JP2012095832A - Radiographic image photographing system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiographic image photographing system which, when photographing is performed for the prescribed number of times, accurately detects that the photographing has been performed for the prescribed number of times, and which enables the power supply mode of a plurality of radiographic image photographing apparatuses inside a photographing chamber to accurately transition to a sleep mode.SOLUTION: The radiographic image photographing system 50 includes the plurality of radiographic image photographing apparatuses 1 which can switch the power supply mode between a photographing possible mode during which power is supplied to a radiation detection element 7 and radiographic image photographing can be performed and the sleep mode during which the power is supplied only to required function parts and the radiographic image photographing cannot be performed, and a console 58 selecting photographing order information. At the point of time when radiographic images p generated on the basis of transmitted image data D is established, the console 58 determines whether or not the number of the selected photographing order information and the number of the established radiographic images p match, and immediately causes the power supply mode of the plurality of radiographic image photographing apparatuses 1 to transition to the sleep mode when they match.

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. In order to digitize radiographic images, CR (Computed Radiography) devices using stimulable phosphor sheets have been developed recently. Then, a radiation image capturing apparatus has been developed in which irradiated radiation is detected by a radiation detection element arranged in a two-dimensional form and acquired as digital image data.

  This type of radiographic image capturing apparatus is known as an FPD (Flat Panel Detector), and is conventionally formed as a so-called dedicated type radiographic image capturing apparatus formed integrally with a support base (for example, Patent Documents). 1). However, in recent years, a portable radiographic imaging apparatus in which a radiation detection element or the like is accommodated in a housing has been developed and put into practical use (see, for example, Patent Documents 2 and 3). In such portable radiographic imaging apparatuses, a radiographic imaging apparatus that has a built-in battery and that transmits and receives signals and data by exchanging radio waves via an antenna apparatus has been developed (for example, Patent Document 4). Etc.).

  In addition, as a radiographic imaging apparatus, a so-called direct type radiographic imaging apparatus that generates a charge in a detection element in accordance with a dose of irradiated radiation such as X-rays and converts it into an electric signal, or irradiated radiation A so-called indirect type in which after being converted into electromagnetic waves of other wavelengths such as visible light with a scintillator or the like, electric charges are generated by photoelectric conversion elements such as photodiodes in accordance with the energy of the converted and irradiated electromagnetic waves and converted into electric signals Various radiographic imaging devices have been developed. In the present invention, the detection element in the direct type radiographic imaging apparatus and the photoelectric conversion element in the indirect type radiographic imaging apparatus are collectively referred to as a radiation detection element.

  By the way, as described in Patent Documents 5 and 6 and the like, in the dedicated radiographic imaging apparatus, the lifetime of the radiation detection element and the like becomes shorter as the energization time of the radiation detection element and the like becomes shorter. As a power supply mode for each function unit such as a detection element and a control means, only a function capable of capturing radiographic images by supplying power to each function unit, and a function unit necessary for suppressing power consumption In many cases, power is supplied and at least the radiation detecting element can be switched between a sleep mode in which the supply of power is stopped and radiographic imaging cannot be performed.

  And in patent document 5, when the some radiographic imaging apparatus (it describes as a sensor unit in the same literature) exists in an imaging | photography room, the radiographic imaging apparatus used for one imaging | photography is one. Therefore, for the radiographic imaging device, the power supply mode is set to the imaging enable mode, but for other radiographic imaging devices, the power supply mode is changed to the sleep mode, and the lifetime of the radiation detection element or the like A radiation imaging system for extending the life is described.

  Further, in Patent Document 6, once the power supply mode of the radiographic image capturing apparatus is changed to the sleep mode, the radiographic image capturing apparatus is used when the radiographic image capturing apparatus is changed from the sleep mode to the radiographable mode in order to use for radiography. Since it takes time until the image capturing apparatus is actually ready for capturing, for example, when a plurality of radiographic image capturing apparatuses in the capturing room are not used for a predetermined time, a transition to sleep mode or radiation is performed. Radiation that prevents the above problems from occurring while prolonging the life of radiation detection elements, etc. by setting a long predetermined time until transition to the sleep mode according to the frequency of use of the image capturing device An imaging system is described.

  In particular, in a portable radiographic imaging device with a built-in battery, if the battery power is consumed wastefully, the battery needs to be charged frequently, and the number of imaging per charge is reduced. The use efficiency for one charge will fall remarkably. Therefore, also in the portable radiographic imaging device with a built-in battery, the power supply mode for each functional unit is switched between the radiographable mode and the sleep mode as in the case of the dedicated radiographic imaging device described above. It is desirable to be able to do so.

Japanese Patent No. 3639750 JP 2006-058124 A JP-A-6-342099 JP-A-7-140255 JP 2000-308630 A JP 2002-272721 A

  However, in the case of a dedicated radiographic imaging apparatus and a portable radiographic imaging apparatus with a built-in battery, for example, it is known that imaging is performed a predetermined number of times. In such a case, since all of the imaging has been completed, the predetermined time has not passed, so the power supply mode of the radiographic imaging device does not transition to the sleep mode, If the state continues, power will be wasted.

  That is, for example, when it is known in advance that four times of imaging are performed using a radiographic imaging device in the imaging room, when those four times of imaging are completed, the imaging is performed after that. No state.

  Nevertheless, for example, because the radiographic imaging device used for the last imaging is left in the imaging enabled mode, or the predetermined time until the transition to the sleep mode has not elapsed, If the image capture mode is maintained until the predetermined time elapses, the power is wasted correspondingly, and the life of the radiation detection element or the like is shortened or the battery power is wasted. There is a possibility of becoming.

  The present invention has been made in view of the above-described problems. When a predetermined number of times of photographing is performed, the fact that the predetermined number of times of photographing has been performed is accurately detected, and a plurality of images in the photographing room are obtained. An object of the present invention is to provide a radiographic image capturing system capable of accurately shifting the power supply mode of the radiographic image capturing apparatus to the sleep mode.

In order to solve the above-described problem, the radiographic imaging system of the present invention includes:
A detection unit in which a plurality of radiation detection elements that generate an electric charge according to an irradiation dose of radiation are arranged in a two-dimensional manner;
A readout circuit that reads out the electric charge from each of the radiation detection elements, converts the electric charge into image data and reads out the data for each of the radiation detection elements;
A communication means capable of transmitting and receiving signals to and from an external device;
The read image data is transmitted via the communication means, and a power supply mode for each functional unit is set to a radiographable mode that enables radiographic imaging by supplying power to the radiation detection element, Control means for switching between a sleep mode in which power is supplied only to necessary function units including a communication means and the radiation detection element is stopped to supply power and radiographic imaging cannot be performed,
A plurality of radiographic imaging devices comprising:
The imaging order information is acquired, the imaging is performed based on the selected imaging order information, and the image data is transmitted from the radiographic imaging apparatus, and is generated and determined based on the image data. A console for associating a radiographic image with the imaging order information;
With
The console, when a radiographic image generated based on the image data transmitted from the radiographic imaging device is determined, the number of selected radiographing order information and the number of the determined radiographic images And the power supply mode of the plurality of radiographic imaging devices is immediately shifted to a sleep mode at the time of matching.

  According to the radiographic image capturing system of the system as in the present invention, the console generates a radiographic image determined based on the number of selected radiographing order information and the image data transmitted from the radiographic image capturing apparatus. When the number of selected radiographing order information matches the number of confirmed radiographic images, the power supply mode of a plurality of radiographic imaging devices is immediately set to the sleep mode. Transition to.

  Therefore, even though all the imaging based on the imaging order information selected by the radiographer or other radiographer is completed, the power supply mode of each radiographic imaging apparatus continues to be the radiographable mode, and power is wasted. It is possible to accurately prevent consumption, and even when viewed as an entire radiographic imaging system as well as individual radiographic imaging apparatuses, wasteful consumption of power is prevented, and the entire radiographic imaging system can be prevented. It becomes possible to further reduce power consumption required for operation.

  For this reason, the power supply mode of the radiographic imaging device remains in the radiographable mode and the energized state continues, shortening the life of the radiation detection element, etc. It is possible to accurately prevent the occurrence of a situation such as a drop in battery power or a battery running out during shooting.

