JP2006025828A - Method, system and program for taking radiation image - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a method, a system, and a program for taking radiation images, capable of accurately matching a subject to a radiation image detector even if there are a number of patients as subjects of the radiography. <P>SOLUTION: The method for taking radiation images comprises a step for detecting a radiation image of a subject by a radiation image detector, receiving the radiation image information from the radiation image detector by a control device and receiving a plurality of subject information from outside, a step for matching the plurality of subject information to radiation image detectors before taking radiation images, a step for storing the information on the matching, a step for selecting a radiation image detector matching a subject selected from a plurality of subjects based on the stored information on the matching, a step for transmitting a matching signal to the selected radiation image detector, a step for indicating that the radiation image detector which receives the matching signal matches the subject, and a step for generating a radiation image by the radiation image detector after taking the radiation images, and matching the generated radiation image to the subject information. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to a radiographic image capturing method, a radiographic image capturing system, and a radiographic image capturing program for detecting a radiographic image obtained by radiography with a radiographic image detector.

  Conventionally, a radiation image corresponding to the transmitted dose of a subject is obtained by irradiating a subject such as a human body with radiation from a radiation source such as X-rays or γ-rays for medical examinations. For example, imaging in which image information is obtained as electrical information by converting the wavelength into a photosensitive wavelength region of the light receiving unit with a wavelength converter such as a fluorescent plate according to the transmitted dose of the subject, and converting this into an electrical signal by the light receiving element. The apparatus is known (see Patent Document 1 below). When such an imaging apparatus is configured in a flat panel shape similar to a radiographic imaging cassette, it is also referred to as an FPD (flat panel detector) as a kind of radiographic image detector.

The radiation image information generated by the above-described FPD or the like is transferred to the control device and subjected to image processing or the like. In hospital facilities and inspection facilities, etc., registration of patients is usually performed with a control device in the radiographing room as in Patent Document 2 below. However, when many patients come at once, it takes time and effort to handle the patients. There is a possibility that it is mistaken for which FPD or the like to perform radiography of a patient, and there is a possibility that the radiographic image taken will be mistaken for the patient.
Japanese Patent Application Laid-Open No. 11-34595 JP 2000-245719 A

  In view of the above-described problems of the prior art, the present invention provides a radiographic image capable of accurately associating a subject such as a patient with a radiographic image detector even when there are a large number of radiographic subjects. An object is to provide an imaging method, a radiographic imaging system, and a radiographic imaging program.

  A radiographic imaging method according to the present invention is a radiographic imaging method in which a radiographic image obtained by radiographic imaging of a subject is detected by a radiographic image detector, and radiological image information is received from the radiographic image detector by a control device. A step of receiving subject information from the outside; a step of associating the plurality of subject information with a radiographic image detector before radiographic imaging; a step of storing the association information; and a plurality of subjects Selecting the radiation image detector corresponding to the subject based on the stored correspondence information; sending a correspondence signal to the selected radiation image detector; and radiation receiving the correspondence signal A step of displaying that the image detector is compatible, and the radiological image detector Form, characterized in that it comprises the steps of associating the generated radiation image to the object information.

  According to this radiographic image capturing method, a plurality of externally received subject information and a radiographic image detector are associated with each other before radiographic imaging, and the radiographic image detector corresponding to the subject based on the stored association information When a large number of subjects such as patients to be radiographed are displayed, a corresponding signal is sent to the selected radiographic image detector and a message indicating that the radiographic image detector receiving the corresponding signal is compatible is displayed. However, a subject such as a patient can be accurately associated with a radiological image detector, and the generated radiographic image can be accurately associated with subject information.

  In the radiographic image capturing method, it is preferable that the associating step is performed by automatically selecting a radiographic image detector based on at least one of the subject information and the radiographic information.

  The transmission source of the plurality of subject information may be at least one of an examination room, a reception, and a photographing room.

  In addition, when the radiographic image detector is a cassette type, there are a large number of subjects such as patients, and even when there are a large number of radiographic image detectors, the radiographic target subject and the radiographic image detector are accurately identified. Since they can be associated with each other, there is no possibility that the radiological image detector that performs radiographic imaging of the target subject will be mistaken.

  A radiographic imaging system according to the present invention is capable of connecting to a plurality of radiographic image detectors for detecting radiographic images obtained by radiography of a subject and the radiographic image detectors, and receiving radiographic image information from the radiographic image detectors. And a control unit that receives a plurality of subject information from the outside, and a corresponding unit that associates each of the received subject information with any of the plurality of radiation image detectors. Means for storing the association information; means for selecting the radiation image detector corresponding to a subject selected from a plurality of subjects based on the stored association information; and the selected radiation Means for sending a correspondence signal to the image detector; and means for associating the radiation image generated by the radiation image detector with the corresponding subject information Wherein the radiation image detector is characterized in that it comprises a notifying means for notifying that the said control device is a radiation image detector corresponding receiving said corresponding signal.

  According to this radiographic imaging system, a plurality of externally received subject information and radiographic image detectors are associated with each other before radiographic imaging, and the radiographic image detector corresponding to the subject based on the stored association information And a corresponding signal is sent to the selected radiographic image detector, and the radiographic image detector is notified by the notification means that it is a corresponding radiographic image detector. Even when there are a large number of subjects such as patients, the subject such as patients and the radiographic image detector can be accurately associated, and the generated radiographic image can be accurately associated with the subject information.

  In the radiographic imaging system, the notification means is at least one of a display unit that can display the subject information, a lighting unit that lights and blinks, and a sound generation unit that utters a subject name and sound. preferable.

  Moreover, it is preferable that the said response | compatibility means respond | corresponds by selecting a radiographic image detector automatically based on at least one of object information and imaging | photography information.

  The transmission source of the plurality of subject information can be configured to be at least one of an examination room, a reception, and a photographing room. When there are many subjects in the examination room / reception / photographing room, etc., it is possible to accurately associate the many subjects with the radiation image detector.

  Further, when the radiographic image detector is a cassette type, even if there are a large number of cassette type radiographic image detectors, it is possible to accurately associate a large number of subjects to be radiographed with the radiographic image detector. Therefore, there is no possibility that the radiological image detector that performs radiography of the target subject is mistaken.

  A program according to the present invention is a program for a computer included in a control device that detects a radiographic image of a subject by radiography with a radiographic image detector and receives radiographic image information from the radiographic image detector, and includes a plurality of subjects. A step of receiving information from the outside; a step of associating the plurality of subject information with a radiation image detector before radiographic imaging; a step of storing the correspondence information; and a subject selected from the plurality of subjects Selecting the radiological image detector corresponding to the basis of the stored correspondence information, sending a correspondence signal to the selected radiographic image detector, and the radiographic image that has received the correspondence signal A step of displaying that the detector is compatible, and releasing the radiation image after the radiation image is captured. Generate the line image, a radiographic image capturing program for executing the steps of associating the generated radiation image to the subject information, to the computer.

