JP2010259688A - Radiation imaging system - Google Patents

Abstract

A radiographic imaging system capable of efficiently performing radiographic imaging and shortening the transmission time of image data is provided.
In a radiographic imaging system 100, a portable radiographic image detector 1 generates thinned-out image data based on image data read by a readout circuit 17, and transmits the thinned image data to a console 107. The console 107 The region of interest is specified based on the thinned image data transmitted from the portable radiological image detector, and the position information of the specified region of interest is notified to the portable radiographic image detector 1. Then, the portable radiological image detector 1 extracts the image data of the region of interest from the image data read from the read circuit 17 and transmits it to the console 107.
[Selection] Figure 1

Description

  The present invention relates to a radiographic imaging system.

  For the purpose of disease diagnosis and the like, radiographic images taken using radiation typified by X-ray images are widely used. Conventionally, such medical radiographic images have been taken using a screen film, but in recent years, digitization of radiographic images has been realized, and a CR (Computed Radiography) apparatus using a stimulable phosphor sheet. In recent years, radiation image detectors have been developed that detect irradiated radiation with a detection element composed of a scintillator, a photodiode, a TFT (thin film transistor), etc., and obtain it as digital image data. This type of radiation image detector is known as an FPD (Flat Panel Detector).

  In recent years, a portable radiation image detector (hereinafter simply referred to as a portable radiation image detector when referring to a portable radiation image detector) in which a radiation detection element or the like is housed in a housing is portable, and a battery. In addition, a cableless portable radiation image detector has been developed that includes a wireless communication means such as an antenna and performs wireless communication with an external device such as a console (see, for example, Patent Document 1). The cableless radiographic image detector does not require a cable for connecting to an external device such as a console or a power source, so that the portability of the radiographic image detector can be utilized, and radiographic image detection at the time of radiographic imaging There is no restriction on the position of the vessel, and the degree of freedom of shooting can be increased.

  In addition, in the CR apparatus, it is necessary to prepare a plurality of CR cassettes according to the number of radiographs. In general, a radiographic image detector temporarily stores each image data obtained by a plurality of radiographic image captures. And is configured to be capable of continuously performing radiographic imaging a plurality of times (see, for example, Patent Document 2).

In addition, the radiation image detector is usually designed and manufactured in accordance with the JIS standard size in the conventional screen / film cassette, and the existing radiation image detector has been introduced to be compatible with the conventional screen / film cassette. It is configured so that it can be loaded into a Bucky device. As the bucky device, there are known a standing-type bucky device for taking a radiographic image while the patient stands up, and a supine type bucky device for taking a radiographic image while the patient is lying on the side.
In addition, in recent years, taking advantage of the portability of the radiological image detector, it is not loaded into the bucky device, so to speak, it is used as a stand alone, and is a subject on the patient's bedside, for example, on the radiation incident surface of the radiographic image detector. Increasingly, patients' hands are placed directly, and radiation images are taken by irradiating radiation from a portable radiation generator.
If such a radiographic image detector is used, a single radiographic image detector can be used for each of the imaging methods of standing imaging, supine imaging, and portable imaging. Therefore, the radiographic image corresponding to each imaging system is used. There is no need to prepare a detector, which is convenient.

Furthermore, in a conventional simple X-ray imaging system, a diagnostic image input as a digital image is output on a recording medium such as a film by an image recording apparatus (making a hard copy), and is read and observed on a Schaukasten. Therefore, the size of the cassette used for imaging is important, and an operator such as a radiographer needs to perform imaging using a cassette having a size suitable for the subject. However, in recent years, the diagnosis image has been displayed on a monitor such as a CRT (Cathode Ray Tube) and the filmless method (monitor method) for making a diagnosis has been shifted. Since it is possible to display a region of interest necessary for diagnosis on a monitor by performing trimming correction or the like, it is not always necessary to use a radiation image detector having a size suitable for the subject.
Therefore, if one radiation image detector having a relatively large size is prepared, almost all subjects can be photographed. In this case, it is not necessary for the operator to search for a radiographic image detector having a size suitable for each subject prior to radiographic imaging, and the operator's workload can be reduced. Further, it is not necessary to prepare a plurality of sizes of radiation image detectors in the facility, which is advantageous in terms of cost.

  However, in such a radiation image detector, image data obtained by each radiation detection element is transmitted to an external device such as a console, and on the external device side such as a console, image data sent from the radiation image detector is received. After image processing or the like is performed and an image to be provided for diagnosis is determined, a diagnosis or the like by a doctor is performed using the diagnosis image. Therefore, after radiographic imaging, a large amount of data is transmitted from the radiographic image detector to an external device such as a console via a network, and the image data is received and received by the external device such as a console. There is a problem that it takes time to display an image based on image data and determine a diagnostic image.

Therefore, thinned image data is generated by reducing the amount of data by thinning out pixels from the original digital image data (raw data) at a predetermined rate, and the generated thinned image data is transmitted prior to transmission of the original digital image data. Sending to external devices, such as a console, is performed (for example, refer patent document 3).
In this way, according to the method of transmitting the thinned image data in preference to the original image data, before receiving all the original image data transmitted from the radiation image detector on the external device side such as a console, A preview image (decimated image) based on the thinned image data can be displayed on the screen, so operators such as radiologists and doctors can quickly confirm on the preview image whether the shooting position of the subject is appropriate. Thus, it is possible to quickly determine whether re-shooting is necessary. In addition, before receiving all the original image data transmitted from the radiation image detector, the image processing condition is determined using the thinned image data, and the thinned image is subjected to the image processing based on the determined image processing condition. Can also be displayed.
Thereafter, the image data (raw data) received subsequent to the thinned image is subjected to image processing or the like and displayed on the monitor, and it is determined whether or not to confirm the image as a diagnostic image. Then, the image data determined as the diagnostic image is awaiting a doctor's diagnosis.

JP-A-7-140255 Japanese Patent Laid-Open No. 06-342099 JP 2002-281289 A

  However, as described above, when radiographic imaging is performed using a radiographic image detector having a size larger than that of the subject, imaging is performed not on the entire imaging region (reading area) of the radiographic image detector. The subject is placed on a part of the area and shooting is performed. In this case, only the image data of the area where the subject is placed is necessary for diagnosis, and the image data of the area where the subject is not placed is not necessary for diagnosis.

  In such a case, like the conventional radiographic image detector disclosed in Patent Document 4, if all image data is transmitted to an external device such as a console, the image data that is not necessary for diagnosis, Since transmission processing to an external device such as a console is performed, extra time is required for transmission processing of image data, and there is a problem in that a diagnostic image cannot be displayed quickly on the external device. In addition, there is a possibility that the network is set in a busy state and communication time of other devices is delayed. Furthermore, in the radiographic image detector, all image data including image data of an area unnecessary for diagnosis is transmitted. Therefore, particularly when image data is transmitted by a wireless method, the communication time becomes long and the power consumption is large. Therefore, there is a problem that the life of the battery is shortened when the built-in battery is used.

  The present invention has been made to solve the above-described problems, and provides a radiographic image capturing system capable of efficiently performing radiographic image capturing and shortening the transmission time of image data. That is.

In order to solve the above-described problem, the radiographic imaging system of the present invention includes:
A portable radiographic image detector having a detection unit that includes two-dimensionally arranged radiation detection elements that include a communication unit and generate a signal in accordance with the radiation dose, and the portable radiographic image detector With a console that can communicate with
The portable radiation image detector is
A readout circuit that reads out the signal from each radiation detection element and converts it into image data;
Storage means for storing the image data read by the read circuit;
Generating means for generating thinned image data based on the image data read by the read circuit;
Transmitting means for transmitting the thinned image data generated by the generating means to the console;
With
The console is
Acquiring the thinned image data transmitted from the portable radiographic image detector, and specifying a region of interest based on the acquired thinned image data;
Notification means for notifying the portable radiation image detector of the positional information of the region of interest specified by the specifying means;
With
The portable radiation image detector is
Based on the position information of the region of interest notified from the console, image data of the region of interest is extracted from the image data read by the readout circuit, and the extracted image data of the region of interest is extracted from the console. It is characterized by transmitting to.

According to the radiographic imaging system of the system as in the present invention, the portable radiographic image detector generates thinned image data based on the image data read by the readout circuit, and transmits the thinned image data to the console. Then, the region of interest is specified based on the thinned image data transmitted from the portable radiation image detector, and the position information of the specified region of interest is notified to the portable radiation image detector. Then, the portable radiographic image detector extracts the image data of the region of interest from the image data read from the reading circuit and transmits it to the console.
Therefore, only the image data of the area necessary for diagnosis can be transmitted from the portable radiographic image detector to the console, not the entire image data of the detection unit that is the imageable area. Therefore, wasteful time and power consumption are expended by eliminating wasted time (waiting time) during sending of image data that is normally prohibited from being photographed without sending image data in areas not necessary for diagnosis. As compared with the case where all the image data of the detection unit is always transmitted to the console, the transmission time of the image data can be shortened, and radiographic imaging can be performed efficiently.

It is a figure showing the whole radiation image system composition concerning a 1st embodiment. It is a figure explaining the portable radiographic image detector with which a Bucky apparatus provided with a cassette holding part and a Bucky apparatus are loaded. It is an external appearance perspective view of the portable radiographic image detector which concerns on 1st Embodiment. It is sectional drawing which follows the AA line in FIG. It is a top view which shows the structure of the board | substrate which concerns on this embodiment. It is an enlarged view which shows the structure of the radiation detection element, the thin-film transistor, etc. which were formed in the small area | region on the board | substrate of FIG. It is sectional drawing which follows the XX line in FIG. It is a side view explaining the board | substrate with which COF, a PCB board | substrate, etc. were attached. It is a figure showing the equivalent circuit schematic of the radiographic image detector concerning this embodiment. FIG. 10 is an equivalent circuit diagram for one pixel in FIG. 9. It is a graph explaining the time change of the voltage value output from an amplifier circuit, and operation | movement in a correlation double sampling circuit. It is a table | surface showing the power consumption mode of the radiographic image detector which concerns on this embodiment, the power consumption in each mode, and the operating condition of each member. It is a graph showing an example of transition of the voltage value output when the electric current which flows through the connection of a bias line is converted into a voltage value by a current detection means. It is a block diagram which shows the functional structure of the console which concerns on 1st Embodiment. It is a figure which shows an example of imaging | photography order information. It is a figure explaining a to-be-photographed object's position and region of interest in radiographic imaging. It is FIG. 1 of the flowchart which shows an example of the process sequence in the radiographic imaging system which concerns on 1st Embodiment. It is FIG. 2 of the flowchart which shows an example of the process sequence in the radiographic imaging system which concerns on 1st Embodiment. It is a figure which shows the whole structure of the radiographic image system which concerns on 2nd Embodiment. It is a figure which shows the structure of each imaging room in the radiographic imaging system which concerns on 2nd Embodiment. It is a block diagram which shows the functional structure of the console which concerns on 2nd Embodiment. It is FIG. 1 of the flowchart which shows an example of the process sequence in the radiographic imaging system which concerns on 2nd Embodiment. It is FIG. 2 of the flowchart which shows an example of the process sequence in the radiographic imaging system which concerns on 2nd Embodiment. It is FIG. 3 of the flowchart which shows an example of the process sequence in the radiographic imaging system which concerns on 2nd Embodiment.

[First Embodiment]
Hereinafter, a first embodiment of a radiographic imaging system according to the present invention will be described with reference to the drawings. However, the present invention is not limited to the following illustrated examples.

[Radiation imaging system]
The radiographic image capturing system 100 according to the first embodiment is a system that assumes radiographic image capturing performed in a hospital or a clinic. As illustrated in FIG. An imaging room R for imaging a subject (a patient's imaging target region), and an anterior room for performing various operations such as control of an exposure switch for radiation irradiated to the subject by a radiographer or doctor (hereinafter referred to as an operator). Ra and a console 107 that is provided outside the radiographing room R and controls the radiation image radiographing system 100 as a whole.

  In the imaging room R, for example, two portable radiation image detectors 1 are arranged. Hereinafter, the portable radiation image detector is simply referred to as a radiation image detector. In the following, when individually identifying each of these radiographic image detectors, it will be described as radiographic image detectors 1A and 1B, and when it is not necessary to individually identify each radiographic image detector, These radiation image detectors 1A and 1B will be collectively referred to as a radiation image detector 1 for explanation.

  Further, in the radiographing room R, a bucky device 101 (see FIG. 2) in which the radiation image detector 1 can be loaded, a radiation generator 102 for irradiating a subject with radiation, and communication between the radiation image detector 1 and the console 107. A wireless access point 103 or the like for relaying is provided. The imaging room R is shielded with lead or the like so that radiation does not leak outside.

Further, the front chamber Ra is operated in accordance with instructions from a tag reader 104 that detects a tag, which will be described later, incorporated in the radiation image detector 1, an operation console 105 that controls radiation irradiation by the radiation generator 102, and a console 107. A management device 106 that manages the desk 105 and the radiation generation apparatus 102 is provided. Note that the console 107 may be directly connected to the console 105 without providing the management device 106.
In addition, the number of each apparatus arrange | positioned in the imaging | photography room R and front chamber Ra, such as the radiographic image detector 1 and the radiation generator 102, is an example, and is not limited to the example of illustration. For example, at least one radiation image detector 1 may be provided.

  Hereinafter, each of the bucky device 101, the radiation generation device 102, the wireless access point 103, the tag reader 104, the console 105, the management device 106, the radiation image detector 1, and the console 107 included in the radiation image capturing system 100 of the present embodiment will be described. This will be described in this order.

(Bucky device)
As shown in FIG. 2, the bucky device 101 is provided with a cassette holding unit 101a for holding the radiographic image detector 1 in a predetermined position, and the radiographic image detector 1 can be loaded into the cassette holding unit 101a. It is like that. In addition, the shooting room R may be provided with a bucky device for standing position photography (not shown) in addition to the bucky device 101 for standing position photography shown in FIG.
The bucky device 101 is configured to be able to load a CR cassette or FPD cassette (radiation image detector 1) having dimensions conforming to the JIS standard for a conventional screen / film cassette.

(Radiation generator)
The radiation generator 102 includes a radiation source (not shown) that irradiates radiation to the radiation image detector 1 through a subject. The radiation source irradiates a dose of radiation corresponding to the voltage when a high voltage is applied. It is like that. Each radiation source is provided with a diaphragm (not shown) that can be opened and closed.

In the present embodiment, the radiation generating apparatus 102 is arranged to be suspended from the ceiling of the imaging room R, and is set up based on an instruction from an operation console 105 (to be described later) at the time of imaging, and is not illustrated. The means is moved to a predetermined position (position facing the radiation image detector 1) according to each imaging, and the direction is adjusted so that the radiation direction of the radiation faces a predetermined direction. . For example, when the standing-up imaging device 101 is selected on the console 107, the radiation generator 102 is automatically controlled to move to a position corresponding to the standing-up imaging device 101.
In addition to the radiation generator 102 shown in FIG. 1, the imaging room R includes a portable radiation generator (not shown) that can be carried to any location in the imaging room R and can irradiate radiation in any direction. May be.

