JP2012105689A - Radiation image photographing apparatus and radiation image photographing system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiation image photographing apparatus and a radiation image photographing system, allowing effective correction of image data in pixel positions of defective pixels even if the defective pixels are present on a sensor panel in a cluster state.SOLUTION: This radiation image photographing apparatus 1 includes: the sensor panel 40 in which a plurality of imaging elements 41 are two-dimensionally arranged; and a correction means 22 replacing the image data F with image data Fcalculated and corrected based on information about the plurality of defective pixels dp including the defective pixels dp of two rows and two columns and distributed in the two-dimensional cluster state. The information about the defective pixels dp is information about the pixel positions (i, j) of the respective defective pixels dp and information about the numbers of pixels a-d to respective normal pixels A-D each nearest to each defective pixel dp in the row and column directions. The correction means 22 calculates the image data Fcorrected by use of image data F(A)-F(D) on the respective normal pixels A-D and the number of the pixels a-d based on the information about the defective pixels dp.

Description

  The present invention relates to a radiographic image capturing apparatus and a radiographic image capturing system.

  For the purpose of disease diagnosis and the like, radiographic images taken using radiation typified by X-ray images are widely used. Conventionally, such medical radiographic images have been taken using a screen film. In order to digitize radiographic images, CR (Computed Radiography) devices using stimulable phosphor sheets have been developed recently. Then, a radiation image capturing apparatus has been developed in which irradiated radiation is detected by a radiation detection element arranged in a two-dimensional form and acquired as digital image data.

  As such a radiographic imaging apparatus, a so-called direct type radiographic imaging apparatus that directly receives irradiated radiation by a radiation detection element and converts it into image data that is an electrical signal, or the irradiated radiation with a scintillator or the like. A variety of so-called indirect radiographic imaging apparatuses have been developed that convert energy of the converted electromagnetic wave into image data by a photoelectric conversion element such as a photodiode after conversion to electromagnetic wave of other wavelengths such as visible light. In the present invention, the radiation detection element in the direct type radiographic imaging apparatus, the photoelectric conversion element in the indirect type radiographic imaging apparatus, the corresponding scintillator portion, and the like are collectively referred to as an imaging element.

  This type of radiographic imaging apparatus is usually provided with a sensor panel in which a plurality of imaging elements are arranged two-dimensionally, and is known as an FPD (Flat Panel Detector). Conventionally, it has been formed integrally with a support base (see, for example, Patent Document 1), but recently, a portable radiographic imaging device in which a sensor panel is housed in a housing and can be carried has been developed ( For example, see Patent Document 2).

  In an FPD type radiographic imaging apparatus, abnormal image data is output constantly or with a certain probability, for example, when impurities are mixed in an image sensor when the image sensor is laminated on a sensor panel. Pixels (hereinafter referred to as defective pixels) may occur. Defective pixels that occur due to such a cause are usually in a state where they exist in isolation from each other in a plurality of image pickup devices that are two-dimensionally arranged on the sensor panel (that is, a so-called point defect state). There are many cases (see, for example, Patent Document 3).

  In addition, a plurality of image pickup devices arranged two-dimensionally on the sensor panel is usually formed so as to be connected to one signal line for each column (or row). Due to disconnection or the like, a defective pixel may exist in a linear form on the sensor panel (that is, a so-called line defect or line defect state).

  In such a case, generally, the abnormal image data output from the defective pixel dp (i, j) of the point defect or the line defect on the sensor panel S illustrated in FIG. 16 is discarded, and those defective pixels dp Linear interpolation is performed using normal image data output from normal image sensors p (i, j-1) and p (i, j + 1) adjacent to the left and right (or top and bottom) of (i, j). Then, a correction process for correcting the image data at the pixel position (i, j) of the defective pixel is performed. Note that i and j represent the row number i and the column number j of each image sensor p on the sensor panel S.

JP-A-9-73144 JP 7-246199 A JP 2002-197450 A

  By the way, when the sensor panel S of the radiographic imaging apparatus is manufactured, mechanical destruction occurs due to an object of the sensor panel S hitting, or a force is applied to bend the flat sensor panel S. Then, as shown in FIG. 17, defective pixels dp may be generated on the sensor panel S in a two-dimensional cluster form.

  In the present invention, as shown in FIG. 17, a two-dimensional shape of defective pixels dp including at least two rows and two columns of defective pixels dp and continuing in the row direction and the column direction is expressed as a cluster shape. The defective pixel dp in 2 rows and 2 columns refers to a defective pixel dp distributed in a so-called square shape as represented by hatching in the lower right corner of FIG.

  As described above, when defective pixels dp are generated in a cluster on the sensor panel S, for example, in the defective pixel dp (i, j) shown in FIG. Therefore, there is a problem that the image data of the defective pixel dp (i, j) cannot be corrected using each of the image data.

  The present invention has been made in view of the above problems, and even when defective pixels exist in a cluster on the sensor panel, it is possible to effectively correct image data at the pixel positions of these defective pixels. An object is to provide a radiographic imaging apparatus and a radiographic imaging system.

In order to solve the above-described problem, the radiographic imaging device of the present invention includes:
A sensor panel in which a plurality of image sensors for generating electric charges according to the dose of irradiated radiation are arranged in a two-dimensional manner;
A readout circuit for reading out image data from each of the image sensors;
Information on a plurality of defective pixels distributed in a two-dimensional cluster including at least two rows and two columns of defective pixels among the pixels corresponding to the plurality of imaging elements arranged two-dimensionally on the sensor panel. Storage means for storing;
Correction means for calculating the corrected image data at the pixel position of each defective pixel based on the information on the defective pixel, and replacing the image data output from each defective pixel with the corrected image data, respectively. When,
With
The information on the defective pixels includes information on pixel positions of the defective pixels on the sensor panel and pixels up to the normal pixels closest to the defective pixels in the row direction and the column direction on the sensor panel. Number information,
The correcting means is configured to determine, based on the information on the defective pixels, the image data and the number of pixels of the normal pixels closest to the defective pixels in the row direction, and the defective pixels in the column direction. The corrected image data is calculated using the image data and the number of pixels of the normal pixels closest to the image.

Moreover, the radiographic imaging system of the present invention is
A sensor panel in which a plurality of image sensors for generating electric charges according to the dose of irradiated radiation are arranged in a two-dimensional manner;
A readout circuit for reading out image data from each of the image sensors;
A communication means for transmitting / receiving data to / from an external device;
A radiographic imaging device comprising:
A plurality of pixels corresponding to the plurality of imaging elements arranged two-dimensionally on the sensor panel of the radiographic imaging apparatus, including at least two rows and two columns of defective pixels and distributed in a two-dimensional cluster shape Storage means for storing information on defective pixels of
The information of the defective pixel related to the radiographic image capturing apparatus is read from the storage unit, and the image data output from each defective pixel is extracted from the image data transmitted from the radiographic image capturing apparatus. A console that respectively replaces the corrected image data at the pixel position of each defective pixel calculated based on the information;
With
The information on the defective pixels includes information on pixel positions of the defective pixels on the sensor panel and pixels up to the normal pixels closest to the defective pixels in the row direction and the column direction on the sensor panel. Number information,
Based on the information on the defective pixels, the console applies the image data and the number of pixels of the normal pixels closest to the defective pixels in the row direction, and the defective pixels in the column direction. The corrected image data is calculated using the image data and the number of pixels of the normal pixels closest to each other.