  According to this radiographic imaging program, a plurality of externally received subject information and radiographic image detectors are associated before radiographic imaging, and radiographic image detection corresponding to the subject is performed based on the stored association information Since a corresponding signal is sent to the selected radiographic image detector and the radiographic image detector that has received the corresponding signal indicates that it corresponds, there are many subjects such as patients to be radiographed. Even in this case, a subject such as a patient can be accurately associated with the radiation image detector, and the generated radiation image can be accurately associated with subject information.

  In the radiographic image capturing program, it is preferable that the associating step is executed by automatically selecting a radiographic image detector based on at least one of the subject information and the imaging information.

  The transmission source of the plurality of subject information may be at least one of an examination room, a reception, and a photographing room.

  According to the radiographic image capturing method, radiographic image capturing system, and radiographic image capturing program of the present invention, it is possible to accurately associate a subject with a radiographic image detector even when there are a large number of subjects to be radiographed. It becomes possible.

  The best mode for carrying out the present invention will be described below with reference to the drawings. FIG. 1 is a schematic diagram for explaining a state in which a radiographic image detector that performs radiographic imaging is selected by a control device in the radiographic imaging system according to the present embodiment. FIG. 5 is a diagram schematically showing a radiographic imaging system that performs radiography with the radiographic detector selected in FIG. FIG. 6 is a block diagram schematically showing the radiographic image capturing system of FIG.

  As shown in FIG. 1, the radiographic imaging system according to the present embodiment includes a control device 1 composed of a personal computer (personal computer) for performing various controls related to radiographic imaging and radiographic images, and performs radiation irradiation on a patient. A plurality of FPDs (Flat Panel Detectors) 5a, 5b, 5c, 5d, 5e, and 5f are prepared as the flat panel radiation image detector 5 in the radiographing room.

  The control device 1 includes a display unit 2 that displays various information and images on a screen 3 including a liquid crystal display and a CRT, a PC communication unit 4 that wirelessly communicates with an external FPD, a pointing device such as a mouse and a keyboard And other input devices (not shown). Each of the FPDs 5a to 5f includes a detector communication unit 35 (see FIG. 3) capable of wireless communication with the PC communication unit 4 of the control device 1, a display unit 33 capable of displaying various information on the outer surface, and the control device 1. And a lighting unit 33a that is turned on when a wireless signal is received from the PC communication unit 4 of the computer. As shown by the broken line in FIG. 1, the control device 1 is installed outside the imaging room, and the PC communication unit 4 is installed in the imaging room.

  When the control device 1 in FIG. 1 receives the radiographic imaging reservation information from the examination room or reception, the control device 1 assigns an FPD to be used for the reserved patient before the patient comes to the imaging room, for example, Corresponding information between a plurality of patients and the FPD collation numbers (FPD001, FPD002, FPD003,...) Assigned to each patient as shown in the screen 3 in FIG. When a patient is selected again by the control device 1, the FPD selected corresponding to the patient is notified, and the patient name is displayed on the display unit 33 of the FPD, or the lighting unit 33a is turned on. .

  When the patient comes to the radiographing room and is identified as the person, for example, when selecting the patient (Yamao) as shown in screen 3 in FIG. 1, the FPD001 assigned and associated as described above (to FPD5a in FIG. 1) In response, a corresponding signal is transmitted from the PC communication unit 4 to the FPD 5a as a wireless signal n. The FPD 5a that has received the response signal displays the patient name on the display unit 33, and the lighting unit 33a is lit or blinks. As described above, when the patient and the FPD are selected and associated, the patient name is displayed on the display unit 33 of the FPD to be used, and the lighting unit 33a is lit or blinked. For this reason, the radiologist can easily select the FPD 5a to be used for the patient who performs radiography from a large number of FPDs by turning on and blinking the lighting unit 33a, and the FPD 5a can be selected by the patient name displayed on the display unit 33. It can be easily confirmed that it is for radiography, and preparations for radiography can be made.

  The confirmation and input of the patient name of the radiologist is performed by, for example, reading patient information from a wireless IC tag provided on the patient's ID card, medical chart, bracelet, or the like by the wireless IC tag reading unit 1a indicated by a broken line in FIG. As shown in FIG. 1, the patient name and the selected FPD reference number corresponding to the patient name may be automatically displayed on the screen 3 as shown in FIG. 1. In addition to the wireless IC tag, any device capable of recognizing the patient can be used, and may be configured to read from an ID card or a barcode attached to a medical record.

  The radiographic imaging system of FIG. 5 is arranged so that the FPD 5a of FIG. 1 is sandwiched between the patient P and the bed 110 as a radiographic subject in a lying position on the bed 110 as the radiographic image detector 5, and the patient P Is irradiated with radiation (X-rays) 100 from the radiation source 101 controlled by the radiation generation control device 102, and transmitted radiation that has passed through the imaging target region of the patient P is detected by the FPD 5a between the bed 110 and the patient P. It has become so.

  The radiation source 101 is generally a fixed anode or a rotary anode X-ray tube, and the X-ray tube has an anode load voltage of, for example, 20 kV to 150 kV when medical.

  As shown in FIGS. 5 and 6, the radiation image detector 5 (FPDs 5 a to 5 e) generates radiation image data based on the detection result of the transmitted radiation, stores the radiation image data in the memory unit 31, and generates the generated radiation image. Data is wirelessly transferred from the detector communication unit 35 to the destination control device 1 as a data wireless signal m.

  As shown in FIG. 5, the control device 1 is configured to display an image on a film, an image display device 51 including a liquid crystal display, a CRT, and the like, a database server 52 that stores and manages image data, for example, via a hospital network 50. The printer 53 and the HIS (hospital information system) / RIS (radiation department information system) 54 that are converted into an image and output, and a host controller 55 that controls the plurality of controllers 1 for overall management are connected. As for the patient who performs radiography, the reservation information is registered in the HIS / RIS 54 together with the patient information, and the control apparatus 1 can receive the registered patient information / reservation information.

  Further, as shown in FIGS. 5 and 6, the control device 1 receives the data radio signal m of the radiation image data from the radiation image detector 5 by the PC communication unit 4, and displays the radiation image on the screen 3 of the display unit 2. The image processing unit 7 performs image processing such as predetermined frequency processing and gradation processing, stores the radiographic image data after the image processing in the memory unit 9, and outputs the image of the examination room from the output unit 8. The data is output to the display device 51, the database server 52, the printer 53, and the like.

  As shown in FIGS. 5 and 6, the control device 1 can transmit a radio signal n such as patient information from the PC communication unit 4 to the detector communication unit 35 of the radiation image detector 5, and the received radiation image detector 5. Then, the patient name can be displayed on the display unit 33.

