JP2011104086A - Radiation image imaging system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiation image imaging system capable of properly switching the power supply mode of a portable radiation image imaging device between an imagable mode and a sleep mode. <P>SOLUTION: The radiation image imaging system 100 has the portable radiation image imaging device 1 having control means 22 for switching the power supply mode between the imagable mode and the sleep mode and a console 58 selectable imaging order information including patient identification information and imaging methods and for transmitting a signal for instructing the control means 22 of the portable radiation image imaging device 1 on the switch over of the power supply mode. The console 58 variably sets a time T from the time when transmitting the sleep signal for shifting the power supply mode to the sleep mode is transmitted to the portable radiation imaging device 1 triggered by the time when an irradiation start signal or an irradiation complete signal to a radiation source 52 is transmitted from an operation table 57 to the console 58 base on the plurality pieces of selected imaging order information. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to a radiographic imaging system, and more particularly to a radiographic imaging system that creates radiographing order information related to radiographic imaging and performs radiographic imaging.

  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 imaging device is known as an FPD (Flat Panel Detector), and has been conventionally formed integrally with a Bucky device (see, for example, Patent Document 1). However, in recent years, a portable radiographic image capturing 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). Moreover, in the portable radiographic imaging apparatus, the radiographic imaging apparatus which incorporates a battery and transmits / receives a signal, data, etc. by exchanging an electromagnetic wave via an antenna apparatus is developed (for example, refer patent document 4 etc.). .

  In such a portable radiographic imaging device with a built-in battery, for the purpose of avoiding battery exhaustion, etc., the power supply state to the radiation detection element etc. Can be switched between an imaging-capable mode that enables image capturing and a sleep mode (also referred to as a standby mode) that stops power supply to the radiation detection elements and supplies power only to necessary members. May be configured. In the sleep mode, power is not supplied to the radiation detection element or the like, so that power consumption can be suppressed, but radiographic imaging cannot be performed.

  The portable radiographic imaging apparatus configured to be able to switch the power supply mode in this way consumes the battery if the radiographic imaging mode is maintained even after the radiographic imaging is completed. In many cases, the power supply mode is configured to be automatically switched from the shootable mode to the sleep mode.

  However, when configured in this way, the power supply mode of the portable radiographic imaging device is automatically switched to the sleep mode when actually performing imaging, and the portable radiographic imaging device has no radiation. Radiation images cannot be obtained even if irradiation is performed, and it is necessary to irradiate radiation again. However, this causes a problem that the X-ray tube of the radiation generating apparatus is wasted and the exposure dose to the patient increases and places a burden on the patient.

  Therefore, in the radiographic imaging system described in Patent Document 5, radiographic imaging is performed in a state where the power supply mode of the radiographic imaging apparatus is switched to a radiographable mode, and whenever an imaging request, that is, radiographic imaging is reserved. It is detected whether or not all radiographic imaging corresponding to the radiographing order information to be created has been completed, and when it is detected that all radiographing has been completed, the power supply mode of the radiographic imaging device is set to sleep from the radiographable mode. A technique for switching to a mode is disclosed.

  Moreover, in the radiographic imaging system described in Patent Document 6, when there are various modalities such as an imaging unit for standing imaging and an imaging unit for standing imaging, the modality that is not likely to be used is used. A technology is disclosed for switching to sleep mode as soon as possible to save power and prolong the life of consumables, and to control to prevent switching to sleep mode for modalities that are used or likely to be used. ing.

JP-A-9-73144 JP 2006-058124 A JP-A-6-342099 JP 2003-210444 A JP 2001-66720 A JP 2002-272721 A

  However, in the case of the radiographic imaging system described in Patent Document 5, the power supply mode of the radiographic imaging apparatus sleeps from the radiographable mode until all radiographic imaging corresponding to the set imaging order information is completed. Since it is not possible to switch to the mode, for example, when the patient changes, or when the portable radiographic imaging device is taken in and out of the modality, the time taken from the current imaging to the next imaging is empty, The power supply mode of the portable radiographic image capturing apparatus remains in the image capturing enable mode.

  However, in this case, the power of the battery of the portable radiographic imaging device is wasted and the battery is consumed, and the power supply mode of the portable radiographic imaging device is set to the radiographable mode and the sleep mode. The implications of being able to switch between and will fade

  Also, in the case of the radiographic image capturing apparatus described in Patent Document 6, when radiographic image capturing is performed using a modality controlled not to switch the power supply mode to the sleep mode, As in the case of the radiographic image capturing apparatus described in Patent Document 5, the power supply mode of the portable radiographic image capturing apparatus remains in the image capture enable mode even while there is time from the current image capture to the next image capture. In addition, the power of the battery of the portable radiographic image capturing apparatus may be wasted and the battery may be consumed.

  On the other hand, in the radiographic imaging apparatus described in Patent Document 6, when radiographic imaging is performed using a modality that switches the power supply mode to the sleep mode early, portable radiographic imaging is performed when imaging is actually performed. Since the power supply mode of the apparatus is automatically switched to the sleep mode, there is a possibility that a radiographic image cannot be obtained even if radiation is applied to the portable radiographic imaging apparatus.

  As described above, in the portable radiographic imaging device with a built-in battery in which the power supply mode can be switched between the radiographable mode and the sleep mode, the battery is consumed in the radiographable mode, but the mode switching timing If there is a mistake, radiographic imaging is performed while the portable radiographic image capturing apparatus is in the sleep mode, and there is a problem that re-imaging is required.

  For this reason, for radiographic imaging systems, the main premise is that it is necessary to avoid increasing the exposure dose for re-imaging and placing a burden on the patient. It is desired that the power supply mode can be appropriately switched between the image capturing possible mode and the sleep mode.

  The present invention has been made in view of the above circumstances, and provides a radiographic imaging system capable of appropriately switching the power supply mode of a portable radiographic imaging apparatus between a radiographable mode and a sleep mode. Objective.

In order to solve the above-described problem, the radiographic imaging system of the present invention includes:
A detection unit in which radiation detection elements that generate charges according to the radiation dose are arranged in a two-dimensional manner;
A readout circuit that reads out the charge from the radiation detection element and converts the charge into image data for each radiation detection element;
A communication means for transmitting / receiving information to / from an external device;
A power supply mode for the electronic component, a radiographable mode that enables radiographic imaging by supplying power to the radiation detection element, and the radiation detection element by supplying power only to necessary functional units including the communication means Control means for switching between the sleep mode in which the supply of power is stopped and radiographic imaging is not possible,
A portable radiographic imaging device with a built-in battery;
A bucky device capable of loading the portable radiographic imaging device;
A radiation generation apparatus comprising a radiation source for irradiating radiation to the portable radiographic imaging apparatus and a console for instructing radiation irradiation;
A console capable of selecting a plurality of pieces of imaging order information including at least patient identification information and an imaging method, and transmitting a signal instructing switching of the power supply mode to the control means of the portable radiographic imaging device; ,
With
The console has an irradiation start signal for instructing start of radiation irradiation to the radiation source of the radiation generating apparatus or an irradiation end signal for instructing end of radiation based on the selected plurality of imaging order information. A sleep signal for switching the power supply mode from the radiographable mode to the sleep mode is transmitted to the portable radiographic imaging device, starting from the time point when the radiographic device is transmitted from the console. It is characterized in that the time until is variable and set.