  According to the radiographic image capturing apparatus and radiographic image capturing system of the system of the present invention, information on a plurality of defective pixels distributed in a two-dimensional cluster shape on the sensor panel of the radiographic image capturing apparatus is created in advance, and based on the information. Then, the corrected image data at the pixel position of each defective pixel is calculated, and the image data output from each defective pixel is replaced with the corrected image data. Therefore, even when defective pixels exist in a two-dimensional cluster form on the sensor panel, it is possible to effectively correct the defective pixel by replacing the image data at the pixel positions of the defective pixels with the corrected image data. .

  Further, at the time of correction, searching for each normal pixel closest to each defective pixel in the row direction and column direction and determining each image data thereof requires a lot of time for the correction process. As in the radiographic imaging apparatus and radiographic imaging system of the present invention, the pixel position of each normal pixel that is closest in the row direction and the column direction of each defective pixel, and each pixel that is normal from each defective pixel By specifying the number of pixels up to this point in advance, the correction process can be performed at high speed.

It is a perspective view which shows the radiographic imaging apparatus which concerns on this embodiment. It is sectional drawing which follows the XX line in FIG. It is an enlarged view which shows the example of the scintillator which has a columnar crystal structure. It is a top view which shows the structure of the board | substrate of the sensor panel which concerns on this embodiment. FIG. 5 is an enlarged view illustrating a configuration of an image pickup element including a photodiode and a thin film transistor formed in a small region on the substrate of FIG. 4. It is sectional drawing which follows the YY line in FIG. It is a side view explaining the sensor panel to which a COF, a PCB board, etc. were attached. It is an expanded sectional view of the image sensor concerning this embodiment. It is a figure showing the equivalent circuit schematic of the radiographic imaging apparatus which concerns on this embodiment. It is a figure which shows the example of the table in which the information of the defective pixel which concerns on this embodiment was described. It is a figure showing an example of a plurality of defective pixels distributed in the shape of a two-dimensional cluster on a sensor panel. FIG. 12 is a diagram illustrating four normal pixels that are closest to each other in the row direction and the column direction of one defective pixel in the two-dimensional cluster-like defective pixel in FIG. 11. FIG. 12 is a diagram illustrating four normal pixels that are closest to each other in the row direction and the column direction of one defective pixel in the two-dimensional cluster-like defective pixel in FIG. 11. It is a perspective view explaining that a sensor panel is inserted in a rectangular tube-shaped housing main-body part. It is a figure which shows the whole structure of the radiographic imaging system which concerns on this embodiment. It is a figure explaining the point defect, the line defect, etc. which exist on a sensor panel. It is a figure which shows the example of the some defective pixel which generate | occur | produced on the sensor panel in the shape of a two-dimensional cluster.

  Embodiments of a radiographic imaging apparatus and a radiographic imaging system according to the present invention will be described below with reference to the drawings. However, the present invention is not limited to the following illustrated examples.

  In the following, the case where the radiographic image capturing apparatus is portable will be described. However, the present invention is not limited to this case, and can be applied to, for example, a radiographic image capturing apparatus formed integrally with a support base. . In the following description, a radiation image capturing apparatus is provided with a scintillator or the like, converts emitted radiation into electromagnetic waves of other wavelengths such as visible light, and irradiates them, and converts them into image data that is an electrical signal with a photodiode. Although an indirect type radiographic imaging apparatus will be described, the present invention can also be applied to a so-called direct type radiographic imaging apparatus that directly detects radiation with a radiation detection element without using a scintillator or the like.

[Radiation imaging equipment]
First, the radiographic imaging device according to the present embodiment will be described. FIG. 1 is an external perspective view of the radiographic image capturing apparatus according to the present embodiment, and FIG. 2 is a cross-sectional view taken along line XX of FIG. As shown in FIGS. 1 and 2, the radiographic imaging apparatus 1 according to the present embodiment is configured by housing a sensor panel 40 including a scintillator 3, a substrate 4, and the like in a housing 2. Yes.

  In the present embodiment, the housing 2 is a so-called monocoque type that includes a housing body 2a formed in a rectangular tube shape and lid members 2b and 2b that cover and close the openings at both ends of the housing body 2a. Is formed. The housing body 2a is provided with a surface R (hereinafter referred to as a radiation incident surface R) that receives radiation, and is made of a material such as a carbon plate or plastic that transmits radiation.

  One lid member 2b is provided with a power switch 36, a terminal 37 for connecting the radiographic imaging apparatus 1 to an external device (not shown) by a wire, indicators 38 for displaying various operation statuses, and the like. ing. In addition, the lid member 2b is provided with an antenna device 39 that is a communication unit for the radiographic imaging device 1 to transmit and receive data and signals to and from an external device in a wireless manner.

  The location where the antenna device 39 is provided is not limited to one lid member 2b of the housing 2 as in the present embodiment, but may be provided at other positions. Further, the number of antenna devices 39 is not necessarily limited to one, and a necessary number is appropriately provided.

  As shown in FIG. 2, a sensor panel 40 is accommodated on the lower side of the substrate 4 inside the housing 2, and a PCB substrate on which an electronic component 32 and the like are disposed on the base 31 of the sensor panel 40. 33, the buffer member 34, etc. are attached. Further, on the substrate 4 of the sensor panel 40 and the radiation incident surface R side of the scintillator 3, a glass substrate 35 for protecting them is disposed.

  As shown in the enlarged view of FIG. 3, for example, the scintillator 3 is formed on a support 3b formed of various polymer materials (polymers) such as a cellulose acetate film, a polyester film, and a polyethylene terephthalate film. The columnar crystals of the phosphor 3a are grown by vapor phase growth methods such as sputtering and chemical vapor deposition (CVD). The support 3b of the scintillator 3 is affixed and fixed to the glass substrate 35 described above.

  The scintillator 3 is, for example, one that converts and outputs an electromagnetic wave having a wavelength of 300 to 800 nm, that is, an electromagnetic wave centered on visible light when receiving incident radiation. In the scintillator 3, the acute-angled tip end Pa side of the columnar crystal of the phosphor 3 a is bonded to a detection unit P described later of the substrate 4.

  In this embodiment, the substrate 4 of the sensor panel 40 is formed of a glass substrate. As shown in FIG. 4, a plurality of scanning lines 5 and a plurality of scanning lines 5 are provided on a surface 4 a of the substrate 4 facing the scintillator 3. The plurality of signal lines 6 are arranged so as to cross each other. A photodiode 7 is provided in each small region r defined by the plurality of scanning lines 5 and the plurality of signal lines 6 on the surface 4 a of the substrate 4.

  Thus, the photodiodes 7 are two-dimensionally arranged on the substrate 4 of the sensor panel 40, and the entire region r in which the plurality of photodiodes 7 are provided, that is, the region indicated by the alternate long and short dash line in FIG. The detection unit P of the sensor panel 40 is used.

  In the present embodiment, the radiation generated from the radiation incident surface R is converted by the scintillator 3 and output, that is, the amount of electromagnetic waves, that is, the amount of light (increased according to the amount of radiation incident on the scintillator 3). Although the photodiode 7 to be used is used, for example, a phototransistor or the like can also be used.

