JP2011212426A - Radiographic imaging management device and radiation image capturing system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiographic imaging management device and a radiation image capturing system that may effectively prevent excessive exposure of radiation with respect to a subject.SOLUTION: A console 26 includes a CPU 114 configured such that an exposure dose per unit time that is irradiated from a radiation source 42 to the subject to capture the movie of the radiation image is calculated for each of divided regions each of which is a predetermined unit area, and exposure dose information that indicates the calculated exposure dose is stored, associated with the divided region specification information to specify the corresponding divided region and subject specification information to specify the subject.

Description

  The present invention relates to a radiation imaging management apparatus and a radiation imaging system, and more particularly to a radiation imaging management apparatus and a radiation imaging system that perform management related to radiation when capturing a moving image of a radiation image.

  A catheter with various devices attached to the tip is inserted into the patient's body, and the state of the patient's body is observed in real time with a radiographic image displayed on the monitor, while the tip of the catheter reaches the lesion, and the catheter IVR (Interventional Radiology), which treats patients by operating them outside the body, is rapidly spreading.

  By the way, when performing IVR, since the surgeon performs treatment while observing the radiation image displayed on the monitor, the radiation dose to the patient increases as the treatment time becomes longer. There is.

  Therefore, as a technique that can be applied to solve this problem, Patent Document 1 discloses a technique for treatment according to an irradiation plan in which radiation irradiation conditions are determined based on a reference dose absorbed in a treatment site and a normal site of a subject. Irradiation means for irradiating a radiation beam; detection means for detecting scattered radiation generated based on the therapeutic radiation beam; acquisition means for acquiring absorbed dose data from the detected scattered radiation data; and the absorbed dose data And a calculation means for calculating a dose distribution including irradiated and unirradiated irradiation based on the irradiation plan, and evaluating the quality of the irradiation plan based on a predetermined evaluation criterion based on the absorbed dose data. There is disclosed a radiation therapy system comprising: an evaluation unit; and a presentation unit that presents the dose distribution and the evaluation result.

  Patent Document 2 and Patent Document 3 store a radiation inspection apparatus, an image of a body part of a subject imaged by the radiation inspection apparatus, and an image information group composed of various information related to the image capturing. An image management server, a dose management device that manages the dose data received by the subject at the time of imaging in the radiation inspection device, and a hospital information database server that manages the personal information of the subject. In the radiation exposure dose management system connected via the above, the exposure dose management device extracts information necessary for calculating the exposure dose from the image information group stored in the image management server, and based on the information The function of calculating the exposure dose is provided, and the dose data calculated by the exposure dose management apparatus is stored in the hospital information database via the network. Are sent to over server, radiation dose management system characterized recording conserved it in personal information database of the subject of the hospital information database server is disclosed.

JP 2009-160308 A JP 2007-97909 A JP 2009-213905 A

  However, in the techniques disclosed in Patent Literature 1 to Patent Literature 3 described above, the exposure dose is managed in units of the human body such as the heart, the large intestine, the chest, and the cervical vertebra. There was a problem that the amount could not be reduced.

  That is, it is necessary to take a radiographic image at least for the region of interest by the operator, but when performing IVR, the region of interest changes according to the state of the catheter entering the body, and so on. The irradiated field changes continuously every moment. Therefore, even if the exposure dose is managed in units of the human body as in the techniques disclosed in the above patent documents, it is difficult to grasp the past exposure dose with respect to the irradiation field that changes every moment with high accuracy. is there.

  The present invention has been made to solve the above-described problems, and provides a radiography management apparatus and a radiographic imaging system that can effectively prevent exposure of excessive radiation to a subject. Objective.

  In order to achieve the above object, the radiation imaging management apparatus according to claim 1, the radiation exposure per unit time by the subject of radiation irradiated from the radiation source to the subject for capturing a moving image of the radiation image. A calculation means for calculating the amount for each divided area set as a predetermined unit area, and a dose area information indicating the exposure dose calculated by the calculation means, a divided area specifying information for specifying the corresponding divided area, and Storage means for storing in association with the subject specifying information for specifying the subject.

  According to the radiation imaging management apparatus according to claim 1, the amount of exposure per unit time by the subject of radiation irradiated to the subject from the radiation source for capturing a radiographic image by the calculating means is calculated by: It is calculated for each divided area having a predetermined unit area.

  Here, in the present invention, the exposure information indicating the exposure dose calculated by the calculation means is stored in the storage means by the classification area specifying information for specifying the corresponding division area and the subject specifying the subject. Stored in association with specific information. The storage means is connected to a semiconductor storage element such as RAM (Random Access Memory) and ROM (Read Only Memory), a portable recording medium such as a flexible disk, a fixed recording medium such as a hard disk, or a network. An external storage device provided in a server computer or the like is included.

  Thus, according to the radiation imaging management apparatus according to claim 1, the exposure amount per unit time by the subject of radiation irradiated from the radiation source to the subject for moving image capturing of the radiation image is determined. Calculated for each segmented area determined as a predetermined unit area, the dose information indicating the calculated dose, the segmented region specifying information for identifying the corresponding segmented region, and the subject identifying the subject Since it is stored in association with specific information, it is possible to effectively prevent excessive radiation exposure to the subject by deriving and using the cumulative exposure dose for each of the divided areas using the stored exposure dose information. can do.

  Note that, as in the invention described in claim 2, the present invention provides time point information indicating a time point at which the subject is irradiated with the radiation, operation dose information indicating an exposure amount per one operation of the radiation, And acquisition means for acquiring at least one of frame rate information indicating a frame rate of the moving image shooting, wherein the storage means is the time information acquired by the acquisition means, the surgical exposure dose information, and the frame At least one of the rate information may be further stored in association with the corresponding subject specifying information. Thereby, the exposure dose indicated by the exposure dose information can be weighted based on at least one of the time point information acquired by the acquisition means, the surgical exposure dose information, and the frame rate information. Excessive radiation exposure to the subject can be effectively prevented.

  Further, according to the present invention, as in the invention described in claim 3, the exposure dose information is provided between the radiation source and the subject, and a part of radiation emitted from the radiation source is obtained. The exposure amount of radiation reaching the subject in a state of being narrowed by a diaphragm having an opening region that is allowed to pass and whose area can be changed may be indicated. As a result, the cumulative exposure dose can be derived with high accuracy even in a radiographic imaging system using the diaphragm, and as a result, it is possible to more effectively prevent exposure of the subject to excessive radiation.

  On the other hand, in order to achieve the above object, a radiographic imaging system according to claim 4 is managed by the radiography management apparatus according to any one of claims 1 to 3 and the radiography management apparatus. A radiographic image capturing apparatus that captures a moving image of a radiographic image indicated by the radiation that is emitted from a radiation source that emits the radiation that is transmitted through the subject.

  A radiation imaging system according to claim 8 is a radiation imaging management apparatus according to any one of claims 1 to 3 and radiation that emits radiation to be managed by the radiation imaging management apparatus. Source.

  Furthermore, a radiographic imaging system according to claim 9 is a radiation imaging management apparatus according to any one of claims 1 to 3 and radiation that emits radiation to be managed by the radiation imaging management apparatus. A radiation image capturing apparatus for capturing a moving image of a radiation image indicated by radiation emitted from a source and transmitted through a subject, and the radiation source.

  Thus, since the invention of claim 4, claim 8, and claim 9 includes the radiography management apparatus of the present invention, exposure of the subject to excessive radiation as in the radiography management apparatus. Shooting can be effectively prevented.

  Further, in the invention described in claim 4, as in the invention described in claim 5, the radiographic image capturing apparatus generates a phosphor layer that generates light when irradiated with radiation, and is generated in the phosphor layer. A radiation detector of an indirect conversion type configured by stacking a substrate on which a photoelectric conversion element that converts the converted light into electric charges is formed may be used to take a moving image.

  Further, in the invention described in claim 5, as in the invention described in claim 6, the phosphor may be CsI.

  Further, in the invention according to claim 5 or 6, as in the invention according to claim 7, the radiation detector is arranged in the radiographic imaging unit so that radiation enters from the substrate side. It is preferable.

  According to the radiation imaging management apparatus and the radiographic imaging system of the present invention, the exposure amount per unit time of the radiation irradiated to the subject from the radiation source for moving image radiography is determined in advance. Calculated for each divided area set as a unit area, exposure amount information indicating the calculated exposure amount, divided region specifying information for specifying the corresponding divided region, and subject specifying information for specifying the subject Since the stored exposure information is used to derive and use the cumulative exposure dose for each of the divided areas, it is possible to effectively prevent excessive radiation exposure to the subject. The effect of being able to be obtained.