  According to the radiographic imaging system of the system of the present invention, the radiation start signal for instructing the radiation source of the radiation generating apparatus to start the radiation based on the plurality of pieces of selected radiographing order information on the console. The time until the sleep signal for switching the power supply mode from the radiographable mode to the sleep mode is transmitted to the portable radiographic imaging device, starting from the time point when it is transmitted from the console of the generator. Is set.

  Therefore, when it is assumed in advance that it will take time from the current imaging to the next imaging, a sleep signal is sent from the console to the portable radiographic imaging device so as to shift to the sleep mode so as to suppress battery consumption. If it is assumed in advance that there will be no time between the current shooting and the next shooting, that is, it is assumed that the time until transmission will be shortened, that is, if shooting is performed continuously, the shooting timing will not be missed. As described above, in order to maintain the imaging mode, it is possible to variably set the time until the sleep signal is transmitted from the console to the portable radiographic imaging device.

  As described above, according to the radiographic imaging system of the system as in the present invention, the power supply mode of the portable radiographic imaging apparatus can be imaged without losing the imaging timing and without consuming the battery wastefully. It is possible to appropriately switch between the enable mode and the sleep mode.

  And when radiographic imaging is performed, since the power supply mode of the portable radiographic imaging device is switched to the radiographable mode accurately, the power supply mode of the portable radiographic imaging device at the time of radiographic imaging is It is possible to accurately prevent a situation in which the radiation image cannot be obtained in the sleep mode. For this reason, it is possible to accurately prevent problems such as the need for re-imaging and the X-ray tube of the radiation generating apparatus being wasted, increasing the exposure dose to the patient and placing a burden on the patient.

  In addition, when it takes time from the current imaging to the next imaging, a sleep signal is accurately transmitted from the console, and the power supply mode of the portable radiographic imaging device is accurately switched from the imaging possible mode to the sleep mode. Therefore, it is possible to accurately prevent a situation where the power supply mode of the portable radiographic image capturing apparatus remains in the image capture enable mode and the battery is consumed.

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 the portable radiographic imaging device concerning this embodiment. It is the external appearance perspective view which looked at the portable radiographic imaging apparatus of FIG. 2 from the opposite 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 portable 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 COF, a PCB board | substrate, etc. were attached. It is a block diagram showing the equivalent circuit of a portable radiographic imaging apparatus. (A) is a figure which shows the structure of a switch means, (B) is the state which pressed the button part half, (C) is a figure explaining the state by which the button part was fully pressed. It is a figure which shows an example of imaging | photography order information. It is a figure which shows an example of the selection screen where the imaging | photography order information displayed on the display part of a console was displayed. It is a flowchart which shows the procedure which varies and sets time until a sleep signal is transmitted to a portable radiographic imaging apparatus with the console 58. FIG.

  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.

  A radiographic image capturing system 100 according to the present embodiment is a system that assumes radiographic image capturing performed in a hospital or a clinic. For example, as shown in FIG. A radiographing room Ra that performs imaging of a patient's radiographing target area, an anterior chamber Rb that performs various operations such as control of radiation that an operator such as a radiographer irradiates a subject, and devices arranged outside the chamber Configured.

  FIG. 1 shows a case where the shooting rooms Ra and the consoles 58 are associated with each other one by one. However, a plurality of shooting rooms Ra and one console 58, or a plurality of shooting rooms Ra and a plurality of shooting rooms Ra. The radiographic imaging system 100 of the present invention can also be applied to the case where the console 58 is associated.

  Here, first, the portable radiographic imaging device 1 used for radiographic imaging in the radiographic imaging system 100 will be described.

  Hereinafter, the portable radiographic imaging device is simply referred to as a radiographic imaging device. 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 according to the present embodiment, and FIG. 3 is an external perspective view of the radiographic image capturing apparatus as 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 FIGS. 2 and 3, in the present embodiment, a hollow rectangular tube-shaped housing body 2A having a radiation incident surface R in the housing 2 is made of a material such as a carbon plate or plastic that transmits radiation. The housing 2 is formed by closing the openings on both sides of the housing 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 has a power switch 37, a changeover switch 38, a connector 39, an LED for displaying a battery state, a power supply mode of the radiographic imaging apparatus 1, and the like. The indicator 40 comprised by these is arrange | positioned. 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.

  The installation position of the antenna device 41 is not limited to the position shown in FIG. 3 and can be installed at an arbitrary position. The number of antenna devices 41 to be installed is also set to an appropriate number. It is also possible to transfer the image data or the like to the console 58 by a wired system. In this case, for example, the cable is connected to the connector 39 described above to transmit and receive.

  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.

  In the present embodiment, a glass substrate 35 for protecting the substrate 4 and the radiation incident surface R of the scintillator 3 is disposed. Moreover, in this embodiment, the buffer material 36 for preventing that they collide between the sensor panel SP and the side surface of the housing | casing 2 is provided.

  The scintillator 3 is bonded to the substrate 4 in a state of facing a detection unit P described later. In the present embodiment, 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 when receiving radiation, that is, an electromagnetic wave centered on visible light and output. .

  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.

  Thus, the entire region r in which the plurality of radiation detection elements 7 arranged in a two-dimensional manner are provided in each small region r partitioned by the scanning line 5 and the signal line 6, that is, shown by a one-dot chain line in FIG. The region is a detection unit P.

  In the present embodiment, a photodiode is used as the radiation detection element 7, but other than this, 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.

  In the present embodiment, as shown in FIG. 6, the bias lines 9 are respectively connected to the plurality of radiation detection elements 7 arranged in a row, and as shown in FIG. 5, each bias line 9 is connected to the substrate 4. Are bound to one connection 10 at a position outside the detection portion P.

  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, 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. 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 supply 14 applies a bias voltage (reverse bias voltage in this embodiment) 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, in radiographic imaging, radiation is applied to the radiographic imaging apparatus 1 through a subject, and the scintillator 3 converts the radiation into electromagnetic waves of other wavelengths and irradiates the radiation detection element 7 directly therebelow. Then, charges are generated according to the radiation dose (the amount of electromagnetic waves) irradiated by the radiation detection element 7.