It is a figure which shows the whole structure of the radiographic imaging system which concerns on this embodiment. It is an external appearance perspective view of a radiographic imaging device. It is the external appearance perspective view which looked at the radiographic imaging apparatus of FIG. 2 from the other side. It is sectional drawing which follows the AA line in FIG. It is a top view which shows the structure of the board | substrate of a radiographic imaging apparatus. It is an enlarged view which shows the structure of the radiation detection element, TFT, etc. which were formed in the small area | region on the board | substrate of FIG. It is a side view explaining the board | substrate with which a flexible circuit board, a PCB board | substrate, etc. were attached. It is a block diagram showing the equivalent circuit of a radiographic imaging apparatus. It is an external appearance perspective view showing the state to which the connector of the radiographic imaging device and the connector of the Bucky device were connected. It is a figure explaining the Bucky apparatus provided with the connector inside the cassette holding | maintenance part. It is sectional drawing showing the state by which the radiographic imaging apparatus was inserted in the cradle and the connectors were connected. It is a figure which shows a structure provided with a tag reader. It is a figure which shows the example of imaging | photography order information. It is a figure which shows the example of the selection screen which displays imaging | photography order information. It is a figure which shows the example of the screen on which each icon etc. corresponding to each imaging | photography order information selected were displayed. FIG. 16 is a diagram illustrating an example of a preview image displayed on the screen of FIG. 15 in an enlarged manner. It is a figure which shows the state by which the preview image was displayed on the position of the focused original icon. It is a figure which shows the state by which the next icon was focused and the radiographic image was displayed in the position of the original icon. It is a figure which shows the display for image quality adjustment displayed on the screen right side. It is a figure which shows the state by which each radiographic image corresponding to each icon was each displayed on the position where each icon was displayed.

  Embodiments of a radiation image capturing system according to the present invention will be described below with reference to the drawings. However, the present invention is not limited to the following illustrated examples.

  In the present embodiment, a plurality of portable radiographic imaging devices 1 with a built-in battery are provided, and the portable radiographic imaging device 1 is loaded into a bucky device 51 (see FIG. 1 and the like described later) or a bucky. The case where imaging is performed by being used alone without being loaded into the apparatus 51 will be described. As described above, the radiographic imaging apparatus 1 is a so-called dedicated machine formed integrally with a support base (not shown). The present invention is also applied to a case where a radiographic imaging apparatus of a type is formed.

  Therefore, a dedicated radiographic imaging device may be included in the plurality of radiographic imaging devices 1, and all the radiographic imaging devices may be dedicated. If the present invention is applied to a dedicated-type radiographic imaging apparatus, beneficial effects such as the extension of the lifetime of the radiation detection element and the like can be obtained.

  Further, when the radiographic imaging device 1 is a portable type with a built-in battery, as described above, if the battery is wasted, the use efficiency is lowered, and further, the battery is cut off during imaging. Since the situation may occur, if the present invention is applied to a portable radiographic imaging device with a built-in battery, the possibility that such a situation may occur can be suppressed to a very low level. An effect is obtained.

  FIG. 1 is a diagram showing an overall configuration of a radiographic imaging system according to a first embodiment of the present invention described below.

  The imaging room Ra is a room that irradiates a subject that is a part of the patient's body (that is, the imaging region of the patient) and performs radiographic imaging, and generates radiation from a radiation irradiation device that irradiates the subject with radiation. A radiation source 52 of the apparatus 57 is disposed. Note that the imaging room Ra is shielded with lead or the like so that radiation does not leak outside the imaging room.

  In the present embodiment, a portable radiographic image capturing device as described below is used as the radiographic image capturing device 1, and the imaging room Ra can be loaded with a bucky that can be loaded with the radiographic image capturing device 1. A device 51 is provided. The bucky device 51 and the radiation source 52 will be described later. In addition, as described above, a part or all of the radiographic imaging apparatus 1 may be a so-called dedicated machine type radiographic imaging apparatus integrally formed with a support base (not shown).

  Here, first, the radiographic image capturing apparatus 1 used for radiographic image capturing in the radiographic image capturing system 50 will be described.

  In the following, a so-called indirect radiation image capturing apparatus that includes a scintillator or the like and converts the emitted radiation into electromagnetic waves of other wavelengths such as visible light to obtain an electrical signal will be described as the radiation image capturing apparatus 1. However, the present invention can also be applied to a so-called direct type radiographic imaging apparatus that directly detects radiation with a radiation detection element without using a scintillator or the like.

  FIG. 2 is an external perspective view of the radiographic image capturing apparatus, and FIG. 3 is an external perspective view of the radiographic image capturing apparatus viewed from the opposite side. 4 is a cross-sectional view taken along the line AA in FIG. As shown in FIGS. 2 to 4, the radiographic image capturing apparatus 1 includes a housing 2 in which a sensor panel SP including a scintillator 3 and a substrate 4 is accommodated.

  As shown in FIG. 2 and FIG. 3, a hollow rectangular tube-shaped housing body 2A having a radiation incident surface R in the housing 2 of the radiographic imaging apparatus 1 is made of a carbon plate or plastic that transmits radiation. The housing 2 is formed by closing the openings on both sides of the housing main body 2A with lid members 2B and 2C. Instead of forming the casing 2 as such a so-called monocoque type, for example, a so-called lunch box type formed of a frame plate and a back plate can be used.

  As shown in FIG. 2, the lid member 2B on one side of the housing 2 is composed of a power switch 37, a selection switch 38, a connector 39, an LED for displaying a battery state, an operating state of the radiographic imaging apparatus 1, and the like. The indicator 40 and the like are arranged.

  As shown in FIG. 3, an antenna device 41 that is a communication means for wirelessly transferring image data or the like to the console 58 is embedded in the lid member 2 </ b> C on the opposite side of the housing 2. In the case where the antenna device 41 is provided, the location of the antenna device 41 on the housing 2 and the number of antenna devices 41 to be arranged are appropriately determined. It is also possible to transfer the image data and the like to the console 58 in a wired manner. In this case, for example, the connector 39 described above functions as a communication means, and a cable or the like is connected to the connector 39 to transmit / receive. Configured to do.

  As shown in FIG. 4, a base 31 is disposed inside the housing 2 via a lead thin plate (not shown) on the lower side of the substrate 4 of the sensor panel SP. A PCB substrate 33, a buffer member 34, and the like on which are disposed are mounted.

  A glass substrate 35 for protecting the substrate 4 and the scintillator 3 on the radiation incident surface R side is disposed. In addition, a cushioning material 36 is provided between the sensor panel SP and the side surface of the housing 2 to prevent them from colliding with each other.

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

  The substrate 4 is made of a glass substrate. As shown in FIG. 5, a plurality of scanning lines 5 and a plurality of signal lines 6 cross each other on the surface 4a of the substrate 4 facing the scintillator 3. It is arranged to do. 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.

  In this way, the entire region r in which a plurality of radiation detection elements 7 arranged in a two-dimensional manner (also referred to as a matrix) is provided in each small region r partitioned by the scanning lines 5 and the signal lines 6, that is, FIG. A region indicated by an alternate long and short dash line in FIG.

  Although a photodiode is used as the radiation detection element 7, for example, a phototransistor or the like can also be used. As shown in FIG. 6 which is an enlarged view of FIG. 5, each radiation detection element 7 is connected to a source electrode 8s of a TFT 8 which is a switch means. The drain electrode 8 d of the TFT 8 is connected to the signal line 6.

  The TFT 8 is turned on when a turn-on voltage is applied to the gate electrode 8g via the scanning line 5 from the scanning driving means 15 described later, and is accumulated in the radiation detection element 7 via the source electrode 8s and the drain electrode 8d. The charged electric charge is discharged to the signal line 6. The TFT 8 is turned off when an off voltage is applied to the gate electrode 8g via the connected scanning line 5, and the emission of the charge from the radiation detecting element 7 to the signal line 6 is stopped, and the radiation detecting element The electric charge is held in 7.

  As shown in FIG. 6, the bias lines 9 are respectively connected to the plurality of radiation detection elements 7 arranged in a row. As shown in FIG. 5, each bias line 9 is connected to the detection unit P of the substrate 4. It is bound to one connection 10 at the outer position.

