JP2010227510A - Radiation detecting device and method, and radiation image photographing system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To satisfy functions and performances necessary for various special photography by resetting an FPD. <P>SOLUTION: Reset to be executed is selected between a regular resetting mode to read unnecessary signal loads in the FPD until a request for photography is received or an additional resetting mode to read unnecessary signal loads in the FPD when a request for photography is received, according to the content of the photography, such as general photography, pediatric photography, or orthopedic diagnostic photography. As the unnecessary signal loads are sequentially read a plurality of lines at a time in parallel reset, the time lag from the request for photography to X-ray exposure is shortened to improve the frame rate. As the unnecessary signal loads are sequentially read one line at a time in sequential reset, deterioration of the image quality caused by current fluctuation can be prevented to achieve the high-quality photography. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to a radiation detection apparatus and method for generating radiation images by detecting radiation transmitted through a subject, and a radiation image capturing system using the radiation detection apparatus.

  Medical radiographic imaging systems that irradiate a subject with radiation such as X-rays, receive radiation transmitted through the subject, and capture a radiation image (hereinafter referred to as an image) that represents the internal structure of the subject have become widespread. . Conventionally, a film has been used to receive radiation, but nowadays, radiation detectors such as an imaging plate (hereinafter referred to as IP) and a flat panel detector (hereinafter referred to as FPD) are being used.

  The FPD includes a thin film transistor array (hereinafter abbreviated as a TFT array) provided on a glass substrate and an X-ray conversion layer provided thereon. The X-ray conversion layer converts X-rays transmitted through the subject into signal charges proportional to the transmission intensity. The TFT array accumulates signal charges and outputs them as digital image data. By using the FPD, it is possible to perform fluoroscopic imaging in which X-rays are continuously exposed and imaging is performed while seeing through the human body.

  The TFT array is provided in the vicinity of the intersection of the plurality of gate lines arranged along the row direction, the plurality of data lines arranged along the column direction orthogonal to the row direction, and the gate lines and the data lines, And a plurality of pixels arranged in the row direction and the column direction. The pixel includes a capacitor for accumulating signal charges and a thin film transistor (hereinafter abbreviated as TFT) that reads the signal charges from the capacitor to the data line. A plurality of TFTs arranged in the same row are connected to a common gate line, and a plurality of TFTs arranged in the same column are connected to a common data line.

  A gate signal is sequentially input to each gate line. The plurality of TFTs connected to the gate line to which the gate signal is input are turned on simultaneously, and signal charges are output from the capacitor to the data line. The signal charges of one row of pixels output to the data line are converted into an analog voltage as an electric signal by a charge amplifier connected to the data line, and the analog voltage is converted into a digital signal by an A / D converter. As a result, the signal charges of all the pixels are converted into digital image data line by line.

  Some radiographic imaging systems include a bucky unit in order to prevent image contrast from being reduced by X-rays scattered when passing through a subject. The Bucky unit includes a grid that removes scattered X-rays in front of the FPD, and a drive mechanism that moves the grid in a direction parallel to the X-ray detection surface of the FPD so that the grid is not photographed. The grid starts to move in response to an operation that causes the radiographic imaging system to perform imaging (hereinafter referred to as an imaging request), and X-rays are exposed after the settling time has elapsed from the start of grid movement. . The settling time is a time required for the grid to reach a predetermined speed or a time required for the vibration generated in the FPD due to the movement of the grid to converge to a level at which the imaging is not adversely affected.

In the FPD, a very small amount of signal charge is accumulated in the capacitor due to dark current that flows when radiation is not irradiated. Unnecessary signal charges due to dark current appear as noise in an image taken by FPD. In order to prevent image noise due to this unnecessary signal charge, conventionally, at the same time as an imaging request, a reset operation for releasing unnecessary signal charge from the FPD was performed, and X-rays were exposed after the completion of this reset operation. . In some cases, the reset operation is repeatedly performed during imaging standby of the FPD, and when an imaging request is received, X-rays are emitted after the reset operation being executed is completed. The reset operation is substantially the same sequence as readout of signal charges after photographing, and unnecessary signal charges are read out row by row.
It was.

  The reset operation performed at the same time as the imaging request has a long time lag from the imaging request until the X-ray is exposed, which restricts the user's operation and may cause an erroneous operation. In addition, it has also caused a decrease in frame rate such as continuous shooting and fluoroscopic shooting. Further, even if the reset operation is performed once immediately before photographing, unnecessary signal charges are not sufficiently released and may remain in the FPD. Further, in the reset operation repeatedly performed during the imaging standby, there is a problem that the time lag from the imaging request to the X-ray exposure varies depending on the timing of the imaging request.

  In order to solve the problems related to the reset operation described above, for example, the inventions of Patent Documents 1 to 6 described below have been made. In the reset operation of Patent Document 1, gate signals are simultaneously input to all gate lines of the FPD when the X-ray exposure switch is operated, all TFTs are simultaneously turned on, and unnecessary signal charges of all pixels are simultaneously released. . According to this, since the time required for the reset operation is sufficiently shorter than the X-ray exposure time, the frame rate is improved.

  In Patent Document 2, the FPD is reset when the first switch is operated, and the X-ray source is exposed to X-rays when the second switch is operated. According to this, it is possible to eliminate a time lag from the operation of the second switch until the X-ray is exposed.

  In Patent Document 3, each pixel of the FPD is divided into a plurality of pixel groups. While one pixel group performs an idle reading operation that is a reset operation, the other pixel group detects X-rays to detect signal charges. The main reading operation to read is performed. According to this, the frame rate is improved. Further, since the signal charges obtained in the main reading operation are added and averaged, noise is reduced.

  Japanese Patent Laid-Open No. 2004-228561 repeatedly performs an FPD reset operation during an idling operation period before X-ray exposure, and informs a photographer that exposure is possible after the completion of each reset operation. A signal is generated. According to this, it is possible to acquire a stable image while suppressing exposure delay.

  Patent Document 5 provides a sensor that detects X-rays separately from the FPD, and repeats the reset operation of the FPD until the sensor detects the X-rays. When the X-rays are detected, the reset operation is stopped halfway. X-rays are exposed to the X-ray source. According to this, an appropriate image can be obtained without electrically connecting and controlling the X-ray source and the FPD.

