is reflected by the mirror 270 toward the collimator 266, passes through the collimator 266, and is projected onto the imaging surface 156.

In this case, if the distance between the radiation source 264 and each of the radiation conversion panels 172a to 172c is adjusted to SID, the projection range of the irradiation light (irradiation field of the radiation 16 ) on the upper surface of the radiation imaging apparatus 20A And the range of the imaging surface 156 (imaging areas 40a to 40c) substantially coincide with each other. Accordingly, the doctor or engineer adjusts the positional relationship between the radiographic imaging device 20A and the radiation irradiation device 18 so that the distance matches the SID.

  The SID detection unit 276 includes a distance measurement sensor using ultrasonic waves or infrared rays, and based on the time from when the transmission wave 272 is transmitted to the radiographic imaging device 20A until the reflected wave 274 is received, the radiation is detected. The distance between the source 264 and the radiographic imaging device 20A is detected. In this case, the control unit 282 of the console 22 transmits the SID stored in the SID management unit 296 to the control unit 262 of the radiation irradiation apparatus 18 via the communication units 280 and 260. Therefore, the SID detection unit 276 compares the distance between the radiation source 264 corresponding to the SID and the radiographic imaging device 20A with the distance detected by the SID detection unit 276, and when both match, The control unit 262 is notified of the result indicating that the distance between the radiation source 264 and each of the radiation conversion panels 172a to 172c is set to the SID. Thereby, the control unit 262 stops the output of the irradiation light from the irradiation field lamp 268.

  The radiographic imaging system 10A according to the first embodiment is basically configured as described above. Next, the operation thereof will be described with reference to the flowcharts of FIGS.

  In step S <b> 1, the communication unit 280 (see FIG. 16) of the console 22 acquires order information from the RIS 26. The acquired order information is stored in the imaging condition setting unit 284. The doctor or engineer operates the operation unit 298 of the console 22 to display the order information stored in the imaging condition setting unit 284 on the display device 24, and the doctor or engineer displays the order information displayed on the display device 24. While operating, the operation unit 298 is operated to input the cassette ID information of the radiation detection units 30a to 30c, and the imaging condition corresponding to the long imaging is selected. As a result, the selected photographing condition is set in the photographing condition setting unit 284, and the input cassette ID information is stored in the ID memory 286. The SID corresponding to the selected shooting condition is also stored in the SID management unit 296.

  In the next step S <b> 2, the doctor or engineer prepares for imaging for imaging a radiographic image of a long imaging region of the subject 14 (for example, the entire body of the subject 14).

  First, in step S21 of step S2, the doctor or engineer displaces the manual operation units 72a to 72c and 76a to 76c in the directions approaching each other for each of the radiation detection units 30a to 30c, thereby claw members 90a to 90c, 96a to 96a. By moving 96c, the engagement state between the claw members 90a to 90c and 96a to 96c and the holes 94a to 94c and 100a to 100c is released, and the blocks 58a to 58c are separated from the casings 34a to 34c. (See FIGS. 5A-6B).

  Further, the doctor or engineer moves the nail members 102a to 102c and 108a to 108c by displacing the manual operation units 80a to 80c and 84a to 84c toward each other, thereby moving the nail members 102a to 102c and 108a to 108a to 108c. 108c and the holes 106a to 106c and 112a to 112c are disengaged, and the blocks 60a to 60c are separated from the casings 34a to 34c.

  In step S22, the doctor or engineer sets the stepped portion 122a of the housing 34a and the stepped portion 120b of the housing 34b so that the concave portion 374a on the housing 34a side and the convex portion 378b on the housing 34b side are fitted. At the same time, the stepped portion 122b of the housing 34b and the stepped portion 120c of the housing 34c are fitted so that the convex portion 382b on the housing 34b side and the concave portion 370c on the housing 34c side are fitted (see FIG. FIG. 7A and FIG. 7B). As a result, the stepped portion 122a and the stepped portion 120b are connected without a gap in the positioned state, and the stepped portion 122b and the stepped portion 120c are also connected without a gap in the positioned state.

  Next, the doctor or technician fits the connector 32 to the connection terminals 126a and 124b on the stepped portions 122a and 120b, and fits another connector 32 to the connection terminals 126b and 124c on the stepped portions 122b and 120c. Let

  In this manner, the stepped portion 122a and the stepped portion 120b, and the stepped portion 122b and the stepped portion 120c are fitted so that the recessed portion 374a and the projected portion 378b, and the projected portion 382b and the recessed portion 370c are fitted, respectively. After the radiation detection units 30a to 30c are sequentially connected, the connector 32 is further fitted to the connection terminals 124b, 124c, 126a, and 126b, thereby generating a step at the connection location of the housings 34a to 34c. However, it is possible to configure one radiographic image capturing apparatus 20A in which the imaging surface 156 is substantially planar (see FIGS. 1 to 4).

  In step S23, the doctor or engineer lays the subject 14 on the imaging surface 156, and then turns on the power switches 168a to 168c. Thereby, the power supply from the power supply units 190a to 190c to the respective units of the radiation detection units 30a to 30c is started.

  In step S24, the connection order information generation units 250a to 250c transmit / receive the cassette ID information stored in the cassette ID memories 244a to 244c with the adjacent radiation detection units via the communication units 194a to 194c and the connector 32. To identify adjacent radiation detection units. Thereby, the connection order of each radiation detection unit 30a-30c which comprises 20 A of radiographic imaging apparatuses can be specified.

  In step S25, the connection order information generation units 250a to 250c generate connection order information indicating the specified connection order and the cassette ID information of the radiation detection units 30a to 30c in the connection order, and then generate the connection order information. The connected order information is transmitted to the console 22 via the communication units 194a to 194c (step S26). The connection order information management unit 294 (see FIG. 16) of the console 22 stores the connection order information received via the communication unit 280 and the control unit 282. In addition, since connection order information is information which shows the connection order etc. of radiation detection unit 30a-30c in 20 A of radiographic imaging apparatuses, among the three radiation detection units 30a-30c, the communication part 194a of one radiation detection unit. ˜194c may be transmitted to the console 22.

  In step S27, the control unit 282 confirms that the connection order information is stored in the connection order information management unit 294, and then stores the information in the SID management unit 296 for the radiation irradiation apparatus 18 via the communication unit 280. An SID and an instruction signal for instructing setting of an irradiation field are transmitted.

  When receiving the instruction signal and the SID via the communication unit 260, the control unit 262 of the radiation irradiation apparatus 18 controls the irradiation field by adjusting the aperture of the collimator 266 and drives the irradiation field lamp 268. As a result, the irradiation field lamp 268 starts to output the irradiation light. The irradiation light is reflected by the mirror 270 toward the collimator 266, passes through the collimator 266, and is projected onto the imaging surface 156.

  The doctor or engineer adjusts the position of the radiation irradiation device 18 with respect to the imaging surface 156 so that the irradiation range of the irradiation light according to the irradiation field of the radiation 16 matches the imaging surface 156.

  In addition, the control unit 262 outputs the SID to the SID detection unit 276 to drive the SID detection unit 276.

  The SID detection unit 276 transmits the transmission wave 272 to the imaging surface 156 and the distance between the radiation source 264 and the radiographic imaging device 20A based on the time from when the reflected wave 274 is received. Is detected, and it is determined whether or not the detected distance matches the distance according to the SID. If the distance detected by the SID detection unit 276 matches the distance corresponding to the SID because the projection range of the irradiated light and the imaging surface 156 match, the SID detection unit 276 matches both. This is notified to the control unit 262.

  In response to the notification from the SID detection unit 276, the control unit 262 stops driving the irradiation field lamp 268. Thereby, since the output of the irradiation light from the radiation irradiation apparatus 18 is stopped, the doctor or engineer immediately understands that the distance between the radiation source 264 and the radiation conversion panels 172a to 172c is set to the SID. be able to. Furthermore, the control unit 262 also notifies the console 22 via the communication unit 260 that the distance has been set to the SID.

  In step S3 of FIG. 17 after the preparation for imaging is completed in this way, the doctor or engineer turns on an exposure switch (not shown) provided in the operation unit 298 (see FIG. 16).

  Accordingly, the synchronization processing unit 292 transmits a synchronization control signal indicating the timing of the output of the radiation 16 from the radiation source 264 to the radiation irradiation device 18 and the radiation image capturing device 20A via the communication unit 280.

  When the synchronization control units 248a to 248c (see FIG. 15) of the radiation detection units 30a to 30c receive the synchronization control signals via the communication units 194a to 194c, the drive circuit units 182a to 182c (see FIGS. 13 and 14). ) Starts supplying a bias voltage to the pixels 200a to 200c. As a result, each of the pixels 200a to 200c reaches a state where charges can be accumulated before the radiation 16 is irradiated.

  On the other hand, when receiving the synchronization control signal via the communication unit 260, the control unit 262 of the radiation irradiation apparatus 18 requests the console 22 to transmit imaging conditions, and the console 22 transmits a transmission request from the control unit 262. In response, the imaging conditions are transmitted to the radiation irradiation device 18 via the communication unit 280.