  As described above, in the radiographic imaging system of FIG. 1, radiographic imaging is performed based on the registered patient information / reservation information received from the HIS / RIS 54, and the radiographic image of the patient P is detected by the radiographic imaging. It can be detected and generated by the device 5 and transferred to the control device 1, and image processing can be performed by the control device 1 so that it can be diagnosed and output or stored. It is also possible to transfer a radiographic image detected and generated by the radiographic image detector 5 to the host control device 55, perform image processing on the host control device 55, output it in a diagnoseable state, and store it.

  1 and 5 uses radio waves for wireless communication between the detector communication unit 35 and the PC communication unit 4, but the present invention is not limited to this, and infrared communication or optical communication may be used. .

  Next, the radiation image detector 5 shown in FIG. 1 will be described with reference to FIGS. FIG. 2 is a perspective view of the radiation image detector of FIG. FIG. 3 is a diagram showing a circuit configuration of the radiation image detector of FIG. 4 is a partial cross-sectional view of the imaging panel of FIG.

  The radiographic image detector 5 is an FPD (flat panel detector) configured to be portable in a flat panel shape and constitutes a radiographic image acquisition device. The present inventor previously disclosed in Japanese Patent Laid-Open No. 2000-250152. This will be described with reference to a configuration example.

  As shown in FIG. 2, the radiation image detector 5 includes an imaging panel 21, a control circuit 30 that controls the operation of the radiation image detector 5, and a rewritable read-only memory such as a flash memory. 1, a memory unit 31 for storing the image signal output from the power supply unit 34, a power supply unit 34 for supplying power necessary for driving the imaging panel 21 to obtain an image signal, the radiation image detector 5, and the PC of FIG. And a detector communication unit 35 for performing wireless communication with the communication unit 4, and these are housed in a flat rectangular housing 40.

  Further, as shown in FIG. 2, on the outer surface of the housing 40, an operation unit 32 for switching the operation of the radiographic image detector 5, a radiographic image preparation completion, and a predetermined amount of image signal to the memory unit 31. Are displayed, and a display unit 33 for displaying patient information such as a patient name, and a lighting unit 33a composed of a light emitting diode or the like are arranged.

  As shown in FIG. 3, the imaging panel 21 includes a scanning drive circuit 25 that reads the stored electrical energy according to the intensity of the irradiated radiation, a signal selection circuit 27 that outputs the stored electrical energy as an image signal, Have

  The casing 40 preferably has an outer shape made of aluminum or an aluminum alloy, which is a material that can withstand external impacts and is as light as possible. The radiation incident surface side of the casing 40 is a non-metal that easily transmits radiation, for example, It is configured using carbon fiber or the like. Further, on the back side opposite to the radiation incident surface, it is generated for the purpose of preventing the radiation from passing through the radiation image detector 5 or when the material constituting the radiation image detector 5 absorbs the radiation 2. In order to prevent influence from secondary radiation, a material that effectively absorbs radiation, such as a lead plate, is used.

  Further, inside the housing 40, the scanning drive circuit 25, the signal selection circuit 27, the control circuit 30, the memory unit 31 and the like are covered with a radiation shielding member (not shown), and radiation inside the housing 40 is detected. Scattering is prevented, and radiation of each circuit is prevented. The power supply unit 34 may be, for example, a primary battery such as a manganese battery, a nickel / cadmium battery, a mercury battery, or a lead battery, a secondary battery such as a rechargeable nickel polymer secondary battery or a lithium ion polymer battery. The flat plate shape is preferable so that the FPD can be thinned.

  As shown in FIG. 3, the imaging panel 21 detects visible light converted by the scintillator, and photoelectrically converts this visible light into an image signal carrying a radiographic image of the subject. ˜412− (m, n) are two-dimensionally arranged. Scanning lines 421-1 to 421-m and signal lines 422-1 to 422-n are disposed between the photoelectric conversion elements 412 so as to be orthogonal to each other, for example. One transistor 423- (1,1) is connected to the photoelectric conversion element 412- (1,1). For example, a field effect transistor is used as the transistor 423- (1,1), the drain electrode or the source electrode is connected to the photoelectric conversion element 412- (1,1), and the gate electrode is the scanning line 421-. Connected with 1. When the drain electrode is connected to the photoelectric conversion element 412- (1,1), the source electrode is connected to the signal line 422-1, and when the source electrode is connected to the photoelectric conversion element 412- (1,1), the drain electrode Is connected to the signal line 422-1. In this way, one pixel is formed.

  Similarly, a transistor 423 is connected to the other photoelectric conversion element 412, a scanning line 421 is connected to a gate electrode of the transistor 423, and a signal line 422 is connected to a source electrode or a drain electrode.

  As shown in FIG. 4, the photoelectric conversion element 412 includes a photodiode including a signal line 413 formed of a conductive film patterned on a substrate 411, an amorphous silicon layer 414, and a transparent electrode 415. The signal line 413 is connected to the drain electrode 423d (or the source electrode 423s) of the thin film transistor 423 formed over the substrate 411. In addition, a scanning line is connected to the gate electrode 423 g of the thin film transistor 423, and a source electrode 423 s (or a drain electrode 423 d) is connected to the signal line 422. Note that a gate insulating film 424 and a semiconductor layer 425 are provided between the source electrode 423 s and the drain electrode 423 d and the gate electrode 423 g.

  A phosphor layer (scintillator layer) 430 is formed on the photoelectric conversion element 412, and a support 431 is provided on the back surface (X-ray source side) in some cases. Note that a protective layer 432 is provided on the surface of the phosphor layer 430 as will be described later. When the phosphor layer 430 is attached on the photoelectric conversion element 412, the gap between the photoelectric conversion element 412 and the phosphor layer 430 is reduced. A protective layer 432 is interposed between the two layers.

  As shown in FIG. 3, the scanning lines 421-1 to 421-m of the imaging panel 21 are connected to the scanning drive circuit 25, and the signal lines 422-1 to 422-n are connected to the charge detectors 425-1 to 425-1. 425-n. Here, when the charge reading signal RS is supplied from the scanning drive circuit 25 to one of the scanning lines 421-1 to 421 -m, the scanning line 421 -p (p is any value from 1 to m). Transistors 423- (p, 1) to 425- (p, n) connected to the scanning line 421-p are turned on, and photoelectric conversion elements 412- (p, 1) to 412- (p, n) ) Is supplied to the charge detectors 425-1 to 425-n via the signal lines 422-1 to 422-n. In the charge detectors 425-1 to 425-n, voltage signals SV-1 to SV-n proportional to the amount of charge supplied via the signal lines 422-1 to 422-n are generated. The voltage signals SV-1 to SV-n output from the charge detectors 425-1 to 425-n are supplied to the signal selection circuit 27.

  The signal selection circuit 27 is configured using a register 45a and an A / D converter 45b, and a voltage signal is supplied to the register 45a from the charge detectors 425-1 to 425-n. In the register 45a, the supplied voltage signals are sequentially selected and converted into digital data by the A / D converter 45b. This data is supplied to the control circuit 30.