  In Patent Document 6, each pixel of the FPD is made into a plurality of pixel groups divided into a plurality of rows, and the reset operation of each pixel group is simultaneously performed by separate shift registers. According to this, the time required for the reset operation can be shortened, and the current fluctuation of the FPD can be reduced as compared with the case where unnecessary signal charges of all the pixels are simultaneously released as in Patent Document 1.

JP 2001-340324 A JP 2001-103378 A JP-A-10-170656 JP 2005-312949 A JP 2007-151761 A Japanese Patent No. 3264663

  The radiographic imaging apparatus includes special imaging such as orthopedic diagnostic imaging and fluoroscopic imaging in addition to general imaging in which the internal structure of the subject is captured as a normal still image. Orthopedic diagnostic imaging is imaging used for diagnosis of musculoskeletal systems such as bones, joints, and muscles of the human body, and sharpness of images is required. Further, fluoroscopic imaging is imaging performed while continuously irradiating X-rays and seeing through the human body, and high sensitivity, high detection quantum efficiency (DQE), and high frame rate are required. Also, general shooting may be special shooting depending on the subject. For example, in pediatric photography for photographing a child, the time lag from the imaging request to the X-ray exposure is short and the variation in the time lag is small in order to photograph a child who cannot remain stationary for a long time. Desired.

  In the inventions described in Patent Documents 1 to 6, the time lag from the imaging request to the X-ray exposure can be shortened, the variation in the time lag can be reduced, or the noise of the image can be reduced. However, it has not been possible to appropriately satisfy the various special photographing requirements described above.

  In addition, the Bucky unit is used in general photography and orthopedic diagnostic photography that do not require a short time lag or high frame rate, such as childhood photography or fluoroscopic photography. However, in the inventions described in Patent Documents 1 to 6, it is difficult to ensure the settling time of the Bucky unit before photographing.

  It is an object of the present invention to satisfy functions and performances necessary for various types of special photography by an FPD reset operation.

  The radiation detection apparatus of the present invention includes a radiation detector, a plurality of switching means, a readout control means, and a control procedure selection means. The radiation detector detects radiation that has passed through the subject, converts it into signal charges, and accumulates the signal charges by a plurality of pixels arranged in a row direction and a column direction. The plurality of switching means sequentially read out the signal charges accumulated in each pixel one by one from each of a plurality of pixel groups obtained by dividing each pixel into a plurality of rows. The readout control means has at least a first control procedure and a second control procedure used for controlling each switching means, and the first control procedure or the first control procedure is received until an imaging request for requesting radiation detection is received from the radiation detector. A steady reset mode in which two control procedures are repeated, and an additional reset mode in which at least one frame of the first control procedure or the second control procedure is executed after completion of the control procedure being executed when an imaging request is received have. The control procedure selection means selects control procedures used for the steady reset mode and the additional reset mode.

  The first control procedure is a parallel reset in which each switching unit is simultaneously driven to sequentially read unnecessary signal charges accumulated in each pixel in a plurality of rows, and the second control procedure is performed sequentially for each switching unit one by one. This is a sequential reset in which unnecessary signal charges accumulated in each pixel are sequentially read out row by row.

  Additional reset mode adjusting means for setting one frame period or the number of frames in the control procedure of the additional reset mode may be provided. Moreover, you may provide the reset mode setting means which sets execution or a stop of a steady reset mode and an additional reset mode.

  In the case of having shooting mode selection means for selecting one of a plurality of shooting modes set based on the subject or shooting purpose, the control procedure selection means is based on the shooting mode selected by the shooting mode selection means. The control procedure used in the standby reset mode and the additional reset mode may be selected.

  In addition, the information conversion means for converting the signal charge read from the radiation detector that has detected the radiation into electrical information, and the information conversion means so that unnecessary signal charges accumulated in the information conversion means are released. There may be provided reset means for setting the reset state, and the reset means may be controlled by the read control means in conjunction with the start of reading of the signal charge to release the reset state of the information conversion means.

  The radiation detection method of the present invention is a first control procedure for reading out signal charges from a radiation detector until receiving an imaging request for detecting radiation from the radiation detector that accumulates signal charges by detecting radiation transmitted through the subject. Alternatively, the second control procedure is repeated to read out unnecessary signal charges accumulated in a plurality of pixels of the radiation detector, and when an imaging request is received, wait for the control procedure being executed to end, Executing at least one frame of one control procedure or second control procedure, and reading out unnecessary signal charges accumulated in each pixel of the radiation detector.

  A radiographic imaging system according to the present invention includes a radiation exposure apparatus that exposes a subject to radiation, a radiation detection apparatus according to any one of claims 1 to 6, and a control apparatus that controls the radiation exposure apparatus and the radiation detection apparatus. And. The readout control means of the radiation detection device transmits a radiation exposure permission signal to the control device at the end of the additional reset mode, and the control device causes the radiation exposure device to emit radiation according to the radiation exposure permission signal. .

  According to the present invention, by arbitrarily selecting and combining the control procedures executed in the steady reset mode and the additional reset mode, for example, the time lag from the imaging request to the radiation exposure is shortened, and the sharpness of the image is improved. It is possible to satisfy functions, performance, and the like required for various photographing such as improvement of sensitivity, DQE, and frame rate.

1 is a schematic diagram illustrating a configuration of an X-ray image capturing system. It is a disassembled perspective view which shows the structure of FPD. It is a schematic diagram which shows the structure of FPD. It is a perspective view which shows the structure of a TFT array. It is a block diagram which shows the structure of a panel unit. It is a block diagram which shows the structure of a TFT gate control circuit. It is a timing chart which shows the parallel reset drive by a TFT gate control circuit. It is a timing chart which shows the sequential reset drive by a TFT gate control circuit. It is the table | surface which showed the characteristic of sequential reset drive and parallel reset drive. It is the table | surface which showed the combination of the reset drive suitable for various imaging | photography. It is a block diagram which shows the structure of a panel unit control circuit. It is a flowchart which shows the operation | movement procedure of the panel unit at the time of general imaging | photography. It is a timing chart which shows the operation | movement procedure of the X-ray image imaging system at the time of general imaging | photography. It is a flowchart which shows the operation | movement procedure of the panel unit at the time of infant imaging | photography. It is a timing chart which shows the operation | movement procedure of the X-ray image imaging system at the time of infant imaging. It is a flowchart which shows the operation | movement procedure of the panel unit at the time of a sharp diagnosis imaging | photography. It is a timing chart which shows the operation | movement procedure of the X-ray image imaging system at the time of orthopedic diagnostic imaging. It is a flowchart which shows the operation | movement procedure of the panel unit at the time of fluoroscopic imaging. It is a timing chart which shows the operation | movement procedure of the X-ray image imaging system at the time of fluoroscopic imaging.

