JP2017108854A - Radiographic apparatus, radiographic system, control method of radiographic system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an imaging system capable of appropriately determining the propriety of a radiation image.SOLUTION: A radiographic system including a radiographic apparatus for acquiring a radiation image based on a radiation ray that has transmitted a subject, and a control apparatus for executing control to cause a display apparatus to display the radiation image transmitted from the radiographic apparatus is capable of capturing an image by a first imaging mode in which an image is captured while the radiographic apparatus and the control apparatus are in a communicatable state, and the display apparatus is caused to display the radiation image each time the radiation image is captured, and by a second imaging mode in which an image is captured while the radiographic apparatus and the control apparatus are in a non-communicatable state, and the radiation image is stored in a storage part inside the radiographic apparatus. The radiographic apparatus includes determination means for determining whether or not the radiation image satisfies a predetermined criterion. The radiographic apparatus performs determination on the acquired radiation image by the determination means when capturing the image by the second imaging mode, and transmits the acquired radiation image to the control apparatus without performing the determination by the determination means when capturing the image by the first imaging mode.SELECTED DRAWING: Figure 1

Description

  The present invention relates to a radiation imaging apparatus, a radiation imaging system, and a control method for the radiation imaging system.

  In recent years, digitization of radiation images such as X-ray images in medical treatment has been advanced. In particular, a radiography system using a radiography apparatus using a flat panel detector (hereinafter referred to as FPD) formed of a semiconductor material is remarkably widespread. In FPD, radiation image data obtained by digitizing the intensity distribution of radiation transmitted through a subject is transmitted to a control device such as a PC or a display device such as a display, so that a radiation image can be confirmed immediately after imaging. For this reason, in addition to diagnostic advantages such as automation of diagnosis by various image processing and improvement of diagnosis accuracy for minute lesions, it is possible to obtain merits such as speeding up judgment of quality of radiographic images.

  Here, the quick determination of the quality of the radiographic image is advantageous in that it can be retaken immediately when re-imaging is necessary, and in addition to burdening the patient side in addition to the photographer such as an engineer or doctor. There is.

  In Patent Document 1, the preview image is displayed on the display device using the reduced image data transmitted prior to the radiation image data, so that the time until the image display is shortened, and the user can quickly determine whether the radiation image is good or bad. A radiation imaging system capable of making a determination is disclosed.

  Patent Document 2 discloses a radiation imaging apparatus having a determination unit that determines whether or not imaging is good from an image signal output from a radiation detector without displaying a radiation image on a display device.

JP 2002-223390 A JP 2000-26501 A

  However, in the radiographic system described in Patent Document 1, when photographing a patient who is unable to move, assistance of a photographer such as an engineer or a doctor may be necessary to maintain the posture. There are cases where the image displayed later cannot be confirmed immediately. On the other hand, as in the system described in Patent Document 2, if the process of determining the quality of the radiographic image is performed for each imaging, the user cannot quickly determine the quality after observing the displayed radiographic image. There was a fear.

  The present invention has been made in view of the above problems, and an object thereof is to provide an imaging system capable of appropriately determining the quality of a radiographic image.

  A radiation imaging system of the present invention includes a radiation imaging apparatus that acquires a radiation image based on radiation that has passed through a subject, and a control device that performs control to display a radiation image transmitted from the radiation imaging apparatus on a display device. A first imaging mode in which the radiation imaging apparatus and the control apparatus perform imaging in a communicable state, and the radiographic image is displayed on the display apparatus for each imaging, and the radiation imaging apparatus and the control apparatus cannot communicate with each other A radiation imaging system capable of performing imaging in a second imaging mode in which the radiation image is stored in an internal storage unit of the radiation imaging apparatus, and the radiation imaging apparatus includes: A determination unit that determines whether or not a radiation image satisfies a predetermined criterion, and the radiation imaging apparatus performs imaging in the second imaging mode; When the determination by the determination unit is performed on the acquired radiographic image and imaging is performed in the first imaging mode, the acquired radiographic image is transmitted to the control device without being determined by the determination unit. It is characterized by that.

  ADVANTAGE OF THE INVENTION According to this invention, the imaging | photography system which can determine appropriately the quality of a radiographic image can be provided.

The figure which shows the radiography system in 1st embodiment. The figure which shows the external appearance of the radiography apparatus in 1st embodiment. The figure which shows the structure of the radiography apparatus in 1st embodiment. The flowchart which shows operation | movement of the radiography system in 1st embodiment. The flowchart which shows operation | movement of the radiography system in 1st embodiment. The figure which shows the display of the display part of the radiography apparatus in 1st embodiment. The figure which shows the radiography system in 2nd embodiment. The figure which shows the structure of the radiography apparatus in 2nd embodiment. The figure which shows the time change of the input signal to the irradiation detection part in 2nd embodiment. The figure which shows the time change of the bias current in 2nd embodiment. The flowchart which shows the determination process of the radiation irradiation start in 2nd embodiment The flowchart which shows operation | movement of the radiography system in 2nd embodiment. The figure which shows the display of the display part of the radiography apparatus in 2nd embodiment. The flowchart which shows operation | movement of the radiography system in 2nd embodiment. The figure which shows the structure of the radiography apparatus in 3rd embodiment. The flowchart which shows operation | movement of the radiography system in 3rd embodiment.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. However, details of dimensions and structures shown in each embodiment are not limited to those shown in the text and the drawings. In this specification, not only X-rays but also α-rays, β-rays, γ-rays, various particle beams, and the like are included in the radiation.

(First embodiment)
FIG. 1 is a diagram showing a radiation imaging system 100 according to the first embodiment. As shown in FIG. 1, the radiation imaging system 100 of the first embodiment is configured to include at least a radiation imaging apparatus 101 and a control apparatus 102.

  The radiation imaging apparatus 101 acquires radiation image data of the subject H based on the radiation 109 emitted from the radiation source 106 and transmitted through the subject H. As the radiation imaging apparatus 101, for example, a radiation imaging apparatus using a flat panel detector in which a plurality of pixels are arranged in a two-dimensional array is suitably used.

  The radiation imaging apparatus 101 includes at least an image information processing unit 110 and a display unit 120. The image information processing unit 110 performs various types of image processing on the radiation image data captured by the radiation imaging apparatus 101, quality determination processing thereof, processing for storing and outputting the radiation image data, and the like. The processed radiation image data is output to the control device 102 or the like. The display unit 120 displays the status of the radiation imaging apparatus. The display unit 120 is preferably an LED, an LCD, or an OLED. The display unit 120 can also be used to display the result of image quality determination performed by the image information processing unit 110.

  The control device 102 is a unit that performs various controls such as control of the operation and imaging mode of the radiation imaging system 100 and processing of radiation image data captured by the radiation imaging device 101, and includes various computers and workstations. Preferably used. The control device 102 may be connected to a display device 103 such as a display for displaying a control menu and radiographic image data after imaging, and an input device 104 such as a mouse and keyboard for performing various inputs.

