JP4692681B2 - Portable radiographic image reading system - Google Patents

Description

  The present invention relates to a portable radiation image reading system.

  Conventionally, a so-called radiographic method combining an intensifying screen and a radiographic film has been used as a method for obtaining a radiographic image. According to this method, when radiation such as X-rays transmitted through the subject is incident on the intensifying screen, the phosphor contained in the intensifying screen absorbs the energy of the radiation and emits fluorescence. By this light emission, the radiographic film superposed so as to be in close contact with the intensifying screen is exposed, and a radiographic image is formed on the radiographic film.

  However, in order to obtain a radiographic image by such a radiographic method, it is necessary to perform imaging while matching the sensitivity areas of the radiographic film used for imaging and the intensifying screen. In addition, the radiographic film must be subjected to processing such as chemical development and fixing after photographing, and it takes time until a radiographic image is obtained.

  On the other hand, when a part of radiation energy is accumulated and subsequently irradiated with excitation light such as visible light, a stimulable phosphor that exhibits stimulated emission according to the accumulated energy is used. A method of obtaining image signals by photoelectrically reading photostimulated luminescence by irradiating laser light or the like after recording radiation image information of a subject on a sheet-like photostimulable phosphor sheet is used.

  In this method using a photostimulable phosphor, by controlling the gain at the time of obtaining an electrical signal corresponding to the amount of photostimulated luminescence by photoelectric conversion, it is possible to reduce the influence of fluctuations in the amount of radiation exposure and to produce a good radiographic image. Obtainable.

  However, such a method using a photostimulable phosphor causes scattering of light (stimulated luminescence, excitation light) in the layer of the photostimulable phosphor, so that the resolution of the radiation image is lowered. Further, since excitation light must be irradiated to generate stimulated emission, an irradiating means for irradiating excitation light is required, the configuration is complicated, and a radiographic image cannot be obtained quickly.

  For this reason, for example, X-rays or the like transmitted through the subject are irradiated onto a photoconductive layer using amorphous selenium or the like, and image data is generated according to the magnitude of charges generated in the photoconductive layer. A method for obtaining a radiation image using image data has been proposed (see, for example, Patent Document 1).

  In this method, as an imaging panel that generates image data corresponding to the amount of irradiated radiation, a charge storage capacitor on a dielectric substrate and a plurality of transistors for reading the stored charge from the charge storage capacitor are arranged adjacent to each other. Further, a photoconductive layer is laminated on the transistor or capacitor. Here, a bias voltage is applied to the photoconductive layer through a dielectric layer, and when charges are generated in the photoconductive layer by radiation transmitted through the subject, the charges are accumulated in the charge storage capacitor. At this time, the transistor is turned off. Thereafter, the transistor is turned on and the charge stored in the charge storage capacitor is read, and image data corresponding to the read charge amount is generated and read. The image data read in this way is stored in a storage means provided inside the cassette type radiation image reading apparatus.

  In order to obtain a radiographic image after completion of imaging, a cassette type radiographic image reading apparatus and a controller are connected by, for example, a cable, and image data stored in a storage unit of the cassette type radiographic image reading apparatus is supplied to the controller. The controller outputs a radiation image based on the supplied image data. Note that image data communication is performed not only by a wired system but also by a wireless system.

JP-A-6-342099

  By the way, as described above, if the image data stored in the storage means of the cassette type radiation image reading apparatus is supplied to the controller and the radiation image is output from the controller, it is confirmed whether or not the imaging can be performed correctly. In order to do this, image data must be supplied to the controller to output a radiation image, which cannot be easily confirmed. In addition, patient identification data is stored in the storage unit in association with image data every time a radiographic image is taken, and the patient identification data stored in the storage unit cannot be easily confirmed.

  Accordingly, the present invention provides a portable radiographic image reading system that can confirm information related to radiographic image capturing and can efficiently obtain a desired radiographic image.

The portable radiographic image reading system according to the present invention generates and reads image data with a plurality of two-dimensionally arranged detection elements in accordance with the intensity of radiation irradiated in radiographic imaging of a subject. Based on the imaging panel, means for displaying the information about the radiographic imaging and the image data obtained by the radiographic imaging for each radiographing, and the information and image data about the radiographic imaging displayed, A means for confirming whether or not radiography has been performed correctly, and a means for associating the displayed radiographic information with image data when confirming that radiography has been performed correctly. It means for storing in association with information about the Tagged radiographic and the image data, image de-information about the stored radiography associated And it has a means for outputting the data.

In the present invention, information regarding radiographic image capturing is displayed every time a radiographic image is captured, and when radiographic image capturing is performed, information regarding radiographic image capturing and image data are displayed. When the captured image data is displayed and a confirmation operation is performed, information related to radiographic image capturing and image data are stored in association with each other. In addition, information regarding the radiographic image capturing of the next person to be captured is displayed.

According to the present invention, when radiographic images are captured, image data is displayed, so that it is possible to easily confirm whether the radiographing has been performed correctly. In addition, information regarding radiographic image capturing is displayed for each radiographic image capturing, and when the captured image data is displayed and a confirmation operation is performed, identification information of the next person to be imaged is displayed. Then, it is possible to efficiently capture a desired radiographic image using the display. Furthermore, if the image data is stored in correspondence with the information related to radiographic image capturing, the image data can be easily managed using the information related to radiographic image capturing.