It is a perspective view which shows the mode of the operating room where the radiographic imaging system which concerns on embodiment was installed. It is a partially broken perspective view which shows the internal structure of the electronic cassette which concerns on embodiment. It is a perspective view which shows the principal part structure of the radiation irradiation apparatus which concerns on embodiment. It is the schematic which shows the mode at the time of implementing IVR which concerns on embodiment. It is a block diagram which shows the structure of the radiographic imaging system which concerns on embodiment. It is the equivalent circuit diagram which paid its attention to 1 pixel part of the radiation detector which concerns on embodiment. It is a schematic diagram which shows an example of a data structure of the exposure amount threshold value information which concerns on embodiment. It is a schematic diagram which shows an example of a data structure of the exposure dose historical information which concerns on embodiment. It is a schematic diagram which shows an example of the data structure of the weight value management information which concerns on embodiment. It is a schematic diagram with which it uses for description of the coordinate information which concerns on embodiment. It is sectional drawing which showed typically the structure of the radiation detector of the indirect conversion system which concerns on embodiment. It is sectional drawing which showed roughly the structure of the TFT substrate which concerns on embodiment. It is a cross-sectional side view for demonstrating a surface reading system and a back surface reading system. It is a flowchart which shows the flow of a process of the radiographic imaging process program which concerns on 1st Embodiment. It is a figure which shows an example of the radiographic image displayed on the display surface of a display by irradiating the whole irradiation surface of the radiation detector which concerns on embodiment. It is a figure which shows an example of the radiographic image displayed on the display surface of a display by irradiating the partial area | region of the irradiation surface of the radiation detector which concerns on embodiment. It is a graph which shows the relationship between the temperature of CsI and GOS, and a sensitivity. It is a graph which shows the relationship between the cumulative exposure amount of CsI, and a sensitivity. 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 perspective view which shows the principal part structure of the radiation irradiation apparatus which concerns on other embodiment. It is a perspective view which shows the principal part structure of the radiation irradiation apparatus which concerns on other embodiment. It is a perspective view which shows the principal part structure of the radiation irradiation apparatus which concerns on other embodiment. It is a perspective view which shows the principal part structure of the radiation irradiation apparatus which concerns on other embodiment. It is a top view which shows the principal part structure of the aperture | diaphragm | squeeze part which concerns on other embodiment.

  DESCRIPTION OF EMBODIMENTS Hereinafter, embodiments for carrying out the present invention will be described in detail with reference to the drawings.

[First Embodiment]
First, the configuration of a radiographic image capturing system (hereinafter also simply referred to as “imaging system”) 10 according to the present embodiment will be described with reference to FIG.

  As shown in the figure, an imaging system 10 according to the present embodiment captures a radiographic image by an operation of a doctor 12 or a radiographer. The imaging system 10 detects the bed 16 on which the patient 14 lies, the radiation irradiation device 18 that irradiates the patient 14 with radiation X having a radiation dose according to preset imaging conditions, and the radiation X that has passed through the patient 14. Then, radiographic image information (hereinafter, also simply referred to as “image information”) indicating a radiographic image corresponding to the detected radiation dose is generated, and the image information is stored in a predetermined storage area to perform imaging. A portable imaging device (hereinafter also referred to as “electronic cassette”) 20, a support member 22 that is provided on the bed 16 and cantilever-supports the electronic cassette 20 on the side of the bed 16 where the patient 14 lies, and a radiation irradiation device 18. And a console 26 for controlling the electronic cassette 20.

  The bed 16 is made of a material that transmits the radiation X, and includes a substantially rectangular flat plate-shaped mounting table 16A on which the patient 14 lies, and leg portions 16B that are provided at four corners of the mounting table 16A and support the mounting table 16A. ing.

  Here, the radiation irradiation device 18 is arranged on the back side of the mounting table 16A so that the patient 14 on the mounting table 16A is irradiated with the radiation X from the back side of the mounting table 16A (the side opposite to the side on which the patient 14 lies). Yes.

  On the other hand, the electronic cassette 20 according to the present embodiment includes a display 28 on the back surface on which a captured radiation image is displayed, and is irradiated from the radiation irradiation device 18 with the display surface 28A of the display 28 facing upward. The radiation X is arranged on the front side of the mounting table 16A (side on which the patient 14 lies) so that the radiation X passes through the mounting table 16A and the patient 14 and is detected by a radiation detector 36 described later.

  A support member 22 is provided on the surface of the mounting table 16A on the side on which the patient 14 lies. The support member 22 is bent in a substantially L shape, a base end portion is fixed to the mounting table 16A, and an electronic cassette 20 is detachably attached to the distal end portion.

  FIG. 2 shows an internal configuration of the electronic cassette 20 according to the present exemplary embodiment.

  As shown in the figure, the electronic cassette 20 includes a substantially rectangular flat plate-shaped casing 30 made of a material that transmits the radiation X. When the electronic cassette 20 is used in an operating room or the like, there is a risk that blood or other germs may adhere. Therefore, one electronic cassette 20 can be repeatedly used by sterilizing and cleaning the casing 30 as a waterproof and airtight structure as necessary.

  A connection terminal 20 </ b> A for connecting a communication cable is provided on the side surface of the housing 30 of the electronic cassette 20. Further, the inside of the housing 30 faces the opposite direction of the grid 34 for removing scattered radiation of the radiation X and the display surface 28A of the display 28 from the irradiation surface 32 side of the housing 30 to which the radiation X is irradiated. Is provided on the opposite side of the display surface 28A, and includes a substantially rectangular irradiation surface 36A on which the radiation X is irradiated, and detects the radiation dose of the radiation X transmitted through the patient 14 and irradiated from the irradiation surface 36A. A radiation detector 36 that outputs image information indicating a radiation image corresponding to the radiation dose, and a lead plate 38 that is interposed between the display 28 and the radiation detector 36 and absorbs backscattered radiation X. They are arranged in order.

  In addition, a case 40 that houses an electronic circuit including a microcomputer and a rechargeable secondary battery is disposed on one end side inside the housing 30. The radiation detector 36 and the electronic circuit are operated by electric power supplied from a secondary battery housed in the case 40. Here, in order to avoid various circuits housed in the case 40 from being damaged by the radiation X irradiation, a shielding member for shielding radiation such as a lead plate is disposed on the irradiation surface 32 side of the case 40. It is desirable to keep it.

  FIG. 3 is a perspective view showing a main configuration of the radiation irradiation apparatus 18 according to the present embodiment.

  As shown in the figure, the radiation irradiation device 18 is provided between a radiation source 42 that emits radiation X, and between the radiation source 42 and the electronic cassette 20, and four slit plates 44A, 44B, 44C, and 44D. And an aperture portion 44 configured to include

  Each of the slit plates 44A to 44D is made of a material that shields the radiation X such as lead or tungsten, and is a plate member having a rectangular shape in plan view that gradually increases in thickness in the height direction from the front end portion to the rear end portion. In the diaphragm portion 44, the tip portions of the slit plate 44A and the slit plate 44B face each other, and the tip portions of the slit plate 44C and the slit plate 44D face each other, and the slit plates 44A to 44A. Each of the slit plates 44A to 44D is arranged so that an opening region 51 having a rectangular shape in plan view is formed by the tip of 44D.

  Here, the slit plate 44A and the slit plate 44B are configured to be movable in the x direction in the figure, whereas the slit plate 44C and the slit plate 44D are in the y direction in the figure which is perpendicular to the x direction. It is configured to be movable. In the diaphragm portion 44 according to the present embodiment, the movable range of each of the slit plates 44A to 44D is in a state where the tip portions of the slit plates arranged in contact with each other, that is, the opening region 51 is fully closed. The range from the state to the state to the state in which the opening region 51 has a rectangular shape in plan view and has a maximum area (hereinafter, referred to as “fully open state”).

  Further, in the radiation irradiation apparatus 18 according to the present embodiment, the slit plate 44A is moved by the driving force of the motor 146 (see FIG. 5) being transmitted through a transmission means (not shown), and the slit plate 44B is moved by the motor 148 ( 5) is transmitted through a transmission means (not shown) and moved, and the slit plate 44C is moved by transmission of a driving force of the motor 150 (see FIG. 5) through a transmission means (not shown). In addition, the slit plate 44D moves when the driving force of the motor 152 (see FIG. 5) is transmitted via a transmission means (not shown).

  On the other hand, as shown in FIG. 1, the radiation irradiation apparatus 18 according to the present embodiment is made of a material that shields radiation X, such as lead and tungsten, and a storage box 52 in which the radiation source 42 and the throttle unit 44 are stored. It has. As shown in the figure, the storage box 52 is formed with an opening 52 </ b> A for irradiating the radiation X emitted from the radiation source 42 and passing through the diaphragm 44 toward the irradiation surface 32 of the electronic cassette 20. .

  Here, the opening 52A has a direct line of the radiation X that has passed through the opening region 51 when the slit plates 44A to 44D in the diaphragm 44 are fully opened, and the thickness of the slit plates 44A to 44D. Both the radiation X (hereinafter referred to as “transmission line”) transmitted with a corresponding transmitted dose can be emitted.

