JP2012100797A - Radiation image photographing system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiation image photographing system enabling control so as to properly perform photographing even in a state that a CR cassette and an FPD cassette are together provided and photographing is performed in FPD type photographing by a synchronous system or a non-synchronous system.SOLUTION: The exposure illumination control means 58 of the radiation image photographing system 50 controls a radiation generator 57 so as to permit the emission of radiation from a radiation source 52 on the basis of the irradiation start signal from an exposure illumination switch 56 in a case that a CR system is set by a changeover means 58 and also controls so as to permit the emission of radiation from the radiation source 52 on the basis of the irradiation start signal from the exposure illumination switch 56 corresponding to whether the FPD cassette 1F is used according to the synchronous system or the non-synchronous system in a case that the FPD system is set by the changeover means 58. The radiation generator 57 adjusts the irradiation dose of the radiation emitted from the radiation source 52 corresponding to the setting of the changeover means 58.

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 radiation images have been taken using a screen film, but a stimulable phosphor plate (also referred to as a stimulable phosphor sheet) is used to digitize the radiation image. A CR (Computed Radiography) apparatus has been developed, and recently, a radiographic imaging apparatus that detects irradiated radiation with a radiation detection element and acquires it as digital image data has been developed.

  This type of radiographic imaging apparatus is known as an FPD (Flat Panel Detector), and can display image data more quickly than the above-described CR apparatus, thereby contributing to early diagnosis. Conventionally, it was developed as a so-called dedicated machine integrally formed with a support base or the like (see, for example, Patent Documents 1 and 2). 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 3 and 4).

  As a radiographic imaging device, a so-called direct type radiographic imaging device that generates a charge by a detection element in accordance with a dose of irradiated radiation such as X-rays and converts it into an electrical signal, or a scintillator that radiates irradiated radiation So-called indirect radiation image that is converted into an electric signal by generating electric charge with a photoelectric conversion element such as a photodiode according to the energy of the converted electromagnetic wave after being converted into electromagnetic wave of other wavelengths such as visible light An imaging device is known. 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.

  In the present invention, a portable radiographic imaging device is referred to as an FPD cassette, and a cassette for a CR device in which a stimulable phosphor plate is incorporated is referred to as a CR cassette. In addition, a system that performs imaging using an FPD cassette may be abbreviated as an FPD system, and a system that performs imaging using a CR cassette may be abbreviated as a CR system.

  By the way, for example, the above-mentioned dedicated machine-type radiographic imaging apparatus is usually configured integrally with a radiation generating apparatus that irradiates the radiographic imaging apparatus with radiation. An interface is constructed between the two, and radiographic imaging is performed while exchanging signals and synchronizing between the two. Hereinafter, a method of performing radiographic image capturing in a state in which the radiographic image capturing apparatus and the radiation generating apparatus are synchronized as described above is referred to as a synchronous system.

  Even when an FPD cassette is used, a console is interposed between the FPD cassette and the radiation generator, and an interface is constructed between the FPD cassette, the console, and the radiation generator, so that radiographic imaging is performed in a synchronous manner. Can be configured.

  When imaging is performed in a synchronous manner using an FPD cassette, usually, before imaging, in order to remove as much as possible the charge remaining in each radiation detection element of the FPD cassette from within each radiation detection element, resetting each radiation detection element Processing is performed. At that time, in the reset process of each radiation detection element, as shown in FIG. 32, the reset process of each radiation detection element Rm for one surface arranged in a two-dimensional form (also referred to as a matrix) in the FPD cassette is performed. Repeatedly.

  When the exposure switch of the radiation generating device is operated by a radiographer or other photographer during the reset process Rm for one surface, this indicates that radiation irradiation starts from the radiation generating device to the console. An irradiation start signal is transmitted. Then, an irradiation start signal is transferred from the console to the FPD cassette.

  When the FPD cassette receives the irradiation start signal, when the reset process Rm for one surface at that time is completed, the FPD cassette turns off the switch means of each radiation detection element and detects each radiation by irradiation. The charge generated in the element is shifted to a charge accumulation state in which the radiation detection element can be accumulated. Then, a signal indicating that photographing is possible (hereinafter referred to as a ready signal) is transmitted to the console.

  When the console receives a ready signal from the FPD cassette, the console transmits an interlock release signal to the radiation generator. And a radiation generator will irradiate a radiation with respect to FPD cassette, if an interlock release signal is received from a console. In this way, in the synchronization method, signals are exchanged among the radiation generator, the console, and the FPD cassette, and radiographic imaging is performed while synchronizing.

  On the other hand, in particular, in the FPD cassette (that is, the portable radiographic imaging device), the manufacturers of the FPD cassette, the console, and the radiation generator may be different. It may not always be easy to configure radiographic imaging while exchanging and synchronizing. Hereinafter, a method for performing radiographic imaging in a state where the FPD cassette and the radiation generation apparatus are not synchronized (or not synchronized) as described above is referred to as an asynchronous method.

  In the case of such an asynchronous method, the FPD cassette does not receive the irradiation start signal as described above from the radiation generator or the console, and must detect that the FPD cassette itself has irradiated the radiation. . Various methods such as those described in Patent Documents 5 to 7 are known as methods for detecting radiation irradiation with the FPD cassette itself.

Japanese Patent No. 3890163 JP-A-9-73144 JP 2006-058124 A JP-A-6-342099 JP 2003-126072 A JP-A-7-72254 Extract from US Pat. No. 7,211,803

  By the way, as a photographing apparatus currently installed in a hospital or a clinic, a CR method using a CR cassette is mainly used for photographing, but it is expected that an FPD cassette will be introduced in a hospital or a clinic in the future. In the future, it is expected that CR cassettes and FPD cassettes will be mixed in a photographing room such as a hospital.

  In such a situation where the CR cassette and the FPD cassette are mixed, for example, the FPD cassette intended to be used for photographing cannot be used due to a battery exhaustion or failure, and the CR cassette is used instead. It is also anticipated that a situation may arise where the cassette used is changed from a CR cassette to an FPD cassette.

  However, in such a case, the radiation dose to be applied to the FPD cassette or CR cassette from the radiation generator is not the same. When the FPD cassette is irradiated with radiation, a relatively small dose may be used. When irradiating with radiation, it is necessary to increase the radiation dose compared to irradiating the FPD cassette.

  When radiation of a large dose for CR cassette is irradiated to the FPD cassette, the output of each detection element is saturated and cannot be relieved by image processing or the like, or radiation of a small dose for the FPD cassette is used for the CR cassette. In the case of irradiation, noise due to insufficient dose is conspicuous and cannot be provided for diagnosis. Eventually, re-imaging is required.

  In addition, when photographing using the FPD cassette (that is, in the case of the FPD method), as described above, there are a case where the photographing is performed using the synchronous method and a case where the photographing is performed using the asynchronous method. In the synchronous method, radiation is emitted while the FPD cassette, console and radiation generator are synchronized as described above. In the asynchronous method, a ready signal is transmitted from the FPD cassette to the console, or radiation is emitted from the console. There is no need to send an interlock release signal to the generator, and the radiation generator basically does not wait for an action from the console side (FPD cassette side) at any timing, as in the CR system. Can be irradiated.

  If the synchronous FPD method is used for imaging, and the radiation generator is set to the specification for the asynchronous method, the console that received the ready signal from the FPD cassette in the synchronous method. Although radiation should be emitted from the radiation generating apparatus only after the interlock release signal is transmitted from, radiation is emitted from the radiation generating apparatus at an arbitrary timing.

  Therefore, radiation is irradiated during the reset process Rm (see FIG. 32) for one surface with the FPD cassette, and the radiation detection element in which the remaining reset process of the reset process Rm for one surface is performed. Then, a situation occurs in which useful charges generated by radiation irradiation flow out of the radiation detection element because the reset process has been performed. When such a situation occurs, re-photographing must be performed under normal circumstances. As described above, when re-imaging is performed, the exposure dose of the patient as the subject increases and the burden on the patient increases.

  In addition, if the asynchronous FPD method is used for imaging, and if the radiation generator is set to the specifications for the synchronous method, the radiation generator transmits from the console in the synchronous method. The radiation is emitted after waiting for the interlock release signal, but the asynchronous FPD cassette does not send the ready signal to the console and does not send the interlock release signal from the console to the radiation generator. However, the interlock release signal is not transmitted from the console, and as a result, the radiation generating apparatus is in a state where radiation cannot be irradiated indefinitely.

  Thus, in a situation where CR cassettes and FPD cassettes are mixed, and in the radiographic imaging system that is required to perform imaging in a synchronous method or an asynchronous method when performing imaging in the FPD method, Although various situations as described above are expected to occur, these situations should not occur, and it is desirable to prevent these situations from occurring accurately.

  The present invention has been made in view of the above points, and even in a situation where a CR cassette and an FPD cassette are mixed, and shooting is performed in a synchronous method or an asynchronous method when shooting with an FPD method. An object of the present invention is to provide a radiographic imaging system that can be controlled so as to perform imaging.

In order to solve the above-described problem, the radiographic imaging system of the present invention includes:
An FPD cassette that includes a plurality of radiation detection elements arranged in a two-dimensional shape, and that reads out the charges generated in each of the radiation detection elements by irradiation with radiation as image data;
A CR cassette containing a stimulable phosphor plate and storing the energy of the emitted radiation in the stimulable phosphor plate;
A radiation generator comprising: a radiation source for irradiating the FPD cassette or the CR cassette; and an exposure switch for instructing the radiation source to start radiation irradiation;
A console that generates a radiation image based on image data read from the FPD cassette or the CR cassette;
A switching unit configured to switch and set whether radiographic imaging is performed using the FPD cassette or the CR cassette for the radiation generating device;
Based on the setting by the switching means, an exposure control means for controlling the start of radiation irradiation to the radiation generating device;
With
The radiation generator adjusts the radiation dose of radiation irradiated from the radiation source according to the setting of the switching means,
The exposure control means includes
When the switching unit is set to perform radiographic imaging using the CR cassette, based on an irradiation start signal that instructs the radiation generator to start irradiation from the exposure switch. Control to allow radiation from the radiation source
When it is set by the switching means that radiographic imaging is performed using the FPD cassette, the FPD cassette is based on the irradiation start signal from the exposure switch and the radiation generating apparatus Control is performed so as to allow irradiation of radiation from the radiation source depending on which method is used, that is, a synchronous method that synchronizes with the non-synchronous method.

  According to the radiographic imaging system of the present invention, the radiographic imaging is performed on the radiation generator by the FPD system using the FPD cassette or the CR system using the CR cassette by the switching unit. Therefore, the radiation generator can accurately irradiate the radiation source with the radiation dose suitable for each method from the radiation source.

  Further, the exposure control means controls the start of radiation irradiation to the radiation generating apparatus based on the setting by the switching means. Therefore, even in a situation where the CR cassette 1C and the FPD cassette 1F are mixed, and shooting can be performed in the synchronous method or the asynchronous method when shooting in the FPD method, it is possible to perform shooting appropriately. It becomes possible to control to.

  For this reason, the FPD cassette and CR cassette are irradiated with an inappropriate dose of radiation, irradiated with an inappropriate timing, or the photographer does not receive the radiation even if the exposure switch is operated. It is possible to accurately prevent various problems from occurring.

It is a figure which shows the whole structure of the radiographic imaging system which concerns on each embodiment. It is an external appearance perspective view of a FPD cassette. It is the external appearance perspective view which looked at the FPD cassette 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 FPD cassette. 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 FPD cassette. 6 is a timing chart showing timings at which an on-voltage is applied to each scanning line of a gate driver when photographing is performed in a synchronous manner using an FPD cassette. It is a figure explaining the Bucky apparatus provided with the connector inside the cassette holding | maintenance part. It is an external appearance perspective view showing the state to which the connector of FPD cassette and the connector of the Bucky device were connected. It is sectional drawing showing the state in which the FPD cassette was inserted in the cradle and the connectors were connected. It is a figure which shows a structure provided with a tag reader as a detection means. (A) is a figure which shows the structure of an exposure switch, (B) is the state in which the 1st step operation was made with respect to a button part, (C) is a figure explaining the state in which the 2nd step operation was made. is there. 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 which displays imaging | photography order information. It is a figure which shows an example of the screen which displays each icon etc. corresponding to each imaging | photography order information. It is a figure which shows an example of the selection screen which selects FPD cassette and CR cassette. FIG. 18 is a diagram illustrating a state in which an icon I2 is focused on the selection screen of FIG. FIG. 20 is a diagram for explaining that a preview image is displayed instead of the icon I2 in the case of FIG. FIG. 21 is a diagram illustrating that a generated radiation image is displayed at a position where a preview image was displayed in the case of FIG. FIG. 21 is a diagram illustrating that focus transition is subsequently made to the icon I3 from the state illustrated in FIG. 20. It is a figure explaining changing the setting which a switching means specified by the console in 2nd Embodiment with respect to a radiation generator, or a setting. When the first-stage operation is performed on the exposure switch, a signal is transmitted from the radiation generator to the FPD cassette or the like via the switching unit, and an OK signal is returned from the FPD cassette or the like to the radiation generator via the switching unit. It is a figure explaining this. In the case of the synchronous method, when the second stage operation is performed, an irradiation start signal is transmitted from the exposure switch to the FPD cassette, and when an interlock release signal is transmitted from the FPD cassette, radiation is irradiated from the radiation source. It is a figure explaining this. In the case of the asynchronous method, when the second stage operation is performed, an irradiation start signal is transmitted from the exposure switch to the console, and when a dummy signal is transmitted from the console, the radiation source is irradiated. It is a figure to do. It is a figure showing the state in which a portable radiation generator is carried in a round-trip car and brought into a hospital room. (A) is a side view showing the structure of a cover apparatus, (B) is a top view showing the structure of the cover apparatus of the state by which the cover part was open | released. It is the schematic showing the structure of an optical detection means. (A) It is the side view which shows the example of the tumbler spring provided in the part of the hinge structure of a cover apparatus, (B) and the enlarged view which looked at the part of the hinge structure from the front. It is the schematic showing another structural example of a cover apparatus. It is a timing chart showing the timing of the irradiation start signal transmission in the synchronous method, the end of the reset process and the transition to the charge accumulation state, the transmission of the ready signal, the transmission of the interlock release signal, the radiation irradiation, and the like.