  Each photodiode 7 is connected to a source electrode 8s of a TFT (thin film transistor) 8 serving as a switching element, as shown in the enlarged views of FIGS. The drain electrode 8 d of the TFT 8 is connected to the signal line 6.

  When the TFT 8 is turned on, that is, when a voltage for reading a signal is applied to the gate electrode 8g and the gate of the TFT 8 is opened, the charge accumulated in the photodiode 7 is released to the signal line 6. It is supposed to let you. Here, the structure of the photodiode 7 and the TFT 8 in this embodiment will be briefly described with reference to a cross-sectional view shown in FIG. 6 is a cross-sectional view taken along line YY in FIG.

A gate electrode 8g of a TFT 8 made of Al, Cr or the like is formed on the surface 4a of the substrate 4 so as to be integrally laminated with the scanning line 5, and silicon nitride (laminated on the gate electrode 8g and the surface 4a). The first electrode 74 of the photodiode 7 is connected to the upper portion of the gate electrode 8g on the gate insulating layer 81 made of SiN _x ) or the like via the semiconductor layer 82 made of hydrogenated amorphous silicon (a-Si) or the like. The source electrode 8s and the drain electrode 8d formed integrally with the signal line 6 are laminated.

The source electrode 8s and the drain electrode 8d are divided by a first passivation layer 83 made of silicon nitride (SiN _x ) or the like, and the first passivation layer 83 covers both electrodes 8s and 8d from above. In addition, ohmic contact layers 84a and 84b formed in an n-type by doping hydrogenated amorphous silicon with a group VI element are laminated between the semiconductor layer 82 and the source electrode 8s and the drain electrode 8d, respectively. The TFT 8 is formed as described above.

  In the photodiode 7 portion, an auxiliary electrode 72 is formed by laminating Al, Cr or the like on the insulating layer 71 formed integrally with the gate insulating layer 81 on the surface 4 a of the substrate 4. A first electrode 74 made of Al, Cr, Mo or the like is laminated on the auxiliary electrode 72 with an insulating layer 73 formed integrally with the first passivation layer 83 interposed therebetween. The first electrode 74 is connected to the source electrode 8 s of the TFT 8 through the hole H formed in the first passivation layer 83.

  On the first electrode 74, an n layer 75 formed in an n-type by doping a hydrogenated amorphous silicon with a group VI element, an i layer 76 which is a conversion layer formed of hydrogenated amorphous silicon, and a hydrogenated amorphous A p layer 77 formed by doping a group III element into silicon and forming a p-type layer is formed by laminating sequentially from below. The order of stacking the p layer 77, the i layer 76, and the n layer 75 may be reversed.

  On the p layer 77, a second electrode 78 made of a transparent electrode such as ITO is laminated and formed so that the irradiated electromagnetic wave reaches the i layer 76 and the like. The photodiode 7 is formed as described above. In the present embodiment, as described above, a case where a so-called pin-type photodiode formed by stacking the p layer 77, the i layer 76, and the n layer 75 is used as the photodiode 7 has been described. 7 is not limited to such a pin type.

A bias line 9 for applying a reverse bias voltage to the photodiode 7 is connected to the upper surface of the second electrode 78 of the photodiode 7 via the second electrode 78. The second electrode 78 and the bias line 9 of the photodiode 7, the first electrode 74 extending to the TFT 8 side, the first passivation layer 83 of the TFT 8, that is, the upper surface portion of the photodiode 7 and TFT 8 are on the upper side. Is covered with a second passivation layer 79 made of silicon nitride (SiN _x ) or the like.

  As shown in FIGS. 4 and 5, in this embodiment, one bias line 9 is connected to a plurality of photodiodes 7 arranged in a row, and each bias line 9 is connected to a signal line 6. They are arranged in parallel. In addition, each bias line 9 is bound to one connection 10 at a position outside the detection portion P of the substrate 4.

  In the present embodiment, the connection lines 10 of the scanning lines 5, the signal lines 6, and the bias lines 9 are respectively connected to input / output terminals (also referred to as pads) 11 provided near the edge of the substrate 4. As shown in FIG. 7, a COF (Chip On Film) 12 in which a chip such as an IC 12a is incorporated in each input / output terminal 11 is an anisotropic conductive adhesive film (Anisotropic Conductive Film) or anisotropic conductive paste (Anisotropic paste). It is connected via an anisotropic conductive adhesive material 13 such as Conductive Paste). The COF 12 is routed to the back surface 4b side of the substrate 4 and connected to the PCB substrate 33 described above on the back surface 4b side.

  Further, a transparent resin or the like is applied to the portion where the photodiodes 7 are arranged on the surface 4a of the substrate 4, that is, the detection portion P, to protect the photodiodes 7 and form a flat surface. Is formed. The scintillator 3 is bonded to the planarization layer 7a.

  In the present embodiment, the sensor panel 40 of the radiographic image capturing apparatus 1 is thus formed. As shown in the enlarged sectional view of FIG. 8, in this embodiment, one photodiode 7 and the phosphor 3a portion of the scintillator 3 thereabove, and one TFT 8 and the like not shown in FIG. One image sensor 41 is formed. In FIG. 8, the photodiode 7 is shown in a simplified manner.

  Here, a circuit configuration of the sensor panel 40 of the radiographic image capturing apparatus 1 will be described. FIG. 9 is an equivalent circuit diagram of the sensor panel 40 of the radiation image capturing apparatus 1 according to the present embodiment.

  As described above, the photodiode 7 of each imaging element 41 of the sensor panel 40 has the second electrode 78 connected to the bias line 9 and the connection 10, respectively, and the connection 10 is connected to the reverse bias power supply 14. . The reverse bias power supply 14 supplies a reverse bias voltage to be applied to each photodiode 7 via the connection 10 and each bias line 9. The reverse bias power supply 14 is connected to a control means 22 described later, and the control means 22 controls the reverse bias voltage applied to each photodiode 7 from the reverse bias power supply 14.

  The first electrode 74 of the photodiode 7 of each imaging element 41 is connected to the source electrode 8s (denoted as S in FIG. 9) of the TFT 8, and the gate electrode 8g (in FIG. 9) of each TFT 8. G) is connected to each scanning line 5 extending from the scanning drive circuit 15. Further, the drain electrode 8 d (denoted as D in FIG. 9) of each TFT 8 is connected to each signal line 6.

  Each signal line 6 is connected to each readout circuit 17 formed in the readout IC 16. Note that a predetermined number of readout circuits 17 are provided in the readout IC 16, and by providing a plurality of readout ICs 16, readout circuits 17 corresponding to the number of signal lines 6 are provided.

  The readout circuit 17 includes an amplifier circuit 18, a correlated double sampling circuit 19, and an A / D converter 20. In the present embodiment, one amplification circuit 18 and one correlated double sampling circuit 19 are provided for each signal line 6, but the A / D converter 20 is shared by a plurality of circuits. . The correlated double sampling circuit 19 is represented as CDS in FIG.

  At the time of radiographic image capturing, radiation is irradiated on a radiation incident surface R of the housing 2 of the radiographic image capturing apparatus 1 in a state where imaging target parts such as a chest and a leg of a patient are arranged as subjects. At that time, the gate electrode 8g of the TFT 8 of each image sensor 41 is turned off and the gate is closed. In this state, when radiation transmitted through the subject is irradiated, the radiation transmitted through the radiation incident surface R enters the scintillator 3 (not shown in FIG. 9), and the scintillator 3 converts the radiation into electromagnetic waves. An electromagnetic wave enters the photodiode 7 of the image sensor 41.