  An X-ray imaging system 10 shown in FIG. 1 exposes X-rays to a standing subject H, detects X-rays transmitted through the subject H, and displays an image representing the internal structure of the subject H in real time. . The X-ray image photographing system 10 can perform special photographing such as child photographing, orthopedic diagnostic photographing, and fluoroscopic photographing in addition to general photographing for photographing the internal structure of the subject H as it is.

  The X-ray imaging system 10 includes an X-ray exposure device 11, a panel unit 12, a console device 13, a system controller 14, and the like. The X-ray exposure apparatus 11 emits X-rays to the subject H, and the panel unit 12 detects X-rays transmitted through the subject H. The system controller 14 controls the X-ray exposure apparatus 11 and the panel unit 12 in an integrated manner, and the console apparatus 13 is used for the operation of the system controller 14.

  The X-ray exposure apparatus 11 includes an X-ray source 17 and an X-ray source control circuit 18 that controls the X-ray source 17. The X-ray source 17 is an X-ray tube that generates X-rays by accelerating and making electrons enter a target such as tungsten or molybdenum from a cathode filament. Based on the control of the system controller 14, the X-ray source control circuit 18 generates a current (tube current) and an accelerating voltage (tube voltage) that flow through the cathode so that X-rays having a predetermined quality and dose are exposed. The X-ray source 17 is exposed to X-rays.

  The panel unit 12 detects X-rays that have passed through the subject H, and transmits image data representing the internal structure of the subject H to the system controller 14. The panel unit 12 includes a housing 21 that is attached to a column (not shown) installed on the floor so as to move up and down. The housing 21 is provided with an X-ray incident surface 21a against which an imaging part of the subject H comes into contact. The X-ray source 17 is disposed so as to face the X-ray incident surface 21a, and the X-rays that have been exposed by the X-ray source 17 and transmitted through the subject H enter the X-ray incident surface 21a.

  In the housing 21, there are a Bucky unit 24 that removes X-rays scattered by the subject H, an FPD 25 that detects X-rays that have passed through the Bucky unit 24, a TFT gate control circuit 26, a readout circuit 27, and a panel unit control circuit. 28 etc. are provided.

  The bucky unit 24 includes a grid 31 disposed in front of the FPD 25, and a drive mechanism 32 that moves the grid 31 in the direction of the arrow parallel to the X-ray detection surface 25a of the FPD 25. The grid 31 has a grid structure in which a large number of lead foils that shield X-rays are stacked while providing a gap along a direction substantially orthogonal to the X-ray detection surface 25a. Of the X-rays exposed from the X-ray source 17, the X-rays that pass through the subject H and go straight while attenuated pass through the gap between the lead foils and reach the X-ray detection surface 25 a of the FPD 25. On the other hand, the scattered X-rays scattered in the subject H and changed in direction are blocked by the lead foil, so that a reduction in contrast is prevented.

  The drive mechanism 32 slides the grid 31 to the right during X-ray irradiation so that the grid structure of the grid 31 is not imaged by the FPD 25. The drive mechanism 32 includes an actuator such as a motor and a mechanism component that moves the grid 31 by the rotation of the motor.

  The FPD 25, which is a radiation detector, is a direct conversion type flat panel detector that detects X-rays incident on the X-ray detection surface 25a and accumulates signal charges corresponding to the X-ray dose. The FPD 25 is arranged so that the X-ray detection surface 25a faces the X-ray incident surface 21a. The X-ray detection surface 25a has, for example, an area that can cover the entire chest of the subject H. As shown in FIG. 2, the FPD 25 includes a glass substrate 35, a TFT array 36, an X-ray conversion layer 37, and a common electrode 38 stacked on the glass substrate 35.

  As shown in FIG. 3, the X-ray conversion layer 37 is made of a photoconductive film such as amorphous selenium, and generates a pair of electrons and holes when X-rays are incident. The common electrode 38 is provided on the surface of the X-ray conversion layer 37, and a DC high voltage is applied thereto. The electron hole pairs generated in the X-ray conversion layer 37 are converged on the TFT array 36 by the high voltage applied to the common electrode 38, and signal charges are generated.

  As shown in FIG. 4, the TFT array 36 includes a plurality of gate lines GL arranged along the row direction and a plurality of data lines DL arranged along the column direction orthogonal to the row direction. ing. A plurality of pixels 41 arranged in the matrix direction are provided in the vicinity of the intersection of the grid-like wiring formed by the gate lines GL and the data lines DL.

  The pixel 41 includes a pixel electrode 44, a capacitor 45 (see FIG. 3), and a TFT 46. The pixel electrodes 44 are arranged along the matrix direction and collect signal charges generated by the X-ray conversion layer 37. The capacitor 45 is provided below the pixel electrode 44 and accumulates signal charges collected by the pixel electrode 44. The TFT 46 is connected to the capacitor 45 in the same pixel 41 and the neighboring gate line GL and data line DL. The TFT 46 is turned on when a gate signal is input from the gate line GL, and reads the signal charge in the capacitor 45 to the data line DL.

As shown in FIG. 5, in the FPD 25, for example, 3072 pixels 41 are arranged along the row direction and the column direction, respectively. 3072 gate lines GL and 30 data lines DL are provided in accordance with the number of pixels 41 arranged. The TFTs 46 arranged in the same row are connected to a common gate line GL, and those arranged in the same column are connected to a common data line DL. Therefore, when the gate signal is inputted to the gate line GL _3, the TFT 46 3072 amino which is connected to the gate line GL ₃ are turned on at the same time, one row of the signal charges the data lines _DL 1 pixel 41 through DL ₃₀₇₂ , respectively.