  When the control unit 262 receives the imaging condition via the communication unit 260, the radiation source 264 applies the radiation 16 having a predetermined dose according to the imaging condition at a timing indicated by the synchronization control signal for a predetermined exposure time. Only the subject 14 is irradiated. The radiation 16 output from the radiation source 264 passes through the collimator 266, is irradiated onto the subject 14, passes through the subject 14 and passes through the subject 14, and the radiation conversion panels 172a to 172c in the radiation detection units 30a to 30c (FIGS. 4 and 7B). To FIG. 14).

  In step S4, in each of the radiation detection units 30a to 30c, the scintillators 150a to 150c constituting the radiation conversion panels 172a to 172c emit visible light having an intensity corresponding to the intensity of the radiation 16, and the photoelectric conversion layers 152a to 152c. Each of the pixels 200a to 200c constituting the light converts visible light into an electric signal and accumulates it as an electric charge. Next, the charge information, which is a radiographic image of the subject 14 held in each of the pixels 200a to 200c, is transferred from the address signal generators 242a to 242c constituting the cassette controllers 192a to 192c to the gate driver circuit 212 and the multiplexer driver circuits 226a to 226c. 236a to 236c are read according to the address signal.

  In this case, in the panel units 198a to 198c, the charge information of the pixels 200a to 200c in the odd-numbered rows is read by the readout circuit units 184a to 184c, and at the same time, the charge information of the pixels 200a to 200c in the even-numbered rows is read out. The data is read by 186c and output to the control units 196a to 196c.

  First, reading of charge information from the pixels 200a to 200c in the odd rows will be described.

  The gate driving circuit 212 supplies a control signal to the gates of the TFTs 210a to 210c connected to the gate lines 202a to 202c corresponding to the address signals supplied from the address signal generators 242a to 242c. On the other hand, the multiplexer driving circuits 226a to 226c output selection signals in accordance with the address signals supplied from the address signal generation units 242a to 242c to sequentially switch (turn on and off) the FET switches 224a to 224c, and the gate driving circuit 212. The radiographic images as the charge information held in the odd-numbered pixels 200a to 200c connected to the gate lines 202a to 202c selected by the above are sequentially read out via the signal lines 204a to 204c.

  The radiographic images read out from the respective pixels 200a to 200c connected to the selected gate lines 202a to 202c are amplified by the respective amplifiers 220a to 220c, and then sampled by the respective sample hold circuits 222a to 222c, so that the FET switch The signals are supplied to A / D converters 228a to 228c via 224a to 224c and converted into digital signals. The radiographic image converted into the digital signal is temporarily stored in the image memories 240a to 240c of the cassette control units 192a to 192c (step S5).

  Similarly, the gate driving circuit 212 sequentially switches the gate lines 202a to 202c that output control signals according to the address signals supplied from the address signal generators 242a to 242c, and is connected to the gate lines 202a to 202c. Radiation images as charge information held in the odd-numbered pixels 200a to 200c are read out via the signal lines 204a to 204c, and the cassette controller 192a is connected via the FET switches 224a to 224c and the A / D converters 228a to 228c. Are stored in the image memories 240a to 240c of .about.192c (step S5).

  The above is the description of reading of charge information from the pixels 200a to 200c in the odd-numbered rows.

  Next, reading of charge information from the pixels 200a to 200c in the even-numbered rows will be described.

  In the readout of the charge information from the pixels 200a to 200c in the even-numbered rows, the readout is basically performed in the same manner as the readout of the charge information from the respective pixels 200a to 200c in the odd-numbered rows. That is, since the readout circuit units 184a to 184c and the readout circuit units 186a to 186c have the same circuit configuration, the signal lines 204a to 204c and the readout circuit units 184a to 184c are described in the description of the pixels 200a to 200c in the odd rows. In the method of reading out charge information from the pixels 200a to 200c in the even-numbered rows, the wording of each component in the signal lines 206a to 206c and the wording of each component in the readout circuit units 186a to 186c are replaced. Explain. Therefore, detailed description thereof is omitted here.

Radiation image stored as described above in the image memory 240a~240c transmission, together with the cassette ID information stored in the cassette ID memory 244A～244c, the console 22 by wireless communication via the communication unit 194A～194 c Is done.

  In the description of steps S4 and S5, the case where the charge information of the pixels 200a to 200c in the odd rows and the charge information of the pixels 200a to 200c in the even rows are simultaneously read and stored in the image memories 240a to 240c will be described. did. Since this readout process does not require a real-time synchronization control process such as irradiation of radiation 16, each pixel 200a to 200c in the odd row is replaced with each pixel 200a in the even row instead of the above readout process. The reading process may be performed in the order of 200c, or in the order of the pixels 200a to 200c in the even-numbered row → the pixels 200a to 200c in the odd-numbered row.

  In step S <b> 6, when the image processing unit 288 of the console 22 receives each radiation image and cassette ID information via the communication unit 280 and the control unit 282, the connection order information stored in the connection order information management unit 294, and the ID With reference to the cassette ID information stored in the memory 286 and the received cassette ID information, the connection order of the radiation detection units 30a to 30c is grasped, and the radiation source 264 and each The SID between the radiation conversion panels 172a to 172c is specified. Next, the image processing unit 288 performs image correction processing on each radiation image based on the attenuation rate of the radiation 16 according to the SID, and then sequentially connects the radiation images according to the connection order. A composite image in which a part of the image overlaps is generated. Then, the image processing unit 288 stores the generated composite image (long photographed image) and each radiographic image used for image synthesis in the image memory 290.

  In step S7, the control unit 282 transmits the long captured image stored in the image memory 290 to the display device 24 via the communication unit 280, and the display device 24 displays the received long captured image.

  The doctor or engineer visually confirms the radiographic image displayed on the display device 24 and confirms that an appropriate long image of the subject 14 has been obtained. In step S8 after the long photographing with respect to the subject 14 is completed, the doctor or engineer turns on the power switches 168a to 168c of the radiation detection units 30a to 30c (FIGS. 1, 2, 5A, 6A to 7A, and 15). Turn off. Thereby, the power supply parts 190a-190c stop the electric power supply to each part of the radiation detection units 30a-30c.

  Next, the doctor or technician removes each connector 32 from the connection terminals 124b, 124c, 126a, 126b, and separates the radiation detection units 30a-30c to release the connected state. Thereafter, the housing 34a is fitted so that the convex portions 372a and 372c and the concave portions 370a and 370c, the convex portions 376a and 376c and the concave portions 374a and 374c, the convex portion 378b and the concave portion 380b, and the convex portion 382b and the concave portion 384b are fitted. The blocks 58a to 58c and 60a to 60c are attached to the step portions 120a to 120c and 122a to 122c of .about.34c, respectively, so that the state shown in FIGS. 5A and 5B is restored.

  As described above, according to the radiographic imaging system 10A and the radiographic imaging apparatus 20A according to the first embodiment, the two types of radiation detection units 30a to 30c are alternately repeated by the stepped portions 120a to 120c and 122a to 122c. The radiographic imaging device 20A is connected to form a radiographic imaging device 20A, and the radiographic imaging device 20A performs long imaging on the subject 14.

  Specifically, the radiation conversion panels 172a to 172c partially overlap each other, and the irradiation surfaces 148a and 148c (first irradiation surface) and the irradiation surface 148b (second irradiation surface) having different areas are alternately arranged in order. As described above, by connecting the casings 34a to 34c using the step portions 120a to 120c and 122a to 122c, the radiation detection units 30a to 30c (the casings 34a to 34c thereof) The imaging surface 156 of the radiographic imaging device 20A configured to include the imaging regions 40a to 40c is maintained in a substantially flat shape without causing a step.

  That is, in the first embodiment, in order to configure the imaging surface 156, the first irradiation surface (irradiation surface 148a) → second irradiation surface (irradiation surface 148b) → first irradiation surface (irradiation surface 148c). By sequentially connecting the two types of radiation detection units 30a to 30c with the stepped portions 120a to 120c and 122a to 122c so as to be alternately repeated in order, the overall thickness of the radiographic imaging device 20A can be reduced to each radiation detection unit 30a. While suppressing to a thickness of ˜30c, a step at the connecting portion is not generated.

  Therefore, according to the first embodiment, it is possible to perform long imaging by connecting the plurality of radiation detection units 30a to 30c without generating a step at the connection location. That is, in the first embodiment, even if the radiation detection units 30a to 30c are sequentially connected, it is possible to avoid an increase in the size of the radiographic image capturing apparatus 20A and to ensure that the imaging surface 156 is planar.

  In addition, since the radiographic imaging apparatus 20A is configured by connecting the casings 34a to 34c with the step portions 120a to 120c and 122a to 122c, it is possible to perform long imaging by irradiating the subject 14 with the radiation 16 once. This makes it possible to reduce the shooting time.

  Further, in the first embodiment, the radiation detection units 30a to 30c are sequentially connected so as not to generate a step at the connecting portion. Therefore, a step is generated at the connecting portion of each electronic cassette as in Patent Document 2. Compared to the case, when the electronic cassettes are disconnected from each other, it is possible to avoid a problem that the electronic cassettes are broken due to an impact (for example, an impact caused by a drop) caused by a step at the connection location.

  Moreover, in 1st Embodiment, when connecting one housing | casing and the other housing | casing by level | step-difference part 120a-120c, 122a-122c, the other in the radiation conversion panel accommodated in one housing | casing, for example. If one casing and the other casing are connected so that a part on the casing side and a part on one casing side of the radiation conversion panel accommodated in the other casing overlap (FIG. 1). (See FIG. 4), when the radiation images obtained by the radiation conversion panels 172a to 172c are combined to obtain a radiation image of a single long subject 14, at the connected portions of the radiation images. It is also possible to prevent missing images.