  When the incident electromagnetic wave reaches the i layer 76 of the photodiode 7 (see FIG. 6), an electron-hole pair is generated according to the amount of electromagnetic wave incident in the i layer 76 (that is, the radiation dose), and vice versa. According to a predetermined potential gradient formed in the photodiode 7 by application of the bias voltage, one of the generated electrons and holes (in this embodiment, a hole) moves to the second electrode 78 side, and the other Charge (electrons in this embodiment) moves to the first electrode 74 side and is accumulated in the vicinity of the first electrode 74.

  When the radiation irradiation is stopped and the radiographic image capturing is completed, the reading operation is started. In the readout operation, a signal readout voltage is applied from the scanning drive circuit 15 to the gate electrode 8g of the TFT 8 of each image sensor 41 via the scanning line 5, the gate of the TFT 8 is turned on, and the photo of the image sensor 41 is turned on. The electric charge accumulated in the diode 7 is emitted from the drain electrode 8d to the signal line 6 through the source electrode 8s of the TFT 8.

  In the readout circuit 17, when the charge accumulated in the photodiode 7 is released from the image pickup device 41 through the signal line 6, the charge is converted into charge-voltage for each image pickup device 41 and amplified into image data F. After the conversion, the image data F output from each correlated double sampling circuit 19 is sequentially transmitted to the A / D converter 20 via the analog multiplexer 21, and is sequentially converted into a digital value by the A / D converter 20 and read out. It is like that.

  The control means 22 is composed of a microcomputer equipped with a CPU (Central Processing Unit) or the like or a dedicated control circuit, and controls the operation of each member of the radiographic image capturing apparatus 1. The control means 22 is connected to a storage means 23 composed of a RAM (Random Access Memory) or the like.

  As described above, the control unit 22 controls the reverse bias power supply 14 to control the reverse bias voltage applied to the photodiode 7 of each image sensor 41 or applies a signal readout voltage from the scanning drive circuit 15. Image data F is read from each image sensor 41 by switching the scanning line 5 or controlling the amplification circuit 18 and the correlated double sampling circuit 19 in each readout circuit 17.

  Each image data F read from each image sensor 41 is stored in the storage unit 23 in accordance with an instruction from a memory controller (not shown) controlled by the control unit 22.

  Further, the above-described antenna device 39 is connected to the control means 22, and data and signals are transmitted / received to / from an external device via the antenna device 39. Furthermore, the control means 22 controls supply of electric power from the battery 42 built in the apparatus to each member such as each image sensor 41. A connection terminal 43 for charging the battery 42 by supplying electric power from an external device is attached to the battery 42.

  By the way, as described above, each of the imaging elements 41 of the sensor panel 40 usually includes one that outputs abnormal image data Fd constantly or with a certain probability. The pixels corresponding to the image sensor 41 that outputs the abnormal image data Fd, that is, the defective pixels dp, exist in a two-dimensional cluster form including at least two rows and two columns of defective pixels dp and continuing in the row direction and the column direction. There may be.

  In the present embodiment, a two-dimensional cluster including at least two rows and two columns of defective pixels dp among the pixels p corresponding to the plurality of imaging elements 41 arranged two-dimensionally on the sensor panel 40 as described above. The information of the plurality of defective pixels dp distributed in a shape is grasped in advance at the time of manufacturing the radiographic image capturing apparatus 1 or the like, and the ROM (Read Only Memory) (not shown) in the control unit 22 stores these defective pixels dp. Information is stored in advance.

  In the present embodiment, as information on the defective pixel dp, information on the pixel position (i, j) of each defective pixel dp on the sensor panel 40 and a row of an array of two-dimensional pixels on the sensor panel 40 are used. Information on the number of pixels up to each normal pixel p closest to each defective pixel dp in the direction and the column direction is known in advance. Then, in the ROM, as information of the defective pixel dp, the pixels from the pixel position (i, j) of each defective pixel dp as shown in FIG. 10 and the normal pixels A to D closest to each defective pixel dp are shown. A number T of tables T is stored in advance.

  For example, it is assumed that there are a plurality of defective pixels dp distributed in a two-dimensional cluster as shown in FIG. 11 on the sensor panel 40. Hereinafter, for convenience, the pixel position (i, j) of the substantially central defective pixel dp is temporarily represented as (m, n), and the defective pixel dp such as the pixel position (m, n) is represented as dp (m, n). Let's represent. In addition, the normal left and right pixels closest in the row direction of the defective pixel dp, that is, the horizontal direction in the drawing, are denoted as A and B, respectively, and the normal vertical direction that is closest to the vertical direction in the column direction of the defective pixel dp, that is, the drawing. These pixels are denoted by C and D, respectively.

  In the cluster-like defective pixel dp as shown in FIG. 11, as shown in FIG. 12, for example, the number of pixels to each normal pixel A closest to the left in the row direction of the defective pixel dp (m−3, n + 1). a is 1, the number b of pixels to the normal pixel B closest to the right side is 1, and the number of pixels c to the normal pixel C closest to the upper side in the column direction is also 1. The number d of pixels to the normal pixels D closest to the lower side is 5. Therefore, for the defective pixel dp (m−3, n + 1), as shown in the table T of FIG. 10, the pixel numbers a to d of the closest normal pixels A to D are 1, 1, 1, 5

  Further, as shown in FIG. 13, for example, the number of pixels a up to each normal pixel A closest to the left side in the row direction of the defective pixel dp (m, n) is 3, and the normal number closest to the right side is normal. The number of pixels b to each pixel B is 2, the number of pixels c to the normal pixel C closest to the upper side in the column direction is 3, and the pixel to the normal pixel D closest to the lower side The number d is 2. Therefore, for the defective pixel dp (m, n), as shown in the table T of FIG. 10, the number of pixels a to d to the normal pixels A to D closest to each other is 3, 2, 3, 2, respectively. Become.

  Similarly, with respect to the other defective pixels dp in the cluster-like defective pixel dp as shown in FIG. 11, the number of pixels from the pixel position (i, j) and the normal pixels A to D closest to the defective pixels dp in the same manner. A table T is created in association with a to d.

  As described above, the control unit 22 irradiates the radiation image capturing apparatus 1 with radiation and performs radiation image capturing, and then reads out the image data F from each imaging element 41 by the readout circuit 17 at the time of reading. Then, the image data F for each of the image pickup devices 41 is temporarily stored in the storage unit 23.

The control means 22 functions as the correction means of the present invention. When the control means 22 stores the image data F for each image sensor 41 in the storage means 23, the control means 22 is then stored in the ROM. The corrected image data F ^* (i, j) at the pixel position (i, j) of each defective pixel dp is calculated based on the information on the defective pixel dp with reference to the above table T, and the corrected image The data F ^* (i, j) is used to replace the image data Fd (i, j) output from each defective pixel dp.

At that time, based on the information of the defective pixel dp, the control unit 22 sets the normal image data F (A), F (B) of each normal pixel A, B closest to each defective pixel dp in the row direction, and The corrected image data F ^* (i, j) is calculated using the image data F (C) and F (D) of the normal pixels C and D closest to each other in the column direction. .