It is a figure which shows the structure of a radiographic imaging system. It is a perspective view which shows the structure of a cassette type radiographic image reading apparatus. It is a figure which shows the structure of an imaging panel. It is a partial cross section figure of an imaging panel. It is a figure which shows the structure of a cassette type radiographic image reading apparatus and a radiographic image information processing apparatus. Other configuration examples of the display unit Display example on the display

  Next, an embodiment of the present invention will be described in detail with reference to the drawings. FIG. 1 is a diagram illustrating a configuration of a radiographic imaging system. In FIG. 1, the radiation emitted from the radiation generation apparatus 10 is applied to an imaging panel of a cassette type radiation image reading apparatus (hereinafter referred to as “radiation image reading apparatus”) 20 constituting a portable radiation image reading system through a subject 5. The In the radiation image reading device 20, image data is generated based on the intensity of the irradiated radiation. The controller 60 uses the image data supplied from the radiation image reading device 20 to display or output a radiation image with good image quality.

  FIG. 2 is a diagram illustrating the structure of the radiation image reading apparatus 20. The imaging panel 21 that generates and outputs image data according to the intensity of the irradiated radiation is housed in a housing 40 configured using carbon fiber or the like. The imaging panel 21 includes a scanning drive circuit 24 that reads out the accumulated charges according to the intensity of the irradiated radiation, and a signal selection circuit 26 that generates and outputs image data based on the accumulated charges.

  Further, the radiographic image reading apparatus 20 receives image data output from the imaging panel 21 by using a control circuit 28 that controls the operation of the radiographic image reading apparatus 20, a rewritable read-only memory (for example, a flash memory), or the like. Memory 29 for storing, operation unit 30 for switching the operation of the radiographic image reading device 20, a sensor 31 for detecting radiation irradiation, display of a captured radiographic image, completion of radiographic image capturing preparation, and the like A power supply unit 33 for supplying power for driving the display unit 32 and the imaging panel 21 to obtain image data, power for displaying on the display unit 32, and power for operating the control circuit 28 and the memory 29, radiation A communication connector 34 for synchronizing the operations of the generator 10 and the radiation image reader 20 is provided.

  The radiation image reading device 20 may be provided with a connector (not shown) for connecting the controller 60 so that the memory 29 and the controller 60 can be connected via a communication cable. May be attached to the controller 60 or the like. Further, if a protective member having a desired strength is provided on the surface of the display unit 32, the display unit 32 can be prevented from being damaged during the handling of the radiation image reading apparatus 20.

  On the radiation irradiation surface side of the imaging panel 21, a grid 35 for absorbing a radiation scattering component is disposed as necessary. Furthermore, a handle 42 is provided in the housing 40 to facilitate carrying of the radiographic image reading device 20 and position adjustment during radiographic image capturing.

  Note that the inside of the housing 40, the scanning drive circuit 24, the signal selection circuit 26, the control circuit 28, the memory 29, and the like are covered with a radiation shielding member (not shown). The circuit is prevented from being exposed to radiation.

  FIG. 3 shows the configuration of the imaging panel 21. The imaging panel 21 has a dielectric substrate 211 having a thickness sufficient to obtain a predetermined rigidity. This dielectric substrate is made of, for example, glass. On the dielectric substrate 211, a plurality of microplates 212- (1,1) to 212- (m, n) using a metal thin film are two-dimensionally arranged. Between the microplates 212, scanning lines 215-1 to 215-m and signal lines 216-1 to 216-n are disposed so as to be orthogonal, for example. One transistor 220- (1,1) is connected to the microplate 212- (1,1). For example, a field effect transistor is used as the transistor 220- (1,1), and the drain electrode or the source electrode is connected to the microplate 212- (1,1), and the gate electrode is the scanning line 215-1. Connected. When the drain electrode is connected to the microplate 212- (1,1), the source electrode is connected to the signal line 216-1. When the source electrode is connected to the microplate 212- (1,1), the drain electrode is connected to the signal line 216-1. Connected to line 216-1. The microplate 212- (1,1) is used as one electrode of the charge storage capacitor 222-1. In this way, one pixel is formed. Similarly, the other microplate 212 is connected to the transistor 220, the scanning line 215 is connected to the gate electrode of the transistor 220, and the signal line 216 is connected to the source electrode or the drain electrode.

  FIG. 4 is a partial cross-sectional view of the imaging panel 21, and a gate electrode 220 g connected to the scanning line 215 is formed on the dielectric substrate 211. A gate insulating film 220p is formed on the gate electrode 220g, and a semiconductor layer 220c using amorphous silicon or the like is formed on the gate insulating film 220p. A source electrode 220s and a drain electrode 220d are formed on the semiconductor layer 220c to form a field effect transistor. One of the source electrode 220 s or the drain electrode 220 d is connected to the signal line 216 and the other electrode is connected to the microplate 212.

  An electrode 222a as an external microplate is formed on the dielectric substrate 211, and a dielectric 222b such as silicon dioxide or silicon nitride is formed on the electrode. Further, the microplate 212 is formed on the dielectric 222b, and the charge storage capacitor 222 is formed by the microplate 212, the electrode 222a, and the dielectric 222b. The microplate 212 formed on the dielectric 222b of the charge storage capacitor 222 is connected to the transistor 220, and the electrode 222a formed on the dielectric substrate 211 is grounded.

  The transistor 220 is covered with a passivation layer 225 and a charge blocking layer 226 is formed on the microplate 212 of the charge storage capacitor 222.