  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.

[First Embodiment]
FIG. 1 is a diagram illustrating an overall configuration of a radiographic image capturing system according to a first embodiment of the present invention.

  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 each of the following embodiments, an FPD cassette (that is, a portable radiographic imaging device) 1F described below is used as the radiographic imaging device. In addition to the FPD cassette IF, the photographing room Ra is also equipped with a CR cassette 1C or can be brought in, and is provided with a bucky device 51 that can be loaded with the FPD cassette 1F and the CR cassette 1C. It has been.

  The bucky device 51 and the radiation source 52 will be described later. In addition, a radiographic imaging device (not shown) may be installed in the radiographing room Ra. As the radiographic imaging device, the FPD cassette 1F and the dedicated radiographic imaging device are mixed. The present invention is also applied to a radiographic imaging system.

  Here, first, the FPD cassette 1F used for radiographic imaging in the radiographic imaging system 50 will be described.

  Hereinafter, as the FPD cassette 1F, a so-called indirect type FPD cassette that includes a scintillator or the like and converts emitted radiation to electromagnetic waves of other wavelengths such as visible light to obtain an electric signal will be described. Can also be applied to a so-called direct FPD cassette that directly detects radiation with a radiation detection element without using a scintillator or the like.

  2 is an external perspective view of the FPD cassette, and FIG. 3 is an external perspective view of the FPD cassette 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, in the FPD cassette 1 </ b> F, a sensor panel SP composed of a scintillator 3, a substrate 4, and the like is housed in a housing 2.

  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 FPD cassette 1F is made of a material such as a carbon plate or plastic that transmits radiation. The housing 2 is formed by closing 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 FPD cassette 1F, and the like. An indicator 40 and the like are arranged.

  As shown in FIG. 3, an antenna device 41 that is a communication unit for wirelessly transmitting 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. It is also possible to configure the image data or the like to be transmitted to the console 58 in a wired manner. In this case, for example, it is configured to transmit / receive data by connecting a cable or the like to the connector 39 described above. In the case where the antenna device 41 is provided, the arrangement location and the number of antenna devices 41 on the housing 2 are appropriately determined.

  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. In this way, the substrate 4 portion of the sensor panel SP of the FPD cassette 1F is formed. In FIG. 7, illustration of the electronic component 32 and the like is omitted.

  Here, the circuit configuration of the FPD cassette 1F 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 radiation is irradiated to the FPD cassette 1F through a subject during radiographic imaging, the scintillator 3 converts the radiation into electromagnetic waves of other wavelengths, and the converted electromagnetic waves are directly below the radiation detection 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.

  In the present embodiment, as shown in FIG. 8, the current detection means 42 that converts the current flowing through the connection 10 into, for example, a voltage value is provided in the connection 10 of the bias line 9. The current detection unit 42 outputs a voltage value converted from the current value to the control unit 22.

  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 scan driving unit 15 and the readout circuit 17 of the FPD cassette 1F. The control means 22 is connected to a storage means 23 constituted by a DRAM (Dynamic RAM) or the like, and a battery 24 for supplying power to each functional part of the FPD cassette 1F. Further, the above-described antenna device 41 is connected to the control means 22.

  In the present embodiment, the FPD cassette 1 </ b> F can perform shooting using the above-described synchronous method or asynchronous method. In the present embodiment, as will be described later, the FPD cassette 1F is a synchronous method when used in the Bucky device 51, and is used in a single state without being loaded into the Bucky device 51. In the asynchronous method, shooting is performed respectively.

  When shooting in the synchronous mode, the control unit 22 sequentially applies ON voltages to the lines L1 to Lx of the scanning line 5 from the gate driver 15b of the scanning driving unit 15 before shooting, as shown in FIG. The TFTs 8 connected to the scanning lines 5 are sequentially turned on to discharge the charges remaining in the radiation detection elements 7, and the reset processing of the radiation detection elements 7 is performed. In this synchronization method, it is not necessary to detect the current flowing through the connection 10 of the bias line 9, and therefore the current detection means 42 is turned off.

  Then, as will be described later, when the irradiation start signal is transferred from the console 58 that has received the irradiation start signal from the radiation generator 57 (see FIG. 1) via the repeater 54, the last line Lx of the scanning line 5. The application of the ON voltage is continued until the reset process Rm (see FIG. 32) for one surface is performed, and then the OFF voltage is applied to each line L1 to Lx of the scanning line 5 from the gate driver 15b to detect each radiation. The TFT 8 of the element 7 is turned off to shift to the charge accumulation state. Then, a ready signal (see FIG. 32) is transmitted to the console 58.

  Note that, as will be described later, when the irradiation start signal is received from the radiation generator 57, instead of being configured to transfer the irradiation start signal from the console 58 to the FPD cassette 1, at that stage, the FPD is transmitted from the console 58. In some cases, the cassette 1 is inquired as to whether or not it is ready to shoot. In this case, the FPD cassette 1 completes the reset process Rm for one surface as described above, and charges A ready signal is transmitted to the console 58 at the time of transition to the accumulation state.

  Then, an interlock release signal is transmitted from the console 58 that has received the ready signal from the FPD cassette 1F to the radiation generator 57.

  As will be described later, when receiving the interlock release signal from the console 58, the radiation generator 57 irradiates the FPD cassette 1F with radiation from the radiation source 52 (see the hatched portion in FIG. 9). When radiation irradiation ends, the FPD cassette 1F sequentially applies on-voltages to the lines L1 to Lx of the scanning line 5 from the gate driver 15b, and reads out the image data D from the radiation detection elements 7. Done.

  In this way, in the synchronization method, signals are exchanged between the FPD cassette 1F and the radiation generator 57, and radiographic imaging is performed while synchronizing.

  In addition, when shooting in an asynchronous manner, the control unit 22 operates the current detection unit 42. And although illustration is omitted, as in the case of the synchronous method (see FIG. 9), before imaging, on-voltages are sequentially applied to the lines L1 to Lx of the scanning line 5 to reset the radiation detection elements 7. Process.

  In the case of the asynchronous system, radiation is emitted from the radiation source 52 based on an operation of an exposure switch 56 of a radiation generation device 57 described later by a radiographer or the like regardless of reset processing or the like in the FPD cassette 1F. When the radiation is irradiated, a part of the electric charge generated in each radiation detection element 7 due to the irradiation of the radiation flows out to the bias line 9, and the current flowing in the connection 10 increases rapidly.

  Therefore, the control unit 22 monitors the voltage value output from the current detection unit 42, and determines that radiation irradiation has started when the voltage value increases, for example, exceeding a preset threshold value. It has become. The detection of the start of radiation irradiation using the current detection means 42 is described in detail in, for example, Japanese Patent Application Laid-Open No. 2009-219538.

  When the control unit 22 determines that radiation irradiation has started, it immediately stops the reset process of each radiation detection element 7 and applies an off voltage to each line L1 to Lx of the scanning line 5 from the gate driver 15b. Thus, the TFT 8 of each radiation detection element 7 is turned off to shift to the charge accumulation state.

  When the radiation irradiation is completed, the on-voltage is sequentially applied from the gate driver 15b to the lines L1 to Lx of the scanning line 5 in the same manner as in the synchronous method, and the image data D from each radiation detection element 7 is applied. Read processing is performed.

  In this way, in the asynchronous method, the radiation image capturing is performed by detecting that the irradiation of radiation is started by the FPD cassette 1F itself. Note that the radiation irradiation start detection method in the asynchronous method is not limited to the method using the current detection unit 42 as in the present embodiment, but various methods such as the methods described in Patent Documents 5 to 7 described above, for example. Is not limited to the method using the current detection means 42.

  On the other hand, in the present embodiment, the control means 22 thins out each image data D at a predetermined ratio based on each image data D read from each radiation detection element 7 and stored in the storage means 23, and thinned data for preview. Dt is created.

  The thinned data Dt is, for example, image data D for one pixel every 3 × 3 pixels or 4 × 4 pixels when each image data D is arranged corresponding to each radiation detecting element 7 arranged in a two-dimensional form. Or the image data D from each radiation detection element 7 connected to each line L1, L4, L7,... Of the scanning line 5, respectively. The image data D from each radiation detection element 7 connected to each line Ln at predetermined intervals may be extracted and created.

  When the radiographic image capturing is completed and the image data D is read out from each radiation detection element 7 and stored in the storage unit 23, the control unit 22 immediately creates the thinned data Dt, and the thinned data Dt includes the FPD cassette 1F. A cassette ID, which is identification information, is assigned and transmitted to the console 58 or the like as will be described later. The thinning data Dt is transmitted every time radiographic images are taken.

  After transmitting the thinned data Dt to the console 58, the control unit 22 assigns a cassette ID to the image data D that is the basis for creating the thinned data Dt, that is, all image data D obtained by the photographing. It is automatically transmitted to the console 58.

  As described above, the thinning data Dt is automatically transmitted without waiting for an instruction from the console 58 or the like. However, the transmission of all the image data D is performed at the time when the transmission instruction is issued from the console 58 or the like. It is also possible to configure so that the data is transmitted.

  When the thinning data Dt is transmitted from the FPD cassette 1F to the console 58 when the thinning data Dt is transmitted, the image data D is transmitted from the FPD cassette 1F to the console 58. Of all the image data D, only the image data D other than the thinned data Dt that has already been transmitted can be transmitted.

  In this case, the console 58 is configured to combine the thinned data Dt that has already been received and the newly transmitted image data D to restore the entire image data D. When the thinned data Dt is directly transmitted from the FPD cassette 1F to a device other than the console 58, since the thinned data Dt is not transmitted to the console 58, the FPD cassette 1F is sent to the console 58. All the image data D is transmitted.

  As will be described later, when the FPD cassette 1F is not loaded in the bucky device 51 and used alone (that is, when nothing is connected to the connector 39 (see FIG. 2)), the control means 22 Transmits the thinned data Dt, the image data D, an offset correction value, which will be described later, and the like to the console 58 via the antenna device 41 by radio.

  Further, when the FPD cassette 1F is loaded and used in the bucky device 51 (that is, when the connector 51b of the bucky device 51 (see FIGS. 10 and 11 described later) is connected to the connector 39), the control means 22 is configured to transmit thinning data Dt and the like to the console 58 in a wired manner via the bucky device 51.

  The control means 22 calculates the offset amount superimposed on the image data D obtained by these radiographic image captures at the end of each radiographic image capture or at the end of a series of radiographic image captures. In order to obtain an offset correction value for correction, so-called dark reading processing is automatically performed. It is also possible to perform a dark reading process before single or a series of radiographic imaging starts.

  In the dark reading process, each TFT 8 of the FPD cassette 1F is turned off and left for a predetermined time in a state where the FPD cassette 1F is not irradiated with radiation. Then, in the same manner as the reading process described above, each radiation detection element 7 The accumulated dark charge or the like is read out as a so-called dark read value. The read dark read value is stored in the storage means 23.

  Then, the control means 22 uses the read dark reading value for each radiation detection element 7 as an offset correction value or performs dark reading processing a plurality of times to obtain a plurality of dark values obtained for each radiation detection element 7. An offset correction value is calculated by averaging the read values. Then, a cassette ID, which is identification information of the FPD cassette 1F, is assigned to the offset correction value and is automatically transmitted to the console 58.

  On the other hand, as will be described later, when the FPD cassette 1F is brought into the photographing room Ra, it is inserted into a cradle 55 described later as detection means. At that time, when the connector 39 (see FIG. 2) is connected to the connector 55a (see FIG. 12 described later) of the cradle 55 when the FPD cassette 1F is inserted into the cradle 55, the control means 22 Through this, a cassette ID which is identification information of the FPD cassette 1F is notified to a repeater 54 (see FIG. 1) which will be described later.

  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.

  As will be described later, the portable FPD cassette 1F has a size compatible with the CR cassette 1C, and can be used by being installed in a later-described Bucky device 51 in the facility.

  Further, when the FPD cassette 1F is loaded in the bucky device 51, the battery 24 (see FIG. 8) is supplied with power from the bucky device 51, but in a single state where the FPD cassette 1F is not loaded in the bucky device 51. The power is supplied from the control unit 22, the bias power source 14, the scanning drive unit 15, and the reading unit 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.

  As will be described later, when the FPD cassette 1F is loaded in the bucky device 51, the FPD cassette 1F is supplied with power from the bucky device 51, but in a single state not loaded in the bucky device 51, the battery 24 (See FIG. 8), 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).

  Then, when the radiographic imaging, the reading process of the image data D, and the like are not performed, if power is supplied to each function unit, the battery 24 is consumed, so the FPD cassette 1F supplies power to each function unit. The mode can be set between a state in which radiographic imaging can be performed, i.e., a radiographable mode in which radiography can be performed, and a sleep mode in which no power is supplied to each functional unit when radiographic imaging is not performed. It can be switched.