As a specific method for calculating the corrected image data F ^* (i, j) at the pixel position (i, j) of the defective pixel dp, the row direction and the column are assigned to each defective pixel dp based on the information of the defective pixel dp. What is necessary is just to calculate using each image data F (A) -F (D) of each normal pixel A-D closest to the direction, and is not limited to a specific method.

For example, when the above-described linear interpolation method is used, first, when linear interpolation is performed in the row direction, the corrected image data F ^* row (i, j) in the row direction at the pixel position (i, j) of the defective pixel dp. Is the number of pixels a, b and the normal image data F (A), F (B) of each pixel A, B,
F ^* row (i, j) = F (A) + {F (B) −F (A)} × a / (a + b)
= {B * F (A) + a * F (B)} / (a + b) (1)
It can be calculated with.

In the linear interpolation in the column direction, the corrected image data F ^* column (i, j) in the column direction at the pixel position (i, j) of the defective pixel dp has the number of pixels c and d and each normal pixel C. , D image data F (C), F (D),
F ^* column (i, j) = F (C) + {F (D) −F (C)} × c / (c + d)
= {D * F (C) + c * F (D)} / (c + d) (2)
It can be calculated with.

Then, the defective pixel dp is obtained by, for example, simply averaging the F ^* row (i, j) and F ^* column (i, j) calculated in this way, or performing weighted averaging according to the characteristics of the sensor panel 40 or the like. The corrected image data F ^* (i, j) at the pixel position (i, j) can be calculated.

For example, it is also possible to calculate the corrected image data F ^* (i, j) at the pixel position (i, j) of the defective pixel dp using a spline curve. That is, as described above, four normal pixels A to D are specified on the left and right in the row direction and on the top and bottom in the column direction with respect to the defective pixel dp (i, j).

Therefore, for example, consider a three-dimensional space having three components of i-coordinate, j-coordinate and image data F of each normal pixel, and pass through four points on the three-dimensional space corresponding to normal pixels A to D, for example 3 A dimensional spline curve is calculated, and based on this, corrected image data F ^* (i, j) at the pixel position (i, j) of the defective pixel dp can be calculated. At this time, since four different normal pixels A to D are specified for each defective pixel dp (i, j), a spline curve is also calculated for each defective pixel dp (i, j). Is done.

In the present embodiment, the control means 22 uses the corrected image data F ^* (i, j) calculated as described above and the image data Fd (i, j) output from each defective pixel dp (i, j). Are replaced respectively. Separately from the raw image data (raw data) read out by the readout circuit 17 and stored in the storage means 23, the normal pixel p is located at the pixel position (i, j) of the normal pixel p. The normal image data F (i, j) output from is assigned, and the corrected image data F ^* (i, j) is assigned to the pixel position (i, j) of the defective pixel dp. Is stored in the storage means 23.

  In this embodiment, the corrected image data is stored in the storage unit 23 separately from the raw data as described above. However, the corrected image data is overwritten and saved on the raw data. It is also possible to delete the abnormal image data Fd (i, j) output from the defective pixel dp. In addition to the corrected image data, only the abnormal image data Fd (i, j) of the defective pixel dp can be extracted from the raw data and stored.

  In this embodiment, an operator such as a radiographer confirms at an early stage whether or not the photographing position of the subject in the image photographed by the radiation image photographing apparatus 1 is appropriate, and determines whether or not re-imaging is necessary. For example, the control unit 22 thins out pixels from the raw data at a predetermined rate and generates thinned image data in which the data amount is reduced to, for example, about 1/16 of the raw data. It has become.

  That is, the control unit 22 also functions as a thinned image data generation unit of the present invention. Then, the thinned image data is transmitted to, for example, a console 58 (see FIG. 15) of the radiation image capturing system 50 described later in a short time and displayed on the display screen 58a, thereby prompting the operator whether or not re-imaging is necessary. Let me judge.

  At this time, the thinned image data is only required to be able to confirm whether the shooting position of the subject in the shot image is appropriate as described above. There is no need to perform a process for calculating corrected image data. Therefore, in the present embodiment, when the control unit 22 generates thinned image data from the image data F of each image sensor 41 read by the read circuit 17, calculation of corrected image data is performed on the thinned image data. It is configured not to perform processing.

  Next, the operation of the radiation image capturing apparatus 1 according to this embodiment will be described.

  Possible causes of defective pixels dp distributed in a two-dimensional cluster form as shown in FIG. 11 on the sensor panel 40 include, for example, the step of stacking the photodiodes 7 shown in FIG. In the manufacturing stage of the scintillator 3 as shown, mechanical stress is applied to the photodiode 7 and the columnar crystal phosphor 3a of the scintillator 3 in a relatively wide area corresponding to a two-dimensional cluster distribution. This may occur when the planarization layer 7a formed by applying a resin or the like on the photodiode 7 shown in FIG. 8 is contaminated in a relatively large area.

  Further, in the bonding process of the scintillator 3 and the planarizing layer 7a shown in FIG. 8, relatively large foreign matter is mixed between the scintillator 3 and the planarizing layer 7a, or the columnar crystal phosphor 3a of the scintillator 3 is used. However, it can also occur when the tip Pa is damaged in a relatively wide range due to an external force or the like from a direction orthogonal to the crystal growth direction.

  Further, in the present embodiment, as described above, the housing body 2a of the housing 2 is formed in a rectangular tube shape, and has a relatively large area such as 14 inches × 17 inches as shown in FIG. The sensor panel 40 is inserted and stored in the rectangular tube-shaped housing main body 2a. At that time, in order to protect the sensor panel 40 housed in the housing body 2a from external force and prevent the sensor panel 40 from being damaged, a cushioning material 2c or the like is provided inside the housing body 2a. When the sensor panel 40 is inserted into the housing body 2a, it may be necessary to push it in with a relatively large pressing force.

  In such a case, stress is applied to the flat sensor panel 40 in the direction in which it is pressed or curved, and the image sensor 41 having a relatively large area is damaged, resulting in a two-dimensional cluster defect. Pixel dp may occur.

  Therefore, after the sensor panel 40 is inserted (press-fitted) into the housing main body 2a to produce the radiographic imaging apparatus 1, the radiographic imaging apparatus 1 is actually irradiated with radiation at the time of shipment from the factory. The value of each image data F output from each image sensor 41 is analyzed, and an inspection is performed as to whether or not a plurality of defective pixels dp are generated in a two-dimensional cluster form on the sensor panel 40.

  At that time, as described above, the defective pixel dp may output abnormally abnormal image data Fd in some cases, but abnormal image data Fd may be output with a certain probability. It is desirable to inspect with multiple irradiations.

  When a plurality of defective pixels dp are generated in a two-dimensional cluster shape, information on the defective pixels dp, that is, the pixel position (i, j) of each defective pixel dp on the sensor panel 40. Information and information on the number of pixels a to d of normal pixels A to D closest to each defective pixel dp in the row direction and the column direction of the two-dimensional pixel array on the sensor panel 40 are controlled. The information is stored in advance in the ROM of the means 22 as the table T shown in FIG.