(Wireless access point)
The wireless access point 103 relays communication between the radiation image detector 1 and the console 107. In FIG. 1, one wireless access point 103 is arranged near the entrance in the radiographing room R, but the number and arrangement position of the wireless access points 103 are not limited to this, and the radiological image detector 1 and the console 107. It is only necessary to be arranged at an appropriate position where the signal between can be relayed.

(Tag reader)
The tag reader 104 transmits predetermined instruction information on radio waves or the like via a built-in antenna (not shown) and enters or exits the radiographing room R, that is, the radiographic image detector 1, that is, the radiographing room R or the front room Ra. The radiation image detector 1 entering the range is detected. The tag reader 104 reads the unique information such as the cassette ID, scintillator type information, size information, and resolution stored in the detected RFID tag of the radiation image detector 1, and transmits the read unique information to the console 107. Therefore, the radiation detector 1 existing in the imaging room R can be grasped by displaying the radiation image detector 1 existing in the imaging room R corresponding to the console 107 as an icon on the console 107.

(Operation console)
The console 105 includes a computer having a general-purpose CPU (Central Processing Unit), a computer having a dedicated processor, and the like. The console 105 is connected to the radiation generation apparatus 102 via a cable or the like, and is also connected to the management apparatus 106 via a cable or the like. The management apparatus 106 receives imaging region information and irradiation conditions (tube voltage or tube) from the radiation generation apparatus 102. Current, irradiation field, etc.) are acquired and set.

  The console 105 is provided with switch means 105a for instructing the start of radiation irradiation from the radiation generator 102. The switch means 105a has a button (not shown), and when the operator operates the button, an activation signal is transmitted from the console 105 to the radiation generator 102, and the activation signal of the radiation generator 102 is transmitted by this activation signal. The radiation source is activated.

(Management device)
The management device 106 is connected to the console 105 via a cable or the like, and is connected to the console 107 via a cable or the like, and acquires the imaging region information transmitted from the console 107, the irradiation conditions of the radiation generator 102, and the like. The control unit 105 is configured to transmit the information to the console 105 and perform control for setting the imaging region information, irradiation conditions, and the like in the console 105.

(Portable radiation image detector)
FIG. 3 is an external perspective view of the radiation image detector according to the present embodiment, and FIG. 4 is a cross-sectional view taken along the line AA of FIG. As shown in FIGS. 3 and 4, the radiological image detector 1 according to the present embodiment is a cassette-type portable radiographic image detector in which a scintillator 3, a substrate 4, and the like are housed in a housing 2. It is configured.
In this embodiment, a so-called indirect radiation image detector that includes a scintillator or the like as a radiation image detector and converts the emitted radiation into electromagnetic waves of other wavelengths such as visible light to obtain an electrical signal will be described. However, the present invention can also be applied to a so-called direct radiation image detector that directly detects radiation with a radiation detection element without using a scintillator or the like.

  Each radiographic image detector 1A, 1B is pre-assigned a cassette ID as identification information for specifying each radiographic image detector 1. For example, a cassette ID “1001” is assigned to the radiation image detector 1A, and a cassette ID “1002” is assigned to the radiation image detector 1B.

  The radiographic image detector 1 includes a tag (not shown). In this embodiment, a tag called a so-called RFID (Radio Frequency IDentification) tag is used as a tag, and the tag stores a control circuit that controls each part of the tag and a storage that stores unique information of the radiation image detector 1. The part is built in compactly. This unique information includes a cassette ID assigned to the radiation image detector 1 itself, scintillator type information, size information, resolution, and the like.

  Moreover, in this embodiment, the radiation image detector 1 is comprised by the dimension based on JISZ4905 (corresponding international standard is IEC 60406) in the cassette for conventional screens / films. That is, the thickness in the radiation incident direction is within a range of 15 mm + 1 mm to 15 mm-2 mm, and is 8 inches × 10 inches, 10 inches × 12 inches, 11 inches × 14 inches, 14 inches × 14 inches, 14 inches × 17 inches. (Half cut size) etc. are prepared.

Thus, since the radiation image detector 1 is formed in conformity with the JIS standard relating to the screen / film cassette, an existing Bucky device that can be similarly loaded with a CR cassette formed in conformity with the JIS standard. 101 can be loaded and used.
Further, the radiation image detector 1 is not loaded in the bucky device 101, and can be used in a so-called single state. That is, the radiation image detector 1 is disposed in a single state, for example, on a support stand provided in the photographing room R, a bucky device for lying down photographing (none of which is shown), and the radiation incident surface R (see FIG. 3)) The patient's hand or the like as the subject can be placed on the top, or the patient's waist or legs lying on the bed can be inserted between the bed and the bed. ing.

  In the present embodiment, the radiation image detector 1 is connected to the console 107 via an antenna device 29 and a wireless access point 103 as communication means, and various control signals and data are transmitted to and from the console 107 wirelessly. It can be sent and received by communication.

  The housing 2 is formed of a material such as a carbon plate or plastic that transmits radiation at least on a surface R (hereinafter referred to as a radiation incident surface R) that receives radiation. 3 and 4 show a case in which the housing 2 is formed of a frame plate 2A and a back plate 2B, that is, a so-called lunch box type. A so-called monocoque type, such as the X-ray imaging apparatus described in Japanese Unexamined Patent Publication No. 2002-31526, can also be used.

  As shown in FIG. 4, a base 31 is disposed on the lower side of the substrate 4 inside the housing 2, and the base 31 includes a PCB substrate 33 on which electronic components 32 and the like are disposed, and a buffer member. 34 etc. are attached. In the present embodiment, a glass substrate 35 for protecting the substrate 4 and the scintillator 3 on the radiation incident surface R side is disposed.

Further, as shown in FIG. 3, a power switch 25 of the radiation image detector 1, an indicator 26 for displaying various operation statuses, and the like are provided on the short side surface portion on one side of the housing 2. .
Further, a lid member 28 for replacing the built-in battery 27 (see FIG. 9) is provided on the side surface portion, and the radiation image detector 1 is provided on the lid member 28 with an external device such as a console 107 described later. An antenna device (communication means) 29 for transmitting and receiving data and signals in a wireless manner is embedded.
The location where the antenna device 29 is provided is not limited to one short side surface portion of the housing 2 as in the present embodiment, but may be provided at another location. Further, the number of antenna devices 29 is not necessarily limited to one, and the necessary number is provided as appropriate.

  The scintillator 3 is, for example, a phosphor whose main component is converted into an electromagnetic wave having a wavelength of 300 to 800 nm, that is, an electromagnetic wave centered on visible light when it receives radiation, and that is output. The scintillator 3 is attached to a detection unit P, which will be described later, of the substrate 4.

  In the present embodiment, the substrate 4 is formed of a glass substrate. As shown in FIG. 5, a plurality of scanning lines 5 and a plurality of signal lines are provided on a surface 4 a of the substrate 4 facing the scintillator 3. 6 are arranged so as to cross each other. In each small region r defined by the plurality of scanning lines 5 and the plurality of signal lines 6 on the surface 4 a of the substrate 4, radiation detection elements 7 are respectively provided. As described above, the radiation detection elements 7 are two-dimensionally arranged on the substrate 4, and the entire region r in which the plurality of radiation detection elements 7 are provided, that is, the region indicated by the alternate long and short dash line in FIG. P.

  Each radiation detection element 7 is configured by, for example, a photodiode, and increases in accordance with the amount of electromagnetic waves output from the radiation incident from the radiation incident surface R converted by the scintillator 3 (the amount of radiation incident on the scintillator 3). ) To generate a charge (signal). In addition to this, for example, a phototransistor or the like can be used as the radiation detection element 7.

Each radiation detection element 7 is connected to a source electrode 8s of a TFT (thin film transistor) 8 as a switch element, as shown in the enlarged views of FIGS. The gate electrode 8 g of each TFT 8 is connected to each scanning line 5, and the drain electrode 8 d of each TFT 8 is connected to each signal line 6.
Then, when the TFT 8 is turned on, that is, when a gate voltage is applied to the gate electrode 8g and the gate of the TFT 8 is opened, the charge accumulated in the radiation detection element 7 is transferred to the signal line 6. To be released.

  Here, the structure of the radiation detection element 7 and the TFT 8 in this embodiment will be briefly described with reference to a cross-sectional view shown in FIG. 7 is a cross-sectional view taken along line XX in FIG.

  On the surface 4a of the substrate 4, a gate electrode 8g of a TFT 8 made of Al, Cr, or the like is integrally laminated with the scanning line 5, and silicon nitride laminated on the gate electrode 8g and the surface 4a. The first electrode 74 of the radiation detecting element 7 is connected to the upper part of the gate electrode 8g on the gate insulating layer 81 made of (SiNx) or the like via the semiconductor layer 82 made of hydrogenated amorphous silicon (a-Si) or the like. The formed source electrode 8s and the drain electrode 8d formed integrally with the signal line 6 are laminated.

  The source electrode 8s and the drain electrode 8d are divided by a first passivation layer 83 made of silicon nitride (SiNx) or the like, and the first passivation layer 83 covers the electrodes 8s and 8d from above. In addition, ohmic contact layers 84a and 84b formed in an n-type by doping hydrogenated amorphous silicon with a group VI element are stacked between the semiconductor layer 82 and the source electrode 8s and the drain electrode 8d, respectively. The TFT 8 is formed as described above.

  In the radiation detecting element 7, an auxiliary electrode 72 is formed by laminating Al, Cr, or the like on the insulating layer 71 formed integrally with the gate insulating layer 81 on the surface 4 a of the substrate 4. A first electrode 74 made of Al, Cr, Mo or the like is laminated on the auxiliary electrode 72 with an insulating layer 73 formed integrally with the first passivation layer 83 interposed therebetween. The first electrode 74 is connected to the source electrode 8 s of the TFT 8 at the hole H formed in the first passivation layer 83.

  On the first electrode 74, an n layer 75 formed in an n-type by doping a hydrogenated amorphous silicon with a group VI element, an i layer 76 which is a conversion layer formed of hydrogenated amorphous silicon, and a hydrogenated amorphous A p layer 77 formed by doping a group III element into silicon and forming a p-type layer is formed by laminating sequentially from below. On the p layer 77, a second electrode 78 made of a transparent electrode such as ITO is laminated and formed so that the irradiated electromagnetic wave reaches the i layer 76 and the like. The radiation detection element 7 is formed as described above.

  The order of stacking the p layer 77, the i layer 76, and the n layer 75 may be reversed. In the present embodiment, as described above, the case where a so-called pin-type radiation detection element formed by stacking the p layer 77, the i layer 76, and the n layer 75 is used as the radiation detection element 7 has been described. The radiation detection element 7 is not limited to such a pin-type radiation detection element.

A bias line 9 for applying a reverse bias voltage to the radiation detection element 7 is connected to the upper surface of the second electrode 78 of the radiation detection element 7 via the second electrode 78.
Further, the second electrode 78 and the bias line 9 of the radiation detection element 7, the first electrode 74 extended to the TFT 8 side, the first passivation layer 83 of the TFT 8, that is, the upper surface portions of the radiation detection element 7 and the TFT 8 are The upper side is covered with a second passivation layer 79 made of silicon nitride (SiNx) or the like.

  As shown in FIGS. 5 and 6, in the present embodiment, one bias line 9 is connected to a plurality of radiation detection elements 7 arranged in rows, and each bias line 9 is connected to a signal line 6. Are arranged in parallel with each other. In addition, each bias line 9 is bound to one connection 10 at a position outside the detection portion P of the substrate 4.

Connections 10 of the scanning lines 5, the signal lines 6, and the bias lines 9 are respectively connected to input / output terminals (also referred to as pads) 11 provided near the edge of the substrate 4. As shown in FIG. 8, a COF (Chip On Film) 12 in which a chip such as an IC 12a is incorporated in each input / output terminal 11 is an anisotropic conductive adhesive film (Anisotropic Conductive Film) or anisotropic conductive paste (Anisotropic paste). It is connected via an anisotropic conductive adhesive material 13 such as Conductive Paste).
The COF 12 is routed to the back surface 4b side of the substrate 4 and connected to the PCB substrate 33 described above on the back surface 4b side. In this way, the substrate 4 portion of the radiation image detector 1 is formed.

  Here, the circuit configuration of the radiation image detector 1 will be described with reference to FIGS. 9 and 10. FIG. 9 is an equivalent circuit diagram of the radiation image detector 1 according to the present embodiment, and FIG. 10 is an equivalent circuit diagram of one pixel constituting the detection unit P.

As described above, each radiation detection element 7 of the detection unit P of the substrate 4 has the second electrode 78 connected to the bias line 9 and the connection 10, respectively, and the connection 10 is connected to the reverse bias power supply 14. .
The reverse bias power supply 14 is connected to the control means 22, and in accordance with control from the control means 22, a negative voltage as a reverse bias voltage is applied to each radiation detection element 7 via the connection 10 and each bias line 9. It is designed to be applied.

  As described above, the p-layer 77, i-layer 76, and n-layer 75 of the radiation detection element 7 are formed in reverse order, and the bias lines 9 A and 9 B are connected to the n-layer 75 through the second electrode 78. In this case, a positive voltage is applied as a reverse bias voltage from the reverse bias power supply 14 to the second electrode 78. In that case, the direction of connection of the radiation detection element to the reverse bias power source 14 in FIGS. 9 and 10 is reversed.

  Further, the connection 10 of the bias line 9 is provided with current detection means 24, and the current detection means 24 is connected to the control means 22.

The current detection means 24 detects the current flowing through the connection 10 in which the bias lines 9 are bundled. Specifically, although not shown, the current detection unit 24 includes a resistor having a predetermined resistance value connected in series to the connection 10 and a differential amplifier that measures a voltage between both terminals of the resistor. By measuring the voltage between the two terminals of the resistor with a differential amplifier, the current flowing through the connection 10 is detected by converting it into a voltage value and output to the control means 22. .
As the resistor provided in the current detection means 24, a resistor having a large resistance value such as 100 kΩ or 1 MΩ is used in order to amplify a current that does not necessarily flow through the connection 10.

  If the resistance value of the resistor provided in the current detection unit 24 is large as described above, there is a possibility that the current flowing through the bias line 9, the connection line 10, or the like may be greatly hindered when reading out the electric charge accumulated by radiation irradiation, for example. Therefore, it is preferable that the current detection unit 24 is provided with a switch or the like so that both terminals of the resistor can be appropriately short-circuited.