  In the imaging system 10 according to the present embodiment, the radiation X is irradiated on the entire irradiation surface 32 of the electronic cassette 20 when the slit plates 44A to 44D of the diaphragm unit 44 are fully opened. In addition, the electronic cassette 20 and the radiation irradiation device 18 are positioned in advance.

  On the other hand, FIG. 4 shows a schematic diagram illustrating an example of a state in which IVR is performed on the patient 14.

  As shown in the figure, a catheter 60 is used in this IVR. The catheter 60 according to the present embodiment is provided with a black and white striped pattern along the longitudinal direction on the surface thereof. Here, the striped pattern includes a wide black region, a narrow white region, a narrow black region, and a wide white region as a group, and a plurality of groups are continuously provided in the longitudinal direction. .

  On the other hand, the skin near the insertion port of the catheter 60 in the patient 14 is irradiated with a light beam on the surface of the catheter 60 inserted into the insertion port, so that the reflection photosensor 62 can receive the reflected light of the light beam. Is provided. The reflective photosensor 62 receives the reflected light from the surface of the catheter 60, converts the received light into an electrical signal, and transmits it to the console 26.

  Next, with reference to FIG. 5, the configuration of the main part of the electrical system of the imaging system 10 according to the present embodiment will be described.

  As shown in the figure, the radiation irradiation apparatus 18 according to the present embodiment is provided with a connection terminal 18 </ b> A for communicating with the console 26. In contrast, the console 26 according to the present embodiment has a connection terminal 26 </ b> A for communicating with the radiation irradiation device 18, a connection terminal 26 </ b> B for communicating with the electronic cassette 20, and the reflective photosensor 62. A connection terminal 26C for receiving an electrical signal is provided.

  The radiation irradiation device 18 is connected to the console 26 via a communication cable 70. The reflective photosensor 62 is connected to the console 26 via the communication cable 71. The electronic cassette 20 has a communication cable 72 connected to the connection terminal 20 </ b> A and is connected to the console 26 via the communication cable 72 when capturing a radiographic image. In the present embodiment, in order to increase the speed of data transfer between the electronic cassette 20 and the console 26, an optical communication cable employing an optical fiber is used as the communication cable 72. Data is transferred between the console 20 and the console 26.

  The radiation detector 36 incorporated in the electronic cassette 20 is an indirect conversion method in which radiation is converted into light by a scintillator and then converted into charges by a photoelectric conversion element such as a photodiode, and radiation is converted into charges by a semiconductor layer such as amorphous selenium. Any direct conversion method may be used. The direct conversion type radiation detector 36 is configured by laminating a photoelectric conversion layer that absorbs radiation X and converts it into charges on a TFT (Thin Film Transistor) active matrix substrate 74. 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. The indirect conversion radiation detector 36 uses a phosphor material and a photoelectric conversion element (photodiode) indirectly instead of the radiation-charge conversion material that directly converts the radiation X such as amorphous selenium into electric charges. It may be converted into an electric charge. As phosphor materials, gadolinium sulfate (GOS) and cesium iodide (CsI) are well known. In this case, radiation X-light conversion is performed using a phosphor material, and light-charge conversion is performed using a photodiode of a photoelectric conversion element. The electronic cassette 20 according to the present embodiment includes an indirect conversion radiation detector 36.

  In addition, on the TFT active matrix substrate 74, a pixel unit 80 including a storage capacitor 76 for storing charges generated in the photoelectric conversion layer and a TFT 78 for reading out the charges stored in the storage capacitor 76 (FIG. 5). In this example, a large number of photoelectric conversion layers and photoelectric conversion elements corresponding to the individual pixel portions 80 are schematically shown as photoelectric conversion portions 82). Along with this, charges generated in the photoelectric conversion layer are stored in the storage capacitors 76 of the individual pixel units 80. As a result, the image information carried on the radiation X irradiated to the electronic cassette 20 is converted into charge information and held in the radiation detector 36.

  The TFT active matrix substrate 74 is extended in a certain direction (row direction), a plurality of gate wirings 84 for turning on and off the TFTs 78 of the individual pixel portions 80, and a direction (column) orthogonal to the gate wirings 84. A plurality of data wirings 86 are provided for reading the stored charge from the storage capacitor 76 through the TFT 78 which is turned on. Each gate wiring 84 is connected to a gate line driver 88, and each data wiring 86 is connected to a signal processing unit 90. When charges are accumulated in the storage capacitors 76 of the individual pixel units 80, the TFTs 78 of the individual pixel units 80 are sequentially turned on in units of rows by a signal supplied from the gate line driver 88 via the gate wiring 84. The charge stored in the storage capacitor 76 of the pixel unit 80 for which is turned on is transmitted as a charge signal through the data wiring 86 and input to the signal processing unit 90. Accordingly, the charges accumulated in the storage capacitors 76 of the individual pixel units 80 are sequentially read out in units of rows.

  FIG. 6 shows an equivalent circuit diagram focusing on one pixel portion of the radiation detector 36 according to the present exemplary embodiment.

  As shown in the figure, the source of the TFT 78 is connected to the data wiring 86, and the data wiring 86 is connected to the signal processing unit 90. The drain of the TFT 78 is connected to the storage capacitor 76 and the photoelectric conversion unit 82, and the gate of the TFT 78 is connected to the gate wiring 84.

  The signal processing unit 90 includes a sample hold circuit 92 for each data wiring 86. The charge signal transmitted through each data wiring 86 is held in the sample hold circuit 92. The sample hold circuit 92 includes an operational amplifier 92A and a capacitor 92B, and converts the charge signal into an analog voltage. The sample hold circuit 92 is provided with a switch 92C as a reset circuit that shorts both electrodes of the capacitor 92B and discharges the electric charge accumulated in the capacitor 92B.

  A multiplexer 94 and an A / D (analog / digital) converter 96 are sequentially connected to the output side of the sample and hold circuit 92, and the charge signals held in the individual sample and hold circuits are converted into analog voltages to be converted into the multiplexer 94. Are sequentially input (serially) and converted into digital image information by the A / D converter 96.

  As shown in FIG. 5, a line memory 98 is connected to the signal processing unit 90, and image information output from the A / D converter 96 of the signal processing unit 90 is sequentially stored in the line memory 98. The line memory 98 has a storage capacity capable of storing image information indicating a radiation image for a predetermined number of lines, and the read image information for one line is stored in the line memory each time the charge is read line by line. 98 are sequentially stored.

  The line memory 98 is connected to a cassette control unit 100 that controls the operation of the entire electronic cassette 20. The cassette control unit 100 is realized by a microcomputer, and an optical communication control unit 102 is connected thereto. The optical communication control unit 102 is connected to the connection terminal 20A, and controls transmission of various information to and from an external device connected via the connection terminal 20A. Therefore, the cassette control unit 100 can transmit and receive various types of information to and from an external device via the optical communication control unit 102.

  The electronic cassette 20 includes a display driver 104 that controls display on the display 28, and a cassette control unit 100 is connected to the display driver 104. The cassette control unit 100 reads the image information stored in the line memory 98 and displays the radiation image indicated by the image information on the display surface 28A of the display 28. Note that the radiation image indicated by the image information obtained by the radiation detector 36 is displayed on the display 28 according to the present embodiment in a substantially actual size.

  Further, the electronic cassette 20 includes a power supply unit 106, and the above-described various circuits and elements (a gate line driver 88, a signal processing unit 90, a line memory 98, an optical communication control unit 102, and a micro controller that functions as the cassette control unit 100). The computer is operated by the power supplied from the power supply unit 106. The power supply unit 106 incorporates a battery (a rechargeable secondary battery) so as not to impair the portability of the electronic cassette 20 and supplies power from the charged battery to various circuits and elements.

  On the other hand, the console 26 is configured as a server computer and includes a touch panel display or the like in which a transparent touch panel is superimposed on the display. Various information such as operation menus and captured radiographic images are displayed on the display surface of the display. And a UI (User Interface) panel 110 on which desired information and instructions are input when the user touches the touch panel with a touch pen, and a plurality of keys. Various information and operation instructions are displayed. And an input operation panel 112 (see also FIG. 1).

  The console 26 temporarily stores a CPU (Central Processing Unit) 114 that controls the operation of the entire apparatus, a ROM (Read Only Memory) 116 in which various programs including a control program are stored in advance, and various data. A RAM (Random Access Memory) 118 and an HDD (Hard Disk Drive) 120 that stores and holds various data are provided.

  In addition, the console 26 controls the display of the UI panel 110, detects the operation state of the touch panel, the UI panel control unit 122, detects the operation state of the operation panel 112, and the connection terminal 26A. And a communication interface (I / F) unit 126 that transmits and receives various kinds of information such as exposure conditions and state information of the radiation irradiation device 18 to and from the radiation irradiation device 18 via the connection terminal 26A and the communication cable 70. Connected to the connection terminal 26B, connected to the connection terminal 26C, an optical communication control unit 128 that transmits and receives various information such as image information to and from the electronic cassette 20 via the connection terminal 26B and the communication cable 72, Reception of an electrical signal from the reflective photosensor 62 via the connection terminal 26C and the communication cable 71 It includes an external I / F unit 130 which performs the.