  Further, when radiation images are captured, if radiation is irradiated in a state where a subject is placed on the radiation incident surface R of the radiation image capturing apparatus 1, the radiation dose applied to the photodiodes 7 of the respective image sensors 41 is determined according to the radiation dose. Charge is accumulated. When the reading operation is started, image data (raw data) is read from each image sensor 41 and stored in the storage unit 23.

Then, the control means 22 which is a correction means reads out the table T as shown in FIG. 10 from the ROM, refers to it and based on the information of the defective pixel dp, the corrected image data F ^* ( The corrected image data F ^* (i, j) is calculated for each defective pixel dp (i, j) distributed in a two-dimensional cluster using the calculation method of i, j), and the calculated correction is performed. The image data Fd (i, j) output from each defective pixel dp (i, j) is replaced with the image data F ^* (i, j), respectively, and the pixel position (i, j) of the normal pixel p is A correction in which normal image data F (i, j) output from the normal pixel p is assigned and corrected image data F ^* (i, j) is assigned to the pixel position (i, j) of the defective pixel dp. Stored image data in the storage means 23 That.

  In the present embodiment, the above-described corrected image data is automatically created following the reading operation, but it is configured to wait for an instruction from an operator such as a radiologist. Is also possible.

As described above, according to the radiographic image capturing apparatus 1 according to the present embodiment, the control unit 22 serving as the correction unit has a plurality of defective pixels dp distributed in a two-dimensional cluster form on the sensor panel 40 that is created in advance. The corrected image data F ^* (i, j) at the pixel position (i, j) of each defective pixel dp is calculated based on the information of the defective pixel dp, and each defective pixel dp is calculated using the corrected image data F ^* (i, j). The image data F (i, j) output from (i, j) is replaced.

Therefore, even when the defective pixels dp exist in the two-dimensional cluster form as shown in FIG. 11 on the sensor panel 40, the image data F (i, j) at the pixel position (i, j) of these defective pixels dp. ) Are replaced with the corrected image data F ^* (i, j), respectively, and can be corrected effectively.

  Further, at the time of correction, normal pixels A to D that are closest to each other in the row direction and the column direction of each defective pixel dp are searched and their respective image data F (A) to F (D) are determined. Although a great deal of time is required for the correction process, the normal pixels A to D that are closest to each other in the row direction and the column direction of each defective pixel dp as in the radiographic image capturing apparatus 1 according to the present embodiment. By specifying the position and the number of pixels a to d from each defective pixel dp to each normal pixel A to D in advance, the correction process can be performed at high speed.

  Note that even when the above-described image sensor 41 on the sensor panel 40 has a point defect or a line defect as described above, the image data F (i, j) output from the defective pixel dp is corrected. Needless to say. However, when creating thinned-out image data as described above, an operator such as a radiographer confirms at an early stage whether or not the shooting position of the subject in the image is appropriate, and determines whether or not re-shooting is necessary. Therefore, it is possible to configure so that point defects and line defects are not corrected.

[Radiation imaging system]
In the above embodiment, the control unit 22 of the radiographic image capturing apparatus 1 functions as a correction unit, refers to the table T stored in the ROM or the like, and based on the information of the defective pixel dp, the pixel position of each defective pixel dp. The corrected image data F ^* (i, j) in (i, j) is calculated, and the image data F (i, j) output from each defective pixel dp is replaced and corrected. Explained the case.

  However, when the radiographic image capturing apparatus 1 includes the battery 42 (see FIG. 9) as in the above-described embodiment, for example, the radiographic image capturing apparatus 1 reads out image data F (i, j). If the image data output from each defective pixel dp is corrected by an external device, the power consumption of the battery 42 of the radiographic image capturing apparatus 1 is reduced accordingly.

  Therefore, it is possible to increase the number of times the radiographic imaging apparatus 1 is used for radiographic imaging per charge of the battery 42, and the radiographic imaging apparatus 1 can be used efficiently. Hereinafter, an embodiment of the radiographic imaging system configured as described above will be described.

  Hereinafter, the case where the radiographic imaging apparatus is portable will be described. However, the present invention is not limited to that case in the present embodiment, and for example, the radiographic imaging apparatus integrally formed with the support base. It can also be applied to. The present invention can also be applied to a so-called direct type radiographic imaging apparatus.

  FIG. 15 is a diagram illustrating an overall configuration of a radiographic image capturing system according to the present embodiment. The radiographic imaging system 50 of this embodiment is a system that assumes radiographic imaging performed in, for example, a hospital or clinic, and can be employed as a system that captures medical diagnostic images as radiographic images.

  As shown in FIG. 15, the radiographic image capturing system 50 includes, for example, an imaging room R <b> 1 that irradiates radiation and shoots a subject such as an imaging target portion of a patient (not shown), and an operator such as a radiographer irradiates the subject. It is arranged in the anterior chamber R2 for performing various operations such as control of radiation to be performed and image processing of acquired radiographic images. The imaging room R1 is often shielded with lead or the like so that radiation does not leak outside.

  Although the configuration of the radiographic image capturing apparatus 1 is as described above, in the present embodiment, the radiographic image capturing apparatus 1 preferably further has the following configuration.

  Specifically, a tag (not shown) is incorporated in the radiation image capturing apparatus 1. In this embodiment, a tag called a so-called RFID (Radio Frequency IDentification) tag is used as the tag, and the tag stores a control circuit that controls each part of the tag and a storage that stores unique information of the radiographic imaging apparatus 1. The part is built in compactly. The unique information includes, for example, a cassette ID, scintillator type information, size information, resolution, and the like as identification information assigned to the radiation image capturing apparatus 1.

  Moreover, in this embodiment, the radiographic imaging device 1 is comprised by the dimension based on JISZ4905 (corresponding international standard is IEC 60406) in the cassette for conventional screens / films. That is, the thickness in the radiation incident direction is within a range of 15 mm + 1 mm to 15 mm-2 mm, and is 8 inches × 10 inches, 10 inches × 12 inches, 11 inches × 14 inches, 14 inches × 14 inches, 14 inches × 17 inches. (Half cut size) etc. are prepared.

  Thus, in this embodiment, since the radiographic imaging device 1 is formed in accordance with the JIS standard relating to the screen / film cassette, a CR cassette formed in accordance with the JIS standard can be loaded in the same manner. The radiographic imaging device 1 can be used by being mounted on a bucky device 51 for a CR cassette.

  In addition, this invention is not limited to the case where the radiographic imaging device 1 is formed in conformity with the JIS standard as described above, or the case where the bucky device 51 for CR cassette is used as the bucky device 51. However, if the bucky device 51 for CR cassette is used as the bucky device 51, it is possible to carry out radiographic imaging by loading both the radiographic imaging device 1 as FPD and the conventional CR cassette into the bucky device 51. It becomes.

  On the other hand, the radiographic image capturing apparatus 1 can be used in a so-called independent state that is not loaded in the bucky apparatus 51. That is, the radiographic image capturing apparatus 1 is arranged in a single state, for example, on a support stand provided in the radiographing room R1 or a bucky apparatus 51B for lying position imaging, and a subject on the radiation incident surface R (see FIG. 1). It can be used by placing the hand, leg, etc., which is the imaging target part of the patient, or inserting it between the waist, leg, etc. of the patient lying on the bed and the bed, for example It has become. In this case, for example, radiation image capturing is performed by irradiating the radiation image capturing apparatus 1 with radiation from a portable radiation source 52B (see FIG. 15) or the like through the subject.