The TFT gate control circuit 26 drives each TFT 46 of the FPD 25 via the connected gate lines GL _{1 to} GL ₃₀₇₂ . As shown in FIG. 6, the TFT gate control circuit 26 includes a signal generation circuit 49, a selector 50, and 12 gate control ICs 51 _{1 to} 51 ₁₂ .

The signal generation circuit 49 inputs the shift clock signal CPV having a predetermined cycle to the gate control ICs 51 _{1 to} 51 ₁₂ and inputs the strobe signal STV to the selector 50. The selector 50 selectively inputs the strobe signal STV input from the signal generation circuit 49 to the gate control ICs 51 _{1 to} 51 ₁₂ .

The gate control ICs 51 _{1 to} 51 _{12 serving as} switching means are so-called shift registers, and 256 gate lines GL are connected to the output side. For example, the gate control IC 51 ₁ is connected to the gate lines _GL 1 _{~GL 256,} the gate control IC 51 _12, the gate line _GL 2817 _{~GL 3072} is connected. The gate control ICs 51 _{1 to} 51 ₁₂ shift the strobe signal STV input from the selector 50 based on the shift clock signal CPV input from the signal generation circuit 49, and sequentially apply gate signals to 256 gate lines GL. Output as.

  The driving sequence of the TFT gate control circuit 26 is switched according to the operation mode of the panel unit 12. For example, the reset mode for releasing unnecessary signal charges from the FPD 25 includes a steady reset mode that is executed until an imaging request is received and an additional reset mode that is executed after the imaging request, and the parallel reset driving or the sequential reset driving is selectively performed. Executed. In the general imaging mode in which the FPD 25 detects X-rays, accumulation driving for accumulating signal charges and readout driving for reading the accumulated signal charges are performed.

FIG. 7 shows the shift clock signal CPV, the strobe signal STV, and the gate signal input to each gate line GL during parallel reset driving. The selector 50 inputs the strobe signal STV to the gate control ICs 51 _{1 to} 51 ₁₂ at the same time. Each of the gate control ICs 51 _{1 to} 51 ₁₂ shifts the strobe signal STV based on the shift clock signal CPV and sequentially outputs it as a gate signal to the 256 gate lines GL connected thereto.

  In the parallel reset based on the parallel reset driving of the TFT gate control circuit 26, unnecessary signal charges accumulated in each pixel 41 of the FPD 25 are sequentially read out by a plurality of rows, that is, every 12 rows.

FIG. 8 shows the shift clock signal CPV, the strobe signal STV, and the gate signal input to each gate line GL at the time of sequential reset driving. The selector 50 inputs the strobe signal STV in the gate control IC 51 _1. The gate control IC 51 ₁ shifts the strobe signal STV based on the shift clock signal CPV, sequentially outputs a gate signal to the data lines _GL 1 _{~GL 256} connected. Strobe signal STV output from the gate control IC 51 ₁ finishing shift via the selector 50 is input to the next gate control IC 51 _2. Thereafter, the strobe signal STV is sequentially input to the gate control ICs 51 _{3 to} 51 ₁₂ by the selector 50.

  In the sequential reset based on the sequential reset driving of the TFT gate control circuit 26, unnecessary signal charges accumulated in each pixel 41 of the FPD 25 are sequentially read out row by row.

  In accumulation driving, all TFTs 46 of the FPD 25 are turned off, and signal charges are accumulated in the capacitors 45 of the respective pixels 41. The read drive has substantially the same sequence as the sequential reset drive. In data reading by read driving, signal charges are sequentially read from each pixel 41 of the FPD 25 one row at a time. Note that since the amount of signal charge read in the reading drive is much larger than the signal charge due to dark current, one frame period is sequentially longer than that of reset driving.

The selector 50, when when the strobe signal STV from the gate control IC 51 ₁ to 51 ₁₂ is entered, or sequentially reset drive and strobe signal STV from the gate control IC 51 ₁₂ in the read drive is entered during parallel reset driving, one frame A completion signal FC is transmitted to the panel unit control circuit 28.

  The TFT gate control circuit 26 repeats the parallel reset driving or the sequential reset driving in the steady reset mode based on the control of the panel unit control circuit 28. Further, when an imaging request is received in the steady reset mode, the process proceeds to the additional reset mode after one frame of the reset drive being executed is completed, and at least one frame of the parallel reset drive or the sequential reset drive is executed.

  Whether to perform parallel reset driving or sequential reset driving in the steady reset mode and the additional reset mode can be arbitrarily selected by the user based on the characteristics of each reset drive and the contents of photographing. As shown in FIG. 9, the discharge characteristics of unnecessary charges are the same between the sequential reset driving and the parallel reset driving and the all-line batch reset described as a reference. The all-line batch reset is a reset in which all TFTs 46 of the FPD 25 are simultaneously turned on and unnecessary signal charges are read.

  In the sequential reset driving, the current fluctuation of the FPD 25 does not occur. On the other hand, in the parallel reset driving, the current fluctuation of the FPD 25 slightly occurs, and one frame period is sequentially shorter than the reset driving. In the all-line batch reset, the current fluctuation is larger than that of the parallel reset drive, but one frame period is much shorter than that of the parallel reset drive. The current fluctuation at the time of resetting affects the noise of the image. Therefore, the image quality of the sequential reset drive that does not cause current fluctuation is the best, and the parallel reset drive can reduce the influence on the image quality more than the batch reset of all lines.

  Examples of photographing contents include the above-described general photographing, child photographing, orthopedic diagnostic photographing, fluoroscopic photographing, and the like. FIG. 10 shows a combination of reset driving optimum for each of the above-described photographing. Note that “sequential” and “parallel” in the table represent sequential reset driving and parallel reset driving, respectively.

  In general imaging, it is required that the time lag from the imaging request to the X-ray exposure is somewhat short, the variation in the time lag is small, and that the settling time of the bucky unit 24 can be secured immediately before imaging. In order to satisfy the conditions necessary for general imaging, for example, it is preferable to perform parallel reset driving in the steady reset mode and sequentially perform reset driving in which one frame period is longer than the settling time in the additional reset mode.