  The CPU 114, the ROM 116, the RAM 118, the HDD 120, the UI panel control unit 122, the operation input detection unit 124, the communication I / F unit 126, the optical communication control unit 128, and the external I / F unit 130 are mutually connected via the system bus BUS. It is connected. Therefore, the CPU 114 can access the ROM 116, the RAM 118, and the HDD 120, controls the display of various information on the display of the UI panel 110 via the UI panel control unit 122, and controls the display via the UI panel control unit 122. Understanding of the user's operation state with respect to the touch panel of the UI panel 110, understanding of the user's operation state with respect to the operation panel 112 via the operation input detection unit 124, and various information with the radiation irradiation apparatus 18 via the communication I / F unit 126. Control of transmission / reception, control of transmission / reception of various information with the electronic cassette 20 via the optical communication control unit 128, and acquisition of the detection result of the reflective photosensor 62 via the external I / F unit 130 can be performed. .

  Note that the touch panel of the UI panel 110 according to the present embodiment is configured by a large number of switches using transparent electrodes arranged in a matrix, and the user uses a touch pen (not shown) to display the screen on the UI panel 110. Touching any one of the switches on the touch panel turns on. When any switch on the touch panel is turned on, the UI panel control unit 122 outputs coordinate information representing the position of the turned-on switch in two-dimensional orthogonal coordinates in the matrix to the CPU 114. When coordinate information is input from the UI panel control unit 122, the CPU 114 stores the coordinate information in the HDD 120.

  On the other hand, the radiation irradiation device 18 includes an irradiation device control unit 140 that controls the operation of the radiation irradiation device 18 as a whole. The irradiation device control unit 140 is realized by a microcomputer, and a communication I / F unit 142 is connected thereto. The communication I / F unit 142 is connected to the connection terminal 18A, and controls transmission of various information to and from the console 26 connected via the connection terminal 18A. Therefore, the irradiation apparatus control unit 140 can transmit and receive various types of information to and from the console 26 via the communication I / F unit 142. Further, the radiation source control unit 140 is connected to the radiation source 42, and the irradiation device control unit 140 controls the radiation source 42 based on the exposure conditions received via the communication I / F unit 142.

  Further, the radiation irradiation device 18 has a motor 146 that generates a driving force for moving the slit plate 44A, a motor 148 that generates a driving force for moving the slit plate 44B, and a motor for moving the slit plate 44C. A motor 150 that generates a driving force and a motor 152 that generates a driving force for moving the slit plate 44D are provided.

  The radiation irradiation device 18 controls the motor driver 154 that controls the drive of the motor 146, the motor driver 156 that controls the drive of the motor 148, the motor driver 158 that controls the drive of the motor 150, and the drive control of the motor 152. And a motor driver 160 for performing.

  The motor 146 is connected to the irradiation device controller 140 via the motor driver 154, the motor 148 is connected to the irradiation device controller 140 via the motor driver 156, and the motor 150 is connected to the irradiation device controller 140 via the motor driver 158. The motor 152 is connected to the irradiation device control unit 140 via the motor driver 160. Accordingly, the driving of the motors 146, 148, 150, and 152 is controlled by the irradiation device control unit 140 in accordance with an instruction from the console 26.

By the way, in the imaging system 10 according to the present embodiment, the cumulative exposure dose per unit area (1 cm ² in the present embodiment) of the patient 14 reaches a predetermined exposure dose threshold. In addition, the exposure dose limiting function for limiting the exposure dose to the irradiation field excluding the region of interest of radiation X is mounted. For this reason, in the imaging system 10 according to the present embodiment, the exposure dose threshold value is set. Information indicating the exposure dose history (hereinafter referred to as “exposure dose threshold information”), information indicating the history of exposure dose (hereinafter referred to as “exposure dose history information”), and a weight value used when calculating the cumulative exposure dose. Information (hereinafter referred to as “weight value management information”) is stored in advance in the HDD 120 of the console 42.

  FIG. 7 schematically shows an example of the exposure dose threshold information. As shown in the figure, the exposure dose threshold information according to the present embodiment stores the exposure dose threshold for each organ type such as heart, lung, and stomach. In addition, what is necessary is just to set the said dose threshold value information based on the medical exposure guideline etc. by the Japan Radiation Engineers Association.

  On the other hand, FIG. 8 schematically shows an example of the exposure dose history information. As shown in the figure, in the exposure history information according to the present embodiment, ID (Identification), imaging date / time, exposure area, exposure dose, exposure period, and frame rate information are stored for each patient. It is structured as a thing.

  The ID is information for specifying a corresponding patient, and information given in advance as information different for each patient is used. The imaging date and time is information indicating the date and time when a radiographic image was captured for the corresponding patient, and the exposure area is information indicating the area where the radiation X was exposed to the corresponding patient.

In the imaging system 10 according to the present embodiment, as schematically shown as an example in FIG. 10, an irradiation field of radiation X (hereinafter referred to as “full-open irradiation field”) when the aperture state of the diaphragm 44 is fully opened. .) Is divided into a matrix by a plurality of rectangular regions 64 each having a unit area (1 cm ² in the present embodiment), and the cumulative exposure dose applied in the exposure dose limiting function for each rectangular region 64. Is calculated.

  The exposure area is coordinate information indicating the position of the rectangular area 64 corresponding to the position where the radiation X is exposed, and the exposure dose is information indicating the exposure dose of the radiation X with respect to the corresponding exposure area. The said exposure period is information which shows the period when the radiation X of the corresponding exposure amount was exposed with respect to the corresponding exposure area | region. In the imaging system 10 according to the present embodiment, the coordinate information of the XY coordinate system based on the rectangular region 64 positioned at the upper left corner point in the fully open irradiation field shown in FIG. 10 is applied as the coordinate information. Needless to say, this is not a limitation.

  Further, the frame rate is information indicating a frame rate at the time of capturing a moving image of a radiographic image performed on a corresponding patient at a corresponding capturing date and time. In the capturing system 10 according to the present embodiment, 15 ( fps) or 30 (fps) is selectively applied.

  In the imaging system 10 according to the present embodiment, each information of the exposure area, the exposure amount, and the exposure period is stored for each frame (one image) in the radiographic image moving image shooting. .

  In the example shown in the figure, for example, for a patient assigned with “01-001” as an ID, a radiographic image is captured between 14:20 and 14:30 on February 16, 2010. The exposure area, exposure dose, and exposure period at this time are stored for each frame as shown in the figure, and the frame rate at this time is stored at 15 (fps). Yes.

  On the other hand, FIG. 9 schematically shows an example of the weight value management information. As shown in the figure, the weight value management information according to the present embodiment is configured by storing information on parameters, conditions, and weight values in advance.

  The parameter is a parameter applied when determining a weight value for the past cumulative exposure dose, the condition is information indicating the range of the parameter, and the weight value is the parameter corresponding to the corresponding condition. Is information indicating a weight value in the case of matching.

  In the example shown in the figure, the elapsed time t (minutes) from the irradiation of the radiation X to the present time is applied as the parameter, and when the elapsed time t is less than 1440 (minutes), the weight value is used. The maximum value “1” is applied, and when the elapsed period t is 1440 (minutes) or more and less than 10080 (minutes), “0.9” is applied as the weight value, etc. .

  Next, the configuration of the radiation detector 36 in the case of adopting an indirect conversion method in which radiation is indirectly converted into electric charges using a phosphor material and a photoelectric conversion element will be described.

  FIG. 11 is a schematic cross-sectional view schematically showing the configuration of three pixel portions of the indirect conversion type radiation detector 36 according to an embodiment of the present invention.

  In the radiation detector 36, a signal output unit 302, a photoelectric conversion unit 82, and a scintillator 304 are sequentially stacked on an insulating substrate 300, and a pixel unit is configured by the signal output unit 302 and the photoelectric conversion unit 82. ing. A plurality of pixel units are arranged on the substrate 300, and the signal output unit 302 and the photoelectric conversion unit 82 in each pixel unit are configured to overlap each other.

  The scintillator 304 is formed on the photoelectric conversion unit 82 via a transparent insulating film 306, and a phosphor that emits light by converting radiation incident from above (on the side opposite to the substrate 300) into light is formed. Is. By providing such a scintillator 304, the radiation transmitted through the subject is absorbed and light is emitted.

  The wavelength range of the light emitted by the scintillator 304 is preferably the visible light range (wavelength 360 nm to 830 nm), and in order to enable monochrome imaging by the radiation detector 36, the wavelength range of green is included. Is more preferable.