  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 and the scanning drive unit 15. Power is not supplied to the read circuit 17 (read IC 16) or the like.

  When the power switch 37 (see FIG. 2) is pressed, whether to start up the FPD cassette 1F in the image-capable mode or the sleep mode is appropriately set, but at least when the selection switch 38 is pressed In addition, when the FPD cassette 1F is in the sleep mode, the mode of the FPD cassette 1F is switched to the photographing enabled mode.

  In addition, after the FPD cassette 1F has been switched to the photographing enabled mode, if radiographic image capturing is not performed even after a predetermined time has elapsed, the mode is automatically switched to the sleep mode when the predetermined time has elapsed. It is like that.

  Then, when the mode is switched, the FPD cassette 1F transmits a signal indicating that the photographing mode has been set or a signal indicating that the sleep mode has been entered, together with its own cassette ID, to the console 38. It has become.

  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 identification of the FPD cassette 1 is performed before the power is turned off. A cassette ID that is information and a stop signal indicating that the cassette ID is turned off are transmitted to the console 58 via the antenna device 41.

  Next, the CR cassette 1C used for radiographic imaging in the radiographic imaging system 50 will be described.

  As a configuration of the CR cassette 1C, for example, a configuration described in Japanese Patent Application Laid-Open No. 2003-287833 or the like can be adopted, but a known one can be used for the CR cassette 1C, There is no particular limitation as long as it includes a stimulable phosphor plate.

  In the present embodiment, a barcode (not shown) carrying identification information of the CR cassette 1C is attached to the CR cassette 1C, for example, on the back surface thereof. When the cassette 1C is loaded into a cassette holding portion 51a of the bucky device 51 to be described later, the cassette 1C is read by a barcode reader provided in the bucky device 51.

  Note that the method for reading the identification information of the CR cassette 1C loaded in the bucky device 51 does not necessarily have to be based on a bar code, and the CR cassette 1C includes the one that carries the identification information. Any configuration may be used as long as it includes a CR cassette identification information reading means for reading the identification information of the loaded CR cassette 1C.

  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 an FPD cassette 1F or a CR cassette 1C into a cassette holding portion 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.

  In the present embodiment, the bucky device 51 is configured so that the conventional CR cassette 1C can be loaded into the cassette holding part 51a and used, and the existing bucky device installed for the CR cassette in the photographing room Ra is used. An apparatus can be used.

  Therefore, in the present embodiment, the FPD cassette 1F is formed to have the same dimensions as the CR cassette 1C. That is, the CR cassette 1C 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) in the conventional cassette for screen films. 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.

  Therefore, the FPD cassette 1F is also compliant with the JIS standard in the cassette for screen films to which the CR cassette 1C complies, in order to be able to be loaded into the Bucky device 51 that can load the JIS standard size CR cassette 1C. 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 FPD cassette 1F with the above dimensions, and the FPD cassette 1F can be formed in an arbitrary size and shape. Is possible. However, in that case, as the bucky device 51, it is necessary to newly install a bucky device that can be loaded with an FPD cassette 1F having an arbitrarily set shape in the photographing room Ra.

  As shown in FIG. 10, a connector 51b connected to the connector 39 (see FIG. 2) of the loaded FPD cassette 1F is provided inside the cassette holding portion 51a of the bucky device 51. This is the same in the bucky device 51B for standing position photography as well as the bucky device 51A for standing position photography shown in FIG.

  As described above, instead of providing the connector 51b inside the cassette holding portion 51a of the bucky device 51, the FPD cassette 1F extends from the bucky device 51 before being loaded into the bucky device 51, as shown in FIG. It is also possible to connect the connector 51b provided at the end of the cable to the connector 39 of the FPD cassette 1F and load the FPD cassette 1F into the cassette holding portion 51a of the bucky device 51 in this state.

  When the connector 51b and the connector 39 of the FPD cassette 1F are connected, the bucky device 51 reads the cassette ID that is the identification information from the FPD cassette 1F, and the cassette ID of the FPD cassette 1F and the bucky ID that is its own identification information. Are associated with each other and transmitted to the console 58.

  As described above, when the FPD cassette 1F is loaded in the cassette holding unit 51a and used, the bucky device 51 uses the thinned data Dt and the image data D output from the FPD cassette 1F via the connector 39. The offset correction value is transmitted to the repeater 54, which will be described later, in a wired manner and transmitted to the console 58.

  Further, the connector 51b of the bucky device 51 and the connector 39 of the FPD cassette 1F are connected to supply power from the bucky device 51 to the FPD cassette 1F. Therefore, when the connectors 39 and 51b are connected to each other, the control means 22 of the FPD cassette 1F stops the supply of power from the battery 24 (see FIG. 8) to each functional unit, and the bucky device via the connector 39 The power supplied from 51 is switched to be supplied to each functional unit. It is also possible to charge the battery 24 at the same time while supplying power to each functional unit.

  Further, as described above, the bucky device 51 is configured so that the CR cassette 1C can be loaded and used in the cassette holding unit 51a. Although not shown, the bucky device 51 is provided in the cassette holding unit 51a of the bucky device 51. Is provided with a barcode reader or the like as CR cassette identification information reading means for optically reading the barcode of the above-described CR cassette 1C when the CR cassette 1C is loaded.

  When the barcode device 51 reads the barcode of the CR cassette 1C with the barcode reader, the bucky device 51 reads the barcode information which is identification information of the CR cassette 1C from the read information, and the barcode information of the CR cassette 1C and itself. This is associated with the Bucky ID, which is the identification information, and is transmitted to the console 58.

  The console 58 knows that imaging is performed by the CR method by transmitting the barcode information, so that the radiation dose from the radiation source 52 of the radiation generator 57 corresponds to the CR method ( In other words, control is performed so that switching is performed (in order to increase the irradiation dose as compared with FPD method imaging).

  Further, after photographing, the CR cassette 1C is loaded into an image reading device 61 (described later) installed outside the photographing room Ra, and the barcode information of the CR cassette 1C read by the image reading device 61 is associated with the image data D. Thus, the console 58 can associate the read image data D with the imaging order information by using the cassette ID of the CR cassette 1C included in the barcode information as a key. Become.

  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 is possible to irradiate the FPD cassette 1F or the CR cassette 1C loaded in the bucky device 51A for standing photographing or the bucky device 51B for standing photographing. It has become.

  The radiographing room Ra is also provided with a portable radiation source 52B that is not associated with the standing-up radiographing or the supine radiographing apparatus 51A, 51B. The portable radiation source 52B can be carried anywhere in the photographing room Ra, and can irradiate radiation in an arbitrary direction. Although FIG. 1 shows a case where the portable radiation source 52B is controlled by the radiation generator 57 of the radiation source 52A, the portable radiation source 52B is independent of the radiation generator 57 of the radiation source 52A. It is also possible to have a configuration of

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

  Note that the FPD cassette 1F and the CR cassette 1C can be used for radiographic imaging in a single state that is not loaded in the bucky device 51 in this way.

  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 photographing room Ra is shielded with lead or the like, even if information such as the image data D is transmitted / received from the FPD cassette 1F via the antenna device 41 in the photographing room Ra, it cannot be transmitted and received as it is. Therefore, as shown in FIG. 1, when the FPD cassette 1F and the console 58 communicate wirelessly, a repeater (also referred to as a base station or a wireless access point) 54 provided with a wireless antenna 53 that relays these communications. Is provided.

  As described above, the bucky device 51 and the repeater 54 are connected by a cable or the like. When the FPD cassette 1F is loaded into the bucky device 51 and used, the thinned data Dt output from the FPD cassette 1F is used. Are transmitted to the console 58 in a wired manner via the bucky device 51, the repeater 54, and the like.

  The repeater 54 transfers an irradiation start signal from the console 58 to the FPD cassette 1F (or inquires from the console 58 to the FPD cassette 1) when the FPD cassette 1F is used for shooting in the above-described synchronization method. ) And transmission of a ready signal from the FPD cassette 1F to the console 58 are relayed.

  A cradle 55 is connected to the repeater 54. As shown in FIG. 12, when the FPD cassette 1F brought into the photographing room Ra is inserted and the connector 39 of the FPD cassette 1F and the connector 55a of the cradle 55 are connected, the cassette is fed from the FPD cassette 1F as described above. The ID is notified to the repeater 54 via the cradle 55. When the cassette ID of the FPD cassette 1F is transmitted from the cradle 55, the repeater 54 notifies the console 58 of the cassette ID.

  The cradle 55 is normally used for storing and charging the FPD cassette 1F and the like. In each of the following embodiments, the cradle 55 can also be configured to have a function such as charging. It is. Furthermore, although FIG. 12 shows the cradle 55 provided with two insertion ports for inserting the FPD cassette 1F, the number of the insertion ports may be one, or three or more.

  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, as a detection means for detecting the FPD cassette 1F brought into the photographing room Ra or the front room Rb and notifying the console 58 of the cassette ID, instead of using the cradle 55 as described above, or in combination with the gradle 55 Then, as shown in FIG. 13, for example, a tag reader 60 may be provided near the door of the front chamber Rb. In FIG. 13, an image reading device 61 (see FIG. 1) to be described later is not shown.

  In such a configuration, a tag (not shown) such as a so-called RFID (Radio Frequency IDentification) tag is built in the FPD cassette 1F in advance, and unique information such as a cassette ID of the FPD cassette 1F is stored in the tag. deep. When the FPD cassette 1F passes through the vicinity of the tag reader 60 and is brought into the photographing room Ra or the front room Rb, the tag reader 60 reads information such as a cassette ID from the tag of the FPD cassette 1F, and the cassette ID is read from the console 58. Can be configured to notify.

  As described above, it is preferable to use the tag reader 60 as the detection means, since it is possible to detect both the FPD cassette 1F brought into the photographing room Ra and the taking-out from the photographing room Ra. In this case, the tag reader 60 and the cradle 55 may be configured to double check whether at least the FPD cassette 1F is brought into the photographing room Ra. When only the tag reader 60 is used as the detection means, the cradle 55 is used only for charging the FPD cassette 1F, for example.

  As shown in FIG. 1, the front chamber Rb is provided with a radiation generator 57 including an exposure switch 56 and the like for instructing the radiation source 52 to start radiation irradiation.

  For example, as shown in FIG. 14A, the exposure switch 56 includes a rod-shaped button portion 56a having a predetermined stroke, and a housing that supports the button portion 56a so as to be movable in a stroke direction indicated by an arrow S in the drawing. It is comprised with the body part 56b. The button part 56a of the exposure switch 56 includes, for example, a cylindrical part 56a1 protruding upward from the casing part 56b and a columnar part 56a2 protruding further upward from the inside thereof.

  Then, as shown in FIG. 14B, when the photographer pushes the column portion 56a2 into the upper end portion of the cylindrical portion 56a1 in the stroke direction S and performs the first stage operation (that is, the so-called half-press operation is performed). Once done, the exposure switch 56 is adapted to send an activation signal to the radiation generator 57. When the radiation generator 57 receives this activation signal, the radiation source 52 is brought into a standby state by starting rotation of the anode of the X-ray tube of the radiation source 52.

  As shown in FIG. 14C, when the cylindrical portion 56a1 and the columnar portion 56a2 of the exposure switch 56 are both pushed up to the upper end portion of the housing portion 56b and the second stage operation is performed (that is, so-called When the full-press operation is performed), the exposure switch 56 transmits an irradiation start signal to the radiation generator 57.

  The radiation generator 57 controls the irradiation of radiation from the radiation source 52 as described above. In the present embodiment, the radiation generator 57 performs radiography by the FPD method from a console 58 serving as a switching unit described later. When the signal indicating the effect or the signal indicating that the CR method is performed is received, the radiation source is adjusted by adjusting the irradiation dose of the radiation irradiated from the radiation source 52 so as to correspond to each method according to the setting of the switching unit. The control for 52 is switched.

  In the present embodiment, when the radiation generator 57 irradiates the radiation from the radiation source 52, the radiation generator 57 irradiates the radiation from the radiation source 52 only when the interlock release signal is received as a response to the transmitted irradiation start signal. It is configured. That is, the radiation generating device 57 does not irradiate the radiation from the radiation source 52 at the stage when the radiographing start signal is transmitted from the exposure switch 56 when the second operation is performed on the exposure switch 56 by the photographer. The radiation source 52 is controlled so that radiation is emitted from the radiation source 52 for the first time when an interlock release signal is transmitted from 58.

  In this embodiment, the console 58 is provided in the front chamber Rb, and is configured 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 is not shown via a network such as a LAN (Local Area Network) or the like (HIS) (Hospital Information System) or RIS (Radiology Information). System), PACS (Picture Archiving and Communication System), etc. are connected.

  Although not shown, the console 58 includes an external device such as another computer or an imager that records and outputs a radiation image on an image recording medium such as a film based on the image data D output from the console 58. Are connected via a LAN or the like.

  As described above, when the FPD cassette 1F brought into the photographing room Ra is inserted into the console 58 and the cassette ID of the FPD cassette 1F is transmitted via the cradle 55 or the repeater 54, the cassette ID is received. Is stored in the storage means 59, and it is recognized and managed that the FPD cassette 1F having the cassette ID has been brought into the photographing room Ra or the front room Rb.

  In addition, as described above, when the console 58 transmits a signal indicating that the photographing enabled mode is entered from the FPD cassette 1F together with the cassette ID, the console 58 is associated with the cassette ID stored in the storage unit 59. If the information indicating the stored mode is information indicating the shootable mode, the information is left as it is. If the information indicating the stored mode is information indicating the sleep mode, the cassette ID is set to the shootable mode. The information to be represented is newly associated and saved.

