WO2013062052A1

WO2013062052A1 - Radiographic display system, radiographic display device, radiographic imaging device, program, radiograph display method, and recording medium

Info

Publication number: WO2013062052A1
Application number: PCT/JP2012/077613
Authority: WO
Inventors: 大田　恭義; 西納　直行; 中津川　晴康; 岩切　直人; 北野　浩一
Original assignee: 富士フイルム株式会社
Priority date: 2011-10-26
Filing date: 2012-10-25
Publication date: 2013-05-02

Abstract

Provided is a radiograph display system that carries out control in such a manner that imaging is continuously performed by an electronic cassette, and if a condition is established in which the number of pixels (number of bins), which are read through the synthesis of charges by thin-film transistors contained in a plurality of adjacent pixels in the electronic cassette, has increased, a frame image combined with a still image obtained by performing imaging immediately before said condition is established, in other words, a still image in which there is no disturbance of the display image, is displayed until the frame image of a predetermined number of frames.

Description

Radiographic image display system, radiographic image display device, radiographic image capturing device, program, radiographic image display method, and storage medium

This application claims the priority of Japanese application No. 2011-235321 filed on October 26, 2011 and Japanese application No. 2011-235322 filed on the same day, the entire text of which is incorporated herein by reference.
The present invention relates to a radiation image display system, a radiation image display device, a radiation image capturing device, a program, a radiation image display method, and a storage medium, and in particular, a radiation image display for displaying a radiation image obtained by continuous imaging. The present invention relates to a system, a radiographic image display apparatus, a radiographic image capturing apparatus, a program, a radiographic image display method, and a storage medium.

In recent years, radiation detectors such as FPD (Flat Panel Detector), which can arrange radiation sensitive layers on TFT (Thin Film Transistor) active matrix substrates and convert radiation directly into digital data (sometimes called "electronic cassettes") Has been put into practical use, and a radiographic imaging apparatus that takes a radiographic image represented by the irradiated radiation using this radiation detector has been put into practical use. The radiation detector used in this radiographic imaging apparatus has an indirect conversion system in which radiation is converted into light by a scintillator and then converted into electric charge in a semiconductor layer such as a photodiode, or the like. There is a direct conversion method in which a semiconductor layer such as amorphous selenium converts into electric charge, and there are various materials that can be used for the semiconductor layer in each method.

By the way, in this kind of radiographic image capturing apparatus, there is an apparatus that can also capture a moving image in addition to capturing a still image of a radiographic image. By using this radiographic imaging device, the state of the patient's body is displayed in real time as a moving image (perspective image) by the display device, so that the endoscope reaches the lesion while observing the moving image, The lesioned part can be treated while observing the lesioned part using the endoscope. Further, in this radiographic imaging apparatus, while observing the moving image, the distal end of a catheter having various instruments attached to the distal end reaches the lesioned part, and treatment is performed by operating the catheter outside the body. ) Etc. can also be performed.

As a technique related to a radiographic image capturing apparatus capable of capturing both this kind of still image and moving image, Japanese Patent Application Laid-Open No. 2008-83031 discloses a sensor array including a plurality of sensors for detecting incident radiation. The electronic cassette type radiation detection apparatus has a connection part with a detachable additional function module, and the additional function module is connected so that the photographing mode is a still image. An electronic cassette type radiation detection apparatus having a selection means for switching to a selectable state from photographing and moving image photographing is disclosed.

Japanese Patent Laid-Open No. 2005-287773 discloses an area sensor, shooting mode setting means for selecting one shooting mode from a plurality of preset shooting modes, and shooting output and offset output from the area sensor. An image comprising: correction means for executing the used arithmetic processing; and control means for controlling operation of the area sensor and arithmetic processing by the correction means in accordance with a signal from the photographing mode setting means. An imaging device is disclosed.

In addition, as a technique related to moving image shooting, for example, techniques described in the following documents have been proposed.

In Japanese Patent Laid-Open No. 2006-158728, a subject is irradiated with radiation at a predetermined cycle from a radiation irradiation unit, a subject image based on the irradiated radiation is detected by a photoelectric conversion circuit, and an offset image is periodically acquired. In accordance with the change in the acquired periodic offset image, the radiation irradiation period of the radiation irradiation unit and the reading period of the subject image from the photoelectric conversion circuit are controlled so that the offset photographing immediately after the start of the photographing where the offset fluctuation occurs. It has been proposed that the subject image is alternately corrected and the subject image is accurately offset corrected, and if the offset is stabilized, the subject can be continuously photographed at a high frame rate.

In Japanese Unexamined Patent Application Publication No. 2011-91771, a conversion unit in which a plurality of pixels each having a conversion element, an output switch element, and an initialization switch element are arranged, an output drive circuit for controlling an output operation, An initialization drive circuit for controlling the initialization operation, a read circuit for performing a signal sample-hold operation for temporarily holding an electrical signal read through the transmission path, and a reset operation for resetting the transmission path; The end of the output operation of the predetermined row and the start of the output operation of another row after the end of the reset operation, and the start of the signal sample hold operation after the end of the output operation of the predetermined row and the start of the output operation of the other row And a control unit for controlling so that the reset operation and the initialization operation after the signal sample and hold operation are finished and the reset operation after the initialization operation is finished are performed. It has been proposed that it is possible to obtain an image signal having a good S / N ratio while achieving a desired frame time.

In addition, since it is necessary to shorten the readout time for moving images, a binning readout method for simultaneously reading out charges on a plurality of lines as in the technique described in Japanese Patent Application Laid-Open No. 2007-68014 when reading out charges according to the radiation dose. Thus, the reading time can be shortened by the technique of simultaneously reading a plurality of lines. In Japanese Patent Laid-Open No. 2007-68014, the voltage supplied from the vertical drive circuit to the transfer unit is varied according to the number of pixels to be read simultaneously, thereby increasing the electrical offset component and decreasing the output voltage of the pixel output amplifier. It has been proposed to prevent this.

By the way, in this type of radiographic imaging apparatus, a plurality of pixels configured to include a sensor unit that generates charges according to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit are matrixed. Arranged in a shape. In this radiographic imaging device, charges generated by a plurality of adjacent pixels of the radiation detector are synthesized for the purpose of reading out image information obtained by radiographing at a high speed and improving imaging sensitivity. In some cases, so-called binning is performed.

However, in the case where an image captured by a radiographic imaging apparatus capable of performing moving image imaging as described above is displayed on a display device, and charge is synthesized by binning during imaging in the radiographic imaging apparatus. When the number of pixels to be read out (hereinafter also referred to as “binning number”) is increased, there is a problem in that the display image for several frames may be disturbed from that time.

That is, the switching element provided in the radiation detector of the radiographic imaging apparatus generates feedthrough noises having opposite polarities at the timing when turned on and when turned off.

On the other hand, the electric charge read out by each switching element of the radiation detector is converted into a voltage while being integrated by an amplifier at a predetermined period, and then converted into a digital value by an A / D (analog / digital) converter. Is done. Therefore, normally, two feedthrough noises having opposite polarities are integrated by the amplifier, so that each feedthrough noise is canceled and the influence of the feedthrough noise can be prevented.

On the other hand, before and after the binning number is increased in the radiation detector, the wiring capacity of the signal wiring for outputting the electric charge read by the switching element changes abruptly. As a result, the display image is considered to be disturbed because the cancellation of the feedthrough noise cannot follow this change.

In the techniques described in Japanese Patent Application Laid-Open Nos. 2006-158728 and 2011-91971, moving image quality that becomes unstable when switching the number of lines to be read simultaneously in the binning reading method (hereinafter sometimes referred to as binning number) is increased. There is room for improvement because it has not been considered.

In the technique described in Japanese Patent Application Laid-Open No. 2007-68014, the voltage supplied from the vertical drive circuit to the transfer unit is varied according to the number of pixels to be read at the same time so as to avoid the dynamic range deterioration and the sensitivity characteristic deterioration. However, as described above, there is room for improvement since the unstable moving image quality that occurs when switching the increase in the number of binning is not taken into consideration.

The present invention has been made in view of the above, and a radiographic image display system, a radiographic image display apparatus, a radiographic image capturing apparatus, a program, and the like, which can suppress the occurrence of disturbance of a display image immediately after the number of binning is increased, A radiation image display method and a storage medium are provided.

In addition, the present invention provides a radiation moving image photographing apparatus, a radiation moving image photographing system, a radiation moving image photographing method, and a radiation moving image photographing program that stabilize the moving image quality at the time of changing photographing conditions such as switching of the number of binning.

A first aspect of the present invention is a radiographic image display system including a sensor unit that generates charges according to irradiated radiation, and a switching element for reading out the charges generated by the sensor unit. A radiographic imaging device having a radiation detector in which a plurality of pixels are arranged in a matrix, display means for displaying an image taken by the radiographic imaging device, and continuous imaging by the radiographic imaging device And when the condition that the number of pixels read out by combining the charges by the switching elements included in the plurality of adjacent pixels by the radiographic imaging apparatus is satisfied is the predetermined number of frames. Up to the frame image is displayed in combination with a still image obtained by shooting immediately before the condition is satisfied. Has a control means for controlling said display means so as to, a.

According to the first aspect, a plurality of pixels configured to include a sensor unit that generates charges according to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit are arranged in a matrix. An image photographed by a radiation image photographing apparatus provided with the radiation detector is displayed on the display means.

Here, in the first aspect, the control unit continuously captures images with the radiographic image capturing device, and charges are synthesized by the switching elements included in the plurality of adjacent pixels by the radiographic image capturing device. When the condition that the number of pixels to be read (binning number) is increased is satisfied, a frame image with a predetermined number of frames is combined with a still image obtained by shooting immediately before the condition is satisfied The display means is controlled so as to display.

As described above, according to the first aspect, pixels that are continuously imaged by the radiographic image capturing device, and charges are synthesized and read by the switching elements included in a plurality of adjacent pixels by the radiographic image capturing device. If the condition that the number (binning number) is increased is satisfied, up to a predetermined number of frame images, a still image obtained by photographing immediately before the condition is satisfied, that is, a display image is disturbed. Since the display is controlled so as to be combined with a still image that is not present, it is possible to suppress the occurrence of disturbance of the display image immediately after the binning number is increased.

In the first aspect, when the condition is satisfied, the control unit superimposes a still image obtained by photographing immediately before the condition is satisfied up to a predetermined number of frame images. The display means may be controlled to display in a state. Thereby, it is possible to smoothly shift to the display of the image that is actually captured.

In particular, when the condition is satisfied, the control unit synthesizes still images obtained by photographing immediately before the condition is satisfied at a predetermined ratio up to a predetermined number of frame images. The display means may be controlled to display in a state. Thereby, it is possible to realize a suitable display state according to the preference and application of the viewer of the display image, the type of the imaging target part to be displayed, and the like.

In addition, when the condition is satisfied, the control unit gradually increases the ratio of the still image to a still image obtained by photographing immediately before the condition is satisfied, up to a predetermined number of frame images. The display means may be controlled so as to display in a synthesized state at a low level. Thereby, it is possible to shift to the display of the actually captured image more smoothly.

In addition, when the condition is satisfied, the control means sets a still image obtained by photographing immediately before the condition is satisfied, up to a predetermined number of frame images, to a ratio of 1 to the still image. The display means may be controlled to display in a combined state as a pair. Thereby, it is possible to display an actually captured image while suppressing the occurrence of a disturbance in the display image.

In addition, when the condition is satisfied, the control unit fades out a still image obtained by photographing immediately before the condition is satisfied, up to an intermediate image of a predetermined number of frame images. The display means may be controlled to display the remaining image while fading in the image. Thereby, it is possible to shift to the display of the actually captured image more smoothly.

Further, when the condition is satisfied, the control means displays a still image obtained by photographing immediately before the condition is satisfied, up to an intermediate image among the frame images of a predetermined number of frames, The display means may be controlled so that the remaining images are displayed as they are. As a result, it is possible to more reliably prevent the display image from being disturbed.

Further, the control means determines whether or not the condition is satisfied by determining whether or not the radiographic image capturing apparatus is switched from a state where still image capturing is performed to a state where moving image capturing is performed. The control means may determine whether or not the condition is satisfied by determining whether or not a frame rate of imaging performed by the radiation image capturing apparatus is increased. The means determines whether or not the condition is satisfied by determining whether or not the radiographic imaging apparatus has switched from a state in which progressive scanning is being performed to a state in which interlaced scanning is performed. Also good. As a result, it is possible to more easily determine whether or not the number of binning has been increased.

Further, the first aspect may further include a receiving unit that receives an input of the predetermined number of frames. Thereby, the predetermined number of frames can be easily set.

A second aspect of the present invention is a radiographic image display device including a sensor unit that generates charges according to irradiated radiation and a switching element for reading out the charges generated by the sensor unit. Display means for displaying an image taken by a radiographic imaging device having a radiation detector in which a plurality of pixels are arranged in a matrix, and continuous radiography by the radiographic imaging device, and the radiographic image When the condition that the number of pixels to be read out by combining the charges by the switching elements included in the plurality of adjacent pixels by the imaging device is satisfied, up to a frame image of a predetermined number of frames, the condition The display means is controlled so as to be displayed in combination with a still image obtained by photographing immediately before the establishment of And control means that includes a.

According to the second aspect, a plurality of pixels configured to include a sensor unit that generates charges according to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit are arranged in a matrix. An image photographed by a radiation image photographing apparatus provided with the radiation detector is displayed on the display means.

Here, in the second aspect, the control means continuously captures images with the radiographic image capturing device, and charges are synthesized by the switching elements included in the plurality of adjacent pixels by the radiographic image capturing device. When the condition that the number of pixels to be read (binning number) is increased is satisfied, a frame image with a predetermined number of frames is combined with a still image obtained by shooting immediately before the condition is satisfied The display means is controlled so as to display.

As described above, according to the second aspect, pixels that are continuously imaged by the radiographic image capturing device, and charges are synthesized and read by the switching elements included in a plurality of adjacent pixels by the radiographic image capturing device. If the condition that the number (binning number) is increased is satisfied, up to a predetermined number of frame images, a still image obtained by photographing immediately before the condition is satisfied, that is, a display image is disturbed. Since the display is controlled so as to be combined with a still image that is not present, it is possible to suppress the occurrence of disturbance of the display image immediately after the binning number is increased.

According to a third aspect of the present invention, there is provided a radiographic imaging device including a sensor unit that generates a charge corresponding to the irradiated radiation and a switching element for reading out the charge generated by the sensor unit. A plurality of pixels arranged in a matrix, and continuous imaging with the radiation detector, and the charge is synthesized by the switching elements included in the adjacent pixels by the radiation detector. If the condition that the number of pixels read out is increased and the condition is satisfied, the image data is combined with the still image obtained by the shooting immediately before the condition is satisfied, up to a predetermined number of frame images. Generating means for generating.