The first electrode 74 of each radiation detection element 7 is connected to the source electrode 8 s (denoted as S in FIG. 9) of the TFT 8. Further, the gate electrode 8 g (denoted as G in FIG. 9) of each TFT 8 is connected to each scanning line 5 extending from the scanning drive circuit 15. Further, the drain electrode 8 d (denoted as D in FIG. 9) of each TFT 8 is connected to each signal line 6.
Under the control of the control means 22, when a signal read-on voltage is applied from the scanning drive circuit 15 to the gate electrode 8 g of the TFT 8 via the scanning line 5, the gate of the TFT 8 is opened and accumulated in the radiation detection element 7. The charged charges are read out from the drain electrode 8d to the signal line 6 through the source electrode 8s of the TFT 8.

  Each signal line 6 is connected to each readout circuit 17 formed in the readout IC 16. The read IC 16 is provided with a predetermined number of read circuits 17, and by providing a plurality of read ICs 16, the read circuits 17 corresponding to the number of signal lines 6 are provided.

  The readout circuit 17 includes an amplifier circuit 18, a correlated double sampling circuit 19, an analog multiplexer 20, and an A / D converter 21. The correlated double sampling circuit 19 is represented as CDS in FIGS. In FIG. 10, the analog multiplexer 20 is omitted.

The amplifier circuit 18 is configured by, for example, a charge amplifier circuit, and includes an operational amplifier 18a, a capacitor 18b and a charge reset switch 18c connected in parallel to the operational amplifier 18a.
The charge reset switch 18c is connected to the control means 22 described later, and is turned on / off by the control means.
The signal line 6 is connected to the inverting input terminal 18a1 on the input side of the operational amplifier 18a of the amplifier circuit 18, and the non-inverting input terminal 18a2 on the input side of the amplifier circuit 18 is grounded (GND).
Hereinafter, the case where the non-inverting input terminal 18a2 on the input side of the amplifier circuit 18 is grounded as described above will be described. However, a predetermined initial voltage is applied to the non-inverting input terminal 18a2 on the input side of the amplifier circuit 18. It is also possible to configure as described above.

  Here, the reading circuit 17 in the present embodiment reads the electric charge (signal) generated and accumulated in each radiation detection element 7 and converts it into an electric signal, and each radiation detection element 7. And a standby mode in which no charge (signal) is read out. Then, switching between the standby mode and the power supply mode is performed under the control of the control means 22.

  First, processing in the power supply mode of the readout circuit 17 will be described. In the power supply mode of the read circuit 17, the read circuit 17 is energized, and the charge amplifier circuit that constitutes the amplifier circuit 18 is put into operation.

In the amplifier circuit 18, when the TFT 8 of the radiation detection element 7 is turned on while the charge reset switch 18c is turned off (that is, an on-voltage is applied to the gate electrode 8g of the TFT 8 via the scanning line 5). The charge discharged from the radiation detection element 7 flows into the capacitor 18b and is accumulated, and a voltage value corresponding to the accumulated charge amount is output from the output terminal 18a3 of the operational amplifier 18a. In this way, the amplification circuit 18 outputs a voltage value according to the amount of charge output from each radiation detection element 7 and amplifies the voltage by voltage conversion.
On the other hand, when the charge reset switch 18c is turned on by the control from the control means 22, the input side and the output side of the amplifier circuit 18 are short-circuited, and the charge accumulated in the capacitor 18b is discharged to discharge the amplifier circuit. 18 is reset.
Note that the amplifier circuit 18 may be configured to output a current in accordance with the charge output from the radiation detection element 7.

  A correlated double sampling circuit 19 is connected to the output side of the amplifier circuit 18. The correlated double sampling circuit 19 has a sample and hold function. The sample and hold function in the correlated double sampling circuit 19 is controlled to be turned on / off by a pulse signal transmitted from the control means 22. It has become.

That is, as shown in FIG. 11, the correlated double sampling circuit 19 receives the first pulse signal from the control means 22 immediately after the charge reset switch 18c is turned off (see “18coff” in the figure). When received, the voltage value Vin output from the amplifier circuit 18 at that time is held (see “CDS hold” on the left side of the figure).
Here, when the charge reset switch 18c is turned off, so-called kTC noise is generated at that moment, and the charge q caused by the kTC noise is accumulated in the capacitor 18b of the amplifier circuit 18. Therefore, the charge reset switch When 18c is turned off, the voltage value output from the amplifier circuit 18 rises from 0 [V] to Vin.

Then, the TFT 8 of the radiation detection element 7 is turned on (see “TFTon” in the figure), and the electric charge discharged from the radiation detection element 7 flows into the capacitor 18b and is accumulated, and is output from the operational amplifier 18a. When the first pulse signal is received from the control means 22 immediately after the TFT 8 of the radiation detection element 7 is turned off (see “TFToff” in the figure) at the time when the value increases, the correlated double sampling circuit 19 Holds the voltage value Vfi output from the amplifier circuit 18 at that time (see “CDS hold” on the right side of the figure).
Furthermore, the correlated double sampling circuit 19 outputs the difference value Vfi−Vin between the voltage values output from the amplifier circuit 18 as an electrical signal downstream. The electrical signal corresponding to the electric charge generated in each radiation detection element 7 output from the correlated double sampling circuit 19 is transmitted to the analog multiplexer 20 (see FIG. 7), and sequentially from the analog multiplexer 20 to the A / D converter 21. The digital signal is sequentially converted by the A / D converter 21 and output to the storage means 23 for storage.

  As described above, when the readout circuit 17 is in the power supply mode, it is possible to read out the electric charge accumulated in each radiation detection element 7 in accordance with the irradiation of radiation and acquire image data. .

Next, processing in the standby mode of the reading circuit 17 will be described.
In the standby mode of the read circuit 17, the read circuit 17 itself is not energized, and the charge amplifier circuit constituting the amplifier circuit 18 is deactivated.

  When the charge amplifier circuit constituting the amplifier circuit 18 is deactivated, a current flows between the inverting input terminal 18a1 and the non-inverting input terminal 18a2 (see FIG. 8) on the input side of the operational amplifier 18a of the amplifier circuit 18. Disappear. Therefore, since the loop electrically connected to ground (GND) → reverse bias power supply 14 → (current detection means 24) → radiation detection element 7 → TFT 8 → signal line 6 is broken at the operational amplifier 18a, the radiation detection element 7 or A closed loop including the reverse bias power supply 14 or the like cannot be formed.

  Therefore, in the present embodiment, as shown in FIG. 10, each operational amplifier 18a of the amplifier circuit 18 of each readout circuit 17 is connected to the inverting input terminal 18a1 to which the signal line 6 is connected and the non-inverting input that is grounded as described above. A mode changeover switch 18d that connects the terminal 18a2 and switches between short-circuiting and canceling the short-circuiting is provided on the upstream side of each operational amplifier 18a.

  In this embodiment, the mode changeover switch 18d is composed of a MOSFET (MOS field effect transistor), and a gate electrode 8g (not shown) of the MOSFET as the mode changeover switch 18d is connected to the control means 22. Then, the application of the voltage from the control means 22a to the gate electrode 8g and the stop of the application are switched, whereby the on / off of the mode changeover switch 18d is controlled.

Then, when switching the readout circuit 171 to the standby mode, the control means 22 stops energization to the readout circuit 17 and puts the charge amplifier circuit constituting the amplifier circuit 18 into a non-operating state and switches each mode. The switch 18d is turned on, and the inverting input terminal 18a1 and the non-inverting input terminal 18a2 of each operational amplifier 18a of the amplifier circuit 18 of the readout circuit 17 are short-circuited.
In this way, even when the charge amplifier circuit constituting the amplifier circuit 18 is in a non-operating state, each mode changeover switch 18d is turned on, so that as shown in FIG. ) → reverse bias power source 14 → (current detection means 24) → radiation detection element 7 → TFT 8 → mode changeover switch 18d → ground (GND) closed loop is formed.

As described above, when the readout circuit 17 is in the standby mode, the charge amplifier circuit that constitutes the amplifier circuit 18 is set in a non-operating state and does not read out charges. Consumption can be kept low.
In the state where the readout circuit 17 is in the standby mode, a closed loop is formed and the current detection unit 24 detects the current flowing through the connection 10 of the bias line 9 to start the radiation irradiation to the radiation image detector 1. Can be detected. Detection of the start of radiation irradiation in the standby mode will be described later.
When the readout circuit 17 is switched from the standby mode to the power supply mode described above, the readout circuit 17 is energized to bring the charge amplifier circuit constituting the amplifier circuit 18 into an operating state, and a mode changeover switch. 18d is turned off.

The control means 22 is composed of a microcomputer equipped with a CPU (Central Processing Unit) or the like or a dedicated control circuit, and controls the operation of each member of the radiation image detector 1.
The control means 22 is connected to a storage means 23 composed of a RAM (Random Access Memory) or the like, and stores image data read from the read circuit 17 and the like.
Further, a battery 27 for supplying electric power to each member of the radiation image detector 1 is connected to the control means 22. The battery 27 is built in the housing 2 of the radiation image detector 1, and a connection terminal (not shown) for supplying power from the external device to the battery 27 to charge the battery 27 is attached.

As described above, the control means 22 controls the reverse bias power supply 14, the scanning drive circuit 15, the amplifier circuit 18 in each readout circuit 17, the correlated double sampling circuit 19, and the like to control various processes in radiographic imaging. To do.
Specifically, the control unit 22 monitors the voltage value output from the current detection unit 24 in a state where the readout circuit 17 is switched to the standby mode, and based on the voltage value output from the current detection unit 24, It is detected whether or not the radiation image detector 1 has started irradiation with radiation. Then, when detecting that radiation irradiation has started, the control means reads out the charges accumulated in each radiation detection element, converts them into electrical signals, and acquires image data (raw data). Further, the control means 22 generates thinned image data based on the image data (raw data) read by the read circuit 17, and the generated thinned image data is given priority over the original image data (raw data). To 107.

  Hereinafter, the control configuration by the control unit 22 will be described, and the operation of the radiation image detector 1 in the radiation image capturing system of the present embodiment will be described together.

The radiological image detector 1 of the present embodiment is configured such that the power consumption mode can be switched between at least three modes mode1 to mode3 as shown in the table of FIG. Has been. The control means 22 is configured to switch the power consumption mode according to an instruction from the console 107.
In the table of FIG. 12, S represents the mode changeover switch 18d, and IC represents the read circuit 17 or the read IC 16.

  First, the radiation image detector 1 is arranged in the imaging room R in a state where the power consumption mode is switched to the first mode mode 1 (sleep state) that is the lowest power consumption.

In the first mode mode 1 (sleep state), as shown in FIG. 12, no reverse bias voltage from the reverse bias power supply 14 is applied to each radiation detection element 7 and no voltage is applied to each TFT 8. That is, when switching on / off of each TFT 8, normally, when each TFT 8 is turned on, an on-voltage for signal readout of, for example, +15 [V] is applied to the gate electrode 8g, and each TFT 8 is turned on. For example, in the first mode mode1, neither an on-voltage nor an off-voltage is applied to the gate electrode 8g of each TFT 8 when the off-state is applied.
In the first mode mode1, no voltage is applied to the gate electrode 8g of the mode changeover switch 18d, and the power is not supplied to the readout circuit 17 (readout IC 16). That is, the radiation image detector 1 is not in a state in which the power is completely turned off, but is in a state in which power is supplied only to necessary members such as the control unit 22 and the storage unit 23 as necessary.

Therefore, as shown in the table of FIG. 12, in the radiation image detector 1 of the present embodiment, the power consumption in the first mode mode1 is as small as 1.6 [W], for example.
In the present embodiment, the antenna device 29 is turned on so that the radiation image detector 1 can receive an external signal even in the sleep state of the first mode mode1, but for example, The radiation image detector 1 is provided with a start switch so that the antenna device 29 can be switched on / off by a start switch operation by an operator, and the antenna device 29 is turned off in the first mode mode1. For example, the power consumption in the first mode mode1 is a smaller value, for example, 0.1 [W].

  And the control means 22 of the radiographic image detector 1 is the state switched to 1st mode mode1 (sleep state), and transfers to 2nd mode which instruct | indicates switching from the console 107 to 2nd mode mode2 (irradiation waiting state) When the signal is received, the power consumption mode of the radiation image detector 1 is switched from the first mode mode1 (sleep state) to the second mode mode2 (irradiation waiting state).

  In the second mode mode 2, as shown in FIG. 12, a reverse bias voltage is applied from the reverse bias power supply 14 to each radiation detection element 7, and an off voltage is first applied to each TFT 8. Further, in order to form the above-described closed loop, the mode changeover switch 18d is turned on and the reading circuit 17 is set in the standby mode, but the reading circuit 17 itself is not energized. Thus, in the second mode mode2, as shown in the table of FIG. 12, the power consumption is, for example, 5.2 [W].

  In this embodiment, the control means 22 will perform the reset process of the radiation detection element 7, if the power consumption mode of the radiation image detector 1 is switched to 2nd mode mode2. In the reset process, the control means 22 applies an on-voltage for signal readout to the gate electrodes 8g of the TFTs 8 serving as the switch elements of the radiation detection elements 7 from the scanning drive circuit 15 via the scanning lines 5 to all the TFTs 8. Is turned on, and excess charges accumulated in the radiation detection element 7 are discharged to the bias line 9.

  In this reset process, since it is not necessary to detect the current flowing through the connection 10 of the bias line 9, the switch of the current detecting means 24 described above is turned on so that excess charge is not hindered from flowing out. It is preferable to short-circuit between both terminals of the resistance of the detection means 24.

  When the reset process is completed, the control means 22 applies an off voltage to the gate electrode 8g of the TFT 8 from the scanning drive circuit 15 via each scanning line 5 to turn off all the TFTs 8 and to the radiation image detector 1. Wait for the radiation.

Here, detection of the start of radiation irradiation to the radiation image detector 1 will be described.
When the radiation image detector 1 is irradiated with radiation, the radiation transmitted through the subject existing on or near the radiation incident surface R (see FIG. 1) of the radiation image detector 1 is scintillator 3 in the present embodiment. (Refer to FIG. 2 etc.), the scintillator 3 converts the radiation into an electromagnetic wave, and the electromagnetic wave enters the radiation detecting element 7 below.

  In the radiation detection element 7, when an incident electromagnetic wave reaches the i layer 76 (see FIG. 5), an electron-hole pair is generated in the i layer 76 due to the energy of the electromagnetic wave, and in the radiation detection element 7 by applying a reverse bias voltage. In accordance with the potential gradient formed on the first electrode, one of the generated electrons and holes (holes in this embodiment) moves to the second electrode 78 side, and the other charge (electrons in this embodiment) moves to the first. Move to one electrode 74 side.