The radiation source 106 includes, for example, an electron gun and a rotor for generating radiation 109. The radiation source 106 is controlled by the radiation source control unit 105.
Communication between the radiation imaging apparatus 101 and the control apparatus 102 is performed by wired communication or wireless communication. The access point 113 relays wireless communication between the radiation imaging apparatus 101 and the control apparatus 102. In the present embodiment, communication between the radiation imaging apparatus 101 and the control apparatus 102 is performed by a wireless LAN via an access point (indicated as AP in the figure) 113. As for communication between the radiation imaging apparatus 101 and the control apparatus 102, either the radiation imaging apparatus 101 or the control apparatus 102 may incorporate an access point function and perform communication without relaying an external access point. Alternatively, the communication between the radiation imaging apparatus 101 and the control apparatus 102 may be based on another wireless communication unit such as Bluetooth (registered trademark). Communication between the radiation imaging apparatus 101 and the control apparatus 102 can also be performed by wired communication based on standards such as Ethernet (registered trademark) and RS232C.

  The interface unit (I / F) 111 is provided between the control device 102 and the radiation control unit 105. The interface unit 111 includes a circuit that mediates communication performed between the radiation imaging apparatus 101 and the radiation source control unit 105, and relays exchange of synchronization signals and the like. The interface unit (I / F) 111 monitors the states of the radiation imaging apparatus 101 and the radiation source control unit 103 to adjust the irradiation timing of radiation from the radiation source 106 according to the state of the radiation imaging apparatus 101, for example. can do. Further, by being connected to the control device 102, the transmission / reception of various control signals and information is relayed.

  The interface unit 111 is connected to the control device 102 by Ethernet (registered trademark) via the HUB 112. The HUB 112 is a unit for connecting a plurality of network devices. Further, the HUB 112 is connected to the radiation imaging apparatus 101 via a wireless LAN by connecting an access point 113.

  Note that the radiation imaging apparatus 101 itself may detect radiation irradiation from the radiation source 106 and start imaging (asynchronous imaging). In this case, it is possible to perform imaging without exchanging a synchronization signal between the radiation imaging apparatus 101 and the radiation control unit 105. Therefore, the interface unit 111 may not be provided when performing asynchronous shooting.

  Here, the radiation imaging system 100 can perform imaging in a plurality of imaging modes. Here, the plurality of shooting modes include at least a first shooting mode and a second shooting mode.

  The first imaging mode is an imaging mode in which imaging is performed in a state where communication between the radiation imaging apparatus 101 and the control apparatus 102 can be wired or wirelessly communicated. The radiation imaging apparatus 101 performs control for transferring the acquired radiation image to the control apparatus 102 for each imaging. The control device 102 causes the display device 103 to display the transferred radiation image.

  The second imaging mode is an imaging mode in which imaging is performed in a state where communication between the radiation imaging apparatus 101 and the control apparatus 102 does not allow wired or wireless communication (a state where communication is not possible). The radiation imaging apparatus 101 accumulates the acquired radiographic image in the storage unit 8 without being transferred to the control apparatus 102 every imaging, and transfers the acquired radiographic image to the control apparatus 102 collectively.

  Here, the first shooting mode includes at least a synchronous shooting mode and an asynchronous shooting mode. The synchronous imaging mode is an imaging mode in which an electrical synchronization signal or the like for adjusting the imaging timing is exchanged between the radiation imaging apparatus 101 and the radiation generation apparatus 106. Matching the imaging timing means matching the radiation irradiation timing with the period during which the radiation detector 11 accumulates charges. In the asynchronous imaging mode, a synchronization signal is not exchanged between the radiation imaging apparatus 101 and the radiation generation apparatus 106, and the radiation imaging apparatus 101 itself detects the incidence of radiation and starts accumulating charges.

  In the second imaging mode, the radiation imaging apparatus 101 itself detects the incidence of radiation, and the radiation image is stored in the storage unit 8 in the radiation imaging apparatus 101 without transferring the radiation image to the information processing apparatus 102 for each imaging. . Therefore, it can be said that the radiation imaging apparatus 101 can capture a plurality of radiation images while being independent of the control apparatus 102.

  FIG. 2 is a diagram illustrating an appearance of the radiation imaging apparatus 101 according to the present embodiment, and is a schematic diagram illustrating a part related to an interface.

  As shown in FIG. 2, the radiation imaging apparatus 101 includes a display unit 120, an external connection interface 130, and an operation unit 150 on the surface. The opening 155 is an opening for installing a speaker, and the speaker is installed inside the housing. The radiation imaging apparatus 101 includes a radiation detector 11 (not shown in FIG. 2) therein.

  The display unit 120 has a function of displaying the state of the photographing unit, information about the photographed image, and the like. The display unit 120 can suitably use a display such as an LCD or an OLED in addition to the status display using an LED or the like. Although the display unit 120 is provided on the side surface of the radiation imaging apparatus 101 in FIG. 2, the display unit 120 can be provided at a position different from the region irradiated with radiation on the radiation incident surface 140.

The external interface 130 is an interface for connecting the radiation imaging apparatus 101 and an external device. The external interface 130 is used, for example, to connect the control device 102 with a dedicated cable or the like to output radiation image data and to input various control signals. In addition, the external interface 130 can receive power (power) necessary for the operation of the radiation imaging apparatus 101 by connecting to a cable connected to a dedicated power source or the like. The operation unit 150 includes buttons, dials, Includes slide switches, touch sensors, touch pads, etc. The operation unit 150 is an input interface for performing various operations of the radiation imaging apparatus 101, and has a function of receiving instructions from an operator. In the present embodiment, four buttons, a cursor button 152, a confirmation / reset button 153, and a power button 154 are arranged.

  When the power button 154 is pressed, the radiation imaging apparatus 101 is controlled to be turned on / off. The operation of the radiation imaging apparatus 101 is changed according to the state of the imaging unit when the confirmation / reset button 153 is pressed. Since the state of the photographing unit is displayed on the display unit 120, the confirmation / reset button 153 is arranged side by side to facilitate an operation while viewing the display unit 120. It is also possible to use the display unit 120 as a touch panel and realize the functions of the power button 154 and the operation / reset button 153 according to a touch operation on the display unit 120.

  The opening 155 is an opening for outputting a notification sound from a speaker disposed inside the radiation imaging apparatus 101.

FIG. 3 is a diagram illustrating an example of the configuration of the radiation imaging apparatus 101 in the present embodiment.
The control unit 1 controls the entire operation of the radiation imaging apparatus 101, and is provided with a drive control unit 2 and an image information processing unit 110.

  The drive processing unit 2 has a function for selecting (driving) a switch element arranged in the radiation detector 11. The radiation detector 11 has a structure in which pixels 200 having photoelectric conversion elements 201 formed of a semiconductor are arranged in a two-dimensional matrix. Each pixel 200 includes a switch element 202 and a photoelectric conversion element 201, and is covered with a scintillator (not shown). The scintillator is excited based on the irradiated radiation and emits visible light. The photoelectric conversion element 201 can convert the visible light into an electric signal, and the pixel 200 can convert radiation into an electric signal. Note that the configuration of the pixel 200 is not limited to this, and may be a direct conversion type pixel 200 that directly converts radiation into visible light without using a scintillator.

  When driving the radiation detector 11, the drive circuit 205 selects which row or column to drive among a plurality of pixels constituting the radiation detector 11 in accordance with a control signal from the drive control unit 2. .