  In addition, since it is difficult to keep a child stationary for a long time in pediatric imaging, it is required that the time lag from the imaging request to the X-ray exposure and the variation in the time lag are shorter than in general imaging. Further, the bucky unit 24 is not used because it requires a settling time. In order to satisfy the conditions necessary for the child photographing, for example, it is preferable that the parallel reset driving is repeated in the steady reset mode and the parallel reset driving is performed for several frames in the additional reset mode.

  In orthopedic imaging, bones, joints, muscles, etc. of the human body are diagnosed, so that sharpness of the image is required. Therefore, the bucky unit 24 is used in the orthopedic diagnostic imaging. In orthopedic diagnostic imaging, in order to suppress image degradation as much as possible, for example, it is preferable to repeat sequential reset driving with good image quality in the steady reset mode and to sequentially perform one frame reset driving in the additional reset mode.

  In fluoroscopic imaging, sensitivity, DQE, high frame rate, and the like are required. Therefore, for fluoroscopic imaging, it is preferable to improve the sensitivity and DQE by sequentially repeating reset driving in the steady reset mode and to improve the frame rate by performing parallel reset driving for one frame in the additional reset mode. Note that in the fluoroscopic imaging in which continuous imaging is performed, the reset is not performed in the second transitional imaging. Therefore, only the reset immediately before the first shooting is set as the additional reset mode.

  Further, the sequential reset driving in the additional reset mode can arbitrarily set one frame period T. Similarly, the parallel reset driving in the additional reset mode can arbitrarily set the number of frames to be executed. This is to ensure the settling time of the Bucky unit 24 before photographing. When the grid 31 is replaced, the settling time varies depending on the weight of the grid 31 and the like, but this can be dealt with by sequentially adjusting one frame period T of reset driving or the number of frames of parallel reset driving. .

The readout circuit 27 shown in FIG. 5 reads out signal charges from the capacitors 45 of the FPD 25 via the connected data lines DL _{1 to} DL ₃₀₇₂ . The read circuit 27 includes a charge amplifier 54, a multiplexer 55, and an A / D converter 56.

The charge amplifier 54 as information conversion means has, for example, a system of 256 ch × 12, and simultaneously converts signal charges read from the data lines DL _{1 to} DL ₃₀₇₂ into analog voltages. One channel of the charge amplifier 54 includes an operational amplifier 54a, a capacitor 54b, and a reset switch 54c. The reset switch 54c is a reset unit that discharges unnecessary charges accumulated by setting the capacitor 54b in a short state.

  The multiplexer 55 selects a predetermined number of analog voltages input from the charge amplifier 54 and inputs them to the A / D converter 56. The A / D converter 56 converts the analog voltage input from the multiplexer 55 into digital pixel data for each pixel 41 and inputs the digital pixel data to the panel unit control circuit 28.

  The panel unit control circuit 28 comprehensively controls the bucky unit 24, the FPD 25, the TFT gate control circuit 26, the readout circuit 27, etc. of the panel unit 12. The panel unit control circuit 28 is connected to the system controller 14 by a high-speed serial communication line using an optical fiber. Register access and various control commands are transmitted from the system controller 14 to the panel unit control circuit 28, and various response commands and image data are transmitted from the panel unit control circuit 28 to the system controller 14.

  As shown in FIG. 11, the panel unit control circuit 28 includes a plurality of registers such as an instruction register 59, a status register 60, and a parameter register 61. A control command is written into the command register 59 by the system controller 14. The panel unit control circuit 28 controls each part of the panel unit 12 based on the control command written in the command register and the control command transmitted from the system controller 14.

  The status register 60 is written by the panel unit control circuit 28 itself with the operation status of the panel unit 12 (for example, the current operation mode) and the result of the control executed based on the control command and control command. The system controller 14 can know the state of the panel unit 12 with reference to the state register 60.

  The parameter register 61 stores parameters used for controlling each part of the panel unit 12. The panel unit control circuit 28 refers to the parameter register 61 when performing various controls according to the control command and the control command. The parameter register 61 has a plurality of surfaces such as an A surface 61a and a B surface 61b, for example, and is switched according to the operation mode of the panel unit 12.

  For example, the parameter A 61 of the parameter register 61 stores parameters necessary for the reset mode, and the B surface 61b stores parameters necessary for the general imaging mode. When changing the operation contents such as the reset mode and the general photographing mode, the contents of the parameter register 61 are appropriately rewritten by the system controller 14. Note that the parameter register 61 may be provided with a C-plane, a D-plane, etc., and may be used for energy subtraction imaging or fluoroscopic imaging, respectively.

  The panel unit control circuit 28 accumulates and rearranges the pixel data transmitted from the readout circuit 27, generates image data for each line, and stores it in the built-in line memory 64. One line of image data is read from the line memory 64 and transmitted to the system controller 14. The storage capacity of the line memory 64 may be a size that can store image data for one frame or a size that can store image data of less than one frame. In the present embodiment, the reading of the pixel data from the reading circuit 27 and the transmission of the image data to the system controller 14 are performed in parallel, so that a storage capacity of less than one frame, for example, image data for 10 lines can be stored. A line memory 64 is used.

  A console device 13 shown in FIG. 1 is a general personal computer, and is connected to a system controller 14 by a high-speed serial communication line using an optical fiber. The console device 13 operates the system controller 14 according to the installed X-ray imaging system operation program. The console device 13 receives the image data output from the panel unit 12 via the system controller 14 and displays an image based on the image data on the monitor.

  Examples of the operation of the system controller 14 by the console device 13 include X-ray line type and quality setting for the X-ray exposure device 11, execution or release of the reset mode of the panel unit 12, steady reset mode, and additional reset mode. There are types of reset driving to be executed, one frame period T when sequential reset driving is performed in the additional reset mode, the number of frames when parallel reset driving is performed in the additional reset mode, imaging condition setting, imaging request, and the like. These operations are performed by a keyboard or a pointing device such as a mouse constituting the console device 13.

  In the imaging condition setting, for example, the type of imaging to be performed, the X-ray exposure time, the use / non-use of the Bucky unit 24, the image size, and the like are set. The types of shooting are, for example, general shooting, energy subtraction shooting, and fluoroscopic shooting. X-ray exposure time, use / non-use of the Bucky unit 24, image size, and the like are input from the console device 13 based on the age, sex, imaging region, imaging mode, and the like of the subject H. The photographing request is made by operating the photographing switch 66 connected to the console device 13, for example.