  The control circuit 30 generates the scanning control signal RC and the output control signal SC based on the control signal CTD included in the radio signal n received from the control device 1 (FIG. 1) via the communication unit 35. The scanning control signal RC is supplied to the scanning drive circuit 25, and the charge readout signal RS is supplied to the scanning lines 421-1 to 421-m based on the scanning control signal RC. Further, the output control signal SC is supplied to the signal selection circuit 27, and the selection operation of the voltage signals from the charge detectors 425-1 to 425-n stored in the register 45a is controlled and the selected voltage signal. Is converted to a data signal and supplied from the signal selection circuit 27 to the control circuit 30 as image data DT.

  In the control circuit 30, the image data DT is transmitted as a radio signal m to the control device 1 (FIG. 1) via the communication unit 35. If the logarithmic conversion process of the image data is performed when the image data DT is supplied to the control apparatus 1, the process of the image data in the control apparatus 1 can be simplified. The logarithmic conversion described above may be performed simultaneously when the read charge amount is converted into the voltage signal SV by the charge detector 425. Thus, by using the A / D converter 45b as digital data after logarithmic conversion, the resolution of the radiation information in the region where the voltage signal SV is small can be increased.

  The phosphor layer 430 of the imaging panel 21 in FIG. 4 is formed by applying a phosphor coating composed of a phosphor and a binder to a support to form the phosphor layer, and then attaching the phosphor layer to the photoelectric conversion element side. The method of attaching is used. In addition, the phosphor coating is applied to the temporary support, and then dried and peeled to form a sheet-like phosphor layer, which is applied, or the phosphor coating is sprayed to form the phosphor layer. The phosphor coating material may be applied to the photoelectric conversion element directly or via a protective layer.

  In order to form the phosphor layer 430, first, a binder and a phosphor are added to an appropriate organic solvent, and a disperser or a ball mill is used to stir and mix so that the phosphor is uniform in the binder. A phosphor coating dispersed in is prepared.

Examples of phosphors include tungstate phosphors (CaWO ₄ , MgWO, CaWO ₄ : Pb, etc.), terbium activated rare earth oxysulfide phosphors [Y ₂ O ₂ S: Tb, Gd ₂ O ₂ S: Tb, La ₂ O ₂ S: Tb, (Y, Gd) ₂ O ₂ S: Tb, (Y, Gd) O ₂ S: Tb, Tm, etc.], terbium-activated rare earth phosphate phosphor (YPO ₄ : Tb, GdPO ₄ : Tb, LaPO ₄ : Tb, etc.), terbium activated rare earth oxyhalide phosphors (LaOBr: Tb, LaOBr: Tb, Tm, LaOCl: Tb, LaOCl: Tb, Tm, LaOCl: Tb, Tm, LaOBr: Tb) , GdOBr: Tb, GdOCl: Tb, etc.), thulium activated rare earth oxyhalide phosphors (LaOBr: Tm, LaOCl: Tm, etc.), barium sulfate Phosphors [BaSO ₄ : Pb, BaSO ₄ : Eu ²⁺ , (Ba, Sr) SO ₄ : Eu ²⁺ etc.], divalent europium activated alkaline earth metal phosphate phosphors [(Ba ₂ PO ₄ ) ₂ : Eu ²⁺ , (Ba ₂ PO ₄ ) 2: Eu ^2+, etc.] Divalent europium-activated alkaline earth metal fluoride halide-based phosphors [BaFCl: Eu ²⁺ , BaFBr: Eu ²⁺ , BaFCl: Eu ²⁺ , Tb, BaFBr: Eu ²⁺ , Tb, BaF ₂ · BaCl · KCl: Eu ²⁺ , (Ba · Mg) F ₂ · BaCl · KCl: Eu ²⁺ etc.], iodide phosphors (CsI: Na, CsI: Tl, NaI, KI: Tl, etc.), sulfide-based phosphors [ZnS: Ag (Zn, Cd) S: Ag, (Zn, Cd) S: Cu, (Zn, Cd) S: Cu, Al, etc.], phosphoric acid Bromide phosphor _{(HfP 2} O 7: Cu, etc.), tantalum based phosphor _{(YTaO 4, YTaO 4: Tm} , YTaO 4: Nb, [Y, Sr] TaO 4-X: Nb, LuTaO 4, LuTaO ₄ : Nb, [Lu, Sr] TaO _{4 -X} : Nb, GdTaO ₄ : Tm, Gd ₂ O ₃ .Ta ₂ O ₅ .B ₂ O ₃ : Tb, etc.), particularly Gd ₂ O ₂ S : Tb, CsI: Tl are desirable.

  However, the phosphor is not limited to those described above, and any phosphor can be used as long as it emits light in the visible region upon irradiation with radiation, and the photoelectric conversion element has sensitivity to the emission wavelength.

  Here, the average particle diameter of the phosphor increases the filling rate of the phosphor in the phosphor layer, enables high-definition light emission, and can reduce scattering of the phosphor emission in the phosphor layer. Thus, it is 0.5 μm or more and 10 μm or less, preferably 1 μm or more and 5 μm or less.

  Solvents for preparing phosphor paints include lower alcohols such as methanol, ethanol, n-propanol and n-butanol, chlorine atom-containing hydrocarbons such as methylene chloride and ethylene chloride, ketones such as acetone, methyl ethyl ketone and methyl isobutyl ketone, Aromatic compounds such as toluene, benzene, cyclohexane, cyclohexanone, xylene, esters of lower fatty acids and lower alcohols such as methyl acetate, ethyl acetate, butyl acetate, dioxane, ethylene glycol monoethyl ester, ethylene glycol monomethyl ester Mention may be made of ethers and their inclusions.

  It should be noted that the phosphor paint has a dispersant for improving the dispersibility of the phosphor in the paint, or a plastic for improving the binding force between the binder and the phosphor in the formed phosphor layer. Various additives such as an agent may be mixed.

  Examples of the dispersant include phthalic acid, stearic acid, caproic acid, lipophilic surfactant and the like. Examples of plasticizers include phosphates such as triphenyl phosphate, tricresyl phosphate and diphenyl phosphate, phthalates such as diethyl phthalate and dimethoxyethyl phthalate, glycols such as ethyl phthalyl ethyl glycolate and butyl phthalbutyl glycolate Examples thereof include acid esters, polyesters of triethylene glycol and adipic acid, polyesters of polyethylene glycol and aliphatic dibasic acid such as polyesters of diethylene glycol and oxalic acid, and the like.

  A coating film of the coating material is formed by uniformly applying the phosphor coating material containing the phosphor and the binder prepared as described above to the surface of the support or the temporary support for forming the sheet.

  The thickness of the phosphor layer 430 is preferably 20 to 150 μm and preferably 20 to 100 μm in order to obtain a sufficient amount of stimulated emission light and to reduce light scattering in the phosphor layer. Is desirable.

  As this coating means, for example, a doctor blade, a roll coater, a knife coater, an extrusion coater or the like can be used.

