JP5622541B2 - 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 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 order to be able to quickly display an image of a long subject, long photographing using electronic cassettes such as Patent Documents 2 and 3 is not used, instead of long photographing using a plurality of storage phosphor sheets as in Patent Document 1. desirable.

  By the way, the electronic cassette includes a control unit that controls the radiation conversion panel. Since the control unit is a component that does not contribute to the detection of radiation (conversion to a radiation image), the control unit is disposed at a location other than the imaging region in the electronic cassette so that the radiation is not irradiated.

  However, when a plurality of electronic cassettes are connected so that a part of the imaging region overlaps each other, the control unit overlaps with the imaging region of other electronic cassettes in plan view, and as a result, during long imaging, radiation is emitted from the control unit. , The control unit is degraded by the radiation, and the control unit may be reflected in a radiographic image.

  In the technique disclosed in Patent Document 3, radiation (imaging) is performed on the subject at each position where the electronic cassette is moved. Therefore, the subject must maintain the same posture for a long time from the start of imaging to the end of imaging. I must. 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 prevents deterioration of the control unit due to irradiation of radiation and reflection of the control unit in a radiographic image without overlapping the control unit on an imaging region. It is an object of the present invention to provide a radiographic image capturing apparatus and a radiographic image capturing system that can perform long imaging.

A radiation image capturing apparatus according to the present invention includes a radiation conversion panel capable of converting radiation into a radiation image, a panel storage unit that stores the radiation conversion panel, and a plurality of radiation detection units that include a control unit that controls the radiation conversion panel. Unit,
A connecting part for connecting the radiation detection units;
Have
The connecting portion is characterized in that the panel accommodating portions are sequentially connected so that a part of each of the radiation conversion panels overlaps and the control portions do not overlap.

The radiation image capturing system according to the present invention includes a plurality of radiation conversion panels that can convert radiation into radiation images, a panel storage unit that stores the radiation conversion panel, and a control unit that controls the radiation conversion panel. A radiographic imaging device having a radiation detection unit and a connecting portion for connecting the radiation detection units;
A control device for controlling the radiographic imaging device;
With
The connecting portion is characterized in that the panel accommodating portions are sequentially connected so that a part of each of the radiation conversion panels overlaps and the control portions do not overlap.

  According to these inventions, the connecting portion sequentially connects the panel accommodating portions so that the radiation conversion panels partially overlap and the control portions do not overlap. That is, even if a part of the imaging region overlaps, the control unit that does not contribute to the detection of radiation (conversion to a radiation image) and the imaging region of each radiation detection unit do not overlap. As a result, it is possible to perform long imaging while preventing deterioration of the control unit due to radiation irradiation and reflection of the control unit on the radiation image without overlapping the control unit on the imaging region. Become. In addition, since each radiation detection unit is connected by the connecting portion to form one radiation image capturing apparatus, it is possible to perform long image capturing with one irradiation of the subject, and to shorten the image capturing time. Can also be realized.

  In the present invention, for example, when one panel housing part and the other panel housing part are connected by a connecting part, the other panel housing part side in the radiation conversion panel housed in the one panel housing part Part of the panel and the part on the one panel housing part side of the radiation conversion panel housed in the other panel housing part overlap, and the one panel housing part does not overlap each other. And the other panel housing portion, the respective radiographic images respectively 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 portion of the radiation image.

  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.

  Here, each panel housing portion is provided with a front surface through which the radiation can be transmitted and a back surface opposite to the front surface, and the surface of each panel housing portion is irradiated with the radiation transmitted through the subject. The radiation area on the radiation surface is an imaging area that can be converted into the radiation image, and the connecting portion connects one panel housing portion and the other panel housing portion. In this case, the other panel housing portion side on the back surface of the one panel housing portion is connected to the one panel housing portion side on the surface of the other panel housing portion.

  Thus, when the radiographic images are combined to obtain a single long image, it is possible to reliably prevent an image from being lost at the connection portion of the radiographic images.

  Further, a side surface of each panel housing portion is provided between the outer peripheral portion of the front surface and the outer peripheral portion of the back surface of each panel housing portion, and the connecting portion is provided on one side surface side of the front surface. A convex portion and a concave portion provided on the other side surface facing the one side surface on the back surface, a concave portion provided on the back surface of the one panel housing portion, and the other panel housing portion. The one panel housing portion and the other panel housing portion side may be connected by fitting a convex portion provided on the surface.

  Thereby, each said panel accommodating part can be connected reliably and easily. In addition, since each said radiation detection unit can perform imaging | photography individually, if the said convex part is provided in the said surface and the said concave part is provided in the said back surface, it is the case where it uses independently. It is possible to prevent the panel housing portion from rattling.

  In addition, if the length of each control unit at the time of connection of the panel storage units is set to be shorter than the width of the panel storage units in plan view or side view, the panel storage units are securely connected. can do.

  And as specific arrangement | positioning of the said control part in each said radiation detection unit, and the relationship between the said control part and the said panel accommodating part, it is desirable that it is either of following (1)-(4).

  (1) Each said control part is an area | region other than the said imaging | photography area | region in the surface of the said panel accommodating part, and between the said convex part and the said recessed part, or the said convex part and said other side surface by side view. When the concave portion of the one panel housing portion and the convex portion of the other panel housing portion are fitted together, the other panel housing portion side of the one panel housing portion is It contacts the control part arranged in the panel housing part.

  Thereby, simultaneously with the fitting of the concave portion and the convex portion, the one panel housing portion and the control portion of the other panel housing portion are brought into contact with each other and positioned. Therefore, it is possible to reliably avoid the overlap between the control units and the imaging regions, and it is possible to accurately connect the panel storage units.

  (2) Each of the control units is disposed between a side surface of the panel housing portion and between the convex portion and the other side surface in a side view, and the concave portion of the one panel housing portion and the other side When the convex part of the panel housing part is fitted, the control part arranged in the one panel housing part comes into contact with the control part arranged in the other panel housing part.

  Thereby, simultaneously with the fitting of the concave portion and the convex portion, the control portion of the one panel housing portion and the control portion of the other panel housing portion are contacted and positioned. Even in this case, it is possible to reliably avoid the overlap between the control units and the imaging regions, and it is possible to accurately connect the panel storage units.

  At that time, each of the radiation detection units includes a first control unit disposed on a side surface of the panel housing unit, and a second control disposed on a side surface opposite to the side surface on which the first control unit is disposed. A first control portion disposed in the one panel housing portion when the concave portion of the one panel housing portion and the convex portion of the other panel housing portion are fitted to each other. The first control unit disposed in the other panel housing unit abuts, the second control unit disposed in the one panel housing unit, and the second control unit disposed in the other panel housing unit. Two control units may be in contact with each other.

  In this case, since each of the radiation detection units includes two control units (the first control unit and the second control unit), when the concave portion and the convex portion are fitted, The first control units are positioned in contact with each other, and the second control units are also positioned in contact with each other. Accordingly, the connection of the panel housing portions can be performed with higher accuracy.