  The system controller 14 is a general personal computer, and comprehensively controls the X-ray exposure apparatus 11 and the panel unit 12 based on an installed X-ray imaging system control program. The system controller 14 includes a communication I / F 67, a CPU 68, a memory 69, a DSP 70, a storage 71, an exposure control circuit 72, and the like, which are connected by a data bus 73.

  The communication I / F 67 is a communication circuit that performs a high-speed serial communication line using an optical fiber, and is connected to the panel unit 12 and the console device 13. The CPU 68 controls the exposure control circuit 72 connected to the X-ray exposure apparatus 11 when the X-ray line type / quality, exposure time, etc. are set by the console device 13, and the X-ray source The X-ray line type / quality and exposure time are set in the control circuit 18. The exposure control circuit 72 is a dedicated circuit for controlling the X-ray exposure apparatus 11 and is connected to an external board connection terminal of the system controller 14.

  The CPU 68 transmits a control command of the panel unit control circuit 28 via the communication I / F 67 or a command register 59 when a control request such as execution or cancellation of the reset mode or a photographing request is input by the console device 13. Write a control command to The control command is a command for causing the panel unit control circuit 28 to perform a prescribed operation, and the control command is a command for causing the panel unit control circuit 28 that is operating based on the control command to perform an interrupt operation. It is an instruction.

  The CPU 68 determines the type of reset driving executed in the steady reset mode and the additional reset mode, one frame period T when sequentially performing the reset driving in the additional reset mode, the number of frames when performing the parallel reset driving in the additional reset mode, and the X-ray. When parameters used for control of the panel unit 12 such as exposure time, use / non-use of the Bucky unit 24, image size, etc. are input from the console device 13, the parameters in the parameter register 61 are rewritten.

  The memory 69 stores various data and image data transmitted from the panel unit 12 when the CPU 68 controls each unit. A digital signal processor (hereinafter abbreviated as DSP) 70 generates one frame of image data from a plurality of lines of image data stored in the memory 69, and performs various image processing such as gradation adjustment and gamma correction on the image data. To generate an image suitable for display on the monitor of the console device 13. An image that has been subjected to various types of image processing by the DSP 70 (hereinafter simply referred to as an image or a captured image) is stored in a storage 71 configured by a memory, an HDD, or the like, and is appropriately read out by the console device 13.

  The operation when performing general imaging will be described with reference to the flowchart of FIG. 12 and the timing chart of FIG. As shown in FIG. 1, when the X-ray imaging system 10 is activated, the panel unit control circuit 28 goes through an initial state in which each part of the panel unit 12 is in an operable state, and is in a NOP (Not Operation) state. It becomes.

  In the NOP state, the FPD 25 and the TFT gate control circuit 26 are stopped. However, the charge amplifier 54 of the readout circuit 27 is in a reset state because the reset switch 54c is turned on by the panel unit control circuit 28. Thereby, unnecessary signal charges in the charge amplifier 54 are released.

  The control instruction is not written in the instruction register 59 in the NOP state, and the state register 60 is written in the NOP state. Further, the parameter register 61 immediately after the start is applied with the A surface 61a for the reset mode.

  After completing the preparation for the system operation, the system controller 14 writes the control command “reset mode setting” in the command register 59 of the panel unit control circuit 28.

  The panel unit control circuit 28 shifts from the NOP state to the reset mode based on the control instruction “reset mode setting” of the instruction register 59 and rewrites the contents of the state register 60 to “reset mode”. Further, the panel unit control circuit 28 refers to the parameter register 61 to obtain one frame period T of reset driving sequentially, and from this one frame period T, one frame period t of parallel reset driving and the shift clock signal CPV. Determine the period. For example, when one frame period T of sequential reset driving is 50 msec, one frame period t of parallel reset driving is 4 msec which is 1/12.

The panel unit control circuit 28 causes the TFT gate control circuit 26 to start a steady reset mode. In the steady reset mode, the parallel reset driving is repeated. As a result, a parallel reset is started in which unnecessary signal charges accumulated in each pixel 41 of the FPD 25 are sequentially read out for 12 rows. The selector 50 transmits a 1-frame completion signal FC to the panel unit control circuit 28 when the shifted strobe signal STV is input from each of the gate control ICs 51 _{1 to} 51 ₁₂ .

  The panel unit control circuit 28 refers to the instruction register 59 when the one-frame completion signal FC is input, confirms that it is “reset mode”, and causes the TFT gate control circuit 26 to execute the steady reset mode. Thereby, in the panel unit 12 in the reset mode, the parallel reset is repeatedly executed, so that the residual charge of the FPD 25 can be minimized.

  When one frame period T of reset driving is sequentially set by the console device 13, the setting content is transmitted to the panel unit control circuit 28 by the system controller 14, and the corresponding item of the parameter register 61 is rewritten. The panel unit control circuit 28 determines a new shift clock signal CPV and one frame period t of the parallel reset driving based on the rewritten one frame period T, and continues the parallel reset driving based on these.

  The system controller 14 refers to the status register 60 of the panel unit control circuit 28 and confirms whether or not the photographing is possible. For example, when the status register 60 is in the “reset mode”, the system controller 14 determines that photographing is possible and transmits the fact to the console device 13. The console device 13 displays on the monitor or the like that the photographing is possible and notifies the user.

  The system controller 14 transmits a control command “shooting request” to the panel unit control circuit 28 when the shooting switch 66 connected to the console device 13 is operated by the user.

  When the panel unit control circuit 28 receives the control command “shooting request”, the panel unit control circuit 28 waits for one frame of the currently executed parallel reset driving to shift to the additional reset mode from the steady reset mode. In the additional reset mode for general imaging, the TFT gate control circuit 26 sequentially starts reset driving. As a result, a sequential reset is started in which unnecessary signal charges accumulated in each pixel 41 of the FPD 25 are sequentially read out row by row. Since the sequential reset has better signal charge emission characteristics than the parallel reset, it is possible to discharge unnecessary signal charges remaining in the parallel reset. Moreover, since the current variation of the FPD 25 does not occur in the sequential reset, the image noise caused by the current variation can be reduced as compared with the case where only the parallel reset is repeated.