  Therefore, according to the first embodiment, the two types of radiation detection units 30a to 30c are alternately connected, and the overall thickness of the radiation imaging apparatus 20A can be detected without causing a step at the connection location. By suppressing the thickness of the units 30a to 30c and reliably maintaining the imaging surface 156 in a flat shape, it is possible to eliminate the uncomfortable feeling of the subject 14 at the time of imaging, and the radiographic image as compared with the conventional technique. It is also possible to reduce the thickness of the photographing apparatus 20A. Further, the radiographic image capturing apparatus 20A is configured by connecting the two types of radiation detection units 30a to 30c with the stepped portions 120a to 120c and 122a to 122c, so that the imaging time can be shortened.

  In addition, each radiation detection unit 30a-30c mentioned above is an electronic cassette which can perform normal imaging | photography individually, and in 1st Embodiment, such several electronic cassette is set to level | step-difference part 120a-120c, Each effect mentioned above is acquired by connecting with 122a-122c.

  Further, by removing the blocks 58a to 58c and 60a to 60c from the casings 34a to 34c, the stepped portions 120a to 120c and 122a to 122c are easily formed, so that the casings 34a to 34c are efficiently connected. It becomes possible.

  Further, the step portions 120a and 120c are provided with recesses 370a, 370c, 374a and 374c, and the step portions 120b and 122b fitted to the step portions 120a and 120c are provided with protrusions 378b and 382b, and the recess portions 370a, 370c, 374a and 374c are provided. When the step portions 120a to 120c and 122a to 122c are fitted so that the projection portions 378b and 382b are fitted to each other, the step portions 120a to 120c and 122a to 122c are fitted with no gap in a positioned state. Is done. Therefore, by providing the convex portions 378b and 382b and the concave portions 370a, 370c, 374a and 374c, the casings 34a to 34c can be reliably and easily connected.

  Furthermore, by providing the handle portions 132a to 132c and 142a to 142c on the side surfaces 50a to 50c and 52a to 52c where the step portions 120a to 120c and 122a to 122c are not formed, the radiation detection units 30a to 30c are easily transported. It is also possible to do.

  In the casings 34a and 34c, the surfaces of the casings 34a and 34c that are close to the stepped portions 120a, 120c, 122a, and 122c are the back surfaces 42a and 42c. Surfaces separated from the portions 120a, 120c, 122a, and 122c are surfaces 36a and 36c (irradiation surfaces 148a and 148c). Further, in the housing 34b, a surface close to the stepped portions 120b and 122b of the housing 34b is a surface 36b (irradiation surface 148b), while facing the irradiation surface 148b and separated from the stepped portions 120b and 122b. The finished surface is the back surface 42b. Thus, by connecting the front surfaces 36a to 36c (irradiation surfaces 148a to 148c) and the back surfaces 42a to 42c in advance, the casings 34a to 34c can be efficiently connected.

  Furthermore, the connection order information generation units 250a to 250c generate the connection order of the casings 34a to 34c as connection order information. As a result, when each radiographic image is synthesized to form an image of one long subject 14, each radiographic image is obtained by which radiation conversion panel 172a to 172c by referring to the connection order information. Whether the image is a radiation image can be specified. As a result, it is possible to efficiently form a single long image.

  Further, the image processing unit 288 of the console 22 corrects each radiographic image based on the connection order information, and synthesizes each radiographic image after correction to generate a long radiographic image. An image can be obtained.

  Further, by arranging the control units 196a to 196c behind the radiation conversion panels 172a to 172c (on the back surfaces 42a to 42c side) via the radiation shielding members 400a to 400c, the control units 196a to 196c are irradiated with the radiation 16. Fear can be avoided.

  Further, if the control units 196a to 196c are smaller than the radiation conversion panels 172a to 172c and the radiation shielding members 400a to 400c in plan view, it is possible to reliably prevent the radiation 16 from being applied to the control units 196a to 196c. it can.

  That is, if irradiation with radiation 16 is performed in a state where the control units 196a to 196c are arranged in the respective imaging regions 40a to 40c or the imaging surface 156, the control units 196a to 196c may be deteriorated by the radiation 16, or the control unit There is a disadvantage that 196a to 196c appear in the radiation image. Therefore, in the first embodiment, as described above, it is possible to prevent the occurrence of these disadvantages by avoiding the irradiation of the radiation 16 with respect to the respective control units 196a to 196c.

  Moreover, since each housing | casing 34a-34c is electrically and mechanically connected by the connector 32, while transmission / reception of the signal between each housing | casing 34a-34c is attained, each housing | casing 34a-34. 34c will be connected reliably.

  In the above description, the case where the synchronization control signal is transmitted from the console 22 to the radiographic imaging apparatus 20A has been described. However, the synchronization control signals 248a to 248c of the radiation detection units 30a to 30c generate synchronization control signals. Each synchronization control signal may be transmitted to the console 22. In this case, since the irradiation timing of the radiation 16 may be different between the synchronization control signals, the synchronization processing unit 292 of the console 22 is, for example, the most of the timings indicated by the synchronization control signals. A synchronous control signal of late timing is transmitted to the radiation irradiation device 18. Thereby, after charge accumulation in each of the radiation conversion panels 172a to 172c becomes possible, the radiation 16 is irradiated from the radiation irradiation device 18, so that the radiation detection units 30a to 30c and the radiation irradiation device 18 are connected. Synchronization can be ensured.

  If there is a specific part to be noticed, it is determined that the specific part should be imaged by the radiation detection unit 30b, and the scintillator 150b of the radiation detection unit 30b is made of CsI, and the radiation detection unit 30b is centered. The connection order information of the connection order may be registered in the connection order information management unit 294 in advance. In this case, the control unit 282 compares the connection order information transmitted from the radiographic image capturing apparatus 20A with the connection order information registered in advance in the connection order information management unit 294, and if both match, If imaging is permitted (synchronization control signal is transmitted) and they are different, it is possible to notify a doctor or a technician that the radiation detection units 30a to 30c are erroneously connected via the display device 24. Become.

  As a result, a desired long photographic image including an image of a specific part can be obtained with certainty. As described above, if the connection order of the radiation detection units 30a to 30c is known in advance, the actual connection state is desired by registering the connection order information in the connection order information management unit 294 in advance. It is possible to check on the console 22 side whether or not it is in the connected state, and it is possible to reliably perform the long photographing in the desired connected state.

  Furthermore, in the above description, the case where the radiographic image is transmitted after transmitting the coupling order information from the radiographic imaging apparatus 20A to the console 22 has been described. However, the coupling order information and the radiographic image may be transmitted simultaneously. Is possible. Thereby, the console 22 can easily grasp that the received radiation image is an image related to the connection order information.

  In the above description, the three radiation detection units 30a to 30c are arranged in the order of the surface 36a (first irradiation surface) → the surface 36b (second irradiation surface) → the surface 36c (first irradiation surface). However, the first embodiment is not limited to this description, and the imaging surface 156 is changed from the first irradiation surface to the first irradiation surface. 2 irradiation surface → first irradiation surface → second irradiation surface →..., Or second irradiation surface → first irradiation surface → second irradiation surface → first irradiation surface →. It is only necessary that a plurality of radiation detection units can be sequentially connected.

  In the above description, the case where the three radiation detection units 30a to 30c are sequentially connected along one direction has been described. However, the step portions 120a to 120c and 122a to 122c are also provided on the side surfaces 50a to 50c and 52a to 52c. Needless to say, one radiographic imaging apparatus 20A may be configured by forming the same stepped portion and sequentially connecting a plurality of radiation detection units along the planar direction (two directions).

  The radiographic image capturing system 10A and the radiographic image capturing apparatus 20A according to the first embodiment are not limited to the above description, and the embodiments shown in FIGS. 19A to 23B can also be realized.

  FIG. 19A illustrates a case where the connection terminals 126a and 124b are optically connected by an optical fiber cable 300 and signals are transmitted and received by optical communication. In this case, the optical connectors 302 and 304 are fitted into the connection terminals 126a and 124b, respectively. In FIG. 19B, the connection terminal 126 a is replaced with the coil 306, the connection terminal 124 b is replaced with the coil 308, and current is passed through the coils 306 and 308 to generate the magnetic flux 310, whereby the coil 306 resulting from the magnetic flux 310 is generated. , 308 shows a case where signals are transmitted and received by magnetic coupling. Even with the optical coupling of FIG. 19A or the magnetic coupling of FIG. 19B, signals can be transmitted and received between the radiation detection units 30a to 30c.

  In FIG. 20, the stepped portion 122a of the housing 34a is provided with a convex portion 375a, and the stepped portion 120b of the housing 34b is provided with a concave portion 379b so that the convex portion 375a and the concave portion 379b are fitted. The case where these are fitted is illustrated. Even in this case, by fitting the convex portion 375a and the concave portion 379b, the stepped portions 122a and 120b can be reliably fitted without any gap and the casings 34a and 34b can be connected.

  FIG. 21 is a perspective view showing a charging process of the power supply units 190a and 190c (see FIG. 9) by the cradle 320 arranged at a necessary place in the medical institution.