  When a signal indicating that the sleep mode has been entered is transmitted from the FPD cassette 1F together with the cassette ID, the mode stored in association with the cassette ID stored in the storage unit 59 is indicated. If the information is information representing the sleep mode, the information is left as it is. If the information representing the stored mode is information representing the shootable mode, the cassette ID is newly associated with the information representing the sleep mode and overwritten. save.

  In this way, the console 58 recognizes whether the FPD cassette 1F is currently in the photographing enabled mode or the sleep mode, and manages the power supply mode of each FPD cassette 1F. Yes.

  Further, as described above, when an activation signal indicating that the console 58 is powered on and activated is transmitted from the FPD cassette 1F together with the cassette ID, the console 58 stores the cassette ID stored in the storage unit 59 in the cassette ID. If the information indicating the state stored in association is information indicating the start state, the information is left as it is. If the information indicating the stored state is information indicating the stop state, the cassette ID indicates the start state. Is newly overwritten and stored in association with the information representing.

  In addition, when a stop signal indicating that the power is turned off and turned off is transmitted from the FPD cassette 1F together with the cassette ID, the FPD cassette 1F is stored in association with the cassette ID stored in the storage unit 59. If the information indicating the stopped state is information indicating the stopped state, the information is left as it is. If the information indicating the stored state is information indicating the activated state, information indicating the stopped state is newly added to the cassette ID. Overwrite and save in association with.

  In this way, the console 58 recognizes whether the FPD cassette 1F is currently activated or stopped, and manages the activation state of each FPD cassette 1F.

  Further, as described above, when the cassette ID and the Bucky ID of the FPD cassette 1F are transmitted from the Bucky device 51 to which the FPD cassette 1F is connected to the connector 51b, the console 58 is stored in the storage unit 59. This cassette ID is stored in association with a Bucky ID.

  Further, when the connection between the FPD cassette 1F and the connector 51b is released, the association between the cassette ID and the bucky ID of the FPD cassette 1F stored in the storage unit 59 is released, and only the cassette ID is obtained. It comes to save.

  In this way, when the FPD cassette 1F is used while being loaded in the bucky device 51, the console 58 recognizes which FPD cassette 1F is loaded in which bucky device 51 or not. To manage.

  When the CR cassette 1C is loaded in the Bucky device 51 and the barcode information and the Bucky ID of the CR cassette 1C are transmitted from the Bucky device 51, the console 58 associates the barcode information with the Bucky ID. In addition, it is stored in the storage means 59.

  In this way, when the CR cassette 1C is loaded in the bucky device 51, the console 58 recognizes and manages which CR cassette 1C is loaded in which bucky device 51.

  Further, in the present embodiment, the console 58 indicates that, when the FPD cassette 1F used for shooting is used at least in an asynchronous manner, the shooting is performed in an asynchronous manner with respect to the FPD cassette 1F. A signal is transmitted. When the control means 22 (see FIG. 8) of the FPD cassette 1F receives a signal from the console 58, the control means 22 activates the current detection means 42 and shifts to a mode in which the FPD cassette 1F itself detects the start of radiation irradiation. It is like that.

  As shown in FIG. 1, the console 58 is connected to an image reading device 61 that reads image data D from the photostimulable phosphor plate of the CR cassette 1C. In this embodiment, the image reading device 61 is installed outside the photographing room Ra and the front room Rb, but the installation location is arbitrarily determined. Further, FIG. 1 shows a case where only one image reading device 61 is installed. However, it is possible to configure a configuration in which a plurality of image reading devices 61 are installed. It is decided appropriately.

  As the configuration of the image reading device 61, for example, the configuration described in Japanese Patent Application Laid-Open No. 2003-287833 described above can be adopted, but the image data D from the photostimulable phosphor plate in the CR cassette 1C is used. If it can read, it will not be limited to said structure.

  Further, as described above, the console 58 is connected to the HIS and RIS, and in the HIS and RIS, imaging necessary for performing predetermined radiographic imaging for individual patients is set in advance. Order information can be registered. Note that, instead of registering the imaging order information in the HIS or RIS, the imaging order information may be registered in advance on the console 58 and stored in the storage unit 59, for example.

  As illustrated in FIG. 15, for example, the imaging order information includes “patient ID” P2, “patient name” P3, “gender” P4, “age” P5, “clinical department” P6, and imaging conditions as patient information. The “imaging region” P7, “imaging direction” P8, and the like, and information on whether or not to perform imaging in a state where the FPD cassette 1F and the CR cassette 1C are loaded in the Bucky device 51, etc. The item “Bucky ID” P <b> 9 is provided, and when the item is loaded in the Bucky device 51, the Bucky ID is described.

  In the example shown in FIG. 15, the Bucky IDs “001” and “002” represent the Standing shooting Bucky device 51A and the Standing shooting Bucky device 51B, respectively, and the Bucky ID “003” indicates the FPD cassette 1F. This means that the device is used alone without being loaded into the bucky device 51. Note that when the FPD cassette 1F is used in a single state without being loaded in the bucky device 51, the “buoy ID” “003” is entered if the FPD cassette 1F is used in a single state and the Bucky ID is blank. This is because it cannot be distinguished from forgetting.

  Therefore, any other display method can be adopted as long as it indicates that the FPD cassette 1F is used in a single state, and can be determined as appropriate. Note that, instead of the bucky ID, three types of icons representing standing bucky, saddle bucky, and single use may be prepared, and one icon may be displayed in association with each photographing order. is there. If comprised in this way, it will become easy to visually recognize which imaging device should be used before a radiographer etc. image | photographing, and it becomes difficult to make a mistake.

  The imaging order information also includes an item “cassette ID” P10 of the cassette to be used. 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 the imaging conditions to be written in the imaging order information are not limited to those described above, and include, for example, information such as the patient's date of birth, the number of examinations, the radiation dose, and whether the patient is fat or thin. It is also possible to configure as described above. Hereinafter, a case where a plurality of pieces of imaging order information are registered for one patient will be described.

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

  In the present embodiment, the console 58 obtains necessary radiographing order information from the HIS and RIS by the operation of a radiographer or other radiographer. Note that when the imaging order information is stored in the storage unit 59, the console 58 obtains each necessary imaging order information from the storage unit 59.

  When obtaining necessary radiographing order information from the HIS, RIS, or storage means 59, for example, the photographer inputs the name, patient ID, etc. of the patient to be radiographed on the console 58, or an imaging request form brought by the patient. Are read by a barcode reader and input to the console 58, or when the shooting date is specified in the shooting order information, the shooting date is input to the console 58, etc. It is possible to obtain the necessary radiographing order information from the HIS, RIS, or storage means 59 by this method.

  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.

  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, shooting order information scheduled to be shot is selected. A selection button h12 is provided for each shooting order information. In addition, a determination button h13 and a return button h14 are provided below the shooting order information display field h11.

  Then, for example, when the photographer clicks the selection button h12, selects, for example, four pieces of imaging order information regarding the patient “A”, and clicks the decision button h13, the console 58 is displayed on the display unit 58a in FIG. A screen H2 as shown in FIG. That is, the console 58 displays the icons I1 to I4 corresponding to each selected shooting order information on the display unit 58a, for example, in ascending order of shooting order ID (see P1 in FIG. 16 and the like), that is, in the order of registration. It has become.

  Although the registration order is basic, for example, when there are imaging orders for both the left and right parts with respect to the limbs, etc., based on the condition that the imaging is from the left to the first, or from the right to the first, in order to prevent left-right confusion. May be rearranged. In addition, when the target region covers the whole body, it may be rearranged on the basis of the condition from upper (head) to lower (leg).

  FIG. 17 shows the case where the icons I1 to I4 are displayed side by side on the screen H2 from the left side in the left-right direction. However, the present invention is not limited to this. For example, the icons I1 to I4 are displayed in the vertical direction. It is also possible to arrange them so as to be arranged from the upper side, and the display method of the icons I1 to I4 is appropriately set.

  Furthermore, the icons I1 to I4 are arranged in the registered order. In addition to this, for example, in each selected radiographing order information, a patient ID (see P3 in FIG. 16 or the like) or a medical treatment is different. When items with different departments (see P6) are included, the icons I corresponding to the imaging order information of the same patient or department can be displayed so as to be adjacent to each other regardless of the registration order. .

  As shown in FIG. 17, the icons I1 to I4 each have an imaging number such as “KM-0001”, an imaging region (P7) such as “abdominal front P → A”, an imaging direction (P8), The presence / absence of the use of the bucky device 51 such as “” and the type of the bucky device 51 to be used are displayed.

  In the example of FIG. 17, the icon I1 corresponding to the shooting order information (see FIG. 16 and the like) with the shooting order ID “001” using the bucky device 51 for the supine position shooting has a display portion Ia in the icon I1. A horizontally long square is displayed on the icon I2 and I3 corresponding to the shooting order information of the shooting order IDs “002” and “003” using the standing-up shooting bucky device 51. A vertically long square is displayed in Ia.

  Further, in the icon I4 corresponding to the imaging order information of the imaging order ID “004” that does not use the bucky device 51, a perspective view-like figure of the FPD cassette 1F is displayed on the display portion Ia in the icon I1.

  It should be noted that the display portion Ia in the icon I displays the use of the stand-up or stand-up shooting bucky device 51 or the use of the FPD cassette 1F alone as described above. As described above, measures are taken as appropriate, such as a display that is easy to understand for radiologists and the like, rather than a square or perspective figure.

  When the console 58 displays the icons I1 to I4, referring to the Bucky ID associated with the cassette ID stored in the storage unit 59, the photographing using the Bucky device 51 as shown in FIG. The cassette ID of the FPD cassette 1F currently loaded in the bucky device 51, the size and resolution of the FPD cassette 1F, and the like are displayed on the display portion Ib of the icon I of the order information.

  In the example of the screen H2 shown in FIG. 17, since the cassette or the like loaded in each bucky device 51 is the FPD cassette 1F, the cassette ID of the FPD cassette 1F is displayed on the display portion Ib of the icon I. However, if the cassette loaded in the bucky device 51 is a CR cassette IC, or the cassette specified in the “cassette ID” P10 column of the imaging order information is a CR cassette 1C, the display portion Ib Is displayed indicating the CR cassette 1C.

  Further, for example, when changing to use a bucky device 51 different from the bucky device 51 set for each icon I1 to I4, or when the FPD cassette 1F wants to shoot in a single state without using the bucky device 51 ( (Or vice versa), for example, the cursor is moved to the display position Ia in the corresponding icon I on the screen H2, and a pop-up is displayed when the mouse is right-clicked. It is also possible to configure such that the item is not used and the Bucky device 51 described in a window (not shown) or the item not using the Bucky device 51 is selected and changed.

  On the other hand, in this embodiment, when changing the FPD cassette 1F set to each of the icons I1 to I4 to the CR cassette 1C (or vice versa), or when changing between the FPD cassettes 1F, For example, by moving the cursor to the display portion Ib in the corresponding icon I on the screen H2 and right-clicking the mouse, for example, a selection screen H3 as shown in FIG. 18 is displayed, and various FPD cassettes 1F are displayed. A change destination FPD cassette 1F can be appropriately selected and changed from each icon group to be represented.

  For example, when changing any of the FPD cassettes 1F set to the icons I1 to I4 to the CR cassette 1C, for example, the same operation is performed to display the selection screen H3 as shown in FIG. For example, it can be changed by clicking an icon displayed as “CR”.

  With this configuration, it is possible to operate even if each cassette device 51 is not provided with CR cassette identification information reading means (that is, for example, the above-described barcode reader). In this case, the radiographer or other radiographer can change the desired radiographing order information from the FPD system to the CR system in the front room Rb in which the console 58 is provided. Conversely, the imaging order information can be changed from the CR method to the FPD method.

  Further, instead of configuring the FPD cassette 1F set to each of the icons I1 to I4 on the selection screen H3 as described above to be changed to the CR cassette 1C, or in combination with it, for example, a selection screen CR cassette identification information reading means (for example, a barcode) provided on the console 58 provided with the desired imaging order information selected on H1 or when the desired icon I is clicked on the screen H2, for example. When the identification information (for example, bar code information) of the CR cassette 1C is input using a reader, the FPD system can be automatically changed to the CR system.

  When the image reading device 61 of the CR cassette 1C is connected to the console 58 at 1: 1, the image data D read from the CR cassette 1C is transmitted to the console 58 every time a reading operation is performed. Therefore, on the selection screen H3, it is possible to perform only the change operation to the CR system and abolish the input of the CR cassette identification information.

  When the number of shots to be changed from the FPD method to the CR method is only one, the above method is particularly preferable because there is no mixing of images taken with the CR cassette 1C. When a plurality of photographings are changed to the CR system, when the plurality of CR cassettes 1C are collectively loaded into the image reading device 61 after completion of all the photographings, the image reading device 61 needs to be careful of the order of photographing. It is necessary to load the cassette 1C.

  When the FPD cassette 1F or the CR cassette 1C used for shooting is changed, the item “cassette ID” P10 in the shooting order information is automatically rewritten to the cassette ID of the changed cassette. .

  In addition, if the FPD cassette 1F is accidentally used during actual shooting even though the FPD method is changed to the CR method on the console 58 in the front room Rb, as described above, Since the console 58 is configured to control the irradiation dose of radiation from the radiation source 52 during the CR method so as to increase the irradiation dose as compared with the FPD method, the dose becomes excessive.