  In the process of reading charges from each radiation detection element 7, the TFT 8 in which an on-voltage is applied to the gate electrode 8 g from the gate driver 15 b of the scanning drive unit 15 through the lines L 1 to Lx of the scanning line 5 is turned on. Electric charges are emitted from the radiation detection element 7 to the signal 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 means 22 controls the operation of each member 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 above-described antenna device 41 is connected to the control means 22, and although not shown in FIG. 8, the above-described power switch 37, changeover switch 38, connector 39, etc. (see FIG. 2) are connected. Has been.

  The control means 22 responds to electronic components constituting each functional part such as the scanning drive means 15 and the readout IC 16 of the radiographic image capturing apparatus 1 described above in response to a signal (that is, a sleep signal or a wake-up signal) from the console 58 described later. Only the necessary function units including the power supply mode, a radiographable mode that enables radiographic imaging by supplying power to the radiation detection element 7, and an antenna device 41 that is a communication unit that transmits and receives information to and from an external device. Although the power is supplied, the radiation detection element 7 is switched between the sleep mode in which the supply of power is stopped and the radiographic imaging cannot be performed.

  In the present embodiment, the control unit 22 switches the power supply mode of the radiographic imaging apparatus 1 from the sleep mode to the radiographable mode when the above-described switch 38 is pressed by an operation of an operator such as a radiographer. It is designed to wake up (ie, so-called wake up). If the changeover switch 38 is pressed when the power supply mode of the radiographic image capturing apparatus 1 is already in the image capture enable mode, the power supply mode is switched from the image capture enable mode to the sleep mode.

  Further, the control means 22 sends image data obtained by radiographic imaging to the console 58 via the antenna device 41 when there is an operation by the operator or when there is a transmission request from the console 58. D etc. are transmitted.

  By the way, in this embodiment, it is assumed that the radiographic imaging device 1 is loaded into an existing Bucky device 51 for a screen / film cassette or a CR cassette, and the radiographic imaging device 1 is JIS standard in the CR cassette. It is formed with dimensions such as 14 inches × 17 inches (half-cut size) conforming to the size (that is, the JIS standard size in the cassette for conventional screen film, and the corresponding international standard is IEC 60406). 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.

  However, when a screen / film cassette or a CR cassette cassette is not used, it is not necessary to form the radiographic imaging apparatus 1 with the above dimensions, and the radiographic imaging apparatus 1 is formed in an arbitrary size and shape. be able to. In that case, the Bucky device 51 needs to be provided with a new Bucky device formed in accordance with the shape of the radiation image capturing device 1 so that the radiation image capturing device 1 can be loaded.

  In addition, the radiographic imaging device 1 can be used in a so-called state where it is not loaded into the bucky device 51. In this case, the radiographic image capturing apparatus 1 can be used, for example, in a state where the radiation image capturing apparatus 1 is applied to a body part of a patient as a subject or is inserted between a bed or the like and the patient's body.

  In the present embodiment, it is assumed that radiographic imaging is performed using one portable radiographic imaging device 1 in the radiographic imaging system 100. However, a plurality of portable radiographic imaging devices are used. The present invention can also be applied to such a case.

  Next, other devices in the radiographic image capturing system 100 shown in FIG. 1 will be described in detail.

  The imaging room is a room that performs radiation imaging by irradiating a region of interest that is an imaging region of a patient, and as shown in FIG. 1, a radiation source 52 of a radiation generator for irradiating a subject with radiation. Is arranged and a so-called radiographing room Ra in which radiation is prevented from leaking outside the radiographing room, and a front room (also referred to as an operation room or the like) in which an operator console 57 of a radiation generator operated by the operator is arranged. Rb.

  In the present embodiment, a radiation source 52 of a radiation generating apparatus including a bucky device 51 that can be loaded with the above-described radiographic imaging device 1 and an X-ray tube (not shown) that generates radiation to be irradiated on the subject is provided in the imaging room Ra. Is provided.

  As described above, the bucky device 51 is an existing bucky device formed so as to be used by loading the CR cassette into the cassette holding portion (cassette holder) 51a in the present embodiment. As described above, the radiographic imaging device 1 having a size compatible with the CR cassette can also be used by being loaded into the cassette holding portion 51a.

  As shown in FIG. 1, in this embodiment, a shooting room Ra is provided with a bucky device 51A for standing position shooting and a bucky device 51B for standing position shooting as the bucky device 51. As described above, a plurality of types of bucky devices 51A and 51B are provided in the present embodiment, but the present invention is also applied to a case where only one bucky device 51 is provided in the photographing room Ra, for example. .

  Further, in the present embodiment, one radiation source 52A among the radiation sources 52 of the radiation generating apparatus changes the position and the irradiation direction of the irradiation line, thereby changing the position of the bucky device 51A for standing position shooting and the position shooting position. Radiation imaging can be performed by irradiating the radiation imaging apparatus 1 loaded in the Bucky apparatus 51B with radiation.

  Further, in the present embodiment, a portable radiation source 52B that is not associated with the bucky devices 51A and 51B for standing position shooting and standing position shooting is also provided. The portable radiation source 52B can be carried anywhere in the photographing room Ra, and can irradiate radiation in an arbitrary direction.

  As described above, when the radiographic image capturing apparatus 1 is used in a single state, the radiographic image capturing apparatus 1 is applied to a part of the patient's body, which is the subject, or between the bucky device 51B for lying position photographing or a bed (not shown) and the patient's body. The radiation image capturing apparatus 1 in a state of being inserted into the device can be irradiated with radiation from an appropriate distance and direction using a portable radiation source 52B.

  The imaging room Ra is shielded with lead or the like so that the radiation irradiated inside does not leak to the outside. Therefore, even if information such as image data D is transmitted / received from the radiation image capturing apparatus 1 via the antenna apparatus 41 in the image capturing room Ra, it cannot be transmitted / received as it is. Therefore, in the present embodiment, when the radiographic image capturing apparatus 1 and the console 58 perform wireless communication, a base station (also referred to as a wireless access point) 54 including a wireless antenna 53 that relays the communication is provided. Yes.

  In addition, in FIG. 1, although each Bucky apparatus 51 and the base station 54 are represented as being connected by a cable or the like, this means that they are connected by a wired method such as a cable or the like. Instead, if there is no cable or the like that connects them to the photographing room Ra, there is no need to provide a new one.

  A cradle 55 is provided in the photographing room Ra. In the present embodiment, the cradle 55 stores and charges the inserted radiation image capturing apparatus 1. 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 of the radiation generator does not reach, that is, For example, it is installed in each corner.