  Simultaneously with the transition to the additional reset mode, the panel unit control circuit 28 drives the drive mechanism 32 of the bucky unit 24 to move the grid 31 in a direction parallel to the X-ray detection surface 25a of the FPD 25. The vibration generated in the panel unit 12 due to the movement of the grid 31 converges to such an extent that the imaging is not affected after the settling time has elapsed. For this reason, if one frame period T of sequential reset driving is set longer than the settling time, the influence of vibration by the bucky unit 24 can be prevented.

  When the one-frame completion signal FC for reset driving is sequentially input from the selector 50, the panel unit control circuit 28 switches the operation mode from the reset mode to the general photographing mode, and rewrites the status register 60 to “general photographing mode”. Further, the parameter register 61 is switched from the A surface 61a to the B surface 61b. After initializing the TFT gate control circuit 26, the panel unit control circuit 28 performs accumulation driving for holding all TFTs 46 in the OFF state during the X-ray exposure time stored in the parameter register 61. 26. Note that the initialization of the TFT gate control circuit 26 is performed in order to eliminate malfunction caused by switching of the parameter register 61.

  The panel unit control circuit 28 transmits a response command “X-ray exposure permission” to the system controller 14 at the end of the reset mode. The system controller 14 that has received the response command “X-ray exposure permission” controls the X-ray source control circuit 18 by the exposure control circuit 72 to cause the X-ray source 17 to emit X-rays.

  In this embodiment, when the system controller 14 confirms the state of the panel unit 12 or receives a command, X-rays can be exposed at an optimal timing. Therefore, it is not necessary to control the panel unit 12 by being electrically connected to the X-ray irradiation apparatus 11. Therefore, the panel unit 12 of the present invention can also be applied to various diagnostic systems configured to be able to access various registers or receive commands.

  The time lag from the imaging request until the X-rays are exposed is a time obtained by adding one frame period t of parallel reset driving and one frame period T of sequential reset driving at maximum. In this embodiment, since one frame period T of sequential reset driving is 50 msec and one frame period t of parallel reset driving is 4 msec, the time lag is 54 msec at the maximum. This time lag is significantly shorter than the reset operation in which signal charges are sequentially read out row by row in the conventional radiographic apparatus.

  Also, the time lag variation from the imaging request until the X-ray is exposed is 4 msec, which is one frame period t of the parallel reset driving at the maximum. Thereby, it is possible to prevent an erroneous operation caused by the time lag being too long and the time lag variation being large.

  The X-rays exposed by the X-ray source 17 pass through the subject H, enter the X-ray detection surface 25a, and are converted into signal charges by the X-ray conversion layer. The generated signal charge is collected at the pixel electrode 44 of each pixel 41 and accumulated by the capacitor 45.

  The panel unit control circuit 28 causes the TFT gate control circuit 26 to start reading after the X-ray exposure time has elapsed. Further, the panel unit control circuit 28 turns off the reset switch 54c of the charge amplifier 54 to release the reset state. Since the charge amplifier 54 is reset until immediately before reading the signal charges from the FPD 25, the influence of unnecessary signal charges can be reduced.

  By the reading drive of the TFT gate control circuit 26, data reading for reading the signal charges accumulated in each pixel 41 of the FPD 25 to the data line DL line by line is started. The read signal charge is converted to an analog voltage by the charge amplifier 54, selected by the multiplexer 55, and converted to digital pixel data by the A / D converter 56. The panel unit control circuit 28 generates image data for each line from the pixel data transmitted from the A / D converter 56 and stores it in the line memory 64.

  The panel unit control circuit 28 transmits a “start one frame data” command to the system controller 14 simultaneously with the start of the reading drive. The system controller 14 that has received the “start one frame data” command transmits a control command “one line data request” to the panel unit control circuit 28 when the image data can be received.

  The panel unit control circuit 28 that has received the control command “one line data request” reads one line of image data from the line memory 64, converts it into serial data, and transmits it to the system controller 14 in units of packets for each line. The system controller 14 stores the received image data for one line in the memory 69, and if it can be received, transmits the next control command “request for one line data” to the panel unit control circuit 28. When the system controller 14 receives a predetermined number of lines, that is, one frame of image data, the system controller 14 stops transmitting the control command “1-line data request” to the panel unit control circuit 28.

  In the system controller 14, the DSP 70 generates one frame of image data from a plurality of lines of image data stored in the memory 69, performs various image processing, and stores the image data in the storage 71. The console device 13 reads the image data from the storage 71 and displays the image on the monitor.

  After completing the transmission of the image data, the panel unit control circuit 28 switches from the general photographing mode to the reset mode, and rewrites the status register 60 to “reset mode”. Further, the parameter register 61 is switched to the A surface 61a. The panel unit control circuit 28 causes the TFT gate control circuit 26 to start parallel reset driving and turns on the reset switch 54c of the charge amplifier 54, thereby releasing unnecessary signal charges.

  When reset mode cancellation is set by the console device 13 during the reset mode, a control command “reset mode cancellation” is transmitted from the system controller 14 to the panel unit control circuit 28. The panel unit control circuit 28 that has received the control command “cancel reset mode” immediately cancels the reset mode and shifts to the NOP state. Thereby, when it is desired to stop the operation of the panel unit 12 urgently due to malfunction or the like, the panel unit 12 can be quickly brought into the NOP state.

  Similar to the general imaging described above, by selecting the reset driving in the steady reset mode and the additional reset mode, and setting the frame period T of the sequential reset driving executed in the additional reset mode or the number of frames of the parallel reset driving, Special photographing such as infant photographing, orthopedic diagnostic photographing, and fluoroscopic photographing can be appropriately performed.

  As shown in FIGS. 14 and 15, in pediatric imaging, parallel reset driving is repeated in the steady reset mode, and parallel reset driving is executed for the set number of frames in the additional reset mode. Further, since the time lag until X-ray exposure is given priority, the Bucky unit 24 is not used. When the frame period t of the parallel reset drive is 8 msec, for example, and the number of frames in the additional reset mode is 1 frame, for example, the time lag from the imaging request to the X-ray exposure is 16 msec at maximum, and the variation in the time lag is maximum Is 8 msec. As a result, a child who is difficult to stand still for a long time can be photographed at an optimal timing.