  The drive circuit 205 selects the pixels 200 in a certain row by the drive signal via the drive wiring 203. Then, the switch elements 202 of the pixels 200 in the selected row are sequentially turned on, and the image signal (charge) accumulated in the photoelectric conversion elements 201 of the pixels 200 in the selected row is connected to each pixel 200. Is output to the existing signal wiring 204.

  The signal wiring 204 is connected to the image information processing unit 110 via the readout circuit 206. The read circuit 206 includes an amplifier IC 6 and an ADC 7. The amplifier IC 6 has a function of sequentially reading and amplifying image signals output to the signal wiring 204. The ADC 7 is a unit for converting an analog image signal read by the amplifier IC 6 into a digital signal. In the ADC 7, digitally converted radiation image data is input to the image information processing unit 110.

  The image information processing unit 110 performs various processes on the input radiation image data. The processing performed here may include, for example, defect correction for correcting image defects, offset correction for correcting image offset data, and noise reduction processing to reduce various noises. Note that the image information processing unit 110 does not have to perform all of the processing for creating a diagnostic image, and a part of the processing can be performed by the control device 102.

  Offset correction is a process for subtracting unnecessary data such as dark current components that occur during the accumulation of radiographic images, and is used for offset correction acquired from radiation image data acquired while irradiating radiation without irradiation. This is done by subtracting image data. Gain correction is a type of processing for correcting image defects caused by individual characteristic differences between pixels arranged in a two-dimensional matrix, and gain obtained by irradiating a uniform dose without a subject. This is for correcting the gain difference for each pixel based on the correction information data.

  Here, the image information processing unit 110 determines whether or not the captured radiographic image satisfies a predetermined criterion. That is, the image information processing unit 110 functions as a determination unit for determining whether or not a radiation image satisfies a predetermined standard. Whether or not a predetermined criterion is satisfied is determined based on whether or not the image is at a level that can be sufficiently used for purposes such as diagnosis. The determination performed by the image information processing unit 110 includes a plurality of determination items. Hereinafter, each determination item that can be performed by the image information processing unit 110 will be described.

  The quality determination of the radiographic image includes a positioning determination for determining whether or not a region to be imaged is included. The image information processing unit 110 determines whether or not the relative position between the region to be captured and the radiation imaging apparatus is appropriate based on the captured radiation image by positioning determination. In addition, the quality of the radiographic image is determined by determining whether the dose of the radiographic image is large or small, detecting the movement of the subject being imaged, detecting the body misalignment, detecting the misalignment of the grid, Includes determination of misidentification of front and back, and determination of shooting at inappropriate timing. The image information processing unit 110 is selected from a plurality of determination items and executed.

  The image information processing unit 110 performs level determination in order to determine whether the dose is excessive or insufficient based on the pixel value of the radiation image. The level determination is a process performed by performing statistical processing on the luminance data of the entire image and comparing the maximum and minimum luminance values with respective threshold values. In the level determination, when the number of pixels exceeding the threshold exceeds a predetermined range, it is determined that there is a possibility of an image defect.

  Body motion detection (or blur detection) is processing performed by detecting a shift amount (edge component) in a certain direction of radiation image data. The image information processing unit 110 confirms whether the structure on the line in the image has a strong component in a specific direction, and determines the presence or absence of body movement. With regard to the presence or absence of body movement, since most radiographing is performed with a very short irradiation time (for example, within a few milliseconds to 1 second), the shift amount generated during that time can be assumed to be one direction. Therefore, the determination becomes possible. At this time, since the edge component in the image affects the result as line segment information in a specific direction, it is necessary to detect an edge in the image and select a region for body motion detection. The detected area is divided into small areas in order to reinforce the assumption that the direction of body movement is one direction, and a determination is made for each of the divided small areas. For body motion detection, in addition to the methods described here, the radiographic image is analyzed for signal components obtained by frequency analysis, and features such as a method for detecting features associated with body motion are used for imaging parts and procedures. Various methods can be applied accordingly. In order to shorten the processing time, the reduced radiation image data may be processed.

  The storage unit 8 stores the radiographic image data processed by the image information processing unit 110 and imaging information in association with each other. The storage unit 8 is a non-volatile memory such as a flash memory. Here, the imaging information includes information regarding the patient who has been imaged, information regarding the photographer, information regarding the region where the image was captured, information regarding the date and time when the image was captured, and information such as a unique ID for identifying the image. Here, the imaging information includes information used for radiation detection determination in the case where imaging is performed in an imaging mode in which the radiation imaging apparatus 101 detects the start of radiation irradiation and starts imaging. The storage unit 8 can store one or a plurality of pieces of imaging information in association with radiation image data. The storage unit 8 may further store defect information used for image correction and gain information for performing gain correction, and may store an operation history of the radiation imaging apparatus.

  The wireless communication unit 9 transmits the radiation image data and the imaging information stored in the storage unit 8 to the control device 102. The wireless communication unit 9 is connected to the antenna 10 and includes a circuit that transmits and receives radio waves via the antenna 10. The wireless communication unit 9 may transmit the radiation image data processed by the image information processing unit 110 to the control device 102. At this time, the wireless communication unit 9 may transmit the radiation image data and store it in the storage unit 8. Transmission to the control apparatus 102 may be performed by wired communication via an external connection interface (indicated as an external connection I / F in the figure) 130.

  The power supply control unit 3 is a unit for controlling the power supply for driving the radiation imaging apparatus 101 and is required for driving the radiation imaging apparatus 101 upon receiving power supply from the secondary battery 4 and the external connection interface 130. Various power sources are generated and supplied to each unit. Further, charging of the secondary battery 4 is controlled.

  4 and 5 are flowcharts showing the operation of the radiation imaging system according to the first embodiment. Below, according to this flowchart, operation | movement of the radiography system in 1st embodiment is demonstrated. 4 and 5, the step with the first character of the number assigned to each step being S indicates an operation performed by the radiation imaging apparatus, and the step having the first character P is an operation performed by the control device. . FIG. 4 shows a flowchart when the second shooting mode is selected, and FIG. 5 shows a flowchart when the first shooting mode is selected.

  First, the operation of the radiation imaging system according to the first embodiment will be described with reference to FIG.

  First, power supply to each part of the radiation imaging apparatus 101 is started as a start-up operation (S101). The radiation imaging apparatus 101 is configured to connect with the radiation source control unit 105 and the control apparatus 102.

  Next, P101 will be described. In P101, shooting preparation information is input to the control apparatus 102. The input is performed via the input device 104. Then, the control apparatus 102 transmits the input imaging preparation information to the radiation imaging apparatus 101. The imaging preparation information includes information on the subject to be imaged, information on the imaging region, and information on the radiation generation conditions. Further, the imaging preparation information includes information related to image quality determination performed by the radiation imaging apparatus 101. The information regarding the image quality determination may include, for example, the type of image quality determination, the shooting mode, the determination criterion, and the like.

  The radiation imaging apparatus 101 performs imaging preparation after receiving imaging preparation information (S102) (S103). Here, the radiation imaging apparatus 101 prepares for imaging based on the imaging mode received from the control device 102 among the plurality of imaging modes. Here, when the first imaging mode is designated, the radiation imaging apparatus 101 is set not to perform image quality determination. On the other hand, when the second imaging mode is designated, the radiation imaging apparatus 101 determines the quality of the radiation image according to the following flow.