According to the third aspect, a plurality of pixels configured to include a sensor unit that generates a charge according to the irradiated radiation and a switching element for reading out the charge generated by the sensor unit are arranged in a matrix. The condition that the number of pixels read out by combining the charges by the switching elements included in the plurality of adjacent pixels by the radiation detector and increasing the number of pixels was continuously satisfied. In this case, the image data is generated by the generation unit in a state of being combined with a still image obtained by photographing immediately before the condition is satisfied, up to a predetermined number of frame images.

As described above, according to the third aspect, the number of pixels that are continuously photographed by the radiation detector and are combined and read by the switching elements included in the plurality of adjacent pixels by the radiation detector ( If the condition that the binning number is increased is satisfied, a still image obtained by photographing immediately before the condition is satisfied, that is, a display image that is not disturbed until a frame image having a predetermined number of frames is satisfied. Since the image data is generated in a state of being combined with the image, it is possible to suppress the occurrence of the disturbance of the display image immediately after the binning number is increased.

According to a fourth aspect of the present invention, there is provided a program including a sensor unit that generates a charge corresponding to irradiated radiation and a switching element for reading out the charge generated by the sensor unit. A plurality of pixels are continuously photographed by a radiographic imaging device having a radiation detector arranged in a matrix, and charges are charged by the switching elements included in the plurality of adjacent pixels by the radiographic imaging device. Determining means for determining whether or not a condition that the number of pixels to be read out is increased and the number of pixels to be read is satisfied, and when the determining means determines that the condition is satisfied, a predetermined number of frames Until the image is displayed, it is displayed in combination with a still image obtained by shooting immediately before the condition is satisfied. It is intended to function as a control means for controlling the display means.

Therefore, according to the fourth aspect, since the computer can be operated in the same manner as the radiological image display apparatus of the second aspect, the display image immediately after the number of binning is increased as in the radiographic image display apparatus. The occurrence of disturbance can be suppressed.

Furthermore, a fifth aspect of the present invention is a radiographic image display method, including a sensor unit that generates charges according to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit. The switching elements that are continuously imaged by a radiographic imaging device including a radiation detector in which a plurality of configured pixels are arranged in a matrix and are included in a plurality of adjacent pixels by the radiographic imaging device A determination step for determining whether or not the condition that the number of pixels to be read out by combining the charges is increased, and a predetermined number of frames when the determination step determines that the condition is satisfied Up to the frame image, it will be displayed in combination with the still image obtained by shooting immediately before the condition is met. And and a control step of controlling the display means.

Therefore, since the fifth mode operates in the same manner as the radiographic image display device of the second mode, it suppresses the occurrence of disturbance in the display image immediately after the binning number is increased, as in the radiographic image display device. Can do.

A sixth aspect of the present invention is a persistent computer-readable storage medium storing a program for causing a computer to execute a radiographic image display process, wherein the radiographic image display process generates a charge corresponding to the irradiated radiation. Imaging is continuously performed by a radiographic imaging apparatus having a radiation detector in which a plurality of pixels configured to include a sensor unit and a switching element for reading out electric charges generated by the sensor unit are arranged in a matrix. Determining whether or not a condition that the number of pixels read out by combining charges by the switching elements included in the plurality of adjacent pixels by the radiographic imaging apparatus is satisfied is satisfied, and the condition is determined by the determination. If it is determined that the above condition is satisfied, the condition is satisfied up to a predetermined number of frame images. Controlling display means to display in a state combined with the obtained still image by capturing just before standing was includes. Since the sixth aspect operates in the same manner as the fourth aspect, similarly, it is possible to suppress the occurrence of a disturbance in the display image immediately after the binning number is increased.

Another aspect of the present invention is a radiographic moving image capturing apparatus including a sensor unit that generates charges according to irradiated radiation and a switching element for reading out the charges generated by the sensor unit. The radiation detector in which a plurality of pixels are arranged in a matrix, and the switching element is turned on / off to read out the electric charge, and the read out electric charge is converted into a voltage by the radiation detector. When the number of pixels read out by combining charges is increased by performing moving image shooting including a plurality of frames and turning on the switching elements included in a plurality of adjacent pixels, the increase is made in advance. Up to a predetermined frame, the stop period from when the switching element is turned off to when the conversion operation is stopped is a frame for capturing the moving image. It is characterized by and a control means for controlling so as to be longer than the predetermined specified time period in accordance with the over and.

According to this aspect, in the radiation detector, the pixels configured to include the sensor unit and the switching element are arranged in a matrix, and charges corresponding to the irradiated radiation are generated in the sensor unit. Read by the switching element.

By the way, noise is generated when the switching element is turned on and off, but the noise at the time of turning on and the noise at the time of turning off are opposite to each other. By including, it is canceled by the integration process.

However, when the shooting conditions change, such as when switching the increase in the number of pixels (binning number) to be read out by combining the charges, the image is considered to be deteriorated.

As a result of analyzing this, immediately after switching to increase the number of binning, the time for generating noise is prolonged, and noise due to switching-off of the switching element is not included in the period of the conversion operation to the voltage of the charge. I understood that it was.

Therefore, in the control means, the switching element is turned on / off to read out the charge, and the read-out charge is converted into a voltage so that the radiation detector performs moving image shooting including a plurality of frames and the adjacent plural In the case where the number of pixels read out by combining charges by the switching elements included in the pixels is increased, from the time of the increase until the predetermined frame, the switching elements are turned off until the conversion operation is stopped. The stop period is controlled to be longer than a predetermined period determined in accordance with the frame rate of moving image shooting.

This makes it possible to stabilize the moving image quality when the shooting conditions change, such as when the number of binning increases.

In this aspect, the radiation detector further includes conversion means for converting the electric charge read by the switching element into voltage, and a reset switch for stopping the conversion operation by the conversion means, and the control means includes: You may make it control a reset switch so that a stop period may become longer than a regulation period. That is, the stop period can be changed by the reset switch.

Further, the control means may further control so that the remaining period after the predetermined frame becomes a specified period. In this case, the control means may be configured to gradually control the specified period so as to control the specified period.

In addition, the detection of whether or not the condition for shifting from the state of performing still image shooting to the state of performing moving image shooting is satisfied, the detection of whether or not the number of pixels has been increased, from the state of performing still image shooting by the radiation detector. Shift to a state in which shooting is performed, or a moving image is shot with a radiation detector and the frame rate of the moving image is increased, or a sequential scanning method that sequentially reads out charges generated in pixels from the odd-numbered row or even-numbered row This can be detected by detecting the establishment of the condition of whether to shift to the jump operation method of reading out the charges generated in each pixel alternately for each line.

Still another aspect of the present invention is a radiation moving image capturing system including the radiation moving image capturing apparatus according to the above aspect and radiation irradiating means for irradiating the radiation detector through a subject.

Still another embodiment of the present invention is a radiographic moving image capturing method including a sensor unit that generates a charge corresponding to irradiated radiation and a switching element for reading out the charge generated by the sensor unit. By turning on and off the switching element of the radiation detector in which a plurality of pixels are arranged in a matrix, the charge is read out, and the read-out charge is converted into a voltage by the radiation detector. A detection step of performing moving image shooting including a plurality of frames and detecting whether or not the number of pixels read out by combining the charges by turning on the switching elements included in the plurality of adjacent pixels is increased; and In the detection step, when the moving image is taken and it is detected that the number of pixels is increased, a predetermined frame from the time when the number is increased Then, a control step of controlling so that a stop period from when the switching element is turned off to when the conversion operation is stopped becomes longer than a predetermined period according to a frame rate of the moving image shooting is included. It is a feature.

Here, as described above, immediately after switching to increase the number of binning, the time during which noise is generated is prolonged, and the noise due to the switching element being turned off is included in the period of the conversion operation of the charge to the voltage. I knew it might not be.

Therefore, in the detection step, the switching element is turned on / off to read out the electric charge, and by performing the conversion operation of the read electric charge into a voltage, the radiation detector performs moving image photographing including a plurality of frames and is adjacent to the voltage. It is detected whether or not the number of pixels read out by combining charges by switching elements included in a plurality of pixels is increased, and in the control step, moving image shooting is performed in the detection step and it is detected that the number of pixels is increased. In such a case, from the time of the increase to the predetermined frame, the stop period from when the switching element is turned off to when the conversion operation is stopped is longer than a predetermined period determined according to the frame rate of moving image shooting. Control.

In this aspect, the radiation detector further includes a conversion unit that converts the electric charge read by the switching element into a voltage, and a reset switch for stopping the conversion operation by the conversion unit, and the control step includes: You may make it control a reset switch so that a stop period may become longer than a regulation period. That is, the stop period can be changed by the reset switch.

Also, the control step may be further controlled so that the remaining period after the predetermined frame becomes a specified period. In this case, the control step may be performed so that the specified period is gradually set when the control is performed so that the specified period is reached.

Still another aspect of the present invention is a radiographic moving image capturing program including a sensor unit that generates electric charge according to irradiated radiation and a switching element for reading out electric charge generated by the sensor unit. By turning on and off the switching element of the radiation detector in which a plurality of pixels are arranged in a matrix, the charge is read out, and the read-out charge is converted into a voltage by the radiation detector. A detection step of performing moving image shooting including a plurality of frames and detecting whether or not the number of pixels read out by combining the charges by turning on the switching elements included in the plurality of adjacent pixels is increased; and In the detection step, when the moving image shooting is performed and it is detected that the number of pixels has been increased, a predetermined frame from the time of increase is detected. A control step for controlling so that a stop period from when the switching element is turned off to when the conversion operation is stopped is longer than a predetermined period according to a frame rate of the moving image shooting. It is characterized by causing a computer to execute processing including the above.

Therefore, in the detection step, the switching element is turned on / off to read out the charge, and the read-out charge is converted into a voltage to perform moving image shooting with a radiation detector and included in a plurality of adjacent pixels. The computer executes a process to detect whether the number of pixels read out by combining the charges by the switching element is increased, and in the control step, it is detected that the number of pixels has been increased by performing moving image shooting in the detection step. In this case, the stop period from when the switching element is turned off until the conversion operation is stopped is longer than a predetermined period that is predetermined according to the frame rate of the moving image shooting until the predetermined frame is increased until the predetermined frame. Causes the computer to execute processing to be controlled.

According to the above-described aspect, the number of pixels (binning number) in which continuous imaging is performed by the radiographic image capturing apparatus and charges are combined and read by the switching elements included in the plurality of adjacent pixels by the radiographic image capturing apparatus. Up to a predetermined number of frame images combined with a still image obtained by shooting immediately before the condition is satisfied, that is, a still image that does not cause disturbance of the display image. Since the display is controlled so as to be displayed, the disturbance of the display image immediately after the binning number is increased can be suppressed.

That is, it is possible to stabilize the moving image quality when the shooting conditions change such as when the increase in the number of binning is switched.

It is a block diagram which shows the structure of the radiation information system which concerns on embodiment. It is a side view which shows an example of the arrangement | positioning state of each apparatus in the radiography room of the radiographic imaging system which concerns on embodiment. It is a cross-sectional schematic diagram which shows schematic structure of the 3 pixel part of the radiation detector which concerns on embodiment. It is the cross-sectional side view which showed schematically the structure of the signal output part of 1 pixel part of the radiation detector which concerns on embodiment. It is a top view which shows the structure of the pixel part of the radiation detector which concerns on embodiment. It is a perspective view which shows the structure of the electronic cassette concerning embodiment. It is a section side view showing the composition of the electronic cassette concerning an embodiment. It is a block diagram which shows the principal part structure of the electrical system of the radiographic imaging system which concerns on embodiment. It is a circuit diagram which shows the structure of the signal processing part which concerns on embodiment. It is a flowchart which shows the flow of a process of the radiographic imaging process program which concerns on 1st Embodiment. It is the schematic which shows an example of the initial stage information input screen which concerns on embodiment. It is a flowchart which shows the flow of a process of the still image photography processing routine program which concerns on embodiment. It is a cross-sectional side view for demonstrating the surface reading system and back surface scanning system of a radiographic image. It is a flowchart which shows the flow of a process of the radiographic imaging process program which concerns on 2nd Embodiment. It is a flowchart which shows the flow of a process of the radiographic imaging process program which concerns on 3rd Embodiment. It is a flowchart which shows the flow of a process of the radiographic imaging process program which concerns on 4th Embodiment. It is a block diagram which shows schematic structure of the signal processing part of the radiation detector which concerns on embodiment. It is a figure which shows the equivalent circuit which paid its attention to 1 pixel part of the radiation detector which concerns on embodiment. It is a control block diagram of the imaging system according to the embodiment. It is a figure for demonstrating the feedthrough noise by ON / OFF of a thin-film transistor. It is a figure which shows the change of QL value for every acquisition frame. It is a figure which shows the delay of the ON timing of a reset switch. It is a flowchart which shows the radiographic imaging photographing preparation control routine which concerns on embodiment. It is a flowchart which shows the radiation irradiation control routine which concerns on embodiment. 4 is a flowchart illustrating an image processing control routine according to the embodiment. It is a flowchart which shows the gradation signal taking-in process routine which concerns on embodiment.

Hereinafter, embodiments for carrying out the present invention will be described in detail with reference to the drawings. Here, a description will be given of an example in which the present invention is applied to a radiation information system that is a system for comprehensively managing information handled in a radiology department in a hospital.

[First Embodiment]
First, the configuration of a radiation information system (hereinafter referred to as “RIS” (Radiology Information System)) 100 according to the present embodiment will be described with reference to FIG. The RIS 100 can shoot moving images in addition to still images. The definition of a moving image means that still images are displayed one after another at a high speed and recognized as a moving image. The still image is shot, converted into an electric signal, transmitted, and the still image is reproduced from the electric signal. This process is repeated at high speed. Therefore, the so-called “frame advance” in which the same area (part or all) is photographed a plurality of times within a predetermined time and continuously reproduced depending on the degree of the “high speed” is also included in the moving image. And

The RIS 100 is a system for managing information such as medical appointments and diagnosis records in the radiology department, and constitutes a part of a hospital information system (hereinafter referred to as “HIS” (Hospital Information System)).