  As the support 431 in FIG. 4, for example, those made of various materials such as glass, wool, cotton, paper, and metal can be used. What can be processed into a roll is preferable. From this point, for example, cellulose acetate film, polyester film, polyethylene terephthalate film, polyamide film, polyimide film, triacetate film, plastic film such as polycarbonate film, metal sheet such as aluminum foil, aluminum alloy foil, general paper, and photographic base paper, for example Printing paper such as coated paper or art paper, baryta paper, resin-coated paper, paper sized with polysaccharides as described in Belgian Patent No. 784,615, titanium dioxide, etc. Particularly preferred are processed papers such as pigmented pigmented paper and paper sized with polyvinyl alcohol.

  In order to reinforce the bond between the support 431 and the phosphor layer 430, an undercoat layer is provided on the support surface by applying a polymer material such as polyester or gelatin to provide adhesion, and image quality (sharpness, graininess) In order to improve the above, a light absorbing layer made of a light absorbing material such as carbon black may be provided to absorb at least a part of light emitted from the scintillator. Although those structures can be arbitrarily selected according to the purpose and application, a carbon black-containing black polyethylene terephthalate support is preferred.

  The phosphor layer 430 is provided with a protective layer 432 for physically and chemically protecting the surface opposite to the side in contact with the support 431 described above. The protective layer 432 is made of, for example, a cellulose derivative such as cellulose acetate or nitrocellulose, or a synthetic polymer substance such as polymethyl methacrylate, polyethylene terephthalate, polyvinyl butyral, polyvinyl formal, polycarbonate, polyvinyl acetate, vinyl chloride, or vinyl acetate copolymer. It can be formed by a method in which a solution prepared by dissolving in a solvent is applied to the surface of the phosphor layer. These polymer substances can be used alone or in combination. Further, when the protective layer 432 is formed by coating, it is desirable to add a cross-linking agent immediately before coating. Alternatively, it can be formed by a method of bonding a plastic sheet made of polyethylene terephthalate, polyethylene naphthalate, polyethylene, polyvinylidene chloride, polyamide or the like using an adhesive.

  Further, it is preferably formed of a coating film containing a fluorine resin soluble in an organic solvent. The fluorine-based resin refers to a polymer of olefin containing fluoro (fluoroolefin) or a copolymer containing olefin containing fluorine as a copolymer component. The protective layer formed of the fluorine resin coating film may be cross-linked. Further, for the purpose of improving the film strength and the like, a fluorine-based resin and other polymer substances may be mixed.

  Such a protective layer 432 has a thickness of 0.5 to 10 μm, preferably 1 to 3 μm. By using such a thin protective layer 432, the distance between the phosphor layer 430 and the photoelectric conversion element is reduced, and thus the light emitted from the phosphor layer 430 is scattered by the protective layer 432. Since it is immediately incident on the photoelectric conversion element, it contributes to improvement of the sharpness of the obtained radiographic image.

  Here, by coloring at least one of the phosphor layer 430 and the protective layer 432, a reduction in sharpness due to scattering of light emission of the phosphor in the phosphor layer can be reduced. The colorant is a colorant that absorbs at least part of light in the emission wavelength region of the phosphor, and a blue to red colorant is appropriately used as a color that absorbs the emission wavelength of the phosphor.

Examples of yellow to red colorants (dyes and pigments) used for phosphors that emit light in the green region include various dyes such as azo dyes, acridine dyes, quinoline dyes, thiazole dyes, nitro dyes; and molybdenum Various pigments such as orange, cadmium yellow, chrome yellow, zinc chromate, cadmium yellow, and red lead can be exemplified. The content of the colorant varies depending on the intended use of the phosphor layer, the portion to be colored, the type of the colorant, etc., but generally 10: 1 to 10 ⁶ when the colorant is a dye. : 1 (phosphor: colorant, weight ratio). When the colorant is a pigment, it is selected from the range of 1:10 to 10 ⁵ : 1 (phosphor: colorant, weight ratio).

  In the case of using a phosphor that emits light in the green region, the phosphor may be colored using a colorant having a main peak of an absorption spectrum in a wavelength region of 420 to 540 nm. Further, the phosphor may be colored using a colorant whose average absorptance in the light emission region longer than the peak wavelength of light emission of the phosphor is higher than that in the light emission region shorter than the peak wavelength.

  By the way, in the formation of the phosphor layer, the phosphor layer is formed by uniformly applying the phosphor coating to the support. However, the phosphor layer can also be formed by a vapor phase method, for example, a vapor deposition method. If this phosphor layer has a columnar crystal structure, it is possible to suppress scattering of phosphor emission in the phosphor layer by the light guide effect.

  As shown in FIG. 3, a memory unit 31, an operation unit 32, a display unit 33, and a communication unit 35 are connected to the control circuit 30, and an operation signal PS from the operation unit 32 and a radio signal n from the control device 1 are connected. Based on this, the operation of the radiation image detector 5 is controlled.

  The operation unit 32 is provided with a plurality of switches. Based on the operation signal PS corresponding to the switch operation from the operation unit 32 or the radio signal n from the control device 1, the imaging panel 21 is initialized and the image signal of the radiographic image is displayed. Is generated. The storage capacity of the memory unit 31 is a capacity capable of storing a plurality of image data.

  Further, the control circuit 30 performs processing for storing the generated image signal in the memory unit 31 and wirelessly transfers the data signal as the data wireless signal m from the detector communication unit 35 to the PC communication unit 4 in FIGS. .

  As described above, the radiographic image detector 5 of FIGS. 2 to 4 is configured to have a flat panel type portable structure by integrating the imaging panel, the power supply unit, the memory unit, and the like, so that radiographic images can be easily captured. It can be carried out.

  The imaging panel 21 of the radiation image detector 5 described with reference to FIGS. 3 and 4 may have other configurations. For example, FIG. 16B of Japanese Patent Laid-Open No. 9-294229, Japanese Patent Laid-Open No. 2004-2004 Each configuration shown in FIG. 4B of Japanese Patent No. 6781 and Japanese Patent Laid-Open No. 2000-61823 may be adopted.

  The imaging panel 21 in FIGS. 3 and 4 described above is a photoelectric conversion element made of an inorganic substance, but may be a photoelectric conversion element made of an organic substance. This will be described with reference to the configuration example disclosed in the Japanese Unexamined Patent Publication No. 2003-344545. FIG. 8 is a diagram showing a circuit configuration of a radiation image detector configured from an imaging panel including a photoelectric conversion element made of organic matter. FIG. 9 is a partial cross-sectional view of the imaging panel of FIG.

  As shown in FIG. 8, the imaging panel 21 has a two-dimensionally arranged collection electrode 220 for reading out the stored electrical energy in accordance with the intensity of the irradiated radiation. Electric energy is stored in the capacitor 221 as one electrode. One collection electrode 220 corresponds to one pixel of the radiation image.