  In this case, since the off voltage is applied to the gate electrode 8g of the TFT 8 and the TFT 8 is in the off state, the electrons moved to the first electrode 74 side in the radiation detection element 7 cannot flow out from the TFT 8 to the signal line 6. . Therefore, electrons are accumulated near the first electrode 74. Further, the same amount of holes is accumulated in the vicinity of the second electrode 78.

However, the TFT 8 cannot normally completely block leakage of electrons to the signal line 6, and although the amount is very small, electrons in the radiation detection element 7 leak through the TFT 8. Accordingly, the same amount of holes leaks from the second electrode 78 of the radiation detection element 7 to the bias line 9.
At this time, since the mode changeover switch 18d of the readout circuit 17 is turned on in the second mode mode2 (see FIG. 12), a closed loop is formed, and the current leaked from the radiation detection element 7 is It is easy to flow to the connection 10.

  In general, as the amount of electrons and holes accumulated in the radiation detection element 7 increases, the amount of leaking electrons and holes increases. Further, even if the amount of holes leaking from the second electrode 78 of each radiation detection element 7 to the bias line 9 is small, the holes leaking from one million to ten million radiation detection elements are biased. When collected in the connection 10 of the line 9, the amount becomes a level that can be detected by the current detection means 24.

Therefore, the switch of the current detection unit 24 is turned off to release the short circuit between both terminals of the resistor of the current detection unit 24, and a small amount of current flowing through the connection 10 of the bias line 9 is amplified and detected as a voltage value.
Then, for example, as shown in FIG. 13, when radiation starts to be taken out of the radiation detection element 7 when radiation irradiation is started in the radiographic imaging, when the holes start to flow out to the bias line 9, The flowing current starts to increase, and the voltage value V output from the current detection unit 24 starts to increase as shown at time t1 in FIG.

Using this, in the present embodiment, a predetermined threshold value Vth is provided in advance for the voltage value V output from the current detection unit 24, and the voltage value V output from the current detection unit 24 is set to the threshold value Vth by the control unit 22. Monitor whether or not
When the radiation image detector is irradiated with radiation, electron-hole pairs are generated in each radiation detection element 7 due to the irradiation of the radiation, and the bias line 9 connected to each radiation detection element 7 is connected to the radiation image detector 7. The current flowing through the binding wire 10 starts to increase, and the voltage value V output from the current detection means 24 increases and exceeds the threshold value Vth.

  When the voltage value V output from the current detection unit 24 exceeds the threshold value Vth, the control unit 22 determines that radiation irradiation has started at the time tstart when the voltage value V exceeds the threshold value Vth.

  As described above, in the radiation image detector 1, when the second mode mode 2 (the irradiation waiting state) in which the reading circuit 17 is set to the standby mode is switched in accordance with the second mode transition signal from the console 107, the current detection unit. The voltage value V output from the current detection unit 24 is monitored to determine whether or not the voltage value V output from the current detection unit 24 exceeds the threshold value Vth, thereby detecting the start of radiation irradiation to the radiation image detector 1. It is supposed to be.

  When the control means 22 of the radiation image detector 1 detects that radiation irradiation has been started in the state switched to the second mode mode 2 (waiting for irradiation), the reading circuit 17 is powered from the standby mode. The mode is changed to the supply mode, and the power consumption mode of the radiation image detector 1 is switched from the second mode mode 2 (waiting for irradiation) to the third mode mode 3 (charge accumulation state).

In the third mode mode3, as shown in FIG. 12, application of the reverse bias voltage from the reverse bias power source 14 to each radiation detection element 7 is continued, and the on / off of each TFT 8 is switched as necessary. Further, each read circuit 17 is energized, the charge amplifier circuit constituting the amplifier circuit 18 is activated, the mode changeover switch 18d is turned off, and the read circuit 17 is shifted from the standby mode to the power supply mode. In this way, in the third mode mode3, as shown in the table of FIG. 12, the power consumption increases to, for example, 8.8 [W].
In the third mode mode 3 (charge accumulation state), a charge is generated in the radiation detection element 7 by irradiation of radiation, and a charge corresponding to the amount of irradiated radiation is stored in each radiation detection element 7.

  Furthermore, after the control unit 22 of the radiation image detector 1 is switched to the third mode mode 3 (charge accumulation state), the radiation irradiation is completed when a predetermined time has elapsed since the detection of the radiation irradiation start. It is determined that the irradiation of radiation to the radiation image detector 1 has been completed. The voltage value V output from the current detection unit 24 is monitored to determine whether or not the voltage value V output from the current detection unit 24 is equal to or lower than the threshold value Vth. You may comprise so that the completion | finish of irradiation of a radiation may be detected.

When it is detected that radiation irradiation has been completed in the state switched to the third mode mode 3 (charge accumulation state), the control means 22 of the radiation image detector 1 changes the power consumption mode of the radiation image detector 1 to the first mode. The mode is switched from the three mode mode 3 (charge accumulation state) to the fourth mode mode 4 (read state), and a read process is performed to read out the charges accumulated in the radiation detection element 7 and convert them into electric signals.
As shown in the table of FIG. 12, the power consumption mode of the radiation image detector 1 shifts from the third mode mode3 (charge accumulation state) to the fourth mode mode4 (readout state) by starting the readout process. As will be described, charge accumulation (third mode mode 3) and charge readout (fourth mode mode 4) in the radiation detection element 7 are a series of processes in the radiation image detector 1.

  When the reading process in the reading circuit 17 is started (fourth mode mode 4 in the table of FIG. 12), the amplifier circuit 18, the correlated double sampling circuit 19, the analog multiplexer 20, the A / D converter 21 and the scanning of the reading circuit 17. Since various members such as the drive circuit 15 start to operate, the power consumption further increases to 13.6 [W], for example.

  In the reading process, since it is not necessary to detect the current flowing through the connection 10 of the bias line 9, the switch of the current detection unit 24 is turned on to short-circuit both terminals of the resistance of the current detection unit 24. Then, an on-voltage for signal reading is applied from the scanning drive circuit 15 to the first scanning line 5, the TFT 8 connected to the scanning line 5 is turned on, and each radiation detection element is connected via the TFT 8. Electric charges (electrons in this embodiment) are emitted from the signal line 6 from 7.

  Then, as described above, the charge flowing out to the signal line 6 is converted into an electric signal by being subjected to charge-voltage conversion and amplification in the readout circuit 17, and sequentially converted into an A / D converter 21 via the analog multiplexer 20. Are converted into digital values and sequentially stored in the storage means 23. Then, the scanning drive circuit 15 switches the voltage applied to the first scanning line 5 to the off voltage to turn off each TFT 8, and then turns the scanning line 5 to which the on voltage for signal readout is applied. By sequentially switching, charges are emitted from each radiation detection element 7.

  In this way, the electric charges read from the radiation detection elements 7 are sequentially converted into electrical signals and sequentially stored in the storage means 23, whereby the read processing of the image data (raw data) by the read circuit 17 is performed. Is called.

  When the reading process of the image data (raw data) by the reading circuit 17 is completed, the control unit 22 of the radiation image detector 1 performs offset / gain correction and defect on the image data (raw data) stored in the storage unit 23. Various correction processes such as correction are performed as necessary.

Subsequently, the control means 22 of the radiation image detector 1 serves as a generation means from image data (raw data) read out by the readout circuit 17 and stored in the storage means 23 from a predetermined thinning rate (for example, 1 / In step 16), thinned-out image data with a reduced data amount is generated by thinning out pixels. Then, the control unit 22 transmits the generated thinned image data to the console 107 via the antenna device 29 and the wireless access point 103 as a transmission unit.
At this time, the radiological image detector 1 notifies the console 107 of its own cassette ID by transmitting the thinned image data in association with the cassette ID assigned in advance to itself. Even when there are a plurality of radiological image detectors 1 in the radiographing room R, the radiographic image detector 1 that is normally used for radiographing (used in opposition to the radiation generator 102) is used. There is only one. Therefore, there is only one radiation image detector that detects the start of radiation irradiation, and only the radiation image detector transmits the thinned image data to the console 107, so the console is accompanied by one radiation irradiation. Only one cassette ID is notified to 107.

  Furthermore, the control unit 22 of the radiation image detector 1 receives a thinned image from the storage unit 23 when position information of the region of interest S described later is notified from the console 107 via the wireless access point 103 and the antenna device 29. The original image data (raw data) of the data is read, and only the image data of the region of interest S is extracted from the image data (raw data) based on the position information of the region of interest notified from the console 107. Further, the extracted image data of the region of interest S is transmitted to the console 107 via the antenna device 29 and the wireless access point 103.

  The control means 22 of the radiation image detector 1 transmits the image data of the region of interest S extracted from the original image data (raw data) to the console 107, and then irradiates the radiation within a predetermined time. When the start is not detected, the power consumption mode of the apparatus is switched to the first mode mode1 (sleep state).

(console)
As shown in FIG. 14, the console 107 includes console control means 107a, communication means 107b, input means 107c, display means 107d, and storage means 107e.

  The console control means 107a is composed of, for example, a general-purpose CPU, a ROM (Read Only Memory), a RAM (Random Access Memory), etc. (all not shown), and reads a predetermined program stored in the ROM. Are expanded in the RAM work area, and the CPU executes various processes according to the program.

  The communication means 107b is for communicating with the radiation image detector 1 via the wireless access point 103, and transmits / receives various control signals and data to / from the radiation image detector 1.

  The input unit 107c includes a keyboard, a mouse, and the like for inputting various instructions, information, and the like, and an operator sets information and imaging conditions of a patient to be subjected to radiographic imaging prior to radiographic imaging. It is operated when. As will be described later, the patient information and imaging conditions are registered by the operator selecting and inputting imaging order information as predetermined information using the input means 107c.

  The display unit 107d includes a CRT (Cathode Ran Tube), an LCD (Liquid Crystal Display), and the like, and displays various kinds of information such as an image transmitted from the radiation image detector 1 and imaging order information.

  The storage means 107e is composed of a hard disk or the like and stores various information.

  Specifically, the storage unit 107e stores a list of radiation image detectors 1 present in the imaging room R. As described above, when the console 107 receives the unique information including the cassette ID of the radiation image detector 1 detected by the tag reader 104 installed in the vicinity of the entrance of the front chamber Ra, it is registered in the storage means 107e. A list of the radiation image detectors 1 existing in the imaging room R is referred.

If the transmitted unique information is not registered in the storage means 107e, the console 107 determines that the radiological image detector 1 is newly brought into the imaging room R, and the radiological image detector. One cassette ID or the like is added to the above list and registered in the storage means 107e.
Further, if the transmitted unique information is already registered in the storage means 107e, it is determined that the radiation image detector 1 has been taken out of the radiographing room R, and the radiation image detector 1 Delete the cassette ID etc. from the above list.
In this way, the console 107 stores the cassette ID and the like of the radiographic image detector 1 in the radiographing room R in the storage unit 107e, and grasps which radiographic image detector 1 is present in the radiographing room R. It is like that.

  The storage unit 107e stores imaging order information including information on a patient who is a target of radiographic imaging in the imaging room R and imaging conditions. The imaging order information is stored in the storage means 107e in advance in a list format prior to radiographic imaging.

  In the present embodiment, as shown in FIG. 15, the imaging order information includes “patient ID” P2, “patient name” P3, “sex” P4, “age” P5 as patient information, and “imaging” as imaging conditions. It includes a “part” P6 and an “imaging direction” P7. Then, “shooting order ID” P1 is automatically assigned to each shooting order information in the order in which the shooting orders are received.

  The patient information and the imaging conditions to be written in the imaging order information are not limited to those described above, and include, for example, information such as the patient's date of birth, the number of medical examinations, the radiation dose, and whether the patient is fat or thin. It can also be configured as described above, and can be set as appropriate. Further, for example, it is possible to connect the console 107 to a HIS (Hospital Information System) or RIS (Radiology Information System) (both not shown) via a network and obtain imaging order information therefrom. It is.

  Further, the storage means 107e stores the image data received from the radiation image detector 1 and the imaging order information in association with each other.

  In addition, for example, an imager that records and outputs a radiographic image on an image recording medium such as a film based on the image data output from the console 107 is connected to the console 107 as appropriate.

  In the present embodiment, the console 107 is previously associated with the imaging room R on a one-to-one basis, and all the radiological image detectors existing in the imaging room R via the communication unit 107b, the wireless access point 103, and the like. Communication is possible between 1A and 1B.

  The console 107 is arranged in the first mode (sleep state) in the photographing room R when new photographing order information is acquired from the RIS or when photographing order information is selected and input by the input unit 107c. By transmitting a second mode transition signal to the radiological image detector 1 that is in operation, the power consumption mode of all the radiographic image detectors 1A and 1B in the imaging room R is changed to the first mode mode1 (sleep state). To the second mode mode2 (irradiation waiting state).

  Furthermore, the console 107 has shifted any radiation image detectors 1A and 1B in the imaging room R to the second mode mode 2 (waiting for irradiation), and then has detected any one radiation image detector that has detected the irradiation of radiation. 1 is received via the wireless access point 103 and the communication means 107b.

Here, there is only one radiographic image detector 1 that is used in one radiographic imaging and irradiated with radiation. That is, the console 107 receives image data transmitted from one radiographic image detector 1 actually used for imaging. When the console 107 receives the image data from only one radiographic image detector 1 that is actually used for imaging, all the radiographic image detectors 1 other than the radiographic image detector 1 that transmitted the image data to the console 107 are used. It can be recognized that the radiation image detector 1 is not used for imaging.
The console 107 that has received the thinned image data transmitted from the radiation image detector 1 acquires a cassette ID associated with the received thinned image data, and exists in the imaging room R stored in the storage unit 107e. The radiographic image detectors 1 other than the radiographic image detector 1 that transmitted the thinned-out image data, that is, the radiographic image detectors 1 that are not used for imaging are identified by referring to the cassette IDs of all the radiographic image detectors 1 To do.

  The console control means 107a of the console 107 receives the thinned image data from the radiographic image detector 1 used for imaging, and then receives radiation other than the radiographic image detector 1 that has transmitted the thinned image data existing in the radiographing room R. By transmitting a first mode transition signal instructing switching to the first mode mode1 (sleep state) to the image detector 1 via the communication means 107b and the wireless access point 103, the image detector 1 is used for photographing. All the radiographic image detectors 1 that are not present can be configured to shift from the second mode mode 2 (irradiation waiting state) capable of detecting radiation irradiation to the first mode mode 1 (sleep state).

  When the console control means 107a of the console 107 receives the thinned image data from the radiation image detector 1 that is actually used for imaging and detects the radiation irradiation, it analyzes the received thinned image data as a specifying means. The region of interest S necessary for diagnosis in the image data (raw data) is specified.