  In this case, for example, the radiation detection units 30 a and 30 c and the cradle 320 are electrically connected by a USB cable 322 having connectors 324 and 326.

  The cradle 320 transmits and receives necessary information to and from the console 22 and the RIS 26 in the medical institution using not only the charging of the power supply units 190a and 190c but also the wireless communication function or the wired communication function of the cradle 320. May be. The information to be transmitted and received can include radiation images recorded in the image memories 240a and 240c of the radiation detection units 30a and 30c.

  In addition, a display unit 328 is provided in the cradle 320, and necessary information including the charged state of the radiation detection units 30a and 30c and the radiation images acquired from the radiation detection units 30a and 30c is displayed on the display unit 328. You may make it make it.

  Further, a plurality of radiation detection units 30a and 30c are connected to a network, and the charge states of the radiation detection units 30a and 30c connected to the respective cradles 320 are collected via the network to detect radiation in a usable charge state. It can also comprise so that the location of unit 30a, 30c can be confirmed.

  Furthermore, in the above description, as shown in FIGS. 4 and 9 to 12, the scintillators 150 a to 150 c are arranged, but instead of this configuration, FIGS. 22A and 22B are shown. As described above, the other scintillators 154a to 154c may be arranged in the casings 34a to 34c. In this case, the scintillators 154a to 154c convert the radiation 16 irradiated from the surfaces 36a to 36c through the shock absorbing members 174a to 174c, the photoelectric conversion layers 152a to 152c, the TFT layers 176a to 176c, and the substrates 178a to 178c into visible light. Convert once. Accordingly, even in this case, the photoelectric conversion layers 152a to 152c can convert the visible light into a radiation image.

  22A and 22B, since the photoelectric conversion layers 152a to 152c and the scintillators 154a to 154c are arranged in this order with respect to the surfaces 36a to 36c, the radiation conversion panels 172a to 172c are ISS radiation detectors. It is configured as.

  23A and 23B, the photoelectric conversion layers 152a to 152c may be sandwiched between the two scintillators 150a to 150c and 154a to 154c. In this case, the radiation 16 is converted into visible light by each of the scintillators 150a to 150c and 154a to 154c, so that the sensitivity and sharpness of the radiation image can be improved. The exposure dose of 16 can be reduced.

  Furthermore, in the case of FIG. 23A and FIG. 23B, since it arrange | positions in order of the scintillators 150a-150c, the photoelectric converting layers 152a-152c, and the scintillators 154a-154c with respect to the surfaces 36a-36c, among radiation conversion panels 172a-172c The arrangement relationship between the scintillators 150a to 150c and the photoelectric conversion layers 152a to 152c is the PSS method, while the arrangement relationship between the photoelectric conversion layers 152a to 152c and the scintillators 154a to 154c is the ISS method. Therefore, the radiation conversion panels 172a to 172c shown in FIGS. 23A and 23B are configured as radiation detectors including both the ISS system and the PSS system.

  In the case of FIGS. 23A and 23B, the scintillators 150a to 150c and 154a to 154c may be made of the same material, or may be made of different materials. In the case of using different materials, one scintillator may be made of CsI and the other scintillator may be made of GOS. When performing long imaging, the scintillators 150a to 150c and 154a to 154c of the radiation detection unit that images a specific part of interest that is desired to be taken out of the long imaging part are configured by CsI, and the scintillators 150a to 150c of other radiation detection units. Of course, 154a to 154c may be made of GOS.

  Furthermore, the first embodiment can also be applied to a case where a radiation image is acquired using a light conversion type radiation conversion panel. In this light readout type radiation conversion panel, when radiation is incident on each solid state detection element, an electrostatic latent image corresponding to the dose is accumulated and recorded in the solid state detection element. When reading the electrostatic latent image, the radiation conversion panel is irradiated with reading light, and the value of the generated current is acquired as a radiation image. In addition, the radiation conversion panel can erase and reuse a radiation image that is a remaining electrostatic latent image by irradiating the radiation conversion panel with erasing light (see Japanese Patent Application Laid-Open No. 2000-105297).

  Furthermore, in the radiographic imaging device 20A, in order to prevent the risk of blood and other germs adhering, for example, the entire device has a waterproof and sealing structure, and is sterilized and washed as necessary. One radiographic imaging device 20A can be used repeatedly.

  In addition, the first embodiment is not limited to radiographic imaging in medical institutions, but is also applied to disaster scenes, home nursing scenes, and also to imaging of subjects in health examinations by being mounted on examination cars. Is possible. Furthermore, the first embodiment is not limited to the imaging of such medical-related radiographic images, and can of course be applied to radiographic imaging in various nondestructive inspections, for example.

  Next, a radiographic image capturing system 10B according to the second embodiment will be described with reference to FIGS. 24 to 26B.

Incidentally, the radiation image capturing system 10B, the same components as the radiation image capturing system 10 A according to the first embodiment (see FIGS. 1 to 23B), with the same reference numerals, a detailed description thereof will be omitted The same shall apply hereinafter.

  As shown in FIGS. 25A to 26B, the radiographic imaging system 10B according to the second embodiment is provided with hinges 340 that connect the casings 34a to 34c and the blocks 58a to 58c to the side surfaces 54a to 54c, respectively. This is different from the radiographic imaging system 10A according to the first embodiment in that hinges 342 for connecting the casings 34a to 34c and the blocks 60a to 60c are respectively provided on the side surfaces 56a to 56c.

  In this case, the blocks 58a to 58c with the hinge 340 as the center are mounted on the casings 34a to 34c in a state where the claw members 90a to 90c and 96a to 96c are engaged with the holes 94a to 94c and 100a to 100c. The step portions 120a to 120c are formed by rotating the steps. Further, the blocks 60a to 60c with respect to the casings 34a to 34c are centered on the hinge 342 in a state where the engagement state between the claw members 102a to 102c and 108a to 108c and the holes 106a to 106c and 112a to 112c is released. By turning, step portions 122a to 122c are formed.

  As described above, since the step portions 120a to 120c and 122a to 122c are easily formed by rotating the blocks 58a to 58c and 60a to 60c, the casings 34a to 34c can be efficiently connected. It becomes possible. Further, since the blocks 58a to 58c and 60a to 60c are not separated from the casings 34a to 34c, the loss of the blocks 58a to 58c and 60a to 60c can be prevented.

  Further, in the case of the second embodiment, unlike the first embodiment, the concave portions 380b and 384b are formed in the step portions 120b and 122b, respectively, while the convex portions 378b and 382b are formed in the blocks 58b and 60b, respectively. .

  Accordingly, when the stepped portion 122a of the housing 34a and the stepped portion 120b of the housing 34b are fitted, the concave portion 374a and the convex portion 378b are fitted, and the convex portion 376a and the concave portion 380b are fitted. Therefore, the stepped portion 122a and the stepped portion 120b can be fitted (connected) in a state in which the stepped portion 122a and the stepped portion 120b are accurately positioned.

  Further, when the stepped portion 122b of the housing 34b and the stepped portion 120c of the housing 34c are fitted, the concave portion 384b and the convex portion 372c are fitted, and the convex portion 382b and the concave portion 370c are fitted. Thus, the stepped portion 122b and the stepped portion 120c can be fitted (connected) in a state where the stepped portion 122b and the stepped portion 120c are accurately positioned.

  In the second embodiment, when the step portions 120a to 120c and 122a to 122c are fitted, the distance between the connection terminals 124a to 124c and 126a to 126c is longer than the first embodiment. Connection by the connector 32 becomes difficult. Therefore, for example, as shown in FIG. 24, the optical connectors 302 and 304 of the optical fiber cable 300 are fitted to the connection terminals 124a to 124c and 126a to 126c, thereby optically connecting the connection terminals 124a to 124c and 126a to 126c. Can be combined.

  Next, a radiographic image capturing system 10C according to the third embodiment will be described with reference to FIGS. 24 and 27 to 29B.

  The radiographic image capturing system 10C according to the third embodiment connects each of the block-like control units 196a to 196c and the block-like panel units 198a to 198c via a hinge (rotation mechanism) 348, thereby providing each radiation. It differs from the radiographic imaging system 10B according to the second embodiment in that each of the detection units 30a to 30c is configured. Therefore, in 3rd Embodiment, panel part 198a-198c functions as a housing | casing (panel accommodating part) which accommodates the radiation conversion panels 172a-172c.

  In this case, the blocks 58a to 58c are configured by a block 350 on the control unit 196a to 196c side and a block 352 on the panel unit 198a to 198c side, while the blocks 60a to 60c are on the control unit 196a to 196c side. The block 354 includes a block 356 on the panel portions 198a to 198c side.

  Therefore, each block 350 and each control part 196a-196c are connected via the hinge 340d as a part of hinge 340 (refer FIG. 25A-FIG. 26B), and each block 354 and each control part 196a-196c are Are connected via a hinge 342d as a part of the hinge 342. Each block 352 and each panel part 198a to 198c are connected via a hinge 340e as a part of the hinge 340, and each block 356 and each panel part 198a to 198c are a part of the hinge 342. It is connected via a hinge 342e.

  Further, a concave portion 360 is provided on a side surface of the panel portions 198a to 198c on the hinge 348 side, and a handle portion 362 is disposed in the concave portion 360. The doctor or engineer can carry the radiation detection units 30a to 30c while holding the handle portion 362.