The RIS 100 includes a plurality of radiography requesting terminal devices (hereinafter referred to as “terminal devices”) 140, a RIS server 150, and a radiographic imaging system (hereinafter referred to as a radiographic imaging room (or operating room) in a hospital). , Which is referred to as “imaging system”) 104, and these are connected to a hospital network 102 formed by a wired or wireless LAN (Local Area Network) or the like. The RIS 100 constitutes a part of the HIS provided in the same hospital, and an HIS server (not shown) for managing the entire HIS is also connected to the in-hospital network 102. In addition, the imaging system 104 may be single or three or more facilities. In FIG. 1, the imaging system 104 is installed for each imaging room, but two or more imaging systems 104 are arranged in a single imaging room. May be.

The terminal device 140 is used by doctors and radiographers to input and browse diagnostic information and facility reservations, and radiographic image capturing requests and imaging reservations are also performed via the terminal device 140. Each terminal device 140 includes a personal computer having a display device, and can communicate with the RIS server 150 via the hospital network 102.

On the other hand, the RIS server 150 receives an imaging request from each terminal device 140 and manages a radiographic imaging schedule in the imaging system 104, and includes a database 150A.

Database 150A includes patient (subject) attribute information (name, sex, date of birth, age, blood type, weight, patient ID (Identification), etc.), medical history, medical history, radiation images taken in the past, etc. Information regarding the patient, information regarding the electronic cassette 40 used in the imaging system 104, such as an identification number (ID information), model, size, sensitivity, start date of use, number of times of use, etc., and the electronic cassette 40 It includes the environment information which shows the environment which takes a radiographic image using, ie, the environment (for example, a radiography room, an operating room, etc.) which uses electronic cassette 40.

In addition, medical-related data managed by medical institutions is stored almost permanently, and when necessary, a system (sometimes referred to as a “medical cloud”) that instantly retrieves data from the required location can be used outside the hospital. You may make it acquire the past personal information etc. of a patient (subject) from a server.

The imaging system 104 captures a radiographic image by an operation of a doctor or a radiographer according to an instruction from the RIS server 150. The imaging system 104 includes a radiation generator 120 that irradiates a subject with radiation X (see also FIG. 6) that has been dosed according to the exposure conditions from a radiation source 121 (see also FIG. 2), and a subject. Electrons that incorporate a radiation detector 20 (see also FIG. 6) that absorbs radiation X that has passed through a region to be imaged by the person and generates charges, and generates image information that indicates a radiation image based on the amount of generated charges. A cassette 40, a cradle 130 for charging a battery built in the electronic cassette 40, and a console 110 for controlling the electronic cassette 40 and the radiation generator 120 are provided.

The console 110 acquires various types of information included in the database 150A from the RIS server 150, stores them in the HDD 116 (see also FIG. 8), which will be described later, and uses the information as necessary to use the electronic cassette 40 and the radiation generator. 120 is controlled.

FIG. 2 shows an example of the arrangement state of each device in the radiation imaging room 180 of the imaging system 104 according to the present embodiment.

As shown in FIG. 2, the radiation imaging room 180 includes a standing table 160 used when performing radiography in a standing position and a prone table 164 used when performing radiography in a lying position. The space in front of the standing stand 160 is set as a photographing position 170 of the subject when performing radiography in the standing position, and the space above the supine stand 164 is when performing radiography in the prone position. The imaging position 172 of the subject.

The standing stand 160 is provided with a holding unit 162 that holds the electronic cassette 40, and the electronic cassette 40 is held by the holding unit 162 when a radiographic image is taken in the standing position. Similarly, the holding table 164 is provided with a holding unit 166 that holds the electronic cassette 40, and the electronic cassette 40 is held by the holding unit 166 when a radiographic image is taken in the lying position.

Further, in the radiation imaging room 180, the radiation source 121 is placed around a horizontal axis (see FIG. 5) in order to enable radiation imaging in a standing position and radiation imaging in a lying position by radiation from a single radiation source 121. 2 is provided, and a support moving mechanism 124 is provided which can be rotated in the vertical direction (arrow b direction in FIG. 2) and can be moved in the horizontal direction (arrow c direction in FIG. 2). It has been. Here, the support moving mechanism 124 includes a drive source that rotates the radiation source 121 around a horizontal axis, a drive source that moves the radiation source 121 in the vertical direction, and a drive source that moves the radiation source 121 in the horizontal direction. Each is provided (not shown).

On the other hand, the cradle 130 is formed with an accommodating portion 130A that can accommodate the electronic cassette 40.

When the electronic cassette 40 is not in use, the built-in battery is charged in a state of being housed in the housing portion 130A of the cradle 130. When a radiographic image is taken, the electronic cassette 40 is taken out from the cradle 130 by a radiographer or the like, and the photographing posture is established. If it is in the upright position, it is held in the holding part 162 of the standing base 160, and if it is in the upright position, it is held in the holding part 166 of the standing base 164.

Here, in the imaging system 104 according to the present embodiment, various types of information are transmitted and received between the radiation generator 120 and the console 110 and between the electronic cassette 40 and the console 110 by wireless communication.

The electronic cassette 40 is not used only in a state where it is held by the holding part 162 of the standing base 160 or the holding part 166 of the prone base 164. When photographing, it can be used in a state where it is not held by the holding unit.

The radiation cassette described later is built in the electronic cassette 40. The built-in radiation detector is an indirect conversion method that converts radiation into light with a scintillator and then converts it into charges with a photoelectric conversion element such as a photodiode, and a direct conversion method that converts radiation into charges with a semiconductor layer such as amorphous selenium. Either may be used. The direct conversion type radiation detector is configured by laminating a photoelectric conversion layer that absorbs radiation X and converts it into charges on a TFT active matrix substrate. The photoelectric conversion layer is made of amorphous a-Se (amorphous selenium) containing, for example, selenium as a main component (for example, a content rate of 50% or more), and when irradiated with radiation X, a charge corresponding to the amount of irradiated radiation. By generating a certain amount of charge (electron-hole pairs) internally, the irradiated radiation X is converted into a charge. An indirect conversion type radiation detector indirectly uses a phosphor material and a photoelectric conversion element (photodiode) instead of the radiation-to-charge conversion material that directly converts the radiation X such as amorphous selenium into an electric charge. It may be converted into an electric charge. As phosphor materials, terbium activated gadolinium oxysulfide (Gd2O2S: Tb) (abbreviation GOS) and thallium activated cesium iodide (CsI: Tl) are well known. In this case, radiation X-light conversion is performed by the phosphor material, and light-charge conversion is performed by the photodiode of the photoelectric conversion element. The electronic cassette 40 according to the present embodiment will be described as including an indirect conversion radiation detector.

Next, the configuration of the radiation detector 20 according to the present embodiment will be described. FIG. 3 is a schematic cross-sectional view schematically showing the configuration of the three pixel portions of the radiation detector 20 according to the present exemplary embodiment.

As shown in FIG. 3, in the radiation detector 20 according to the present embodiment, a signal output unit 14, a sensor unit 13 (TFT substrate 30), and a scintillator 8 are sequentially stacked on an insulating substrate 1. The pixel group of the TFT substrate 30 is configured by the signal output unit 14 and the sensor unit 13. A plurality of pixels are arranged in a matrix on the substrate 1, and the signal output unit 14 and the sensor unit 13 in each pixel are configured to overlap each other. Note that an insulating film 11 is interposed between the signal output unit 14 and the sensor unit 13.

The scintillator 8 is formed on the sensor unit 13 via the transparent insulating film 7, and forms a phosphor that emits light by converting radiation incident from above (opposite side of the substrate 1) or from below into light. It is a thing. Providing such a scintillator 8 absorbs the radiation transmitted through the subject and emits light.

The wavelength range of light emitted by the scintillator 8 is preferably the visible light range (wavelength 360 nm to 830 nm), and in order to enable monochrome imaging by the radiation detector 20, the wavelength range of green is included. Is more preferable.

Specifically, the phosphor used in the scintillator 8 preferably contains cesium iodide (CsI) when imaging using X-rays as radiation, and has an emission spectrum of 400 nm to 700 nm when irradiated with X-rays. It is particularly preferable to use CsI (Tl) (cesium iodide with thallium added). Note that the emission peak wavelength of CsI (Tl) in the visible light region is 565 nm.

The sensor unit 13 includes an upper electrode 6, a lower electrode 2, and a photoelectric conversion film 4 disposed between the upper and lower electrodes. The photoelectric conversion film 4 absorbs light emitted from the scintillator 8 and generates charges. It is composed of an organic photoelectric conversion material.

Since it is necessary for the upper electrode 6 to cause the light generated by the scintillator 8 to be incident on the photoelectric conversion film 4, it is preferable that the upper electrode 6 be made of a conductive material that is transparent at least with respect to the emission wavelength of the scintillator 8. It is preferable to use a transparent conductive oxide (TCO) having a high transmittance for visible light and a small resistance value. Although a metal thin film such as Au can be used as the upper electrode 6, TCO is preferable because it tends to increase the resistance value when it is desired to obtain a transmittance of 90% or more. For example, ITO, IZO, AZO, FTO, SnO ₂ , TiO ₂ , ZnO _{2 and the} like can be preferably used, and ITO is most preferable from the viewpoint of process simplicity, low resistance, and transparency. Note that the upper electrode 6 may have a single configuration common to all pixels, or may be divided for each pixel.

The photoelectric conversion film 4 includes an organic photoelectric conversion material, absorbs light emitted from the scintillator 8, and generates electric charges according to the absorbed light. In this way, the photoelectric conversion film 4 containing an organic photoelectric conversion material has a sharp absorption spectrum in the visible range, and electromagnetic waves other than light emitted by the scintillator 8 are hardly absorbed by the photoelectric conversion film 4. The noise generated by the radiation such as being absorbed by the photoelectric conversion film 4 can be effectively suppressed.

The organic photoelectric conversion material constituting the photoelectric conversion film 4 is preferably such that its absorption peak wavelength is closer to the emission peak wavelength of the scintillator 8 in order to absorb light emitted by the scintillator 8 most efficiently. Ideally, the absorption peak wavelength of the organic photoelectric conversion material matches the emission peak wavelength of the scintillator 8, but if the difference between the two is small, the light emitted from the scintillator 8 can be sufficiently absorbed. . Specifically, the difference between the absorption peak wavelength of the organic photoelectric conversion material and the emission peak wavelength with respect to the radiation of the scintillator 8 is preferably within 10 nm, and more preferably within 5 nm.

Examples of the organic photoelectric conversion material that can satisfy such conditions include quinacridone organic compounds and phthalocyanine organic compounds. For example, since the absorption peak wavelength in the visible region of quinacridone is 560 nm, if quinacridone is used as the organic photoelectric conversion material and CsI (Tl) is used as the material of the scintillator 8, the difference in peak wavelength can be within 5 nm. Thus, the amount of charge generated in the photoelectric conversion film 4 can be substantially maximized. In the present embodiment, the photoelectric conversion film 4 including an organic photoelectric conversion material will be described as an example. However, the present invention is not limited to this, and the photoelectric conversion film 4 may be a material that absorbs light and generates charges. For example, other materials such as amorphous silicon may be applied. When the photoelectric conversion film 4 is made of amorphous silicon, it can be configured to absorb light emitted from the scintillator over a wide wavelength range.

Next, the photoelectric conversion film 4 applicable to the radiation detector 20 according to the present embodiment will be specifically described.

The electromagnetic wave absorption / photoelectric conversion site in the radiation detector 20 according to the present embodiment is configured by an organic layer including a pair of

electrodes

2 and 6 and an organic photoelectric conversion film 4 sandwiched between the

electrodes

2 and 6. be able to. More specifically, this organic layer is a part that absorbs electromagnetic waves, a photoelectric conversion part, an electron transport part, a hole transport part, an electron blocking part, a hole blocking part, a crystallization preventing part, an electrode, and an interlayer contact improvement. It can be formed by stacking or mixing parts.

The organic layer preferably contains an organic p-type compound or an organic n-type compound.

An organic p-type semiconductor (compound) is a donor organic semiconductor (compound) typified by a hole-transporting organic compound and refers to an organic compound having a property of easily donating electrons. More specifically, an organic compound having a smaller ionization potential when two organic materials are used in contact with each other. Accordingly, any organic compound can be used as the donor organic compound as long as it is an electron-donating organic compound.

An organic n-type semiconductor (compound) is an acceptor organic semiconductor (compound) typified by an electron-transporting organic compound and refers to an organic compound having a property of easily accepting electrons. More specifically, the organic compound having the higher electron affinity when two organic compounds are used in contact with each other. Accordingly, as the acceptor organic compound, any organic compound can be used as long as it is an electron-accepting organic compound.

The materials applicable as the organic p-type semiconductor and the organic n-type semiconductor and the configuration of the photoelectric conversion film 4 are described in detail in Japanese Patent Application Laid-Open No. 2009-32854, and thus the description thereof is omitted. The photoelectric conversion film 4 may be formed by further containing fullerenes or carbon nanotubes.

The thickness of the photoelectric conversion film 4 is preferably as large as possible in terms of absorbing light from the scintillator 8. However, when the thickness is more than a certain level, the photoelectric conversion film 4 is generated in the photoelectric conversion film 4 by a bias voltage applied from both ends of the photoelectric conversion film 4. Since electric field strength is reduced and charges cannot be collected, the thickness is preferably 30 nm to 300 nm, more preferably 50 nm to 250 nm, and particularly preferably 80 nm to 200 nm.

In the radiation detector 20 shown in FIG. 3, the photoelectric conversion film 4 has a single configuration common to all pixels, but may be divided for each pixel.

The lower electrode 2 is a thin film divided for each pixel. The lower electrode 2 can be made of a transparent or opaque conductive material, and aluminum, silver, or the like can be suitably used.

The thickness of the lower electrode 2 can be, for example, 30 nm or more and 300 nm or less.

In the sensor unit 13, by applying a predetermined bias voltage between the upper electrode 6 and the lower electrode 2, one of electric charges (holes, electrons) generated in the photoelectric conversion film 4 is moved to the upper electrode 6. The other can be moved to the lower electrode 2. In the radiation detector 20 of the present embodiment, a wiring is connected to the upper electrode 6, and a bias voltage is applied to the upper electrode 6 through this wiring. In addition, the polarity of the bias voltage is determined so that electrons generated in the photoelectric conversion film 4 move to the upper electrode 6 and holes move to the lower electrode 2, but this polarity is reversed. May be.

The sensor unit 13 constituting each pixel only needs to include at least the lower electrode 2, the photoelectric conversion film 4, and the upper electrode 6. In order to suppress an increase in dark current, the electron blocking film 3 and the hole blocking film are used. 5 is preferably provided, and it is more preferable to provide both.