Hereinafter, the identification of the region of interest S based on the thinned image data will be described.
When a radiographic image detector having a size larger than that of the subject is used in radiographic image capturing, as shown in FIG. 16, not the entire region of the detection unit P of the radiographic image detector 1 but a part of the detection unit P Thus, the subject is placed only in the shooting. In FIG. 16, as an example, a state where a patient's hand as a subject is arranged in a lower central region of the detection unit P is shown. In such a case, the image data of the lower center region where the subject is arranged in the detection unit P is necessary for diagnosis and is set as the region of interest S. On the other hand, the image data of the area where the subject is not arranged (in FIG. 16, the upper central area and the left and right areas) is image data unnecessary for diagnosis.
Further, as illustrated in FIG. 16, when a subject is arranged in a part of the detection unit P, imaging is performed by narrowing the radiation irradiation field so that the region where the subject is not arranged is not irradiated with radiation. Often done. In this case, the image data of the area not irradiated with radiation has an output value (signal value) close to “0”. Alternatively, in an ideal system in which there is no variation in the characteristics of each radiation detection element 7, the value is “0”.

When the region of interest S is specified, the console 107 first extracts a radiation irradiation region A (irradiation field) irradiated with radiation in the thinned image data. Then, based on the pixel signal value in the extracted radiation irradiation area A, the direct irradiation area where the radiation is directly irradiated without passing through the subject is detected, and the remaining area excluding the detected direct irradiation area is the region of interest. S is specified.
Note that the shape of the region of interest S to be specified can be a rectangular shape (see FIG. 16) inscribed in the subject portion, a polygon, a circle, or any other shape.

As a method for extracting the radiation irradiation region A, for example, methods disclosed in Japanese Patent Laid-Open Nos. 5-7579 and 7-181609 can be appropriately used. Specifically, the target image data is divided into a plurality of vertical and horizontal small areas, and the characteristic value of each small area (for example, the variance value of the image data in each small area) is calculated. Based on the calculated characteristic value, a boundary point (or boundary line) between the radiation irradiation region A and the irradiation field stop region is calculated, and the region surrounded by the boundary point group (or boundary line) is determined as the radiation irradiation region. Extract as A. As a result, a region that is not irradiated with radiation can be excluded from the region of interest S.
Further, as a method for extracting a direct irradiation region, as disclosed in Japanese Patent Application Laid-Open No. 2003-17283, etc., a method of detecting a blank region directly irradiated with radiation based on a histogram shape of image data. Can be used.

Note that the region of interest S may be the entire radiation irradiation region A excluding the irradiation field where the radiation has not been irradiated.
Further, when the irradiation field stop is not performed in radiographic imaging, the radiation irradiation area A is not extracted, the direct irradiation area where the radiation is directly irradiated without passing through the subject is detected, and the detected direct It is also possible to specify the remaining region excluding the irradiation region as the region of interest S, or to specify the rectangular region, the circular region, or the like that includes the remaining region and is inscribed in the subject portion as the region of interest S.
Further, after extracting a subject area using the method disclosed in Japanese Patent Laid-Open No. 2001-331800, a characteristic pattern is detected as a feature quantity from the distribution of signal changes of pixels in the subject area, and the feature quantity is detected. It is possible to automatically recognize an imaging region based on the above and determine a predetermined range corresponding to each imaging region as the region of interest S.
Furthermore, it is also possible to determine a region predetermined as the region of interest S corresponding to each imaging region designated by the operation of the imaging condition key according to the operation of the imaging condition key described later.

  When the console control means 107a of the console 107 specifies the region of interest S necessary for diagnosis based on the thinned image data transmitted from the radiation image detector 1, the position of the region of interest S in the image data (raw data) is calculated. Then, the position information of the region of interest S in the calculated image data (raw data) is transmitted to the radiation image detector 1 that has transmitted the thinned image data via the communication unit 107b and the wireless access point 103.

Then, as described above, in the radiation image detector 1 that has transmitted the thinned image data, the original image of the thinned image data is received based on the positional information of the region of interest S in the image data (raw data) received from the console 107. The image data of the region of interest S is extracted from the data (raw data), and the extracted image data of the region of interest S is transmitted to the console 107. The console 107 receives the image data of the region of interest S transmitted from the radiation image detector 1 via the wireless access point 103 and the communication unit 107b.
Note that the console 107 transmits the position information of the region of interest S in the thinned data to the radiation image detector 1 and calculates the position of the thinned image data in the original image data (raw data) on the radiation image detector 1 side. It's also good.

  Next, the console control means 107a of the console 107 performs image processing on the image data of the region of interest S acquired from the radiation image detector 1 under image processing conditions corresponding to the imaging region. The imaging region can be specified using, for example, the distribution of pixel signal changes in the image data in the subject area, as in the method disclosed in Japanese Patent Laid-Open No. 2001-331800 described above. Further, as disclosed in Japanese Patent Laid-Open No. 2001-218759, an operator designates an imaging region by operating an imaging region key displayed on the display unit 107d, and image processing corresponding to the specified imaging region is performed. It is also possible to obtain an image optimized for the imaging region by performing image processing under conditions.

  Thereafter, the console control means 107a of the console 107 displays a diagnostic image on the display means 107d based on the image data of the region of interest S which has been subjected to image processing under the image processing conditions corresponding to the imaging region, and trims as necessary. Correction, gradation correction, etc. are executed and determined as diagnostic image data. Further, diagnostic image data is stored in association with the registered imaging order information.

  Note that when the diagnostic image is copied and output on a recording medium such as a film, the console 107 uniformly assigns the highest density Dmax to the portion other than the region of interest S and outputs it in order to prevent dazzling. To do. Further, when the console 107 outputs a diagnostic image as a viewer, the console 107 assigns a low luminance value to a portion other than the region of interest S and outputs it at the stage of output processing.

  Next, a flow of radiographic imaging in the radiographic imaging system 100 according to the present embodiment will be described with reference to the flowcharts of FIGS. 17 and 18.

  First, the radiation image detectors 1A and 1B are arranged in the imaging room R in a state where the power consumption mode is the first mode mode1 (sleep state) (step S1 in FIG. 17).

Prior to radiographic imaging, the console control means 107a of the console 107 reads out the imaging order information stored in the storage means 107e (or obtains imaging order information from the HIS / RIS via the network) and acquires it. Displayed on the display means 107d.
The operator selects the imaging order information for the current radiographic imaging using the input unit 107c from the imaging order information displayed on the display unit 107d (step S2 in FIG. 17). Thereby, the imaging order information of the current radiographic imaging is registered.

  When the radiographing order information is registered, the console control unit 107a shifts to the second mode instructing switching to the second mode mode2 (waiting for irradiation) via the communication unit 107b and the wireless access point 103. The signal is transmitted to all the radiation image detectors 1A and 1B existing in the imaging room R (step S3 in FIG. 17). In addition, the console 107 transmits the registered imaging order information to the management device 106 disposed in the front room Ra via a cable or the like. Then, based on the imaging order information transmitted from the console 107, the management apparatus 106 transmits and sets imaging part information, irradiation conditions, and the like to the console 105 via the management apparatus 106.

On the other hand, when the control means 22 of each of the radiation image detectors 1A and 1B arranged in the imaging room R receives the second mode transition signal from the console 107 (step S4 in FIG. 17), a reverse bias is applied to the radiation detection element 7. While applying a voltage, the mode changeover switch 18d is controlled to be in an ON state, and the readout circuit 17 is shifted to a standby mode in which no power is supplied, whereby the power consumption mode of the radiation image detector 1 is changed to the first mode mode1 (sleep mode). State) is switched to the second mode mode2 (irradiation waiting state) (step S5 in the figure).
Here, the second mode transition signal transmitted from the console 107 is received by all the radiation image detectors 1A and 1B in the imaging room R. Accordingly, all the radiation image detectors 1A and 1B in the imaging room R are shifted from the first mode mode1 (sleep state) to the second mode mode2 (irradiation waiting state) in response to an instruction from the console 107.

In addition, the console 107 performs a so-called dark reading process in which reading is performed without irradiating radiation in each of the radiation image detectors 1A and 1B arranged in the imaging room R, and a dark reading value is acquired. The dark read value acquired by the dark reading process is used as an offset correction value for performing offset correction on the image data read by the read circuit 17 as will be described later.
It should be noted that the timing for executing the dark reading process is not limited to before shooting, and may be configured to be executed after shooting. Further, the dark reading value may be stored on the radiation image detector 1 side, and the offset correction process based on the dark reading process may be performed on the radiation image detector 1 side.

  When the operation of registering the imaging order information on the console 107 is completed, the operator moves from the console 107 to the imaging room R and is arranged in the imaging room R in the second mode mode 2 (waiting for irradiation) 2. A desired radiological image detector 1 is selected from the two radiographic image detectors 1A and 1B, and is loaded into, for example, a standing-up imaging device 101 to execute radiographic imaging. Specifically, the operator positions the patient with respect to the bucky device 101, moves to the anterior chamber Ra, operates the switch means 105a of the arranged console 105, and emits radiation from the radiation generator 102. The desired radiation image detector 1 is irradiated.

  At this time, the operator uses which radiographic image detector 1 among the radiographic image detectors 1A and 1B arranged in the imaging room R in the second mode mode2 (waiting for irradiation) to perform radiographic imaging. May be executed. That is, the operator can select a radiographic image detector 1 to be used for radiographing and perform radiographic imaging for the first time at the stage of actually taking radiographic images in the radiographing room R. In addition, the operator does not need to perform any operation or work for selecting the radiographic image detector 1 used for imaging as the radiographic image detector 1 used for imaging, and simply the radiographic image used for imaging. It is only necessary to irradiate the detector 1 with radiation from the radiation generation apparatus 102 and perform radiographic imaging.

  At this time, the operator does not need to use the radiation image detector 1 having a size suitable for the subject as long as the subject can be accommodated, and uses the radiation image detector 1 having a size larger than that of the subject. be able to. Therefore, it is not necessary to prepare the radiation image detector 1 having a size suitable for each subject. For example, a bucky device 101 (FIG. 2) used for previous shooting and a bucky camera for standing position shooting is used. The radiation image detector 1 that is still loaded in the apparatus 101 can be used as it is.

  In the following, the process performed by the radiological image detector 1 used for imaging and the process performed by the radiographic image detector 1 not used for imaging will be described separately. Of the two radiological image detectors 1A and 1B arranged in the above, a case where radiographic imaging is performed using the radiographic image detector 1B will be described.

The control means 22 of the radiation image detectors 1A and 1B in the radiographing room R determines whether or not radiation irradiation has started by determining whether or not the voltage value V output from the current detection means 24 exceeds the threshold value Vth. Judge whether or not. Then, the control means 22 of the radiation image detector 1B that is used for imaging and detects radiation irradiation detects that the voltage output from the current detection means 24 has exceeded the threshold value Vth due to radiation irradiation, and When it is determined that the irradiation has started (step S6 in FIG. 17), the mode changeover switch 18d is turned off to supply power to the readout circuit 17, and the readout circuit 17 is shifted to the power supply mode, whereby its own power consumption mode. Is switched from the second mode mode2 (waiting for irradiation) to the third mode mode3 (charge accumulation state) (step S7 in FIG. 17).
That is, of the two radiographic image detectors 1A and 1B arranged in the radiographing room R, only one radiographic image detector 1B that is actually used for radiographing receives the radiation irradiation and automatically performs the third operation. While shifting to mode mode 3 (charge accumulation state), other radiation image detectors 1A that are not used for imaging are maintained in the second mode mode 2 (waiting for irradiation) state.

  Next, when a predetermined time, for example, 500 msec to 1 second elapses from the start of radiation irradiation, the control means 22 of the radiation image detector 1B used for imaging determines that the radiation irradiation has ended (FIG. 17). Step S8). Then, the TFT 8 connected to each scanning line 5 is turned on by applying an on-voltage for signal reading to each scanning line 5 to the scanning drive circuit 15, and the power consumption mode is set to the third mode mode 3 (charge charge mode). The mode is switched from the accumulation state to the fourth mode mode 4 (reading state). Then, a read process is performed to acquire the image data (raw data) by converting the electric charge accumulated in the radiation detection element 7 by the irradiation of radiation into an electric signal (step S9 in FIG. 17), and the read circuit 17 reads the data. The image data (raw data) is subjected to various image correction processes such as offset correction and stored in the storage means 23 (step S10 in FIG. 17).

  Next, the control means 22 of the radiation image detector 1B generates thinned image data based on the image data (raw data) read by the read circuit 17 (step S11 in FIG. 17). Then, the generated thinned image data is associated with the cassette ID “1005” assigned to itself and transmitted to the console 107 via the antenna device 29 and the wireless access point 103 (step S12 in FIG. 18).

  Then, the console 107 receives the thinned image data transmitted from the radiation image detector 1B used for imaging via the wireless access point 103 and the communication means 107b (step S13 in FIG. 18).

Upon receiving the thinned image data transmitted from the radiation image detector 1B, the console control means 107a of the console 107 receives the cassette ID “1002” associated with the thinned image data and the imaging room stored in the storage means 107a. Of the radiographic image detectors 1A and 1B in the radiographing room R, based on the radiographic image detectors 1A and 1B existing in R, the radiographic image detector 1B that has detected the irradiation of radiation, and The radiation image detector 1A that does not detect radiation irradiation is identified.
Then, the console control unit 107a transmits a first mode transition signal that instructs the radiographic image detector 1A that is not used for imaging to switch the power consumption mode to the first mode mode1 (sleep state). 107b and the wireless access point 103 (step S14 in FIG. 18).
The first mode transition signal transmitted from the console 107 is received by each radiation image detector 1A that is not used for imaging, and the power consumption mode of the radiation image detector 1A is changed from the second mode mode2 (waiting for irradiation). It will be switched to the first mode mode1 (sleep state).

  Next, the console control unit 107a performs image processing or the like according to the imaging region based on the thinned image data received from the radiation image detector 1B, and generates a preview image (thinned image) as a display image. The generated preview image (decimated image) is displayed on the display means 107d in association with the photographing order information selected and registered by the input means 107c (step S15 in FIG. 18). The operator looks at the preview image (thinned-out image) displayed on the display unit 107d of the console 107, and confirms whether re-shooting is necessary, whether it is associated with correct shooting order information, or the like.

Next, the console control means 107a specifies the region of interest S in the original image data (raw data) using the above-described method based on the thinned image data received from the radiation image detector 1B (FIG. 18). Step S16).
Further, when the region of interest S is specified, the console control unit 107a uses the position information indicating the position of the region of interest S in the image data (raw data) to the radiographic image detector 1 that has been used for imaging and transmitted the thinned image data. The position information of the region of interest S in the image data (raw data) is notified (step S17 in step S18).