  In addition, each scanning line 5, each signal line 6, and connection line 10 of the bias line 9 are connected to input / output terminals (also referred to as pads) 11 provided near the edge of the substrate 4. As shown in FIG. 7, each input / output terminal 11 includes a flexible circuit board (also referred to as a chip on film) 12 in which a chip such as an IC 12a is incorporated on a film, an anisotropic conductive adhesive film (Anisotropic Conductive Film). And an anisotropic conductive adhesive material 13 such as anisotropic conductive paste (Anisotropic Conductive Paste).

  The flexible circuit board 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. Thus, the board | substrate 4 part of sensor panel SP of the radiographic imaging apparatus 1 is formed. In FIG. 7, illustration of the electronic component 32 and the like is omitted.

  Here, the circuit configuration of the radiation image capturing apparatus 1 will be described with reference to FIG.

  A bias line 9 is connected to one electrode of each radiation detection element 7, and each bias line 9 is bound to a connection 10 and connected to a bias power supply 14. The bias power source 14 applies a bias voltage (strictly speaking, a reverse bias voltage) to the electrode of each radiation detection element 7 via the connection 10 and each bias line 9.

  The other electrode of each radiation detection element 7 is connected to the source electrode 8s (denoted as S in FIG. 8) of the TFT 8, and the gate electrode 8g (denoted as G in FIG. 8) of each TFT 8. Are connected to the lines L1 to Lx of the scanning line 5 extending from the gate driver 15b of the scanning driving means 15, respectively. Further, the drain electrode 8d (denoted as D in FIG. 8) of each TFT 8 is connected to each signal line 6.

  The scanning drive unit 15 includes a power supply circuit 15a that supplies an on voltage and an off voltage to the gate driver 15b, and a gate driver 15b that switches a voltage applied to each of the lines L1 to Lx of the scanning line 5 between the on voltage and the off voltage. It has. As described above, the gate driver 15b switches the voltage applied to the gate electrode 8g of the TFT 8 via the lines L1 to Lx of the scanning line 5 between the on-voltage and the off-voltage, It is designed to control the off state.

  Each signal line 6 is connected to each readout circuit 17 formed in the readout IC 16. The readout circuit 17 includes an amplifier circuit 18, a correlated double sampling circuit 19, an analog multiplexer 21, and an A / D converter 20.

  For example, when a radiation image is captured, when radiation is applied to the radiation image capturing apparatus 1 through a subject, the scintillator 3 converts the radiation into an electromagnetic wave of another wavelength, and the converted electromagnetic wave is detected immediately below the radiation. The element 7 is irradiated. Then, charges are generated in the radiation detection element 7 in accordance with the dose of irradiated radiation (that is, the amount of electromagnetic wave).

  In the reading process of the image data D from each radiation detection element 7, when an ON voltage is applied to a predetermined line Ln of the scanning line 5 from the gate driver 15 b of the scanning driving unit 15, the line Ln of the scanning line 5 is A turn-on voltage is applied to the gate electrode 8g of each TFT 8 connected to the TFT 8 so that each TFT 8 is turned on, and a signal is transmitted from the radiation detection element 7 connected to each turned-on TFT 8 through each TFT 8. Charge is released to the line 6.

  Then, a voltage value is output from the amplifier circuit 18 in accordance with the amount of charge emitted from the radiation detection element 7, and is correlated double-sampled by the correlated double sampling circuit 19, and the analog value image data D is sent to the multiplexer 21. Is output. The image data D sequentially output from the multiplexer 21 is sequentially converted to digital image data D by the A / D converter 20, output to the storage means 23 and sequentially stored.

  The control means 22 includes a CPU (Central Processing Unit), ROM (Read Only Memory), RAM (Random Access Memory), a computer having an input / output interface connected to the bus, an FPGA (Field Programmable Gate Array), and the like. ing. It may be configured by a dedicated control circuit.

  The control unit 22 controls the operation of each functional unit such as the scanning drive unit 15 and the readout circuit 17 of the radiographic image capturing apparatus 1. The control means 22 is connected to a storage means 23 constituted by a DRAM (Dynamic RAM) or the like, and a battery 24 that supplies power to each functional unit of the radiographic image capturing apparatus 1. Further, the antenna device 41 and the connector 39 (not shown in FIG. 8) are connected to the control means 22.

  The control unit 22 controls the scanning drive unit 15 and the readout circuit 17 to read out the image data D from each radiation detection element 7 and each radiation detection for removing the charge remaining in each radiation detection element 7. For each functional unit of the radiographic imaging apparatus 1, such as resetting the element 7 or controlling the bias power supply 14 to set or vary the bias voltage applied from the bias power supply 14 to each radiation detection element 7. Various controls are performed.

  In addition, when the control unit 22 performs the reading process of the image data D from each radiation detection element 7 as described above, the control unit 22 transmits the read image data D and the like to the console 58 described later.

  On the other hand, as will be described later, when the radiographic image capturing apparatus 1 is brought into the imaging room Ra, it is inserted into a cradle 55 described later. At that time, when the radiographic imaging apparatus 1 is inserted into the cradle 55, the control means 22 will connect the connector 39 (see FIG. 2) to the connector 55a (see FIG. 12 described later) of the cradle 55. A cassette ID which is identification information of the radiographic imaging apparatus 1 is notified to a relay unit 54 (see FIG. 1) described later via 55.

  Further, when the radiographer or other radiographer presses the selection switch 38 (see FIG. 2) as a selection unit, the control unit 22 indicates that the cassette ID, which is its own identification information, has been selected. The selection signal is transmitted to the console 58 via the antenna device 41.

  Further, when the power switch 37 is pressed by a radiographer or other radiographer to turn on the power, the control means 22 sends a cassette ID that is its own identification information and an activation signal indicating that it has been activated to the antenna. When the power switch 37 is pressed by a radiographer or other radiographer and the power is turned off, the radiographic imaging apparatus 1 is turned off before turning off the power. The cassette ID, which is the identification information, and the stop signal indicating that the device is turned off are transmitted to the console 58 via the antenna device 41.

  Then, when power is supplied to each function unit when radiographic imaging, image data D reading processing, or the like is not performed, the battery 24 is consumed. Therefore, as described above, the control unit 22 includes each function unit. A state in which radiation image capturing can be performed by supplying power to the device, that is, a radiographable mode in which imaging is possible, and at least a radiation detection element that supplies power only to functional units necessary for suppressing power consumption The power supply mode for each functional unit can be switched between the sleep mode in which the supply of power is stopped and the radiographic image cannot be captured.

  In the present embodiment, in the sleep mode, power is supplied only to functional units that need to be minimally activated such as the antenna device 41 and the control unit 22 so that signals from the console 58 and the like can be received, and the bias power source 14, the scanning drive unit 15, the readout circuit 17 (readout IC 16) and the like are not supplied with power.

  When the power switch 37 (see FIG. 2) is pressed, whether to start up the radiographic image capturing apparatus 1 in the radiographable mode or the sleep mode is set as appropriate. If the radiographic imaging device 1 is in the sleep mode when the switch 38 is pressed, the power supply mode is switched to the radiographable mode.

  In addition, the control means 22 switches the power supply mode to the imaging enable mode and makes a transition, and if radiographic imaging is not performed even after a predetermined time has elapsed, the power supply mode is set when the predetermined time has elapsed. Is automatically switched to sleep mode for transition. In this case, it is described in Patent Document 6 and the like described above that the predetermined time until transition to the sleep mode may be varied according to the usage frequency of the radiographic imaging device 1 or the like. That's right.

  Then, when the power supply mode is switched, the control unit 22 transmits a signal indicating that the photographing mode has been set or a signal indicating that the sleep mode has been entered to the console 38 together with its own cassette ID. It is like that.

  As will be described later, the radiographic image capturing apparatus 1 has a size compatible with a CR cassette, and can be used by being installed in a later-described Bucky apparatus 51 in a facility.