  (3) Each of the radiation detection units has a rotation mechanism capable of rotating the control unit with respect to the panel housing unit, and each of the control units is moved relative to the panel housing unit by the rotation mechanism. And rotating so that they do not overlap with each of the panel housing portions when irradiated with the radiation.

  Thereby, it is possible to reliably prevent the respective control units and the respective imaging regions from overlapping at the time of shooting.

  In this case, the one side surface side and the other side surface side of each control unit are each configured as a block that is detachable from the control unit, and by removing each block from the control unit, the one side surface side The concave portion of the panel housing portion and the convex portion of the other panel housing portion can be fitted.

  As described above, since the fitting between the concave portion and the convex portion is permitted by removing the block from the respective control portions, it becomes possible to efficiently connect the respective panel housing portions.

(4) The radiation conversion panel and a radiation shielding member for blocking the transmission of the radiation are sequentially arranged from the front surface to the back surface in each panel housing portion. On the back side, the control unit is arranged, and each control unit is arranged between the convex part and the concave part in a side view, and the concave part of the one panel housing part and the other panel housing When the convex part of a part fits, the said control part and said other panel accommodating part contact | abut.

  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.

  And the said radiographic imaging apparatus may further have a connection order information generation part which detects the connection order of each said panel accommodating part connected by the said connection part, and produces | generates a detection result as connection order information.

  Since each of the panel accommodating portions is sequentially connected, the radiation obtained by referring to the connection order information when forming an image of one long subject by synthesizing the radiation images. It is possible to specify which radiation conversion panel the image is obtained from. As a result, the one long image can be efficiently formed.

  The control device includes an image processing unit that generates an image of a subject based on the radiographic images obtained by the radiation conversion panels, and the image processing unit is generated by the connection order information generating unit. After correcting each radiographic image based on the connection order information, the radiographic images after correction are combined to generate an image of the subject.

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

  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, the connecting portion sequentially connects the panel accommodating portions so that the radiation conversion panels partially overlap and the control portions do not overlap. That is, even if a part of the imaging region overlaps, the control unit that does not contribute to the detection of radiation (conversion to a radiation image) and the imaging region of each radiation detection unit do not overlap. As a result, it is possible to perform long imaging while preventing deterioration of the control unit due to radiation irradiation and reflection of the control unit on the radiation image without overlapping the control unit on the imaging region. Become. In addition, since each radiation detection unit is connected by the connecting portion to form one radiation image capturing apparatus, it is possible to perform long image capturing with one irradiation of the subject, and to shorten the image capturing time. Can also be realized.

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. 4A and 4B are perspective views of one radiation detection unit. 5A is a perspective view showing a state in which two blocks are separated from the control unit of the radiation detection unit in FIGS. 4A and 4B, and FIG. 5B is a perspective view showing a state in which the two radiation detection units are connected. is there. FIG. 6A is a cross-sectional view showing a state of a connection portion of two radiation detection units, and FIG. 6B is a side view schematically showing the radiographic image capturing apparatus of FIG. It is the top view which fractured | ruptured and illustrated some radiation detection units of FIG. It is sectional drawing along the XIII-XIII line of FIG. It is sectional drawing along the IX-IX line of FIG. 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 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. 16A and 16B are explanatory views showing other connections between the radiation detection units. It is a perspective view which shows the state of the charge process with respect to the radiation detection unit of FIG. FIG. 18A is a cross-sectional view showing a state in which one scintillator is housed in the housing, and FIG. 18B is a cross-sectional view showing a state in which two scintillators are housed in the housing. It is a block diagram of the radiographic imaging system which concerns on 2nd Embodiment. It is a top view of the radiographic imaging apparatus of FIG. It is a top view which shows the other structure of a radiographic imaging apparatus. It is a top view which shows the other structure of a radiographic imaging apparatus. It is a top view which shows the other structure of a radiographic imaging apparatus. It is a side view which shows the other structure of a 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. 26 is a schematic configuration diagram of a TFT and a charge storage unit shown in FIG. 25.

  Preferred embodiments 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 18B.

  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. In addition, since the imaging | photography stand 12 accommodates the radiographic imaging apparatus 20A, it is desirable to be comprised so that the radiation 16 can be permeate | transmitted.

  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 inside the imaging table 12, and electrically and mechanically connects three radiation detection units 30a to 30c of one type and the same shape with the radiation detection units 30a to 30c. Two connectors (connection portions) 32 are provided.

  That is, with respect to the radiation detection units 30a to 30c which are one type and the same shape of the electronic cassette, as shown in FIGS. 1 to 6B, a part of the radiation detection unit 30a and a part of the radiation detection unit 30b are overlapped. In addition to being connected, a part of the radiation detection unit 30b and a part of the radiation detection unit 30c are overlapped and connected to each other so that the radiation detection unit 30a → the radiation detection unit 30b → the radiation detection unit 30c are connected in this order. A single radiographic imaging apparatus 20A is configured by electrical and mechanical connection by two connectors 32.

  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. 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. 6B). In the radiation detection units 30a to 30c, portions where the radiation conversion panels 172a to 172c are arranged are configured as panel portions 198a to 198c. That is, in the first embodiment, the casings 34a to 34c and the insides of the casings 34a to 34c become the panel portions 198a to 198c.

  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. Further, convex portions 410a to 410c are formed on one side of the outer frame (one side on the side surfaces 54a to 54c) indicating the imaging regions 40a to 40c, respectively.

  On the other hand, on the back surfaces 42a to 42c facing the front surfaces 36a to 36c, the side surfaces 56a to 56c are on the inner side of the imaging regions 40a to 40c in plan view with respect to the convex portions 410a to 410c. Concave portions 412a to 412c that are formed in parallel and can be fitted to the convex portions 410a to 410c are provided (see FIGS. 3 and 6A).

  It should be noted that no guide lines or photographing areas are provided on the back surfaces 42a to 42c. That is, the radiation detection units 30a to 30c have the surfaces 36a to 36c as irradiation surfaces 148a to 148c of the radiation 16, and the radiation 16 is irradiated only from the outside to the irradiation surfaces 148a to 148c. It is an electronic cassette that can be converted into

  As shown in FIGS. 2, 3 and 6B, when the radiation detection units 30a to 30c are connected, the guide lines 38a to 38c partially overlap and the radiation conversion panels accommodated in the casings 34a to 34c. 172a to 172c also partially overlap. On the other hand, at the time of long shooting, the control units 196a to 196c and the panel units 198a to 198c (the shooting areas 40a to 40c thereof) do not overlap.

  Further, 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. ing.

  Concave portions 420a to 420c are respectively formed in the central portions of the side surfaces 50a to 50c, and handle portions 422a to 422c are disposed in the concave portions 420a to 420c (see FIG. 4A). A doctor or an engineer can grip the handle portions 422a to 422c and carry the radiation detection units 30a to 30c by rotating the proximal end portions of the handle portions 422a to 422c.