When the control means 22 of the radiation image detector 1B receives the position information of the region of interest S in the image data (raw data) transmitted from the console 107, the original image data (raw data) read by the reading circuit 17 is received. Is extracted from the storage means 23, and the image data of the region of interest S is extracted from the original image data (raw data) based on the received position information of the region of interest S (step S18 in FIG. 18).
Then, the control means 22 of the radiation image detector 1B transmits the extracted image data of the region of interest S to the console 107 via the antenna device 29 and the wireless access point 103 (step S19 in FIG. 18).
Further, the radiation image detector 1B automatically switches the power consumption mode to the first mode mode1 (sleep state) when a predetermined time has elapsed after the transmission of the image data of the region of interest S, and ends this processing ( Step S20 in FIG.

On the other hand, when the console 107 receives the image data of the region of interest S transmitted from the radiation image detector 1B (step S21 in FIG. 18), the image corresponding to the imaging region is received with respect to the received image data of the region of interest S. Image processing is performed under the processing conditions, and the image of the region of interest S is displayed on the display unit 107d in association with the imaging order information input by the input unit 107c (step S22 in FIG. 18).
The operator looks at the image of the region of interest S displayed on the display means 107d of the console 107, and operates the input means 107c to perform trimming correction as necessary (step S23 in FIG. 18). An operation to confirm the image for diagnosis is performed.
Then, the console control unit 107c determines the image data subjected to image processing or trimming correction under the image processing condition corresponding to the imaging region as a diagnostic image, and stores it in the storage unit 107a in association with the imaging order information. Then (step S24 in FIG. 18), the present process is terminated.

As described above, according to the radiographic image capturing system 100 according to the first embodiment, the radiographic image detector 1 generates thinned image data based on the image data (raw data) read by the read circuit 17. The region of interest S is identified based on the thinned image data transmitted from the portable radiographic image detector 1 in the console 107, and the positional information of the identified region of interest S is the radiographic image detector. 1 is notified. Further, in the radiation image detector 1, the image data of the region of interest S is extracted from the image data (raw data) read from the reading circuit 17 and stored in the storage unit 23, and transmitted to the console 107.
Therefore, when a subject is arranged in a part of the detection unit P and radiographic image capturing is performed, the subject is arranged from the radiographic image capturing apparatus 1 instead of the entire image data of the detection unit P that is an imageable region. In addition, only the image data of the region irradiated with radiation, that is, the image data of the region of interest S necessary for diagnosis can be transmitted to the console 107, and the image data of the region unnecessary for diagnosis can be transmitted. The useless time is not spent, and the transmission time of the image data can be shortened as compared with the case where all the image data of the detection unit P is transmitted to the console 107.
As a result, the console 107 can quickly receive only the image data of the region of interest S necessary for diagnosis, and can quickly display a diagnostic image based on the received image data of the region of interest S. The system is easy for the patient to use.

  Further, since only the image data of the region of interest S necessary for diagnosis is transmitted to the console 107, wasteful power consumption is not spent for transmitting image data of the region unnecessary for diagnosis, Compared with the case where all image data of the detection unit P is always transmitted to the console 107, radiographic imaging can be performed efficiently.

  That is, even when radiographic imaging is performed using the radiographic image detector 1 having a size larger than that of the subject, a reduction in efficiency in radiographic imaging can be suppressed. If at least one radiographic image detector 1 is prepared, radiographic imaging can be performed regardless of the size of each subject. Therefore, it is not necessary for the operator to prepare a radiation image detector having a size suitable for the subject prior to radiographic imaging, and the operator's workload can be reduced.

  Further, in the console 107, the imaging order information input and registered by the input unit 107c is associated with the image data transmitted from the radiation image detector 1, so that convenience is improved.

  Further, the console 107 extracts the radiation irradiation area A irradiated with radiation when specifying the region of interest S based on the thinned-out image data, and the radiation detects the subject based on the pixel signal value in the extracted radiation irradiation area A. Since the remaining region excluding the direct irradiation region directly irradiated without passing through is identified as the region of interest S, the region other than the radiation irradiation region A and the direct irradiation region can be excluded from the region of interest S. The required area can be identified more reliably.

  The console 107 can detect the start of radiation irradiation in the power consumption mode of all the radiation image detectors 1A and 1B existing in the imaging room R at the timing when the imaging order information is input by the input unit 107c. Transition to the second mode mode 2 (waiting for irradiation). Of the radiographic image detectors 1A and 1B arranged in the radiographing room R, the control means 22 of one radiographic image detector 1B used for imaging uses the bias line 9 detected by the current detection means 24. When radiation irradiation is detected by monitoring the amount of flowing current, the power consumption mode is switched to the third mode mode 3 (charge accumulation state) in which the readout circuit 17 is in the power supply mode. Further, the radiation image detector 1B switched to the third mode mode 3 (charge accumulation state) reads out the charge accumulated in the radiation detection element 7 by irradiation of radiation, generates image data, and transmits it to the console 107. .

That is, even if the operator does not select the radiation image detector 1 to be used for imaging before imaging, the operator simply performs the operation of inputting the imaging order information from the radiation image detector 1 actually used for imaging to the console 107. The image data is transmitted to.
Therefore, in the radiographic image capturing system 100 according to the present embodiment, the operator does not need to consciously identify and use the individual radiographic image detectors 1, and is free to use for radiography.
There is no need to perform any operation or work for selecting the ray image detector 1. That is, the operator recognizes the cassette ID of the radiation image detector 1 used for imaging, and searches for the radiation image detector 1 attached with the cassette ID from the plurality of radiation image detectors 1. There is no need to perform the operation or work to switch the power consumption mode of the radiation image detector 1 used for imaging to a mode capable of imaging.

Thereby, the operator decides the radiographic image detector 1 to be used for radiographing according to the condition of the patient for the first time at the stage of actually performing radiographic imaging, and uses the radiographic image detector 1. Radiographic imaging can be performed. Even when it is necessary to use a radiographic image detector 1 other than the radiographic image detector 1 that was originally intended to be used at the stage of using radiographic imaging, the operator can There is no need to perform any operation for performing imaging using another radiation image detector 1. Further, the operator only inputs the shooting order information on the console 107 before shooting, and thereafter, in the shooting room R, without performing any operation such as operation of the switch or removal from the cradle. It is only necessary to perform radiographic imaging using the desired radiographic image detector 1. Further, the operator does not need to be aware of which radiographic image detector 1 is the radiographic image detector 1 used by the operator when taking radiographic images.
As described above, the radiographic image capturing system of the present embodiment is very convenient for the operator because the burden on the operator is very light.

  In addition, since the readout circuit 17 is maintained in a standby mode with lower power consumption until the radiation image detector 1 is irradiated with radiation, the readout circuit 17 is set to a power supply mode that consumes more power than the standby mode. It becomes possible to suppress that the time which exists is longer than necessary. For this reason, it is possible to reduce power consumption during radiographic imaging, and it is possible to suppress wasteful consumption of power.

  In the above embodiment, the case where a single radiographic imaging is performed has been described. However, the radiographic imaging system 100 of the present invention is also applicable to a case where a plurality of radiographic imaging is continuously performed. can do. Whether or not radiographic imaging is performed a plurality of times can be determined based on, for example, the number of imaging order information input prior to imaging.

[Second Embodiment]
Hereinafter, a second embodiment of the radiographic imaging system according to the present invention will be described. About this 2nd Embodiment, about the structure similar to 1st Embodiment mentioned above, the same code | symbol is attached | subjected and the overlapping description shall be abbreviate | omitted. In the second embodiment, only the parts different from the first embodiment will be described, and unless otherwise specified, the second embodiment has the same configuration as the first embodiment.

  The radiographic imaging system 200 according to the present embodiment is a system that assumes radiographic imaging performed in a hospital or a clinic. For example, as shown in FIG. A plurality of imaging rooms R for imaging (parts to be imaged by the patient), a plurality of consoles C for controlling the entire radiographic imaging system 200, a data management server S, and the like are configured.

In this embodiment, as shown in FIG. 19, a case where four shooting rooms R are provided from R1 to R4 and three consoles C are provided from C1 to C3 will be described. It is not limited to. The present invention is also applied to a system in which one console C is provided in common in a plurality of shooting rooms R.
In the following, when each of the shooting rooms R is individually identified, the shooting rooms R1 to R4 will be described. When it is not necessary to individually identify each of the shooting rooms R, these shooting rooms R are described. R1 to R4 will be collectively referred to as a photographing room R. Similarly, when each of these consoles C is identified individually, it is described as consoles C1 to C3. When there is no need to identify each console C individually, these consoles C1 to C3 are designated as consoles C. And will be described collectively.

In each imaging room R, at least one radiation image detector 1 described above is arranged. For example, as shown in FIG. 20, two radiographic image detectors 1A and 1B are arranged in the imaging room R1. Although illustration is omitted, for example, two radiological image detectors 1C and 1D are arranged in the radiographing room R2, and three radiographic image detectors 1E to 1G are arranged in the radiographing room R3. Four radiation image detectors 1H to 1K are arranged in R4.
In the following, when individually identifying each of these radiation image detectors, it will be described as radiation image detectors 1A to 1K, and when it is not necessary to individually identify each radiation image detector, These radiation image detectors 1 </ b> A to 1 </ b> K will be collectively referred to as a radiation image detector 1.

(console)
As shown in FIG. 21, the console C includes console control means 207a, communication means 107b, input means 207c, display means 207d, and storage means 207e.

  The console control means 207a is composed of, for example, a general-purpose CPU, ROM (Read Only Memory), RAM (Random Access Memory), etc. (all not shown), and reads a predetermined program stored in the ROM. Are expanded in the RAM work area, and the CPU executes various processes according to the program.

  The input unit 207c includes a keyboard, a mouse, and the like for inputting various instructions and information.

Specifically, the input unit 207c is operated as a selection unit when the operator selects the imaging room R in which imaging is performed from the plurality of imaging rooms R1 to R4 prior to radiographic image capturing.
The input unit 207c is operated when an operator inputs an operator ID prior to radiographic image capturing, and an operator who has completed imaging in the imaging room R inputs the operator ID again. When operated.
Further, the input unit 207c selects the console C as an image data transmission destination to which the operator transmits image data acquired by radiographic imaging from among a plurality of consoles C1 to C3 prior to radiographic imaging. It is operated when doing.

The input unit 207c is operated when the operator sets information or imaging conditions of a patient who is a subject of radiographic imaging. As will be described later, the patient information and the imaging conditions are registered when the operator selects and inputs the imaging order information using the input unit 207c. The registration of the imaging order information can be performed at any timing before or after radiographic image capturing.
Further, the input unit 207c is configured to receive one or a plurality of input images transmitted from the radiographic image detector 1 used by the operator for radiographic imaging in the radiographic room R after radiographic imaging in the selected radiographic room R. This operation is performed when the association between the image data and the shooting order information input before or after shooting is determined.

  The display unit 207d includes a CRT (Cathode Ran Tube), an LCD (Liquid Crystal Display), and the like, and displays various information such as an image transmitted from the radiation image detector 1 and imaging order information. When a plurality of image data is transmitted from the same shooting room R, the display unit 207d displays the image data for each shooting room R together on the same screen.

  The storage means 207e is composed of a hard disk or the like and stores various information.

Specifically, the storage unit 207e stores the usage status of each of the imaging rooms R1 to R4, that is, whether each of the imaging rooms R1 to R4 is “in use” or “empty”. The console C assumes that the imaging room R that has not been selected by any operator can be selected as the imaging room R to be used for imaging, and notifies the storage means 207e that the imaging room R is “vacant”. Remember.
When the operator selects the selection room R using the input unit 207c prior to radiographic imaging, the console C determines that the imaging room R selected by the operator cannot be selected, and the imaging room in the storage unit 207e. Change the usage status of R from “vacant” to “in use”.

  The storage unit 207e stores a list of the radiation image detectors 1 that exist in each imaging room R. The list of the radiation image detectors 1 stored in the storage unit 207e stores the cassette ID, scintillator type information, size information, resolution, and the like of the radiation image detectors 1A to 1K existing in the imaging rooms R1 to R4. Has been. As described above, when the console C receives unique information including the cassette ID of the radiation image detector 1 detected by the tag reader 104 installed in the vicinity of the entrance of the front chamber Ra, it is registered in the storage means 207e. A list of radiation image detectors 1 existing in each imaging room R is referred to.

  Further, the storage unit 207e stores imaging order information including information on a patient who is a subject of radiographic imaging in the imaging room R1 and imaging conditions. The imaging order information is stored in advance in the storage unit 207e in a list format prior to radiographic imaging.

Further, the storage unit 207e stores the image data received from the radiation image detector 1 in association with the imaging order information.
In addition, the storage unit 207e stores the image data received from the radiation image detector 1 existing in the imaging room R where the imaging was performed in association with the imaging room ID of the imaging room R where the imaging was performed. The image data received from each photographing room R is stored for each photographing room R.
In addition, when a plurality of image data is transmitted from the radiation image detector 1 existing in one selected radiographing room R, the storage unit 207e groups and groups the image data. The image data is stored in association with the shooting room ID of the shooting room R.

The storage unit 207e receives the operator ID from the input unit 207c prior to radiographic imaging, and when the imaging room R is selected, the imaging room ID and operator ID of the selected imaging room R are selected. Are stored in association with each other.
When the console control unit 207a of the console C receives the image data transmitted from the radiation image detector in the imaging room R via the wireless access point 103 and the communication unit 107b, the console control unit 207a includes a header in the received image data. Based on the address of the wireless access point 103 attached as information, the wireless access point 103 through which the image data passes is determined. Then, the imaging room R corresponding to the wireless access point 103 through which the image data passes is specified as the imaging room R in which the radiation image detector 1 that transmitted the image data is arranged.

  Further, when the operator who has finished shooting in the shooting room R moves from the shooting room R to the console C selected as the image transmission destination and inputs the operator ID by the input means 207c, the console control means 207a The radiographic image detector 1 that has read the radiographing room ID of the radiographing room R and the image data that has been read out is arranged from the storage unit 207e, and the radiographing room ID of the radiographing room R associated with the input operator ID is read out. It is determined whether or not the shooting room ID of the shooting room R matches. If the two match, it is determined that the image was taken in the correct shooting room R, that is, the shooting room R selected by the operator. On the other hand, if the two do not match, it is determined that the image was taken by another operator.

  Further, when each of the consoles C1 to C3 updates its own storage unit 207e, the console C1 to C3 transmits the updated contents to other consoles C connected to the same network N. The contents of the storage means 207e of each console C1 to C3 are updated based on the latest data transmitted from the other consoles C.

  It should be noted that the list of radiographic image detectors 1, imaging order information, image data, etc. stored in the storage means 207e of each console C are stored in the data management server S, and the data management server S responds to a request from the console C. The data may be transmitted to the console C.