  The front chamber Rb is provided with a radiation generator console 57 including switch means 56 and the like for instructing the radiation source 52 of the radiation generator to start radiation irradiation. Although not shown in FIG. 1, display means such as a monitor for displaying a list of photographing order information transmitted from the console 58 is provided in the console 57 and the photographing room Ra as will be described later. It is also possible to configure.

  The console 57 may be configured with a general-purpose computer including a CPU or the like, or may be configured with a computer including a dedicated processor. The configuration of the console 57 is not particularly limited.

  The switch means 56 can normally be operated in two stages by an operator such as a radiologist. Specifically, in the present embodiment, as shown in FIGS. 9A to 9C, for example, the switch means 56 includes a rod-shaped button portion 56a having a predetermined length of stroke and a button portion 56a. It is comprised with the housing | casing part 56b supported so that a movement in the stroke direction shown by the arrow S is possible.

  As shown in FIG. 9A, the button portion 56a of the switch means 56 includes a cylindrical portion 56a1 protruding upward from the housing portion 56b and a columnar portion 56a2 protruding further upward from the inside thereof. Has been.

  Then, as shown in FIG. 9B, when the column portion 56a2 is pushed in the stroke direction S up to the upper end portion of the cylindrical portion 56a1 and is half-pressed, an activation signal is sent from the switch means 56 to the console 57. It is supposed to be sent. Then, the console 57 transmits the activation signal to the radiation source 52. When the radiation source 52 receives the activation signal, the console 57 starts rotating the anode of the X-ray tube so as to be in a standby state. It has become.

  After that, as shown in FIG. 9C, when both the cylindrical portion 56a1 and the columnar portion 56a2 are further pushed to the upper end portion of the housing portion 56b and are fully pushed, the operation is performed from the switch means 56. An irradiation start signal for instructing the start of radiation irradiation is transmitted to the table 57. Then, the console 57 transmits the irradiation start signal to the radiation source 52 to instruct the radiation imaging apparatus 1 to start irradiation of radiation, and when the radiation source 52 receives the irradiation start signal, X Radiation from the tube is started.

  In addition, the console 57 of the radiation generating apparatus transmits an irradiation start signal to the radiation source 52 and simultaneously to the console 58. The radiation generator console 57 transmits the activation signal and the irradiation start signal to the radiation source 52 and simultaneously transmits the radiation signal to the radiation imaging apparatus 1 via the base station 54. In the present embodiment, the radiographic image capturing apparatus 1 recognizes that radiation irradiation to the radiographic image capturing apparatus 1 has started based on the irradiation start signal transmitted from the console 57. The radiation image capturing apparatus 1 itself may be configured to detect the start of radiation irradiation.

  The console 58 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 composed of a CRT, an LCD, or the like, and other input means such as a keyboard or a mouse are connected thereto. The console 58 is connected to a storage means 58b composed of a hard disk or the like, and the storage means 58b is associated with information such as scintillator type information, size information, and resolution of the radiation image capturing apparatus 1. Table is stored in advance.

  In this embodiment, radiographic imaging imaging order information generated in advance by a RIS (Radiology Information System) (not shown) or the like is acquired and stored in the storage unit 58b of the console 58. Although not shown, the console 58 is appropriately connected to an imager that records and outputs a radiographic image on an image recording medium such as a film based on the image data D output from the console 58. It goes without saying that the storage means 58b may be built in the console 58.

  Prior to radiographic image capture, the console 58 reads out radiographing order information from the storage means 58b. In the present embodiment, as shown in FIG. 10, the imaging order information includes “patient ID” P2, “patient name” P3, “sex” P4, “age” P5, and “clinical department” as patient identification information. P6, “imaging region” P7 as an imaging method, “imaging direction” P8, and “bucket ID” P9 of the bucky device 51 to be used are configured. Then, “shooting order ID” P1 is automatically assigned to each shooting order information in the order in which the shooting orders are received.

  In the present embodiment, “001” in “Bucky ID” P9 represents a Bucky device 51A for standing position shooting, and “002” represents a Bucky ID of the Bucky device 51B for standing position shooting. Further, when “Bucky ID” P9 is not described and the column is blank, it indicates that the radiographic image capturing apparatus 1 is used alone.

  In addition, the patient identification information and the contents of the imaging method to be written in the imaging order information are not limited to those described above. For example, information such as the patient's date of birth, the number of medical examinations, the radiation dose, whether the patient is fat or thin It can also be configured to include, and can be set as appropriate.

  In the present embodiment, when the console 58 reads the imaging order information from the storage unit 58b, as shown in FIG. 11, a list of each imaging order information in a list format is displayed on the display unit 58a as the selection screen H1. It has become.

  The selection screen H1 is provided with a shooting order information display field h11 for displaying a list of each shooting order information. On the left side of the shooting order information display field h11, a shooting order scheduled to be shot in the shooting room Ra. A selection button h12 for selecting 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.

  An operator such as a radiologist clicks the selection button h12 to select a plurality of pieces of imaging order information scheduled to be taken in the imaging room Ra, and clicks the decision button h13. It is possible to select a plurality of pieces of shooting order information including In addition, when a plurality of pieces of imaging order information are selected, the console 58 transmits a list of the selected pieces of imaging order information to the operation console 57 of the radiation generating apparatus in the order of selection.

  In the present embodiment, the console 58 selects a plurality of radiographing order information as described above and transmits the radiographing order information to the console 57. An awakening signal for switching the power supply mode of the radiographic imaging apparatus 1 from the sleep mode to the radiographable mode is transmitted to the control means 22.

  If comprised in this way, it will become possible to switch the power supply mode of the radiographic imaging apparatus 1 to imaging | photography possible mode previously by operation with the console 58 (namely, awakening of the radiographic imaging apparatus 1), and the radiographic imaging apparatus 1 It is possible to prevent the radiation image capturing apparatus 1 from being accidentally irradiated with radiation while the power supply mode is the sleep mode.

  In the present embodiment, the radiation source 52 of the radiation generating apparatus is activated by the console 57 when at least one piece of imaging order information is transmitted from the console 58 to the console 57 of the radiation generating apparatus. By referring to the Bucky ID or the imaging method specified in the imaging order information, it is determined which radiation source 52 of the radiation generator is used for the imaging, and the radiation source 52 is automatically set. It is configured to be activated and moved to a position corresponding to the bucky device 51 to be used.

  On the other hand, as described later, the console 58 transmits a sleep signal for switching the power supply mode from the radiographable mode to the sleep mode to the radiographic image capturing apparatus 1 after a series of radiographic image capturing is completed. It has become. Further, the console 58 determines the time until the sleep signal is transmitted based on the selected plurality of pieces of radiographing order information, that is, at least radiographing order information relating to current radiographic imaging and radiographing order information relating to the next radiographic imaging. It is designed to be variable based on the relationship.