  However, in such a case, the analog film normally cannot be relieved, but in the case of the FPD cassette 1F, it can be assumed that the image can be relieved by image processing. Accordingly, in such a case, the image data D transmitted from the FPD cassette 1F is temporarily stored on the console 58 without being associated with the photographing order information, and the gradation processing conditions and the like are corrected. When it is determined that the diagnosis can be provided, it is preferable that the image data D after the image processing can be associated with the imaging order information. If it cannot be used for diagnosis even after image processing, the re-shooting mode is set.

  Then, the Bucky device 51 to be used is changed as described above, the Bucky device 51 is not used or the Bucky device 51 is used, the FPD cassette 1F to be used is changed, or the FPD cassette 1F is used. Change to CR cassette 1C, the display in the changed icons I1 to I4 switches to the changed content.

  In the case of changing as described above, for example, when a photographer tries to take a picture without using the changed Bucky device 51, FPD cassette 1F, or CR cassette 1C, a warning is given by voice or the like. It is also possible to use an appropriate apparatus, or to take measures as appropriate so that photographing is performed under appropriate conditions.

  Moreover, the gauge G that represents the degree of progress of processing, which is displayed below the icons I1 to I4 in FIG. 17, will be described later.

  Next, under the configuration as described above, how to display the icons I1 to I4 on the display unit 58a of the console 58, and switching of the setting to the FPD method or the CR method for the radiation generator 57 by the console 58. An example of these will be described.

  The console 58 automatically selects one icon I from the icons I1 to I4 corresponding to each shooting order information displayed on the display unit 58a as described above, and selects the selected icon I for another. The icon I is displayed in a different manner. In the following, displaying an icon I in a different form from the other icons I is abbreviated as focusing on the icon I. Further, when the focused icon I is illustrated, the icon I is indicated by hatching.

  As a method of focusing the icon I, for example, when the icon I is basically displayed in a color close to the background color of the screen H2, such as blue or black, and a certain icon I is focused and displayed, Only the icon I can be configured to be displayed in red or yellow. In addition, the focused icon I is displayed in a shape different from that of the other icons I, the focused icon I is blinked, the display position of the focused icon I on the screen H2 is changed, or zooming is performed. It is also possible to configure the display so as to be up.

  When the console 58 automatically selects the icon I, in this embodiment, the icon I is selected and focused according to the following criteria.

[Standard 1]
Imaging is performed without changing the current state of each FPD cassette 1F, the loading state with respect to the Bucky device 51, the activation and arrangement state of each radiation source 52, the position and orientation of the radiation source 52A (see FIG. 1), and the like. The icon I corresponding to the shooting order information for which the shooting conditions that can be taken or the shooting can be performed with the least degree of change is designated is selected and focused.

[Standard 2]
When the FPD cassette 1F is not brought into the shooting room Ra, or when it is impossible to determine which icon I is to be focused according to the above criteria (hereinafter, this state is abbreviated to the default state) The console 58 has the highest order among the icons I that have not yet been photographed among the icons I1 to I4 displayed in a predetermined order such as the registration order on the display unit 58a. The previous icon I (the icon I1 displayed on the left side in the case of FIG. 17) is selected and focused.

[Standard 3]
When a radiographer or other photographer clicks and selects an icon I different from the focused icon I, the icon 58 selected by the photographer is focused and the console 58 automatically selects the original The focus of the icon I is released. That is, the icon I automatically selected by the console 58 is displayed in the same manner as the other icons I by returning to the display of the original state which is not focused.

  In the following description, it is assumed that the icon I is selected and focused according to the above criteria. For example, the icons I1 to I4 displayed on the screen H2 are displayed in the display order, that is, from the top icon I1. It is also possible to configure the focus transition in the order of the icons I1, I2, I3, and I4, and the focus transition method is not limited to the above example.

  For example, as shown in FIG. 17, the console 58 displays the icons I1 to I4 on the screen H2, and, for example, the radiation source 52A is activated and faces the direction of the standing-up imaging device 51A. If so, the icon I2 or the icon I3 is selected according to the above criterion 1. Then, when only the icons I2 and I3 are viewed, the above-mentioned default criterion 2 is applied, so the icon I2 is selected. Therefore, on the screen H2 of the display unit 58a of the console 58, the icon I2 is selected and focused as shown in FIG.

  In the present embodiment, when the console 58 displays the selected icon I (in this case, the icon I2 in FIG. 19) with focus in this manner, the console 58 immediately determines the icon I based on the shooting order information corresponding to the icon I. Each device used for photographing is activated in a predetermined state.

  That is, if the method specified by the selected icon I is the FPD method, the console 58 transmits an FPD method information to the radiation generator 57, and the method specified by the selected icon I is the CR method. If there is, the fact that the CR system is used is transmitted to the radiation generator 57. In this way, the radiation dose from the radiation source 52 of the radiation generator 57 is switched so as to correspond to each of the FPD method and the CR method.

  As described above, in this embodiment, the console 58 determines whether the radiographic image capturing is performed on the radiation generator 57 by the FPD method using the FPD cassette 1F or the CR method using the CR cassette 1C. It functions as switching means for switching and setting.

  And the radiation generator 57 which received the signal from the console 58 adjusts the irradiation dose of the radiation irradiated from the radiation source 52 according to the setting. That is, if the focused icon I on the screen H2 of the console 58 is the icon I2 that designates imaging using the FPD cassette 1F, radiation imaging is performed from the console 58 to the radiation generator 57 by the FPD method. Since the setting is made, the radiation generator 57 controls the radiation source 52A so as to emit a smaller dose than in the CR system.

  In addition, if the icon I focused on the screen H2 of the console 58 is an icon I that specifies shooting using the CR cassette 1C, or the FPD cassette 1F that was originally specified in the icon I (for example, the icon I2). However, when it is changed to the CR cassette 1C as described above, since the setting that the radiographic imaging is performed by the CR method from the console 58 to the radiation generation apparatus 57 is performed, the radiation generation apparatus 57 is configured as the FPD. The radiation source 52A is controlled so as to irradiate a larger dose than in the case of the method.

  The radiation generating device 57 moves the radiation source 52A to a predetermined position to change the irradiation direction if the radiation source 52A is not in a state where it can irradiate the standing-up imaging device 51A. Adjust to.

  In addition, if the power supply mode of the FPD cassette 1F used for the imaging is the sleep mode, the console 58 transmits an awakening signal (also referred to as a wake up signal) to the FPD cassette 1F to shift to the imaging enable mode. Etc. are performed.

  On the other hand, in the present embodiment, the console 58 controls the radiation generation start of the radiation generator 57 based on the setting by the switching means (that is, the setting of the console 58 itself as the switching means in the present embodiment). It also functions as a means.

  In the present embodiment, as described above, the radiation generator 57 is configured to irradiate radiation from the radiation source 52 when receiving the interlock release signal as a response to the transmitted irradiation start signal. However, even if the irradiation start signal is transmitted to the CR cassette 1C, the interlock release signal is not transmitted from the CR cassette 1C.

  Therefore, in the present embodiment, when imaging is performed by the CR method, the console 58 as the exposure control means receives the irradiation start signal transmitted from the radiation generator 57 by the console 58, and from the console 58, the above-described irradiation start signal is transmitted. By transmitting a dummy signal corresponding to the interlock release signal to the radiation generator 57, the radiation source 52 is controlled to allow radiation.

  If comprised in this way, the radiation generator 57 will transmit a dummy signal from the console 58 as an exposure control means, and exposure will be permitted. As described above, when the exposure switch 56 is operated by a radiographer or other photographer and an irradiation start signal is transmitted from the exposure switch 56, the irradiation start signal is transmitted to the console 58, and a dummy signal is transmitted from the console 58. After transmission, the radiation source 52 emits radiation.

  However, since the transmission of the irradiation start signal from the radiation generator 57 to the console 58 and the transmission of the dummy signal from the console 58 are performed instantaneously, for the radiographer, from the radiation source 52 immediately after operating the exposure switch 56. It feels like radiation.

  Therefore, as in the case of normal imaging using the CR cassette 1C, the radiation generation device 57 is larger than the FPD system from the radiation source 52 as soon as the exposure switch 56 is operated by the photographer. Imaging can be performed by irradiating with an irradiation dose of radiation. It is also possible to configure so that radiation is emitted after a preset time after the exposure switch 56 is operated.

  Thus, in this embodiment, the radiation generator 57 receives the signal that radiographic imaging is performed by the CR method using the CR cassette 1C from the console 58 as the switching unit, and uses the CR method. In this situation, exposure is permitted by the console 58 as the exposure control means, so that even in a situation where the CR cassette 1C and the FPD cassette 1F are mixed, Therefore, it is possible to accurately irradiate the CR cassette 1C with radiation, and it is possible to perform photographing appropriately.

  On the other hand, when the console 58 as the exposure control means (that is, the console 58 as the switching means) is set so that the radiographic image shooting is performed using the FPD cassette 1F, Thus, the radiation source 52 is allowed to irradiate radiation depending on not only the irradiation start signal from the exposure switch 56 but also whether the FPD cassette 1F is used in the synchronous method or the asynchronous method. It comes to control.

  That is, as described above, in the present embodiment, the radiation generator 57 is configured to irradiate radiation from the radiation source 52 for the first time when the interlock release signal is received as a response to the transmitted irradiation start signal. . Further, in the present embodiment, as described above, the FPD cassette 1F is a synchronous method when used in the bucky device 51, as described later, and is not loaded in the bucky device 51 and is used alone. When used in a state, each of them is photographed in an asynchronous manner.

  Accordingly, for example, as shown by an icon I2 in FIG. 19, the FPD cassette 1F used in the current photographing is loaded in the Bucky device 51 (for example, the standing-up photographing Bucky device 51A) and photographing can be performed in a synchronous manner. If possible, an irradiation start signal is transmitted from the radiation generator 57 to the console 58, and the console 58 transfers the irradiation start signal to the FPD cassette 1F.

  As described above, instead of configuring the console 58 to transfer the irradiation start signal to the FPD cassette 1 when the irradiation start signal is received from the radiation generating device 57, at that stage, from the console 58. The FPD cassette 1 can be inquired as to whether or not photographing is possible. In the following, there is a case where the inquiry from the console 58 to the FPD cassette 1 is not described, but in the same way, the console 58 sends the FPD cassette 1 to the FPD cassette 1 when the irradiation start signal is received from the radiation generator 57. It can be configured to query.

  As described above, in response to the transfer and inquiry of the irradiation start signal from the console 58, when the ready signal is transmitted from the FPD cassette 1F in which the reset processing of each radiation detection element 7 has been completed to the console 58, An interlock release signal is transmitted from the console 58 to the radiation generator 57. Then, when the radiation generator 57 receives the interlock release signal from the console 58, it can be set to emit radiation from the radiation source 52A.

  Therefore, when the FPD cassette 1F is loaded in the bucky device 51 and the console 58 as the exposure control means performs photographing in a synchronous manner, the FPD cassette 1F is in a state where photographing is possible and a ready signal is output from the FPD cassette 1F. When transmitted, an interlock release signal is transmitted to the radiation generator 57, and control is performed so as to allow the radiation from the radiation source 52 to the FPD cassette 1F.

  On the other hand, for example, as shown by an icon I4 in FIG. 19, when the FPD cassette 1F used in the current photographing is used in a single state without being loaded into the bucky device 51, the FPD cassette 1F is connected to the console 58. And the radiation generator 57 cannot be synchronized (or not synchronized).

  Therefore, in the present embodiment, the console 58 as the exposure control means, when performing imaging in the asynchronous method as in the case where the FPD cassette 1F is used alone, is the same as in the case of the CR method described above. The irradiation start signal transmitted from the radiation generator 57 is received by the console 58, and a dummy signal corresponding to the interlock release signal is transmitted from the console 58 to the radiation generator 57. It is controlled to allow the irradiation.

  With this configuration, the radiation generator 57 is permitted to be exposed by the console 58 as an exposure control means, and the exposure switch 56 is operated by a radiographer or other photographer to start irradiation from the exposure switch 56. When the signal is transmitted, the interlock release signal is transmitted from the console 58 to the ready signal from the FPD cassette 1F in the synchronous system, and the dummy signal is transmitted from the console 58 in the asynchronous system. Therefore, the radiation generator 57 can irradiate the radiation from the radiation source 52 when receiving the interlock release signal or the dummy signal corresponding thereto.

  Therefore, the radiation generator 57 is configured to irradiate radiation from the radiation source 52 for the first time when the interlock release signal is received as a response to the transmitted irradiation start signal as in this embodiment. However, after the exposure switch 56 is operated by the photographer, when the interlock release signal or the dummy signal is transmitted, the radiation source 52 emits radiation having a smaller irradiation dose than in the case of the CR method. Can be taken.

  Thus, in this embodiment, the radiation generator 57 receives the signal that radiographic imaging is performed by the FPD method using the FPD cassette 1F from the console 58 as the switching unit, and uses the FPD method. Recognizing this, the radiation dose is appropriately adjusted, and in this state, the exposure is permitted by the console 58 as the exposure control means.

  When the shooting is performed in a synchronous manner and an interlock release signal is transmitted from the console 58, a dummy signal corresponding to the interlock release signal is transmitted from the console 58 when the shooting is performed in an asynchronous manner. Therefore, shooting can be performed accurately. Therefore, even in a situation where the CR cassette 1C and the FPD cassette 1F are mixed, it is possible to accurately irradiate the CR cassette 1C with radiation, and it is possible to perform imaging appropriately.