  Further, on the passivation layer 225, the charge blocking layer 226, the scanning line 215 (not shown), and the signal line 216 (not shown), electron-hole pairs are generated by irradiating with radiation, resulting in a resistance value. A photoconductive layer 227 is formed in which changes. The photoconductive layer 227 preferably has a high dark resistance value, such as amorphous selenium, lead oxide, cadmium sulfide, mercuric iodide, or an organic material exhibiting photoconductivity (photoconductivity to which an X-ray absorption compound is added. In particular, amorphous selenium is desirable. A dielectric layer 228 is preferably formed on the photoconductive layer 227, and a bias electrode 229 is formed on the dielectric layer 228.

  Here, when radiation is incident on the photoconductive layer 227 while a high voltage (for example, several kV) is applied to the bias electrode 229 from the voltage source, an amount of electron-hole pairs corresponding to the intensity of the radiation is generated. At the same time, since a high voltage is applied to the bias electrode 229, the generated charge is moved to the dielectric layer 228 side, and the charge having the opposite polarity is moved to the charge blocking layer 226 side. . The dielectric layer 228 prevents injection of charges from the bias electrode 229 to the photoconductive layer 227, and the charge blocking layer 226 blocks injection of charges from the microplate 212 of the charge storage capacitor 222 to the photoconductive layer 227. Is done. For this reason, it is possible to prevent a leakage current from flowing through the photoconductive layer 227, and an amount of electric charge corresponding to the intensity of radiation can be stored in the charge storage capacitor 222.

  In this way, the charge storage capacitors 222- (1,1) to 222- (m, n) each having the microplates 212- (1,1) to 212- (m, n) shown in FIG. ) Can store a charge indicating a radiation image, and can generate image data by determining the amount of charge stored in the charge storage capacitors 222- (1,1) to 222- (m, n). it can.

  In the imaging panel 21, initialization transistors 232-1 to 232-n, for example, connected to drain electrodes are provided on the signal lines 216-1 to 216-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 215-1 to 215-m and the reset line 231 of the imaging panel 21 are connected to the scanning drive circuit 24 as shown in FIG. When the charge read signal RS is supplied from the scanning drive circuit 24 to one of the scanning lines 215-1 to 215-m, p is a value of 1 to m, this scanning line Transistors 220- (p, 1) to 220- (p, n) connected to 215-p are turned on and stored in the charge storage capacitors 222- (p, 1) to 222- (p, n) The charged charges are read out to the signal lines 216-1 to 216-n, respectively. The signal lines 216-1 to 216-n are connected to the charge detectors 233-1 to 233-n, and the charge detectors 233-1 to 233-n read on the signal lines 216-1 to 216-n. Voltage signals SV-1 to SV-n that are proportional to the amount of electric charge that has been output are generated. The voltage signals SV-1 to SV-n output from the charge detectors 233-1 to 233-n are supplied to the signal selection circuit 26.

  The signal selection circuit 26 includes a register 26a and an A / D converter 26b, and a voltage signal is supplied to the register 26a from charge detectors 233-1 to 233-n. In the register 26a, the supplied voltage signal is sequentially selected and converted into digital data (for example, 12 bits to 14 bits) by the A / D converter 26b. This data is supplied to the control circuit 28. In the state where a high voltage is applied to the bias electrode 229, the reset signal RT is supplied from the scanning drive circuit 24 to the reset line 231 to turn on the transistors 232-1 to 232-n and the scanning line 215-1. When the charge read signal RS is supplied to ˜215-m and the transistors 220- (1,1) to 220- (m, n) are turned on, the charge storage capacitors 222- (1,1) to 222- (m , n) is discharged through the transistors 232-1 to 232-n, so that the imaging panel 21 can be initialized, that is, the residual charges can be removed.

  An operation unit 30, a sensor 31, and a memory 29 are connected to the control circuit 28, and the operation of the radiation image reading apparatus 20 is controlled based on the operation signal PS from the operation unit 30 and the sensor signal SS from the sensor 31. . The operation unit 30 is provided with a plurality of switches. Based on an operation signal PS corresponding to the switch operation from the operation unit 30, the imaging panel 21 is initialized and then a high voltage is applied to the bias electrode 229 to perform radiation irradiation. A standby state of radiation irradiation is performed by applying a high voltage to the bias electrode 229 without setting the imaging panel 21 to the standby state.

  Further, the control circuit 28 performs scanning control when it is detected that radiation irradiation has been completed based on the sensor signal SS, or when a radiation irradiation end signal is supplied from the radiation generator 10 via the connector 34. The signal RC and the output control signal SC are generated. This scanning control signal RC is supplied to the scanning drive circuit 24, and based on the scanning control signal RC, supply of the charge read signal RS to the scanning lines 215-1 to 215-m and reset signal to the reset line 231 are performed. RT is supplied. The output control signal SC is supplied to the signal selection circuit 26, and the selection operation of the voltage signals from the charge detectors 233-1 to 233-n stored in the register 26a is controlled. Thus, in the case of (m × n) microplates, data based on the charges stored in the charge storage capacitors 222- (1,1) to 222- (m, n) is represented by data DP ( 1,1) to DP (m, n), data DP (1,1), DP (1,2),... DP (1, n), DP (2,1),. A process of storing the image data DT in the memory 29 in the order of DP (m, n) is also performed. Furthermore, an image display signal for displaying a radiographic image taken from the image data DT is also generated.