  In addition, connection terminals 124a to 124c that can be fitted to the connector 32 are disposed at the positions on the side surfaces 50a to 54c on the side surfaces 54a to 54c, respectively, while the side surfaces 50a to 50c are on the side surfaces 56a to 56c side. Are provided with connection terminals 126a to 126c that can be fitted to the connector 32, respectively.

  Hinge portions (rotating mechanisms) 415a to 415c are provided on the side surfaces 50a to 50c of the surfaces 36a to 36c, and block-like controls for controlling the radiation conversion panels 172a to 172c via the hinge portions 415a to 415c. The parts 196a to 196c are connected to the panel parts 198a to 198c (casings 34a to 34c), respectively.

In this case, the hinge portion 415a~415c has two protrusions 414a to 414c disposed respectively on the surface 36 a - 36 c, and a shaft portion 416A～416 c penetrating the two protrusions 414a to 414c. Controller 196a~196c is pivotally supported in a central portion of the shaft portion 416A～416 c between two projections 414a~414 c. In addition, the total length of the hinge portions 415a to 415c is set to be shorter than the lateral width of the imaging regions 40a to 40c (the width along the left-right direction in FIGS. 1 to 5B). That is, in the side view of FIGS. 1 and 6B and the plan view of FIG. 3, the lengths of the hinge portions 415a to 415c at the time of connecting the housings 34a to 34c are larger than the widths of the housings 34a to 34c. Therefore, the hinge portions 415a to 415c are arranged between the convex portions 410a to 410c and the concave portions 412a to 412c, respectively.

  The lateral widths of the control units 196a to 196c are set to a width that is substantially the same as the entire length of the hinge units 415a to 415c. That is, in the side view of FIGS. 1 and 6B and the plan view of FIG. 3, the horizontal widths of the control units 196a to 196c when the casings 34a to 34c are connected are the same as the hinge units 415a to 415c. It is set shorter than the width of the bodies 34a to 34c. Therefore, the control units 196a to 196c are disposed between the convex portions 410a to 410c and the concave portions 412a to 412c, respectively, in the side view of FIG. 6B.

  Further, the height of the control units 196a to 196c is such that when the control units 196a to 196c are rotated from the position of FIG. 4A to the position of FIG. 4B around the shafts 416a to 416c, the casings 34a to 34c. Are set to substantially the same height as the height from the back surfaces 42a to 42c to the upper positions of the shaft portions 416a to 416c.

  The blocks 350a to 350c are detachably attached to the side surfaces 54a to 54c of the control units 196a to 196c, while the blocks 354a to 354c are detachably attached to the side surfaces 56a to 56c of the control units 196a to 196c. (See FIGS. 4A to 5A).

  In this case, the blocks 350a to 350c are respectively provided with recesses 74a to 74c, and the manual operation portions 76a to 76c are disposed in the recesses 74a to 74c. Further, claw members 96a to 96c connected to the manual operation portions 76a to 76c are respectively disposed through the holes 98a to 98c on the control portions 196a to 196c side of the blocks 350a to 350c. Hole portions 100a to 100c that can be engaged with the claw members 96a to 96c are formed at positions facing the hole portions 98a to 98c in ˜196c.

  On the other hand, also in the blocks 354a to 354c, recesses 78a to 78c are provided so as to face the recesses 74a to 74c, respectively, and manual operation portions 80a to 80c are disposed in the recesses 78a to 78c. Also, the claw members 108a to 108c connected to the manual operation units 80a to 80c penetrate the holes 110a to 110c on the control units 196a to 196c side of the blocks 354a to 354c, similarly to the claw members 96a to 96c described above. Thus, holes 112a to 112c that can be engaged with the claw members 108a to 108c are formed at locations facing the holes 110a to 110c in the control portions 196a to 196c, respectively.

  Further, in the control units 196a to 196c, concave portions 130a to 130c are respectively formed in the central portions of the side surfaces opposed to the side surfaces pivotally supported by the shaft portions 416a to 416c, and handle portions are formed in the concave portions 130a to 130c. 132a to 132c are disposed. A doctor or an engineer can easily rotate the control portions 196a to 196c around the shaft portions 416a to 416c by rotating the proximal end side of the handle portions 132a to 132c to grip the handle portions 132a to 132c. It can be moved.

  Further, on the side surfaces of the control units 196a to 196c, in addition to the recesses 130a to 130c and the handle units 132a to 132c, an input terminal of an AC adapter for charging the radiation detection units 30a to 30c from an external power source 160a to 160c and USB (Universal Serial Bus) terminals 162a to 162c as interface means capable of transmitting and receiving information between external devices, and a memory card 164 such as a PC card (see FIG. 12) Card slots 166a to 166c and power switches 168a to 168c for activating the radiation detection units 30a to 30c are provided, respectively.

  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, as shown in FIG. 4A, control units 196a to 196c are arranged on the surfaces 36a to 36c of the casings 34a to 34c, and blocks 350a to 350c and 354a to 354c are attached to the control units 196a to 196c, respectively. In this state, the doctor or engineer rotates the control units 196a to 196c around the shafts 416a to 416c to the position shown in FIG. 4B while gripping the handle units 132a to 132c. Thereby, control part 196a-196c is arrange | positioned on the outer side of panel part 198a-198c by planar view. Note that the connection terminals 124a to 124c and 126a to 126c cannot be temporarily visually recognized from the outside due to the rotation of the control units 196a to 196c.

  Next, the doctor or engineer separates blocks 350a to 350c and 354a to 354c from the control units 196a to 196c, respectively (see FIG. 5A). Thereby, the connection terminals 124a to 124c and 126a to 126c are exposed again to the outside and become visible.

  In this state, the doctor or engineer fits the concave portion 412a of the housing 34a and the convex portion 410b of the housing 34b and also fits the concave portion 412b of the housing 34b and the convex portion 410c of the housing 34c ( FIG. 5B and FIG. 6A).

  The housing 34a and the housing 34b are connected by fitting the concave portion 412a and the convex portion 410b, and a step is generated at the connecting portion, and the housing 34b and the convex portion 410c are fitted by fitting. The housing 34c is connected, and a step is generated at the connecting portion. At that time, the side surface 56a of the casing 34a constituting the step portion between the casing 34a and the casing 34b and the side portion of the hinge portion 415b are in contact (contact), while the casing 34b and the casing 34 The side surface 56b of the housing 34b constituting the step portion with respect to 34c and the side portion of the hinge portion 415c come into contact (contact) (see FIGS. 2 and 6B).

  Therefore, the back surface 42a of the housing 34a and the front surface 36b of the housing 34b are fitted (coupled) reliably without any gaps while being positioned with respect to each other. Further, the back surface 42b of the housing 34b and the front surface 36c of the housing 34c are also fitted (coupled) securely without any gaps while being positioned with respect to each other.

  Next, the doctor or technician fits the substantially U-shaped connector 32 to the connection terminals 126a and 124b, and also fits another connector 32 to the connection terminals 126b and 124c.

  By assembling in this way, in the radiographic imaging apparatus 20A, one type of electronic cassette is 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 in FIGS. The radiographic imaging device 20A is connected in order, and the upper surface of the radiographic imaging device 20A is in the order of the surface 36a → the surface 36b → the surface 36c (first irradiation surface).