The electron blocking film 3 can be provided between the lower electrode 2 and the photoelectric conversion film 4. When a bias voltage is applied between the lower electrode 2 and the upper electrode 6, electrons are transferred from the lower electrode 2 to the photoelectric conversion film 4. It is possible to suppress the dark current from increasing due to the injection of.

An electron donating organic material can be used for the electron blocking film 3.

The material actually used for the electron blocking film 3 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 4 and the like, and 1.3 eV or more from the work function (Wf) of the material of the adjacent electrode. Those having a large electron affinity (Ea) and an Ip equivalent to or smaller than the ionization potential (Ip) of the material of the adjacent photoelectric conversion film 4 are preferable. The material applicable as the electron donating organic material is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, and thus the description thereof is omitted.

The thickness of the electron blocking film 3 is preferably 10 nm or more and 200 nm or less, more preferably 30 nm or more and 150 nm or less, and particularly preferably, in order to surely exhibit the dark current suppressing effect and prevent a decrease in photoelectric conversion efficiency of the sensor unit 13. It is 50 nm or more and 100 nm or less.

The hole blocking film 5 can be provided between the photoelectric conversion film 4 and the upper electrode 6. When a bias voltage is applied between the lower electrode 2 and the upper electrode 6, the hole blocking film 5 is transferred from the upper electrode 6 to the photoelectric conversion film 4. It is possible to suppress the increase in dark current due to the injection of holes.

An electron-accepting organic material can be used for the hole blocking film 5.

The thickness of the hole blocking film 5 is preferably 10 nm or more and 200 nm or less, more preferably 30 nm or more and 150 nm or less, and particularly preferably, in order to surely exhibit the dark current suppressing effect and prevent a decrease in photoelectric conversion efficiency of the sensor unit 13. Is from 50 nm to 100 nm.

The material actually used for the hole blocking film 5 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 4 and the like, and 1.3 eV from the work function (Wf) of the material of the adjacent electrode. As described above, it is preferable that the ionization potential (Ip) is large and that the Ea is equal to or larger than the electron affinity (Ea) of the material of the adjacent photoelectric conversion film 4. Since the material applicable as the electron-accepting organic material is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, description thereof is omitted.

In addition, when a bias voltage is set so that holes move to the upper electrode 6 and electrons move to the lower electrode 2 among the charges generated in the photoelectric conversion film 4, the electron blocking film 3 and the hole blocking are set. The position of the film 5 may be reversed. Moreover, it is not necessary to provide both the electron blocking film 3 and the hole blocking film 5. If either one is provided, a certain degree of dark current suppressing effect can be obtained.

A signal output unit 14 is formed on the surface of the substrate 1 below the lower electrode 2 of each pixel. FIG. 4 schematically shows the configuration of the signal output unit 14.

As shown in the figure, the signal output unit 14 according to the present embodiment corresponds to the lower electrode 2, and a capacitor 9 that accumulates the charges transferred to the lower electrode 2, and the electric charges accumulated in the capacitor 9 are electrically A field effect thin film transistor (Thin Film Transistor, hereinafter simply referred to as a thin film transistor) 10 is formed which is converted into a signal and output. The region in which the capacitor 9 and the thin film transistor 10 are formed has a portion that overlaps the lower electrode 2 in a plan view. With this configuration, the signal output unit 14 and the sensor unit 13 in each pixel are thick. There will be overlap in the vertical direction. In order to minimize the plane area of the radiation detector 20 (pixel), it is desirable that the region where the capacitor 9 and the thin film transistor 10 are formed is completely covered by the lower electrode 2.

The capacitor 9 is electrically connected to the corresponding lower electrode 2 via a wiring made of a conductive material penetrating an insulating film 11 provided between the substrate 1 and the lower electrode 2. Thereby, the electric charge collected by the lower electrode 2 can be moved to the capacitor 9.

In the thin film transistor 10, a gate electrode 15, a gate insulating film 16, and an active layer (channel layer) 17 are stacked, and a source electrode 18 and a drain electrode 19 are formed on the active layer 17 at a predetermined interval. .

The active layer 17 can be formed of, for example, amorphous silicon, amorphous oxide, organic semiconductor material, carbon nanotube, or the like. In addition, the material which comprises the active layer 17 is not limited to these.

The amorphous oxide constituting the active layer 17 is preferably an oxide containing at least one of In, Ga, and Zn (for example, In—O-based), and at least two of In, Ga, and Zn. An oxide containing In (eg, In—Zn—O, In—Ga—O, or Ga—Zn—O) is more preferable, and an oxide containing In, Ga, and Zn is particularly preferable. As the In—Ga—Zn—O-based amorphous oxide, an amorphous oxide whose composition in a crystalline state is represented by InGaO ₃ (ZnO) m (m is a natural number of less than 6) is preferable, and InGaZnO is particularly preferable. ₄ is more preferable.

Examples of the organic semiconductor material that can form the active layer 17 include, but are not limited to, phthalocyanine compounds, pentacene, vanadyl phthalocyanine, and the like. Note that the configuration of the phthalocyanine compound is described in detail in JP-A-2009-212389, and thus the description thereof is omitted.

If the active layer 17 of the thin film transistor 10 is formed of an amorphous oxide, an organic semiconductor material, or a carbon nanotube, it will not absorb radiation such as X-rays, or even if it absorbs it, it will remain in a very small amount. Generation of noise in the portion 14 can be effectively suppressed.

Further, when the active layer 17 is formed of carbon nanotubes, the switching speed of the thin film transistor 10 can be increased, and the thin film transistor 10 having a low degree of light absorption in the visible light region can be formed. In addition, when the active layer 17 is formed of carbon nanotubes, the performance of the thin film transistor 10 is remarkably deteriorated only by mixing a very small amount of metallic impurities into the active layer 17, so that extremely high purity carbon nanotubes can be obtained by centrifugation or the like. It is necessary to form by separating and extracting.

Here, any of the amorphous oxides, organic semiconductor materials, carbon nanotubes constituting the active layer 17 of the thin film transistor 10 and organic photoelectric conversion materials constituting the photoelectric conversion film 4 can be formed at a low temperature. . Therefore, the substrate 1 is not limited to a substrate having high heat resistance such as a semiconductor substrate, a quartz substrate, and a glass substrate, and a flexible substrate such as plastic, aramid, or bionanofiber can also be used. Specifically, flexible materials such as polyesters such as polyethylene terephthalate, polybutylene phthalate, and polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, and poly (chlorotrifluoroethylene). A conductive substrate can be used. If such a plastic flexible substrate is used, it is possible to reduce the weight, which is advantageous for carrying around, for example.

In addition, the substrate 1 is provided with an insulating layer for ensuring insulation, a gas barrier layer for preventing permeation of moisture and oxygen, an undercoat layer for improving flatness or adhesion to electrodes, and the like. May be.

On the other hand, since aramid can be applied at a high temperature process of 200 ° C. or higher, the transparent electrode material can be cured at high temperature to reduce the resistance, and can also be used for automatic mounting of driver ICs including a solder reflow process. Aramid has a thermal expansion coefficient close to that of ITO (Indium Tin Oxide) or glass substrate, so there is little warping after manufacturing and it is difficult to crack. In addition, aramid can form a substrate thinner than a glass substrate or the like. The substrate may be formed by laminating an ultrathin glass substrate and aramid.

In addition, the bionanofiber is a composite of a cellulose microfibril bundle (bacterial cellulose) produced by bacteria (Acetobacter Xylinum) and a transparent resin. The cellulose microfibril bundle has a width of 50 nm and a size of 1/10 of the visible light wavelength, and has high strength, high elasticity, and low thermal expansion. By impregnating and curing a transparent resin such as acrylic resin or epoxy resin in bacterial cellulose, a bio-nanofiber having a light transmittance of about 90% at a wavelength of 500 nm can be obtained while containing 60 to 70% of the fiber. Bionanofiber has a low coefficient of thermal expansion (3-7ppm) comparable to silicon crystals, and is as strong as steel (460MPa), highly elastic (30GPa), and flexible. The substrate 1 can be formed thinly.

In the present embodiment, the TFT substrate 30 is formed on the substrate 1 by sequentially forming the signal output unit 14, the sensor unit 13, and the transparent insulating film 7, and the light-absorbing adhesive resin is formed on the TFT substrate 30. The radiation detector 20 is formed by pasting the scintillator 8 using, for example.

As shown in FIG. 5, the TFT substrate 30 includes a pixel 32 including the sensor unit 13, the capacitor 9, and the thin film transistor 10 described above in a certain direction (a gate wiring direction described later in FIG. 5), and the certain constant. A plurality of lines are provided in a two-dimensional manner in a direction crossing the direction (a data wiring direction described later in FIG. 5).

The radiation detector 20 has a plurality of gate wirings 34 extending in the predetermined direction and for turning on / off each thin film transistor 10, and extending in the crossing direction through the thin film transistor 10 in the on state. And a plurality of data wirings 36 for reading out charges.

The radiation detector 20 has a flat plate shape and a quadrilateral shape having four sides on the outer edge in a plan view, more specifically, a rectangular shape.

Next, the configuration of the electronic cassette 40 according to the present embodiment will be described. FIG. 6 is a perspective view showing the configuration of the electronic cassette 40 according to the present exemplary embodiment.

As shown in the figure, an electronic cassette 40 according to the present embodiment includes a casing 41 made of a material that transmits radiation, and has a waterproof and airtight structure. When the electronic cassette 40 is used in an operating room or the like, there is a risk that blood or other germs may adhere. Therefore, one electronic cassette 40 can be used repeatedly by sterilizing and cleaning the electronic cassette 40 as necessary with a waterproof and hermetic structure.

A space A for accommodating various components is formed inside the housing 41, and the radiation X transmitted through the subject from the irradiation surface side of the housing 41 to which the radiation X is irradiated is formed in the space A. The radiation detector 20 for detecting the radiation X and the lead plate 43 for absorbing the back scattered radiation of the radiation X are arranged in this order.

Here, in the electronic cassette 40 according to the present exemplary embodiment, the area corresponding to the arrangement position of the radiation detector 20 on one flat surface of the housing 41 is a quadrilateral imaging area 41A capable of detecting radiation. Has been. The surface having the imaging region 41A of the casing 41 is a top plate 41B in the electronic cassette 40. In the electronic cassette 40 according to the present embodiment, the radiation detector 20 is connected to the TFT substrate 30 on the top plate 41B side. The top plate 41B is affixed to the inner surface of the casing 41 (the surface on the opposite side of the surface on which the radiation of the top plate 41B is incident).

On the other hand, as shown in FIG. 6, a cassette control unit 58 and a power supply unit 70 (both described later) are placed on one end side inside the housing 41 so as not to overlap with the radiation detector 20 (outside the imaging region 41A). The case 42 which accommodates (refer FIG. 8) is arrange | positioned.

The housing 41 is made of, for example, carbon fiber (carbon fiber), aluminum, magnesium, bionanofiber (cellulose microfibril), or a composite material in order to reduce the weight of the entire electronic cassette 40.

As the composite material, for example, a material including a reinforcing fiber resin is used, and the reinforcing fiber resin includes carbon, cellulose, and the like. Specifically, as the composite material, carbon fiber reinforced plastic (CFRP), a structure in which a foamed material is sandwiched with CFRP, or a material in which the surface of the foamed material is coated with CFRP is used. In the present embodiment, a structure in which a foam material is sandwiched with CFRP is used. Thereby, compared with the case where the housing | casing 41 is comprised with a carbon single-piece | unit, the intensity | strength (rigidity) of the housing | casing 41 can be improved.

On the other hand, as shown in FIG. 7, a support body 44 is disposed on the inner surface of the back surface portion 41 </ b> C facing the top plate 41 </ b> B inside the housing 41, and radiation between the support body 44 and the top plate 41 </ b> B. The detector 20 and the lead plate 43 are arranged in this order in the radiation X irradiation direction. The support body 44 is made of, for example, a foam material from the viewpoint of weight reduction and absorption of dimensional deviation, and supports the lead plate 43.

As shown in the figure, an adhesive member 80 is provided on the inner surface of the top plate 41B to adhere the TFT substrate 30 of the radiation detector 20 in a peelable manner. As the adhesive member 80, for example, a double-sided tape is used. In this case, the double-sided tape is formed so that the adhesive force of one adhesive surface is stronger than the adhesive force of the other adhesive surface.

Specifically, the surface with weak adhesive strength (weak adhesive surface) is set to 1.0 N / cm or less with 180 ° peel adhesive strength. Then, the surface having a strong adhesive force (strong adhesion surface) is in contact with the top plate 41B, and the weak adhesion surface is in contact with the TFT substrate 30. Thereby, compared with the case where the radiation detector 20 is fixed to the top plate 41B with fixing members, such as a screw, the thickness of the electronic cassette 40 can be made thin. Even if the top plate 41B is deformed by an impact or load, the radiation detector 20 follows the deformation of the top plate 41B having high rigidity, so that only a large curvature (slow bend) is generated, and a local low curvature is generated. Therefore, the possibility that the radiation detector 20 is damaged is reduced. Furthermore, the radiation detector 20 contributes to the improvement of the rigidity of the top plate 41B.

As described above, in the electronic cassette 40 according to the present exemplary embodiment, the radiation detector 20 is attached to the inside of the top plate 41B of the housing 41, so that the housing 41 is on the top plate 41B side and the back surface portion 41C side. When the radiation detector 20 is attached to the top plate 41B or the radiation detector 20 is peeled off from the top plate 41B, the housing 41 is placed on the top plate 41B side. And the back surface portion 41C side are separated into two.

In the present embodiment, the radiation detector 20 may not be bonded to the top plate 41B in a clean room or the like. This is because when a foreign object such as a metal piece that absorbs radiation is mixed between the radiation detector 20 and the top plate 41B, the foreign object can be removed by peeling the radiation detector 20 from the top plate 41B.

Next, with reference to FIG. 8, the configuration of the main part of the electrical system of the imaging system 104 according to the present embodiment will be described.

As shown in FIG. 8, in the radiation detector 20 built in the electronic cassette 40, a gate line driver 52 is arranged on one side of two adjacent sides, and a signal processing unit 54 is arranged on the other side. Each gate wiring 34 of the TFT substrate 30 (indicated in FIG. 8 as

gate wirings

34a, 34b,... Individually, and this symbol is used as necessary) is connected to the gate line driver 52, and the TFT substrate. The 30 individual data wirings 36 are connected to the signal processing unit 54.

Further, the housing 41 includes an image memory 56, a cassette control unit 58, and a wireless communication unit 60.