  Specifically, the phosphor used in the scintillator 304 preferably contains cesium iodide (CsI) when imaging using X-rays as radiation, and has an emission spectrum of 420 nm to 600 nm at the time of X-ray irradiation. It is particularly preferable to use CsI (Tl). Note that the emission peak wavelength of CsI (Tl) in the visible light region is 565 nm.

  For example, when the scintillator 304 is formed of a columnar crystal such as CsI (Tl), the scintillator 304 may be formed by vapor deposition on a vapor deposition substrate. When the scintillator 304 is formed by vapor deposition as described above, an Al plate is often used as the vapor deposition substrate from the viewpoint of X-ray transmittance and cost, but is not limited thereto. When GOS is used as the scintillator 304, the scintillator 304 may be formed by applying GOS to the surface of the TFT active matrix substrate 74 without using a vapor deposition substrate.

  The photoelectric conversion unit 82 includes an upper electrode 310, a lower electrode 312, and a photoelectric conversion film 314 disposed between the upper and lower electrodes.

Since it is necessary for the upper electrode 310 to cause the light generated by the scintillator 304 to be incident on the photoelectric conversion film 314, it is preferable that the upper electrode 310 be formed of a conductive material that is transparent at least with respect to the emission wavelength of the scintillator 304. It is preferable to use a transparent conductive oxide (TCO) having a high transmittance for visible light and a small resistance value. Note that although a metal thin film such as Au can be used as the upper electrode 310, the TCO is preferable because the resistance value is likely to increase when the transmittance of 90% or more is obtained. 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 310 may have a single configuration common to all pixel portions, or may be divided for each pixel portion.

  The photoelectric conversion film 314 absorbs light emitted from the scintillator 304 and generates charges corresponding to the absorbed light. The photoelectric conversion film 314 may be formed using a material that generates charges when irradiated with light, and can be formed using, for example, amorphous silicon, an organic photoelectric conversion material, or the like. The photoelectric conversion film 314 containing amorphous silicon has a wide absorption spectrum and can absorb light emitted by the scintillator 304. If the photoelectric conversion film 314 containing an organic photoelectric conversion material has a sharp absorption spectrum in the visible range, electromagnetic waves other than light emitted by the scintillator 304 are hardly absorbed by the photoelectric conversion film 314, and radiation such as X-rays. Can be effectively suppressed noise generated by the absorption by the photoelectric conversion film 314.

  The organic photoelectric conversion material constituting the photoelectric conversion film 314 is preferably such that its absorption peak wavelength is closer to the emission peak wavelength of the scintillator 304 in order to absorb light emitted by the scintillator 304 most efficiently. Ideally, the absorption peak wavelength of the organic photoelectric conversion material matches the emission peak wavelength of the scintillator 304, but if the difference between the two is small, the light emitted from the scintillator 304 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 304 is preferably within 10 nm, and more preferably within 5 nm.

  Examples of organic photoelectric conversion materials that can satisfy such conditions include quinacridone-based organic compounds and phthalocyanine-based organic compounds. For example, since the absorption peak wavelength of quinacridone in the visible region is 560 nm, if quinacridone is used as the organic photoelectric conversion material and CsI (Tl) is used as the material of the scintillator 304, the difference between the peak wavelengths can be within 5 nm. Thus, the amount of charge generated in the photoelectric conversion film 314 can be substantially maximized.

  Next, the photoelectric conversion film 314 applicable to the radiation detector 36 according to the present embodiment will be specifically described.

  The electromagnetic wave absorption / photoelectric conversion site in the radiation detector 36 according to the present invention includes a pair of lower electrode 312 and upper electrode 310, and an organic photoelectric conversion film 314 sandwiched between the lower electrode 312 and upper electrode 310. It can be composed of layers. 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.

  The organic p-type semiconductor (compound) is a donor organic semiconductor (compound) mainly represented 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. Therefore, 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) mainly represented 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. Therefore, 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 314 are described in detail in Japanese Patent Application Laid-Open No. 2009-32854, and thus the description thereof is omitted. Note that the photoelectric conversion film 314 may be formed by further containing fullerenes or carbon nanotubes.

  The thickness of the photoelectric conversion film 314 is preferably as large as possible in terms of absorbing light from the scintillator 304. However, when the thickness is larger than a certain level, the photoelectric conversion film 314 is generated in the photoelectric conversion film 314 by a bias voltage applied from both ends of the photoelectric conversion film 314. 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 36 shown in FIG. 11, the photoelectric conversion film 314 has a single-sheet configuration common to all the pixel portions, but may be divided for each pixel portion.

  The lower electrode 312 is a thin film divided for each pixel portion. The lower electrode 312 can be made of a transparent or opaque conductive material, and aluminum, silver, or the like can be preferably used.

  The thickness of the lower electrode 312 can be, for example, 30 nm or more and 300 nm or less.

  In the photoelectric conversion unit 82, by applying a predetermined bias voltage between the upper electrode 310 and the lower electrode 312, one of charges (holes, electrons) generated in the photoelectric conversion film 314 is moved to the upper electrode 310. And the other can be moved to the lower electrode 312. In the radiation detector 36 of the present embodiment, a wiring is connected to the upper electrode 310, and a bias voltage is applied to the upper electrode 310 via this wiring. In addition, the polarity of the bias voltage is determined so that electrons generated in the photoelectric conversion film 314 move to the upper electrode 310 and holes move to the lower electrode 312, but this polarity is opposite. May be.

  The photoelectric conversion unit 82 constituting each pixel unit only needs to include at least the lower electrode 312, the photoelectric conversion film 314, and the upper electrode 310, but in order to suppress an increase in dark current, the electron blocking film 316 and the holes are included. It is preferable to provide at least one of the blocking films 318, and it is more preferable to provide both.

  The electron blocking film 316 can be provided between the lower electrode 312 and the photoelectric conversion film 314. When a bias voltage is applied between the lower electrode 312 and the upper electrode 310, electrons are transferred from the lower electrode 312 to the photoelectric conversion film 314. 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 316.

  The material actually used for the electron blocking film 316 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 314, etc., 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 314 are preferable. Since the material applicable as the electron donating organic material is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, description thereof is omitted.

  The thickness of the electron blocking film 316 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 the photoelectric conversion efficiency of the photoelectric conversion unit 82. Is from 50 nm to 100 nm.

  The hole blocking film 318 can be provided between the photoelectric conversion film 314 and the upper electrode 310. When a bias voltage is applied between the lower electrode 312 and the upper electrode 310, the hole blocking film 318 is transferred from the upper electrode 310 to the photoelectric conversion film 314. 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 318.

  The thickness of the hole blocking film 318 is preferably 10 nm or more and 200 nm or less, more preferably 30 nm or more and 150 nm or less, in order to reliably exhibit the dark current suppressing effect and prevent a decrease in the photoelectric conversion efficiency of the photoelectric conversion unit 82. Preferably they are 50 nm or more and 100 nm or less.

  The material actually used for the hole blocking film 318 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 314, etc., 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 the Ea is equal to or larger than the electron affinity (Ea) of the material of the adjacent photoelectric conversion film 314. 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 the case where the bias voltage is set so that holes move to the upper electrode 310 and electrons move to the lower electrode 312 among the charges generated in the photoelectric conversion film 314, the electron blocking film 316 and the hole blocking are set. The position of the film 318 may be reversed. Further, it is not necessary to provide both the electron blocking film 316 and the hole blocking film 318. If either one is provided, a certain degree of dark current suppressing effect can be obtained.

  A signal output unit 302 is formed on the surface of the substrate 300 below the lower electrode 312 of each pixel unit.

  FIG. 12 schematically shows the configuration of the signal output unit 302.

  Corresponding to the lower electrode 312, there are formed a storage capacitor 76 for storing the charge transferred to the lower electrode 312, and a TFT 78 for converting the charge stored in the storage capacitor 76 into an electric signal and outputting it. The region where the storage capacitor 76 and the TFT 78 are formed has a portion that overlaps the lower electrode 312 in a plan view. With such a configuration, the signal output unit 302 and the photoelectric conversion unit 82 in each pixel unit are provided. Will have an overlap in the thickness direction. In order to minimize the plane area of the radiation detector 36 (pixel portion), it is desirable that the region where the storage capacitor 76 and the TFT 78 are formed is completely covered by the lower electrode 312.

  The storage capacitor 76 is electrically connected to the corresponding lower electrode 312 through a conductive material wiring formed through an insulating film 319 provided between the substrate 300 and the lower electrode 312. Thereby, the charges collected by the lower electrode 312 can be moved to the storage capacitor 76.

  In the TFT 78, a gate electrode 320, a gate insulating film 322, and an active layer (channel layer) 324 are stacked, and a source electrode 326 and a drain electrode 328 are formed on the active layer 324 at a predetermined interval. The active layer 324 can be formed of, for example, amorphous silicon, amorphous oxide, organic semiconductor material, carbon nanotube, or the like. Note that the material forming the active layer 324 is not limited thereto.