  Here, when each radiation detection unit 30a-30c is connected and the one radiographic imaging device 20C shown in FIG.24 and FIG.27 is comprised, a doctor or an engineer first makes the panel part 198a centering on the hinge 348. FIG. The control units 196a to 196c are rotated with respect to ˜198c. In this case, if the thickness of the control units 196a to 196c is the same as that of the panel units 198a to 198b, the upper surfaces of the radiation detection units 30a to 30c can be made substantially planar.

  Next, as shown in FIGS. 29A and 29B, the doctor or engineer rotates the block 350 around the hinge 340d with respect to the control units 196a to 196c and moves the block 352 around the hinge 340e to the panel units 198a to 198a. Step portions 120a to 120c are formed by rotating with respect to 198c. Similarly, the doctor or engineer rotates the block 354 with respect to the control units 196a to 196c around the hinge 342d and rotates the block 356 with respect to the panel units 198a to 198c around the hinge 342e. Step portions 122a to 122c are formed.

  Then, in the order shown in FIGS. 24 and 27, the step portions 120a to 120c and 122a to 122c of the radiation detection units 30a to 30c are fitted, and the optical fiber cable 300 is connected to the connection terminals 124b, 124c, 126a, and 126b. Each of the optical connectors 302 and 304 is fitted to constitute one radiographic image capturing apparatus 20C.

  Even in this case, the same effect as the second embodiment can be obtained. Further, since the control units 196a to 196c rotate with respect to the panel units 198a to 198c around the hinge 348, it is possible to reliably avoid the control units 196a to 196c from being irradiated with the radiation 16 at the time of photographing. Furthermore, since the thickness of each control part 196a-196c is substantially the same as the thickness of each panel part 198a-198c, a level | step difference does not generate | occur | produce in a connection location, and the imaging | photography surface 156 and control part 196a-196c are taken at the time of imaging | photography. As a result, even if the subject 14 contacts the control units 196a to 196c, there is no sense of incongruity.

  Further, when disassembling the radiographic image capturing device 20C into the radiation detection units 30a to 30c, the disassembly operation may be performed in the reverse order to the assembly operation described above. 27 to 29B, manual operation units 72a to 72c, 76a to 76c, and the like are not provided. However, the manual operation units 72a to 72c, 76a to 76c, and the like may be provided. It is.

  Furthermore, in 3rd Embodiment, as shown in FIG. 30, you may arrange | position the control parts 196a-196c on the panel parts 198a-198c, respectively. In this case, the control units 196a to 196c are fixed to the portions of the panel units 198a to 198c where the radiation 16 is not irradiated. In this case, the control units 196a to 196c cannot be rotated by the hinge 348 or the like, but irradiation of the radiation 16 to the control units 196a to 196c can be reliably avoided.

  In the case of FIG. 30, the control units 196a to 196c are arranged in the panel units 198a to 198c, and the substantial thickness of the panel units 198a to 198c is increased. However, since there is no complicated mechanism such as the hinge 348, an effect that the configuration of the entire apparatus can be simplified can be obtained.

  Moreover, in said description, it is set as the surface 36a-36c depending on whether it is a surface close | similar to the level | step-difference part 120a-120c, 122a-122c, or a separated surface, or back surface 42a-42c. It was decided whether or not.

  In 1st-3rd embodiment, it is not limited to such definition, When the level | step-difference part 120a-120c, 122a-122c is formed in the side surfaces 54a-54c, 56a-56c, the side surface 50a ˜50c, 52a to 52c, 54a to 54c, and 56a to 56c, one of the two surfaces facing each other may be one surface 36a to 36c and the other surface 42a to 42c.

  Therefore, as schematically shown in FIG. 31, in the radiographic imaging apparatus 20D, by providing a protrusion protruding in the horizontal direction at the intermediate portion of the side surfaces 54a, 54c, 56a, 56c of the radiation detection units 30a, 30c, Step portions 120a, 120c, 122a, and 122c are formed on the 36a and 36c sides and the back surfaces 42a and 42c, respectively, while grooves that can be fitted to the protrusions are formed in the intermediate portions of the side surfaces 54b and 56b of the radiation detection unit 30b. By providing, the structure which forms the level | step-difference part 120b, 122b is also attained.

  Even in this case, the stepped portion 122a and the stepped portion 120b and the stepped portion 122b and the stepped portion 120c are respectively fitted by fitting the protrusion and the groove. Similarly to the description in the embodiment, the thickness of the radiographic imaging device 20D can be made the same as that of each of the radiation detection units 30a to 30c without causing a step at the connection portion of the casings 34a to 34c. The upper surface of the radiographic image capturing apparatus 20D can be substantially planar. Therefore, each effect due to the fact that no step is generated at the connecting portion can be easily obtained.

  Note that the present invention is not limited to the above-described embodiment, and it is needless to say that various configurations can be adopted without departing from the gist of the present invention.

  For example, the radiation conversion panels 172a to 172c may be the radiation detector 600 according to the modification shown in FIGS. FIG. 32 is a schematic cross-sectional view schematically showing the configuration of three pixel portions of the radiation detector 600 according to the modification.

  The radiation detector 600 includes a signal output unit 604 corresponding to TFT layers 176a to 176c (see FIG. 7B, FIGS. 9 to 12 and FIGS. 22A to 23B) including switching elements on an insulating substrate 602, solid state detection. A sensor unit 606 corresponding to the photoelectric conversion layers 152 a to 152 c including the elements and a scintillator 608 corresponding to the scintillators 150 a to 150 c and 154 a to 154 c are sequentially stacked. The signal output unit 604 and the sensor unit 606 A pixel portion is configured. The pixel units are arranged in a matrix on the substrate 602, and the signal output unit 604 and the sensor unit 606 in each pixel unit are configured to overlap each other.

  The scintillator 608 is formed by forming a phosphor that is formed on the sensor unit 606 via the transparent insulating film 610 and emits light by converting the radiation 16 into light. 32, for example, the upper side (the side opposite to the side where the substrate 602 is located) is the surface 36a to 36c (see FIGS. 2 to 12, FIGS. 20 to 23B and FIGS. 25A to 26B), and the lower side. If the radiation 16 is incident from above, the radiation detector 600 functions as a PSS radiation detector, and the phosphor of the scintillator 608 uses the incident radiation 16 as light. The light is converted into light.

  The wavelength range of light emitted by the scintillator 608 is preferably the visible light range (wavelength 360 nm to 830 nm), and in order to enable monochrome imaging by the radiation detector 600, the wavelength range of green is included. Is more preferable.

  Specifically, the phosphor used in the scintillator 608 preferably contains CsI when imaging using X-rays as the radiation 16, and CsI (Tl) having an emission spectrum of 420 nm to 600 nm during X-ray irradiation. It is particularly preferable to use (cesium iodide added with thallium). Note that the emission peak wavelength of CsI (Tl) in the visible light region is 565 nm.

  The scintillator 608 may be formed, for example, by vapor-depositing CsI (Tl) having a columnar crystal structure on a vapor deposition base. When the scintillator 608 is formed by vapor deposition as described above, Al is often used as the vapor deposition substrate from the viewpoint of X-ray transmittance and cost, but is not limited thereto. Note that in the case where GOS is used as the scintillator 608, GOS is preferably applied to a resin base and then bonded to the surface of the TFT active matrix substrate. As a result, the TFT active matrix substrate can be preserved even if GOS application fails.

  The sensor unit 606 includes an upper electrode 612, a lower electrode 614, and a photoelectric conversion film 616 disposed between the upper electrode 612 and the lower electrode 614.

Since the upper electrode 612 needs to make the light generated by the scintillator 608 incident on the photoelectric conversion film 616, it is preferable that the upper electrode 612 is made of a conductive material that is transparent at least with respect to the emission wavelength of the scintillator 608. It is preferable to use a transparent conductive oxide (TCO) having a high transmittance for visible light and a small resistance value. Note that although a metal thin film such as Au can be used as the upper electrode 612, a resistance value tends to increase when the transmittance of 90% or more is obtained, so that the TCO is preferable. For example, ITO (Indium Tin Oxide), IZO, AZO, FTO, SnO ₂ , TiO ₂ , ZnO _{2 and the} like can be preferably used, and ITO is most preferable from the viewpoint of process simplicity, low resistance, and transparency. Note that the upper electrode 612 may have a single configuration common to all the pixel portions, or may be divided for each pixel portion.

  The photoelectric conversion film 616 includes an organic photoconductor (OPC), absorbs light emitted from the scintillator 608, and generates a charge corresponding to the absorbed light. If the photoelectric conversion film 616 includes an organic photoconductor (organic photoelectric conversion material), the photoelectric conversion film 616 has a sharp absorption spectrum in the visible light region, and electromagnetic waves other than light emitted by the scintillator 608 are almost absorbed by the photoelectric conversion film 616. In addition, noise generated when the radiation 16 is absorbed by the photoelectric conversion film 616 can be effectively suppressed. Note that the photoelectric conversion film 616 may be configured to include a-Si instead of the organic photoconductor. In this case, it has a wide absorption spectrum and can efficiently absorb light emitted by the scintillator 608.