  As described above, in the present embodiment, the console 58 is activated in the FPD cassette 1F in the photographing room Ra (that is, the power is turned on or off) or in the power supply mode (that is, capable of photographing). Mode) or the sleep mode, the current activation state and power supply mode of the FPD cassette 1F when the asynchronous shooting is performed using the FPD cassette 1F. There is no need to check.

  However, in order to ensure that imaging is performed, when imaging is performed in an asynchronous manner using the FPD cassette 1F, when the irradiation start signal is transmitted from the radiation generator 57 as described above, The console 58 inquires the FPD cassette 1F used for the imaging about the activation state and the power supply mode. When the FPD cassette 1F is activated and is in the imaging enabled mode, the console 58 outputs a dummy signal to the radiation generator 57. Can also be configured to transmit.

  At this time, for example, when the state of the FPD cassette 1F is in a stopped state, the FPD cassette is notified to a radiographer or other radiographer by uttering a voice or displaying it on the display unit 58a of the console 58. If the FPD cassette 1F is instructed to be activated, or if the power supply mode of the FPD cassette 1F is the sleep mode, an awakening signal is transmitted to the FPD cassette 1F to shift to the photographing enable mode, and at the same time, the FPD cassette 1F However, it is possible to delay the transmission of the dummy signal from the console 58 to the radiation generator 57 while the reset process is performed a predetermined number of times.

  Further, depending on the radiographic imaging system 50, when radiographic imaging is performed in the FPD method and in the synchronous method, for example, first, the reset processing of each radiation detection element 7 is performed on the FPD cassette 1F side, and the reset processing is performed. Upon completion, a ready signal is sent from the FPD cassette 1F to the console 58, and a signal is sent from the console 58 to the radiation generator 57 to allow the operation of the exposure switch 56. In some cases, the switch 56 is operated to emit radiation from the radiation source 52. Even in such a case, the present invention can be applied.

  At this time, when a signal is transmitted from the console 58 to the radiation generator 57, the signal is also transmitted to the console 58, and a display indicating that radiation can be emitted on the display unit 58a of the console 58. It is also possible to configure so that

  In addition, when the cover device 70 is provided in the exposure switch 56 as in a third embodiment to be described later, when the console 58 transmits a signal to the radiation generator 57, the console 58 It is also possible to allow the photographer to operate the exposure switch 56 by opening a cover 71 (see FIGS. 28A and 28B described later) of the cover device 70. .

  When radiographic imaging is performed, as described above, the control means 22 of the FPD cassette 1F reads the image data D from each radiation detection element 7 and stores it in the storage means 23. Further, the control means 22 automatically thins out the image data D at a predetermined ratio based on the image data D read out from the radiation detection elements 7 and automatically creates the thinned data Dt for preview. The thinned data Dt with the cassette ID is transmitted to the console 58 via 41 or the Bucky device 51.

  Further, after transmitting the thinned data Dt to the console 58, the control unit 22 assigns a cassette ID to the image data D that is the basis for creating the thinned data Dt and automatically transmits it to the console 58. Further, the control unit 22 calculates an offset correction value based on the dark reading value read out by the dark reading process performed at a predetermined timing, and assigns a cassette ID to the calculated offset correction value, and automatically controls the console 58. Send to.

  On the other hand, when radiographic imaging is performed using the CR cassette 1C, after imaging, the CR cassette is carried by the photographer or the like to the image reading device 61 outside the imaging room Ra, and processing for reading the image data D is performed. Done. Then, the image data D is transmitted from the image reading device 61 to the console 58 together with the barcode information of the CR cassette 1C.

  In this embodiment, the console 58 is in a stage where the thinned data Dt or the like has been transmitted from the FPD cassette 1F, or in a stage in which the image data D photographed with the CR cassette 1C has been transmitted from the image reading device 61. A preview image is created based on the thinned data Dt and image data D transmitted.

  Then, as shown in FIG. 20, the console 58 displays the created preview image p_pre instead of the icon I2 at the position where the focused icon I2 is displayed on the screen H2 of the display unit 58a. It is supposed to be displayed. Then, an “OK” button and an “NG” button are displayed below the preview image p_pre.

  When the “NG” button is clicked by the photographer who has viewed the preview image p_pre, the console 58 discards the preview image p_pre, the image data D, and the like, and returns to the display of the original focused icon I2. Then, re-photographing is performed.

  When the “OK” button is clicked by the photographer, the console 58 sets the offset correction, gain correction, logarithmic conversion correction, logarithmic conversion correction, part, and imaging condition for the image data D based on the transmitted image data D or the like. Various image processing such as gradation processing is performed, and a final radiographic image p for image processing is generated. At this time, the display of the gauge G below the preview image p_pre is changed according to the progress of the process.

  Then, when the diagnostic radiation image p is generated, the console 58 overwrites and displays the preview image p_pre with the radiation image p as shown in FIG. 21, and displays an “OK” button displayed below the radiation image p. When is clicked, processing such as associating the data of the radiation image p with the imaging order information is performed. When the “NG” button is clicked, necessary image processing can be performed on the radiation image p.

  On the other hand, as shown in FIG. 20, even when the preview image p_pre is displayed on the screen H2, when the “OK” button on the lower side is clicked, the console 58 continues as shown in FIG. Again, the next icon I is selected and focused according to each of the above criteria. And radiographic image photography is performed like the above.

  That is, the console 58 is used according to the type of cassette (that is, FPD cassette 1F or CR cassette 1C) specified by the imaging order information corresponding to the next icon I, or by the photographer's operation (see FIG. 18 and the like). When the type of cassette to be changed is changed, it is determined whether the radiographic imaging is performed by the FPD method or the CR method according to the changed type of the cassette. Further, when shooting is performed by the FPD method, it is determined whether the method is a synchronous method or an asynchronous method.

  And the console 58 performs the process as said switching means and the process as an exposure control means, controls the radiation generator 57, and makes it suitable for the radiation generator 57 from the radiation source 52 according to a system. It is possible to appropriately perform imaging by irradiating with an irradiation dose of radiation.

  As described above, according to the radiographic imaging system 50 according to the present embodiment, is radiographic imaging performed on the radiation generator 57 by the FPD method using the FPD cassette 1F by the console 58 as the switching unit. Since the CR method using the CR cassette 1C is switched and set, the radiation generation device 57 can accurately irradiate the radiation source 52 with the radiation dose suitable for each method.

  Further, the console 58 as the exposure control means controls the start of radiation irradiation to the radiation generator 57 based on the setting by the switching means (that is, based on the above-mentioned setting set by itself as the switching means in this embodiment). To do. That is, in the case where the imaging is set to be performed by the CR method, when an irradiation start signal is transmitted from the radiation generation device 57, a dummy signal is transmitted from the console 58 based on that and immediately. Allow radiation from the radiation source 52 (or after a preset time).

  In addition, when the imaging is set to be performed by the FPD method, the radiation generating device 57 is based on the irradiation start signal from the exposure switch 56 and is either a synchronous method or an asynchronous method. Depending on whether it is used, radiation from the radiation source 52 is permitted.

  That is, when the synchronization is performed, for example, when an irradiation start signal is transmitted from the radiation generator 57 to the console 58, the signal is transferred to the FPD cassette 1F, and the FPD cassette 1F in the imaging ready state is consoled. When a ready signal is transmitted to 58, an interlock release signal is transmitted from the console 58 to the radiation generator 57. In this manner, the radiation source 52 is allowed to irradiate radiation while synchronizing the radiation generator 57 and the FPD cassette 1F via the console 58.

  Further, in the case of being performed in an asynchronous manner, for example, a radiation signal is emitted from the radiation source 52 by transmitting a dummy signal corresponding to the interlock release signal from the console 58 to the radiation generator 57. to approve.

  With this configuration, even when the CR cassette 1C and the FPD cassette 1F are mixed, and the FPD method can be used, it is possible to perform the shooting appropriately in the synchronous method or the asynchronous method. It becomes possible to control so that it can be performed.

  Therefore, even if the FPD cassette 1F or the CR cassette 1C is irradiated with an inappropriate dose of radiation, irradiated with an inappropriate timing, or even if the photographer operates the exposure switch 56, the radiation is irradiated. It is possible to accurately prevent various problems such as not being performed.

  Although the same applies to the second embodiment described below, in this embodiment, as described above, when the radiation generator 57 emits radiation from the radiation source 52, a response to the irradiation start signal transmitted. As described above, it is assumed that the radiation source 52 is configured to emit radiation for the first time when the interlock release signal is received.

  Therefore, when imaging is performed by the CR system, a dummy signal corresponding to the interlock release signal is generated from the console 58 as the exposure control means in response to the irradiation start signal transmitted from the radiation generator 57. It became necessary to transmit to the device 57.

  However, for example, the radiation generator 57 is configured to switch control between the CR method and the FPD method, and when the FPD method is set, the interlock release signal as a response to the irradiation start signal is set as described above. In the CR method, the CR system does not require the interlock release signal as described above, and immediately (or a preset time) when the irradiation start signal is transmitted from the exposure switch 56. It can also be configured to emit radiation).

  The radiation generator 57 can be configured to automatically switch control between the CR method and the FPD method in accordance with the setting switching by the switching means (the console 58 in this embodiment). .

  With this configuration, at least when imaging is performed by the CR method, a dummy signal is transmitted from the console 58 serving as an exposure control unit to the radiation generation device 57 with respect to the irradiation start signal transmitted from the radiation generation device 57. No need to send to

  Further, as described above, in the present embodiment, the case where an irradiation start signal is transmitted from the radiation generator 57 to the console 58 when the exposure switch 56 is operated by the photographer has been described. Depending on the case, the irradiation start signal may be transmitted directly from the radiation generator 57 to the FPD cassette 1F via the relay 54 (that is, not via the console 58).

  In such a case, for example, in the case of the CR system, even if an irradiation start signal is transmitted from the radiation generator 57 to the CR cassette 1C, there is naturally no response from the CR cassette 1C. Therefore, in this case, the irradiation start signal transmitted from the radiation generator 57 is configured to be transmitted from the repeater 54 to the console 58. Alternatively, when the radiation generating device 57 and the console 58 are connected as in the present embodiment, an irradiation start signal is transmitted from the radiation generating device 57 to the console 58 and the repeater 54, so that the repeater The irradiation start signal transmitted to 54 is stopped by the repeater 54.

  Then, as described above, it is possible to transmit a dummy signal from the console 58 to the radiation generator 57 so that the radiation source 52 emits radiation.

  For example, when imaging is performed in a synchronous manner using the FPD cassette 1F, the radiation detection elements 7 are reset from the FPD cassette 1F in response to the irradiation start signal transmitted from the radiation generator 57 to the FPD cassette 1F. Since the interlock release signal is transmitted when the processing is completed and the imaging is ready, the radiation generation device 57 can emit radiation from the radiation source 52 in accordance with the interlock release signal.

  At that time, the FPD cassette 1F may be configured to transmit an interlock release signal to the console 58 via the repeater 54, and the console 58 may be configured to perform appropriate processing accordingly.

  On the other hand, for example, when imaging is performed in an asynchronous manner using the FPD cassette 1F, even if an irradiation start signal is transmitted from the radiation generator 57 to the repeater 54, an irradiation start signal is transmitted from the repeater 54 to the FPD cassette 1F. Not sent.

  Therefore, also in this case, the irradiation start signal transmitted from the radiation generator 57 is transmitted from the repeater 54 to the console 58 as in the case of the CR system. Alternatively, when the radiation generating device 57 and the console 58 are connected as in the present embodiment, an irradiation start signal is transmitted from the radiation generating device 57 to the console 58 and the relay device 54, so that the relay device 54. The irradiation start signal transmitted to is stopped by the repeater 54.

  Then, as described above, the console 58 confirms that the FPD cassette 1F has been activated and is in the imaging enabled mode, and transmits a dummy signal from the console 58 to the radiation generator 57. Alternatively, as described above, the console 58 inquires of the FPD cassette 1F about the activation state and the power supply mode, and when the FPD cassette 1F is activated and is in the radiographable mode, the radiation generation device 57 is output from the console 58. It is possible to transmit a dummy signal.

[Second Embodiment]
In the first embodiment, the case where the console 58 has the functions of both the switching unit and the exposure control unit has been described. That is, the console 58 functions as switching means for switching and setting the radiation generator 57 to at least whether radiographic imaging is performed by the FPD method using the FPD cassette 1F or the CR method using the CR cassette 1C. Explained when to do.

  However, depending on the radiation image capturing system 50, the console 58 may not have such a function as a switching unit, and the switching unit may be configured to be provided separately from the console 58. . In the second embodiment, such a case will be described.

  For example, when a radiographer or other radiographer changes, for example, the FPD cassette 1F loaded in the bucky device 51 to the CR cassette 1C in the imaging room Ra (or vice versa), the console 58 It is necessary to operate the switching means separate from the above and set for the radiation generating apparatus 57 whether the imaging is performed by the FPD method or the CR method. Is convenient because it does not have to be moved to the front room with the console.

  Therefore, it is possible to construct the switching means in, for example, the repeater 54 (see FIG. 1) so that the switching means is provided in the photographing room Ra. With this configuration, the repeater 54 is connected to the radiation generator 57 and the console 58 as described above, so a signal is sent from the switching means to the radiation generator 57 to set the method and change the setting. It becomes possible to do. In addition, by operating the console 58, it is possible to activate the switching unit, or to instruct the switching unit to set or change the setting.