Each thin film transistor 10 on the TFT substrate 30 is sequentially turned on in a row unit by a signal supplied from the gate line driver 52 via the gate wiring 34, and the charge accumulated in the capacitor 9 of the pixel portion where the thin film transistor 10 is turned on is The data wiring 36 is transmitted as an analog electric signal and input to the signal processing unit 54. As a result, the charges accumulated in the capacitors 9 of the individual pixel portions are sequentially read out in units of rows, and a two-dimensional radiation image can be acquired.

Further, the gate line driver 52 sequentially outputs a turn-on signal to each gate wiring 34 one line at a time in one image reading operation to read out charges accumulated in the capacitor 9 of each pixel portion line by line. In addition to (a so-called progressive scanning method), an ON signal is sequentially output from the gate line driver 52 to each gate wiring 34 by a plurality of lines (for example, 2 lines or 4 lines) in a single image reading operation, and a plurality of lines are output. It is possible to read out the charge accumulated in the capacitor 9 of each pixel unit (by combining and reading out the charges of the pixels read out simultaneously) in the binning readout method. The reading method can be switched.

The sequential scanning method and the gate wiring 34 are divided into odd and even rows for each row, and an ON signal is output to the odd or even gate wiring 34 for each image reading operation. In addition, the image reading method may be switched between an interlaced scanning method (so-called interlaced scanning method) that reads out charges accumulated in each pixel portion alternately for each line.

Also, a cassette control unit 58 is connected to the signal processing unit 54 and the gate line driver 52, and the gate line driver 71 and the signal processing unit 54 are controlled by the cassette control unit 58. The cassette control unit 58 is configured by a microcomputer including a CPU, ROM, RAM, HDD, flash memory, and the like.

Here, the configuration of the signal processing unit 54 according to the present embodiment will be described. FIG. 9 is a circuit diagram showing a configuration of the signal processing unit 54 according to the present embodiment.

As shown in FIG. 9, the signal processing unit 54 according to the present embodiment corresponds to each of the data lines 36, a variable gain preamplifier (charge amplifier) 82, a binning unit 84, a sample hold circuit 86, Is provided.

The variable gain preamplifier 82 includes an operational amplifier 82A whose positive input side is grounded, a capacitor 82B connected in parallel between the negative input side and the output side of the operational amplifier 82A, and a reset switch 82C. The reset switch 82C is switched by the cassette control unit 58.

The binning unit 84 includes a switch 84A connected between adjacent communication lines and switches 84B and 84C connected in the middle of the communication lines. The

switches

84A, 84B and 84C are also cassette controlled. Switching is performed by the unit 58. In the present embodiment, the switch 84A and the switch 84B are turned on, and the switch 84C is turned off to be in the binning connection state. The switch 84B and the switch 84C are turned on, and the switch 84A is turned off. By doing so, a normal connection state is established.

Further, the signal processing unit 54 according to the present embodiment includes a multiplexer 88 and an A / D (analog / digital) converter 89. Note that the sample control of the sample hold circuit 86 and the selection output by the switch 88A provided in the multiplexer 88 are also switched by the cassette control unit 58.

Each of the data wirings 36 is individually connected to the input terminal of the multiplexer 88 through the variable gain preamplifier 82, the binning unit 84, and the sample hold circuit 86 in this order. The output end of the multiplexer 88 is connected to the input end of an A / D converter 89 whose output end is connected to the image memory 56.

When detecting the radiation image, the cassette control unit 58 first discharges (resets) the charge accumulated in the capacitor 82B by turning on the reset switch 82C of the variable gain preamplifier 82 for a predetermined period.

Next, the cassette control unit 58 turns off the reset switch 82C of the variable gain preamplifier 82, and sets the binning connection state or the normal connection state by setting the on / off states of the switches 84A to 84C of the binning unit 84. .

On the other hand, the electric charge accumulated in each capacitor 9 of the pixel 32 by irradiation with the radiation X is transmitted through the data wiring 36 connected as an electrical signal when the connected thin film transistor 10 is turned on. The electric signal transmitted through the data wiring 36 is amplified by the corresponding variable gain preamplifier 82 at a predetermined amplification factor, and then synthesized by the binning unit 84 as necessary.

On the other hand, the cassette control unit 58 performs the discharge of the capacitor 82B and the setting of the binning unit 84, and then drives the sample hold circuit 86 for a predetermined period, so that it is amplified by the variable gain preamplifier 82 and binned as necessary. The signal level of the (synthesized) electric signal is held in the sample hold circuit 86.

The signal levels held in each sample and hold circuit 86 are sequentially selected by the multiplexer 88 in accordance with control by the cassette control unit 58 and are A / D converted by the A / D converter 89 and photographed. Image data indicating a radiation image is generated.

FIG. 17 is a block diagram illustrating a schematic configuration of the signal processing unit of the radiation detector 20 according to the present embodiment, and FIG. 18 is an equivalent view focusing on one pixel portion of the radiation detector 20 according to the present embodiment. It is a figure which shows a circuit. In FIG. 17, the binning portion 84 is not shown.

As shown in FIG. 17, the electric charge photoelectrically converted by the scintillator 8 is read and output to the signal processing unit 54 when the thin film transistor 10 is turned on.

The signal processing unit 54 includes a charge amplifier 82, a sample hold circuit 86, a multiplexer 88, and an A / D converter 89 as shown in FIG.

The charge read out by the thin film transistor 10 is integrated by the charge amplifier 82, held by the sample hold circuit 86, and output to the A / D converter 89 via the multiplexer 88. The analog signal is converted into a digital signal by the A / D converter 89 so that image processing can be performed.

More specifically, as shown in FIG. 18, the source of the thin film transistor 10 is connected to the data wiring 36, and the data wiring 36 is connected to the charge amplifier 82. The drain of the thin film transistor 10 is connected to the capacitor 9, and the gate of the thin film transistor 10 is connected to the gate wiring 34.

The charge signals transmitted through the individual data wirings 36 are integrated by the charge amplifier 82 and held in the sample and hold circuit 86. The charge amplifier 82 is provided with a reset switch 79. While the reset switch 79 is turned off, the charge is read and the charge signal is held in the sample hold circuit 86.

The charge signal held in the sample and hold circuit 86 is converted into an analog voltage, sequentially (serially) input to the multiplexer 88, and converted into digital image information by the A / D converter 89.

The cassette control unit 58 controls on / off of the thin film transistor 10 and on / off of the reset switch 79 of the charge amplifier 82.

On the other hand, an image memory 56 is connected to the signal processing unit 54, and the image data output from the A / D converter 89 of the signal processing unit 54 is sequentially stored in the image memory 56. The image memory 56 has a storage capacity capable of storing a predetermined number of image data, and image data obtained by imaging is sequentially stored in the image memory 56 each time a radiographic image is captured.

The image memory 56 is connected to the cassette control unit 58. The cassette control unit 58 includes a microcomputer, and includes a CPU (Central Processing Unit) 58A, a memory 58B including a ROM (Read Only Memory) and a RAM (Random Access Memory), a nonvolatile storage unit 58C including a flash memory and the like. And controls the entire operation of the electronic cassette 40.

Furthermore, a wireless communication unit 60 is connected to the cassette control unit 58. The wireless communication unit 60 corresponds to a wireless LAN (Local Area Network) standard represented by IEEE (Institute of Electrical and Electronics Electronics) (802.11a / b / g / n), etc., and communicates with an external device by wireless communication. Control the transmission of various information between them. The cassette control unit 58 can wirelessly communicate with an external device such as the console 110 that performs control related to radiographic image capturing via the wireless communication unit 60, and can transmit and receive various types of information to and from the console 110 and the like. It is possible.

The electronic cassette 40 is provided with a power supply unit 70, which functions as the above-described various circuits and elements (gate line driver 52, signal processing unit 54, image memory 56, wireless communication unit 60, and cassette control unit 58). The microcomputer or the like) is operated by the power supplied from the power supply unit 70. The power supply unit 70 incorporates a battery (a rechargeable secondary battery) so as not to impair the portability of the electronic cassette 40, and supplies power from the charged battery to various circuits and elements. In FIG. 8, wiring for connecting the power supply unit 70 to various circuits and elements is omitted.

On the other hand, as shown in FIG. 8, the console 110 is configured as a server computer, and includes a display 111 that displays an operation menu, a captured radiographic image, and the like, and a plurality of keys. And an operation panel 112 for inputting operation instructions.

The console 110 according to the present embodiment includes a CPU 113 that controls the operation of the entire apparatus, a ROM 114 that stores various programs including a control program in advance, a RAM 115 that temporarily stores various data, and various data. An HDD (Hard Disk Drive) 116 that stores and holds, a display driver 117 that controls display of various types of information on the display 111, and an operation input detection unit 118 that detects an operation state of the operation panel 112 are provided. . In addition, the console 110 transmits and receives various types of information such as an exposure condition, which will be described later, to and from the radiation generation apparatus 120 through wireless communication, and transmits and receives various types of information such as image data to and from the electronic cassette 40. A wireless communication unit 119 is provided.

The CPU 113, ROM 114, RAM 115, HDD 116, display driver 117, operation input detection unit 118, and wireless communication unit 119 are connected to each other via a system bus BUS. Therefore, the CPU 113 can access the ROM 114, RAM 115, and HDD 116, controls the display of various information on the display 111 via the display driver 117, and the radiation generator 120 via the wireless communication unit 119 and Control of transmission and reception of various types of information with the electronic cassette 40 can be performed. Further, the CPU 113 can grasp the operation state of the user with respect to the operation panel 112 via the operation input detection unit 118.

On the other hand, the radiation generator 120 includes a radio communication unit 123 that transmits and receives various types of information such as an exposure condition between the radiation source 121 and the console 110, and a line that controls the radiation source 121 based on the received exposure condition. A source control unit 122.

The radiation source control unit 122 is also configured to include a microcomputer, and stores the received exposure conditions and the like. The exposure conditions received from the console 110 include information such as tube voltage and tube current. The radiation source control unit 122 causes the radiation source 121 to emit radiation X based on the received exposure conditions.

By the way, in the imaging system 104 according to the present embodiment, while the moving image is captured by the electronic cassette 40, the moving image (perspective image) obtained by the imaging is displayed in real time on the display 111 of the console 110, and the photographer When a predetermined operation (hereinafter referred to as “still image shooting instruction operation”) such as an operation on the operation panel 112 or an operation of pressing an exposure button (not shown) is performed by the electronic cassette 40, a still image is displayed. It is equipped with a fluoroscopy function that can shoot images.

In the imaging system 104 according to the present embodiment, when the electronic cassette 40 performs moving image shooting, the binning unit 84 is brought into the binning connection state, and compared with the case of still image shooting, the radiation generator 120 Imaging is performed with a reduced dose of radiation. On the other hand, when taking a still image with the electronic cassette 40, the binning unit 84 is set in a normal connection state, and radiation is exposed under the exposure conditions set by the photographer according to the part to be imaged. Shooting is performed in the state where the

Here, in the photographing system 104 according to the present embodiment, when a still image is photographed by the fluoroscopic photographing function, the shooting system 104 returns to moving image photographing after the photographing, but in the conventional photographing system, the number immediately after the restoration is returned. Disturbances occurred in the display image of the moving image for the frame.

Therefore, in the imaging system 104 according to the present embodiment, a display image having a preset number of frames (hereinafter referred to as “the number of frames to be processed”) immediately after returning to moving image shooting is obtained by immediately preceding still image shooting. A combination display function for displaying in combination with the obtained still image is installed.

Next, the operation of the imaging system 104 according to the present embodiment will be described with reference to FIG. FIG. 10 is a flowchart showing a flow of processing of the radiographic imaging processing program executed by the CPU 113 of the console 110 when an instruction input for executing the fluoroscopic imaging function is performed via the operation panel 112. The program is stored in advance in a predetermined area of the ROM 114. Further, here, in order to avoid complications, the radiation exposure conditions (in this embodiment, the tube voltage and the tube current when the radiation X is exposed) when moving images are taken with the electronic cassette 40 are as follows. The case where it is set in advance will be described.

In step 300 of the figure, the display driver 117 is controlled so that a predetermined initial information input screen is displayed on the display 111, and in step 302, input of predetermined information is waited.

FIG. 11 shows an example of an initial information input screen displayed on the display 111 by the process of step 300 described above. As shown in the figure, in the initial information input screen according to the present embodiment, the name of the subject who will take a radiographic image, the part to be imaged, the posture at the time of radiography, and the radiation X at the time of radiography of the still image Message for prompting input of exposure conditions (in this embodiment, tube voltage, tube current, and exposure period when radiation X is exposed) and the number of frames to be processed as described above, and an input area for these information Is displayed.

When the initial information input screen shown in FIG. 3 is displayed on the display 111, the photographer sets the name of the subject to be imaged, the region to be imaged, the posture at the time of imaging, the exposure conditions, and the number of frames to be processed. , Each can be input to the corresponding input area via the operation panel 112.

When the posture at the time of imaging is the standing position or the lying position, the photographer holds the electronic cassette 40 in the holding section 162 of the corresponding standing table 160 or the holding section 166 of the lying table 164 and also the radiation source. After positioning 121 at the corresponding position, the subject can be positioned at a predetermined imaging position. On the other hand, when a radiographic image is captured in a state where the imaging target part does not hold the electronic cassette 40 such as an arm part or a leg part on the holding part, the photographer covers the imaging target part in a state where the imaging target part can be imaged. The examiner, electronic cassette 40, and radiation source 121 can be positioned. Thereafter, the photographer can specify an end button displayed near the lower end of the initial information input screen via the operation panel 112. When an end button is designated by the photographer, step 302 is affirmative and the process proceeds to step 304.

In step 304, information input on the initial information input screen (hereinafter referred to as “initial information”) is transmitted to the electronic cassette 40 via the wireless communication unit 119, and then preset in step 306. The exposure conditions at the time of moving image shooting are transmitted to the radiation generation apparatus 120 via the wireless communication unit 119 to set the exposure conditions. In response to this, the radiation source control unit 122 of the radiation generator 120 prepares for exposure under the received exposure conditions.

In the next step 308, instruction information for instructing the start of exposure is transmitted to the radiation generation apparatus 120, and instruction information for instructing the start of moving image shooting is transmitted to the electronic cassette 40. In response to this, the radiation source 121 generates and emits radiation X with a tube voltage and a tube current corresponding to the exposure conditions received by the radiation generator 120 from the console 110.

The radiation X emitted from the radiation source 121 reaches the electronic cassette 40 after passing through the subject. As a result, electric charges are accumulated in the capacitor 9 of each pixel 32 of the radiation detector 20 incorporated in the electronic cassette 40.