  If the logarithmic conversion processing of the image data is performed when the image data DT obtained by the radiation image reading device 20 is stored in the memory 29, the processing of the image data in the controller 60 can be simplified. . The logarithmic conversion may be performed at the same time when the read charge amount is converted into the voltage signal SV by the charge detector 233. Thus, by converting the logarithm to digital data by the A / D converter 26b, the resolution of the radiation information in the region where the voltage signal SV is small is increased.

  Further, as shown in FIG. 5, the radiation image reading apparatus 20 includes a power supply unit 33, and the power VP necessary for driving the imaging panel 21 to obtain image data is the radiation image reading apparatus 20. Supplied to each circuit. Although not shown, when power is supplied to the power supply unit 33 from the outside, the power VP may be supplied to each unit using the power supplied from the outside.

  A CPU (Central Processing Unit) 61 for controlling the operation of the controller 60 is connected to a system bus 62 and an image bus 63 and to an input interface 67. The operation of the CPU 61 for controlling the operation of the controller 60 is controlled based on a control program stored in the memory 64.

  A display control circuit 65, a frame memory control circuit 66, an output interface 68, a data reading circuit 69, a disk control circuit 70, and the like are connected to the system bus 62 and the image bus 63. The operation of the circuit is controlled, and image data is transferred between the circuits via the image bus 63.

  In the data reading circuit 69, the memory 29 removed from the radiation image reading device 20 can be mounted, and the image data stored in the memory 29 is read. Note that the radiation image reading device 20 may be connected to the data reading circuit 69 via a communication cable to read image data.

  A frame memory 71 is connected to the frame memory control circuit 66, and image data read from the memory 29 by the data reading circuit 69 is stored in the frame memory 71 via the frame memory control circuit 66. The image data stored in the frame memory 71 is read out and supplied to the display control circuit 65 and the disk control circuit 70.

  An image display device 72 is connected to the display control circuit 65, and a radiographic image based on the image data supplied to the display control circuit 65 is displayed on the screen of the image display device 72. Here, when the number of display pixels of the image display device 72 is smaller than the number of pixels of the radiation image reading device 20, the number of pixels can be reduced by thinning out and reading the image data, or pixel data of a plurality of pixels. Thus, for example, by calculating an average value or the like, one image data is generated and replaced with pixel data of a plurality of pixels, thereby reducing the number of pixels, whereby the entire captured image can be displayed on the screen. Further, if image data in an area corresponding to the number of display pixels of the image display device 72 is read, a captured image at a desired position can be displayed in detail.

  When image data is supplied from the frame memory 71 to the disk control circuit 70, for example, the image data is continuously read out and written into the FIFO memory in the disk control circuit 70, and then sequentially recorded in the disk device 73. The

  Further, the image data read from the frame memory 71 and the image data read from the disk device 73 can be supplied to the external device 100 via the output interface 68.

  As the external device 100, a scanning laser exposure apparatus called a laser imager is used. In this scanning laser exposure apparatus, the intensity of a laser beam is modulated by image data, and after exposure to a conventional silver halide photographic light-sensitive material or thermal phenomenon silver halide photographic light-sensitive material, an appropriate development process is carried out to produce a radiographic image. A hard copy can be obtained.

  This scanning laser exposure apparatus uses a solid laser such as a ruby laser, a YAG laser, or a glass laser as a laser light source; a He—Ne laser, an Ar ion laser, a Kr ion laser, a C02 laser, a C0 laser, a He—Cd laser, an N2 laser, Gas lasers such as excimer lasers; semiconductor lasers such as InGaP lasers, AlGaAs lasers, GaAs lasers, InGaAs lasers, InAsP lasers, CdSnP2 lasers, GaSb lasers, and GaN lasers; chemical lasers and dye lasers.

  The silver halide photographic light-sensitive material is coated with an undercoat layer that imparts adhesion to a transparent or non-colored transparent polymer material such as polyester, triacetate acetate, polyethylene naphthalate, polycarbonate, or polynorbornene resin. Further, a polymer layer such as gelatin in which silver halide grains are dispersed is coated on one side or both sides of the support. When a photosensitive layer containing silver halide grains or the like is coated only on one side, a gelatin layer containing an antihalation dye, antistatic agent, matting agent, etc., if necessary, is coated on the other side of the layer. be able to. The film thickness of the polymer film such as gelatin in this layer can be adjusted so that the photosensitive material does not cause strong curl during environmental humidity change or underwater processing.