  In the following, assuming that the switching means is built in the repeater 54, the switching means 54 is referred to, but it is not necessary to build the switching means in the repeater 54, and it is not necessarily provided in the photographing room Ra. It does not have to be. When the switching unit is not constructed in the repeater 54 and is provided separately from the repeater 54, the switching unit and the radiation generator 57 are configured to be connected. Further, if the switching unit and the console 58 are configured to be connected, the switching unit is activated, the switching unit is set, or the setting is changed by the operation on the console 58 as described above. It is also possible to give instructions.

  The switching means 54 is provided with input means such as a touch panel and a toggle switch (not shown), and a radiographer or other radiographer manually inputs settings to the switching means 54 or changes the settings. You can enter.

  The switching means 54 is configured to function as shown in FIGS. 23 to 26, for example.

  That is, as shown in FIG. 23, the switching unit 54 determines whether the current photographing is performed by the FPD method or the CR method from the console 58 in which the icon I is focused on the screen H2 (see FIG. 19). Is transmitted to the radiation generator 57, the method designated by the console 58 is set.

  When the photographer manually inputs a method to the switching unit 54, the switching unit 54 sets the input method in the radiation generator 57. Further, as described above, when the system is switched by an operation on the console 58 (see, for example, FIG. 18) or by a photographer's input to the switching unit 54, the system after the switching is changed to radiation. Set to generator 57.

  The radiation generation device 57 adjusts or changes the irradiation dose of the radiation emitted from the radiation source 52 in accordance with the set setting or the setting after switching.

  Then, for example, as shown in FIG. 24, when the photographer performs the first-stage operation (for example, half-press operation) on the exposure switch 56, synchronization is performed from the radiation generator 57 via the switching unit 54. A signal for inquiring whether the photographing can be performed is transmitted to the FPD cassette 1F of the system, or a signal for inquiring to the console 58 is transmitted in the case of the asynchronous system, and the switching means 54 is sent from the synchronous FPD cassette 1F or the console 58. It is also possible to configure the radiation generator 57 to confirm that the entire system is ready for imaging when an OK signal is replied to. In this case, the synchronous FPD cassette 1F returns an OK signal when imaging is possible, for example, by resetting each radiation detection element 7 a preset number of times.

  In the case of the CR method, since it is not necessary to inquire of the console 58 or the CR cassette 1C whether or not imaging is possible, the switching unit 54 receives a signal inquiring whether or not imaging is possible from the radiation generator 57, Alternatively, the OK signal is always returned directly to the radiation generator 57 before the signal is received.

  The radiation generator 57 confirms that the system is ready for imaging when the OK signal is returned via the switching means 54 or from the switching means 54, and the second operation on the exposure switch 56 is performed. (For example, full-press operation) is allowed.

  When the photographer performs the second stage operation and an irradiation start signal is input from the exposure switch 57, the switching unit 54 returns an OK signal to the radiation generator 57 from the exposure switch 56. Since it is permitted to irradiate radiation from the radiation source 52 based on the irradiation start signal, the radiation generator 57 irradiates the radiation from the radiation source 52 immediately (or after a preset time).

  Further, when imaging is performed in the FPD method and in the synchronous method, as described in the first embodiment, the console 58 as the exposure control means causes the radiation generator 57 and the FPD cassette 1F to Control is performed to allow the radiation of radiation from the radiation source 52 to the FPD cassette 1F by allowing transmission and reception of signals (that is, an irradiation start signal, an interlock release signal, etc.) between them.

  Therefore, as shown in FIG. 25, the repeater (switching means) 54 transmits the irradiation start signal transmitted from the radiation generator 57 to the FPD cassette 1F, and the interlock release signal is transmitted from the FPD cassette 1F. When it comes, it is transmitted to the radiation generator 57. Then, radiation is emitted from the radiation source 52.

  Further, when imaging is performed by the FPD method and the asynchronous method, as described in the first embodiment, the repeater (switching means) 54 is connected to the radiation generator 57 as shown in FIG. When an irradiation start signal is transmitted, it is transmitted to the console 58 as an exposure control means, and when a dummy signal corresponding to the interlock release signal is transmitted from the console 58, it is transmitted to the radiation generator 57. Send. Then, radiation is emitted from the radiation source 52.

  As described above, according to the radiographic image capturing system 50 according to the present embodiment, the FPD system that uses the FPD cassette 1F for radiographic image capturing with respect to the radiation generating device 57 by the switching unit 54 separate from the console 58. Or the CR method using the CR cassette 1C is set by switching, so that the radiation generating device 57 can accurately irradiate the radiation source 52 with the radiation dose suitable for each method. It becomes possible. Therefore, it is possible to exhibit the same beneficial effect as in the case of the first embodiment.

  Further, according to the radiographic image capturing system 50 according to the present embodiment, even when the console 58 does not have a function as a switching unit, the same beneficial effects as in the case of the first embodiment are exhibited. It becomes possible to do.

  For example, if the switching means 54 is provided in the photographing room Ra, the type of cassette loaded in the bucky device 51 is changed in the photographing room Ra, that is, for example, when the FPD cassette 1F is changed to the CR cassette 1C ( In the other case, the system can be easily switched by operating the switching means 54 in the photographing room Ra without moving to the console 58 outside the photographing room Ra.

[Third Embodiment]
In the first and second embodiments described above, as described above, the radiation generating device 57 irradiates radiation from the radiation source 52 for the first time when receiving the interlock release signal as a response to the transmitted irradiation start signal. The case where it is configured is described.

  That is, the radiation generator 57 does not immediately irradiate the radiation from the radiation source 52 even if the irradiation switch 56 is operated in the second stage and the irradiation start signal is transmitted from the exposure switch 56. Radiation is emitted from the radiation source 52 for the first time when an interlock release signal is transmitted from the FPD cassette 1F.

  For this reason, in the case of the CR method that does not respond to the interlock release signal even if the irradiation start signal is transmitted from the radiation generation device 57, the irradiation start signal is transmitted from the radiation generation device 57 in the case of the asynchronous method of the FPD method. In this case, it is necessary to transmit a dummy signal corresponding to the interlock release signal from the console 58 as the exposure control means to the radiation generator 57.

  However, the radiation generator 57 does not need to receive an interlock release signal as a response to the irradiation start signal, and immediately (or preset) when the irradiation start signal is transmitted from the exposure switch 56. It may be configured to emit radiation from the radiation source 52 (after time).

  At present, this type of radiation generator is often used in the so-called fixed radiation generator 57 installed in the radiographing room Ra as shown in FIG. 1 or the anterior chamber Rb associated therewith. However, as shown in FIG. 27, for example, a radiation generating apparatus 57 of a type in which a so-called portable radiation generating apparatus 57 is mounted on a round-trip car and brought into a hospital room R3 is currently equipped with such a type of apparatus. Often used. In FIG. 27, B represents a bed in a hospital room Rc, and H represents a patient as a subject.

  In the hospital room Rc, since there is no charging device for the FPD cassette 1F such as the cradle 55 (see FIG. 1), the battery 24 of the FPD cassette 1F brought into the hospital room Rc is insufficient, and the cassette used for imaging is used as the FPD. Switching of the cassette, such as switching from the cassette 1F to the CR cassette 1C, or switching the cassette used for shooting from the CR cassette 1C to the FPD cassette 1F when the number of CR cassettes 1C brought in is insufficient, and shooting is performed in the shooting room Ra. It may occur more frequently than the case.

  In the present embodiment, even when the radiation generator 57 is provided in the radiographing room Ra or the front chamber Rb (see FIG. 1), or the portable radiation generator 57 is mounted on the round-trip car and brought into the hospital room R3. In such a case (see FIG. 27), the present invention is effectively applied in any case.

  By the way, as described above, the radiation generating device 57 does not need to receive the interlock release signal as a response to the irradiation start signal, and immediately when the irradiation start signal is transmitted from the exposure switch 56 ( Alternatively, when the radiation source 52 is configured to emit radiation (after a preset time), the following problems may occur particularly in the case of the FPD method.

  That is, when the FPD cassette 1F is used in a synchronous manner, the radiation source 52 is originally only when the interlock release signal is transmitted from the FPD cassette 1F in response to the irradiation start signal transmitted from the radiation generator 57. In the case where the radiation generator 57 does not require the response of the interlock release signal as described above, the FPD cassette 1F performs the reset process of each radiation detection element 7 (see FIG. 9 and FIG. 32). In the middle of performing, there may be a problem that radiation is emitted even though the imaging is not yet possible.

  The same applies when the FPD cassette 1F is used in a synchronous manner or in an asynchronous manner. However, the power supply mode of the FPD cassette 1F used for photographing is the sleep mode, and the photographing is not ready. Regardless, there may be a problem that radiation is emitted.

  Therefore, as in the present embodiment, the radiation generator 57 does not need to receive the interlock release signal as a response to the irradiation start signal, and immediately when the irradiation start signal is transmitted from the exposure switch 56. (Or after a preset time), the radiation source 52 emits radiation, as described above, at least after the FPD cassette 1F is ready for imaging, the radiation source 52 It is necessary to be configured to be irradiated with radiation.

  Therefore, in the present embodiment, when the radiation generating device 57 is configured as described above, it is not possible to perform imaging because the FPD cassette 1F is not ready for imaging. In such a case, an erroneous exposure prevention means for preventing the exposure switch 56 from being operated is provided.

  As the erroneous exposure prevention means, for example, as shown in FIGS. 28A and 28B, a cover device 70 attached to the exposure switch can be used. The console 58 as the exposure control means controls the opening and closing of the cover device 70.

  The cover device 70 is disposed, for example, above the exposure switch 56, and is closed with a lid 71 that opens the cover device 70 when opened and closes the cover device 70 when closed. And a support plate 72 that supports the lid portion 71 in a state from the lower side.

  In the present embodiment, the support plate 72 is composed of a total of two plate-like members standing in parallel one by one on both sides of the exposure switch 56 in the state of being housed in the holder H. A lid 71 is swingably attached to the support plate 72 via a hinge structure 73 provided on one end of the upper portion of the plate 72.

  As described above, in this embodiment, a radiographer or other photographer can visually recognize the exposure switch 56 accommodated in the holder H from between the two support plates 72. Even if the user puts his hand between the support plates 72 and tries to take out the exposure switch 56 from the holder H, the exposure switch 56 cannot be taken out from the holder H because of being obstructed by the closed lid 71. ing.

  In other words, the positional relationship between the upper end of the exposure switch 56 and the closed lid 71 is that the photographer puts his hand between the two support plates 72 as described above. Even if the shooting switch 56 is to be removed from the holder H, the closed lid 71 is arranged at a position where the exposure switch 56 cannot be removed from the holder H by being blocked by the closed lid 71. Adjusted to

  Note that the exposure switch 56 can be removed from the holder H if the lid 71 is in the open state (see the one-dot chain line in FIG. 28A). Further, instead of providing only the above two support plates 72 of the cover device 70, three support plates 72 are provided so as to surround the exposure switch 56 from three directions, or four support plates 72 are provided to provide four sides of the exposure switch 56. It is also possible to configure so as to surround, and is configured appropriately.

  Further, as described above, when the exposure switch 56 is configured to operate the holder H by rotating or horizontally moving the holder H, the support plate 72 of the cover device 70 is moved to the above-described 2. When only a single sheet is provided, even when the lid 71 is closed, the photographer puts his hand between the support plates 72 to rotate or horizontally move the holder H to operate the exposure switch 56. When the exposure switch 56 is configured in this way, three support plates 72 are provided to surround the exposure switch 56 from three directions, or four are provided. It is necessary to configure so as to surround the four sides of the exposure switch 56 so that the exposure switch 56 cannot be operated when the lid 71 is closed.

  On the other hand, a motor 74 is attached to the outer side of the one end side of the support plate 72, and the rotating shaft 75 of the motor 74 holds the two support plates 72 substantially vertically below the hinge structure 73. It arrange | positions so that it may penetrate. The motor 74 is electrically connected to the console 58 via, for example, a USB (Universal Serial Bus) cable C, and power (for example, 5 [V] or 24 [V]) is supplied from the console 58 to the motor 74. Supply or power supply is stopped.

  Further, a gear 76 is fixed at a predetermined position inside the two support plates 72 of the rotating shaft 75 of the motor 74, and at the end of the lid portion 71 where the hinge structure 73 is formed. A gear 77 that meshes with the gear 76 is fixed at a position corresponding to the gear 76 provided on the rotating shaft 75 of the motor 74.

  Then, when electric power is supplied from the console 58 and the rotating shaft 75 of the motor 74 rotates, the rotational driving force is transmitted from the gear 76 fixed to the rotating shaft 75 to the gear 77 fixed to the lid portion 71. The lid 71 swings around the hinge structure 73 so that the lid 71 is opened or closed.

  In addition, a sensor 78 that detects that the lid 71 has been closed by contact when the lid 71 is closed is provided at the upper end portion of the support plate 72, and the sensor 78 is electrically connected to the console 58. Connected. When the console 58 closes the lid 71, the console 58 receives a signal indicating that the lid 71 is closed, which is transmitted from the sensor 78, so that the lid 71 of the cover device 70 is reliably closed. It has come to confirm that.

  In FIG. 28A, the display of electrical connection between the sensor 78 and the console 58 is omitted. FIGS. 28A and 28B show the case where the sensor 78 is provided only on one of the two support plates 72, but it is configured to be provided on both support plates 72. It is also possible.