  Between the pixels, scanning lines 223-1 to 223-m and signal lines 224-1 to 224-n are disposed so as to be orthogonal, for example. The capacitor 221- (1,1) is connected to a transistor 222- (1,1) made of a silicon laminated structure or an organic semiconductor. The transistor 222- (1,1) is, for example, a field effect transistor, and the drain electrode or the source electrode is connected to the collecting electrode 220- (1,1), and the gate electrode is connected to the scanning line 223-1. The When the drain electrode is connected to the collecting electrode 220- (1,1), the source electrode is connected to the signal line 224-1, and when the source electrode is connected to the collecting electrode 220- (1,1), the drain electrode is connected to the signal line 224-1. Connected to line 224-1. Similarly, the scanning line 223 and the signal line 224 are connected to the collecting electrode 220, the capacitor 221 and the transistor 222 of other pixels.

As shown in the partial cross-sectional view of the imaging panel 21 in FIG. 9, a first layer 211 that is a scintillator layer that emits light according to the intensity of incident radiation is provided on the radiation irradiation surface side. Here, the first layer 211 is irradiated with X-rays (radiation), which is electromagnetic waves that pass through a human body or the like having a wavelength of about 1 mm (1 × 10 ⁻¹⁰ m), for example, from the radiation source 101 of FIG.

  The first layer 211 is mainly composed of a phosphor, and based on incident radiation, an electromagnetic wave having a wavelength of 300 nm to 800 nm, that is, an electromagnetic wave (light) ranging from ultraviolet light to infrared light centering on visible light. Is output. The phosphors used in the first layer 211 are tungstate phosphors, terbium activated rare earth oxysulfide phosphors, terbium activated rare earth phosphate phosphors, terbium activated rare earth oxyhalide phosphors, cesium iodide. However, the present invention is not limited to these, and any phosphor that outputs an electromagnetic wave in a region where the light receiving element has sensitivity such as the visible, ultraviolet, or infrared region by irradiation of radiation may be used.

  Next, a second layer 212 that converts electromagnetic waves (light) output from the first layer into electrical energy is formed on the side of the first layer 211 opposite to the radiation irradiation surface side. The second layer 212 includes a diaphragm 212a, a transparent electrode film 212b, a hole conduction layer 212c, a charge generation layer 212d, an electron conduction layer 212e, and a conduction layer 212f from the first layer 211 side. Here, the charge generation layer 212d contains an organic compound capable of photoelectric conversion, that is, an organic compound capable of generating electrons and holes by electromagnetic waves (light), and is separated into several functions in order to smoothly perform photoelectric conversion. For example, the second layer is configured as shown in FIG.

The diaphragm 212a is for separating the first layer 211 from other layers, and for example, Oxi-nitride is used. The transparent electrode film 212b is formed using a conductive transparent material such as indium tin oxide (ITO), SnO ₂ , or ZnO. In the formation of the transparent electrode film 212b, a thin film can be formed using a method such as vapor deposition or sputtering. In addition, a pattern having a desired shape may be formed by a photolithography method, or when high pattern accuracy is not required (about 100 μm or more), a mask having a desired shape is used during vapor deposition or sputtering of the electrode material. A pattern may be formed.

  In the charge generation layer 212d, electrons and holes are generated by the electromagnetic wave (light) output from the first layer 211. The holes generated here are collected in the hole conduction layer 212c, and the electrons are collected in the electron conduction layer 212e. In this structure, the hole conduction layer 212c and the electron conduction layer 212e are not necessarily essential.

  The conductive layer 212f is made of, for example, chromium. In addition, a general metal electrode or the transparent electrode can be selected, but in order to obtain good characteristics, a metal, an alloy, an electrically conductive compound and a mixture thereof having a small work function (4.5 eV or less) are used. What is used as an electrode material is preferable. Specific examples of such electrode materials include, but are not limited to, sodium, sodium-potassium alloy, magnesium, lithium, and aluminum. The conductive layer 212f can be generated using a method such as vapor deposition or sputtering using these electrode materials as raw materials.

  Next, the charge generation layer 212d is formed using an organic compound that forms an aggregate of cyanine dyes or a J aggregate. Cyanine dyes are widely used as spectral sensitizers for silver halide photography. In the J aggregate, electrons constituting the dye molecule are absorbed by absorbing visible light, and the excited electrons move to the silver halide grains, so that the silver halide grains are exposed. This cyanine dye is generally said to form a dye molecule aggregate on silver halide grains. When the dye molecule forms an aggregate, the dye molecule itself is stabilized.

  Next, the third layer 213 that accumulates the electrical energy obtained in the second layer 212 and outputs a signal based on the accumulated electrical energy is provided on the side opposite to the radiation irradiation surface side of the second layer 212. Is formed. The third layer 213 includes a capacitor 221 that stores the electrical energy generated in the second layer 212 for each pixel, and a transistor 222 that is a switching element for outputting the stored electrical energy as a signal. . Note that the third layer is not limited to the one using the switching element, and may be configured to generate and output a signal corresponding to the energy level of the stored electrical energy, for example.

  As the transistor 222, for example, a TFT (Thin Film Transistor) is used. This TFT may be an inorganic semiconductor type used in a liquid crystal display or the like or an organic semiconductor type, and is preferably a TFT formed on a plastic film. As the TFT formed on the plastic film, an amorphous silicon type is known.

  As shown in FIGS. 8 and 9, the transistor 222 that is a switching element accumulates the electric energy generated in the second layer 212 and is connected to a collecting electrode 220 that is one electrode of the capacitor 221. . The capacitor 221 stores the electric energy generated in the second layer 212, and the stored electric energy is read by driving the transistor 222. In other words, a radiation image can be generated for each pixel by driving the switching element. In FIG. 9, the transistor 222 includes a gate electrode 222a, a source electrode (drain electrode) 222b, a drain electrode (source electrode) 222c, an organic semiconductor layer 222d, and an insulating layer 222e.

  The fourth layer 214 is a substrate of the imaging panel 21. The substrate preferably used as the fourth layer 214 is a plastic film, and examples of the plastic film include polyethylene terephthalate (PET), polyethylene naphthalate (PEN), polyethersulfone (PES), polyetherimide, and polyetheretherketone. , Films made of polyphenylene sulfide, polyarylate, polyimide, polycarbonate (PC), cellulose triacetate (TAC), cellulose acetate propionate (CAP), and the like. Thus, by using a plastic film, it is possible to reduce the weight as compared with the case of using a glass substrate and to improve resistance to impact.

  Furthermore, on the side opposite to the third layer side surface of the fourth layer 214, a power source 34, for example, a primary battery such as a manganese battery, a nickel cadmium battery, a mercury battery, a lead battery, a rechargeable nickel polymer secondary battery, It is good also as a structure which provides secondary batteries, such as a lithium ion polymer battery, and this battery has a preferable flat form so that FPD can be made thin.

  Further, as shown in FIG. 8, in the imaging panel 21, initialization transistors 232-1 to 232-n connected to, for example, drain electrodes are provided on the signal lines 224-1 to 224-n. The source electrodes of the transistors 232-1 to 232-n are grounded. The gate electrode is connected to the reset line 231.