  The photosensitive layer used in this photosensitive material disperses silver halide grains. This silver halide grain has a composition such as silver iodobromide, silver bromide, silver chloride, silver chlorobromide, and the shape is dice, octahedron, potato, spherical, rod, flat, etc. The particle size distribution can be selected from narrow to wide depending on the purpose. The average particle diameter is preferably 0.1 to 1 μm in terms of spherical silver halide grains. In the case of a flat plate, those having an average aspect ratio of 100: 1 to 2: 1 can be used. It is preferable to use a core / shell type grain having a multilayer structure having different halogen compositions on the inside and on the surface of the silver halide grain. JP-A-59-177535, 59-17844, 60-35726, 60-147727 and the like can be referred to for the method for producing the silver halide grains. These silver halide grains are preferably chemically sensitized using hypo, selenium compounds, tellurium compounds and gold compounds, and iridium compounds, other metal ions, and sensitizing dyes may be added at the time of silver halide grain formation. it can. The spectral maximum wavelength of the sensitizing dye used in the light-sensitive material is 500 to 1500 nm, and cyanine dyes and merocyanine dyes are generally used. E. K. Mees, T .; H. James, The Theory of the Photographic Process, 3rd edition, pages 198-201 (Macmillan, New York, 1986). The photosensitive layer preferably contains various nitrogen-containing organic compounds and mercapto compounds containing sulfur atoms that suppress fogging during storage or development. Further, the photosensitive layer may contain a dye for preventing irradiation. Further, it can contain non-photosensitive silver halide grains for imparting irregularities to the film surface after the development processing to suppress reflection of external light. A gelatin protective layer for protecting the photosensitive layer can be coated on the photosensitive layer, and the layer can contain an antistatic agent, a matting agent, a sliding agent and the like depending on the purpose. The photosensitive layer and the protective layer preferably contain a hardener that crosslinks gelatin chains and reinforces the film surface.

  The silver halide light-sensitive material is preferably developed using an automatic processor, and the processing time (Dry to Dry) can be processed from 10 seconds to 210 seconds. In the developer used in the automatic processor, dihydroxybenzenes, 3-pyrazolidones and ascorbic acids described in JP-A-4-1544641 and JP-A-4-16841 are preferably used as developing agents. Sulfites are used as preservatives, and hydroxides and carbonates are used as alkali agents together with the buffering agents described in JP-A-61-28708 and JP-A-60-93439. Glycols are used as dissolution aids, and sulfides, disulfide compounds and triazines are used as silver sludge inhibitors. Organic inhibitors are azole organic inhibitors, inorganic inhibitors are potassium bromide and the like. F. A. The compounds described on pages 226 to 229 of “Photographic Processing Chemistry” by Mason, published by Focal Press (1966) can be used. Moreover, an organic chelating agent and a dialdehyde type development hardening agent can be included. The replenishment amount of the developer during the development process is preferably 5-15 ml / 4 cut. The fixing solution may include a fixing material generally used in the art, and may include a chelating agent, a fixing hardener, and a fixing accelerator.

  A silver halide light-sensitive material described in JP-A-9-31407, which is heat-developed without performing the wet treatment as described above, can be used. This photosensitive material is a photothermographic material having at least one photosensitive layer on a support and containing an organic silver salt, photosensitive silver halide grains, a reducing agent for silver ions and bindery. The composition of the silver halide grains of the light-sensitive material is silver iodobromide, silver bromide, silver chlorobromide or silver bromide, which is cubic, octahedral, spherical, and potato-like, and the average grain size is converted as spherical grains. 0.2 to 0.010 μm is preferable. Further, it is preferable to use a spectral sensitizing dye that chemically sensitizes the silver halide grains with hypo, selenium, and a gold compound to impart color sensitivity to 400 to 1500 nm. The photosensitive material preferably contains an organic carboxylate or an isocyanate compound in order to suppress an increase in fog during storage of the photosensitive material. The organic silver salt used for the light-sensitive material is preferably a long-chain carboxylic acid silver salt having 10 to 30 carbon atoms. Examples include silver behenate, silver stearate, silver oleate, silver laurate, silver caproate, silver myristate, silver palmitate, silver maleate, silver fumarate, silver tartrate, silver linoleate, silver butyrate And silver camphorate and mixtures thereof. As the reducing agent for the organic silver salt, dihydroxybenzenes such as phenidone and hydroquinone are used. In addition, a wide range of reducing agents can be used, such as a combination of amide oximes, azines, aliphatic carboxylic acid aryl hydroazides and ascorbic acid. Further, it is preferable to coat a protective film on the photosensitive layer of the light-sensitive material, and an antistatic agent, a matting agent, a sliding agent, etc. can be added to this protective film depending on the purpose. These photosensitive layers and protective layers are supported by colored or non-colored transparent polymer materials such as polyester, triacetate acetate, polyethylene naphthalate, polycarbonate, and polynorbornene resin coated with an undercoat layer for imparting adhesiveness. Apply on top. It is preferable to apply a backing layer containing an antihalation dye, a matting agent and an antistatic agent on a support on which a photosensitive layer is not applied. The photosensitive material is exposed to an image signal using a scanning laser exposure apparatus, and is subjected to thermal development at 80 ° C. or more and 200 ° C. or less.

  Further, the image information obtained by this radiation image information processing apparatus is exposed with a high-density laser beam by an image signal using a scanning laser exposure apparatus, as described in, for example, JP-A-8-282099. A hard copy can be obtained by transferring from the transfer layer having a color developing component to the receiving layer.

  This scanning laser exposure apparatus uses a solid laser such as a ruby laser, a YAG laser, and a glass laser as a laser light source; He-Ne laser, Ar ion laser, Kr ion laser, C02 laser, C0 laser, He-Cd laser, N2 laser, Gas lasers such as excimer lasers; semiconductor lasers such as InGaP lasers, AlGaAs lasers, GaAs lasers, InGaAs lasers, InAsP lasers, CdSnP2 lasers, GaSb lasers, and GaN lasers; chemical lasers and dye lasers. The laser beam is 400 to 1200 nm.