When the cassette control unit 58 of the electronic cassette 40 receives the instruction information for instructing the start of moving image shooting, the binning unit 84 is set to the binning connection state, and the accumulation of charges in the capacitor 9 of each pixel 32 of the radiation detector 20 is completed. After the elapse of a predetermined period, the gate line driver 52 is controlled to output an ON signal to each gate line 34 sequentially from the gate line driver 52 line by line, and connected to each gate line 34. Each thin film transistor 10 is sequentially turned on line by line.

In the radiation detector 20, when the thin film transistors 10 connected to the gate lines 34 are turned on one line at a time, the charges accumulated in the capacitors 9 one line at a time flow out to the data lines 36 as electric signals. The electric signal flowing out to each data wiring 36 is converted into digital image data by the signal processing unit 54 and stored in the image memory 56.

The cassette control unit 58 performs predetermined image correction processing on the image data stored in the image memory 56 and then transmits the image data to the console 110 via the wireless communication unit 60.

The cassette control unit 58 performs moving image shooting by executing the above operation at a predetermined speed (30 frames / second in the present embodiment) as the moving image shooting speed.

Therefore, in the next step 310, the process waits until image data for one frame is received from the electronic cassette 40, and in the next step 312, the radiographic image indicated by the received image data is displayed on the display 111. The display driver 117 is controlled.

In the next step 314, it is determined whether or not the above-described still image shooting instruction operation has been performed. If the determination is affirmative, the process proceeds to step 316 to execute a still image shooting processing routine program. Hereinafter, the still image shooting processing routine program according to the present embodiment will be described with reference to FIG. FIG. 12 is a flowchart showing the flow of processing of the still image shooting processing routine program. The program is also stored in a predetermined area of the ROM 114 in advance.

In step 400 of FIG. 12, the exposure condition is set by transmitting the exposure condition included in the initial information to the radiation generation apparatus 120 via the wireless communication unit 119. In response to this, the radiation source control unit 122 of the radiation generator 120 prepares for exposure under the received exposure conditions.

In the next step 402, instruction information for instructing the start of exposure under the set exposure conditions is transmitted to the radiation generation apparatus 120, and instruction information for instructing the start of still image shooting is transmitted to the electronic cassette 40.

Correspondingly, the radiation source 121 starts emission of radiation X in the tube voltage, tube current, and exposure period according to the exposure conditions received by the radiation generator 120 from the console 110. The radiation X emitted from the radiation source 121 reaches the electronic cassette 40 after passing through the subject.

On the other hand, when the cassette control unit 58 of the electronic cassette 40 receives the instruction information for instructing the start of still image shooting, after the binning unit 84 is brought into a normal connection state, the cassette control unit 58 is stopped in substantially the same operation as that for moving image shooting described above. Image capturing is performed, and image data obtained thereby is subjected to predetermined image correction processing, and then transmitted to the console 110 via the wireless communication unit 60.

Therefore, in the next step 404, the process waits until the image data is received from the electronic cassette 40, and in the next step 406, image processing for performing various corrections such as shading correction on the received image data is executed. To do.

In the next step 408, the image data subjected to the image processing (hereinafter referred to as “still image data”) is stored in the HDD 116, and in the next step 410, the radiation image indicated by the still image data is confirmed. For example, the display driver 117 is controlled so that the display 111 displays only for a predetermined period.

In the next step 412, the still image data is transmitted to the RIS server 150 via the in-hospital network 102, and then the still image shooting processing routine program is terminated. Note that the still image data transmitted to the RIS server 150 is stored in the database 150A, so that the doctor can perform interpretation, diagnosis, and the like of the radiographic image taken.

When the still image shooting processing routine program ends, the process proceeds to step 318 of the radiographic image shooting processing program (FIG. 10) which is the main program, and in the same way as the processing of step 306 above, the previously set moving image shooting time The exposure condition is set by transmitting the exposure condition to the radiation generator 120 via the wireless communication unit 119. In response to this, the radiation source control unit 122 of the radiation generator 120 prepares for exposure under the received exposure conditions.

In the next step 320, instruction information for instructing the start of exposure is transmitted to the radiation generation apparatus 120, and instruction information for instructing the start of moving image shooting is transmitted to the electronic cassette 40. In response to this, the radiation source 121 generates and emits radiation at a tube voltage and a tube current corresponding to the exposure conditions received by the radiation generator 120 from the console 110. Note that when the CPU 113 transmits instruction information for instructing the electronic cassette 40 to start moving image shooting in the process of step 320, the electronic cassette 40 is switched from a state where still image shooting is performed to a state where moving image shooting is performed. After that, the combination display function described above is executed.

When the electronic cassette 40 receives the instruction information for instructing the start of moving image shooting, the electronic cassette 40 operates in the same manner as the moving image shooting described above, and the image data obtained by the moving image shooting is transmitted to the console 110 via the wireless communication unit 60. Send continuously.

Therefore, in the next step 322, the process waits until image data for one frame is received from the electronic cassette 40, and in the next step 324, the received image data (hereinafter referred to as “moving image data”). The synthesized image data is generated by superimposing the still image data received and stored from the electronic cassette 40 in the immediately preceding still image shooting processing routine program.

Note that in the imaging system 104 according to the present embodiment, the superimposition of the moving image data and the still image data in this step 324 is performed using a ratio in which the ratio of the still image data to the moving image data is predetermined (in this embodiment, , 60%) by calculating a weighted addition average value of pixel data of corresponding pixels.

In the next step 326, the display driver 117 is controlled so that the radiation image indicated by the composite image data obtained by the processing in step 324 is displayed on the display 111.

In the next step 328, it is determined whether or not the number of display frames of the radiographic image obtained by the processing in steps 322 to 326 has reached the number of processing target frames included in the initial information. While returning to step 322, the process returns to step 310 when an affirmative determination is made.

On the other hand, if a negative determination is made in step 314, the process proceeds to step 330, where it is determined whether or not the timing for ending the fluoroscopic imaging function has come. If a negative determination is made, the process proceeds to step 310. On the other hand, when the determination is affirmative, the routine proceeds to step 332. Note that, in the imaging system 104 according to the present embodiment, the photographer determines whether or not the timing for ending the execution of the fluoroscopic imaging function in step 330 is reached via the operation panel 112 of the console 110 by the photographer. Although it is performed by determining whether or not an operation for instructing the stop of the fluoroscopic imaging function has been performed, it goes without saying that the present invention is not limited to this.

In step 332, instruction information for instructing to stop radiation exposure is transmitted to the radiation generation apparatus 120, and then the radiation image capturing processing program is terminated.

Incidentally, in the electronic cassette 40 according to the present embodiment, as shown in FIG. 7, the radiation detector 20 is incorporated so that the radiation X is irradiated from the TFT substrate 30 side.

Here, as shown in FIG. 13, the radiation detector 20 is irradiated with radiation from the side where the scintillator 8 is formed, and reads a radiation image by the TFT substrate 30 provided on the back side of the incident surface of the radiation. In the case of the so-called back surface reading method, the scintillator 8 emits light more strongly on the upper surface side of the scintillator 8 (the side opposite to the TFT substrate 30). In the case of a so-called surface reading method in which radiation is irradiated from the TFT substrate 30 side and a radiation image is read by the TFT substrate 30 provided on the surface side of the radiation incident surface, the radiation transmitted through the TFT substrate 30 is scintillator. 8, the TFT substrate 30 side of the scintillator 8 emits light more intensely. Electric charges are generated in each sensor unit 13 provided on the TFT substrate 30 by light generated by the scintillator 8. For this reason, since the radiation detector 20 is closer to the light emission position of the scintillator 8 with respect to the TFT substrate 30 when the front surface reading method is used than when the rear surface reading method is used, the resolution of the radiation image obtained by imaging is higher. high.

In the radiation detector 20, the photoelectric conversion film 4 is made of an organic photoelectric conversion material, and the photoelectric conversion film 4 hardly absorbs radiation. For this reason, the radiation detector 20 according to the present embodiment suppresses a decrease in sensitivity to radiation because the amount of radiation absorbed by the photoelectric conversion film 4 is small even when radiation is transmitted through the TFT substrate 30 by the surface reading method. Can do. In the surface reading method, radiation passes through the TFT substrate 30 and reaches the scintillator 8. Thus, when the photoelectric conversion film 4 of the TFT substrate 30 is made of an organic photoelectric conversion material, the radiation in the photoelectric conversion film 4 is obtained. Therefore, it is suitable for the surface reading method.

Further, both the amorphous oxide constituting the active layer 17 of the thin film transistor 10 and the organic photoelectric conversion material constituting the photoelectric conversion film 4 can be formed at a low temperature. For this reason, the board | substrate 1 can be formed with a plastic resin, aramid, and bio-nanofiber with little radiation absorption. Since the substrate 1 formed in this way has a small amount of radiation absorption, even when the radiation passes through the TFT substrate 30 by the surface reading method, it is possible to suppress a decrease in sensitivity to radiation.

Further, according to the present embodiment, as shown in FIG. 7, the radiation detector 20 is attached to the top plate 41B in the housing 41 so that the TFT substrate 30 is on the top plate 41B side. When 1 is formed of a highly rigid plastic resin, aramid, or bio-nanofiber, the radiation detector 20 itself has high rigidity, so that the top plate 41B of the housing 41 can be formed thin. In addition, when the substrate 1 is formed of a highly rigid plastic resin, aramid, or bionanofiber, the radiation detector 20 itself has flexibility, so that even when an impact is applied to the imaging region 41A, the radiation detector 20 is damaged. It ’s hard.

As described above in detail, in the present embodiment, continuous imaging is performed by the radiographic image capturing apparatus (in this exemplary embodiment, the electronic cassette 40), and a plurality of adjacent pixels by the radiographic image capturing apparatus are captured. When the condition that the number of pixels (binning number) read out by combining the charges by the included switching elements is satisfied, a frame image of a predetermined number of frames (the number of frames to be processed in this embodiment) Up to the point immediately after the number of binning is increased, the display is controlled in combination with a still image obtained by photographing immediately before the condition is satisfied, that is, a still image in which the display image is not disturbed. It is possible to suppress the occurrence of disturbance in the display image.

In particular, in the present embodiment, when the condition is satisfied, up to a predetermined number of frame images are displayed in a state in which still images obtained by photographing immediately before the condition is satisfied are superimposed. Therefore, it is possible to smoothly shift to the display of the actually captured image.

Furthermore, in the present embodiment, when the condition is satisfied, up to a predetermined number of frame images, a still image obtained by shooting immediately before the condition is satisfied is synthesized at a predetermined ratio. Therefore, it is possible to realize a suitable display state by setting the ratio according to the photographer's preference and application, the type of the imaging target part to be displayed, etc. it can.

Further, in the present embodiment, the determination as to whether or not the condition is satisfied is made as to whether or not the radiographic imaging device has switched from a still image shooting state to a moving image shooting state. Therefore, it can be more easily determined whether or not the number of binning has been increased.

Furthermore, in the present embodiment, since the input of the predetermined number of frames is accepted, the predetermined number of frames can be easily set.

In the present embodiment, whether or not the condition is satisfied is determined by determining whether or not the electronic cassette 40 is switched from a state where still image shooting is performed to a state where movie shooting is performed. Although the present invention has been described, the present invention is not limited to this, and may be performed by determining whether or not the frame rate of shooting by the electronic cassette 40 is increased. The electronic cassette 40 may be a still image. It is assumed that image information is read by progressive scan when shooting is performed, and image information is read by interlace scan when shooting moving images, and whether or not the above condition is satisfied is determined by the electronic cassette 40 in a progressive manner.・ Switched from scanning state to interlaced scanning state May form performed by determining whether or not. These also make it possible to easily determine whether or not the number of binning has been increased.

In this embodiment, the ratio of still image data and moving image data is different for all display images for the number of processing target frames (in this embodiment, the ratio of still image data to moving image data is 60%). However, the present invention is not limited to this, and the ratio may be the same (the ratio of still image data to moving image data is 50%). Also by this, substantially the same effect as the present embodiment can be obtained.

[Second Embodiment]
Next, a second embodiment for carrying out the present invention will be described in detail. Note that the configurations of the RIS 100, the radiation imaging room, the electronic cassette 40, and the imaging system 104 according to the second embodiment are the same as those in the first embodiment, and a description thereof is omitted here.

Hereinafter, with reference to FIG. 14, the operation of the imaging system 104 according to the present embodiment will be described. Note that FIG. 14 illustrates the radiographic imaging process according to the second embodiment, which is executed by the CPU 113 of the console 110 when an instruction input for executing the fluoroscopic imaging function is performed via the operation panel 112. It is a flowchart which shows the flow of a process of a program, and the said program is beforehand memorize | stored in the predetermined area | region of ROM114. Further, steps in FIG. 14 that perform the same processing as in FIG. 10 are denoted by the same step numbers as in FIG. 10, and description thereof is omitted as much as possible.

In step 324 ′ of FIG. 14, the image data (moving image data) received from the electronic cassette 40 is superimposed on the still image data received from the electronic cassette 40 and stored in the immediately preceding still image shooting processing routine program. Generate composite image data.

Note that in the imaging system 104 according to the present embodiment, the superimposition of the moving image data and the still image data in step 324 ′ is repeated each time the processes in steps 322 to 328 are repeated, and the still image data for the moving image data is repeated. This is performed by calculating a weighted average value of pixel data of corresponding pixels so that the ratio is gradually lowered.

For example, when the number of processing target frames set by the photographer is 5, the ratio is, for example, 90%, 70%, 50%, 30 from the first process of step 324 ′ to the fifth process. %, 10%, and so on.

In the second embodiment, the same effects as in the first embodiment can be obtained, and a frame image of a predetermined number of frames (number of frames to be processed) can be obtained by immediately preceding shooting. Since the obtained still image is controlled to be displayed in a state where the ratio of the still image is gradually lowered and synthesized, the display can be shifted to the display of the actually captured image more smoothly. Can do.

[Third Embodiment]
Next, a third embodiment for carrying out the present invention will be described in detail. Note that the configurations of the RIS 100, the radiation imaging room, the electronic cassette 40, and the imaging system 104 according to the third embodiment are the same as those in the first embodiment, and a description thereof is omitted here.

Hereinafter, the operation of the imaging system 104 according to the present embodiment will be described with reference to FIG. Note that FIG. 15 illustrates the radiographic image capturing process according to the third embodiment, which is executed by the CPU 113 of the console 110 when an instruction is input to execute the fluoroscopic function via the operation panel 112. It is a flowchart which shows the flow of a process of a program, and the said program is beforehand memorize | stored in the predetermined area | region of ROM114. Further, steps in FIG. 15 that perform the same processing as in FIG. 10 are denoted by the same step numbers as in FIG. 10, and description thereof is omitted as much as possible.