  The organic photoconductor constituting the photoelectric conversion film 616 preferably has a peak wavelength closer to the emission peak wavelength of the scintillator 608 in order to absorb light emitted by the scintillator 608 most efficiently. Ideally, the absorption peak wavelength of the organic photoconductor coincides with the emission peak wavelength of the scintillator 608. However, if the difference between the two is small, the light emitted from the scintillator 608 can be sufficiently absorbed. . Specifically, the difference between the absorption peak wavelength of the organic photoconductor and the emission peak wavelength of the scintillator 608 with respect to the radiation 16 is preferably within 10 nm, and more preferably within 5 nm.

  Examples of organic photoconductors that can satisfy such conditions include quinacridone organic compounds and phthalocyanine organic compounds. For example, since the absorption peak wavelength of quinacridone in the visible region is 560 nm, if quinacridone is used as the organic photoconductor and CsI (Tl) is used as the material of the scintillator 608, the difference between the peak wavelengths may be within 5 nm. Thus, the amount of charge generated in the photoelectric conversion film 616 can be substantially maximized.

  The sensor unit 606 is a stack of a part that absorbs electromagnetic waves, a photoelectric conversion part, an electron transport part, a hole transport part, an electron blocking part, a hole blocking part, a crystallization prevention part, an electrode, an interlayer contact improvement part, or the like. An organic layer formed by mixing is included. The organic layer preferably contains an organic p-type compound (organic p-type semiconductor) or an organic n-type compound (organic n-type semiconductor).

  An organic p-type semiconductor is a donor organic semiconductor (compound) typified by a hole-transporting organic compound and refers to an organic compound having a property of easily donating electrons. More specifically, an organic compound having a smaller ionization potential when two organic materials are used in contact with each other. Therefore, any organic compound can be used as the donor organic compound as long as it is an electron-donating organic compound.

  An organic n-type semiconductor is an acceptor organic semiconductor (compound) typified by an electron-transporting organic compound and refers to an organic compound having a property of easily accepting electrons. More specifically, the organic compound having the higher electron affinity when two organic compounds are used in contact with each other. Accordingly, as the acceptor organic compound, any organic compound can be used as long as it is an electron-accepting organic compound.

  The materials applicable as the organic p-type semiconductor and the organic n-type semiconductor and the configuration of the photoelectric conversion film 616 are described in detail in Japanese Patent Application Laid-Open No. 2009-32854, and thus the description thereof is omitted. Note that the photoelectric conversion film 616 may be formed to further contain fullerene or carbon nanotube.

  The thickness of the photoelectric conversion film 616 is preferably as large as possible in terms of absorbing light from the scintillator 608. However, when the thickness is more than a certain level, the photoelectric conversion film 616 is generated in the photoelectric conversion film 616 by a bias voltage applied from both ends of the photoelectric conversion film 616. In this case, the electric field strength is reduced and the charge cannot be collected. Therefore, the thickness is preferably 30 nm to 300 nm, more preferably 50 nm to 250 nm, and particularly preferably 80 nm to 200 nm.

  The photoelectric conversion film 616 has a single-layer configuration common to all the pixel portions, but may be divided for each pixel portion. The lower electrode 614 is a thin film divided for each pixel portion. However, the lower electrode 614 may have a single configuration common to all the pixel portions. The lower electrode 614 can be made of a transparent or opaque conductive material, and Al, silver, or the like can be suitably used. The thickness of the lower electrode 614 can be, for example, 30 nm or more and 300 nm or less.

  In the sensor unit 606, by applying a predetermined bias voltage between the upper electrode 612 and the lower electrode 614, one of charges (holes, electrons) generated in the photoelectric conversion film 616 is moved to the upper electrode 612. And the other can be moved to the lower electrode 614. In the radiation detector 600 according to this modification, a wiring is connected to the upper electrode 612, and a bias voltage is applied to the upper electrode 612 via the wiring. In addition, the polarity of the bias voltage is determined so that electrons generated in the photoelectric conversion film 616 move to the upper electrode 612 and holes move to the lower electrode 614, but this polarity is opposite. May be.

  The sensor unit 606 included in each pixel unit only needs to include at least the lower electrode 614, the photoelectric conversion film 616, and the upper electrode 612. In order to suppress an increase in dark current, the electron blocking film 618 and the hole are included. It is preferable to provide at least one of the blocking films 620, and it is more preferable to provide both.

  The electron blocking film 618 can be provided between the lower electrode 614 and the photoelectric conversion film 616. When a bias voltage is applied between the lower electrode 614 and the upper electrode 612, the electron blocking film 618 is exposed from the lower electrode 614 to the photoelectric conversion film 616. It is possible to prevent the dark current from being increased due to the injection of electrons.

  An electron-donating organic material can be used for the electron blocking film 618. The material actually used for the electron blocking film 618 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 616, and the like, and 1.3 eV or more from the work function (Wf) of the material of the adjacent electrode. Those having a large electron affinity (Ea) and an Ip equivalent to or smaller than the ionization potential (Ip) of the material of the adjacent photoelectric conversion film 616 are preferable. Since the material applicable as the electron donating organic material is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, description thereof is omitted.

  The thickness of the electron blocking film 618 is preferably 10 nm or more and 200 nm or less, more preferably 30 nm or more and 150 nm or less, and particularly preferably, in order to surely exhibit the dark current suppressing effect and prevent a decrease in photoelectric conversion efficiency of the sensor unit 606. It is good to set it to 50 nm or more and 100 nm or less.

  The hole blocking film 620 can be provided between the photoelectric conversion film 616 and the upper electrode 612, and when a bias voltage is applied between the lower electrode 614 and the upper electrode 612, the photoelectric conversion film is formed from the upper electrode 612. An increase in dark current due to injection of holes into 616 can be suppressed.

  An electron-accepting organic material can be used for the hole blocking film 620. The thickness of the hole blocking film 620 is preferably 10 nm or more and 200 nm or less, more preferably 30 nm or more and 150 nm or less, and particularly preferably, in order to reliably exhibit the dark current suppressing effect and prevent a decrease in photoelectric conversion efficiency of the sensor unit 606. Is preferably 50 nm to 100 nm.

  The material actually used for the hole blocking film 620 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 616, and the like, and 1.3 eV from the work function (Wf) of the material of the adjacent electrode. As described above, it is preferable that the ionization potential (Ip) is large and that the Ea is equal to or larger than the electron affinity (Ea) of the material of the adjacent photoelectric conversion film 616. Since the material applicable as the electron-accepting organic material is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, description thereof is omitted.

  Note that, among the charges generated in the photoelectric conversion film 616, when a bias voltage is set so that holes move to the upper electrode 612 and electrons move to the lower electrode 614, the electron blocking film 618 and the hole blocking are set. The position relative to the film 620 may be reversed. Further, it is not necessary to provide both the electron blocking film 618 and the hole blocking film 620. If either of them is provided, a certain dark current suppressing effect can be obtained.

  As shown in FIG. 33, the signal output unit 604 is provided on the surface of the substrate 602 corresponding to the lower electrode 614 of each pixel unit, and the storage capacitor 622 for storing the electric charge moved to the lower electrode 614, The TFT 624 converts the electric charge accumulated in the accumulation capacitor 622 into an electric signal and outputs the electric signal. The region where the storage capacitor 622 and the TFT 624 are formed has a portion that overlaps with the lower electrode 614 in plan view. With such a configuration, the signal output unit 604 and the sensor unit 606 in each pixel unit Will have an overlap in the thickness direction. If the signal output unit 604 is formed so as to completely cover the storage capacitor 622 and the TFT 624 with the lower electrode 614, the plane area of the radiation detector 600 (pixel unit) can be minimized.

  The storage capacitor 622 is electrically connected to the corresponding lower electrode 614 through a wiring made of a conductive material formed through an insulating film 626 provided between the substrate 602 and the lower electrode 614. Thereby, the charge collected by the lower electrode 614 can be moved to the storage capacitor 622.

  The TFT 624 includes a gate electrode 628, a gate insulating film 630, and an active layer (channel layer) 632, and a source electrode 634 and a drain electrode 636 are formed on the active layer 632 at a predetermined interval. Yes. The active layer 632 can be formed of, for example, a-Si, amorphous oxide, organic semiconductor material, carbon nanotube, or the like. Note that the material forming the active layer 632 is not limited thereto.

The amorphous oxide that can form the active layer 632 is preferably an oxide containing at least one of In, Ga, and Zn (for example, In—O-based), and at least two of In, Ga, and Zn. Oxides containing one (for example, In—Zn—O, In—Ga—O, and Ga—Zn—O) are more preferable, and oxides including In, Ga, and Zn are particularly preferable. As the In—Ga—Zn—O-based amorphous oxide, an amorphous oxide whose composition in a crystalline state is represented by InGaO ₃ (ZnO) _m (m is a natural number less than 6) is preferable, and InGaZnO is particularly preferable. ₄ is more preferable. Note that the amorphous oxide that can form the active layer 632 is not limited thereto.

  Examples of the organic semiconductor material that can form the active layer 632 include, but are not limited to, phthalocyanine compounds, pentacene, vanadyl phthalocyanine, and the like. In addition, about the structure of a phthalocyanine compound, since it describes in detail in Unexamined-Japanese-Patent No. 2009-212389, description is abbreviate | omitted.

  If the active layer 632 of the TFT 624 is formed of an amorphous oxide, an organic semiconductor material, or a carbon nanotube, the radiation 16 such as X-rays is not absorbed, or even if it is absorbed, a very small amount remains. Generation of noise in the output unit 604 can be effectively suppressed.