  Further, as described above, the control units 196a to 196c are arranged outside the panel units 198a to 198c in a plan view by the hinge units 415a to 415c (see FIG. 2 and FIG. 3). In 20A, long imaging | photography with respect to the to-be-photographed object 14 is performed by not overlapping the imaging | photography area | regions 40a-40c and the imaging | photography surface 156, and control part 196a-196c, but overlapping and connecting a part of radiation detection unit 30a-30c. Can be made possible.

  Furthermore, when the radiation 16 is irradiated on the upper surface of the radiographic image capturing apparatus 20A via the imaging table 12 on which the subject 14 is lying (see FIGS. 1 and 2), the surfaces 36a to 36c are irradiated with the radiation 16. In addition to the surfaces 148a to 148c, 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 imaging device 20A. As described above, since the imaging surface 156 and the control units 196a to 196c are not overlapped, the control unit 196a to 196c is not irradiated with the radiation 16, and as a result, the control unit 196a to 196c by the radiation 16 is not irradiated. Degradation and reflection of the control units 196a to 196c in the radiation image can be avoided.

  As shown in FIG. 6B, radiation conversion panels 172 a to 172 c that have scintillators 150 a to 150 c and photoelectric conversion layers 152 a to 152 c inside the casings 34 a to 34 c and convert the radiation 16 into a radiation image. Each is housed.

  The imaging regions 40a to 40c substantially coincide with the scintillators 150a to 150c (and the photoelectric conversion layers 152a to 152c) in plan view (see FIG. 7). In addition, as described above, the convex portions 410a to 410c are formed on one side of the guide lines 38a to 38c constituting the imaging regions 40a to 40c, and the concave portions 412a to 412 are formed at positions inside the imaging regions 40a to 40c in a plan view. 412c is provided.

  Therefore, when the concave portion 412a and the convex portion 410b are fitted, a part of the radiation conversion panel 172b on the side of the radiation conversion panel 172b and a part of the radiation conversion panel 172b on the side of the radiation conversion panel 172a are (in plan view). The casing 34a and the casing 34b are connected so as to overlap each other. Further, when the concave portion 412b and the convex portion 410c are fitted, a part of the radiation conversion panel 172b on the side of the radiation conversion panel 172c and a part of the radiation conversion panel 172c on the side of the radiation conversion panel 172b are (in plan view). The casing 34b and the casing 34c are connected so as to overlap each other.

  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 FIGS. 7 to 9, inside the control units 196a to 196c, there are power supply units 190a to 190c such as batteries for supplying power to the respective units in the radiation detection units 30a to 30c, and radiation conversion panels 172a to 172c. Is capable of wirelessly transmitting / receiving signals between the cassette control units 192a to 192c for controlling the console 22 and the console 22, and also capable of transmitting / receiving signals to / from other radiation detection units via the connector 32. Parts 194a to 194c are arranged. The control units 196a to 196c and the panel units 198a to 198c (casings 34a to 34c) transmit and receive signals via cables (not shown) penetrating the protruding portions 414a to 414c and the shaft portions 416a to 416c, for example. It has been broken.

  On the other hand, inside the casings 34a to 34c constituting the panel portions 198a to 198c, the shock absorbing members 170a to 170c, the radiation conversion panels 172a to 172c, and the shock absorbing members are directed from the back surfaces 42a to 42c toward the front surfaces 36a to 36c. 174a to 174c are sequentially stacked.

  The impact absorbing members 170a to 170c absorb (relax) the impact caused by the load when a load is applied to the casings 34a to 34c from the outside. When the radiation detection units 30a to 30c are used alone, the shock absorbing members 174a to 174c absorb (relax) the shock caused by the load when the load is applied from the subject 14 to the surfaces 36a to 36c.

  The radiation conversion panels 172a to 172c are formed with light transmissive and radiation transmissive substrates 178a to 178c such as glass substrates, transparent electrodes, and the like from the shock absorbing members 170a to 170c toward the shock absorbing members 174a to 174c. The transparent TFT layers 176a to 176c, the photoelectric conversion layers 152a to 152c, and the scintillators 150a to 150c are stacked in this order.

  The scintillators 150a to 150c temporarily convert the radiation 16 irradiated from the surfaces 36a to 36c through the impact absorbing members 174a to 174c into visible light.

  The scintillators 150a to 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 image capturing apparatus 20A, the scintillators 150a to 150c of the radiation detection unit that captures a specific region to be noticed out of a long imaging region (the entire body of the subject 14). 150c may be composed of CsI, and the scintillators 150a to 150c of other radiation detection units may be composed of GOS.

  The photoelectric conversion layers 152a to 152c use the solid detection elements (hereinafter referred to as pixels) 200a to 200c (see FIG. 10) made of a material 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 to 176c are thin film transistors (TFTs) in which signal lines 204a to 204c or signal lines 206a to 206c (see FIG. 11) are connected to one signal electrode, and gate lines 202a to 202c are connected to gate electrodes. 210a to 210c are arranged in a matrix and can transmit the radiation 16 and the visible light.

  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 11 sequentially arrange scintillators 150a to 150c and photoelectric conversion layers 152a to 152c using the pixels 200a to 200c with respect to the surfaces 36a to 36c. It is configured as a PSS radiation detector.

  8 and 9, the indirect conversion type radiation conversion panels 172a to 172c are illustrated, but 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. 7 to 9), 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, the readout circuit units 184a to 184c, and 186a to 186c, and the casings 34a to 34c that house the radiation conversion panels 172a to 172c, Panel portions 198a to 198c that convert to an image and output are configured.

  As schematically shown in FIG. 10, in each of the radiation detection units 30a to 30c, in the radiation conversion panels 172a to 172c, as described above, a large number of pixels 200a to 200c are TFT layers 176a to 176c (FIGS. 8 and 9) and a plurality of gate lines 202a to 202c for supplying control signals from the drive circuit portions 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.

  Note that the electric signals of the odd-numbered pixels 200a to 200c are output to the readout circuit units 184a to 184c through the signal lines 204a to 204c from the upper side to the lower side of FIG. 10, 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. 8 and 9) in which the respective pixels 200a to 200b made of a substance 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. 11 include gate lines 202a to 202c extending in parallel to the column direction, 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. 7 and 12) 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. 12, 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 synchronize the radiation detection units 30a to 30b at the time of imaging by transmitting and receiving synchronization control signals to and from other radiation detection units via the connector 32. 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 connector 32, thereby connecting the radiation detection units 30a to 30c in the radiographic imaging apparatus 20A. Is identified (detected), and connection order information indicating the specified connection order and cassette ID information of each radiation detection unit in the connection order is generated.

As shown in FIGS. 1, 2 and 6B, in the radiographic imaging apparatus 20A, a part of each of the radiation detection units 30a to 30c is overlapped and sequentially connected to each other, thereby connecting the radiation detection units 30a to 30c. Then, the heights are different from each other along the vertical direction. Therefore, the said connection order number information, together with the linking order, the height in the vertical direction of the order (e.g., the connection order is # 1 for radiation detection unit 30a, information indicating the highest order) be included Good.