  Further, when the radiographic imaging device 1 is loaded in the bucky device 51, the radiographic imaging device 1 receives power supply from the bucky device 51, but in a single state not loaded in the bucky device 51, the battery 24 (FIG. 8). The power is supplied to each functional unit such as the control unit 22, the bias power supply 14, the scanning drive unit 15, and the readout circuit 17 (readout IC 16). When the bucky is loaded, transmission of the image data D, control communication, and the like are performed via the bucky device 51 in a wired manner.

  Further, as will be described later, when the radiographic imaging device 1 is loaded in the bucky device 51, the radiographic imaging device 1 receives power supply from the bucky device 51, but in a single state not loaded in the bucky device 51, Power is supplied from the battery 24 (see FIG. 8) to each functional unit such as the control unit 22, the bias power supply 14, the scanning drive unit 15, and the readout circuit 17 (readout IC 16).

  Next, other devices in the radiographic image capturing system 50 will be described.

  As shown in FIG. 1, the bucky device 51 can be used by loading the radiographic imaging device 1 into a cassette holding portion (also referred to as a cassette holder) 51a. In FIG. 1, a case is shown in which, in the photographing room Ra, a bucky device 51 </ b> A for standing position shooting and a bucky device 51 </ b> B for standing position shooting are installed as the bucky device 51. The present invention is also applied to a case where only the bucky device 51A for the camera or only the bucky device 51B for the position photographing is provided.

  The bucky device 51 is configured to be used by loading a conventional CR cassette into the cassette holding unit 51a, and an existing bucky device installed for the CR cassette in the photographing room Ra is used.

  Therefore, the radiation image capturing apparatus 1 is formed to have the same dimensions as the CR cassette. That is, the CR cassette is formed in a size such as 14 inches × 17 inches (half-cut size) in accordance with the JIS standard size (corresponding international standard is IEC 60406) for conventional screen film cassettes. Further, the thickness in the radiation incident direction is formed to be within a range of 15 mm + 1 mm to 15 mm-2 mm.

  The radiographic imaging apparatus 1 is also compliant with the JIS standard for the cassette for screen films to which the CR cassette conforms, in order to be able to be loaded into the Bucky device 51 that can be loaded with this JIS standard size CR cassette. It is formed with the dimensions.

  In addition, when the existing bucky device for a screen / film cassette or a CR cassette is not used, it is not necessary to form the radiographic image capturing device 1 with the above-described dimensions, and the radiographic image capturing device 1 has an arbitrary size and shape. It is possible to form. However, in that case, it is necessary to newly install a bucky device capable of loading the radiographic imaging device 1 having an arbitrarily set shape as the bucky device 51 in the imaging room Ra.

  In the present embodiment, as shown in FIG. 9, the connector 51 b provided at the end of the cable extending from the bucky device 51 is connected to the connector 39 of the radiation imaging device 1 before the radiation imaging device 1 is loaded into the bucky device 51. In this state, the radiographic image capturing apparatus 1 is loaded into the cassette holding part 51a of the bucky apparatus 51.

  For example, as shown in FIG. 10, a connector 51 b connected to the connector 39 (see FIG. 2) of the loaded radiographic imaging device 1 is provided inside the cassette holding portion 51 a of the bucky device 51. It is also possible. In this case, the connector 51b is similarly provided not only in the case of the standing-up shooting bucky device 51A shown in FIG. 10, but also in the standing-up shooting bucky device 51B.

  When the connector 51b and the connector 39 of the radiographic imaging device 1 are connected, the bucky device 51 reads out the cassette ID that is identification information from the radiographic imaging device 1, and the cassette ID of the radiographic imaging device 1 and its own The identification information is associated with a Bucky ID and transmitted to the console 58.

  As described above, the bucky device 51 uses the image data D output from the radiographic image capturing device 1 via the connector 39 when the radiographic image capturing device 1 is loaded and used in the cassette holding unit 51a. Is transmitted to a repeater 54 to be described later in a wired manner and transmitted to the console 58 via the repeater 54.

  Further, the connector 51 b of the bucky device 51 and the connector 39 of the radiographic imaging device 1 are connected to supply power from the bucky device 51 to the radiographic imaging device 1. Therefore, when the connectors 39 and 51b are connected to each other, the control means 22 of the radiographic image capturing apparatus 1 stops the supply of power from the battery 24 (see FIG. 8) to each functional unit, and via the connector 39. The power supplied from the bucky device 51 is switched so as to be supplied to each functional unit.

  If comprised in this way, when using at least the portable radiographic imaging device 1 loaded in the Bucky device 51, the power of the battery 24 built in the radiographic imaging device 1 will not be consumed. It is possible to accurately prevent the battery 24 from consuming power wastefully and to improve the usage efficiency of the battery 24. In addition, during the shooting, the battery runs out and shooting cannot be performed or re-shooting is possible. It is possible to accurately prevent the occurrence of a necessary situation.

  Further, when the portable radiographic imaging device 1 is loaded and used in the bucky device 51, the power supply mode of the radiographic imaging device 1 is changed from the console 58 to the sleep mode as will be described later. When receiving an instruction, the radiographic imaging apparatus 1 may be configured to supply power supplied from the bucky device 51 to the battery 24 and charge the battery 24.

  If comprised in this way, since it will become possible to charge the battery 24 automatically in the portable radiographic imaging device 1 which was not used for imaging | photography and was made to change to sleep mode, it will be in the middle of imaging | photography. It is possible to reliably prevent the occurrence of a situation in which shooting becomes impossible due to battery exhaustion or re-shooting is required.

  In the present embodiment, only one Bucky device 51 as described above may be provided in the imaging room Ra, but at least two radiographic imaging devices 1 exist in the imaging room Ra. Is the premise. That is, the radiographic image capturing apparatus 1 is used such that the portable radiographic image capturing apparatus 1 is loaded into the Bucky apparatus 51, or the portable radiographic image capturing apparatus 1 is used without being loaded into the Bucky apparatus 51. Alternatively, at least two or more machines are present in the radiographing room Ra in the form of the dedicated radiographic imaging apparatus 1.

  As shown in FIG. 1, at least one radiation source 52 for irradiating the subject with radiation is provided in the imaging room Ra. Of the radiation sources 52, one radiation source 52A is arranged suspended from the ceiling of the imaging room Ra, for example, and is activated based on an instruction from the console 58 at the time of imaging, not shown. The moving means is moved to a predetermined position.

  Then, by changing the irradiation direction of the radiation, it becomes possible to irradiate the radiation image capturing apparatus 1 loaded in the standing position photographing Bucky device 51A or the standing position photographing Bucky device 51B. ing. Further, in the case where the dedicated type radiographic imaging device 1 exists, a dedicated radiation source 52 may be provided, or the radiation source 52 used for the bucky device 51 may be shared. It is.

  The radiographing room Ra is also provided with a portable radiation source 52B that is not associated with the stand-up radiographing or the supine radiographing device 51A, 51B. The portable radiation source 52B can be carried anywhere in the photographing room Ra, and can irradiate radiation in an arbitrary direction.

  Then, the radiographic imaging device 1 is applied to the body part of the patient who is the subject in a single state (that is, not loaded into the bucky device 51), or the table of the bucky device 51B for lying position photographing or a bed and a patient (not shown). The radiation can be emitted from the portable radiation source 52B at an appropriate distance and direction while being inserted between the body and the body.

  In addition, the radiographic imaging device 1 can be used for radiographic imaging in a single state that is not loaded in the bucky device 51 as described above.

  The radiation source 52 includes an X-ray tube, and when the X-ray tube is supplied with a predetermined tube voltage or tube current from a radiation generator 57 described later, the X-ray tube is set to a tube voltage or the like for a specified irradiation time. A corresponding dose of radiation is emitted.

  As described above, since the imaging room Ra is shielded by lead or the like, even if information such as the image data D is transmitted / received from the radiographic imaging apparatus 1 via the antenna apparatus 41 in the imaging room Ra, it is transmitted and received as it is. Can not. Therefore, as shown in FIG. 1, when the radiographic imaging apparatus 1 and the console 58 communicate wirelessly, a repeater (also referred to as a base station or a wireless access point) provided with a wireless antenna 53 that relays these communications. 54 is provided.

  As described above, the bucky device 51 and the repeater 54 are connected by a cable or the like. When the radiographic image capturing device 1 is loaded into the bucky device 51 and used, it is output from the radiographic image capturing device 1. The image data D and the like are transmitted to the console 58 in a wired manner via the bucky device 51, the relay 54, and the like.