  The radiation imaging apparatus 101 controls the radiation detector 11 to perform preparation driving as preparation for imaging. The preparation drive is an operation for making the radiation imaging apparatus 101 ready for imaging, and may include an operation for discharging the electrical signal accumulated in each pixel 200 of the radiation detector 11. The user adjusts the positional relationship between the subject, the radiation imaging apparatus 101, and the radiation source 106 in the imaging preparation process. Further, the user includes an input of imaging conditions to the radiation source control unit 105. Note that the positional relationship may be automatically adjusted based on the input result of the imaging conditions to the radiation source control unit 105.

  The radiation imaging apparatus 101 acquires digital image data based on the irradiated radiation as an operation for imaging (S104). Specifically, the radiation detector 11 converts the radiation irradiated from the radiation source 106 and transmitted through the subject into electric charges. The converted charge is converted into digital data by reading 206 and sent to the image information processing unit 110.

  The image information processing unit 110 performs image processing on the digital data (radiation image data) (S105). The image information processing unit 110 performs offset correction and gain correction as image processing. Data stored in the storage unit 8 is used as various data for gain correction. Note that the image information processing unit 110 can perform image processing on the digital data corresponding to all the pixels at once, or can execute the digital data on each of the divided or reduced radiation image data, and later It is also possible to combine them.

  The image information processing unit 110 performs image quality determination (image quality determination) after image processing (S106). Here, it is determined whether or not the photographed image is at a level that can be sufficiently used for purposes such as diagnosis. In the present embodiment, the image information processing unit 110 performs level determination and body motion detection.

  Next, a difference in processing based on the result of image quality determination will be described. First, the case where the radiation imaging apparatus 101 determines that there is no problem in the captured radiation image data as a result of the image quality determination will be described. In this case, the radiation image data is transferred to the control device 102 (S107). After receiving the radiation image data (P102), the control device 102 performs additional image processing (P103). The control device 102 controls to display the image after image processing on the display device 103. The user can check the displayed image and perform various diagnoses (P104). The control device 102 inputs information for the next shooting from the input device 104 (P105). After the next shooting information is input, the control apparatus 102 proceeds to process P101.

  Next, a case will be described in which the radiation imaging apparatus 101 determines that there is a possibility of some problem in the captured image as a result of the image quality determination. In this case, the radiation imaging apparatus 101 performs notification in a manner that can identify that the result of the image quality determination is not good. The radiation imaging apparatus 101 can display on the display unit 120 that the radiation image may be inappropriate. Note that the radiation imaging apparatus 101 may display the display on the display unit 120 and notify the user in an identifiable manner by sound or vibration.

  FIG. 6 illustrates an example of a display displayed on the display unit 120. As illustrated in FIG. 6, the radiation imaging apparatus 101 causes the display unit 120 to perform a display for allowing the user to select whether or not to perform re-shooting. (S109). When the user selects whether or not to take a picture again, Y or N is selected by the cursor button of the operation unit, and the confirmation / reset button is pressed.

  Here, when it is selected that re-taking is selected (Y is selected), the radiation imaging apparatus 101 transmits, to the control apparatus 102, data with the result of image quality determination and information indicating that re-imaging is performed. (S111). Note that the radiation imaging apparatus 101 may further add information indicating that the radiation image is unsatisfactory and the reason thereof to data for which the image quality determination result is not good.

  When the control device 102 receives the data to which re-imaging information is added (P106), preparation for re-imaging is started immediately, and the imaging preparation information under the same conditions as the previous imaging is sent to the radiation imaging device. Sent. For this reason, when it is determined that the radiographic image is inappropriate as a result of the image quality determination, the control device 102 can quickly prepare for re-imaging and perform a preparation operation for re-taking. Become.

  On the other hand, when it is selected that re-taking is not performed (N is selected), the radiation imaging apparatus 101 transfers the radiation image to which the radiation image and the image quality determination result are attached to the control apparatus 102. In this case, the control device 102 sequentially performs the processing from P102 to P105 in the same manner as when an appropriate image is transferred. When displaying the radiographic image on the display device 103, the control device 102 also displays a display indicating that there is a possibility that the radiological image includes a quality problem. For this reason, the user can visually confirm the radiation image displayed on the display device 103 and the display related to the image pass / fail determination result, and determine whether to perform re-imaging. Thereafter, the control device 102 performs settings for re-shooting. Note that the control device 102 performs display control of the image and automatically re-photographs when an image to which information indicating that the image is inappropriate is transferred as a result of the image quality determination. You may control to implement the setting for this.

  Note that the determination items and determination criteria for image quality determination are set from the control device 102, but may be set by an operation from the operation unit 150 of the radiation imaging apparatus 101. In this flowchart, the image information processing unit 110 performs two pass / fail determinations on the radiation image, but may be one or may select three or more processes. Furthermore, the control device 102 may determine whether or not the image is good after processing inside the radiation imaging apparatus 101. At this time, the determination item for the image quality determination performed by the radiation imaging apparatus 101 and the determination item for the image quality determination performed by the control device may be different or the same. When the control device 102 performs image quality determination, the control device 102 functions as a second determination unit that is a determination unit different from the image information processing unit 110. Alternatively, when the radiation imaging apparatus 101 and the control apparatus 102 perform different determination items, the radiation imaging apparatus 101 performs items that can determine the quality of the image at least, and assists in visually diagnosing the image. It is preferable to cause the control device 102 to perform a normal pass / fail determination.

  The control device 102 designates image quality determination as an imaging protocol by designating an arbitrary combination with respect to an imaged region, imaging conditions, and the like.

  Next, a flowchart of the radiation imaging system when the second imaging mode is designated will be described with reference to FIG. The radiographic apparatus 101 performs predetermined image processing in S105, and immediately transfers the radiographic image to the control apparatus 102 (S107).

Then, the control device 102 receives the radiation image (P102), and determines whether the transferred radiation image is acceptable or not in P108. Further, the control device 102 may immediately display the radiation image on the display device 103 without performing the quality determination of the radiation image. In this case, since the user can quickly confirm the radiation image, the user can easily make a visual judgment.
As described above, in the first embodiment, the case has been described in which the quality of a radiographic image is determined in a radiographic system capable of performing imaging in a selected imaging mode among a plurality of imaging modes. The first imaging mode is a system that performs imaging in a state where the radiation imaging apparatus and the control apparatus can communicate with each other. Since the radiographic apparatus transfers a radiographic image for each radiographing, the diagnostic efficiency is improved because the radiographic image is displayed immediately without performing the determination process inside the radiographic apparatus. On the other hand, the second imaging mode is a system that performs imaging in a state where the radiation imaging apparatus and the control apparatus cannot communicate. In the second imaging mode, the radiation imaging apparatus stores a radiation image in the storage unit, and continuously captures a plurality of images. For this reason, a user cannot confirm a radiographic image visually for every imaging | photography. Therefore, in the second imaging mode, it is possible to efficiently determine the quality of the radiographic image by determining the quality of the radiographic image inside the radiation imaging apparatus.
With the configuration of the present embodiment, it is possible to appropriately determine the quality of the radiation image based on the imaging mode.