  The bucky device 51 is provided with a cassette holding portion 51a for holding the radiographic image capturing device 1 in a predetermined position, and the radiographic image capturing device 1 can be loaded into the cassette holding portion 51a. Further, in the present embodiment, as the bucky device 51, there are provided a bucky device 51A for standing position shooting and a bucky device 51B for standing position shooting.

  It should be noted that in the bucky device 51A for standing position photography and the bucky device 51B for standing position photography, for example, it is possible to appropriately adjust the position of the device itself or the height of the cassette holding portion 51a with respect to the bucky device body. It is the same as that of a known Bucky device.

  In the imaging room R1, at least one radiation source 52 including an X-ray tube that irradiates the radiation image capturing apparatus 1 with radiation through a subject is provided. In the present embodiment, one radiation source 52A is shared by the bucky devices 51A and 51B for standing position shooting and standing position shooting. It should be noted that it is also possible to configure each of the bucky devices 51A and 51B in association with a separate radiation generating device.

  The radiation source 52A is arranged suspended from the ceiling of the imaging room R1, for example, and is set up based on an instruction from an operation console 56 (to be described later) at the time of imaging. And the direction of the radiation is adjusted so that the radiation direction is in a predetermined direction.

  Further, in the present embodiment, a portable radiation source 52B that is not associated with the standing-up imaging device 51A or the lying-up imaging device 51B is also provided, and the portable radiation source 52B has an imaging function. It can be carried to any place in the room R1, and radiation can be emitted in any direction.

  In the present embodiment, the portable radiation source 52B is also set up based on an instruction from the console 56. In addition to this, for example, the operator manually sets up the radiation source 52B. It is also possible to configure to set up by transmitting a radio signal from the image capturing apparatus 1 to the portable radiation source 52B.

  A radio access point (base station) provided with a radio antenna 53 for relaying radio communication between the radiographic imaging apparatus 1 and the console 58, the switch means 55, etc., in a corner of the radiographing room R1. 54 is installed. FIG. 15 shows the case where the wireless access point 54 is provided near the entrance of the imaging room R1, but the present invention is not limited to this, and wireless communication with the antenna device 39 and the like of the radiographic image capturing apparatus 1 is possible. It is installed at an appropriate position where possible.

  In the present embodiment, the wireless access point 54 is connected to each of the bucky devices 51A and 51B via a cable or the like, and communicates with the bucky devices 51A and 51B or the radiographic imaging device 1 loaded therein and the console 58 or the like. It can also be performed by a wired system.

  On the other hand, the front room R2 is provided with an operation console 56 provided with a switch means 55 for instructing the start of radiation irradiation from the radiation source 52. The console 56 includes a computer having a general-purpose CPU (Central Processing Unit), a computer having a dedicated processor, or the like. In the present embodiment, the console 56 is connected to the switch means 55 and the radiation source 52 and also to the console 58.

  In the present embodiment, the switch means 55 is provided with stroke detecting means 60 for detecting that a button part (not shown) of the switch means 55 is pressed by the operator, and the button part of the switch means 55 is pressed. When a signal instructing the start of radiation irradiation is transmitted from the console 56 to the radiation source 52, at the same time, the stroke detection means 60 detects that the button part of the switch means 55 has been pressed and that the press has been released. Thus, a radiation irradiation start signal and an end signal are transmitted to the radiation image capturing apparatus 1 via the wireless access point 54.

  In the vicinity of the entrance of the front chamber R2, a tag reader 57 for exchanging information with the radiographic imaging apparatus 1 using the RFID technology described above is installed. The tag reader 57 transmits predetermined instruction information on radio waves or the like via a built-in antenna (not shown), and detects the radiographic imaging apparatus 1 that enters or leaves the front room R2 or the imaging room R1. Yes. The tag reader 57 reads the unique information stored in the detected RFID tag of the radiographic imaging device 1 and transmits the read unique information to the console 58.

  The console 58 is composed of a computer in which a CPU, a ROM (Read Only Memory), a RAM (Random Access Memory), an input / output interface and the like (not shown) are connected to the bus, and reads a predetermined program stored in the ROM. The entire radiographic imaging system 50 is controlled as described above by developing it in the work area of the RAM and executing various processes according to the program.

  In FIG. 15, the case where the console 58 is installed outside the photographing room R1 and the front room R2 is described, but for example, the console 58 may be configured to be installed in the front room R2 and the like. It is.

  The console 58 is connected to the above-described console 56, tag reader 57, and the like, and is connected to the wireless access point 54 via the console 56 and the like. The console 58 is provided with a display screen 58a composed of a CRT (Cathode Ray Tube), an LCD (Liquid Crystal Display), or the like, and other input means such as a keyboard and a mouse are connected thereto.

  The console 58 is connected to a storage means 59 composed of an HDD (Hard Disk Drive) or the like, and the storage means 59 captures each radiographic image of each radiographic imaging apparatus 1 usable in the radiographing room R1. FIG. 10 shows information on a plurality of defective pixels dp distributed in a two-dimensional cluster form in each pixel p corresponding to a plurality of image sensors 41 arranged two-dimensionally on the sensor panel 40 of the apparatus 1. It is stored in the form of a table T.

  When the console 58 receives the unique information including the cassette ID of the radiographic imaging apparatus 1 detected by the tag reader 57 as described above, the radiation existing in the imaging room R1 and the like registered in the storage unit 59 is transmitted to the console 58. A list of the image capturing device 1 is referred to. If the transmitted unique information is not registered in the storage means 59, the console 58 assumes that the radiographic imaging device 1 is newly brought into the radiographic room R1 or the front room R2, and the radiographic imaging thereof is performed. The cassette ID or the like of the device 1 is added to the above list and registered in the storage unit 59.

  If the transmitted unique information is already registered in the storage means 59, the radiographic image capturing apparatus 1 is assumed to have been taken out of the radiographing room R1 or the front room R2. Delete the cassette ID etc. from the above list. In this way, the console 58 grasps the radiation image photographing apparatus 1 brought into or taken out from the photographing room R1 or the like and manages it on the storage means 59.

  On the other hand, when the read operation is completed in the radiographic imaging apparatus 1 used for radiographic imaging and the image data F (i, j), that is, raw data of each imaging element 41 is transmitted, the console 58 receives each defect. Correction processing is performed on the image data F (i, j) output from the pixel dp.

  Specifically, radiation image capturing is performed by irradiating the radiation image capturing apparatus 1 with radiation, and image data F (i, j) for each image sensor 41 from the radiation image capturing apparatus 1 and the ID of the apparatus. Is transmitted, the image data F (i, j) is temporarily stored in the storage means 59.

Then, the console 58 is a table in which information of defective pixels dp distributed in a two-dimensional cluster for the radiographic imaging device 1 stored in the storage unit 59 based on the ID of the device is described. Read T, refer to it, and perform normal processing closest to each defective pixel dp in the row direction and the column direction in the same manner as the correction process in the control unit 22 in the above embodiment based on the information of the defective pixel dp. Using the image data F (A) to F (D) of each pixel A to D and the number of pixels a to d of the normal pixels A to D, the pixel position (i, j) of each defective pixel dp. The corrected image data F ^* (i, j) in (1) is calculated.