  In the present embodiment, the console C communicates with all the radiological image detectors 1A to 1K existing in each photographing room R via the communication means 107b, the wireless access point 103 provided in each photographing room R, or the like. Communication is now possible. The console C is associated with the selected shooting room R when the operator selects the shooting room R to be used for shooting by the input unit 207c.

  When the imaging room R to be used for imaging is selected by the input unit 207c, the console C has the radiation image detector 1 arranged in the first mode (sleep state) in the selected imaging room R. On the other hand, by transmitting the second mode transition signal, the power consumption mode of all the radiation image detectors 1 in the imaging room R is changed from the first mode mode1 (sleep state) to the second mode mode2 (waiting for irradiation). State).

  Further, when transmitting the second mode transition signal, the console C selects the console C that has been selected and input as the image data transmission destination by the input means 207c with respect to the radiation image detector 1 in the selected imaging room R. It comes to notify. The console C transmits, for example, identification information for identifying the console C selected as the image data transmission destination together with the second mode transition signal to detect the console C selected as the image data transmission destination as a radiation image. Notify vessel 1

  Further, when the console C is selected as the image data transmission destination console C, the console C wirelessly accesses the thinned-out image data transmitted from any one of the radiation image detectors 1 that detected the irradiation of radiation. Reception is made via the point 103 and the communication means 107b.

  The console control unit 207a of the console C is used for imaging, and receives the thinned image data from the radiation image detector 1 that has detected the irradiation of radiation, and as a specifying unit, analyzes the received thinned image data and is necessary for diagnosis A region of interest S is identified.

When the console control unit 207a of the console C specifies the region of interest S in the image data (raw data) based on the thinned image data transmitted from the radiation image detector 1, the console control unit 207a of the console C identifies the region of interest S in the image data (raw data). The position information is transmitted to the radiation image detector 1 that has transmitted the thinned image data via the communication unit 107 b and the wireless access point 103.
Further, the console control unit 207a transmits the position information of the region of interest S to the radiation image detector 1, and on the other hand, based on the analysis of the thinned image data and the operation of the imaging condition key, the imaging part in the radiographic imaging The image processing is performed on the thinned-out image data under the image processing conditions corresponding to the recognized imaging region, and a preview image (thinned-out image) as a display image is displayed on the display unit 107d.

  Then, as described above, in the radiation image detector 1 that has transmitted the thinned image data, based on the position information of the region of interest in the image data (raw data) received from the console C, the original image data ( The image data of the region of interest S is extracted from the raw data), and the extracted image data of the region of interest S is transmitted to the console C. The console C receives the image data of the region of interest S transmitted from the radiation image detector 1 via the wireless access point 103 and the communication unit 107b.

  Next, the console C performs image processing on the image data of the region of interest S acquired from the radiation image detector 1 under the same image processing conditions as the thinned image data, and the image is processed under the image processing conditions according to the imaging region. A diagnostic image based on the processed image data of the region of interest S is displayed on the display means 207d, and trimming correction, gradation correction, etc. are executed as necessary to determine the diagnostic image data. Further, diagnostic image data is stored in association with the registered imaging order information.

  When the association between the diagnostic image data and the registered imaging order information is confirmed, the console C determines that the radiographic imaging in the imaging room R has been completed, and the communication unit 107b and the wireless access point By transmitting a first mode transition signal instructing switching to the first mode mode1 (sleep state) via 103, all the radiation image detectors 1 existing in the imaging room R are irradiated with radiation. The mode is shifted from the detectable second mode mode2 (waiting for irradiation) to the first mode mode1 (sleeping state).

  Furthermore, after determining that the radiographic image capturing in the selected imaging room R has been completed, the console C changes the usage status of the imaging room R stored in the storage unit 207e from “in use” to “vacant”. Change to As a result, the photographing room R is switched from the non-selectable photographing room R to the selectable photographing room R.

  Next, a flow of radiographic imaging in the radiographic imaging system 200 according to the present embodiment will be described with reference to the flowcharts of FIGS.

  First, the radiation image detector 1 is arranged in the imaging room R in a state where the power consumption mode is the first mode mode1 (sleep state) (step S31 in FIG. 22).

  Prior to radiographic imaging, an operator who performs radiographic imaging inputs an operator ID assigned to the operator beforehand by using the input means 207c of the console C (step S32 in FIG. 22).

Next, the console control unit 207a of the console C reads out the imaging order information stored in the storage unit 207e (or obtains the imaging order information from the HIS / RIS via the network), and obtains it. To display.
The operator selects the imaging order information for the current radiographic imaging using the input unit 207c from the imaging order information displayed on the display unit 207d (step S33 in FIG. 22). Thereby, the imaging order information of the current radiographic imaging is registered.

Next, the console control unit 207a of the console C displays a selection screen (not shown) for selecting the console C as the image data transmission destination on the display unit 207d. On this selection screen, the operator selects the console C as the transmission destination of the image data from the radiation image detector 1 from the selectable consoles C1 to C3 (step S34 in FIG. 22).
Note that, in the default setting in selecting the image data transmission destination, the console C that has selected the imaging order information and the imaging room R is selected as the console of the image data transmission destination, and the operator can select another console. Unless C is selected as the image transmission destination, the console C that has selected the imaging order information and the imaging room R is automatically selected as the image data transmission destination.

  Next, the console control means 207a of the console C causes the display means 207d to display a selection screen (not shown) for selecting the imaging room R in which the imaging is performed, and the operator can take the current radiographic imaging on this selection screen. The shooting room R to be used is selected (step S35 in FIG. 33).

  In this selection screen, only “vacant” shooting rooms (for example, shooting rooms R1, R3, R4) can be selected, and a shooting room that is “in use” (for example, shooting room R2) is selected. I can't do it. In addition, in the selection screen, the cassette IDs of the radiation image detectors 1A to 1K existing in the imaging rooms R are displayed. For example, the operator can enter cassette IDs “1001” and “1002” in the imaging room R1. It can be recognized that there are two radiological image detectors 1A and 1B to which. As described above, the operator can select the imaging room R to be used for imaging after recognizing the radiation image detector 1 existing in each imaging room R. For example, information such as the type information, size information, and resolution of the scintillator of each radiation image detector may be displayed on the selection screen.

  When the shooting room R is selected, the console control unit 207a of the console C changes the usage status of the selected shooting room R from “vacant” to “usage” in the usage status of each shooting room R stored in the storage unit 207e. It is changed to “in use” (step S36 in FIG. 22). Thus, the photographing room R1 cannot be selected as the photographing room R used for photographing until the photographing is completed.

  Further, the console control means 207a of the console C associates the shooting room ID assigned in advance to the selected shooting room R with the operator ID input by the operator in the process of step S2, and stores the storage means 207e. (Step S37 in FIG. 22).

  In the following description, for example, an operator has four shooting rooms R1 to R4 so that the process in the shooting room R selected as the shooting room R used for shooting can be distinguished from the process in the other shooting rooms R. A case will be described in which the shooting room R1 is selected as the shooting room R for shooting. Further, for example, the operator selects the console C1 from among the three consoles C1 to C3 so that the processing in the console C selected as the image data transmission destination can be distinguished from the processing in the other consoles C. The case where it is selected as the destination console C will be described.

  Next, the console control unit 207a selects the second mode transition signal instructing switching to the second mode mode2 (irradiation waiting state) as the image data transmission destination via the communication unit 107b and the wireless access point 103. Along with the identification information of the console C1, the data is transmitted to all the radiation image detectors 1A and 1B existing in the selected imaging room R1 (step S38 in FIG. 22). In addition, the console C transmits the registered imaging order information to the management device 106 disposed in the front room Ra via a cable or the like. Then, based on the imaging order information transmitted from the console C, the management device 106 transmits and sets imaging region information, irradiation conditions, and the like to the console 105 via the management device 106.

On the other hand, when the control means 22 of each of the radiation image detectors 1A and 1B arranged in the selected imaging room R1 receives the second mode transition signal from the console C (step S39 in FIG. 22), the radiation detection element 7 In addition, the power switch mode is changed from the first mode mode 1 (sleep state) to the first mode by controlling the mode switch to be turned on and switching the reading circuit 17 to the standby mode in which power is not supplied. It switches to 2 mode mode2 (waiting for irradiation) (step S40 of FIG. 22).
Here, the second mode transition signal transmitted from the console C is received by all the radiation image detectors 1A and 1B in the selected imaging room R1. Therefore, all the radiographic image detectors 1A and 1B in the radiographing room R1 shift from the first mode mode1 (sleep state) to the second mode mode2 (irradiation waiting state) according to an instruction from the console C.

  When the operator completes the registration of shooting order information on the console C and the operation of selecting the shooting room R1 for shooting and the console C1 as the image data transmission destination, the operator moves from the console C to the shooting room R1, Radiographic imaging is performed using the desired radiographic image detector 1 from the radiographic image detectors 1A and 1B arranged in the second mode mode2 (waiting for irradiation) in the imaging room R1.

  When performing radiographic image capturing, the operator does not need to use the radiographic image detector 1 having a size suitable for the subject as long as the subject can be accommodated, as in the first embodiment. A large-size radiation image detector 1 can be used. Therefore, the operator does not need to prepare the radiation image detector 1 having a size suitable for the subject. For example, the operator can use the radiographic image detector 1 that has been used for the previous imaging and is still mounted on the standing-type or supine-type bucky device 101. The radiological image detector 1 can be used as it is.

  In the following, the process performed by the radiological image detector 1 used for imaging and the process performed by the radiographic image detector 1 not used for imaging will be described separately. Of the two radiological image detectors 1A and 1B arranged in the above, a case where radiographic imaging is performed using the radiographic image detector 1B will be described.

The control means 22 of the radiation image detectors 1A and 1B in the radiographing room R1 determines whether or not the voltage value V output from the current detection means 24 exceeds the threshold value Vth, and whether or not radiation irradiation has started. Determine whether. Then, the control means 22 of the radiation image detector 1B that is used for imaging and detects radiation irradiation detects that the voltage output from the current detection means 24 has exceeded the threshold value Vth due to radiation irradiation, and When it is determined that the irradiation has started (step S41 in FIG. 22), the mode changeover switch 18d is turned off to supply power to the readout circuit 17, and the readout circuit 17 is shifted to the power supply mode, whereby its own power consumption mode. Is switched from the second mode mode2 (waiting for irradiation) to the third mode mode3 (charge accumulation state) (step S42 in FIG. 22).
That is, of the two radiographic image detectors 1A and 1B arranged in the radiographing room R1, only one radiographic image detector 1B that is actually used for radiography is automatically exposed to the third radiation. While shifting to mode mode 3 (charge accumulation state), other radiation image detectors 1A that are not used for imaging are maintained in the second mode mode 2 (waiting for irradiation) state.

  Next, when a predetermined time has elapsed from the start of radiation irradiation, the control means 22 of the radiation image detector 1B used for imaging determines that radiation irradiation has ended (step S43 in FIG. 23). Then, the TFT 8 connected to each scanning line 5 is turned on by applying an on-voltage for signal reading to each scanning line 5 to the scanning drive circuit 15, and the power consumption mode is set to the third mode mode 3 (charge charge mode). The mode is switched from the accumulation state to the fourth mode mode 4 (reading state). Then, a read process for converting the electric charge accumulated in the radiation detection element 7 by the irradiation of radiation into an electric signal to acquire image data (raw data) is executed (step S44 in FIG. 23), and the read circuit 17 reads the data. The image data (raw data) is subjected to various image correction processes such as offset correction and stored in the storage means 23 (step S45 in FIG. 23).

  Next, the control means 22 of the radiation image detector 1B generates thinned image data based on the image data (raw data) read by the read circuit 17 (step S46 in FIG. 23). Then, the generated thinned image data is associated with the cassette ID “1005” assigned to itself and transmitted to the console C1 as the image data transmission destination via the antenna device 29 and the wireless access point 103 (FIG. 23 step S47).

  Then, the console C receives the thinned image data transmitted from the radiation image detector 1B used for imaging via the wireless access point 103 and the communication means 107b (step S48 in FIG. 23).

  Next, the console control unit 207a of the console C1 determines the wireless access point 103 through which the thinned-out image data has passed based on the address of the wireless access point 103 attached as the header information of the received thinned-out image data. It is determined whether shooting has been performed in the room R (step S49 in FIG. 23).

  Next, the operator who has finished taking radiographic images in the radiographing room R1 returns to the console C1 designated as the image data transmission destination from the radiographing room R1, and inputs the operator ID assigned to the operator by the input means 207c. (Step S50 in FIG. 23).

  When the operator ID is input by the input unit 207c, the console control unit 207a of the console C1 reads out the reading room ID of the shooting room R associated with the input operator ID from the storage unit 207e. Based on whether or not the shooting room ID of the shooting room R1 (that is, the shooting room R1 selected as the shooting room R used for shooting) matches the shooting room ID of the shooting room R where the shooting was actually performed. Then, it is confirmed that shooting has been performed in the shooting room R1 selected by the operator (step S51 in FIG. 23).

  Next, the console control unit 207a generates a preview image (thinned image) as a display image based on the thinned image data received from the radiation image detector 1B, and the generated preview image (thinned image) is input to the input unit 207c. In association with the imaging order information selected and registered by (2), it is displayed on the display means 207d (step S52 in FIG. 23). The operator looks at the thinned image (preview image) displayed on the display means 207d of the console C, and confirms whether re-shooting is necessary, whether it is associated with correct shooting order information, or the like.

  Here, when the console control means 207a of the console C1 receives a plurality of thinned-out image data from the same shooting room R1, the console control means 207a groups those image data received from the same shooting room R1 into the display means 207d. Display. As described above, when a plurality of thinned image data received from the same photographing room R1 is displayed on the display means 207d, an operator such as an engineer can display each thinned image data and photographing order information displayed on the display means 207d. Is corrected and the corresponding relationship between each thinned-out image data and photographing order information can be appropriately corrected and saved by pressing a confirmation button (not shown).

Next, the console control unit 207a specifies the region of interest S in the entire image data (raw data) of the detection unit P using the above-described method or the like based on the thinned image data received from the radiation image detector 1B ( Step S53 in FIG.
Further, when the region of interest S is specified, the console control unit 207a notifies the radiation image detector 1 that has transmitted the thinned image data of the position information indicating the position of the region of interest S in the image data (raw data). (Step S54 in FIG. 24).
When a plurality of thinned image data is received from the same shooting room R1, the console control unit 207a specifies the region of interest S based on each of the thinned image data received from the same shooting room R1. The specified region of interest S is notified to the radiation image detector 1 that has transmitted the thinned image data.

When the control means 22 of the radiation image detector 1B receives the position information of the region of interest S in the image data (raw data) transmitted from the console C, the original image data (raw data) read by the reading circuit 17 is received. Is extracted from the original image data (raw data) based on the received positional information of the region of interest S (step S55 in FIG. 24).
Then, the extracted image data of the region of interest S is transmitted to the console C via the antenna device 29 and the wireless access point 103 (step S56 in FIG. 24).