  Further, as a method for confirming that the lid 71 has been opened and closed, instead of providing the sensor 78 or in combination with it, for example, as shown in FIG. 29, for example, a light emitting element 79a and a light receiving element 79b are provided. The optical detection means 79 provided is provided in the vicinity of the cover device 70, and when the lid 71 is opened, the light emitted from the light emitting element 79a is reflected by the opened lid 71 and reaches the light receiving element 79b. By doing so, it is also possible to configure to detect opening and closing of the cover device 70.

  Further, as shown in FIGS. 30A and 30B, a tumbler spring T is provided on a portion of the hinge structure 73 of the cover device 70 to urge the lid 71 into a closed state. However, it may be configured to be biased so as to be in an open state when it is opened beyond a predetermined position.

  If comprised in this way, even if the supply of the electric power with respect to the motor 74 from the console 58 is stopped in the state where the lid portion 71 is closed or opened, those states are maintained by the tumbler spring T. Therefore, power consumption can be reduced.

  Furthermore, instead of configuring the cover 71 of the cover device 70 to be swingably attached to the support plate 72 via the hinge structure 73 as described above, for example, as schematically shown in FIG. The rack and pinion structure is a combination of a rack 71 a provided on the lower surface side of the lid portion 71 and a gear (in this case, also referred to as a pinion) 76 fixed to the rotating shaft 75 of the motor 74. It is also possible to configure so that the lid 71 is opened and closed by moving the 71 on the support plate 72 in the horizontal direction.

  On the other hand, the console 58 as the exposure control means controls the cover device 70 as the erroneous exposure prevention means as follows.

[Control 1]
The console 58 controls the cover device 70 to be normally open when radiographic imaging is performed by the CR method using the CR cassette 1C. This is because the CR system does not require an interlock release signal response or the like, and radiation may be emitted from the radiation source 52 at any time when it is ready.

[Control 2]
Further, the console 58 controls the cover device 70 to be closed in a normal state when radiographic imaging is performed by the FPD method using the FPD cassette 1F.

  If the power supply mode of the FPD cassette 1F used for photographing is the sleep mode, a wake-up signal is transmitted to the FPD cassette 1F, and the power supply mode of the FPD cassette 1F is shifted to the photographing enable mode. In addition, when the power supply of FPD cassette 1F used for imaging | photography is turned off, you may comprise so that a warning may be emitted by an audio | voice etc.

[Control 2-1]
The console 58 is an FPD system that uses the FPD cassette 1F for radiographic imaging. When the console 58 is performed in an asynchronous system, the console 58 switches the power supply mode of the FPD cassette 1F to the imaging enable mode (or the FPD). At the time when it is confirmed that the power supply mode of the cassette 1F is the photographing enabled mode), the cover unit 71 is opened and the cover device 70 is opened.

  This is because, in the asynchronous method of the FPD method, the FPD cassette 1F itself detects the start of radiation irradiation, so that radiation can be emitted from the radiation source 52 at any time when it is ready.

  When the power supply mode of the FPD cassette 1F is changed to the imaging enable mode, the cover device 70 is opened after allowing the FPD cassette 1F to reset each radiation detection element 7 for a predetermined time. You may comprise so that it may be in a state. Further, as described above, the FPD cassette 1F continues the reset process of each radiation detection element 7 until the start of radiation irradiation.

  After the exposure switch 56 is operated by the photographer to irradiate the radiation and photographing is performed, when the thinned data Dt and the image data D are transmitted from the FPD cassette 1F, the console 58 The cover device 70 is controlled to be in a closed state.

[Control 2-2]
Further, when radiographic imaging is an FPD method using the FPD cassette 1F and is performed in a synchronous manner, the FPD cassette 1F needs to receive an irradiation start signal and transmit an interlock release signal. On the other hand, if the time from when the FPD cassette 1F transmits the interlock release signal to when the radiation is irradiated becomes longer, the amount of dark charge accumulated in each radiation detection element 7 of the FPD cassette 1F increases. .

  Therefore, when the radiographic image capturing is an FPD method using the FPD cassette 1F and is performed in a synchronous manner, the console 58 changes the power supply mode of the FPD cassette 1F to the image capturing possible mode as described above. Thereafter, when the photographer performs an operation for starting imaging on the console 58, an irradiation start signal is sent from the console 58 to the FPD cassette 1F that is performing the reset processing of each radiation detection element 7. Send. Then, when the interlock release signal is received from the FPD cassette 1F, control is performed to open the cover 71 and open the cover device 70.

  After the exposure switch 56 is operated by the photographer to irradiate the radiation and photographing is performed, when the thinned data Dt and the image data D are transmitted from the FPD cassette 1F, the console 58 The cover device 70 is controlled to be in a closed state.

  On the other hand, although not shown, the exposure switch 56 is erroneously operated as an erroneous exposure prevention means instead of the cover device 70 that physically blocks or permits the operation on the exposure switch 56 as described above. It is also possible to provide the radiation generating device 57 with a visual display device for preventing this.

  As the display device, for example, a lamp made of LED or the like, or a display made of CRT, LCD or the like can be provided in the exposure switch 56 or in the vicinity thereof.

  And also when using a display apparatus as an erroneous exposure prevention means, it can be comprised so that it may control similarly to the above. That is, in each of the above controls, instead of opening the cover device 70, a display indicating that the exposure is allowed on the display device (that is, turning on the lamp or displaying that fact on the display) Instead of the cover device 70 being in the closed state, the display device is configured to display that the exposure is not permitted (that is, the lamp is turned off or the display is informed).

  In the present embodiment, when imaging is performed by the CR method or the FPD method, the radiation generator 57 is set in advance from the console 58 as a switching unit, and the radiation generator 57 is set according to the setting. As described in the first embodiment, the control of adjusting the irradiation dose of the radiation irradiated from the radiation source 52 is performed.

  As described above, according to the radiation imaging system 50 according to the present embodiment, the radiation generator 57 immediately (or after a preset time) when the irradiation start signal is transmitted from the exposure switch 56. ) Even when the radiation source 52 is configured to irradiate the radiation, the radiation generator 57 is provided with the erroneous exposure prevention means (the cover device 70 and the display device), so that the CR method is used by the erroneous exposure prevention means. In the FPD method, the operation on the exposure switch 56 is allowed only when the FPD cassette 1F is ready for photographing.

  Therefore, it is possible to accurately prevent the exposure switch 56 from being operated when photographing cannot be performed, and it is possible to exhibit the same beneficial effects as in the case of the first embodiment. . Therefore, even in a situation where the CR cassette 1C and the FPD cassette 1F are mixed, and shooting can be performed in the synchronous method or the asynchronous method when shooting in the FPD method, it is possible to perform shooting appropriately. It becomes possible to control to.

  The FPD cassette 1F and the CR cassette 1C are irradiated with an inappropriate dose of radiation, irradiated with an inappropriate timing, or even if the photographer operates the exposure switch 56. It is possible to accurately prevent various problems such as not being performed.

  In each of the above embodiments, the radiation generator 57 can irradiate the radiation at an arbitrary timing by operating the exposure switch 56 in the default state where nothing is set from the switching unit. It is desirable to be set to. With this configuration, for example, the interlock release signal is not transmitted from the console 58 or the like to the radiation generation device 57, and therefore the radiation source 57 cannot irradiate the radiation from the radiation source 52 no matter how long. Can be prevented from occurring.

  In each of the above-described embodiments, the case where the console 58 that generates the radiation image p based on the image data D or the like is configured to function as at least the exposure control unit. It is also possible to configure with a computer separate from the console 58. That is, the exposure control means can be configured not to have a function of generating the radiation image p.

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

1C CR cassette 1F FPD cassette 7 Radiation detection element 50 Radiation imaging system 52 Radiation source 54 Repeater (switching means)
56 Exposure switch 57 Radiation generator 58 Console (switching means, exposure control means)
70 Cover device (means to prevent accidental exposure)
D Image data p Radiation image Ra Shooting room

Claims (11)

An FPD cassette that includes a plurality of radiation detection elements arranged in a two-dimensional shape, and that reads out the charges generated in each of the radiation detection elements by irradiation with radiation as image data;
A CR cassette containing a stimulable phosphor plate and storing the energy of the emitted radiation in the stimulable phosphor plate;
A radiation generator comprising: a radiation source for irradiating the FPD cassette or the CR cassette; and an exposure switch for instructing the radiation source to start radiation irradiation;
A console that generates a radiation image based on image data read from the FPD cassette or the CR cassette;
A switching unit configured to switch and set whether radiographic imaging is performed using the FPD cassette or the CR cassette for the radiation generating device;
Based on the setting by the switching means, an exposure control means for controlling the start of radiation irradiation to the radiation generating device;
With
The radiation generator adjusts the radiation dose of radiation irradiated from the radiation source according to the setting of the switching means,
The exposure control means includes
When the switching unit is set to perform radiographic imaging using the CR cassette, based on an irradiation start signal that instructs the radiation generator to start irradiation from the exposure switch. Control to allow radiation from the radiation source
When it is set by the switching means that radiographic imaging is performed using the FPD cassette, the FPD cassette is based on the irradiation start signal from the exposure switch and the radiation generating apparatus A radiographic imaging system that controls to allow irradiation of radiation from the radiation source, depending on which of a synchronization method that synchronizes with and an asynchronous method that does not synchronize.   2. The radiographic imaging according to claim 1, wherein the console is electrically connected to the radiation generator and is configured to function as the switching unit and the exposure control unit. system. The console is electrically connected to the radiation generator, and is configured to function as the exposure control means.
The radiographic image capturing system according to claim 1, wherein the switching unit is provided separately from the console. At least the FPD cassette, the CR cassette, the radiation source of the radiation generator, and the switching means are provided in the imaging room,
The radiographic imaging system according to claim 3, wherein at least the exposure switch of the radiation generating device and the console are provided outside the imaging room. The radiation generator is configured to irradiate radiation from the radiation source when receiving an interlock release signal as a response to the transmitted irradiation start signal when irradiating radiation from the radiation source,
The console as the exposure control means is configured to respond to the irradiation start signal transmitted from the radiation generator when the switching means is set so that radiographic imaging is performed using the CR cassette. 3. A control for permitting irradiation of radiation from the radiation source by transmitting a dummy signal corresponding to the interlock release signal from the console to the radiation generator. The radiographic imaging system as described in any one of Claims 1-4. The radiation generator is configured to irradiate radiation from the radiation source when receiving an interlock release signal as a response to the transmitted irradiation start signal when irradiating radiation from the radiation source,
The console as the exposure control means is
When the FPD cassette is used in the synchronous method, when the irradiation start signal is transmitted from the radiation generation apparatus, the FPD cassette is inquired as to whether or not the FPD cassette is ready for imaging, and imaging is performed from the FPD cassette. When receiving a signal indicating that it is in a possible state, by transmitting the interlock release signal to the radiation generator, control to allow radiation from the radiation source,
When the FPD cassette is used in the asynchronous system, a dummy signal corresponding to the interlock release signal is transmitted from the console to the radiation generation apparatus in response to the irradiation start signal transmitted from the radiation generation apparatus. Then, the radiation image capturing system according to any one of claims 2 to 5 is controlled so as to allow irradiation of radiation from the radiation source. The radiation generator is configured to irradiate radiation from the radiation source when receiving an interlock release signal as a response to the transmitted irradiation start signal when irradiating radiation from the radiation source,
The console as the exposure control means is
When the FPD cassette is used in the synchronous method, when the irradiation start signal is transmitted from the radiation generator, the irradiation start signal is transferred to the FPD cassette, and imaging can be performed from the FPD cassette. When receiving a signal indicating the state, control is performed to allow radiation from the radiation source by transmitting the interlock release signal to the radiation generator,
When the FPD cassette is used in the asynchronous system, a dummy signal corresponding to the interlock release signal is transmitted from the console to the radiation generation apparatus in response to the irradiation start signal transmitted from the radiation generation apparatus. Then, the radiation image capturing system according to any one of claims 2 to 5 is controlled so as to allow irradiation of radiation from the radiation source. The radiation generator is configured to irradiate radiation from the radiation source when the radiation start signal is transmitted from the exposure switch when irradiating radiation from the radiation source,
5. The apparatus according to claim 1, wherein the radiation generating device is provided with an erroneous exposure prevention means for preventing the exposure switch from being operated when imaging cannot be performed. The radiographic imaging system as described in any one of Claims 1-3. The erroneous exposure prevention means is a cover device attached to the exposure switch,
The cover device is configured to allow an operation on the exposure switch in an open state and to prevent an operation on the exposure switch in a closed state;
The exposure control means includes
When radiographic imaging is performed using the CR cassette, the cover device is always open,
When radiographic imaging is performed using the FPD cassette, the cover device is opened when the FPD cassette is ready for imaging, and otherwise the cover device is closed. The radiographic imaging system according to claim 8, wherein the radiographic imaging system is controlled so as to do The erroneous exposure prevention means is a display device provided near the exposure switch or the exposure switch,
The display device displays that the exposure is permitted when the operation on the exposure switch is allowed, and the display device indicates that the exposure is not allowed when the operation on the exposure switch is not allowed. Configured to display,
The exposure control means includes
When radiographic imaging is performed using the CR cassette, the display device is displayed to indicate that continuous exposure is permitted,
When radiographic imaging is performed using the FPD cassette, when the FPD cassette is ready for imaging, the display device is displayed to indicate that exposure is permitted, and otherwise 9. The radiographic image capturing system according to claim 8, wherein control is performed to cause the display device to display an indication that exposure is not permitted.   11. The radiation generator according to claim 1, wherein the radiation generator is set so that radiation can be emitted at an arbitrary timing in a default state where the setting from the switching unit is not performed. The radiographic imaging system according to one item.

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