  A cradle 55 is connected to the repeater 54. As shown in FIG. 11, when the radiographic imaging device 1 brought into the radiographic room Ra is inserted and the connector 39 of the radiographic imaging device 1 and the connector 55a of the cradle 55 are connected, as described above, the radiation The cassette ID is notified from the image capturing apparatus 1 to the repeater 54 via the cradle 55. When the cassette ID of the radiation image capturing apparatus 1 is transmitted from the cradle 55, the relay unit 54 notifies the console 58 of the cassette ID.

  The cradle 55 is normally used for storing and charging the radiation image capturing apparatus 1 and the like, and the cradle 55 has a function such as charging in each of the following embodiments. Is also possible. Furthermore, although FIG. 11 shows the cradle 55 provided with two insertion openings for inserting the radiographic imaging apparatus 1, the number of insertion openings may be one, or three or more may be provided.

  The cradle 55 may be installed in either the imaging room Ra or the front room Rb. When the cradle 55 is installed in the imaging room Ra, a position where the radiation irradiated from the radiation source 52 does not reach, that is, for example, the imaging room. Installed at the corner of Ra.

  On the other hand, instead of using the cradle 55 as described above, or as a means for detecting the radiographic image capturing apparatus 1 brought into the imaging room Ra or the front room Rb and notifying the console 58 of the cassette ID, In combination, as shown in FIG. 12, for example, a tag reader 60 may be provided near the door of the front chamber Rb.

  In the case of such a configuration, a tag (not shown) such as a so-called RFID (Radio Frequency IDentification) tag is built in the radiographic imaging apparatus 1 in advance, and unique information such as a cassette ID of the radiographic imaging apparatus 1 is included in the tag. Remember me. When the radiographic image capturing apparatus 1 passes through the vicinity of the tag reader 60 and is brought into the imaging room Ra or the front chamber Rb, the tag reader 60 reads information such as a cassette ID from the tag of the radiographic image capturing apparatus 1, and the cassette It can be configured to notify the console 58 of the ID.

  As described above, it is preferable to use the tag reader 60 because it is possible to detect both the radiographic image capturing apparatus 1 being brought into the radiographing room Ra and being taken out from the radiographing room Ra. In this case, the tag reader 60 and the cradle 55 can be configured to double check at least whether the radiation image capturing apparatus 1 is brought into the photographing room Ra. When only the tag reader 60 is used, the cradle 55 is used only for charging the radiation image capturing apparatus 1, for example.

  As shown in FIG. 1, a radiation generator 57 having an exposure switch 56 and the like for instructing the radiation source 52 to start radiation irradiation and the like is provided in the front chamber (also referred to as an operation room or the like) Rb. Is provided.

  The console 58 is provided in the front room Rb, and is constituted by a computer or the like in which a CPU, a ROM, a RAM, an input / output interface and the like (not shown) are connected to a bus. A predetermined program is stored in the ROM, and the console 58 reads out a necessary program, expands it in a work area of the RAM, and executes various processes according to the program.

  The console 58 is provided with a display unit 58a made up of a CRT (Cathode Ray Tube), LCD (Liquid Crystal Display), or the like, and is connected to input means (not shown) such as a keyboard and a mouse. The console 58 is connected to a storage means 59 composed of a hard disk or the like, and the storage means 59 stores image data D transmitted from the radiation image capturing apparatus 1. Yes.

  Further, a HIS (Hospital Information System) 61 and a RIS (Radiology Information System) 62 are connected to the console 58 via the network N, and other illustrations are omitted. Other computers and an external device such as an imager for recording and outputting a radiation image on an image recording medium such as a film are connected. In addition, in FIG. 12 mentioned above, illustration of HIS61, RIS62, etc. is abbreviate | omitted.

  As described above, when the radiographic imaging device 1 brought into the radiographing room Ra is inserted into the console 58 and the cassette ID of the radiographic imaging device 1 is transmitted via the cradle 55 or the repeater 54. The cassette ID is stored in the storage means 59, and it is recognized and managed that the radiation image capturing apparatus 1 having the cassette ID is brought into the imaging room Ra or the front room Rb.

  Further, when the above-mentioned stop signal is transmitted from the radiographic imaging device 1 in the radiographing room Ra, the console 58 stores the radiation stored in association with the cassette ID stored in the storage unit 59. If the information indicating the operating state of the image capturing apparatus 1 is information indicating the stopped state, the information is left as it is. If the information indicating the starting state is information, the cassette ID is newly associated with the information indicating the stopped state and saved. To do.

  When the activation signal described above is transmitted from the radiation imaging apparatus 1 in the imaging room Ra, the console 58 stores the radiation stored in association with the cassette ID stored in the storage unit 59. If the information representing the operating state of the image capturing apparatus 1 is information representing the activated state, the information is left as it is. If the information representing the stopped state is retained, the cassette ID is newly associated with the information representing the activated state and overwritten. To do.

  In this way, the console 58 is in any state in which the operation state of the radiation imaging apparatus 1 is currently in the activated state (that is, the power is turned on) or in the stopped state (that is, the power is turned off). It is designed to recognize and manage.

  Instead of configuring the radiographic imaging apparatus 1 to transmit a signal indicating the operating state of the radiographic imaging apparatus 1, that is, a start signal or a stop signal, to the console 58, for example, the console 58 is periodically or At the necessary timing, the inside of the imaging room Ra is surveyed via the wireless antenna 53 of the repeater 54, and the operating state of each radiographic imaging device 1 existing in the imaging room Ra is in the activated state or in the stopped state. It is also possible to configure to monitor and manage this.

  On the other hand, as described above, when a signal indicating that the radiographic imaging apparatus 1 has entered the radiographable mode is transmitted together with the cassette ID, the console 58 corresponds to the cassette ID stored in the storage unit 59. If the information indicating the power supply mode of the radiographic image capturing apparatus 1 attached and stored is information indicating the radiographable mode, the information is left as it is. If the information indicating the sleep mode is information, the cassette ID can be imaged. The information indicating the mode is newly overwritten and saved.

  Further, when a signal indicating that the sleep mode has been entered is transmitted from the radiographic image capturing apparatus 1 together with the cassette ID, the signal stored in association with the cassette ID stored in the storage unit 59 is stored. If the information indicating the power supply mode mode of the radiographic image capturing apparatus 1 is information indicating the sleep mode, the information is left as it is. If the information indicating the stored mode is information indicating the imageable mode, the cassette ID is set. Information indicating the sleep mode is newly overwritten and saved.

  In this way, the console 58 recognizes and manages whether the radiographic image capturing apparatus 1 is currently in a power supply mode of the radiographable mode or the sleep mode. At least the management of the power supply mode by the console 58 is also performed for the dedicated radiographic imaging apparatus 1.

  As described above, the console 58 stores the storage unit 59 when the cassette ID and the Bucky ID of the radiographic imaging device 1 are transmitted from the Bucky device 51 to which the radiographic imaging device 1 is connected to the connector 51b. The cassette ID stored in is stored in association with the Bucky ID.

  When the connection between the radiographic image capturing apparatus 1 and the connector 51b is released, the association between the cassette ID and the Bucky ID of the radiographic image capturing apparatus 1 stored in the storage unit 59 is canceled, Only the cassette ID is stored.

  In this way, in the present embodiment, when the radiographic imaging device 1 is loaded and used in the bucky device 51, which radiographic imaging device 1 is loaded in which bucky device 51. Or, it recognizes and manages whether it is not loaded.

  Further, in the HIS 61 and the RIS 62 (see FIG. 1), imaging order information in which information necessary for performing predetermined radiographic imaging for individual patients can be registered in advance.

  The imaging order information is set by specifying at least an imaging region and imaging conditions. Specifically, as shown in FIG. 13, the imaging order information includes “patient ID” P2, “patient name” P3, “gender” P4, “age” P5, “clinical department” P6 as patient information, And “imaging region” P7, “imaging direction” P8 as an imaging condition, and the like.