(Second embodiment)
FIG. 7 is a diagram illustrating a radiation imaging system 600 according to the second embodiment. The radiation imaging system 600 of this embodiment is a suitable configuration when the radiation imaging apparatus 101 detects the start of radiation irradiation and captures a radiation image (asynchronous imaging mode). The configuration of the radiation imaging system 600 is different from that of the first embodiment in that the interface unit 111 is not connected.

  The radiation imaging system 600 can perform imaging in a plurality of imaging modes as in the first embodiment. Here, since the interface unit 111 does not exist, the radiation imaging system 600 of this embodiment can perform imaging selectively in the asynchronous imaging mode and the second imaging mode in the first imaging mode.

  FIG. 8 is a diagram showing a radiation imaging apparatus 701 in the present embodiment. The radiation imaging apparatus 701 includes an irradiation detection unit 180.

  The irradiation detection unit 180 has a function of detecting the start of radiation irradiation. The irradiation detection unit 180 is connected to the output of the ADC, and is configured to detect the start of radiation irradiation according to the output. The radiation imaging apparatus 701 determines whether detection of the start of radiation irradiation is performed based on a predetermined reference based on the detection result of the irradiation detection unit 180. The predetermined criteria includes a threshold that can be set by a detection method. In the present embodiment, the determination is performed by the irradiation detection unit 180, but may be performed by the control unit 1 or the image information processing unit 110.

  The irradiation detection unit 180 can detect the start of radiation irradiation according to a change in current (bias current) flowing through a bias wiring that supplies a bias voltage to the photoelectric conversion element 201 of each pixel 200. The irradiation detection unit 180 uses information obtained by variously converting information indicating a bias current in order to appropriately detect the start of irradiation. The irradiation detection unit 180 includes a circuit for converting bias current information. For example, the irradiation detection unit 180 converts a bias current into a voltage signal using a current-voltage conversion circuit including an operational amplifier and a resistor, and converts the voltage signal converted by the AD conversion circuit into a digital value. The irradiation detection unit 180 may use a current-voltage conversion circuit using a shunt resistor. In addition, the irradiation detection unit 180 may output the output voltage of the current-voltage conversion circuit as an analog value as it is. Furthermore, the irradiation detection unit 180 may output a physical quantity corresponding to the amount of current flowing through the bias wiring. Alternatively, the irradiation detection unit 180 can detect the start of radiation irradiation by detecting the output of a pixel in which the source and drain of the switch element 202 are short-circuited (hereinafter, short-circuited pixel).

  The irradiation detection unit 180 acquires an input signal generated by radiation irradiation to the radiation detector 11, and detects the start of radiation irradiation based on the acquired input signal. The irradiation detection unit 180 can determine the start of radiation irradiation by determining that the sample value of the input signal has exceeded a predetermined threshold. Note that the irradiation detection unit 180 can detect in a short time from the start of irradiation when the threshold setting value is low, but it becomes weak against shock and electromagnetic noise, and it is accidentally irradiated even though no radiation is irradiated. There is a case where it is determined to be started (false detection). On the other hand, when the threshold setting value is high, the irradiation detection unit 180 may reduce the possibility of erroneous detection, but the detection determination may be delayed and the image quality may deteriorate.

  The irradiation detection unit 180 cannot obtain a correct image when an erroneous detection due to an impact or electromagnetic noise occurs because radiation is not irradiated. Therefore, the radiation imaging apparatus 701 determines whether it is a false detection prior to determining whether the image is good or bad. The determination as to whether or not it is erroneous detection is performed by the irradiation detection unit 180 or is performed by the control unit 1 (image information processing unit 110) that has received the irradiation start detection signal. The following description will be made assuming that the irradiation detection unit 180 executes the process.

  The irradiation detection unit 180 analyzes the waveform of the input signal and determines whether it is a false detection. FIG. 9 is a diagram showing a case where the start of radiation irradiation is detected using an input signal indicating a current of a short-circuited pixel of the radiation detector 11. FIG. 9A shows the case where radiation is applied, and FIG. 9B shows the time change of the input signal when an impact is applied. FIG. 9A also shows a radiation irradiation waveform. The horizontal axis of FIG. 9 indicates time, and the vertical axis indicates the value (voltage value) of the input signal obtained by converting the input current signal into a voltage. Vth is a threshold value for detecting the start of irradiation.

  In FIG. 9A, when radiation irradiation is started at time t1, the irradiation detector 180 detects irradiation start by detecting an input signal larger than the threshold value Vth at time t2. After that, the input signal continues to exceed Vth while radiation irradiation continues, and after irradiation ends at time t3, the input signal falls below Vth at time t4 after showing attenuation.

  In FIG. 9B, when a mechanical impact of a certain level or more is applied to the radiation imaging apparatus at time t1, the capacitance due to the vibration of the radiation detector 11 and various control circuits changes, and the irradiation detection unit 180. The current caused by the signal is input to. The voltage signal based on the current input to the irradiation detection unit 180 at time t2 exceeds Vth. At time t4, the voltage signal falls below the threshold value Vth. It vibrates at a period caused by the resonance frequency of the radiation imaging apparatus 701 and the sign of the input signal is inverted.

  The irradiation detection unit 180 makes a false detection determination based on the time Δt = t4-t2 when the voltage signal exceeds Vth. Compared with radiation irradiation, Δt at the time of impact application is small. Therefore, the irradiation detection unit 180 can determine that a detection error has occurred when Δt is smaller than a predetermined threshold time set for Δt. The predetermined threshold time may be set to a time sufficiently shorter than the irradiation time of the radiation, for example, set to 0.1 msec. Furthermore, the irradiation detection unit 180 may continue to observe the subsequent voltage signal and make a determination based on the presence or absence of the sign inversion.

  Next, the case where the start of radiation irradiation is detected using the amount of current flowing through the bias wiring will be described with reference to FIGS. In this case, the irradiation detection unit 180 sets a plurality of integration ranges, and determines whether there is a false detection based on the number of integration ranges for which the irradiation start determination has been performed. The irradiation detection unit 180 detects the start of irradiation using a value obtained by integrating the input signals in order to cope with various conditions with different irradiation energy and irradiation time.

  First, the change in the bias current will be described with reference to FIG. FIG. 10 is a diagram illustrating a change in the input signal when radiation irradiation is performed twice. Since the areas A and B are the same for the first irradiation and the second irradiation, there is no difference in the pixel values of the acquired radiation image. On the other hand, the first imaging has a shorter irradiation time than the second imaging. The first irradiation corresponds to a higher dragon value in the tube than the second irradiation (assuming the tube voltages are equal). In this case, the maximum value of the change in the bias current is higher in the first irradiation than in the second irradiation. When the threshold is set to the value shown in FIG. 10, it may occur that the irradiation detection unit 180 cannot detect the second irradiation.

  For this reason, the irradiation detection unit 180 can perform irradiation detection corresponding to various irradiation conditions and erroneous detection by setting a plurality of integration intervals for integrating the sampled input signals. In the irradiation detection unit 180, a threshold is set for each integration interval.