The amorphous oxide that can form the active layer 324 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. Oxides containing one (for example, In—Zn—O, In—Ga—O, and Ga—Zn—O) are more preferable, and oxides including In, Ga, and Zn are 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 less than 6) is preferable, and InGaZnO is particularly preferable. ₄ is more preferable. Note that the amorphous oxide that can form the active layer 324 is not limited thereto.

  Examples of the organic semiconductor material that can constitute the active layer 324 include, but are not limited to, phthalocyanine compounds, pentacene, vanadyl phthalocyanine, and the like. In addition, about the structure of a phthalocyanine compound, since it is demonstrated in detail in Unexamined-Japanese-Patent No. 2009-212389, description is abbreviate | omitted.

  If the active layer 324 of the TFT 78 is formed of an amorphous oxide, an organic semiconductor material, or a carbon nanotube, it does not absorb radiation such as X-rays, or even if it is absorbed, it remains extremely small. The generation of noise in 302 can be effectively suppressed.

  When the active layer 324 is formed of carbon nanotubes, the switching speed of the TFT 78 can be increased, and the TFT 78 having a low light absorption in the visible light region can be formed. In addition, when the active layer 324 is formed of carbon nanotubes, the performance of the TFT 78 is remarkably deteriorated only by mixing a very small amount of metallic impurities into the active layer 324. Therefore, extremely high purity carbon nanotubes are separated by centrifugation or the like.・ It needs to be extracted and formed.

  Here, any of the above-described amorphous oxide, organic semiconductor material, carbon nanotube, and organic photoelectric conversion material can be formed at a low temperature. Therefore, the substrate 300 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, an aramid, or bionanofiber can also be used. Specifically, flexible materials such as polyesters such as polyethylene terephthalate, polybutylene phthalate, polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, poly (chlorotrifluoroethylene), etc. 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 300 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.

  Since aramid can be applied at a high temperature process of 200 ° C. or more, the transparent electrode material can be cured at a high temperature to reduce the resistance, and can also be used for automatic mounting of a driver IC including a solder reflow process. Moreover, since aramid has a thermal expansion coefficient close to that of ITO (indium tin oxide) or a glass substrate, warping after production is small and it is difficult to crack. In addition, aramid can form a substrate thinner than a glass substrate or the like. Note that the substrate 300 may be formed by stacking an ultrathin glass substrate and aramid.

  Bionanofiber is a composite of cellulose microfibril bundles (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 an acrylic resin or an 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 60-70% 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, compared to glass substrates, etc. The substrate 300 can be thinly formed.

  In this embodiment mode, the signal output portion 302, the photoelectric conversion portion 82, and the transparent insulating film 306 are formed in this order on the substrate 300, and the scintillator 304 is attached to the substrate 300 using an adhesive resin having low light absorption. The radiation detector 36 is formed by attaching. Hereinafter, the substrate 300 formed up to the transparent insulating film 306 is referred to as a TFT active matrix substrate (hereinafter also referred to as “TFT substrate”) 74.

  In the electronic cassette 20 according to the present embodiment, the radiation detector 36 is incorporated so that the radiation X is irradiated from the TFT substrate 74 side.

  Here, as shown in FIG. 13, the radiation detector 36 is irradiated with radiation from the side on which the scintillator 304 is formed, and reads a radiation image by the TFT substrate 74 provided on the back side of the incident surface of the radiation. In the case of the so-called back side scanning method (so-called PSS (Penetration Side Sampling) method), the scintillator 304 emits light more strongly on the upper surface side of the figure (opposite side of the TFT substrate 74), and radiation is irradiated from the TFT substrate 74 side. Thus, in the case of a so-called surface reading method (so-called ISS (Irradiation Side Sampling) method) in which a radiation image is read by a TFT substrate 74 provided on the surface side of the radiation incident surface, radiation transmitted through the TFT substrate 74 is transmitted. The light enters the scintillator 304 and the TFT substrate 74 side of the scintillator 304 emits light more intensely. Electric charges are generated by the light generated by the scintillator 304 in each photoelectric conversion unit 82 provided on the TFT substrate 74. For this reason, since the radiation detector 36 is closer to the light emission position of the scintillator 304 with respect to the TFT substrate 74 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 36, the photoelectric conversion film 314 is made of an organic photoelectric conversion material, and radiation is hardly absorbed by the photoelectric conversion film 314. For this reason, the radiation detector 36 according to the present embodiment suppresses a decrease in sensitivity to the radiation X because the amount of radiation absorbed by the photoelectric conversion film 314 is small even when the radiation is transmitted through the TFT substrate 74 by the surface reading method. be able to. In the surface reading method, radiation passes through the TFT substrate 74 and reaches the scintillator 304. Thus, when the photoelectric conversion film 314 of the TFT substrate 74 is formed of an organic photoelectric conversion material, the radiation in the photoelectric conversion film 314 is obtained. Therefore, it is suitable for the surface reading method.

  Further, the amorphous oxide constituting the active layer 324 of the TFT 78 and the organic photoelectric conversion material constituting the photoelectric conversion film 314 can be formed at a low temperature. Therefore, the substrate 300 can be formed of a plastic resin, aramid, or bionanofiber that absorbs little radiation. Since the substrate 300 formed in this way has a small amount of radiation absorption, a decrease in sensitivity to the radiation X can be suppressed even when the radiation passes through the TFT substrate 74 by the surface reading method.

  Further, for example, the radiation detector 36 is attached to the irradiation surface 32 portion in the housing 30 so that the TFT substrate 74 is on the irradiation surface 32 side, and the substrate 300 is made of a highly rigid plastic resin, aramid, or bio-nanofiber. When formed, since the radiation detector 36 itself has high rigidity, the irradiation surface 32 portion of the housing 30 can be formed thin. Further, when the substrate 300 is formed of a highly rigid plastic resin, aramid, or bionanofiber, the radiation detector 36 itself has flexibility, so that even when an impact is applied to the irradiation surface 32, the radiation detector 36 is damaged. It ’s hard.

  Next, the operation of the imaging system 10 according to the present embodiment will be described.

  When performing an IVR on a patient 14 using the imaging system 10 according to the present embodiment, an operator who performs the IVR firstly has coordinate information indicating a planned approach path of the catheter 60 as a preparation stage of the IVR. Enter as shown below.

  That is, the surgeon first sets the catheter 60 in the state where the insertion port and the lesioned part can be imaged by the electronic cassette 20 and the predetermined reference portion (the top of the head in the present embodiment) is placed on the mounting table. The patient 14 is laid on the mounting table 16A so as to be positioned at a reference position predetermined for each patient in 16A. Next, the surgeon opens the slit plates 44 </ b> A to 44 </ b> D of the diaphragm 44 to the radiation irradiation device 18 through the console 26 and then emits the radiation X with a predetermined exposure dose. In this manner, the radiation source 42 is controlled so that the electronic cassette 20 is controlled to take a radiation image. As a result, the electronic cassette 20 captures a radiographic image as will be described in detail in the description of a radiographic image capturing process (see FIG. 14) described later, and transmits image information obtained by the capturing to the console 26. The On the other hand, when the image information is received, the console 26 displays the radiographic image indicated by the image information on the display of the UI panel 110.

  Therefore, the surgeon traces the planned entry path of the catheter 60 in the body of the patient 14 on the radiographic image displayed on the display of the UI panel 110 with a touch pen, thereby obtaining coordinate information (hereinafter referred to as “path”). "Coordinate information"). At this time, the surgeon touches the outline of the planned entry path and the outline of an organ (hereinafter referred to as “determination target organ”) existing in the vicinity of the planned entry path and in the region that can be the radiation X irradiation field. The coordinate information indicating the region where the determination target organ exists (hereinafter referred to as “organ coordinate information”) is input, and the name of the determination target organ existing in the region indicated by the organ coordinate information is input. Information (hereinafter referred to as “organ name information”) is input via the operation panel 112. The route coordinate information and the organ coordinate information are coordinate information of the same XY coordinate system as the coordinate information indicating the exposure area described above.

  The path coordinate information, the organ coordinate information, and the organ name information input from the operator as described above are stored in the HDD 120 by the console 26 in a state in which the corresponding organ coordinate information and organ name information are associated with each other. .

  When the above preparation steps are completed, the surgeon determines the exposure conditions such as tube voltage and tube current when irradiating the radiation X via the operation panel 112 of the console 26 according to the imaging region and imaging conditions of the patient 14. After performing the exposure condition designation operation for designating, the instruction operation for instructing the start of IVR is performed.

  When the instruction operation is performed, the console 26 executes a radiation image capturing process.

  Next, with reference to FIG. 14, the operation of the console 26 at the time of executing the radiographic image capturing process will be described. FIG. 14 is a flowchart showing the flow of processing of the radiographic image capturing processing program executed by the CPU 114 of the console 26 at this time, and the program is stored in a predetermined area of the ROM 116 in advance. Here, a case where the ID of the patient 14 to be treated is set in advance by an operator or the like will be described.