  In addition, when the active layer 632 is formed of carbon nanotubes, the switching speed of the TFT 624 can be increased, and a TFT 624 having a low light absorption in the visible light region can be formed. Note that when the active layer 632 is formed of carbon nanotubes, the performance of the TFT 624 is remarkably deteriorated only by mixing a very small amount of metallic impurities into the active layer 632, so that extremely high purity carbon nanotubes are separated by centrifugation or the like.・ It needs to be extracted and formed.

  Here, any of the above-described amorphous oxide, organic semiconductor material, carbon nanotube, and organic photoconductor can be formed at a low temperature. Therefore, the substrate 602 is not limited to a substrate having high heat resistance such as a semiconductor substrate, a quartz substrate, and a glass substrate, and a flexible substrate such as plastic, aramid, or bio-nanofiber can also be used. Specifically, flexible substrates such as polyesters such as polyethylene terephthalate, polybutylene phthalate, polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, polychlorotrifluoroethylene, etc. Can be used. If such a plastic flexible substrate is used, it is possible to reduce the weight, which is advantageous for carrying around, for example.

  In addition, the photoelectric conversion film 616 is formed from an organic photoconductor, and the TFT 624 is formed from an organic semiconductor material, whereby the photoelectric conversion film 616 and the TFT 624 are formed at a low temperature on a plastic flexible substrate (substrate 602). It is possible to reduce the thickness and weight of the radiation detector 600 as a whole. Accordingly, the radiation detection units 30a to 30c (see FIGS. 1 to 14, 16 and 19B to 31) that accommodate the radiation detector 600 can be reduced in thickness and weight, and the radiation detection units 30a to 30c can be reduced. Are more easily connected, and a step at the connecting portion is less likely to occur.

  In this case, at least in the radiation conversion panels 172a and 172c (radiation detector 600) on the irradiation side of the radiation 16, the substrate 602 is formed of a plastic flexible substrate, and the flexible substrate is formed of an organic photoconductor. If the photoelectric conversion film 616 and the TFT 624 made of an organic semiconductor material are respectively formed, the plastic and organic materials hardly absorb the radiation 16, so the radiation detection unit 30b regardless of whether the ISS method or the PSS method is used. The radiation conversion panel 172b can be made to receive as much radiation 16 as possible. Further, as described above, if plastic and organic materials are used, at least the radiation conversion panels 172a and 172c can be thinned, so that the level difference at the connection location of the radiation detection units 30a to 30c can be reduced. it can.

  Further adding to the above-described effects, in the present embodiment, in order to obtain a single long image with no image loss at a joint portion (connection portion), a part of the radiation conversion panels 172a to 172c is provided. Two types of electronic cassettes (radiation detection units 30a to 30c) are alternately connected so as to overlap, and the imaging surface 156 is flattened. As a result, a step is generated between the radiation conversion panels 172a to 172c, the enlargement magnification (distance between the radiation source 264 and the radiation conversion panels 172a to 172c) is different, or the radiation distal to the irradiation direction of the radiation 16 is detected. There is a concern that the density of the radiation image (sensitivities of the radiation conversion panels 172a to 172c) may be different due to insufficient sensitivity at the overlapping portions of the conversion panel 172b with the radiation conversion panels 172a and 172c. In this case, the image processing unit 288 needs to obtain a single long image by connecting the radiation images after performing the image correction processing according to the enlargement magnification and the density.

  In such a case, as described above, at least the radiation conversion panels 172a and 172c on the irradiation side of the radiation 16 are made of plastic and an organic material, so that a step or radiation conversion between the radiation conversion panels 172a to 172c is achieved. Insufficient sensitivity in the panel 172b can be reduced, and the image correction process can be reduced or eliminated.

  Further, at least one type of radiation conversion panel (any kind of radiation conversion panel 172a, 172c or radiation conversion panel 172b) is made of a plastic and an organic material, and along the irradiation direction of the radiation 16, An ISS panel in which the substrate 602, the TFT 624, the photoelectric conversion film 616, and the CsI scintillator 608 are arranged in this order can easily obtain a high-quality radiation image and one long image. Of course, as long as all the radiation conversion panels 172a to 172c are made of plastics and organic materials and are ISS type panels adopting CsI scintillators 150a to 150c, the radiation conversion panels 172a to 172c have high image quality. A radiographic image is obtained.

  Furthermore, since the radiation detection units 30a to 30c are expensive electronic cassettes including the radiation conversion panels 172a to 172c, the radiation detection units 30a to 30c are not limited to being connected to each other and may be used alone. As described above, high-quality radiation images can be easily obtained with the ISS radiation conversion panels 172a to 172c using plastic and organic materials and a CsI scintillator, so that the radiation detection units 30a to 30c ( Ease of use when using the electronic cassette alone is also improved.

  Note that the substrate 602 is provided with an insulating layer for ensuring insulation, a gas barrier layer for preventing permeation of moisture and oxygen, an undercoat layer for improving flatness or adhesion to electrodes, and the like. May be.

  In addition, since aramid can be applied at a high temperature process of 200 ° C. or higher, the transparent electrode material can be cured at a high temperature to reduce the resistance, and can also be used for automatic mounting of a driver IC including a solder reflow process. Moreover, since aramid has a thermal expansion coefficient close to that of ITO or a glass substrate, warping after production is small and it is difficult to break. In addition, aramid can form a substrate thinner than a glass substrate or the like. Note that the substrate 602 may be formed by stacking an ultrathin glass substrate and an aramid.

  The bionanofiber is a composite of a cellulose microfibril bundle (bacterial cellulose) produced by bacteria (acetobacterium Xylinum) and a transparent resin. The cellulose microfibril bundle has a width of 50 nm and a size of 1/10 of the visible light wavelength, and has high strength, high elasticity, and low thermal expansion. By impregnating and curing a transparent resin such as acrylic resin and epoxy resin in bacterial cellulose, a bio-nanofiber having a light transmittance of about 90% at a wavelength of 500 nm can be obtained while containing 60% to 70% of the fiber. Bionanofiber has a low coefficient of thermal expansion (3-7 ppm) comparable to silicon crystals, is as strong as steel (460 MPa), has high elasticity (30 GPa), and is flexible, compared to glass substrates, etc. Thus, the substrate 602 can be formed thin.

  In this modification, the signal output unit 604, the sensor unit 606, and the transparent insulating film 610 are formed in order on the substrate 602, and the scintillator 608 is attached to the substrate 602 using an adhesive resin having low light absorption. Thus, the radiation detector 600 is formed.

  In the radiation detector 600 according to the above-described modification, the photoelectric conversion film 616 is made of an organic photoconductor, and the active layer 632 of the TFT 624 is made of an organic semiconductor material. The part 604 hardly absorbs the radiation 16. Thereby, the fall of the sensitivity with respect to the radiation 16 (refer FIG.1, FIG.2, FIG.4 and FIG.16) can be suppressed.

  Both the organic semiconductor material constituting the active layer 632 of the TFT 624 and the organic photoconductor constituting the photoelectric conversion film 616 can be formed at a low temperature. Therefore, the substrate 602 can be formed of a plastic resin, aramid, or bionanofiber that absorbs less radiation 16. Thereby, the fall of the sensitivity with respect to the radiation 16 can be suppressed further.

  Further, for example, the radiation detector 600 is disposed in the casings 34a to 34c (see FIGS. 5A to 7A, FIGS. 8 to 12, FIGS. 20 to 23B, and FIGS. 25A to 26B), and the substrate 602 is rigid. When formed of high plastic resin, aramid, or bio-nanofiber, the rigidity of the radiation detector 600 itself can be increased, so that the casings 34a to 34c can be formed thin. Further, when the substrate 602 is formed of a highly rigid plastic resin, aramid, or bionanofiber, the radiation detector 600 itself has flexibility, so that even when an impact is applied to the casings 34a to 34c, the radiation detector 600 is Hard to break.

  In FIG. 32, as described above, as an example, as described above, the light emitted from the scintillator 608 is a sensor unit 606 (photoelectric sensor) positioned on the side opposite to the side where the radiation irradiation device 18 (see FIGS. 1 and 16) is positioned. A PSS radiation detector 600 that reads a radiation image after being converted into electric charge by a conversion film 616) is illustrated.

  The radiation detector 600 is not limited to this configuration, and may be configured as an ISS radiation detector. In this case, the substrate 602, the signal output unit 604, the sensor unit 606, and the scintillator 608 are stacked in this order along the irradiation direction of the radiation 16, and the light emitted from the scintillator 608 is sensor on the side where the radiation irradiation device 18 is located. The radiation image is read by converting into electric charges in the unit 606. In general, the scintillator 608 emits light more strongly on the irradiation surface side of the radiation 16 than on the back side. Therefore, the radiation detector 600 configured by the ISS system is more scintillator than the radiation detector 600 configured by the PSS system. The distance until the light emitted in 608 reaches the photoelectric conversion film 616 can be shortened. Thereby, since the diffusion / attenuation of the light can be suppressed, the resolution of the radiation image can be increased.