  The mechanical shock is easy to be detected when the voltage signal oscillates in a short cycle and has a short integration interval because of its short duration, but is difficult to detect when the integration interval is long. This is because the signal due to the impact suppresses an increase in the integral value because the waveform vibrates positively and negatively. Based on the difference in voltage characteristics between the mechanical shock and the radiation, the irradiation detection unit 180 can determine that it is a false detection when it can only be detected under a short integration period.

  Here, the input signal when mechanical shock noise or electromagnetic noise is applied has a shorter duration than the input signal at the time of general radiation irradiation. Furthermore, the input signal due to such noise often vibrates, and periodically shows positive and negative values. Therefore, when such noise is input, even if the integration interval exceeds the threshold value with a short integrator, the integrator with a long integration interval often does not exceed the threshold value. These characteristics are used to determine false detection. That is, the detection determination is performed only with the integrator having the shortest integration interval, and when the detection is not performed with the integrator having the longer integration interval, it is determined that the detection is erroneous. By doing in this way, it can be determined whether it is a false detection immediately after irradiation detection.

  FIG. 11 shows a flowchart of the radiation irradiation start determination. Each process in FIG. 11 is executed inside the irradiation detection unit 180. It may be executed by the control unit 1.

  In step S <b> 1301, the irradiation detection unit 180 sets initial values to Sum, which is an integral value of a voltage signal, n, which is an index of a sample value, and m, which is an integral section number. The initial values are Sum = 0, n = 0, and m = 1. The setting of the initial value is called integration value reset.

  In S1302, as a cumulative addition process, the irradiation detection unit 180 sets a value obtained by adding the integral value Sum and X [n], which is the n-th previous sample value, as a new integral value Sum. That is, the irradiation detection unit 180 sets Sum = Sum + X [n] and sets an integral value.

  In step S1303, the irradiation detection unit 180 performs section determination after setting n = n + 1. The irradiation detection unit 180 performs cumulative addition again when the index n of the sample value does not exceed the m-th integration interval W [m] designated in advance in the interval determination in S1304 (NO). And irradiation detection part 180 performs detection judgment, when index n of a sample value exceeds W [m] (YES).

  In the detection determination in S1305, when the integrated value Sum exceeds the threshold value T [m] of the m-th section specified in advance (YES), the irradiation detection unit 180 outputs information indicating the start of radiation irradiation and starts The judgment ends.

  If the integrated value Sum does not exceed the threshold value T [m] of the m-th section as S1306 (NO), the irradiation detection unit 180 determines m = m + 1 and determines the end.

  In the end determination in S1307, the irradiation detection unit 180 performs cumulative addition again when the number m of integration sections does not exceed the number M of integration sections (NO). When m exceeds M (YES), radiation information indicating that radiation has not started is output. In general, M is a value of 1 or more, and the range of detectable irradiation conditions increases as M increases. When the integration interval is small, the range corresponding to the imaging condition with high output and short irradiation time is widened. Conversely, when the integration interval is lengthened, the range corresponding to the imaging condition with low output and long irradiation time is widened. Since there are differences in the irradiation conditions that can be handled depending on the setting of the integration interval, it is possible to cope with almost all the necessary irradiation conditions by setting a plurality of integration intervals at appropriate intervals. The threshold value T [m] for each integration interval may be constant regardless of the integration interval number m, or an optimal value may be set for each integration interval. In general, it is desirable to set an optimum threshold value according to the amount of noise included in a current signal that is different for each integration interval. For example, the standard deviation of the noise amount can be measured in advance, and a value that is an integer multiple of the standard deviation can be set as the threshold value.

  As an example, the number M of integration intervals is 4, the first integration interval W [1] = 8, the second integration interval W [2] = 16, the third integration interval W [3] = 32, the fourth The operation of the irradiation detector 180 when the integration interval W [4] = 64 is described in detail.

  First, the irradiation detection unit 180 gives initial values to Sum, which is an integral value, n, which is an index of sample values, and m, which is an integral section number. The initial values are Sum = 0, n = 0, and m = 1. Next, the irradiation detection unit 180 sets a value obtained by adding the integral value Sum and X [0] which is the previous sample value X as a new integral value Sum. That is, the irradiation detection unit 180 sets Sum = Sum + X [0]. After such cumulative addition, the irradiation detection unit 180 determines the section of the sample value after setting the index of the sample value to n = n + 1. Since the index of the sample value after the first cumulative addition is n = 1, it does not exceed the first integration interval W [1] = 8. That is, since the section determination is NO, the irradiation detection unit 180 performs cumulative addition again. When such cumulative addition is repeated eight times, the integrated value Sum stores a value obtained by integrating eight sample values. Further, since the index of the sample value is n = 8, it exceeds the first integration interval W [1] = 8. That is, since the section determination is YES, the irradiation detection unit 180 performs detection determination. In the detection determination, when the integral value Sum does not exceed the threshold value T [1] of the first section specified in advance in the detection determination, the irradiation detection unit 180 performs the end determination after setting the number of the integration section as m = m + 1. Since the number of the integration interval after the first detection determination is m = 1, the number of integration intervals M does not exceed 4. That is, since the end determination is NO, the irradiation detection unit 180 performs cumulative addition again after setting m = m + 1. The irradiation detection unit 180 repeats cumulative addition 64 times without exceeding the threshold value T [m] in any integration interval, and then the integration interval number becomes m = 4, and is determined to be ended in the end determination. The irradiation detection unit 180 outputs radiation information indicating that radiation has not started. If any of the detection determinations exceeds the threshold T [m], the irradiation detection unit 180 outputs a radiation signal indicating the start of radiation irradiation at that time.

  In the above, the irradiation detection part 180 comprised the one integrator, and demonstrated the structure which performs the detection determination in a some integration area. However, the configuration of the integrator is not limited to this, and the irradiation detection unit 180 includes M integrators according to the number M of integration intervals, and each integrator performs detection determination in parallel. Also good. Moreover, although the irradiation detection part 180 demonstrated the structure which detects the irradiation start of a radiation when any one integration area exceeds a threshold value, it determines the irradiation start when a some integration area exceeds a threshold value You may do it.

  Further, the determination method of erroneous detection is not limited to the above-described method, and determination may be made based on an image acquired by the control unit 1 (image information processing unit 110). Since the radiation image data acquired when erroneous detection occurs is data that is not irradiated with radiation, the level of all pixels is very low. For this reason, after the irradiation detection part 180 determines with the waveform of an input signal, the control part 1 may perform determination using radiographic image data. Since the determination of erroneous detection is performed in addition to the detection of the start of irradiation, the radiation imaging apparatus 701 can improve the accuracy of the determination of the start of irradiation of radiation. Here, the radiation imaging apparatus 701 may reverse the order of the determinations, or may perform the determination by only one of them. The radiation imaging system may be configured to be able to select a detection determination method and whether the control unit 1 determines erroneous detection by an operation from the input device 103 or the operation unit 150.

  FIG. 12 is a flowchart illustrating the operation of the radiation imaging system according to the second embodiment. The operation of the radiation imaging system will be described using the flowchart of FIG. As in the first embodiment, when the first letter of the number assigned to each step is S, the operation of the radiation imaging apparatus is indicated, and when the first letter is P, the operation of the control apparatus is indicated. . Note that the same steps as those in the first embodiment will be omitted as appropriate. Note that the flowchart of FIG. 12 shows the operation of the radiation imaging system when the second imaging mode is selected. The difference when the first shooting mode and the second shooting mode in the present embodiment are selected is the same as in the first embodiment, and thus the description thereof is omitted.