  As shown in FIG. 13, 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. 13, 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, since a part between adjacent radiation conversion panels overlap each other, when the radiation image is connected, a part of the image overlaps, but by performing the image correction process in advance, A composite image with uniform image quality (a long image of the subject 14 corresponding to the long image) can be obtained.

  The long captured image thus obtained and each radiation image used for image synthesis 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, a load-bearing glass plate that is light transmissive and can withstand the load of the subject 14 is disposed on the upper surface of the imaging table 12 so that the irradiation light can be projected onto the imaging surface 156. Is desirable.

Here, 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 addition, it is desirable that a hole is formed on the upper surface of the imaging table 12 so that the transmission wave 272 and the reflected wave 274 can pass therethrough.

  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. 13) 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, a doctor or an engineer controls the control units 196a to 196c with respect to each of the radiation detection units 30a to 30c while holding the handle portions 132a to 132c with the shaft portions 416a to 416c as the center. To the position of FIG. 4B. Thereby, the control units 196a to 196c are arranged outside the panel units 198a to 198c.

  Next, the doctor or engineer displaces the manual operation units 76a to 76c and moves the claw members 96a to 96c in the rotated control units 196a to 196c, thereby moving the claw members 96a to 96c and the hole 100a. ˜100c is released, and the blocks 350a to 350c are separated from the controllers 196a to 196c (see FIG. 5A). Similarly, the doctor or engineer disengages the nail members 108a to 108c and the holes 112a to 112c by moving the nail members 108a to 108c by displacing the manual operation portions 80a to 80c. Thus, the blocks 354a to 354c are separated from the control units 196a to 196c.

  In step S22, the doctor or engineer fits the back surface 42a of the housing 34a and the front surface 36b of the housing 34b so that the concave portion 412a of the housing 34a and the convex portion 410b of the housing 34b are fitted. Then, the back surface 42b of the housing 34b and the front surface 36c of the housing 34c are fitted so that the concave portion 412b of the housing 34b and the convex portion 410c of the housing 34c are fitted (see FIGS. 5B and 6A). As a result, the side surface 56a of the housing 34a and the side surface 54b side of the hinge portion 415b come into contact with each other, and the side surface 56b of the housing 34b and the side surface 54c side of the hinge portion 415c come into contact with each other. The front surface 36b of the housing 34b is connected without a gap in a positioned state, and the back surface 42b of the housing 34b and the front surface 36c of the housing 34c are also connected without a gap in a positioned state.

  Next, the doctor or technician fits the connector 32 to the connection terminals 126a and 124b, and fits another connector 32 to the connection terminals 126b and 124c.

  As described above, the concave portion 412a and the convex portion 410b, the concave portion 412b and the convex portion 410c are fitted, and the side surface 56a and the hinge portion 415b, and the side surface 56b and the hinge portion 415c are brought into contact with each other. After sequentially connecting the radiation detection units 30a to 30c, the connector 32 is further fitted to the connection terminals 124b, 124c, 126a, and 126b, thereby forming the imaging surface 156 on the irradiation surfaces 148a to 148c and the imaging region 40a. ˜40c and the imaging surface 156 and the control units 196a to 196c can be configured as one radiographic imaging device 20A (see FIGS. 1 to 3 and 6B).

  In step S <b> 23, the doctor or engineer places the radiographic image capturing apparatus 20 </ b> A on the imaging table 12 and lies the subject 14 on the imaging table 12, and then turns on the power switches 168 a to 168 c. Thereby, the power supply to each part of the radiation detection units 30a to 30c is started from the power supply units 190a to 190c (see FIGS. 7 and 12).

  In step S24, the connection order information generation units 250a to 250c transmit and receive the cassette ID information stored in the cassette ID memories 244a to 244c to and from the adjacent radiation detection units via the connector 32. Identify the radiation detection unit to be used. 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. 13) 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. 14 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. 13).

  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. 12) 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. 10 and 11). ) 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 (FIGS. 6B to 11) in the radiation detection units 30a to 30c. To see).

  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 for the subject 14 is completed, the doctor or the engineer releases the subject 14 from the photographing, and power switches 168a to 168c of the radiation detection units 30a to 30c (FIGS. 1, 4B, and 12). 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 124 b, 124 c, 126 a, and 126 b after removing the radiation image capturing apparatus 20 </ b> A from the imaging table 12, and separates the radiation detection units 30 a to 30 c from each other. Release the connected state. Thereafter, the doctor or engineer attaches the blocks 350a to 350c and 354a to 354c to the control units 196a to 196c, respectively, and then controls the shaft units 416a to 416c as the center while holding the handle units 132a to 132c. The parts 196a to 196c are rotated from the position of FIG. 4B to the position of FIG. 4A.

  As described above, according to the radiographic image capturing system 10A and the radiographic image capturing apparatus 20A according to the first embodiment, the radiation conversion panels 172a to 172c partially overlap and the controllers 196a to 196c do not overlap. As described above, the casings 34a to 34c are sequentially connected. That is, even if a part of the imaging regions 40a to 40c overlaps, the control units 196a to 196c that do not contribute to the detection of the radiation 16 (conversion to the radiation image), and the imaging regions 40a to 40c of the radiation detection units 30a to 30c, To avoid overlapping. Thereby, without superimposing control part 196a-196c on imaging region 40a-40c (imaging surface 156), degradation of control part 196a-196c by irradiation of radiation 16, or reflection of control part 196a-196c to a radiographic image is carried out. This makes it possible to perform long shooting. Further, since each of the housings 34a to 34c is connected using the convex portions 410a to 410c and the concave portions 412a to 412c to constitute one radiographic image capturing apparatus 20A, the subject 14 is irradiated with a single radiation 16 for a long time. It is possible to carry out a length photography and to shorten the photographing time.

  In the first embodiment, for example, when one casing and the other casing are connected by the convex portions 410a to 410c and the concave portions 412a to 412c, the other in the radiation conversion panel accommodated in the one casing. One housing and the other so that each control unit 196a to 196c does not overlap, while a part on the other side of the housing and a part on one side of the radiation conversion panel housed in the other housing overlap. (See FIG. 1 to FIG. 3 and FIG. 6B), the radiation images respectively obtained by the radiation conversion panels 172a to 172c are combined to form one long subject 14. When obtaining the radiographic image, it is possible to prevent the image at the connection portion of the radiographic images from being lost.

  Moreover, if the horizontal width of each control part 196a-196c at the time of connection of each housing | casing 34a-34c is set shorter than the horizontal width of each housing | casing 34a-34c by planar view or side view, each housing | casing 34a-34c Can be reliably connected.

  In addition, each radiation detection unit 30a-30c mentioned above is an electronic cassette which can perform normal imaging | photography independently, respectively, In 1st Embodiment, such several electronic cassette is made into convex part 410a-410c and convex part 410a-410c. Each effect mentioned above is acquired by connecting with crevice 412a-412c.