  At that time, the console 58 sets the starting point of the elapsed time for determining whether or not the time until the sleep signal is transmitted to the radiographic image capturing apparatus 1 and the irradiation start signal is that of the radiation generating apparatus. It is configured to be a point in time when it is transmitted from the console 57 to the console 58.

  Note that when the radiation of the radiation 52 is terminated from the radiation generator console 57, an irradiation end signal for instructing the radiation source 52 to end the radiation is transmitted to the radiation source 52. However, it is also possible to obtain the irradiation end signal from the console 57 and use it as a starting point for counting the passage of time. Hereinafter, a case will be described in which the time point at which the irradiation start signal is transmitted from the console 57 to the console 58 is used as the starting point of the elapsed time count.

  That is, the console 58 starts counting the elapsed time when the irradiation start signal is transmitted from the console 57 of the radiation generating apparatus, monitors the count number, and sets the time set based on the imaging order information. When the time has elapsed, it is determined that the time until the sleep signal is transmitted to the radiation image capturing apparatus 1 has elapsed, and the sleep signal is transmitted to the control unit 22 of the radiation image capturing apparatus 1 via the base station 54. It is like that.

  As described above, the console 58 indicates the time from when the irradiation start signal is transmitted from the console 57 of the radiation generating apparatus to when the sleep signal is transmitted to the radiographic image capturing apparatus 1. However, how to change the time until the sleep signal is transmitted to the radiographic image capturing apparatus 1 in the console 58 will be described in detail later.

  When the radiographic imaging is completed and the image data D is transmitted from the radiographic imaging apparatus 1, the console 58 can perform image processing such as gradation processing and frequency enhancement processing according to the region of interest and provide it for diagnosis. If it is determined, the image processed image data is stored in the storage means 58b as diagnostic image data in association with the imaging order information. The diagnostic image data associated with the imaging order information is transmitted to an interpretation waiting server (not shown) or a QA station for image inspection as necessary.

  In addition, a preview image is displayed on the display unit 58a based on the image data D transmitted and the thinned data Dt created by thinning out the image data D at a predetermined rate for each radiographic image capture at the console 58. It can also be configured to display. These preview images can also be stored in the storage means 58b in association with the shooting order information.

  Hereinafter, how to change the time T until the sleep signal is transmitted to the radiographic imaging apparatus 1 in the console 58 will be described with reference to the flowchart shown in FIG.

  In the present embodiment, as described below, the time T until the sleep signal is transmitted to the radiographic imaging apparatus 1 is configured to be variable and set by the processing according to the flowchart shown in FIG. For example, a table or the like may be prepared in advance, and the console 58 may be configured to change the time T by referring to it.

  In order to change the time T until the sleep signal is transmitted to the radiographic imaging apparatus 1 in the console 58, basically, a reference time (hereinafter referred to as a reference time) To is set in advance. If the patient identification information differs between the imaging order information related to the current radiographic imaging and the imaging order information related to the next radiographic imaging (that is, the patient to be imaged changes), or the imaging direction changes (that is, radiation) When the bucky device 51 into which the image capturing device 1 is loaded changes, or when the radiographic image capturing device 1 is loaded into the bucky device 51 or used alone, the time T is set to be shorter than the reference time To. It is made to be variable.

  That is, when the patient is switched, the interval between the current imaging and the next imaging is the longest. Accordingly, if the power supply mode of the radiographic image capturing apparatus 1 is kept in the radiographable mode during this period, it leads to wasteful consumption of the battery 24. Therefore, it is desirable to switch to the sleep mode immediately after the current radiographing is completed. In the next imaging, when an operator such as a radiographer confirms that a new patient has reached the imaging room Ra, the changeover switch 38 of the radiographic imaging apparatus 1 is operated to operate the radiographic imaging apparatus 1. Switch the power supply mode to the shootable mode.

  In addition, in the case of photographing the chest front and the chest side of the same patient in the current photographing and the next photographing, for example, there is no replacement of the patient, and since the same bucky device 51 is used, The shooting interval between the shooting and the next shooting is the shortest. Therefore, in such a case, rather than switching the power supply mode of the radiographic imaging device 1 to the sleep mode, rather than switching to the sleep mode so as not to miss the imaging timing, the imaging mode is maintained. Better to do. Therefore, in such a case, the time T is varied so as to be longer than the reference time To.

  In such a case, even if the time T is varied so as to be longer than the reference time To, an irradiation start signal in the next imaging is transmitted from the console 57 to the console 58 before the time T elapses. And the count is reset. For this reason, the power supply mode of the radiographic image capturing apparatus 1 does not transition to the sleep mode, but is maintained in the radiographable mode.

  Specifically, first, the console 58 starts counting the passage of time when an irradiation start signal is transmitted from the console 57 of the radiation generating apparatus (step S1), and sets the reference time To. (Step S2). For example, the reference time To is set to 1 minute.

  Then, the console 58 determines whether or not the current photographing is the last radiographic image photographing designated by the selected plurality of pieces of photographing order information (step S3), and the current photographing is the last photographing. When there is no next imaging (step S3; YES), since it is not necessary to vary and extend the reference time To, the time T until the sleep signal is transmitted to the radiation image capturing apparatus 1 is set to the reference time To. It is set (step S8).

  When the current radiographing is not the last radiographic image capturing designated by the selected plurality of radiographing order information (step S3; NO), the console 58 subsequently continues the radiographing order related to the current radiographic image capturing. With reference to “patient ID” P2 (see FIGS. 10 and 11) as patient identification information in the information and “patient ID” P2 in the imaging order information relating to the next radiographic imaging, the patient at the current imaging and the next imaging Are determined to be the same (step S4). In order to confirm whether the patients are the same, in addition to “Patient ID” P2, “Patient name” P3, “Gender” P4, “Age” P5, etc. are also referred to. Is also possible.

  If the patient is not the same as the current image and the next image (step S4; NO), in addition to the current patient's clothes, the next patient's undressing, the patient's guidance, and positioning, a radiographic imaging device It is assumed in advance that it takes time for a patient to be replaced because there may be cases where replacement is performed between the one Bucky device 51. For this reason, the console 58 is configured to vary the time T until the sleep signal is transmitted to the radiation image capturing apparatus 1 so as to be shorter than the reference time To (step S5). In this case, the time T is shortened to 30 seconds, for example.