15, the display driver 117 is controlled so that the radiographic image received from the electronic cassette 40 and stored by the stored still image data in the immediately preceding still image shooting processing routine program is displayed on the display 111.

Then, in the next step 317B, it is determined whether or not radiographic images for the first number of frames predetermined as a number smaller than the number of frames to be processed are displayed on the display 111. While returning to 317A, the process proceeds to step 318 when an affirmative determination is made. In the present embodiment, half the number of frames to be processed is applied as the first number of frames, but it goes without saying that the number is not limited to this.

Here, in the processing of step 317A to step 317B, the display speed of the still image in step 317A is the display speed of each frame image of the moving image in this radiographic image capturing processing program (in this embodiment, 30 frames / second). ) Is repeatedly executed so as to be the same as. Further, when repeatedly executing the processing of step 317A to step 317B, control is performed so as to gradually fade out the still image displayed on the display 111 in the processing of step 317A.

Thereafter, in step 326 ′, the display driver 117 is controlled so that the radiographic image indicated by the moving image data received from the electronic cassette 40 by the processing in the immediately preceding step 322 is displayed on the display 111.

In step 328 ′, the initial information includes the total number of radiographic image display frames by the processing in steps 322 to 326 ′ and still image display frames by the processing in steps 317A to 317B. It is determined whether or not the number of processing target frames to be reached has been reached, and if a negative determination is made, the process returns to step 322, whereas if an affirmative determination is made, the process returns to step 310.

It should be noted that when the processes in steps 322 to 328 'are repeatedly executed, the image displayed on the display 111 is controlled to gradually fade in in the process in step 326'.

The third embodiment can achieve substantially the same effects as those of the first embodiment, and can also include intermediate images of frame images having a predetermined number of frames (number of frames to be processed). Controls the display so that the still image obtained by the previous shooting is faded out and the remaining images are displayed while the image is faded in. You can move to the display.

[Fourth Embodiment]
Next, a fourth embodiment for carrying out the present invention will be described in detail. Note that the configurations of the RIS 100, the radiation imaging room, the electronic cassette 40, and the imaging system 104 according to the fourth embodiment are the same as those in the first embodiment, and a description thereof is omitted here.

Hereinafter, the operation of the imaging system 104 according to the present embodiment will be described with reference to FIG. Note that FIG. 16 illustrates the radiographic imaging process according to the fourth embodiment, which is executed by the CPU 113 of the console 110 when an instruction to execute the fluoroscopic imaging function is performed via the operation panel 112. It is a flowchart which shows the flow of a process of a program, and the said program is beforehand memorize | stored in the predetermined area | region of ROM114. Also, steps in FIG. 16 that perform the same processing as in FIG. 15 are denoted by the same step numbers as in FIG. 15, and description thereof is omitted as much as possible.

In step 317A 'of FIG. 16, the display driver 117 is controlled so that the radiographic image received from the electronic cassette 40 and stored by the stored still image data in the immediately preceding still image shooting processing routine program is displayed on the display 111.

Then, in the next step 317B, it is determined whether or not radiographic images for the first number of frames predetermined as a number smaller than the number of frames to be processed are displayed on the display 111. While returning to 317A ′, the process proceeds to step 318 when an affirmative determination is made. In this embodiment as well, the number of frames to be processed is half as the first number of frames, but it goes without saying that the number is not limited to this.

Here, in the processing of step 317A ′ to step 317B, the display speed of the still image in step 317A ′ is the display speed of each frame image of the moving image in the radiographic image capturing processing program (in this embodiment, 30 frames). ) Repeatedly. Further, when repeatedly executing the processing of step 317A ′ to step 317B, the image displayed on the display 111 by the processing of step 317A ′ is controlled to be the same image (image indicated by still image data). .

After that, in step 326 ″, the display driver 117 is controlled so that the radiographic image indicated by the moving image data received from the electronic cassette 40 by the processing of the previous step 322 is displayed on the display 111.

In step 328 ′, the total number of the radiographic image display frames by the processing in steps 322 to 326 ″ and the still image display frames in the processing of steps 317A ′ to 317B is the initial information. It is determined whether or not the number of processing target frames included in is reached, and if a negative determination is made, the process returns to step 322, while returning to step 310 when the determination is affirmative.

The fourth embodiment can achieve substantially the same effects as those of the first embodiment, and can also include intermediate images of frame images of a predetermined number of frames (number of frames to be processed). Since the control is performed so that the still image obtained by the previous photographing is displayed and the remaining images are displayed as they are, the occurrence of the disturbance of the display image can be suppressed more reliably.

[Fifth Embodiment]
FIG. 19 is a control block diagram of imaging system 104 according to the present embodiment. Note that the configuration of the imaging system 104 of the fifth embodiment is substantially the same as that of the first embodiment except that the configuration of the imaging system 104 further includes an image processing device 23. Therefore, here, the first embodiment is described. Only the differences will be described.

The console 110 transmits and receives various types of information such as irradiation conditions described later between the image processing apparatus 23 and the radiation generation apparatus 120 by wireless communication, and transmits and receives various types of information such as image data to and from the electronic cassette 40. I / F (for example, wireless communication unit) 96 and I / O 94 are provided.

On the other hand, the image processing device 23 includes an I / F (for example, a wireless communication unit) 101 that transmits and receives various types of information such as irradiation conditions to and from the console 110, and an electronic cassette 40 and a radiation generation device 120 based on the irradiation conditions. And an image processing control unit 103 for controlling. Further, the radiation generation apparatus 120 includes a radiation irradiation control unit (a radiation source control unit) 122 that controls radiation irradiation from the radiation irradiation source 121.

The image processing control unit 103 includes a system control unit 105, a panel control unit 106, and an image processing control unit 108, and exchanges information with each other via a bus 190. The panel control unit 106 receives information from the electronic cassette 40 wirelessly or by wire, and the image processing control unit 108 performs image processing.

On the other hand, the system control unit 105 receives information such as tube voltage and tube current as irradiation conditions from the console 110, and irradiates the radiation X from the radiation irradiation source 121 of the radiation irradiation control unit 122 based on the received irradiation conditions. Take control.

By the way, in the radiation detector 20, when the thin film transistor 10 is turned on / off in order to read out the electric charge accumulated in the capacitor 9, as shown in FIG. 20, the thin film transistor 10 is turned on / off (TFT Gate in FIG. 20). It is known that noise (hereinafter sometimes referred to as “feedthrough noise”) is generated.

However, since the noise when the thin film transistor 10 is on and the noise when it is off are in opposite directions (reverse polarity), integration is performed by the charge amplifier 82 during the reading period in which the reset switch 79 of the charge amplifier 82 is off. By processing, feedthrough noise is canceled.

In addition, at the time of moving image shooting, the resolution decreases, but the reading speed is improved by reading the charge with the binning readout method that reads out a plurality of lines at the same time. As shown by 2-line reading in FIG. 20, the above-described feedthrough noise increases by a plurality of lines (in FIG. 20, since 2-line reading is performed, it is increased approximately twice).

Normally, as described above, the on-time noise and the off-time noise of the thin film transistor 10 are offset, which is not a problem. However, the number of lines to be binned increases immediately after switching from the sequential reading method to the binning reading method. In several frames when the shooting conditions are changed, such as immediately after switching, image degradation that is thought to be caused by noise occurs.

Specifically, as shown in FIG. 21, the QL value is not stable until the first to third frames, and is stabilized after the third frame. The QL value is a value corresponding to the density of the film of the radiographic image obtained by irradiating the radiation, and may be the gradation signal itself, or a predetermined process is performed on the gradation signal. It may be a signal. Further, the QL value in FIG. 21 is a value normalized with a predetermined value as a reference.

As a result of analyzing the factor that causes the QL value to become unstable, immediately after switching the readout method and the number of binning, the absolute value of the feedthrough noise does not increase, as shown in the lowermost part of FIG. It was found that the time when the noise was generated was extended and overlapped with the amplifier reset timing, and the noise when the thin film transistor 10 was turned off was not integrated by the charge amplifier 82 and could not be canceled. .

Therefore, in this embodiment, when switching to increase the number of binning, as shown in FIG. 22, the period from when the thin film transistor 10 is turned off to when the reset switch 79 of the charge amplifier 82 is turned on becomes longer. Thus, the reset switch 79 is controlled. That is, when the cassette control unit 58 switches so that the number of binning increases, the on-timing of the reset switch 79 of the charge amplifier 82 is delayed.

This prevents the noise when the thin film transistor 10 is turned off and the amplifier reset timing from overlapping, and prevents the feedthrough noise from being canceled out.

Subsequently, the operation of the present embodiment will be described with reference to the flowcharts of FIGS.

FIG. 23 is a flowchart showing the radiographic imaging preparation control routine.

In step 200, it is determined whether or not a shooting instruction has been issued. If the determination is negative, the routine ends. If the determination is affirmative, the routine proceeds to step 202.

In step 202, an initial information input screen is displayed on the display 111, and the process proceeds to step 204. That is, the display driver 117 is controlled to display a predetermined initial information input screen on the display 111.

In step 204, it is determined whether or not predetermined information has been input. The process waits until the determination is affirmed, and the process proceeds to step 206. On the initial information input screen, for example, the name of the subject who is going to take a radiographic image, the part to be imaged, the posture at the time of imaging, and the irradiation condition of the radiation X at the time of imaging (in this embodiment, the radiation X is irradiated) Message for prompting the input of the tube voltage and tube current) and an input area for such information are displayed.

When the initial information input screen is displayed on the display 111, the photographer displays the name of the subject to be imaged, the region to be imaged, the posture at the time of imaging, and the irradiation conditions in the corresponding input areas on the operation panel 112. Enter through.

The radiographer enters the radiographic room 180 together with the subject. For example, when the radiographer is in the supine position, the radiocassette holder 164 of the corresponding prone position table 164 holds the electronic cassette 40 and the radiation irradiation source 121 corresponds. After positioning at the position, the subject can be positioned (positioned) at a predetermined imaging position. In addition, when radiography is performed in a state where the imaging target site does not hold the electronic cassette 40 such as an arm or a leg on the holding unit, the subject and the electronic cassette 40 are ready to capture the imaging target site. , And the radiation source 121 can be positioned.

Thereafter, the photographer can leave the radiation imaging room 180 and specify, for example, an end button displayed near the lower end of the initial information input screen via the operation panel 112. When an end button is designated by the photographer, step 204 is affirmed and the routine proceeds to step 206. In the flowchart of FIG. 23, step 204 is an infinite loop, but it may be forcibly terminated by operating a cancel button provided on the operation panel 112.

In step 206, information input on the initial information input screen (hereinafter referred to as “initial information”) is transmitted to the electronic cassette 40 via the wireless communication unit 96, and then the process proceeds to the next step 208. The irradiation conditions included in the initial information are set by transmitting the irradiation conditions to the radiation generator 120 via the wireless communication unit 96. In response to this, the radiation irradiation control unit 122 of the radiation generator 120 prepares for irradiation under the received irradiation conditions.

In the next step 210, the start of ABC control is instructed, and then the process proceeds to step 212, where the instruction information instructing the start of radiation irradiation is transmitted to the radiation generator 120 via the wireless communication unit 96. Ends.

Next, the flow of radiation irradiation control will be described according to the flowchart of FIG. FIG. 24 is a flowchart showing a radiation irradiation control routine.

In step 1300, it is determined whether or not there is an irradiation start instruction. If a negative determination is made, this routine ends. If an affirmative determination is made, the routine proceeds to step 1302.

In step 1302, the steady-state radiation dose (initial value) _XN is read, and the process proceeds to step 1304.

In step 1304, irradiation is started with the read steady-state radiation dose, and the process proceeds to step 1306. That is, irradiation from the radiation irradiation source 121 is started by applying a tube voltage and a tube current corresponding to the irradiation upper limit received from the console 110 to the radiation generator 120. The radiation X emitted from the radiation irradiation source 121 reaches the electronic cassette 40 after passing through the subject.

In step 1306, the currently stored radiation dose correction information is read, and the process proceeds to step 1306. This radiation dose correction information is generated by ABC control and is stored as a correction coefficient ΔX.

In the next step 1308, correction processing based on ABC control is executed, and the process proceeds to step 1310. That is, based on the gradation signal (QL value) obtained from the electronic cassette 40, the average value of the QL values of the region of interest image is calculated, and the average value of the QL values is compared with a predetermined threshold value. The radiation dose is feedback controlled so as to converge to the threshold value.

In step 1310, it is determined whether or not an instruction to end shooting is given. If the determination is affirmative, the process proceeds to step 1312. If the determination is negative, the process returns to step 1306 and the above-described processing is repeated.

In step 1312, the irradiation is finished and the radiation image capturing control is finished.

Subsequently, the flow of image processing control will be described with reference to the flowchart of FIG. FIG. 25 is a flowchart showing an image processing control routine.

When the radiographic imaging control is performed as described above, in step 1400, gradation information for one frame is sequentially fetched and the process proceeds to step 1402. That is, gradation signals generated by the TFT substrate 30 of the electronic cassette 40 are sequentially taken into the image processing control unit 103 under the control of the panel control unit 106. Before the gradation signal is taken into the image processing control unit 103, the gradation signal is sequentially taken into the cassette control unit 58 by a gradation signal taking process which will be described later, and the gradation signals taken in by the cassette control unit 58 are sequentially displayed on the panel. The image is sent to the image donation processing control unit 103 under the control of the control unit 106.

In step 1402, a still image is generated, and the process proceeds to step 1404. That is, a still image is generated when a grayscale signal for one frame is captured.

In step 1404, the moving image editing process is performed, and the process proceeds to step 1406. In the moving image editing process, moving image editing is performed by combining still images for each frame generated in step 1402.

In step 1406, image display processing is performed, and the process proceeds to step 1408. In the image display process, the display driver 117 displays the moving image generated by the moving image editing process on the display 111 by sending it to the display driver 117.

In step 1408, the region of interest is set, and the process proceeds to step 1410. The region of interest is set by, for example, pattern matching or detecting a region with a large amount of movement, but the region of interest may be set by a user operation.

In step 1410, the gradation signal of the set region of interest is extracted, and the process proceeds to step 1412.

In step 1412, the average QL value of the gradation signal of the region of interest is calculated and the process proceeds to step 1414, the pre-stored reference QL value is read, and the process proceeds to step 1416.