  The convex portions 410a to 410c are provided on the front surfaces 36a to 36c as the irradiation surfaces 148a to 148c of the casings 34a to 34c, while the concave portions 412a to 412c are provided on the back surfaces 42a to 42c side. Since each housing | casing 34a-34c is connected by fitting 410a-410c and recessed part 412a-412c, when combining each radiographic image and obtaining one elongate image, each radiation | emission is carried out. It is possible to reliably prevent the image from being lost at the image connection location, and to reliably and easily connect the housings 34a to 34c.

  In addition, by providing the convex portions 410a to 410c on the front surfaces 36a to 36c and providing the concave portions 412a to 412c on the back surfaces 42a to 42c, the housings 34a to 34c when the radiation detection units 30a to 30c are used alone are used. The rattling of 34c can be prevented.

  Further, each of the radiation detection units 30a to 30c includes hinge portions 415a to 415c that can rotate the control portions 196a to 196c with respect to the casings 34a to 34c, respectively, and each of the control portions 196a to 196c includes a hinge portion 415a. By rotating with respect to the casings 34a to 34c by ˜415c, they are arranged so as not to overlap with the respective casings 34a to 34c when the radiation 16 is irradiated. Thereby, it is possible to reliably prevent the respective control units 196a to 196c and the respective imaging regions 40a to 40c (imaging surface 156) from overlapping at the time of imaging.

  In this case, the respective control units 196a to 196c are provided with blocks 350a to 350c and 354a to 354c which are removable from the respective control units 196a to 196c, and the respective blocks 350a to 350c, 354a to 354a to 354c are provided from the respective control units 196a to 196c. By removing 354c, the projections 410a to 410c and the recesses 412a to 412c can be fitted (allowed), so that the casings 34a to 34c can be efficiently connected.

  Furthermore, the connection order information generation parts 250a-250c generate | occur | produce the connection order etc. of each housing | casing 34a-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.

  Moreover, since each housing | casing 34a-34c is electrically and mechanically connected by the connector 32, while transmitting / receiving the signal between each radiation detection unit 30a-30c, it becomes possible each housing | casing 34a. -34c will be connected reliably.

  In the above description, the case where the radiographic imaging device 20A is accommodated in the imaging table 12 has been described. However, if the casings 34a to 34c are thin and flexible enough, the subject 14 can be used. It is also possible to directly arrange the radiographic image capturing apparatus 20A between the radiographing table 12 and the imaging table 12. In this case, the level difference between the casings 34a to 34c described above is reduced, so that the sense of discomfort felt by the subject 14 at the time of shooting can be alleviated.

  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.

  Further, if there is a specific part to be noticed, it is determined that the specific part is imaged by the radiation detection unit 30b, and the scintillator 150b of the radiation detection unit 30b is configured by 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. In addition, as described above, if the connection order of the radiation detection units 30a to 30c and the height order in the vertical direction are known in advance, the connection order information is registered in the connection order information management unit 294 in advance. Thus, it is possible to inspect whether or not the actual connection state is the desired connection state on the console 22 side, and it is possible to reliably perform long photographing in the desired connection 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 case where one radiation image capturing apparatus 20A is configured by sequentially connecting the three radiation detection units 30a to 30c so as to be in the order of the surface 36a → the surface 36b → the surface 36c has been described. However, 1st Embodiment is not limited to this description, A several radiation detection unit should just be connected sequentially.

  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 illustrated in FIGS. 16A to 18B can also be realized.

  FIG. 16A 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. 16B, 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, 308 to generate the magnetic flux 310, thereby generating the coil 306 resulting from the magnetic flux 310. , 308 shows a case where signals are transmitted and received by magnetic coupling. Even with the optical coupling of FIG. 16A or the magnetic coupling of FIG. 16B, signals can be transmitted and received between the radiation detection units 30a to 30c.

  FIG. 17 is a perspective view showing a charging process of the power supply units 190a to 190c (see FIG. 7) by the cradle 320 arranged at a necessary place in the medical institution.

  In this case, the radiation detection units 30 a to 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 to 190c but also the wireless communication function or the wired communication function of the cradle 320. May be. The information to be transmitted / received can include radiation images recorded in the image memories 240a to 240c of the radiation detection units 30a to 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 to 30c and the radiation images acquired from the radiation detection units 30a to 30c is displayed on the display unit 328. You may make it make it.

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

  Furthermore, in the above description, the scintillators 150a to 150c are arranged as shown in FIGS. 6B, 8 and 9, but instead of this configuration, as shown in FIG. 18A, One other scintillator 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.

  In the case of FIG. 18A, 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 configured as ISS radiation detectors. ing.

  Further, as shown in FIG. 18B, 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.

  Further, in the case of FIG. 18B, since the scintillators 150a to 150c, 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 scintillator 150a among the radiation conversion panels 172a to 172c. -150c and the photoelectric conversion layers 152a-152c are in the PSS system, while the photoelectric conversion layers 152a-152c and the scintillators 154a-154c are in the ISS system. Therefore, the radiation conversion panels 172a to 172c shown in FIG. 18B are configured as radiation detectors including both the ISS system and the PSS system.

  In the case of FIG. 18B, the scintillators 150a to 150c and 154a to 154c may be made of the same material or 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.

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 18B), with the same reference numerals, a detailed description thereof will be omitted The same shall apply hereinafter.

  As shown in FIGS. 19 and 20, in the radiographic image capturing system 10B according to the second embodiment, in the radiographic image capturing apparatus 20B, the control units 196a to 196c are regions other than the capturing regions 40a to 40c on the surfaces 36a to 36c. And it is different from the radiographic imaging system 10A according to the first embodiment in that it is disposed at each of the side surfaces 50a to 50c.

  Accordingly, the radiation detection units 30a to 30c are not provided with the hinge portions 415a to 415c, and the control portions 196a to 196c are fixed to the side surfaces 50a to 50c of the surfaces 36a to 36c. Further, the control units 196a to 196c are not provided with the blocks 350a to 350c and 354a to 354c.

  In this case, when the concave portion 412a and the convex portion 410b and the concave portion 412b and the convex portion 410c are fitted, the side surface 56a and the control unit 196b come into contact with each other, and the side surface 56b and the control unit 196c come into contact with each other. The back surface 42a of the body 34a and the front surface 36b of the housing 34b, and the back surface 42b of the housing 34b and the front surface 36c of the housing 34c are connected without any gaps in a positioned state.

  Thus, each housing | casing 34a-34c can be accurately connected only by making the recessed part 412a, the convex part 410b, and the recessed part 412b and the convex part 410c each fit. Even in this case, since the control units 196a to 196c do not overlap the imaging surface 156 (imaging regions 40a to 40c), the control units 196a to 196c are deteriorated due to the irradiation of the radiation 16, and the control unit 196a for the radiographic image is used. It is possible to perform long shooting while reliably preventing reflection of ˜196c.