  On the other hand, when the console C receives the image data of the region of interest S transmitted from the radiation image detector 1B (step S57 in FIG. 24), has the image data of the plurality of regions of interest S received from the same imaging room R? It is determined whether or not (step S58 in FIG. 24). If it is determined that image data of a plurality of regions of interest S has been received from the same imaging room R (step S58 in FIG. 24; Yes), the imaging data of the imaging room R is added to the image data of the plurality of regions of interest S. By associating the room IDs, the image data (raw data) of each region of interest S is grouped by the photographing room R (step S59 in FIG. 24). Note that the same processing as the grouping processing of image data in the photographing room R unit is also performed when the above-described thinned image data is acquired.

  Further, the console control unit 207a of the console C1 performs image processing on the received image data of the region of interest S under image processing conditions corresponding to the imaging region, and the image of the region of interest S is input by the input unit 207c. It is displayed on the display means 207d in association with the photographing order information (step S60 in FIG. 24). At this time, when there are a plurality of image data received from the same photographing room R, the console control means 207a displays the image data as a group on the same screen.

The operator looks at the image of the region of interest S displayed on the display means 207d of the console C, and operates the input means 207c as necessary to perform trimming correction (step S61 in FIG. 24). An operation to confirm the image for diagnosis is performed.
Then, the console control unit 207c determines the image data that has undergone image processing or trimming correction under the image processing conditions according to the imaging region as a diagnostic image, associates it with imaging order information, and imaging is performed. Each of the shooting rooms R is stored in the storage unit 207a in association with the shooting room ID of the shooting room R (step S62 in FIG. 24).

  Further, when the correspondence between the diagnostic image data and the imaging order information is determined, the console control means 207a determines that the imaging in the imaging room R1 has ended, and all the existing in the imaging room R1. A first mode transition signal instructing the radiographic image detectors 1A and 1B to switch the power consumption mode to the first mode mode1 (sleep state) is transmitted via the communication unit 107b and the wireless access point 103 ( Step S63 in FIG.

  Then, the first mode transition signal transmitted from the console C1 selected as the image data transmission destination is received by all the radiation image detectors 1A and 1B arranged in the imaging room R1. Thereby, the power consumption mode of all the radiation image detectors 1A and 1B in the imaging room R1 used for imaging is switched from the second mode mode2 (irradiation waiting state) to the first mode mode1 (sleep state) ( In addition, in step S64 in FIG. 24, the photographing room R1 is switched to the vacant state, and a series of processing ends.

  As described above, even in the radiographic image capturing system 200 according to the second embodiment, when a subject is arranged in a part of the detection unit P and radiographic image capturing is performed, detection of the imageable region is detected. Only the image data of the region where the subject is arranged and irradiated with radiation, that is, the image data of the region of interest S necessary for diagnosis can be transmitted to the console C instead of the entire image data of the part P. It is no longer necessary to spend unnecessary time and power consumption in transmitting image data of unnecessary areas, and the transmission time of image data can be shortened compared to the case where all image data of the detection unit P is transmitted to the console C. In addition, the efficiency of radiographic image capturing can be improved.

  Further, even in a system in which the console C is shared among a plurality of imaging rooms R as in the radiographic imaging system 200 of the present embodiment, the image data acquired in the console C is transferred to the selected imaging room R. Since the images are associated and stored for each photographing room R, it is possible to prevent image data from being mixed and to correctly associate with photographing order information.

  Further, since the operator can select a shooting room R to be used for shooting from a plurality of shooting rooms R, the operator can perform shooting in a desired shooting room R, and the operation System that is easy for users to use.

  In the second embodiment, the radiological image detector 1 in the radiographing room R selected as the radiographing room R used for radiographing is the region of interest transmitted from the radiographic image detector 1 in the radiographing room R. After the association between the image data of S and the imaging order information is confirmed, the power consumption mode is changed from the second mode mode 2 (waiting for irradiation) to the first mode mode 1 (in accordance with the first mode transition signal transmitted from the console C). Although the case where it was comprised so that it may switch to a sleep state) was demonstrated, the timing which switches the power consumption mode of the radiographic image detector 1 which does not detect irradiation of radiation to 1st mode mode1 (sleep state) is not limited to this.

  For example, in the radiation image detector 1, the power consumption mode is switched from the first mode mode 1 (sleep state) to the second mode mode 2 (irradiation waiting state) in response to the second mode transition signal transmitted from the console C. Thereafter, when radiation irradiation is not detected within a predetermined time, the control means 22 automatically switches the power consumption mode from the second mode mode2 (waiting for irradiation) to the first mode mode1 (sleeping state). You may do it. With this configuration, it is necessary to exchange a signal or the like for shifting the power consumption mode of the radiation image detector 1 to the first mode mode 1 (sleep state) between the console C and the radiation image detector 1. And the control configuration is further simplified.

  In addition, when radiographic imaging is performed only once in one imaging room R, the console C is used for imaging after receiving thinned image data from the radiographic image detector 1 used for imaging. All the radiation image detectors 1 other than the radiation image detector 1 may be configured to be switched from the second mode mode 2 (irradiation waiting state) to the first mode mode 1 (sleep state). Whether or not radiographic imaging is performed a plurality of times can be determined based on, for example, the number of imaging order information input prior to imaging.

  In addition, when radiographic imaging is performed only once in the radiographing room R, the radiation image detector 1 that has detected the irradiation of radiation further performs the irradiation of the radiation immediately when the radiation irradiation is detected. The console C is notified of the detection together with its own cassette ID, and the console C that has received the notification enters the first mode for the radiation image detectors 1 other than the radiation image detector 1 that has detected the radiation irradiation. By transmitting a first mode transition signal instructing switching, the power consumption mode of the radiation image detector 1 that does not detect radiation irradiation is changed from the second mode mode2 (waiting for irradiation) to the first mode mode1 (sleeping state). You may comprise so that it may switch to. With this configuration, the power consumption mode of the radiation image detector 1 that is not used for imaging can be switched to the first mode mode1 (sleep state) at an earlier stage, and the power consumption can be further reduced. .

Further, the control means 22 of the radiation image detector 1 used for imaging and detecting radiation irradiation transmits the original image data (raw data) to the console C, and then sets the power consumption mode of the apparatus to the first. You may be comprised so that it may switch to mode mode1 (sleep state).

  The scope of the present invention is not limited to the above embodiment, and various improvements and design changes may be made without departing from the spirit of the present invention.

  For example, in the first embodiment and the second embodiment, the readout circuit 17 of the radiation image detector 1 reads out the electric charges generated and accumulated in each radiation detection element 7 and converts them into electrical signals. A possible power supply mode and a standby mode in which no charge is read from each radiation detection element 7, and the readout circuit 17 is in the standby mode, based on an increase in current flowing through the bias line. The case where it is configured to detect the start of radiation irradiation has been described. However, the present invention can also be applied to the radiation image detector 1 that does not switch the mode of the readout circuit 17 and does not detect the start of radiation irradiation. Even in that case, only the thinned-out image data and the image data of the region of interest S are transmitted from the radiological image detector 1 to the console as in the above-described embodiment. It is possible to improve and shorten the transmission time of image data.

In order to detect the start of radiation irradiation, instead of providing a threshold value Vth for the voltage value V itself, for example, a threshold value ΔVth is provided for the change rate ΔV of the voltage value V, and the increase rate ΔV of the voltage value V is the threshold value. The time when ΔVth is exceeded may be detected as the radiation irradiation start time tstart, and the time when the absolute value of the decrease rate ΔV of the voltage value V becomes equal to or greater than the threshold value ΔVth may be detected as the radiation irradiation end time tend.
Further, for example, by integrating the voltage value V output from the current detection means 24 from the irradiation start time tstart to the irradiation end time tend and converting it to a current value corresponding thereto, a radiographic image detector You may comprise so that the dose of the radiation irradiated to 1 may be estimated.
In addition, the voltage value V output from the current detection unit 24 is configured to be peak-held, and the product of the maximum value Vp and the time interval between the irradiation start time tstart and the irradiation end time tend is calculated. The transition of the trapezoidal shape of the voltage value V shown in FIG. 11 is approximated to a rectangular shape to estimate the total amount of the voltage value V, and based on this, the radiation dose irradiated to the radiation image detector 1 is estimated. May be.

In each of the above embodiments, the configuration has been described in which the console grasps in advance the radiological image detector existing in the imaging room. However, the radiological image detectors existing in the imaging room are shifted to the second mode mode2. In this case, the thinned image data and the original image data are automatically transmitted to the console from the radiation image detector that has detected the radiation irradiation. It is not always necessary to know.
For this reason, in the above-described embodiment, a case has been described in which the radiographic image detector includes a tag that stores a cassette ID or the like, and the radiographic image detector present in the imaging room R is detected by the tag reader. A tag or tag reader is not necessarily required.

  In addition, it goes without saying that the present invention is not limited to the above-described embodiment and can be modified as appropriate.

DESCRIPTION OF SYMBOLS 100 Radiographic imaging system 1 Portable radiographic image detector 7 Radiation detection element 9 Bias line 14 Reverse bias power supply 17 Read-out circuit 22 Control means (generation means, transmission means, control means)
24 Current detection means 27 Battery 20 Antenna device (communication means)
107 console 107a console control means (identification means, notification means)
107c Input means 200 Radiographic imaging system 207a Console control means (identification means, notification means)
207c Input means (selection means)
A Direct irradiation area C1 to C3 (C) Console P Detection unit R1 to R4 (R) Imaging room S Area of interest
mode 1 first mode
mode 2 Second mode
mode 3 3rd mode

Claims (8)

A portable radiographic image detector having a detection unit that includes two-dimensionally arranged radiation detection elements that include a communication unit and generate a signal in accordance with the radiation dose, and the portable radiographic image detector A radiographic imaging system comprising a console capable of communicating with
The portable radiation image detector is
A readout circuit that reads out the signal from each radiation detection element and converts it into image data;
Storage means for storing the image data read by the read circuit;
Generating means for generating thinned image data based on the image data read by the read circuit;
Transmitting means for transmitting the thinned image data generated by the generating means to the console;
With
The console is
Acquiring the thinned image data transmitted from the portable radiographic image detector, and specifying a region of interest based on the acquired thinned image data;
Notification means for notifying the portable radiation image detector of the positional information of the region of interest specified by the specifying means;
With
The portable radiation image detector is
Based on the position information of the region of interest notified from the console, image data of the region of interest is extracted from the image data read by the readout circuit, and the extracted image data of the region of interest is extracted from the console. The radiographic imaging system characterized by transmitting to. The console is
The radiation irradiation region in the thinned image data is extracted based on the thinned image data transmitted from the portable radiation image detector, and the extracted radiation irradiation region is specified as the region of interest. Item 2. The radiographic image capturing system according to Item 1. The console is
Based on the thinned image data transmitted from the portable radiation image detector, the radiation irradiation area in the thinned image data is extracted, and the direct irradiation area directly irradiated with radiation is excluded from the extracted radiation irradiation area The radiographic image capturing system according to claim 1, wherein the remaining region is specified as the region of interest. The console is
The radiation according to any one of claims 1 to 3, wherein the registered imaging order information and the image data of the region of interest transmitted from the portable radiation image detector are associated with each other. Image shooting system. The console is
The radiographic image capturing system according to claim 1, wherein a display image is generated based on the thinned image data transmitted from the portable radiographic image detector. The portable radiation image detector includes a battery,
The radiographic imaging system according to claim 1, wherein the portable radiographic image detector and the console communicate with each other in a wireless manner. The readout circuit is
A power supply mode in which a signal generated and accumulated in each radiation detection element can be read and converted into image data, and the power consumption mode is lower than that in the power supply mode without reading the signal. And a standby mode that is
The portable radiation image detector is
It is arranged in one shooting room,
A reverse bias power source for applying a reverse bias voltage to each radiation detection element via a bias line;
Current detection means for detecting a current flowing through the bias line;
A battery serving as a power supply source of the portable radiation image detector;
When the readout circuit is in the standby mode, the readout is performed when it is detected that the radiation irradiation has started due to an increase in the amount of the current flowing through the bias line detected by the current detection unit. Control means for transitioning the circuit from the standby mode to the power supply mode;
With
The control means includes a power consumption mode of the apparatus, a first mode in which the reverse bias voltage is not applied to each radiation detection element and power is not supplied to the readout circuit, and the reverse bias voltage is applied to each radiation detection element. And a second mode in which the readout circuit is set to the standby mode, and a third mode in which the reverse bias voltage is applied to each radiation detection element and the readout circuit is changed from the standby mode to the power supply mode. Can be switched between and
The console is
An input means for inputting predetermined information;
In response to the input of the predetermined information in the input means, the power consumption mode of all the portable radiographic image detectors existing in the imaging room is shifted to the second mode,
The control means of the portable radiation image detector that has shifted to the second mode,
The image data is read by the reading circuit by switching the power consumption mode from the second mode to the third mode when detecting that the irradiation of the radiation is started. The radiographic imaging system according to any one of claims 1 to 6. The readout circuit is
A power supply mode in which a signal generated and accumulated in each radiation detection element can be read and converted into image data, and the power consumption mode is lower than that in the power supply mode without reading the signal. And a standby mode that is
The portable radiation image detector is
It is arranged in each of multiple shooting rooms,
A reverse bias power source for applying a reverse bias voltage to each radiation detection element via a bias line;
Current detection means for detecting a current flowing through the bias line;
A battery serving as a power supply source of the portable radiation image detector;
When the readout circuit is in the standby mode, the readout is performed when it is detected that the radiation irradiation has started due to an increase in the amount of the current flowing through the bias line detected by the current detection unit. Control means for transitioning the circuit from the standby mode to the power supply mode;
With
The control means includes a power consumption mode of the apparatus, a first mode in which the reverse bias voltage is not applied to each radiation detection element and power is not supplied to the readout circuit, and the reverse bias voltage is applied to each radiation detection element. And a second mode in which the readout circuit is set to the standby mode, and a third mode in which the reverse bias voltage is applied to each radiation detection element and the readout circuit is changed from the standby mode to the power supply mode. Can be switched between and
The console is
A selection means for selecting a shooting room to be used for shooting from the shooting room;
In response to the selection of the imaging room used for the imaging by the selection unit, the power consumption mode of all the portable radiation image detectors present in the imaging room selected by the selection unit is set to the second mode. To
The control means of the portable radiation image detector that has shifted to the second mode,
When it is detected that the irradiation of radiation is started, the power consumption mode is switched from the second mode to the third mode, and the image data is read by the readout circuit,
The radiographic imaging system according to claim 1, wherein the console stores image data received from the selected imaging room in association with the imaging room.

Images