  In the present embodiment, the two radiation conversion panels 172a and 172c and the one radiation conversion panel 172b are not the same type of panel, but, for example, (1) a thin panel using plastic and organic materials; Combination with normal thickness panel, (2) Combination of panel using GOS scintillator and panel using CsI scintillator, or (3) Combination of ISS panel and PSS panel, etc. There may be a mixture of panel types. Therefore, the magnification (the distance between the radiation source 264 and the panel) may be different or the density of the radiation image (the panel sensitivity) may be different depending on the type of the panel. In such a case, after performing image correction processing corresponding to the type of panel on the radiation images obtained by the radiation conversion panels 172a to 172c, these radiation images are connected to form a single long sheet. It is necessary to obtain an image.

  Therefore, the connection order information generation unit 250 includes the types of radiation conversion panels 172a to 172c (materials of the scintillators 150a to 150c and 608, materials of the photoelectric conversion layers 152a to 152c or the photoelectric conversion film 616, materials of the TFTs 210a to 210c and 624, Information regarding the materials of the substrates 178a to 178c, 602, the type of the ISS system or the PSS system) may be included in the connection order information, and the connection order information may be transmitted to the console 22. Accordingly, the image processing unit 288 of the console 22 performs image correction processing on the radiation images obtained by the radiation conversion panels 172a to 172c based on the connection order information including information on the types of the radiation conversion panels 172a to 172c. After being performed, the three radiographic images after the image correction processing can be connected to generate one long image.

  Moreover, when using the scintillator which consists of CsI (Tl) of columnar crystal structure, it is desirable to use it as the scintillator 150b of the radiation conversion panel 172b. This is because the radiation source 264 irradiates the subject 14 with radiation 16 having a certain extent, so that the columnar crystal structure scintillator is separated from the central axis of the radiation 16 (for example, the radiation conversion panel 172a or 172c). If used, the radiation 16 is obliquely incident on the columnar portion. As a result, the scintillator emits light between the columns, which may cause crosstalk.

10A to 10C ... Radiation imaging system 14 ... Subject 16 ... Radiation 20A-20D ... Radiation imaging apparatus 22 ... Console 30a-30c ... Radiation detection unit 32 ... Connectors 34a-34c ... Housings 36a-36c ... Surfaces 40a-40c ... Imaging regions 50a to 50c, 52a to 52c, 54a to 54c, 56a to 56c ... Side surfaces 58a to 58c, 60a to 60c, 350 to 356 ... Blocks 120a to 120c, 122a to 122c ... Stepped portions 124a to 124c, 126a to 126c ... Connection terminals 148a to 148c ... irradiation surface 156 ... imaging surfaces 172a to 172c ... radiation conversion panels 192a to 192c ... cassette control units 196a to 196c ... control units 198a to 198c ... panel units 250a to 250c ... connection order information generation unit 288 ... image Processing unit 34 , 340d, 340e, 342,342d, 342e, 348 ... hinge 370a~370c, 374a~374c, 379b ... recess 372a~372c, 375a, 376a~376c ... protrusions 400a to 400c ... shielding member

Claims (19)

In a radiographic imaging apparatus, comprising: a radiation conversion panel capable of converting radiation into a radiation image; a plurality of radiation detection units including a panel housing portion that houses the radiation conversion panel; and a coupling portion that couples the radiation detection units.
Each panel accommodating portion is provided with a front surface through which the radiation can be transmitted and a back surface opposite to the front surface,
The surface of each panel housing portion is an irradiation surface irradiated with the radiation that has passed through the subject, and the irradiation region of the radiation on the irradiation surface is an imaging region that can be converted into the radiation image.
Each said panel accommodating part is the 1st panel accommodating part which has a 1st irradiation surface, and the 2nd panel accommodating part which has a 2nd irradiation surface,
By connecting the panel accommodating portions by the connecting portion so that a part of each of the radiation conversion panels overlaps and alternately repeating in order of the first irradiation surface and the second irradiation surface, A radiographic imaging apparatus characterized in that an imaging plane of the radiographic imaging apparatus configured to include each imaging area is maintained in a substantially flat shape. The apparatus of claim 1.
Between the outer peripheral portion of the front surface of each panel housing portion and the outer peripheral portion of the back surface, side surfaces of the respective panel housing portions are provided, respectively.
The connecting portion is a stepped portion formed on a side surface of each panel housing portion,
The radiographic image capturing apparatus according to claim 1, wherein the panel accommodating portions are connected by fitting the step portions. The apparatus of claim 2.
Each of the panel housing portions is a substantially rectangular housing,
A part of the side portion of each casing is configured as a block that is removable from the casing, respectively.
The radiographic image capturing apparatus according to claim 1, wherein the step portions are formed by removing the block from the housing. The apparatus of claim 2.
Each of the panel housing portions is a substantially rectangular housing,
A part of the side portion of each casing is configured as a block that can rotate with respect to the casing,
The radiographic image capturing apparatus according to claim 1, wherein the step portions are formed by rotating the block with respect to the housing. The device according to any one of claims 2 to 4,
Of the step portion of the first panel housing portion and the step portion of the second panel housing portion, one step portion is provided with a convex portion, and the other step portion is a recess that fits into the convex portion. A radiographic imaging apparatus characterized in that is provided. In the apparatus of any one of Claims 2-5,
In the first panel housing portion, the surface close to the stepped portion of the first panel housing portion is the back surface, and the surface facing the back surface and spaced from the stepped portion is the first irradiation surface. Yes,
In the second panel housing portion, a surface close to the stepped portion of the second panel housing portion is the second irradiation surface, and faces the second irradiation surface and is separated from the stepped portion. A radiographic imaging apparatus characterized in that the surface is a back surface. In the apparatus of any one of Claims 1-6,
A radiographic imaging apparatus, further comprising: a connection order information generation unit that detects a connection order of the panel storage units connected by the connection unit and generates a detection result as connection order information. In the apparatus of any one of Claims 1-7,
Each of the radiation detection units further includes a control unit that controls the radiation conversion panel. The apparatus of claim 8.
Inside each of the panel housing portions, the radiation conversion panel, a radiation shielding member for blocking the transmission of the radiation, and the control unit are sequentially arranged from the front surface to the back surface. A radiographic imaging device. The apparatus of claim 9.
The radiographic imaging apparatus, wherein the control unit is smaller than the radiation conversion panel in a plan view. The apparatus of claim 8.
Each of the radiation detection units has a rotation mechanism capable of rotating the control unit with respect to the panel housing unit,
Each said control part is each arrange | positioned so that it may not overlap with each said panel accommodating part at the time of the irradiation of the said radiation by rotating with respect to the said panel accommodating part by the said rotation mechanism. Image shooting device. The apparatus of claim 11.
The thickness of each control unit is such that when the control unit is arranged so as not to overlap each panel housing unit by the rotation mechanism, the control unit is substantially flush with the imaging surface. A radiographic imaging device as a feature. The apparatus of claim 8.
Each said control part is arrange | positioned in places other than the said imaging area | region in the said surface, The radiographic imaging apparatus characterized by the above-mentioned. The device according to any one of claims 1 to 13,
The radiographic imaging apparatus further comprising a connecting portion that connects the panel accommodating portions connected by the connecting portion. The device according to any one of claims 1 to 14,
Each of the radiation conversion panels includes a scintillator that converts the radiation into visible light, a solid-state detection element that converts the visible light into an electrical signal indicating the radiation image, and a switching element that reads the electrical signal from the solid-state detection element. Each having a substrate on which the solid state detection element and the switching element are formed,
In at least the radiation conversion panel disposed on the radiation irradiation side, the substrate is a flexible plastic substrate, the solid-state detection element is made of an organic photoconductor, and the switching element is organic A radiographic imaging apparatus comprising a semiconductor material. The apparatus of claim 15.
A radiographic imaging apparatus, wherein the substrate, the switching element, the solid state detection element, and the scintillator made of CsI are arranged in this order along the radiation direction. A radiation image capturing apparatus comprising: a radiation conversion panel capable of converting radiation into a radiation image; a plurality of radiation detection units including a panel housing portion that houses the radiation conversion panel; and a coupling portion that couples the radiation detection units;
A control device for controlling the radiographic imaging device;
In a radiographic imaging system comprising:
Each panel accommodating portion is provided with a front surface through which the radiation can be transmitted and a back surface opposite to the front surface,
The surface of each panel housing portion is an irradiation surface irradiated with the radiation that has passed through the subject, and the irradiation region of the radiation on the irradiation surface is an imaging region that can be converted into the radiation image.
Each said panel accommodating part is the 1st panel accommodating part which has a 1st irradiation surface, and the 2nd panel accommodating part which has a 2nd irradiation surface,
By connecting the panel accommodating portions by the connecting portion so that a part of each of the radiation conversion panels overlaps and alternately repeating in order of the first irradiation surface and the second irradiation surface, A radiographic imaging system characterized in that an imaging plane of the radiographic imaging apparatus configured to include each imaging area is maintained in a substantially flat shape. The system of claim 17, wherein
The radiographic image capturing apparatus further includes a connection order information generation unit that detects a connection order of the panel storage units connected by the connection unit and generates a detection result as connection order information. Shooting system. The system of claim 18, wherein
The control device includes an image processing unit that generates an image of the subject based on a radiation image obtained by each radiation conversion panel,
Wherein the image processing part, based on the connection order information the connection order information generating unit has generated, the after correcting the respective radiation images, by combining the radiation ray image after correction to generate an image of the object A radiographic imaging system characterized by that.

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