  In the second embodiment, since the control portions 196a to 196c are not rotated by the hinge portions 415a to 415c as in the first embodiment, the control portions 196a to 196c are arranged on the panel portions 198a to 198c, The substantial thickness of panel parts 198a-198c becomes large. However, in the second embodiment, since there is no complicated mechanism such as the hinge portions 415a to 415c, there is an effect that the configuration of the entire apparatus can be simplified.

  Next, a radiographic imaging system 10 </ b> C according to the third embodiment will be described with reference to FIGS. 19 and 21.

  The radiographic image capturing system 10C according to the third embodiment is different from the radiographic image capturing system 10B according to the second embodiment in that the control units 196a to 196c extend to the side surfaces 56a to 56c. In the third embodiment, the components other than the radiographic image capturing apparatus 20C are the same as those in the second embodiment, and compared with the second embodiment, the control unit 196a is a side view in FIG. Since only the difference is such that the side portions of ˜196c extend to the side surfaces 56a to 56c, the illustration of the radiographic imaging device 20C is omitted in FIG.

  In this case, when the concave portion 412a and the convex portion 410b and the concave portion 412b and the convex portion 410c are fitted, the side surface 56a and the control unit 196b come into contact with each other, and the side surface 56b and the control unit 196c come into contact with each other. Therefore, the back surface 42a of the housing 34a and the front surface 36b of the housing 34b, and the back surface 42b of the housing 34b and the front surface 36c of the housing 34c are connected with no gap in a precisely positioned state. Even in this case, the same effect as the second embodiment can be obtained.

  In addition, if the height of each control part 196a-196c is made higher than the height of each control part 196a-196c shown in FIG. 19, while the side surface 56a and the control part 196a and the control part 196b will contact | abut, side surface 56b and Since the control unit 196b and the control unit 196c come into contact with each other, it becomes possible to connect the back surface 42a and the front surface 36b and the back surface 42b and the front surface 36c without any gaps in a state of positioning with higher accuracy. .

  Next, a radiographic image capturing system 10D according to the fourth embodiment will be described with reference to FIGS.

  The radiographic image capturing system 10D according to the fourth embodiment is different from the radiographic image capturing system 10C according to the third embodiment in that the control units 196a to 196c are fixed to the side surfaces 50a to 50c.

  In this case, when the concave portion 412a and the convex portion 410b and the concave portion 412b and the convex portion 410c are fitted, the control unit 196a and the control unit 196b come into contact with each other, and the control unit 196b and the control unit 196c come into contact with each other. Accordingly, even in this case, the back surface 42a of the housing 34a and the front surface 36b of the housing 34b, and the back surface 42b of the housing 34b and the front surface 36c of the housing 34c are connected with no gap in a precisely positioned state. The same effects as in the third embodiment can be obtained.

  Next, a radiographic image capturing system 10E according to the fifth embodiment will be described with reference to FIGS.

  In a radiographic imaging system 10E according to the fifth embodiment, control units 440a to 440c having functions similar to the control units 196a to 196c are fixed to the side surfaces 52a to 52c so as to face the control units 196a to 196c. This is different from the radiographic image capturing system 10D according to the fourth embodiment.

  In this case, when the concave portion 412a and the convex portion 410b, and the concave portion 412b and the convex portion 410c are fitted, the control unit 196a and the control unit 196b, the control unit 196b and the control unit 196c, the control unit 440a and the control unit 440b, and The control unit 440b and the control unit 440c come into contact with each other. Therefore, compared with the fourth embodiment, the back surface 42a of the housing 34a and the front surface 36b of the housing 34b, and the back surface 42b of the housing 34b and the front surface 36c of the housing 34c are positioned more accurately. Connected without gaps.

  Next, a radiographic image capturing system 10F according to the sixth embodiment will be described with reference to FIG.

  In the radiographic imaging system 10F according to the sixth exemplary embodiment, the control units 196a to 196c are disposed on the back surfaces 42a to 42c of the casings 34a to 34c, and the back of the radiation conversion panels 172a to 172c inside the casings 34a to 34c. Radiation image capturing systems 10A to 10E according to the first to fifth embodiments in that radiation shielding members 400a to 400c such as lead plates that prevent transmission of radiation 16 are disposed on the back surfaces 42a to 42c side. Is different.

  In this case, the lateral widths of the control units 196a to 196c are set shorter than the lateral widths of the radiation conversion panels 172a to 172c in a side view. The control units 196a to 196c are fixed to the back surfaces 42a to 42c so as to be positioned directly below the radiation shielding members 400a to 400c.

  Here, when the concave portion 412a and the convex portion 410b, and the concave portion 412b and the convex portion 410c are respectively fitted, the control unit 196a and the casing 34b, and the control unit 196b and the casing 34c come into contact with each other. Even in this case, the back surface 42a of the housing 34a and the front surface 36b of the housing 34b, and the back surface 42b of the housing 34b and the front surface 36c of the housing 34c can be accurately positioned and connected without a gap.

  In the radiographic imaging device 20F configured as described above, the control units 196a to 196c are disposed behind the radiation conversion panels 172a to 172c via the radiation shielding members 400a to 400c, and further, the control units 196a to 196c are provided. Since it is smaller than the radiation conversion panels 172a to 172c, it is possible to reliably prevent (avoid) the possibility that the control units 196a to 196c are irradiated with the radiation 16 during imaging.

  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. 25 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, on an insulating substrate 602, a signal output unit 604 corresponding to TFT layers 176a to 176c including switching elements (see FIGS. 8, 9, 18A and 18B), and a solid state detection element. A sensor unit 606 corresponding to the photoelectric conversion layers 152a to 152c and a scintillator 608 corresponding to the scintillators 150a to 150c and 154a to 154c are sequentially stacked. A pixel portion is formed by the signal output unit 604 and the sensor unit 606. It 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. 25, for example, the upper surfaces 36a to 36c (FIGS. 2 to 5B, FIGS. 7 to 9, FIGS. 17 to 18B, and FIGS. 20 to 24) are arranged on the upper side (the side opposite to the side where the substrate 602 is located). Reference) side and the lower side is the back surfaces 42a to 42c side, and if radiation 16 enters from above, the radiation detector 600 functions as a PSS radiation detector, and the scintillator 608 phosphor is The incident radiation 16 is converted into light and emitted.

  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 when 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 without using a vapor deposition 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. 26, 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 13 and 17 to 24) that house the radiation detector 600 can be made thinner and lighter, and the radiation detection units 30a to 30c can be connected. It becomes easier, and a step at the connecting portion is less likely to occur.

  In this case, among the three radiation conversion panels 172a to 172c that partially overlap each other, at least two radiation conversion panels 172a and 172b (radiation detector 600) on the irradiation side of the radiation 16 are made of plastic flexible substrate 602. If a photoelectric conversion film 616 made of an organic photoconductor and a TFT 624 made of an organic semiconductor material are formed on the flexible substrate, respectively, the plastic and the organic material absorb almost the radiation 16. Therefore, regardless of whether the ISS system or the PSS system is used, the radiation conversion panel 172b, 172c can be made to receive the radiation 16 having as much dose as possible. Further, as described above, if plastic and organic materials are used, at least the radiation conversion panels 172a and 172b 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. The radiation detection units 30a to 30c are connected so as to overlap each other. 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 conversion panel 172b overlaps with the radiation conversion panel 172a. 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 portion or insufficient sensitivity at the overlapping portion of the radiation conversion panel 172c with the radiation conversion panel 172b. 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 172b on the irradiation side of the radiation 16 are made of a 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 panels 172b and 172c can be reduced, and the image correction process can be reduced or eliminated.