  The sensitive material is composed of three supports. A transfer material having a developer component provided on the first support and a release material having a third support are provided so as to face the transfer layer, and high-density energy light is imaged from the first support side. By exposing the exposed part to the release material, the bonding force between the support of the exposed part and the transfer layer is reduced by ablation, the single car material and the release material are separated, the exposed part of the transfer layer is transferred onto the release material, and then the release material is exposed. An image is formed by superimposing a part of the transfer layer and a receiving layer side of a receiving material having a receiving layer containing a coloring component on the second support. Ablation here means that the transfer layer in the image exposure portion does not break, and only the bonding force between the support and the transfer layer is reduced or eliminated, or a part of the transfer layer in the image exposure portion is thermally broken and scattered. In addition to the above, a phenomenon until a crack occurs in the transfer layer of the image exposure portion is included. The image formation is performed by mixing the color forming component and the color developing component at the time of forming the latent image or after forming the latent image, and it is preferable to further heat or pressurize. The heating means may be an open, thermal head, heat roll, hot stamp, hot pen, or the like that applies temperature only, or may apply pressure at the same time as the temperature is applied. The color developing component of the first layer is, for example, an organic reducing agent, and the coloring component of the second support is a silver source that develops color with the organic reducing agent. Examples of the organic reducing agent include succinimide, phthalimide, 2-methylsuccinimide, dithiouracil, 5-methyl-5-n-pentylhydratoin, phthalimide and the like. The silver source is a silver salt with an aliphatic carboxylic acid (for example, silver behenate, silver stearate, silver oleate, silver laurate, etc.).

  Further, the thermal transfer thermal recording method described in JP-A-9-188073 can be used. By facing the dye layer surface of the thermal transfer sheet and the receiving layer surface of the thermal transfer image receiving sheet so as to contact each other, and applying thermal energy corresponding to the image information to the interface between the dye layer and the receiving layer by a heating application means such as a thermal head The dye in the dye layer is transferred to the receiving layer. After the transition, the unreacted dye is fixed by applying predetermined heat energy from the back side of the thermal transfer sheet by a heating application means such as a thermal head. Specific examples of heat transferable dyes in the dye layer include those described in JP-A Nos. 59-78893, 59-10909394, and 60-2398. Representative examples of the binder resin used in the dye layer can be selected from cellulose, polyacrylic acid, polyvinyl alcohol, and the like. For the receiving layer, a resin that is easily dyed by a sublimation dye is selected. For example, a polyolefin resin, a polyvinyl chloride resin, a polyvinylidene chloride resin, or the like can be selected.

  Furthermore, it is possible to output an image by so-called inkjet, which forms an image by ejecting ink fine particles in an image-like manner based on an input image signal due to a piezo effect, and further, the image signal is replaced with an optical signal, An image can be output by a so-called digital copier, which is one of xerography that forms an image using toner.

  An input device 74 such as a keyboard is connected to the input interface 67. By operating the input device 74, identification information for identifying the obtained image data is input.

  The frame memory 71 stores the image data supplied from the radiation image reading device 20, but the supplied image data may be stored after being processed by the CPU 61.

  Further, the disk device 73 can store image data supplied from the radiation image reading device 20 stored in the frame memory 71 and image data obtained by processing the image data by the CPU 61 together with identification information and the like. .

  Next, the operation will be described. When obtaining a radiographic image of the subject 5, the subject 5 is assumed to be positioned between the radiation generator 10 and the imaging panel 21 of the radiographic image reader 20, and the radiation emitted from the radiation generator 10 is the subject 5. In addition, the radiation that has passed through the subject 5 enters the imaging panel 21.

  When the operation unit 30 of the radiation image reading apparatus 20 is operated and the operation is started, the imaging panel 21 is initialized according to the operated switch. Initialization of the imaging panel 21 is performed by turning on the transistors 220- (1,1) to 220- (m, n) and 232-1 to 232-n in a state where a high voltage is applied to the bias electrode 229. This is performed by discharging the charge stored in the storage capacitors 222- (1,1) to 222- (m, n) (that is, erasing the charge).

  As described above, since the imaging panel 21 is initialized, even if charges are stored in the imaging panel 21, the charges are prevented from affecting the photographed image. Note that the stored charge may be released by performing a read operation of the stored charge.

  When initialization of the imaging panel 21 is completed and preparation for shooting is completed, the display unit 32 configured by a flat panel display such as a liquid crystal display or a plasma display displays that shooting is possible. Thereafter, when the switch of the radiation generation apparatus 10 is operated in a state where a high voltage is applied to the bias electrode 229, radiation is emitted from the radiation generation apparatus 10 toward the subject 5 for a predetermined time, and the radiation image reading apparatus 20 Then, it is determined whether or not radiation is being applied based on the sensor signal SS from the sensor 31. When the radiation generation apparatus 10 and the radiation image reading apparatus 20 are connected, the radiation irradiation end signal DFE is supplied from the radiation generation apparatus 10 to the radiation image reading apparatus 20 to determine the end of radiation irradiation. it can. When the radiation generation apparatus 10 and the radiation image reading apparatus 20 are connected, the operation of the operation unit 30 of the radiation image reading apparatus 20 may be operated to control radiation irradiation by the radiation generation apparatus 10.

  The intensity of the radiation incident on the imaging panel 21 of the radiation image reading device 20 is modulated by the subject 5 because the degree of radiation absorption by the subject 5 is different. When the imaging panel 21 is irradiated with the radiation modulated by the subject 5, the charge storage capacitors 222- (1,1) to 222- (m, n) of the imaging panel 21 are based on the intensity of the irradiated radiation. Charge is stored.