In step 1416, the calculated average QL value is compared with the read reference QL value to determine whether correction is possible or not, and the process proceeds to step 1418. For example, the determination as to whether or not correction is possible may be a so-called on / off determination in which a predetermined amount of correction is performed if the difference is greater than or equal to a predetermined value and no correction is performed if the difference is less than a predetermined value. Then, based on the difference, it may be a solution of a calculation by a predetermined calculation formula (for example, a calculation formula based on PID control or the like).

In step 1418, radiation dose correction information ΔX is generated based on the comparison / correction determination result in step 1416, and the process proceeds to step 1420.

In step 1420, the generated correction information ΔX is stored, and the image processing control is terminated.

Next, according to the flowchart of FIG. 26, the flow of the gradation signal capturing process performed by the cassette control unit 58 when the above-described gradation signals are sequentially captured will be described. FIG. 26 is a flowchart showing a gradation signal fetch processing routine.

When fetching a gradation signal, it is first determined in step 500 whether or not to switch the binning number. In this determination, it is determined whether or not switching has been performed so that the number of binning increases. If the determination is affirmative, the process proceeds to step 502, and if the determination is negative, the process proceeds to step 510. In this determination, when the number of binning increases when moving from a still image to a moving image, it may be determined whether or not an instruction to switch from the still image to the moving image is given by the operation panel 112, or reading It may be determined whether or not the method has been switched, it may be determined whether or not an instruction to increase the number of binning has been performed by the operation panel 112, and the binning number changes depending on the frame rate. May determine whether the frame rate has changed.

In step 502, the amplifier reset timing of the charge amplifier 82 is delayed from a predetermined value (for example, a timing determined according to the frame rate), and the process proceeds to step 504. As for the delay amount of the amplifier reset timing, for example, a delay amount corresponding to the number of binning is predetermined.

In step 504, gradation signals for one frame are sequentially read, and the process proceeds to step 506. That is, as shown in FIG. 22, the amplifier reset timing of the reset switch 79 for each line is delayed from the specified value and the grayscale signal is sequentially read, so that the noise and the amplifier reset timing when the thin film transistor 10 is turned off are reduced. Overlap can be prevented. This can prevent a phenomenon that feedthrough noise is not canceled out.

In step 506, it is determined whether or not a predetermined frame has elapsed. The determination is made, for example, by determining whether or not a predetermined number of frames determined based on the number of frames (FIG. 21) until the QL value is stabilized for each number of binning, and when the determination is negative, a step is performed. Returning to 504, the above-described processing is repeated, and if the determination is affirmative, the routine proceeds to step 508.

In step 508, the amplifier reset timing of the reset switch 79 is changed to a specified value, and the process proceeds to step 510. That is, as shown in FIG. 21, the QL value is stabilized when a predetermined frame (for example, 3 frames) immediately after the binning number is switched, so that the reset timing of the charge amplifier 82 is changed to a specified value. In this embodiment, when the reset timing of the charge amplifier 82 is changed to the specified value, it is immediately returned to the specified value. However, the reset timing may be gradually changed so as to become the specified value. For example, at the time of switching the number of binning, the amplifier reset timing may be delayed with respect to the frame at that time, and the application set timing may be gradually returned to the specified value every time a frame passes from the subsequent frame.

In step 510, gradation information for one frame is sequentially fetched, and a series of processing is completed. That is, amplifier reset is performed at a timing of a predetermined value predetermined for each frame rate, and frame images are sequentially read.

As described above, in the present embodiment, when switching is made so that the number of binning is increased, the first few frames sequentially capture the gradation signals by delaying the reset timing by the reset switch 79 of the charge amplifier 82. Therefore, it is possible to prevent the noise when the thin film transistor 10 is turned off and the amplifier reset timing from overlapping, and it is possible to prevent the feedthrough noise from being canceled out. Accordingly, it is possible to stabilize the moving image quality (QL value fluctuation) when the shooting condition changes such as when the number of binning is switched.

In the above embodiment, when the increase in the number of binning is changed, the amplifier reset timing is delayed to surely cancel out the feedthrough noise. However, the present invention is not limited to this. The feedthrough noise is considered to be unstable even when the shooting method is changed, such as when changing to the scanning method, when changing the reading method (for example, when changing from the progressive scanning method to the interlaced scanning method), or when changing the frame rate. You may make it delay amplifier reset timing at the time of a change. Also in this case, when the amplifier reset timing is changed to the specified value, it may be immediately set to the specified value, or may be gradually set to the specified value.

As mentioned above, although this invention was demonstrated using embodiment, the technical scope of this invention is not limited to the range as described in the said embodiment. Various modifications or improvements can be added to the above-described embodiment without departing from the gist of the invention, and embodiments to which such modifications or improvements are added are also included in the technical scope of the present invention.

The above embodiments do not limit the invention according to the claims (claims), and all the combinations of features described in the embodiments are essential for the solution means of the invention. Is not limited. The embodiments described above include inventions at various stages, and various inventions can be extracted by appropriately combining a plurality of disclosed constituent elements. Even if some constituent requirements are deleted from all the constituent requirements shown in the embodiment, as long as an effect is obtained, a configuration from which these some constituent requirements are deleted can be extracted as an invention.

For example, in each of the above-described embodiments, the case where the combination display function is realized by processing by the console 110 has been described. However, the present invention is not limited to this, and for example, as an embodiment realized by processing by the electronic cassette 40 Also good. As an example of this case, when the number of binning is increased in the electronic cassette 40, the CPU 58A of the cassette control unit 58 displays an image showing a radiographic image combining a still image and a moving image as in the above embodiments. A mode for executing a process of generating data can be exemplified.

Further, in each of the above embodiments, the case where the number of binning when performing binning is 2 has been described, but the present invention is not limited to this. For example, the number of binning is 3 or more. Also good. In this case, a radiographic image obtained by combining a still image and a moving image in the same manner as in each of the above embodiments when the binning state is shifted from the non-binning state and the binning number is increased in the binning state. Execute the display process.

In each of the above embodiments, the case where an indirect conversion type apparatus is applied as the radiographic image capturing apparatus of the present invention has been described. However, the present invention is not limited to this, and a direct conversion type apparatus is applied. It is good also as a form to do.

In each of the above embodiments, the case where the photographer sets the number of frames to be processed has been described. However, the present invention is not limited to this, and the display image is not visually perturbed as the number of frames to be processed. Alternatively, a statistical number that does not matter even when visually recognized may be obtained in advance by a sensory test, and the number may be fixedly applied.

In each of the above-described embodiments, the case has been described in which a battery is incorporated as the electronic cassette 40 and the battery is charged via the cradle 130 when not in use. However, the present invention is not limited thereto. Instead, for example, two batteries, a replaceable main battery and a spare battery built in the casing, are provided, and during the replacement of the main battery, the electronic cassette 40 is operated by power supply from the spare battery, It is good also as a form which applies the electronic cassette 40 in which replacement | exchange of a battery, what is called a hot swap (hot-swap of a battery) is enabled. As a result, when replacing the battery, it is not necessary to turn off the power source of the electronic cassette. This form is also effective when shooting continuously as in the above embodiments.

Further, in each of the above embodiments, the case where the sensor unit 13 is configured to include an organic photoelectric conversion material that generates charges by receiving light generated by the scintillator 8 has been described. It is good also as a form which applies what was constituted without including an organic photoelectric conversion material as sensor part 13 without being limited to.

Further, in each of the above-described embodiments, the case has been described in which the case 42 that accommodates the cassette control unit 58 and the power supply unit 70 and the radiation detector 20 are arranged so as not to overlap each other inside the casing 41 of the electronic cassette 40. However, the present invention is not limited to this. For example, the radiation detector 20 and the cassette control unit 58 or the power supply unit 70 may be arranged so as to overlap each other.

In each of the above embodiments, the case where wireless communication is performed between the electronic cassette 40 and the console 110 and between the radiation generator 120 and the console 110 has been described, but the present invention is not limited thereto. For example, at least one of these may be configured to perform wired communication.

In each of the above embodiments, the case where X-rays are applied as radiation has been described. However, the present invention is not limited to this, and other radiation such as γ-rays may be applied.

In addition, the configuration of the RIS 100 described in the above embodiments (see FIG. 1), the configuration of the radiation imaging room (see FIG. 2), the configuration of the electronic cassette 40 (see FIGS. 3 to 7 and FIG. 9), The configuration of the imaging system 104 (see FIG. 8) is an example, and unnecessary parts are deleted, new parts are added, connection states, etc. are changed without departing from the gist of the present invention. It goes without saying that you can do it.

The configuration of the initial information described in the above embodiments is also an example, and it is possible to delete unnecessary information or add new information without departing from the gist of the present invention. Needless to say.

Further, the flow of processing of various programs described in the above embodiments (see FIGS. 10, 12, and 14 to 16) is also an example, and unnecessary steps are within the scope not departing from the gist of the present invention. Needless to say, can be deleted, a new step can be added, and the processing order can be changed.

The configuration of the initial information input screen described in the above embodiments (see FIG. 11) is also an example, and unnecessary information can be deleted or new information can be added without departing from the gist of the present invention. Needless to say, it can be added.

Further, the processing shown in each flowchart in the above embodiment may be stored and distributed as a program in various non-transitory computer-readable storage media.

Claims

Provided is a radiation detector in which a plurality of pixels configured to include a sensor unit that generates charges corresponding to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit are arranged in a matrix. A radiographic imaging device;
Display means for displaying an image captured by the radiation image capturing apparatus;
The condition that the number of pixels read out by combining the charges by the switching elements included in the plurality of adjacent pixels by the radiographic imaging device and the radiographic imaging device being continuously captured is satisfied. In this case, control means for controlling the display means to display up to a predetermined number of frame images in combination with a still image obtained by photographing immediately before the condition is satisfied;
A radiation image display system.
When the condition is satisfied, the control means displays the still image obtained by photographing immediately before the condition is satisfied in a state of being superimposed until a predetermined number of frame images. The radiation image display system according to claim 1, wherein the means is controlled.
When the condition is satisfied, the control means synthesizes a still image obtained by photographing immediately before the condition is satisfied at a predetermined ratio up to a predetermined number of frame images. The radiographic image display system according to claim 2, wherein the display means is controlled to display.
When the condition is satisfied, the control means gradually reduces the ratio of the still image obtained by photographing immediately before the condition is satisfied up to a predetermined number of frame images. The radiographic image display system according to claim 3, wherein the display unit is controlled to display in a combined state.
When the condition is satisfied, the control means has a one-to-one ratio of a still image obtained by photographing immediately before the condition is satisfied, up to a predetermined number of frame images, to the still image. The radiographic image display system according to claim 3, wherein the display unit is controlled to display in a combined state.
When the condition is satisfied, the control means displays a still image obtained by photographing immediately before the condition is satisfied while fading out until an intermediate image of the predetermined number of frame images. The radiographic image display system according to claim 1, wherein the display unit is controlled so that the remaining image is displayed while fading in the image.
When the condition is satisfied, the control means displays a still image obtained by photographing immediately before the condition is satisfied, up to an intermediate image of the predetermined number of frame images, and the remaining images The radiation image display system according to claim 1, wherein the display unit is controlled so that an image is displayed as it is.
The control means determines whether or not the condition is satisfied by determining whether or not the radiographic image capturing apparatus is switched from a state where still image capturing is performed to a state where moving image capturing is performed. The radiation image display system according to any one of claims 1 to 7.
8. The control unit according to claim 1, wherein the control unit determines whether or not the condition is satisfied by determining whether or not a frame rate of imaging by the radiographic image capturing apparatus is increased. The radiation image display system according to item.
The control means determines whether or not the condition is satisfied by determining whether or not the radiographic imaging apparatus is switched from a state in which progressive scanning is performed to a state in which interlaced scanning is performed. The radiation image display system according to any one of claims 1 to 7.
The radiation image display system according to any one of claims 1 to 10, further comprising a reception unit configured to receive an input of the predetermined number of frames.
Provided is a radiation detector in which a plurality of pixels configured to include a sensor unit that generates charges corresponding to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit are arranged in a matrix. Display means for displaying an image captured by the radiation image capturing apparatus;
The condition that the number of pixels read out by combining the charges by the switching elements included in the plurality of adjacent pixels by the radiographic imaging device and the radiographic imaging device being continuously captured is satisfied. In this case, control means for controlling the display means to display up to a predetermined number of frame images in combination with a still image obtained by photographing immediately before the condition is satisfied;
A radiographic image display device comprising:
A radiation detector in which a plurality of pixels configured to include a sensor unit that generates charges according to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit are arranged in a matrix;
When the condition that the number of pixels read by combining the charges by the switching elements included in the plurality of adjacent pixels by the radiation detector is increased by continuously capturing images by the radiation detector is satisfied. Generating means for generating image data in a state combined with a still image obtained by photographing immediately before the condition is satisfied, up to a predetermined number of frame images;
A radiographic imaging apparatus comprising:
Computer
Provided is a radiation detector in which a plurality of pixels configured to include a sensor unit that generates charges corresponding to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit are arranged in a matrix. The condition that the number of pixels read out by combining the charges by the switching elements included in the plurality of adjacent pixels by the radiographic imaging device and the radiographic imaging device being continuously captured is satisfied. Determination means for determining whether or not,
When it is determined by the determination means that the condition is satisfied, a frame image having a predetermined number of frames is displayed in combination with a still image obtained by photographing immediately before the condition is satisfied. Control means for controlling the display means;
Program to function as.
Provided is a radiation detector in which a plurality of pixels configured to include a sensor unit that generates charges corresponding to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit are arranged in a matrix. The condition that the number of pixels read out by combining the charges by the switching elements included in the plurality of adjacent pixels by the radiographic imaging device and the radiographic imaging device being continuously captured is satisfied. A determination step of determining whether or not,
When it is determined by the determination step that the condition is satisfied, a frame image having a predetermined number of frames is displayed in combination with a still image obtained by shooting immediately before the condition is satisfied. A control process for controlling the display means;
A radiation image display method comprising:
A persistent computer-readable storage medium storing a program for causing a computer to execute a radiation image display process, wherein the radiation image display process includes:
Provided is a radiation detector in which a plurality of pixels configured to include a sensor unit that generates charges corresponding to the irradiated radiation and a switching element for reading out the charges generated by the sensor unit are arranged in a matrix. Taking images continuously with a radiographic device,
It is determined whether or not a condition that the number of pixels read out by combining charges by the switching elements included in the plurality of adjacent pixels by the radiographic imaging apparatus is satisfied is satisfied,
When it is determined that the condition is satisfied by the determination, a frame image having a predetermined number of frames is displayed so as to be combined with a still image obtained by photographing immediately before the condition is satisfied. Controlling the means,
Including a storage medium.