  In step 200 in the figure, information on the imaging date / time, the exposure area, the exposure dose, and the exposure period corresponding to the ID of the patient 14 set in advance is read from the exposure dose history information of the HDD 120, and the next step 202 is performed. Then, the exposure condition specified by the operator is transmitted to the radiation irradiation device 18 and the electronic cassette 20 to set the exposure condition. In response to this, the irradiation apparatus control unit 140 prepares for exposure under the received exposure conditions. In some cases, information related to the patient 14 to be treated is not stored in the exposure history information. In this case, it is needless to say that each information is not read in step 200 described above.

  In the next step 204, information indicating the position of the insertion port of the catheter 60 indicated by the path coordinate information stored in the IVR preparation stage described above is set together with setting instruction information for instructing the setting of the opening state of the diaphragm 44, and radiation. Transmit to the irradiation device 18.

  When the setting instruction information is received, in the radiation irradiation apparatus 18, the position corresponding to the position of the insertion port of the catheter 60 indicated by the information received together with the setting instruction information is set in the opening region 51 by the irradiation apparatus control unit 140. The position of each of the slit plates 44A to 44D so as to be the center and the shape of the opening region 51 is a predetermined shape and the area of the opening region 51 is a predetermined area that is at least narrower than in the fully open state. To control. Note that, in the imaging system 10 according to the present embodiment, a region (hereinafter referred to as “direct radiation field”) on which a direct line in the radiation X of the patient 14 is irradiated as the predetermined shape and the predetermined area. However, the shape and area preset by the surgeon or the like are applied as the shape and area to be a region including at least the region of interest.

  In addition, since the predetermined area is an area irradiated with the direct line of the radiation X, it is preferable to appropriately set according to the size of the lesioned part. However, for example, the irradiation surface of the radiation detector 36 A predetermined fixed area such as an area irradiated with a direct line of radiation X may be applied to an area of a predetermined ratio (10% as an example) with respect to the area of 36A.

  In the next step 206, instruction information for instructing the start of exposure is transmitted to the radiation irradiation device 18 and the electronic cassette 20. In response to this, the radiation source 42 generates and emits radiation at a tube voltage, tube current, or the like according to the exposure conditions received by the radiation irradiation device 18 from the console 26.

  The radiation X emitted from the radiation source 42 reaches the electronic cassette 20 after passing through the patient 14 via the diaphragm 44. As a result, electric charges are accumulated in the accumulation capacitors 76 of the respective pixel portions 80 of the radiation detector 36 incorporated in the electronic cassette 20.

  The cassette control unit 100 of the electronic cassette 20 receives in advance a period from when the instruction information instructing the start of exposure is received until the accumulation of charges in the storage capacitors 76 of the pixel units 80 of the radiation detector 36 is completed. After the elapse of a predetermined period, the gate line driver 88 is controlled so that the gate line driver 88 outputs an ON signal to each gate wiring 84 one line at a time, and each TFT 78 connected to each gate wiring 84 is sequentially output one line at a time. Turn it on.

  In the radiation detector 36, when the TFTs 78 connected to the gate wirings 84 are turned on one line at a time, the charges accumulated in the storage capacitors 76 one line at a time flow out to the data wirings 86 as electric signals. The electric signal flowing out to each data wiring 86 is converted into digital image information by the signal processing unit 90 and stored in the line memory 98.

  The cassette control unit 100 performs predetermined image correction processing on the image information stored in the line memory 98 and transmits the image information to the console 26 via the optical communication control unit 102.

  The cassette control unit 100 repeatedly executes the above operation at a speed (15 (fps) or 30 (fps) in the present embodiment) preset by an operator or the like as a moving image shooting speed (frame rate). At the same time, the display driver 104 is controlled so that the radiation image indicated by the image information subjected to the image correction processing is displayed on the display 28.

  Therefore, in the next step 208, the process waits until image information for one frame is received from the electronic cassette 20, and in the next step 210, the received image information is stored in the HDD 120, and further in the next step 212. Then, the UI panel control unit 122 is controlled so that the radiation image indicated by the received image information is displayed on the display of the UI panel 110 for confirmation or the like.

  In the next step 214, position information indicating the position of the distal end portion of the catheter 60 is acquired.

  In the console 26 according to the present embodiment, the CPU 114 executes a position specifying process program for specifying the position of the distal end portion of the catheter 60 in a time-sharing manner in parallel with the radiographic image capturing process program.

  In this position specifying processing program, electrical signals received in real time from the reflective photosensor 62 in time series are wide white areas, narrow black areas, and narrow white areas in the stripe pattern provided on the catheter 60. It is determined that the catheter 60 is moving in the direction in which it is inserted into the body of the patient 14 when it indicates that the region has shifted in the order of the regions, and the amount of movement at this time is represented by the number of occurrences of the wide white region. It is specified by multiplying the width of one group. Similarly, the catheter 60 moves in the direction of being pulled out of the body of the patient 14 when the electrical signal indicates that the wide black region, the narrow white region, and the narrow black region in the striped pattern have shifted in this order. The amount of movement at this time is specified by multiplying the number of appearances of the wide black region by the width of the group of the striped pattern.

  In the position specifying processing program, the movement amount obtained when the catheter 60 is moving in the direction of insertion into the body of the patient 14 obtained by the above processing is integrated, and the catheter 60 is moved from the body of the patient 14. The amount of insertion of the catheter 60 into the body of the patient 14 is specified by subtracting the amount of movement when moving in the direction of removal.

  In the position specifying processing program, the position of the distal end portion of the catheter 60 is specified based on the specified insertion amount and the path coordinate information indicating the planned approach path of the catheter 60 stored in the IVR preparation stage described above. The coordinate information indicating the position (hereinafter referred to as “tip portion coordinate information”) is stored in a predetermined area of the RAM 118 in real time.

  Therefore, in step 214, the position information indicating the position of the distal end portion of the catheter 60 is acquired by reading the distal end portion coordinate information stored by the position specifying processing program from the RAM 118.

  In the next step 216, information indicating the position of the distal end portion of the catheter 60 indicated by the acquired position information is transmitted to the radiation irradiating apparatus 18 together with change instruction information for instructing a change in the opening state of the throttle portion 44.

  When the change instruction information is received, in the radiation irradiation apparatus 18, the irradiation apparatus control unit 140 sets the position corresponding to the position of the distal end portion of the catheter 60 indicated by the information received together with the change instruction information in the opening region 51. The positions of the slit plates 44A to 44D are controlled so as to be centered. At this time, the irradiation device control unit 140 controls each of the slit plates 44A to 44D so as to maintain the shape and area of the opening region 51 so far.

  In the imaging system 10 according to the present embodiment, the position of the distal end portion of the catheter 60 is assumed to be the center position of the region of interest, and a radiographic image including at least the region of interest is converted into an electronic cassette 20 by the processing of step 216. Will be displayed on the display 28.

  In the next step 218, the exposure dose to the patient 14 when obtaining image information for one frame received from the electronic cassette 20 in the processing of step 208 is calculated as follows.

  First, the exposure amount r per unit area of the imaging period for one frame in the radiation X irradiation field (fully opened irradiation field) when assuming that the aperture state of the aperture 44 is in a fully open state is calculated per unit time. It is calculated based on various factors such as tube voltage and FSD (Focus Skin Distance) which influence the irradiation amount of the radiation X. At this time, in the imaging system 10 according to the present embodiment, the exposure dose r is calculated for each rectangular area 64. The exposure dose r can be calculated using, for example, the NDD method (Non Desimeter Dosimetry Method).

  Then, among the calculated exposure dose r for each rectangular area 64, the exposure dose r of the rectangular area 64 located in the area where the radiation X is blocked by the slit plates 44A to 44D of the diaphragm 44 is set to the corresponding slit plate 44A to 44A. It is converted into an amount attenuated at an attenuation rate corresponding to the thickness in the height direction of 44D.

  In the next step 220, the exposure dose r and the exposure period of the radiation X for each rectangular area 64 calculated by the processing in step 218, together with coordinate information (exposed area) indicating the position of the corresponding rectangular area 64, The information is additionally stored (registered) in the dose history information in association with the ID of the patient 14 to be treated. At this time, as the exposure period, an imaging period of one frame corresponding to a frame rate (15 (fps) or 30 (fps) in the present embodiment) preset by an operator or the like is applied. The

  In the next step 222, the cumulative exposure dose R so far in the irradiation field of the radiation X at this time is calculated as follows.

  That is, first, all the conditions and weight values are read from the weight value management information of the HDD 120, while the past exposure dose for the patient 14 to be treated, indicated by the information read by the processing of step 200, is determined for each photographing date and time. (For each treatment) and for each rectangular region 64.