  When the irradiation of radiation from the radiation generating apparatus 10 is completed and the control circuit 28 of the radiation image reading apparatus 20 determines that the irradiation of radiation has ended based on the sensor signal SS from the sensor 31, or a radiation irradiation end signal When it is determined by the DFE that the irradiation of radiation has been completed, a scanning control signal RC is supplied from the control circuit 28 to the scanning drive circuit 24. Based on the scanning control signal RC, the charge readout signal RS is sequentially supplied to the scanning lines 215-1 to 215-m and stored in the charge storage capacitors 222- (1,1) to 222- (m, n). The charges are sequentially read out. Further, the output control signal SC is supplied from the control circuit 28 to the signal selection circuit 26, and the selection operation of the voltage signals from the charge detectors 233-1 to 233-n stored in the register 26a is controlled and selected. Data is generated based on the applied voltage signal and stored in the memory 29 as image data DT.

  When the reading of the charges stored in the charge storage capacitors 222- (1,1) to 222- (m, n) is completed, the charge reading signal RS and the reset signal RT are used so that the next shooting can be performed. As a result, the transistors 220- (1,1) to 220- (m, n), 232-1 to 232-n are turned on, and the imaging panel 21 is initialized. Further, when the data amount of image data that can be newly stored in the memory 29 is determined and image data for one screen can be recorded, the next photographing can be performed.

  In the same manner, radiographic images are sequentially taken and image data DT is sequentially stored in the memory 29.

  When a radiographic image is taken, the control circuit 28 generates an image display signal DS based on the image data DT. Since this image display signal DS is supplied to the display unit 32 and a radiographic image is displayed on the display unit 32, it can be easily confirmed whether or not imaging has been performed correctly.

  Further, the control circuit 28 performs image processing on the image data DT (gradation processing: processing for expressing an image with density and contrast suitable for diagnosis, frequency processing: processing for controlling the sharpness of the image, dynamic range. Compression processing: processing for keeping the entire image in an easily viewable range, irradiation field recognition: processing for identifying a region irradiated with radiation, parallel movement, rotational movement, black-and-white reversal, etc.) and then generating an image display signal DS It may be a thing. In this case, the processed radiographic image is displayed on the display unit 32, or the processed radiographic image is displayed when the operation key of the operation unit 30 is operated after the preprocessed radiographic image is displayed. In this way, it is possible to confirm whether or not a desired radiographic image has been obtained by displaying the processed radiographic image.

  Further, the control circuit 28 reads the image data DT stored in the memory 29 when, for example, an operation key for image confirmation of the operation unit 30 is operated, generates an image display signal DS, and displays it on the display unit 32 before processing. Or it is good also as what displays the radiographic image after a process. As described above, if the image data DT stored in the memory 29 is read and the radiation image is displayed on the display unit 32, it is easy to determine what kind of radiation image is stored in the memory 29 without using the controller 60. Can be confirmed. In addition, referring to the radiographic image displayed on the display unit 32, unnecessary radiographic image data DT can be erased from the memory 29. In addition, the effect of the processing can be easily and easily confirmed by switching and displaying the radiation image before and after the processing with a switch.

  The control circuit 28 monitors the data amount of the image data DT stored in the memory 29, and the number of radiation images stored in the memory 29, the number of storable radiation images, and the free space of the memory 29 are, for example, one screen. An information display signal DJ for displaying a warning or the like indicating that the amount of image data is less than the amount of image data is generated. By supplying this information display signal DJ to the display unit 32, the use state of the memory 29 can be easily confirmed by the display on the display unit 32. Although not shown, the warning may be performed by voice or the like.

  Further, identification information including information related to radiographic image capturing, such as ID number, name, date of birth, sex, imaging region, imaging date and time, is stored in advance in the memory 29, for example. The identification information is sequentially displayed on the display unit 32 for each photographing, or the identification information of the next person to be photographed is displayed when the photographed image is displayed on the display part 32 and, for example, a confirmation switch or the like is operated. If so, it is possible to efficiently capture a desired radiographic image using the display of the display unit 32. The display unit 32 may sequentially display all of the identification information, or may sequentially display a part of the identification information. Further, the imaging conditions are also stored in the memory 29 as information related to radiographic imaging, and the imaging conditions are displayed on the display unit 32, whereby imaging can be performed under correct imaging conditions, and the cassette type radiographic image reader and Imaging can be easily performed by connecting the radiation generating apparatus 10 with a communication cable or the like and supplying imaging conditions to the radiation generating apparatus 10. Further, if the obtained image data DT is stored in the memory 29 in correspondence with the identification information and the photographing conditions, the management of the image data DT can be facilitated using the identification information or the like. If the memory 29 is provided with data protection means for prohibiting rewriting or erasing of image data, the data protection means prohibits rewriting or erasing of image data or the like by the data protection means after the photographing is completed, and is stored in the memory 29. Image data and the like can be protected.

  In addition, when the imaging order is changed during radiographic imaging or when imaging is added, identification information and imaging conditions can be changed by operating the operation unit 30.

  By the way, in the radiographic image reading apparatus 20 shown in FIG. 2, the display unit 32 is provided at the end portion on the front side. However, the imaging unit 21 is arranged so that the display unit 32 is not captured when radiographic images are captured. As long as it is provided at a position that does not overlap, it is not limited to the front side end. The display unit 32 may be large or small, and may be provided on the rear surface side of the radiation image reading apparatus 20. For example, a display unit having a large display area can be provided on the back side of the radiation image reading apparatus 20 as shown in FIG.