Then, the calculated corrected image data F ^* (i, j) replaces the image data Fd (i, j) output from each defective pixel dp (i, j), respectively, and the pixel position ( The normal image data F (i, j) output from the normal pixel p is assigned to i, j), and the corrected image data F ^* (i, j) is assigned to the pixel position (i, j) of the defective pixel dp. The corrected image data assigned with j) is created and stored in the storage means 59.

  In the present embodiment, as described above, the corrected image data may be stored in the storage unit 59 separately from the raw data, and the corrected image data is overwritten and stored on the raw data. For example, the abnormal image data Fd (i, j) output from the defective pixel dp can be deleted. In addition to the corrected image data, only the abnormal image data Fd (i, j) of the defective pixel dp can be extracted from the raw data and stored.

  Also in the present embodiment, when the thinned image data is transmitted from the radiation image capturing apparatus 1, the console 58 does not perform the above correction processing on the thinned image data, and the thinned image data. Is displayed as it is on the display screen 58a. If comprised in this way, it will become possible to display the thinning image data transmitted from the radiographic imaging device 1 on the display screen 58a of the console 58 quickly, and in the image taken by the radiographic imaging device 1. It is possible to determine at an early stage whether or not the re-shooting is necessary by confirming at an early stage whether or not the shooting position of the subject is appropriate.

As described above, according to the radiographic image capturing system 50 according to the present embodiment, the console 58 is created in advance for a plurality of defective pixels dp distributed in a two-dimensional cluster on the sensor panel 40 of the radiographic image capturing apparatus 1. has been based on the information of the defect pixel dp pixel position of each defective pixel dp (i, j) the image data ^F * was corrected in (i, j) was calculated, corrected image data ^F * (i, j) The image data F (i, j) output from each defective pixel dp (i, j) can be replaced and corrected, and the same effective effect as in the first embodiment can be obtained. It becomes possible to play.

  Further, when the radiographic image capturing apparatus 1 is portable and has a built-in battery 42 (see FIG. 9), the radiographic image capturing apparatus 1 does not perform correction processing, and thus the battery 42 of the radiographic image capturing apparatus 1 is used. Power consumption is suppressed. For this reason, it is possible to increase the number of times the radiographic imaging apparatus 1 is used for radiographic imaging per charge of the battery 42, and the radiographic imaging apparatus 1 can be used efficiently.

  Also in the present embodiment, when the above-described point defects and line defects exist in each imaging element 41 on the sensor panel 40 of the radiographic image capturing apparatus 1, the console 58 outputs the defect pixels dp. Needless to say, the corrected image data F (i, j) is corrected. However, when the thinned image data is transmitted from the radiographic image capturing apparatus 1 as described above, an operator such as a radiographer confirms at an early stage whether or not the photographing position of the subject in the image is appropriate. Therefore, it is only necessary to determine whether or not re-photographing is necessary at an early stage. Therefore, the console 58 can be configured not to correct point defects or line defects.

In the first and second embodiments, the case where the phosphor 3a of the scintillator 3 of the radiographic imaging apparatus 1 has a columnar crystal structure has been described. However, the phosphor 6a of the scintillator 6 does not necessarily have a columnar crystal structure. For example, a scintillator formed by applying a phosphor 3a made of GOS (Gd ₂ O ₂ S: Tb) or the like to the support 3b or the glass substrate 35 (see FIG. 8 or the like) in layers. The present invention can be similarly applied when used.

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

DESCRIPTION OF SYMBOLS 1 Radiographic imaging apparatus 2 Housing 3 Scintillator 3a Phosphor 17 Reading circuit 22 Control means (correction means, thinned image data generation means)
39 Antenna device (communication means)
40 Sensor panel 41 Image sensor 50 Radiation imaging system 58 Console 58a Display screen 59 Storage means A to D Normal pixels a to d closest to defective pixels Number of pixels dp Defective pixels F (A) to F (D) Defects Image data F (i, j) of each normal pixel closest to the pixel Image data F ^* (i, j) Corrected image data (i, j) Pixel position p Pixel T table (defective pixel information)

Claims (7)

A sensor panel in which a plurality of image sensors for generating electric charges according to the dose of irradiated radiation are arranged in a two-dimensional manner;
A readout circuit for reading out image data from each of the image sensors;
Information on a plurality of defective pixels distributed in a two-dimensional cluster including at least two rows and two columns of defective pixels among the pixels corresponding to the plurality of imaging elements arranged two-dimensionally on the sensor panel. Storage means for storing;
Correction means for calculating the corrected image data at the pixel position of each defective pixel based on the information on the defective pixel, and replacing the image data output from each defective pixel with the corrected image data, respectively. When,
With
The information on the defective pixels includes information on pixel positions of the defective pixels on the sensor panel and pixels up to the normal pixels closest to the defective pixels in the row direction and the column direction on the sensor panel. Number information,
The correcting means is configured to determine, based on the information on the defective pixels, the image data and the number of pixels of the normal pixels closest to the defective pixels in the row direction, and the defective pixels in the column direction. The corrected image data is calculated using the image data and the number of pixels of the normal pixels closest to the image.   The radiographic imaging apparatus according to claim 1, wherein the sensor panel includes a scintillator that converts the irradiated radiation into an electromagnetic wave having a wavelength that can be detected by the imaging device.   The radiographic image capturing apparatus according to claim 1, wherein the scintillator is made of a columnar crystal of a phosphor. Comprising thinned image data generating means for generating thinned image data from the image data of each of the image sensors read by the read circuit;
The correction means does not calculate the corrected image data for the thinned image data generated by the thinned image data generation means. The radiographic imaging apparatus described.   The radiographic imaging apparatus according to any one of claims 1 to 4, wherein the sensor panel is housed in a monocoque housing and is portable. A sensor panel in which a plurality of image sensors for generating electric charges according to the dose of irradiated radiation are arranged in a two-dimensional manner;
A readout circuit for reading out image data from each of the image sensors;
A communication means for transmitting / receiving data to / from an external device;
A radiographic imaging device comprising:
A plurality of pixels corresponding to the plurality of imaging elements arranged two-dimensionally on the sensor panel of the radiographic imaging apparatus, including at least two rows and two columns of defective pixels and distributed in a two-dimensional cluster shape Storage means for storing information on defective pixels of
The information of the defective pixel related to the radiographic image capturing apparatus is read from the storage unit, and the image data output from each defective pixel is extracted from the image data transmitted from the radiographic image capturing apparatus. A console that respectively replaces the corrected image data at the pixel position of each defective pixel calculated based on the information;
With
The information on the defective pixels includes information on pixel positions of the defective pixels on the sensor panel and pixels up to the normal pixels closest to the defective pixels in the row direction and the column direction on the sensor panel. Number information,
Based on the information on the defective pixels, the console applies the image data and the number of pixels of the normal pixels closest to the defective pixels in the row direction, and the defective pixels in the column direction. A radiographic imaging system characterized in that the corrected image data is calculated using the image data and the number of pixels of the normal pixels closest to each other. The radiographic image capturing device is capable of generating thinned image data from image data of each imaging element read by the readout circuit,
When the thinned image data is transmitted from the radiographic image capturing apparatus, the console does not calculate the corrected image data for the thinned image data, and the thinned image data is displayed on a display screen. The radiographic image capturing system according to claim 6, wherein:

Images