  If the patients are the same (step S4; YES), the console 58 then continues with “Bucky ID” P9 (see FIGS. 10 and 11) as an imaging method in the imaging order information relating to the next radiographic imaging. Referring to FIG. 4, it is determined whether or not the radiographic image capturing apparatus (FPD) 1 is continuously used while being mounted on the same bucky apparatus 51 (step S6). For example, the radiographic imaging device 1 may be loaded into the same standing-up imaging Bucky device 51A and used continuously in the current imaging and the next imaging to image the front and side of the chest of the patient. This is the case.

  In this case, the imaging interval between the current imaging and the next imaging is the shortest, and the power supply mode of the radiographic imaging device 1 is switched to the sleep mode rather than the battery 24 of the radiographic imaging device 1 being consumed. In this case, it should be emphasized to prevent the shooting timing from being lost. Therefore, in this case (step S6; YES), the console 58 is configured to change the time T until the sleep signal is transmitted to the radiographic imaging device 1 to be longer than the reference time To ( Step S7). In this case, the time T is extended to, for example, 10 minutes.

  Therefore, in such a case, as described above, before the elapsed time count reaches the set time T, an irradiation start signal in the next imaging is transmitted from the console 57 to the console 58, and the count is reset. Therefore, the power supply mode of the radiographic image capturing apparatus 1 does not transition to the sleep mode, but is maintained in the radiographable mode.

  In addition, the patient is the same in the current imaging and the next imaging (step S4; YES), but the radiographic imaging device 1 is not used continuously with the radiographic imaging device 1 loaded in the same Bucky device 51 in the next imaging. In (Step S6; NO), the console 58 sets the time T until the sleep signal is transmitted to the radiation image capturing apparatus 1 to the reference time To (Step S8).

  As described above, the console 58 starts counting the passage of time at the time when the irradiation start signal is transmitted from the console 57 of the radiation generating apparatus (step S1). Is set by varying the time T until the transmission.

  Note that what was planned to be taken for the same patient in the current photographing and the next photographing may be changed to photographing for another patient, or the radiographic imaging device 1 may be used in the next photographing. What was planned to be photographed on the patient's chest and the like after being mounted on the standing-position photographing Bucky device 51A is changed to, for example, the standing-position photographing Bucky device 51B without the patient standing. As a result, there is a case where the photographing method in the next photographing or the patient to be photographed is changed suddenly.

  In this embodiment, in such a case, when an operator such as a radiologist operates the radiation image capturing apparatus 1 or the console 58 to give an instruction, the console 58 operates the radiation generating apparatus. The progress of the elapsed time count (see step S1) started when the irradiation start signal is transmitted from the table 57 is stopped.

  Then, the console 58 resumes the variable processing of the time T shown in the flowchart shown in FIG. 12 when a new irradiation start signal is transmitted from the console 57 of the radiation generating apparatus in the next imaging. It is like that. Therefore, in the above case, the console 58 does not transmit a sleep signal to the radiographic image capturing apparatus 1 until an irradiation start signal is newly transmitted from the console 57 of the radiation generating apparatus at least at the next imaging.

  Next, the operation of the radiographic image capturing system 100 according to the present embodiment will be described.

  As described above, an operator such as a radiographer operates the console 58 to display the selection screen H1 (see FIG. 11) on the display unit 58a and captures an image in the imaging room Ra prior to radiographic imaging. A plurality of radiographing order information relating to scheduled radiographic imaging is selected. When a plurality of pieces of imaging order information are selected, the console 58 transmits a list of the selected pieces of imaging order information to the operation console 57 (see FIG. 1) of the radiation generating apparatus in the order of selection.

  In addition, the console 58 transmits a plurality of selected radiographing order information to the console 57, and transmits an awakening signal to the control means 22 of the radiographic imaging apparatus 1 via the base station 54, thereby taking radiographic imaging. The power supply mode of the apparatus 1 is switched from the sleep mode to the photographing enable mode. The operator who has moved to the imaging room Ra later may press the changeover switch 38 (see FIG. 2) of the radiographic imaging apparatus 1 to wake up the radiographic imaging apparatus 1.

  In addition, the console 57 performs activation, movement, adjustment of the radiation direction, and the like of the radiation source 52A (see FIG. 1) of the radiation generation apparatus in accordance with the transmitted imaging order information.

  Then, the operator moves to the imaging room Ra, invites the patient to the imaging room Ra, and performs the first radiographic imaging. At that time, when the radiographic image capturing apparatus 1 is loaded and used in the bucky device 51 in the first radiographic image capturing, the operator uses the radiographic image capturing device 1 in the cassette holding portion 51a of the bucky device 51. (See FIG. 1). Then, the patient and the bucky device 51 are aligned.

  Then, the operator moves to the front chamber Rb, operates the switch means 56 of the console 57, and half-presses the button portion 56a of the switch means 56 (see FIG. 9B). Then, an activation signal is transmitted from the switch means 56 to the console 57, an activation signal is transmitted from the console 57 to the radiation source 52, and the radiation source 52 starts rotation of the anode of the X-ray tube. Moreover, in the radiographic imaging device 1 which received the starting signal, the reset process of each radiation detection element 7 is performed.

  Further, when the operator subsequently presses down the button portion 56a of the switch means 56 (see FIG. 9C), an irradiation start signal is transmitted from the switch means 56 to the console 57, and from the console 57. An irradiation start signal is transmitted to the radiation source 52, and the radiation source 52 starts irradiation of radiation from the X-ray tube. The console 57 also transmits this irradiation start signal to the console 58 at the same time.

  When an irradiation start signal is transmitted from the console 57 of the radiation generating apparatus, the console 58 starts from that point in time until a sleep signal is transmitted to the radiographic image capturing apparatus 1 according to the flowchart shown in FIG. A variable process for changing T is executed to start counting the time elapsed from the time when the irradiation start signal is transmitted from the console 57 of the radiation generating apparatus (step S1).

  And when a patient changes by the present imaging | photography and the next imaging | photography (step S4; NO), since it is assumed beforehand that it takes time from the present imaging | photography to the next imaging | photography, radiographic imaging. The time T until the sleep signal is transmitted to the device 1 is variably set so as to be shorter than the reference time To (step S5).

  Further, when the radiographic image capturing apparatus 1 is continuously used with the same bucky device 51 loaded in the next radiographing (step S6; YES), the power supply mode of the radiographic image capturing apparatus 1 is set to the sleep mode. In order to prevent the imaging timing from being lost due to the switching, the time T until the sleep signal is transmitted to the radiographic imaging device 1 is variably set to be longer than the reference time To (step S7). .

  In addition, the patient is the same in the current imaging and the next imaging (step S4; YES), but the radiographic imaging device 1 is not used continuously with the radiographic imaging device 1 loaded in the same Bucky device 51 in the next imaging. In (Step S6; NO), the console 58 sets the time T until the sleep signal is transmitted to the radiation image capturing apparatus 1 to the reference time To (Step S8).