  The operations in S201 to S203 correspond to the operations in S101 to S203, respectively.

  The radiation imaging apparatus 701 waits for radiation irradiation start detection after completion of imaging preparation (S212). Specifically, the radiation imaging apparatus 701 starts driving in an imaging mode capable of detecting radiation. The irradiation detection unit 180 compares the input signal with a predetermined threshold value (S212). When the input signal exceeds the threshold value, it is determined that radiation irradiation has started.

  Here, the radiation imaging apparatus 710 starts an operation for imaging in accordance with the determination (S204), but the radiation detection unit 180 continuously analyzes the input signal waveform to determine whether it is a false detection. (S213).

  When the radiation detection unit 180 does not determine that there is a false detection, the radiation imaging apparatus 710 performs processing after imaging in the same manner as in the first embodiment.

  When the radiation detection unit 180 determines that there is a false detection (YES in S213), the control unit 1 acquires the determination result. Even when the erroneous detection is determined, the same processing as that of the first embodiment is performed until the image quality determination (S206). If the image information processing unit 110 determines that there is no problem as a result of the image quality determination, the radiation imaging apparatus 710 adds information indicating that there is a possibility of erroneous detection to the control unit 1. The radiographic image data thus transferred is transferred (S207). In response to the acquisition of the radiation image data, the control device 102 causes the display device 103 to display a display that can identify that there is a possibility of erroneous detection.

  Further, when it is determined that the captured image is not suitable as a diagnostic image as a result of the image quality determination, the radiation imaging apparatus 701 displays the display unit 120 as shown in FIG. 13 and emits a warning sound. . Subsequent processing is the same as in the first embodiment.

  FIG. 14 is a diagram illustrating an operation of the radiation imaging system when detection is performed by setting a plurality of integration ranges. In the following, the points different from FIG. 12 will be mainly described according to the flowchart of FIG. As in FIG. 12, the step with the first letter of the number assigned to each step indicates the operation of the radiation imaging apparatus, and the step with the first letter P indicates the operation of the control apparatus. In FIG. 14, steps denoted by the same numbers as in FIG. 12 indicate the same operations.

  In FIG. 14, when the radiation imaging apparatus 701 determines that there is a false detection (YES in S213), the display unit of the radiation imaging apparatus displays the message of FIG. 13 and a warning sound is emitted from the speaker (S214). Here, the operator can select whether or not to retake the message on the screen (S216). In the selection, Y or N is selected by the input to the operation unit 150 (cursor button 152) (Y is selected in the figure). Subsequently, when the confirmation / reset button 153 is pressed by the user, the radiation imaging apparatus 701 starts a re-imaging operation. In this case, the radiation imaging apparatus 701 and the control apparatus 102 immediately start preparation for re-imaging, and preparation for imaging under the same conditions as the previous imaging is started.

  On the other hand, when it is selected not to perform re-imaging, the radiation imaging apparatus 701 transmits information indicating that a false detection has occurred to the control apparatus 102 (S215). The control device that has received the information displays a message indicating that a false detection has occurred on the display device, and starts shooting preparation (S203) under conditions different from the previous shooting.

  In the second embodiment, the case has been described in which the quality of the radiation image is determined in the radiation imaging system that can perform imaging in either the first imaging mode (asynchronous imaging) or the second imaging mode. The configuration of the present embodiment makes it possible to appropriately determine the quality of the radiation image.

(Third embodiment)
Next, a radiation imaging system according to the third embodiment will be described with reference to FIG. FIG. 15 is a radiation imaging apparatus 1400 according to the present embodiment, and particularly shows the configuration of the operation unit.

  In the radiation imaging apparatus 1400 in this embodiment, the radiation imaging apparatus independently performs continuous imaging without performing communication with the control apparatus 102 (a state where communication is not possible). The radiation imaging apparatus 1400 stores a plurality of captured images in the storage unit 8. The radiation imaging apparatus 1400 is different from the other embodiments in that the imaging mode can be set without performing communication with the control apparatus 102 by operating the mode switching unit 151.

  The radiation imaging apparatus 1400 is provided with a mode switching unit 151 as the operation unit 150. The operator can select whether or not to perform photographing by the photographing apparatus alone by operating the mode switching unit 151. Although the switching means is an independent slide switch, the present invention is not limited to this, and other buttons of the operation unit 150 may have a switching function. The radiation imaging apparatus 1400 may switch modes by a touch operation using the display unit 120 as a touch panel. Or you may comprise so that a mode may be switched by the instruction | indication from the control apparatus 102. FIG.

  As in the first embodiment, the storage unit 8 stores the radiographic image data processed by the image information processing unit 110 and imaging information in association with each other. The storage unit 8 is a non-volatile memory such as a flash memory. When shooting alone, the storage unit 8 may receive or store shooting information prior to the mode switching. Alternatively, it may be input by operating the radiation imaging apparatus main body and stored in the storage unit 8. In a case where a plurality of subjects are continuously photographed, the radiation imaging apparatus 1400 receives list information of imaging targets from the control apparatus 102, and in addition to the radiographic image and information for identifying the radiographic image, imaging Information regarding the object and the radiographic image may be stored in association with each other.

  The radiation imaging apparatus 1400 transfers the radiation image data saved in the storage unit 8 to the control apparatus when connected to the control apparatus 102. All images may be automatically transferred simultaneously with connection, or control may be performed so that the images to be transferred can be displayed on the display device 103 in a selectable manner. When the radiation imaging apparatus 1400 is connected to a removable external storage device, it may be transferred to an external storage device. For example, a USB memory, an SD card, or a hard disk drive is used as the external storage device. In this case, the radiation imaging apparatus 1400 is provided with a connection interface (not shown) in order to correspond to the external storage device.

  The operation of the radiation imaging system according to the third embodiment will be described with reference to FIG. Here, as in the first embodiment, the step with the first letter of the number assigned to each step indicates the operation of the radiation imaging apparatus 1400, and the step with the first letter P indicates the operation of the control apparatus 102. Show.

  Following the system startup (S301), the radiation imaging system switches the imaging mode to the second imaging mode (S317). When the imaging mode is switched, the radiation imaging apparatus 1400 outputs a notification sound from the speaker and displays a counter indicating the number of radiographic images already captured on the display unit 120. In the radiation imaging apparatus 1400, the display value of the counter is reset to zero when the mode is switched (S322). At this time, the radiation imaging apparatus 1400 may display the number of radiation image data stored in the storage unit 8 and not transferred to the control apparatus 102. The radiation imaging apparatus 1400 can make the user recognize that switching to the single mode has been performed based on a counter display or a notification sound. Note that the radiation imaging apparatus 1400 may notify a notification indicating that the mode has been switched by a display other than the counter or by turning on / off the LED.

  The radiation imaging apparatus 1400 starts driving in the irradiation detection mode described in the second embodiment in order to detect radiation irradiation after a certain preparation drive (S312). In this case, similarly to the second embodiment, the irradiation detection unit 180 determines whether to start irradiation with radiation and to detect erroneous detection (S312 and S313).