  Further, at least the radiation conversion panels 172a and 172b are made of a plastic and an organic material, and the substrate 602, the TFT 624, the photoelectric conversion film 616, and the CsI scintillator 608 are arranged in this order along the irradiation direction of the radiation 16. With the ISS panel arranged, a high-quality radiation image and one long image can be easily obtained. 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.6B and FIG. 13) 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. 4A to 6A, FIGS. 7 to 9 and FIGS. 16A to 24), and the substrate 602 is made of a highly rigid plastic resin or aramid, When formed with bionanofiber, 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.

  25, as described above, in FIG. 25, as an example, the light emitted from the scintillator 608 is positioned on the side opposite to the side where the radiation irradiation device 18 (see FIGS. 1, 13, 19, and 24) is positioned. A PSS radiation detector 600 that reads a radiation image by converting it into an electric charge by a sensor unit 606 (photoelectric conversion film 616) is shown.

  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 this embodiment, the three radiation conversion panels 172a to 172c are the same type of panel, but even if it is a single type of panel, for example, (1) a thin panel using plastic and organic materials Or a panel having a normal thickness, (2) a panel using a GOS scintillator, or a panel using a CsI scintillator, or (3) an ISS panel. Depending on whether the panel is a PSS panel or the like, the magnification (distance between the radiation source 264 and the panel) may be different, or the density of the radiation image (panel sensitivity) may be different. 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 units 250a to 250c include the types of the 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, TFTs 210a to 210c, and 624). Information regarding the material, the material 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.

  Furthermore, in this embodiment, it is not limited to the connection state shown in FIGS. 1-24, What is necessary is just a connection state that the control parts 196a-196c and the panel parts 198a-198c do not overlap. For example, the control units 196a to 196c can be alternately arranged by disposing the control unit 196b on the upper side of FIG. 3 in the housing 34b. In this case, the hinge portion 415b is provided on the upper side of FIG. 3 in the housing 34b, or the convex portions 410b, 410c, and so on can be connected to the other radiation detection units 30a, 30c with the radiation detection unit 30b turned over. By providing the recesses 412a and 412b in the casings 34a to 34c, the above-described alternate configuration can be realized.

10A to 10F ... Radiation imaging system 14 ... Subject 16 ... Radiation 20A-20F ... Radiation imaging apparatus 22 ... Console 30a-30c ... Radiation detection unit 32 ... Connectors 34a-34c ... Housings 36a-36c ... Surfaces 40a-40c ... Imaging regions 50a-50c, 52a-52c, 54a-54c, 56a-56c ... side surfaces 124a-124c, 126a-126c ... connection terminals 148a-148c ... irradiation surface 156 ... imaging surface 172a-172c ... radiation conversion panels 192a-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 units 350a to 350c, 354a to 354c ... blocks 400a to 400c ... radiation shielding members 410a to 410c ... convex Part 12a~412c ... recess 415a~415c ... hinge part

Claims (10)

A plurality of radiation conversion panels capable of converting radiation into a radiation image, a panel storage unit that stores the radiation conversion panel, and a control unit that is configured separately from the panel storage unit and controls the radiation conversion panel A radiation detection unit;
A connecting part for connecting the radiation detection units;
Have
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,
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 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.
The connecting portion is a convex portion provided on one side surface on the front surface and a concave portion provided on the other side surface facing the one side surface on the back surface,
The other panel housing portion on the back surface of the one panel housing portion by fitting a concave portion provided on the back surface of one panel housing portion and a convex portion provided on the surface of the other panel housing portion. By connecting the side and the one panel housing part side on the surface of the other panel housing part, the radiation conversion panels are partially overlapped with each other so that the control parts do not overlap each other. Connect the panel housing parts in sequence ,
The length of each control unit at the time of connection of each panel housing unit is shorter than the width of each panel housing unit in plan view or side view,
Each of the control units is a region other than the imaging region on the surface of the panel housing unit, and in a side view, between the convex portion and the concave portion, or between the convex portion and the other side surface. Arranged,
When the concave portion of the one panel housing portion and the convex portion of the other panel housing portion are fitted, the other panel housing portion side of the one panel housing portion is disposed in the other panel housing portion. A radiographic imaging apparatus, wherein the radiographic imaging apparatus is brought into contact with the control unit . The apparatus of claim 1 .
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. The apparatus according to claim 1 or 2 ,
The radiographic imaging apparatus further comprising a connecting portion that connects the panel accommodating portions connected by the connecting portion. The apparatus according to any one of claims 1 to 3
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 4 .
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. In the apparatus of any one of Claims 1-5 ,
The radiographic imaging apparatus characterized in that the control unit is provided externally to the panel housing unit. A plurality of radiation conversion panels capable of converting radiation into a radiation image, a panel storage unit that stores the radiation conversion panel, and a control unit that is configured separately from the panel storage unit and controls the radiation conversion panel A radiographic imaging device having a radiation detection unit and a connecting portion for connecting the radiation detection units;
A control device for controlling the radiographic imaging device;
With
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,
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 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.
The connecting portion is a convex portion provided on one side surface on the front surface and a concave portion provided on the other side surface facing the one side surface on the back surface,
The other panel housing portion on the back surface of the one panel housing portion by fitting a concave portion provided on the back surface of one panel housing portion and a convex portion provided on the surface of the other panel housing portion. By connecting the side and the one panel housing part side on the surface of the other panel housing part, the radiation conversion panels are partially overlapped with each other so that the control parts do not overlap each other. Connect the panel housing parts in sequence ,
The length of each control unit at the time of connection of each panel housing unit is shorter than the width of each panel housing unit in plan view or side view,
Each of the control units is a region other than the imaging region on the surface of the panel housing unit, and in a side view, between the convex portion and the concave portion, or between the convex portion and the other side surface. Arranged,
When the concave portion of the one panel housing portion and the convex portion of the other panel housing portion are fitted, the other panel housing portion side of the one panel housing portion is disposed in the other panel housing portion. A radiographic imaging system, wherein the radiographic imaging system is brought into contact with the control unit . The system of claim 7 , 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 8 , wherein
The control device includes an image processing unit that generates an image of a subject based on the radiation images obtained by the radiation conversion panels.
The image processing unit corrects the radiographic images based on the connection order information generated by the connection order information generation unit, and then combines the corrected radiographic images to generate an image of the subject. A radiographic imaging system characterized by The system according to any one of claims 7 to 9 ,
The radiographic imaging system, wherein the control unit is provided externally to the panel housing unit.

Images