  In the present embodiment, as an imaging condition, an item “Bucky ID” P <b> 9 is provided as information as to whether or not imaging is performed in a state where the radiographic imaging device 1 is loaded in the Bucky device 51. When loading, the Bucky ID is described. In the example shown in FIG. 13, the bucky IDs “001” and “002” represent the standing-up imaging device 51 </ b> A and the standing-up imaging device 51 </ b> B, respectively. 1 is used in a single state without being loaded into the bucky device 51.

  Then, “shooting order ID” P1 is automatically assigned to each shooting order information in the order in which shooting orders are registered. The patient information and imaging conditions written in the imaging order information are not limited to those described above. For example, information such as the date of birth of the patient, the number of medical examinations, the radiation dose, and whether the patient is fat or thin. It can also be configured to include.

  Hereinafter, the configuration of processing in the console 58 will be described, and the operation of the radiation image capturing system 50 according to the present embodiment will be described.

  The console 58 obtains each necessary radiographing order information from the HIS 61 or RIS 62 in which each radiographing order information is registered by an operation of a radiographer or other radiographer. If each shooting order information is registered in the console 58 itself, the necessary shooting order information is obtained by accessing the storage means 59 in which each shooting order information is stored.

  In this case, for example, the photographer inputs the name, patient ID, etc. of the patient to be photographed in the console 58, or reads the barcode described in the photographing request document brought by the patient with the reader 58. Necessary photographing order information is obtained from the HIS 61, the RIS 62, or the like by an appropriate method, such as inputting the photographing date in the photographing order information or inputting the photographing date to the console 58.

  When the console 58 obtains the imaging order information, a list of each imaging order information is displayed on the display unit 58a of the console 58 as a selection screen H1, as shown in FIG.

  In the present embodiment, the selection screen H1 is provided with a shooting order information display field h11 for displaying a list of each shooting order information, and on the left side of the shooting order information display field h11, a shooting to be shot is taken. A selection button h12 for selecting order information is provided corresponding to each photographing order information. In addition, a determination button h13 and a return button h14 are provided below the shooting order information display field h11.

  For example, when the photographer clicks the selection button h12 to select all the four pieces of imaging order information displayed for the patient “M” and clicks the decision button h13, in this embodiment, the console 58 is selected. 15 stores information on the number of selected shooting order information (in this case, 4) in the memory of the CPU or the like, and then displays a screen H2 as shown in FIG. 15 on the display unit 58a. ing.

  Here, the general display method displayed on the screen H2 will be described. As shown in FIG. 15, in the present embodiment, on the upper side of the screen H2, the patient's name “M”, patient ID, sex, The date, age, etc. are displayed. Further, in the present embodiment, icons I1 to I4 corresponding to each selected shooting order information are displayed in the center portion of the screen H2 in the shooting order ID order of the shooting order information (see P1 in FIG. 14 and the like), that is, in the registration order. Displayed in order of upper left, upper right, lower left, lower right.

  As described above, the icons I1 to I4 can be arranged and displayed in the order of registration. For example, the photographer can change the order in which the icons I1 to I4 are displayed. Is possible.

  Further, as will be described later, a radiographer or other photographer sees the radiographic image p displayed at the position of the icon I, and a normal image p is obtained at the lower part of each icon I. The “OK” button that is clicked when it is determined that the shooting specified in the step is completed and the shooting is finalized, and the “NG” button that is clicked when it is determined that shooting, image processing, or the like needs to be redone. Each is displayed.

  As shown in FIG. 15, each of the icons I1 to I4 displays a pattern imitating the bucky device 51B for the supine position designated by the corresponding photographing order information and “prone position”, and for standing position shooting. The display imitating the Bucky device 51A and the display of “standing position”, and when the radiographic image capturing device 1 is used alone, a pattern imitating the radiographic image capturing device 1 is displayed. It is possible to know at a glance which device (modality) a radiographer or other photographer uses to perform imaging.

  Moreover, in each icon I1-I4, irradiation conditions, such as a tube voltage at the time of irradiating a radiation from the radiation source 52 (refer FIG. 2) of the radiation generator 57 (refer FIG. 2), etc. are shown on the right side of those symbols. It is displayed. FIG. 15 shows a case where, for example, 100 kV, 200 mA, and 300 ms are set as the values in the default state, and these irradiation conditions are for setting the irradiation conditions displayed on the right side of the screen H2. The item can be changed and set by clicking the “+” button or the “−” button of each item on the display Ia.

  Also, below each icon I1 to I4, the type and direction of use of the radiographic imaging device 1 used in radiographic imaging corresponding to each icon I1 to I4 is displayed, and further below that, The imaging region (P7) and the imaging direction (P8) such as “abdominal front P → A” are displayed.

  On the other hand, in the present embodiment, any one of the icons I1 to I4 is focused and displayed. FIG. 15 shows a case where the icon I2 is displayed in focus. Further, as shown in FIG. 15, the icon I may be focused so that the border line of the icon I is boldly emphasized, and the color, brightness, etc. of the focused icon I can be changed. For example, the photographer can display at a glance that the icon I is focused by displaying the icon I in a different manner from the other icons I.

  In the present embodiment, the console 58 automatically shifts the focus of the icon I.

  Specifically, the console 58 is loaded in the bucky device 51 of each radiographic imaging apparatus 1 (that is, whether or not it is loaded), the activation and arrangement of each radiation source 52, and the radiation source 52A (FIG. 2). Shooting conditions under which the next shooting can be performed without changing each current state, or the next shooting can be performed with the least degree of change. Is automatically selected and the icon I is displayed with the focus shifted.

  Note that it is possible to shift the focus in the order of upper left → upper right → lower left → lower right in the order of shooting order information. In the default setting, the above automatic transition mode is set.

  For example, when the portable radiographic image capturing apparatus 1 is loaded in the standing-up imaging bucky device 51A and the radiation source 52A is facing the standing-up imaging bucky device 51A, FIG. Of the icons I1 to I4 shown in FIG. 15, the radiographic image corresponding to the icon I2 is taken without changing this state because it matches the radiographing conditions specified by the radiographing order information corresponding to the icon I2. Can do.

  Therefore, in such a case, as shown in FIG. 15, the icon I2 is automatically selected and displayed in focus. A radiographer such as a radiographer who performs radiographing recognizes that this focus is started to start from radiographing using the bucky device 51A for standing radiographing in the radiographing room Ra.

  Further, for example, when imaging corresponding to the icon I2 is performed, at that time, the portable radiographic imaging device 1 is loaded in the standing-up imaging bucky device 51A, and the radiation source 52A is used for standing imaging. The console 58 shifts the focus to the icon I3 that can be photographed without changing the above-described state at the time of the next photographing. .

  However, the reason why the console 58 displays the icon I in such a manner that the focus is changed or the focus is changed is to recommend that the photographer select the icon I. It does not force to perform shooting based on the shooting order information corresponding to the focused icon I.

  Therefore, when a radiographer or other photographer wants to perform imaging based on imaging order information other than the imaging order information corresponding to the focused icon I, another icon I corresponding to the imaging order information for imaging. Can be clicked.

  When the photographer clicks another icon I, the focus of the original icon I disappears, and the clicked another icon I is displayed in focus. Then, for example, when I1 that uses the bucky device 51B for supine photography is selected, the console 58 instructs the radiation generating device 57 to match the conditions (irradiation direction, aperture, etc.) corresponding to the bucky device 51B. Then, the radiation source 52A is controlled.

  On the left side of the screen H2, a human body model Ib is displayed that shows the imaging part designated by the imaging order information corresponding to the icon I displayed in focus so that the photographer can see at a glance. In the case of FIG. 15, since the icon I2 for designating photographing of the front of the chest is focused, the chest part of the human body model Ib is displayed in a different manner from the other parts, that is, for example, colored in red. .

  The console 58 corresponds to the focused icon I when the selected icon I (icon I2 in the case of FIG. 15) is displayed in focus or when another icon I clicked by the photographer is displayed in focus. Based on the photographing order information to be performed, each device used for the photographing is activated in a predetermined state.

  That is, in the case shown in FIG. 15, the console 58 instructs the radiation generator 57 to start up the radiation source 52A if it is not activated, so that the standing-up imaging device 51A can be irradiated with radiation. If not, the radiation source 52A is moved to a predetermined position and controlled to change the irradiation direction.