  In the console 58, the time T until the sleep signal is transmitted to the radiographic image capturing apparatus 1 set for the radiographic image capturing apparatus 1 in the current radiographic image capturing is varied and set as described above.

  On the other hand, as described above, when the button part 56a of the switch unit 56 is fully pressed by the operator (see FIG. 9C), radiation is emitted from the X-ray tube of the radiation source 52, and radiographic imaging is performed. Is done.

  Then, in the radiographic imaging device 1 that has received the irradiation start signal, it is determined that radiation has been emitted from the radiation source 52, and after a predetermined time from that point, a process of reading out charges from each radiation detection element 7 is performed. In the reading process, as described above, radiation is generated by sequentially applying an ON voltage to the gate electrode 8g of each TFT 8 from the gate driver 15b (see FIG. 8) of the scanning drive unit 15 via the lines L1 to Lx of the scanning line 5. Electric charges are released from the detection element 7.

  Then, a voltage value is output from the amplifier circuit 18 in accordance with the released charge amount, and is correlated double-sampled by the correlated double sampling circuit 19, and the analog value image data D is converted by the A / D converter 20. Sequentially converted into digital image data D. Then, the image data D is sequentially stored in the storage unit 23.

  When radiographic imaging is not performed continuously, that is, when it is performed in a single shot, dark reading processing is performed once or a plurality of times by the radiographic imaging apparatus 1 at this stage. In the dark reading process, after the radiation image capturing apparatus 1 is left in a state where the radiation image capturing apparatus 1 is not irradiated with radiation, the dark charge accumulated in each radiation detection element 7 is set as the dark read value d in the same manner as the reading process. Read out. The read dark read value d is also stored in the storage means 23 sequentially. The dark reading process generally ends within a few hundred milliseconds, and can be completed in any case within the set time described above.

  When radiographic imaging based on a plurality of selected radiographing order information is continuously performed one after another (steps S4 and S6; YES), the radiation set by the console 58 is set to be long for the current radiographic imaging. Before the time T until the sleep signal is transmitted to the image capturing apparatus 1, an irradiation start signal in the next radiographic image capturing is transmitted from the console 57 to the console 58.

  Each time, the console 58 resets the count of elapsed time and restarts the count (see step S1 in FIG. 12), and in accordance with the flowchart shown in FIG. A time T until a sleep signal is transmitted is set. Therefore, in this case, since the sleep signal is not transmitted from the console 58 to the control unit 22 of the radiographic image capturing apparatus 1, the power supply mode of the radiographic image capturing apparatus 1 remains in the radiographable mode.

  Thus, in the radiographic imaging system 100 according to the present embodiment, when radiographic imaging is performed, the power supply mode of the radiographic imaging apparatus 1 is accurately switched to the radiographable mode. It is possible to accurately prevent a situation in which a radiographic image cannot be obtained because the power supply mode of the radiographic image capturing apparatus 1 is in the sleep mode at the time of imaging.

  On the other hand, for example, if the patient is different between the current shooting and the next shooting, the patient of the next shooting has not yet visited when the current shooting is completed, and the time interval between the current shooting and the next shooting is In some cases, it may be vacant (step S4; NO).

  In such a case, when the time T until the sleep signal is transmitted to the radiographic image capturing apparatus 1 that is set to be short and variable for the current radiographic image capturing has elapsed, the console 58 causes the base station 54 (see FIG. 1). ), A sleep signal for switching the power supply mode from the radiographable mode to the sleep mode is transmitted to the radiographic image capturing apparatus 1.

  And the control means 22 of the radiographic imaging device 1 is a communication means from the imaging | photography possible mode in which the power supply mode of the radiographic imaging device 1 is supplied to the radiation detection element 7, and radiographic imaging is possible. The mode is switched to a sleep mode in which power is supplied only to necessary function units including the antenna device 41.

  As described above, in the radiographic image capturing system 100 according to the present embodiment, the power supply mode of the radiographic image capturing apparatus 1 is changed from the image capture enable mode to the sleep mode when there is a time lapse from the current image capture to the next image capture. Since switching is performed accurately, it is possible to accurately prevent the situation where the power supply mode of the radiographic image capturing apparatus 1 remains in the image capturing enable mode and the battery 24 is consumed.

  It is also possible for the operator to instruct the console 58 to stop the counting of elapsed time (see step S1) by operating the radiation image capturing apparatus 1 or the console 58 at the operator's discretion. This is as described above. In this case, until a new irradiation start signal is transmitted from the console 57 of the radiation generating apparatus in the next imaging, or unless the operator instructs to switch to the sleep mode, the radiation imaging apparatus 1 The power supply mode remains in the photographing enabled mode.

  Further, in such a case, when the radiographic image capturing is to be stopped, the operator presses the changeover switch 38 of the radiographic image capturing device 1 to change the power supply mode of the radiographic image capturing device 1 from the radiographable mode to the sleep mode. Switch to mode.

  In the present embodiment, as described above, when the indicator 40 (see FIG. 2) of the radiographic image capturing apparatus 1 is viewed, whether the power supply mode of the radiographic image capturing apparatus 1 is the imaging enable mode or the sleep mode. Can be understood.

  Therefore, when imaging is resumed in the above case, or when it is determined that the time T until the sleep signal is transmitted to the radiographic imaging device 1 has elapsed, the operator checks the indicator 40. To do. If the power supply mode of the radiographic image capturing apparatus 1 is the sleep mode, the changeover switch 38 is pressed, and the power supply mode of the radiographic image capturing apparatus 1 is switched from the sleep mode to the radiographable mode. The next shooting can be performed.

  In this case, as described above, the console 58 may be operated to transmit a wake-up signal from the console 58 to the radiographic image capturing apparatus 1 to switch the power supply mode of the radiographic image capturing apparatus 1 to the radiographable mode. .

  However, when the radiographic imaging device 1 is loaded in the bucky device 51, the indicator 40 may not be visible in that state. Further, the operator forgets to check the indicator 40 or misunderstands that the power supply mode of the radiographic image capturing apparatus 1 is the radiographable mode and tries to use the radiographic image capturing apparatus 1 in the sleep mode. There is also a possibility.

  Therefore, in order to avoid such a situation, for example, an informing means for informing that the power supply mode of the radiographic image capturing apparatus 1 is switched to the sleep mode by sound or blinking of light or the like is set in the imaging room Ra or the front. It is provided in the room Rb, the console 58, etc., and the notification means is activated from the time when the sleep signal is transmitted from the console 58 to the radiographic image capturing apparatus 1, so that the power supply mode of the radiographic image capturing apparatus 1 is set to the sleep mode. It can also be configured to notify that it has been switched.