  As shown in FIGS. 16 and 17, in the shaping diagnosis imaging, the reset driving is sequentially repeated in the steady reset mode, and one frame of reset driving is sequentially executed in the additional reset mode. In order to prioritize the sharpness of the image, the Bucky unit 24 is used. According to this, since only sequential reset driving that does not cause deterioration in image quality due to current fluctuations is used, it is possible to obtain an image quality that is optimal for shaping diagnosis.

  As shown in FIGS. 18 and 19, in fluoroscopic imaging, the reset driving is sequentially repeated in the steady reset mode, and the parallel reset driving is executed for the set number of frames in the additional reset mode. In order to maintain the frame rate of continuous shooting, the Bucky unit 24 is not used. According to this, since sequential reset driving is used in the steady reset mode, the time lag until X-ray exposure is longer than when parallel reset driving is used, but imaging is performed with high sensitivity, high DQE, and high frame rate. be able to.

  In the above embodiment, the type of reset drive executed by the user in the steady reset mode and the additional reset mode, the one-frame cycle of the sequential reset drive executed in the additional reset mode, or the number of frames of the parallel reset drive, etc. Is set. However, when applied to an X-ray imaging apparatus capable of setting imaging modes such as general imaging and pediatric imaging, the panel unit control circuit 28 automatically sets the items relating to the reset according to the selected imaging mode. You may make it set to. This eliminates the need for user settings regarding resetting.

  In the above-described embodiment, the system controller 14 automatically writes the control command “reset mode setting” in the command register 59 after the X-ray imaging system 10 is activated, but after waiting for the setting in the console device 13. The instruction register 59 may be written. In addition, although one frame period T of reset driving can be set sequentially, for example, one frame period per gate control IC 51 may be set.

  In addition, the panel unit control circuit 28 transmits one line of image data as it is to the system controller 14. However, even if the panel unit control circuit 28 performs image processing such as filter processing as much as possible, the panel unit control circuit 28 transmits the image data. Good. Further, one line of image data may be transmitted to the system controller 14 as it is without being stored in the line memory 64.

  Further, the charge amplifier 54 is always in the reset state except when the TFT gate control circuit 26 performs the read driving, but may be in the reset state only during the reset mode.

  In each of the above embodiments, a direct conversion type FPD has been described as an example, but the present invention can also be applied to an indirect conversion type FPD. In addition, while an example of a standing X-ray imaging apparatus that performs imaging while the subject is standing up has been described, a radiographic imaging apparatus that performs imaging while lying on the examination table and breast cancer screening It can also be applied to mammography and the like used in

  The X-ray imaging system according to the present invention has been described above. However, the present invention is not limited to the above-described embodiments, and various improvements and modifications may be made without departing from the gist of the present invention. Of course.

DESCRIPTION OF SYMBOLS 10 X-ray imaging system 11 X-ray exposure apparatus 12 Panel unit 13 Console apparatus 14 System controller 24 Bucky unit 25 FPD
26 TFT gate control circuit 27 Reading circuit 28 Panel unit control circuit 36 TFT array 41 Pixel 45 Capacitor 46 TFT
54 Charge amplifier 54c Reset switch 50 Selector 51 Gate control IC
55 selector

Claims (8)

A radiation detector that detects radiation transmitted through a subject, converts the radiation into signal charges, and accumulates the signal charges by a plurality of pixels arranged in a row direction and a column direction;
A plurality of switching means for sequentially reading out the signal charges accumulated in the pixels one by one from each of a plurality of pixel groups obtained by dividing the pixels into a plurality of rows;
The first control procedure or the second control procedure until at least a first control procedure and a second control procedure used for controlling each of the switching means are received and an imaging request for requesting the radiation detector to detect radiation is received. And an additional reset mode in which at least one frame of the first control procedure or the second control procedure is executed after completion of the control procedure being executed when the imaging request is received. Read control means having
A radiation detection apparatus comprising: control procedure selection means for selecting each of the control procedures used in the steady reset mode and the additional reset mode.   The first control procedure is a parallel reset that simultaneously drives the switching units to sequentially read unnecessary signal charges accumulated in the pixels in a plurality of rows, and the second control procedure includes the switching units. The radiation detection apparatus according to claim 1, wherein the radiation detection apparatus is sequentially reset by sequentially driving unnecessary signal charges stored in the respective pixels and sequentially reading unnecessary signals one row at a time.   The radiation detection apparatus according to claim 1, further comprising an additional reset mode adjustment unit that sets one frame period or the number of frames of the control procedure of the additional reset mode.   The radiation detection apparatus according to claim 1, further comprising a reset mode setting unit configured to set execution or stop of the steady reset mode and the additional reset mode.   And a shooting mode selection unit that selects one of a plurality of types of shooting modes set based on the subject or shooting purpose, and the control procedure selection unit selects the shooting selected by the shooting mode selection unit. The radiation detection apparatus according to claim 1, wherein the control procedure used in the standby reset mode and the additional reset mode is selected based on a mode.   Information converting means for converting signal charges read from the radiation detector that has detected radiation into electrical information, and the information converting means so that unnecessary signal charges accumulated in the information converting means are released. 2. The reset means for resetting the information conversion means to release the reset state of the information conversion means by the reset means in conjunction with the start of reading of the signal charge. The radiation detection apparatus in any one of -5. The first control procedure or the second control procedure for reading out signal charges from the radiation detector is repeated until a radiographing request for detecting radiation is received from the radiation detector that detects radiation transmitted through the subject and accumulates signal charges. Reading unnecessary signal charges accumulated in a plurality of pixels of the radiation detector;
When the imaging request is received, at least one frame of the first control procedure or the second control procedure is executed after waiting for the completion of the control procedure being executed, and stored in each pixel of the radiation detector. And a step of reading out unnecessary signal charges. A radiation exposure device for exposing the subject to radiation;
The radiation detection apparatus according to claim 1,
A control device for controlling the radiation exposure device and the radiation detection device;
The readout control means of the radiation detection device transmits a radiation exposure permission signal to the control device at the end of the additional reset mode, and the control device responds to the radiation exposure permission signal with the radiation exposure device. A radiographic imaging system characterized by exposing radiation to radiation.

Images