  On the other hand, when radiographic imaging based on radiographing order information corresponding to the displayed icon I that has been focused is performed, as described above, the control unit 22 of the radiographic imaging device 1 receives image data D from each radiation detection element 7. Is stored in the storage means 23. Then, the control unit 22 transmits the image data D and the like to the console 58 via the antenna device 41 and the bucky device 51.

  The control means 22 of the radiographic image capturing apparatus 1 is configured to create thinned data Dt in which the data amount is reduced by thinning data from each image data D read from each radiation detection element 7 at a predetermined rate. May be. When configured to create the thinned data Dt, after the thinned data Dt is transmitted from the radiation image capturing apparatus 1 to the console 58, each image data D and the like is automatically transmitted to the console 58.

  Further, the control means 22 performs a dark reading process for acquiring an offset due to the dark charge superimposed on each image data D at a predetermined timing, and the dark read by the dark reading process is performed. The offset correction value O calculated based on the read value d is automatically transmitted to the console 58.

  The console 58 creates a preview image based on the thinned data Dt transmitted when the thinned data Dt and the like are transmitted from the radiation image capturing apparatus 1.

  In the present embodiment, the console 58 displays the created preview image p_pre on the screen H2 of the display unit 58a using the entire display area of the icons I1 to I4 for a predetermined time, for example, as shown in FIG. When a predetermined time elapses or when a radiographer or the like who has seen the preview image p_pre clicks on the preview image p_pre, the screen H2 returns to the original screen as shown in FIG. However, the preview image p_pre is displayed at the position of the original icon I2 that has been focused.

  When the photographer who has viewed the preview image p_pre determines that the photographing positioning is abnormal and re-photographing is necessary, the user clicks the “NG” button below the preview image p_pre to display the preview image p_pre. Discarded and the screen H2 returns to the original display shown in FIG. At that time, the image data D, the thinned data Dt, and the like related to the imaging transmitted from the radiation image capturing apparatus 1 are also discarded.

  When the photographer views the preview image p_pre and determines that re-photographing is not necessary and clicks the “OK” button, the console 58 focuses and displays the next icon I3 as described above ( (See FIG. 18). Then, shooting specified in the shooting order information corresponding to the icon I3 is performed. For example, when the “NG” button is not operated within a certain time after displaying the preview image p_pre, the photographer accepts the preview image p_pre and regards it as operating the “OK” button. It is also possible to configure so that the operation of the “OK” button is unnecessary.

  On the other hand, on the console 58, generation processing of the radiation image p such as offset correction processing and gradation processing according to the imaging region is advanced based on the image data D obtained by imaging corresponding to the icon I2. When the diagnostic radiation image p is generated, the preview image p_pre displayed at the position of the icon I2 is automatically replaced with the diagnostic radiation image p and displayed as shown in FIG. It has become. Hereinafter, the radiographic images p acquired and generated by imaging corresponding to the icons I1 to I4 are referred to as radiographic images p1 to p4, respectively.

  A radiographer or other radiographer checks the radiographic image p2 and confirms that, if it is a normal radiographic image p2, clicks the “OK” button below and determines that it is necessary to re-execute radiography or image processing. In such a case, the “NG” button is clicked. When the “NG” button is clicked, necessary measures such as redoing the image and redoing the image processing are taken.

For example, on the screen H2 shown in FIG. 18, when the photographer views the radiation image p2 and determines that image processing must be performed again and fine adjustment is performed and the “NG” button is clicked, the screen is displayed on the right side of the screen H2. It is possible to configure the irradiation condition setting display Ia which has been changed to an image quality adjustment display Ia ^* as shown in FIG.

Note that the switching process for switching the display on the right side of the screen H2 from Ia to display Ia ^* is performed, for example, by clicking the buttons such as “irradiation condition” and “image quality adjustment” on the upper right side instead of clicking the “NG” button. It is also possible to configure so that it can also be performed.

In the image quality adjustment display Ia ^* , by clicking various buttons or sliding the lever-shaped display, the density and contrast of the clicked diagnostic radiation image p can be adjusted, frequency enhancement, resolution, and size. Can be changed. When a processing parameter is newly input, the radiation image p based on the input processing parameter is displayed by being overwritten on the original radiation image p.

  When the photographer performs the above adjustment or change on the radiographic image p2 and determines that the radiographic image p2 is normal, the photographer clicks an “OK” button below the radiographic image p2. If it is determined that the radiographic image p2 is not normal even after adjustment or change, the “NG” button below the radiographic image p2 is clicked. When the “NG” button is clicked, the radiation image p2 is discarded, and necessary measures are taken such that imaging corresponding to the icon I2 is performed again.

  In the present embodiment, when the “OK” button is clicked and the radiation image p2 is confirmed, the console 58 associates the confirmed radiation image p2 with the imaging order information corresponding to the icon I2.

  When a radiographer or other radiographer announces that the displayed image is not a preview image p_pre but a radiographic image p, and the “NG” button is not operated within a certain period after the notification. It is also possible to assume that the “OK” button has been operated, and to confirm the radiographic image p and associate it with the imaging order information. With this configuration, the operator can operate the button. The burden can be reduced.

  On the other hand, when the radiation image p2 is confirmed, the console 58 counts the number of the confirmed radiation images p, and the number of the confirmed radiation images p is the number of the selected imaging order information (in this case). 4) It is determined whether or not 4) has been reached.

  In the case illustrated in FIG. 18, since the confirmed radiographic image p is only the radiographic image p2 and the number of the confirmed radiographic images p is 1, the console 58 determines that the number of the confirmed radiographic images p is It is determined that the number of selected photographing order information has not been reached, and the above processing is continued.

  Thereafter, imaging is performed in the same manner, and the radiographic image p is displayed at the position of the icon I. Every time the radiographer confirms the radiographic image p by clicking the “OK” button, the console 58 The determined radiographic image p is associated with the corresponding radiographing order information, and the number of radiographic images p that have been determined is counted. The number of radiographic images p that has been determined reaches the number of selected radiographing order information. Determine whether or not.

  During this time, in the standing-up shooting device 51A, the countdown to the sleep transition is started on the basis of the sleep transition timer set from the console 58 at the end of one shooting, but the shooting based on the next shooting order is instructed immediately. Therefore, the countdown is stopped. When shooting based on the second shooting order that designates the standing-up shooting bucky device 51A is completed, the standing-up shooting bucky device 51A starts counting down for sleep transition again. Similarly, when shooting based on the shooting order for specifying the bucky device 51B for the supine position shooting is completed, the bucky device 51B for the supine position shooting starts a countdown for the sleep transition.

  Then, as shown in FIG. 20, for example, the last imaging corresponding to the icon I4 is performed, the radiation image p4 is displayed at the position of the icon I4, and the radiograph p4 is displayed when the photographer clicks the “OK” button. When confirmed, the number of confirmed radiation images p becomes four. Therefore, the console 58 associates the determined radiographic image p4 with the imaging order information corresponding to the icon I4, and determines that the number of determined radiographic images p has reached the number of selected imaging order information. To do.

  In the present embodiment, when the console 58 determines that the number of confirmed radiographic images p has reached the number of selected radiographing order information, at that time, the console 58 passes through the repeater 54 (see FIG. 1). A signal instructing to immediately switch the power supply mode to the sleep mode is sent to the plurality of radiographic imaging devices 1 existing in Ra, and the power supply mode of all the radiographic imaging devices 1 in the imaging room Ra is set. Immediately and even during the countdown to the sleep transition, the mode is forcibly shifted to the sleep mode.

  As described above, when the console 58 is configured to manage the radiographic image capturing apparatus 1 existing in the imaging room Ra and to manage whether the power supply mode is the imaging enable mode or the sleep mode. Alternatively, the above-described signal may be transmitted to the radiation image capturing apparatus 1 whose power supply mode is the image capture enable mode.

  For example, in the above example, even when the last imaging corresponding to at least the icon I4 is performed and the corresponding radiographic image p4 is determined, the radiographic imaging device 1 used for the imaging is supplied with power. There is a case where the power supply mode has not been changed to the sleep mode yet because the predetermined time has not elapsed since the mode was changed to the shootable mode, and the power supply mode remains in the shootable mode. .