  The scanning lines 223-1 to 223-m and the reset line 231 of the imaging panel 21 are connected to the scanning drive circuit 25 as shown in FIG. When the readout signal RS is supplied from the scanning drive circuit 25 to one of the scanning lines 223-1 to 223 -m, the scanning line 223 -p (p is any value from 1 to m). The transistors 222- (p, 1) to 222- (p, n) connected to -p are turned on, and the electricity stored in the capacitors 221- (p, 1) to 221- (p, n) Energy is read out to the signal lines 224-1 to 224-n, respectively. The signal lines 224-1 to 224-n are connected to the signal converters 271-1 to 271-n of the signal selection circuit 27. In the signal converters 271-1 to 271-n, the signal lines 224-1 to 224 are connected. Voltage signals SV-1 to SV-n proportional to the amount of electric energy read on -n are generated. The voltage signals SV-1 to SV-n output from the signal converters 271-1 to 271-n are supplied to the register 272.

  In the register 272, the supplied voltage signal is sequentially selected and converted into a digital image signal for one scanning line (for example, 12 bits to 14 bits) by the A / D converter 273. A scanning signal is supplied to each of the lines 223-1 to 223-m through the scanning drive circuit 25 to perform image scanning, and a digital image signal for each scanning line is captured to generate an image signal of a radiation image. Do. This image signal is supplied to the control circuit 30.

  Further, the reset signal RT is supplied from the scanning drive circuit 25 to the reset line 231 to turn on the transistors 232-1 to 232-n, and the readout signal RS is supplied to the scanning lines 223-1 to 223-m. When the transistors 222- (1,1) to 222- (m, n) are turned on, the electric energy stored in the capacitors 221- (1,1) to 221- (m, n) is converted to the transistors 232-1 to The imaging panel 21 can be initialized by being emitted through 232-n.

  As shown in FIG. 8, a memory unit 31, an operation unit 32, a display unit 33, and a communication unit 35 are connected to the control circuit 30, and an operation signal PS from the operation unit 32 and a radio signal n from the control device 1 are connected. Based on this, the operation of the radiation image detector 5 is controlled.

  The operation unit 32 is provided with a plurality of switches. Based on the operation signal PS corresponding to the switch operation from the operation unit 32 or the radio signal n from the control device 1, the imaging panel 21 is initialized and the image signal of the radiographic image is displayed. Is generated. The storage capacity of the memory unit 31 is a capacity capable of storing a plurality of image data.

  Further, the control circuit 30 performs processing for storing the generated image signal in the memory unit 31 and wirelessly transfers the data signal as the data wireless signal m from the detector communication unit 35 to the PC communication unit 4 in FIGS. .

  As described above, the radiation image detector 5 of FIGS. 2, 8, and 9 is integrated with an imaging panel, a power supply unit, a memory unit, and the like in a flat panel type portable structure as in FIGS. Since it comprised, radiographic imaging can be performed easily.

  Next, each step S01-S13 of the radiographic imaging method by the radiographic imaging system of FIGS. 1-6 is demonstrated with reference to the flowchart of FIG.

  First, when a patient's radiography reservation is made at the examination room or at the reception (S01), the reservation information is transmitted from the HIS / RIS 54 or the like to the control device 1 via the network 50 (S02) and received by the control device 1. (S03), an FPD selected from a plurality of FPDs is assigned to the patient (S04). Then, the control device 1 stores correspondence information between the patient and the assigned FPD (S05). The processes up to step S05 are usually performed before the patient arrives in the radiographing room, and the control device 1 receives reservation information for a large number of patients. For example, as shown in screen 3 in FIG. Is stored.

  Note that reservation information may be input to the control device 1 in advance in steps S02 and S03 described above. A large number of FPDs are registered in the host control device 55, and the control device 1 can select and assign from these many usable FPDs. For example, when there are a plurality of FPDs in each shooting room Alternatively, the control device 1 may select from FPDs in the shooting room of the jurisdiction (for one room).

  Next, when the patient comes to the radiographing room, the radiologist confirms the patient name (S06). The wireless IC tag of the patient may be confirmed by reading with the reading unit 1a in FIG. At this time, if there is an imaging history of the patient, it is displayed on the display unit 2 for reference of the current imaging condition, and the previous imaging condition is input to the radiation generation control apparatus 102 by default. Good.

  Next, the radiologist selects a patient to perform radiography on the screen 3 of the display unit 2 in the control device 1 (S07). For example, when a patient (○ Yama △ husband) is selected on the screen 3 in FIG. 1, a corresponding signal is transmitted as a radio signal n from the PC communication unit 4 to the FPD 5 a in FIG. 1 assigned to the patient and corresponding to “FPD001”. The FPD 5a that is transmitted (S08) and receives the corresponding signal displays the patient name on the display unit 33, and the lighting unit 33a lights (or blinks) (S09). As a result, it is easy and certain to know which FPD should be used to image a patient (patient selected by the control device) who will perform radiation imaging from now on, and the captured radiation image is not mistaken for the patient. Further, since the name of the patient is displayed on the display unit 33 of the selected FPD 5a, it is possible to confirm the patient to be radiographed and to know that the patient is waiting for radiography.

  Next, using the FPD 5a for the patient, as shown in FIG. 5, radiography is performed by irradiating the radiation 100 from the radiation source 101 under the control of the radiation generation control device 102 (S10), and the radiation image is obtained by the FPD 5a. Is generated (S11), and the generated image data is transferred to the control device 1 by the wireless signal m as that of the corresponding patient (S12). The control apparatus 1 confirms the image of the transferred image data, performs necessary image processing, and the image data is transferred to the database server 52 via the network 50 as the corresponding patient and stored. (S13).

  By setting in advance at the time of reservation, the image data is automatically transferred to the designated destination, for example, the image display device 51 or the printer 53 of the requesting doctor after transfer / save to the database server 52. it can. Further, it may be set so that it is automatically transferred to the image display device 51 and the printer 53 simultaneously with the transfer to the database server 52. Further, when such setting is not performed, the doctor can read out the image data from the database server 52 and display the image data on the image display device 51 as necessary after transfer and storage to the database server 52.

  In addition, when radiographing is performed in a hospital room, the patient is associated with the FPD using patient confirmation information such as a patient ID. That is, the patient confirmation information of the inpatient is read to confirm whether it corresponds to the reservation of the control device 1 (whether or not the patient has a reservation), and the patient information of the patient to be radiographed before going around the hospital room is input. When it returns, the image data is transferred to the host controller 55.

  The control device 1 shown in FIGS. 1, 5, and 6 is composed of a personal computer, but the storage device stores a program for executing the operation shown in FIG. 7, and starts up (starts up) the device. At this time, the data is read from the storage device, and each operation is controlled according to the program. The storage device of the personal computer may be a built-in or external hard disk storage device or the like, but is not limited thereto, and may be a built-in or external storage medium reader. As this storage medium, various portable storage media such as an optical disk such as a CD and a DVD, a magnetic disk or a magnetic tape can be used, and the program is stored in one storage medium or divided into a plurality of storage media. May be remembered.