  Further, when the power supply mode of the radiographic imaging apparatus 1 is switched to the sleep mode, an irradiation prohibition signal is issued from the console 58 to the console 57 of the radiographic generation apparatus, and the operator powers the radiographic imaging apparatus 1. It is also possible to configure so that irradiation of radiation from the radiation source 52 is prohibited until the supply mode is switched to the imaging enable mode.

  As described above, according to the radiographic image capturing system 100 according to the present embodiment, the console 58 instructs the start of radiation irradiation to the radiation source 52 of the radiation generating device based on the selected plurality of pieces of imaging order information. The radiographic imaging apparatus 1 is imaged in the power supply mode starting from the time when the irradiation start signal to be transmitted or the irradiation end signal instructing the end of radiation irradiation is transmitted from the console 57 of the radiation generating apparatus to the console 58. A time T until transmission of a sleep signal for switching from the enable mode to the sleep mode is varied and set according to the situation.

  Therefore, when it is assumed in advance that it will take a long time from the current imaging to the next imaging, the console sleeps from the console to the portable radiographic imaging device so as to shift to the sleep mode so as to suppress the consumption of the battery 24. If it is assumed in advance that the time until the signal is transmitted is shortened and it does not take time from the current shooting to the next shooting, that is, if the shooting is performed continuously, the radiation Time until the sleep signal is transmitted from the console 58 to the radiographic image capturing apparatus 1 so that the power supply mode of the image capturing apparatus 1 is in the sleep mode and the power supply mode is maintained so as not to miss the capturing timing. It is possible to set it so that T becomes longer.

  As described above, according to the radiographic imaging system of the system of the present invention, the power supply mode of the radiographic imaging apparatus 1 is imaged without losing the imaging timing and without consuming the battery 24 wastefully. It is possible to appropriately switch between the enable mode and the sleep mode.

  When radiographic imaging is performed, the power supply mode of the radiographic imaging apparatus 1 is switched to the radiographable mode accurately, so that the power supply mode of the radiographic imaging apparatus 1 is set to the sleep mode during radiographic imaging. Therefore, it is possible to accurately prevent the occurrence of a situation in which a radiation image cannot be obtained. For this reason, it is possible to accurately prevent problems such as the need for re-imaging and the X-ray tube of the radiation generating apparatus being wasted, increasing the exposure dose to the patient and placing a burden on the patient.

  Further, when it takes time from the current imaging to the next imaging, a sleep signal is transmitted from the console 58, and the power supply mode of the radiographic image capturing apparatus 1 is accurately switched from the imaging enable mode to the sleep mode. Therefore, it is possible to accurately prevent a situation where the power supply mode of the radiation image capturing apparatus 1 remains in the image capturing enable mode and the battery 24 is consumed.

  Needless to say, the present invention is not limited to the above-described embodiment, and can be changed as appropriate.

  For example, when the distance between the place where the console 58 is installed and the radiographing room Ra is long, an operator such as a radiologist who has selected radiographing order information on the console 58 arrives at the radiographing room Ra where the radiographing is performed. It will take time. Therefore, in order to suppress battery consumption during this period, the power supply mode of the radiographic image capturing apparatus 1 can be imaged from the sleep mode after the elapse of time corresponding to the movement from the selection of a plurality of radiographing order information on the console 58. It is also possible to configure to awaken by switching to.

  In addition, when the radiographic image capturing apparatuses 1 are provided in the plurality of radiographing rooms Ra and one console 58 is commonly used in the plural radiographing rooms Ra, the radiographing rooms Ra used on the console 58 are used. After the time corresponding to the movement set in advance for each imaging room Ra has elapsed, the power supply mode of the radiographic imaging device 1 installed in the selected imaging room Ra is switched from the sleep mode to the imaging enabled mode. It can also be configured to awaken.

1 Radiographic imaging device (portable radiographic imaging device)
7 Radiation detection element 17 Reading circuit 22 Control means 24 Battery 38 Changeover switch 41 Antenna device (communication means)
51 Bucky devices 51A, 51B Plural types of Bucky devices 52 Radiation source 57 Console 58 Console 100 Radiation imaging system D Image data P Detection unit P2 Patient ID (patient identification information)
T time

Claims (5)

A detection unit in which radiation detection elements that generate charges according to the radiation dose are arranged in a two-dimensional manner;
A readout circuit that reads out the charge from the radiation detection element and converts the charge into image data for each radiation detection element;
A communication means for transmitting / receiving information to / from an external device;
A power supply mode for the electronic component, a radiographable mode that enables radiographic imaging by supplying power to the radiation detection element, and the radiation detection element by supplying power only to necessary functional units including the communication means Control means for switching between the sleep mode in which the supply of power is stopped and radiographic imaging is not possible,
A portable radiographic imaging device with a built-in battery;
A bucky device capable of loading the portable radiographic imaging device;
A radiation generation apparatus comprising a radiation source for irradiating radiation to the portable radiographic imaging apparatus and a console for instructing radiation irradiation;
A console capable of selecting a plurality of pieces of imaging order information including at least patient identification information and an imaging method, and transmitting a signal instructing switching of the power supply mode to the control means of the portable radiographic imaging device; ,
With
The console has an irradiation start signal for instructing start of radiation irradiation to the radiation source of the radiation generating apparatus or an irradiation end signal for instructing end of radiation based on the selected plurality of imaging order information. A sleep signal for switching the power supply mode from the radiographable mode to the sleep mode is transmitted to the portable radiographic imaging device, starting from the time point when the radiographic device is transmitted from the console. A radiographic imaging system, characterized in that the time until is variable and set.   In the case where the patient identification information in the radiographing order information regarding the radiographic imaging currently performed is different from the patient identification information in the radiographing order information regarding the next radiographic imaging, the console is more than the case where they are the same. The radiographic imaging system according to claim 1, wherein the radiographic imaging system is varied so as to shorten a time until the sleep signal is transmitted to the portable radiographic imaging device.   In the imaging method in the imaging order information relating to next radiographic imaging, the console is configured to continuously use the portable radiographic imaging device with the same Bucky device, The radiographic image capturing system according to claim 1, wherein the radiographic image capturing system is varied so as to increase a time until the sleep signal is transmitted to a portable radiographic image capturing apparatus.   4. The portable radiographic image capturing apparatus includes a changeover switch for switching the power supply mode from the sleep mode to the imageable mode by an operator's operation. The radiographic imaging system according to one item.   The console transmits a wake-up signal for switching the power supply mode from the sleep mode to the radiographable mode to the portable radiographic imaging device, starting from the time when the plurality of radiographing order information is selected. The radiographic imaging system according to any one of claims 1 to 4, wherein

Images