  Further, as shown in FIG. 6B, a display device 32 </ b> A for displaying a radiographic image may be provided separately from the radiographic image reading device 20. In this case, if the display device is detachable from the radiation image reading device, the portability of the radiation image reading device can be improved.

  In addition, when the display unit or the display device is small, the number of display pixels is smaller than the number of pixels of the imaging panel 21. Therefore, by thinning out the image data or setting representative data such as an average value from the image data in units of a predetermined number of images, the data amount is reduced to generate the image display signal DS, and this image display signal DS is displayed. By supplying to the unit or the display device, at least the entire radiation image can be displayed with the number of display pixels. In addition, an image display signal DS is generated based on image data of a desired area, and the image display signal DS is supplied to a display unit or a display device, so that a radiographic image of at least the desired area can be displayed in detail. Can be displayed.

  FIG. 7 shows a display example on the display unit 32. For example, when the display unit is composed of one display element 321 as shown in FIG. 7A, the radiation image, the identification information, the imaging condition, etc. are one. Displayed on the display element 321. In this case, all the displays may be displayed on one screen, or each display may be switched and displayed on one screen. In addition, as shown in FIG. 7B, when the display unit is configured by two display elements 322 and 323, the radiation image, identification information, imaging conditions, and the like are displayed on separate display elements. Furthermore, when a touch panel is provided on the display screen of the display unit as shown in FIG. 7C, not only a radiographic image, identification information, imaging conditions, etc., but also a display showing the operation corresponding to the switch 324s of the touch panel is performed. Is called.

  When the captured radiographic image is displayed and output by the controller 60, the controller 60 is connected to the memory 29 via a cable, or the memory 29 is removed from the radiographic image reading device 20 and attached to the controller 60. The controller 60 downloads image data DT and identification information stored in the memory 29. The image data DT downloaded from the memory 29 is stored in the frame memory 71 via the data reading circuit 69, the frame memory control circuit 66, and the like. Using the image data stored in the frame memory 71, a radiation image can be displayed on the image display device 72, or a hard copy of the radiation image can be output from the external device 100. It is also possible to perform gradation processing of image data stored in the frame memory 71 and display or output a radiation image based on the processed image data. The image data stored in the frame memory 71 and the image data on which gradation processing has been performed can be stored in the disk device 73, and the image data stored when the image data is stored in the disk device 73. It is also possible to display and output a radiographic image using.

  In addition, when image data processing is performed to display a processed radiographic image on the display unit 32 of the radiographic image reading device 20, if the processed image data is stored in the memory 29, this image is stored. By reading the data with the controller 60, it is possible to output a good radiographic image without processing the image data on the controller 60 side.

  Further, by storing the identification information and the like together with the image data in the disk device 73, it is possible to easily manage and identify the image data stored in the disk device 73. When identification information or the like is not stored in the memory 29, the identification information is input using the input device 74 provided in the controller 60. This identification information is input by operating a keyboard, using a magnetic card, a bar code, or HIS (in-hospital information system: network-based information management). In addition, the storage of identification information and the like in the memory 29 is performed by attaching the memory 29 to the controller 60 or connecting the radiographic image reading apparatus 20 to which the memory 29 is attached and the controller 60 with a cable or the like. It can be stored using the input device 74.

  As described above, in the above-described embodiment, the display unit 32 of the radiographic image reading device 20 displays information on the use state of the memory 29, the operating state of the radiographic image reading device 20, or radiographic image and radiographic image capturing. A radiographic image can be captured correctly and easily, and whether a desired radiographic image can be obtained can be easily confirmed without using a controller.

  The imaging panel generates charges according to the intensity of the irradiated radiation in the photoconductive layer, accumulates the charges with a number of charge storage capacitors arranged in a two-dimensional form, and reads the accumulated charges. Thus, the present invention is not limited to the one that generates image data, and various radiological image reading apparatuses can be obtained by changing the detection device to another one. For example, the radiation image reader may convert the irradiated radiation into light energy by a phosphor such as a scintillator and read the light energy with a photodiode to generate image data.

  The present invention is applied to a cassette type radiation image reading apparatus that incorporates an image processing function and a display function and enables confirmation of an image at an imaging location, and a portable radiation image reading system having the cassette type radiation image reading apparatus. The

DESCRIPTION OF SYMBOLS 10 Radiation generator 20 Cassette type radiation image reader 21 Imaging panel 28 Control circuit 29 Memory 30 Operation part 32 Display part 32A Display device 60 Controller 321, 322, 323 Display element 324s Switch

Claims (2)

An imaging panel that generates and reads image data with a plurality of detection elements that are two-dimensionally arranged according to the intensity of radiation emitted in capturing a radiographic image of a subject; and
A means for displaying information on radiographic imaging and the image data obtained by radiography for each radiography;
A means for confirming whether or not the current radiography has been performed correctly based on the displayed radiographic information and image data;
Means for associating the displayed radiographic information with image data when confirmation input indicating that radiography has been performed correctly,
Means for storing the associated radiographic information and image data in association with each other;
And a means for outputting image data associated with stored information relating to radiography . A portable radiographic image reading system. The portable radiographic image reading system according to claim 1, wherein the display unit displays information on radiography and image data on the same screen .

Images