  When it is determined that the radiation imaging apparatus 1400 is not a false detection (NO in S313), the imaging unit immediately performs imaging (S304). The radiographic image is subjected to predetermined image processing and then stored in the storage unit 8 in association with identification information.

  Next, as in the first embodiment, the quality determination of the radiographic image is performed following the radiographic image (S306). When it is determined that there is no problem in the image as a result of the quality determination of the radiographic image, the radiation imaging apparatus 1400 advances the numerical value of the counter by one and proceeds to imaging preparation.

  When it is determined that there is some problem with the captured image as a result of the quality determination, the radiation imaging apparatus 1400 displays the message in FIG. 6 on the display unit 120 and emits a notification sound from the speaker. The radiation imaging apparatus 1400 further stores information indicating the determination result in association with the radiation image.

  Next, the radiation imaging apparatus 1400 displays a display for allowing the operator to select re-imaging. This process is the same as in the second embodiment.

  If it is selected in S309 that re-imaging is not performed, the radiation imaging apparatus 1400 proceeds to preparation for imaging after incrementing the counter value by one. On the other hand, if the radiographic apparatus 1400 is selected to perform re-taking, the radiographic apparatus 1400 shifts to preparation for imaging without proceeding with the counter. In this way, the radiation imaging apparatus 1400 can easily recognize that the same counter value in the radiographic image data after being transferred to the control apparatus is a radiographic image that has been retaken.

  When all shooting is completed, the mode is switched to the normal mode by operating the changeover switch. Here, the normal mode is a mode in which shooting is performed in a state where the control device is connected. When the control device is connected after the mode is switched, the radiation image data stored in the storage unit of the radiation imaging device is collectively transferred to the control device.

  In the third embodiment, the case has been described in which the quality of the radiation image is determined in the radiation imaging system in which the second imaging mode is selected. The configuration of the present embodiment makes it possible to appropriately determine the quality of the radiation image.

  Each embodiment can also be realized by a computer or a control computer executing a program (computer program). Further, means for supplying a program to a computer, for example, a computer-readable recording medium such as a CD-ROM recording such a program or a transmission medium such as the Internet for transmitting such a program can also be applied as an embodiment. . The above program can also be applied as an embodiment. The above program, recording medium, transmission medium, and program product are included in the scope of the present invention.

  As mentioned above, although it explained in full detail based on embodiment, it is not restricted to these specific embodiment, Various forms of the range which does not deviate from the summary of invention are also included in the category of this invention. Furthermore, the above-described embodiment is merely an embodiment, and an invention that can be easily imagined from the above-described embodiment is also included in the scope of the present invention.

DESCRIPTION OF SYMBOLS 8 Memory | storage part 11 Radiation detector 100 Radiography system 101 Radiography apparatus 102 Control apparatus 110 Image information processing part

Claims (14)

A radiation imaging apparatus that acquires a radiation image based on radiation that has passed through a subject, and a control device that performs control to display a radiation image transmitted from the radiation imaging apparatus on a display device;
A first imaging mode for imaging the radiographic apparatus and the control device in a communicable state and displaying the radiographic image on the display device for each radiographing; and the radiographic apparatus and the control device cannot communicate with each other A radiation imaging system capable of performing imaging in a second imaging mode in which imaging is performed in a state and storing the radiation image in a storage unit inside the radiation imaging apparatus,
The radiation imaging apparatus includes a determination unit that determines whether or not the radiation image satisfies a predetermined criterion.
When the radiation imaging apparatus performs imaging in the second imaging mode, the determination by the determination unit is performed on the acquired radiation image, and when imaging is performed in the first imaging mode, A radiation imaging system, wherein the acquired radiation image is transmitted to the control device without being judged by the judging means.   In the first imaging mode, imaging is performed in a state where the control device and the radiation imaging device are connected by wire or wirelessly, and in the second imaging mode, the control device and the radiation imaging device are operated. The radiation imaging system according to claim 1, wherein imaging is performed in a state where the wired or wireless connection is not established.   The radiation imaging system according to claim 1 or 2, wherein the radiation imaging apparatus includes a display unit for displaying a determination result by the determination unit in an identifiable manner.   The radiation according to claim 3, wherein the display unit displays a display for selecting whether or not to perform re-imaging when the determination unit determines that the predetermined criterion is not satisfied. Shooting system.   5. The radiation imaging system according to claim 4, wherein when the re-imaging is selected, the radiation imaging apparatus transmits information indicating that the re-imaging is performed to the control device.   The radiation control system according to claim 5, wherein the control device prepares for re-imaging when receiving information indicating that the re-imaging is performed. The radiographic apparatus has storage means,
The storage means stores the determination result of the determination means and the radiation image in association with each other when the determination result by the determination means does not satisfy the predetermined criterion. The radiation imaging system according to any one of the above.   The radiation imaging system according to claim 1, wherein the determination unit selects at least one item from among a plurality of determination items.   The plurality of determination items include at least one item of whether or not an appropriate dose of radiation has been applied, whether or not a subject has moved during imaging, and whether or not imaging has been performed at an appropriate timing. The radiation imaging system according to claim 8.   The radiation imaging system according to claim 1, wherein the control device includes a second determination unit that is different from the determination unit. The radiation imaging apparatus has an irradiation detection unit for detecting that irradiation of radiation has started,
The said determination means determines whether the detection of the start of the said radiation irradiation was performed on the basis of the predetermined | prescribed reference | standard based on the detection result of the said irradiation detection part. The radiation imaging system according to item.   The radiation imaging system according to claim 11, wherein the determination unit determines whether to perform imaging based on a detection result of the irradiation detection unit. A radiation detector that detects radiation transmitted through the subject, and a storage unit that stores a radiation image based on the detected radiation,
A first imaging mode for imaging in a state communicable with a control device and transmitting the radiation image to the control device for each radiographing, photographing in a state incapable of communicating with the control device, and storing the data in the storage unit A radiation imaging apparatus capable of imaging in a second imaging mode for storing radiation images,
Determination means for determining whether or not the radiation image satisfies a predetermined criterion;
When imaging is performed in the second imaging mode, determination by the determination unit is performed on the acquired radiation image, and when imaging is performed in the first imaging mode, determination by the determination unit is performed. The radiation imaging apparatus is characterized in that the radiation imaging apparatus transmits the control information to the control apparatus. A radiation imaging apparatus that acquires a radiation image based on radiation that has passed through a subject; and a control device that performs control to display a radiation image transmitted from the radiation imaging apparatus on a display device, the radiation imaging apparatus and the control A first imaging mode for imaging the apparatus in a communicable state and displaying the radiographic image on the display device for each radiographing; imaging the radiographic apparatus and the control apparatus in an incommunicable state; and A control method of a radiation imaging system capable of performing imaging in a second imaging mode in which the radiation image is stored in a storage unit inside the radiation imaging apparatus,
The radiation imaging apparatus has a determination step of determining whether or not the radiation image satisfies a predetermined standard,
When imaging in the second imaging mode, the determination by the determination unit is performed on the acquired radiographic image, and when imaging in the first imaging mode, the acquired radiographic image is A method for controlling a radiation imaging system, comprising: a step of transmitting from the radiation imaging apparatus to the control apparatus without performing determination by a determination process.

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