  As described above, according to the radiographic imaging method of the radiographic imaging system in FIG. 7, when the control device 1 receives the radiographic imaging reservation information of the patient in the radiographing room, the control device 1 before each radiographic imaging, for each patient. When an FPD used for radiography is selected and assigned, correspondence information between the patient and the FPD is stored in advance, and a patient who has entered the imaging room is selected on the screen 3 of the control device 1, a correspondence signal between the patient and the FPD 5a is transmitted to the control device. 1 is sent to the FPD 5a of FIG. 1, the FPD 5a displays the patient name on the display unit 33, and the lighting unit 33a is lit or blinked. Therefore, the patient to be radiographed can be accurately associated with the FPD and generated. Radiographic image data can be accurately associated with patient information. For this reason, even if a large number of patients are reserved, it is possible to accurately know the FPD for performing radiography of each patient, and there is no possibility that the captured radiographic image is mistaken for the patient.

  As described above, the best mode for carrying out the present invention has been described. However, the present invention is not limited to these, and various modifications are possible within the scope of the technical idea of the present invention. For example, the cassette type radiation image detector 5 in FIGS. 2 to 4 converts radiation into light by a phosphor such as a scintillator, reads this light with a photodetector, and generates radiation image data (indirect conversion). However, the present invention is not limited to this, and a configuration (direct conversion type) in which radiation is directly converted into charges and the charges are read with a capacitor or the like to generate image data may be used. Further, the radiation image detector may be a standing radiation imaging apparatus in which an FPD can be inserted instead of the cassette type.

  5 and 6, the communication between the detector communication unit 35 and the PC communication unit 4 is wireless. However, the present invention is not limited to this, and may be performed by a wired connection cable. Of course. For example, as shown in FIG. 2, a connector 35a is provided on the side surface of the housing 40 of the radiation image detector 5, and the connector 35a and the control device 1 are connected by a connection cable, and signal communication can be performed in the same manner.

  When the FPD associated with the patient receives the correspondence signal, the patient name is displayed on the display unit 33 on the FPD side, and the lighting unit 33a is turned on or blinking. Or you may provide the audio | voice generation part which utters a patient name and a sound with the lighting part 33a or instead.

  Moreover, although the control apparatus 1 was comprised from the personal computer, it is not limited to this, For example, you may comprise from PDA (portable terminal).

It is a schematic diagram for demonstrating a mode that the radiographic imaging detector which performs radiography with a control apparatus is selected in the radiographic imaging system by this Embodiment. It is the perspective view which fractured | ruptured partially and looked at the inside in order to show the radiographic image detector of FIG. It is a figure which shows the circuit structure of the radiographic image detector of FIG. FIG. 3 is a partial cross-sectional view of the imaging panel in FIG. 2. It is a figure which shows roughly the radiographic imaging system which performs radiography with the radiographic image detector selected in FIG. It is a block diagram which shows roughly the radiographic imaging system of FIG. It is a flowchart for demonstrating each step S01-S10 of the radiographic imaging method by the radiographic imaging system of FIGS. It is a figure which shows the circuit structure of the radiographic image detector comprised from the imaging panel containing the photoelectric conversion element by organic substance. FIG. 9 is a partial cross-sectional view of the imaging panel in FIG. 8.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Control apparatus 2 Display part 3 Screen 4 PC communication part 5 Radiation image detector, FPD
5a-5f FPD
33 display unit 33a lighting unit 35 detector communication unit 50 network 52 database server P patient (subject)

Claims (12)

A radiographic imaging method in which a radiographic image obtained by radiography of a subject is detected by a radiographic image detector, and a radiographic image information is received by the control device from the radiographic image detector,
Receiving a plurality of subject information from outside,
Associating the plurality of subject information with a radiation image detector before capturing a radiation image;
Storing the association information;
Selecting the radiological image detector corresponding to a subject selected from a plurality of subjects based on the stored association information;
Sending a corresponding signal to the selected radiation image detector;
Displaying that the radiation image detector that has received the correspondence signal corresponds; and
And a step of generating a radiation image by the radiation image detector after capturing the radiation image and associating the generated radiation image with the subject information. The radiographic imaging method according to claim 1, wherein the associating step is executed by automatically selecting a radiographic image detector based on at least one of subject information and imaging information. The radiographic image capturing method according to claim 1, wherein a transmission source of the plurality of subject information is at least one of an examination room, a reception, and an imaging room. The radiographic image capturing method according to claim 1, wherein the radiographic image detector is a cassette type. A plurality of radiological image detectors for detecting radiographic images obtained by radiography of a subject;
A control device that is connectable to each of the radiation image detectors and receives radiation image information from each of the radiation image detectors,
The control apparatus stores means for receiving a plurality of pieces of subject information from the outside, correspondence means for associating each of the received pieces of subject information with the plurality of radiation image detectors, and the correspondence information. Means for selecting the radiation image detector corresponding to the subject selected from a plurality of subjects based on the stored association information, and a correspondence signal for the selected radiation image detector. Means for sending, and means for associating the radiographic image generated by the radiographic image detector with the corresponding subject information,
The radiographic image detector includes a notifying unit that receives the correspondence signal from the control device and notifies that the radiographic image detector is a corresponding radiographic image detector. 6. The notification means is at least one of a display unit that can display the subject information, a lighting unit that lights and blinks, and a sound generation unit that utters a subject name and sound. The radiographic imaging system described in 1. The radiographic image capturing system according to claim 5, wherein the corresponding unit is configured to automatically select a radiographic image detector based on at least one of subject information and imaging information. The radiographic imaging system according to claim 5, 6 or 7, wherein the transmission source of the plurality of subject information is at least one of an examination room, a reception, and an imaging room. The radiation image capturing system according to claim 5, wherein the radiation image detector is a cassette type. A program for a computer included in a control device that detects a radiographic image obtained by radiography of a subject with a radiographic image detector and receives radiographic image information from the radiographic image detector,
Receiving a plurality of subject information from outside,
Associating the plurality of subject information with a radiation image detector before capturing a radiation image;
Storing the association information;
Selecting the radiological image detector corresponding to a subject selected from a plurality of subjects based on the stored association information;
Sending a corresponding signal to the selected radiation image detector;
Displaying that the radiation image detector that has received the correspondence signal corresponds; and
A radiographic image capturing program for causing the computer to execute a step of generating a radiographic image with the radiographic image detector after capturing a radiographic image and associating the generated radiographic image with the subject information. The radiographic imaging program according to claim 10, wherein the associating step is executed by automatically selecting a radiographic image detector based on at least one of subject information and imaging information. The radiographic image capturing program according to claim 10 or 11, wherein the plurality of subject information transmission sources are at least one of an examination room, a reception, and an imaging room.

Images