  Further, the radiographic image capturing apparatus 1 used for the previous imaging may not yet shift the power supply mode to the sleep mode, and the power supply mode may remain in the image capture enable mode. In particular, in the standing-up imaging bucky device 51A for imaging the front of the chest that is frequently used as an imaging mode, the imaging request by the radiographer is not obstructed (that is, in order not to miss an imaging opportunity). Time sleep transition time setting is performed. This is because the sleep transition is performed only when the patient is really interrupted, and the sleep transition is not performed in the case of continuous imaging such as the front of the chest or the side of the chest.

  However, if configured as described above, as described above, the power supply mode of some of the radiographic imaging apparatuses 1 among the radiographic imaging apparatuses 1 existing in the imaging room Ra remains in the imaging enable mode. Even in such a case, the console 58 determines that the number of confirmed radiographic images p matches the number of selected radiographing order information, and transmits the above signals. The power supply mode of the radiation image capturing apparatus 1 is forcibly shifted to the sleep mode.

  Therefore, the state in which the power supply mode of the radiographic imaging device 1 in the imaging room Ra is in the imaging enabled mode continues even though all imaging based on the imaging order information selected by the radiographer or other radiographer is completed. Thus, it is possible to accurately prevent the power from being wasted.

  And even when viewed as the whole radiographic imaging system 50 as well as the individual radiographic imaging apparatus 1, wasteful power consumption is prevented and the power consumption required for the operation of the entire radiographic imaging system 50 is further reduced. Is possible.

  As described above, according to the radiographic image capturing system 50 according to the present embodiment, the console 58 is generated based on the number of selected radiographing order information and the image data D transmitted from the radiographic image capturing apparatus 1. Then, it is determined whether or not the number of confirmed radiographic images p matches, and immediately after the number of selected radiographing order information matches the number of confirmed radiographic images p, the inside of the radiographing room Ra The power supply mode of the plurality of radiation image capturing apparatuses 1 is shifted to the sleep mode.

  Therefore, the state in which the power supply mode of the radiographic imaging device 1 in the imaging room Ra is in the imaging enabled mode continues even though all imaging based on the imaging order information selected by the radiographer or other radiographer is completed. Thus, wasteful consumption of power can be prevented even when viewed as the whole radiographic imaging system 50 as well as the individual radiographic imaging apparatuses 1. Thus, it is possible to further reduce the power consumption required for the operation of the entire radiographic imaging system 50.

  For this reason, the power supply mode of the radiographic imaging apparatus 1 remains in the radiographable mode and the energized state continues, shortening the life of the radiation detection element 7 or the like, or the power of the battery 24 is wastefully consumed. Thus, it is possible to accurately prevent the occurrence of such a situation that the usage efficiency of the battery 24 decreases or the battery runs out during shooting.

  In the above embodiment, when the radiographic image p generated by the console 58 based on the image data D transmitted from the radiographic image capturing apparatus 1 in the radiographing room Ra is determined by a radiographer or other radiographer. Then, it is determined whether or not the number of selected radiographing order information matches the number of confirmed radiographic images p. When they match, the power supply mode of all radiographic imaging devices 1 is forcibly set. The case where it is configured to immediately shift to the sleep mode has been described.

However, when a photographer such as a skilled radiographer views the preview image p_pre displayed on the display unit 58a of the console 58 based on the image data D and the thinning data Dt transmitted from the radiation image capturing apparatus 1. Then, the radiographic image p generated based on the image data D becomes a normal image, or the density and contrast adjustment and frequency enhancement of the radiographic image p are performed on the display Ia ^* for image quality adjustment shown in FIG. If the resolution or size is changed, it may be determined that the normal radiation image p is obtained.

  In such a case, the preview image p_pre is displayed and the photographer clicks the “OK” button to approve the preview image p_pre without waiting until the radiation image p is confirmed as in the above embodiment. At this point, the console 58 determines whether or not the number of selected radiographing order information matches the number of approved preview images p_pre. It is also possible to configure the apparatus 1 to immediately shift the power supply mode to the sleep mode.

  If comprised in this way, it will become possible to change the power supply mode of all the radiographic imaging apparatuses 1 to sleep mode more rapidly than the case of said embodiment, and not only individual radiographic imaging apparatuses 1 but radiation. Even when viewed as the entire image capturing system 50, the power consumption can be further reduced, and the same beneficial effect as the above-described embodiment can be more effectively exhibited.

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

DESCRIPTION OF SYMBOLS 1 Radiation imaging device 7 Radiation detection element 17 Reading circuit 22 Control means 24 Battery 39 Connector (communication means)
41 Antenna device (communication means)
50 Radiation Imaging System 51 Bucky Device 58 Console D Image Data Dt Thinning-out Data P Detection Unit p Radiation Image p_pre Preview Image

Claims (8)

A detection unit in which a plurality of radiation detection elements that generate an electric charge according to an irradiation dose of radiation are arranged in a two-dimensional manner;
A readout circuit that reads out the electric charge from each of the radiation detection elements, converts the electric charge into image data and reads out the data for each of the radiation detection elements;
A communication means capable of transmitting and receiving signals to and from an external device;
The read image data is transmitted via the communication means, and a power supply mode for each functional unit is set to a radiographable mode that enables radiographic imaging by supplying power to the radiation detection element, Control means for switching between a sleep mode in which power is supplied only to necessary function units including a communication means and the radiation detection element is stopped to supply power and radiographic imaging cannot be performed,
A plurality of radiographic imaging devices comprising:
The imaging order information is acquired, the imaging is performed based on the selected imaging order information, and the image data is transmitted from the radiographic imaging apparatus, and is generated and determined based on the image data. A console for associating a radiographic image with the imaging order information;
With
The console, when a radiographic image generated based on the image data transmitted from the radiographic imaging device is determined, the number of selected radiographing order information and the number of the determined radiographic images The radiographic image capturing system is characterized in that it is determined whether or not and the power supply mode of the plurality of radiographic image capturing apparatuses is shifted to a sleep mode immediately after the determination. The control means of the radiographic image capturing apparatus may be configured so that when a predetermined time elapses from when the radiation image capturing apparatus is irradiated with radiation or after the power supply mode is changed to the radiographable mode. The power supply mode is configured to transition to the sleep mode,
The console, when a radiographic image generated based on the image data transmitted from the radiographic imaging device is determined, the number of selected radiographing order information and the number of the determined radiographic images The radiographic image capturing system according to claim 1, wherein the power supply mode of the plurality of radiographic image capturing apparatuses is shifted to a sleep mode immediately after the determination is made.   The console is based on the image data transmitted from the radiographic image capturing apparatus instead of determining whether or not the number of selected radiographing order information matches the determined number of radiographic images. When the displayed preview image is approved, it is determined whether or not the number of the selected photographing order information matches the number of the approved preview images. The radiographic imaging system according to claim 1, wherein the power supply mode of the radiographic imaging apparatus is shifted to a sleep mode. The control means of the radiographic imaging apparatus creates thinned data by thinning out data at a predetermined rate from the image data read from each radiation detection element, and transmits the thinned data to the console.
The console, when the preview image displayed based on the thinning data transmitted from the radiographic imaging device is approved, the number of the selected imaging order information and the number of the approved preview images The radiographic imaging system according to claim 3, wherein it is determined whether or not coincides with each other.   The radiographic image capturing system according to claim 4, wherein the control unit of the radiographic image capturing apparatus transmits the image data after transmitting the thinning data to the console.   The at least one of the plurality of radiographic imaging apparatuses is a portable radiographic imaging apparatus having a built-in battery for supplying power to each functional unit. The radiographic image capturing system according to claim 5. A bucky device capable of loading the portable radiographic imaging device;
The portable radiographic imaging device is:
When used in a single state without being loaded into the bucky device, power is supplied from the battery to each functional unit,
The power supply from the battery is stopped and the power supplied from the bucky device is supplied to each function unit when being used in the bucky device. Radiation imaging system.   When the portable radiographic imaging device is used by being loaded into the Bucky device, the power supplied from the Bucky device is supplied to the battery when the power supply mode transitions to the sleep mode. The radiographic imaging system according to claim 7, wherein the battery is charged.

Images