  Next, after multiplying the dose obtained by the above by the weight value corresponding to the elapsed period corresponding to each treatment, the dose obtained by multiplying the weight value obtained for each treatment by this is obtained. Summing up for each of the rectangular regions 64. Note that the elapsed period can be obtained by deriving the elapsed period from the time indicated by the corresponding shooting date and time (in this embodiment, the time at the end of shooting) to the present time.

  Then, the exposure amount obtained as described above and the total value for each of the rectangular regions 64 of the exposure amount r stored in the exposure amount history information by the processing of step 220 in the current treatment are obtained for each of the rectangular regions 64. To calculate the cumulative exposure dose R for each of the rectangular areas 64.

  If the information is not read out in step 200, in step 222, the sum of each of the rectangular areas 64 of the exposure dose r stored in the exposure dose history information by the processing in step 220 in the current operation is added. The value is calculated as the cumulative exposure dose R for each of the rectangular areas 64.

  In the next step 224, the cumulative exposure dose R for each rectangular region 64 included in the region excluding the region of interest in the fully open irradiation field calculated by the processing in step 222 (hereinafter referred to as “non-region of interest irradiation field”) It is determined whether there is an organ that reaches the exposure dose threshold of the organ located at the corresponding position. If the determination is affirmative, the process proceeds to step 226.

  At this time, in step 224, the names of organs included in the coordinate range corresponding to the non-region of interest field are identified based on the organ coordinate information and organ name information stored in the IVR preparation stage described above. Then, the exposure dose threshold value (see also FIG. 7) corresponding to the specified organ is read from the HDD 120.

  In step 224, it is determined whether or not there is a cumulative exposure dose R of the rectangular region 64 included in the non-interest region irradiation field that reaches the exposure dose threshold value of the organ located at the corresponding position. At this time, if there is no organ located at the corresponding position, a threshold set in advance by an operator or the like is applied as an exposure dose threshold in a region other than the organ. Here, the exposure dose threshold in the region other than the organ may be set in advance for each region in a wider range than the organ such as the chest, abdomen, arm, and leg, or the entire region other than the organ. A common threshold may be set for.

  In step 226, the shape and area of the opening region 51 of the diaphragm 44 are set such that at least the region of interest is irradiated with a direct line, and the non-region of interest irradiation field is the rectangular region 64 included in the non-region of interest irradiation field. Of these, the cumulative exposure dose R is derived such that the sum of the exposure doses for the rectangular region 64 that reaches the corresponding exposure dose threshold value has a shape and area that minimizes the cumulative exposure dose R.

  In the next step 228, information indicating the shape and area of the opening region 51 derived by the processing in step 226 is transmitted to the radiation irradiation device 18 together with change instruction information for instructing change of the opening state of the aperture 44, and thereafter Step 236 follows.

  When the change instruction information is received, the radiation irradiating apparatus 18 causes the irradiation apparatus control unit 140 to position the slit plates 44A to 44D so as to have the shape and area indicated by the information received together with the change instruction information. Control.

  On the other hand, when a negative determination is made in step 224, the process proceeds to step 230, in which all cumulative exposure doses R of the rectangular region 64 included in the non-interesting region irradiation field are the exposure doses of the organ located at the corresponding position. It is determined whether or not the amount is less than an amount obtained by subtracting a predetermined margin amount from the threshold value. If a negative determination is made, the process proceeds to step 236 described later, whereas if a positive determination is made, the process proceeds to step 232. .

  At this time, in step 230, the names of the organs included in the coordinate range corresponding to the non-region of interest irradiation field are specified based on the organ coordinate information and organ name information stored in the IVR preparation stage described above. Then, the exposure dose threshold value (see also FIG. 7) corresponding to the specified organ is read from the HDD 120.

  In step 230, whether or not all of the cumulative exposure dose R of the rectangular region 64 included in the non-interest region irradiation field is less than the amount obtained by subtracting the margin amount from the exposure dose threshold value of the organ located at the corresponding position. Determine whether or not. In this case as well, if there is no organ located at the corresponding position, the threshold value preset by the operator or the like as the exposure dose threshold value in the region other than the organ as in the above-described processing of step 224. Apply.

  In step 232, the shape and area of the opening region 51 of the diaphragm 44 are set such that at least a region of interest is irradiated with a direct line, and for a non-interest region irradiation field, any rectangular region included in the non-interest region irradiation field. 64 is derived so that the total value of the exposure dose for the rectangular region 64 is the maximum in the range that does not reach the corresponding exposure dose threshold.

  In the next step 234, information indicating the shape and area of the opening region 51 derived by the processing in step 232 is transmitted to the radiation irradiation device 18 together with change instruction information for instructing change of the opening state of the aperture 44, and thereafter Step 236 follows.

  When the change instruction information is received, the radiation irradiating apparatus 18 causes the irradiation apparatus control unit 140 to position the slit plates 44A to 44D so as to have the shape and area indicated by the information received together with the change instruction information. Control.

  In step 236, it is determined whether or not the timing for ending the radiographic image capture has arrived. If a negative determination is made, the process returns to step 208, whereas if an affirmative determination is made, the process proceeds to step 238. In the radiographic image capturing processing program according to the present embodiment, it is determined whether or not the timing for ending the imaging in step 236 has been reached by an operator via an input unit such as the operation panel 112. However, the present invention is not limited to this, but is not limited to this. Whether the power switch (not shown) of the electronic cassette 20 or the radiation irradiating apparatus 18 is turned off. It goes without saying that other forms, such as a form performed by determining whether or not, may be used.

  In step 238, the shooting date and time and the frame rate corresponding to the information stored in the exposure history information in this treatment are stored in the exposure dose history information. In the next step 240, the processing of step 206 is started. Instruction information for instructing to stop the exposure is transmitted to the radiation irradiating apparatus 18 and the electronic cassette 20, and in the next step 242, the image information stored by the process of step 210 is sent to a RIS (Radiology Information System) server (not shown). After transmitting via a hospital network (not shown), the radiographic imaging program is terminated. In the RIS server, it is possible to interpret and diagnose a radiographic image taken by a doctor using the image information received from the console 26.

  FIG. 15 is a diagram illustrating an example of a radiation image displayed on the display surface 28A of the display 28 by irradiating the entire surface of the irradiation surface 36A of the radiation detector 36 according to the present embodiment with the radiation X. The patient 14 displayed on the display surface 28A of the display 28 by irradiating the partial area of the irradiation surface 36A of the radiation detector 36 with the radiation X by executing the radiographic imaging processing program according to the present embodiment. It is a figure which shows an example of the radiographic image in the case of being supine in the same state as the state shown in FIG.

  As shown in FIG. 16, in imaging system 10 according to the present embodiment, the irradiation region of the direct line of radiation X can be limited to a predetermined region (a region including a region of interest in the present embodiment). As a result, the exposure dose to the patient 14 can be suppressed, and the transmitted dose at the position of the corresponding slit plate is also applied to the peripheral area of the predetermined area (gradation area in the display image of the figure). Since the corresponding image is displayed in the state shown in the figure as an example, the radiation image of the peripheral part can also be observed.

  As described above in detail, in the present embodiment, the exposure amount per unit time by the subject of the radiation irradiated from the radiation source to the subject for moving image radiography is determined in advance. Calculated for each section area (rectangular area 64 in the present embodiment) defined as a unit area, and exposure information (in this embodiment, "exposure" in the exposure history information) indicating the calculated exposure. , Segmented region specifying information for identifying the corresponding segmented region (in this embodiment, “exposed region” in the dose history information) and subject specifying information for identifying the subject (in this embodiment, Since the stored dose information is used to derive and use the accumulated dose for each of the divided areas, the excessive radiation dose to the subject is stored. Effective exposure It is possible to prevent.

  Further, in the present embodiment, time point information (in this embodiment, “imaging date / time” in the dose history information) indicating the time point at which the subject is irradiated with the radiation, exposure per one treatment of the radiation. Surgical exposure dose information indicating the amount (in this embodiment, “exposure dose” corresponding to the same “shooting date” in the exposure dose history information), and frame rate information indicating the frame rate of the moving image shooting (this embodiment In the embodiment, the “frame rate” in the exposure dose history information) is acquired, and the acquired time point information, the treatment exposure information, and the frame rate information are further stored in association with the corresponding subject specifying information. Therefore, the exposure dose indicated by the exposure dose information can be weighted based on the time point information, the treatment exposure dose information, and the frame rate information. Ri, it is possible to prevent the exposure of excess radiation on more effectively subject.

  Furthermore, in the present embodiment, the exposure information is provided between the radiation source and the subject, allows a part of the radiation emitted from the radiation source to pass, and the area can be changed. The amount of radiation that reaches the subject in a state of being narrowed down by the diaphragm (in this embodiment, the diaphragm 44 in the present embodiment) having the configured opening area is indicated, so the diaphragm is used. As a result, the accumulated exposure dose can be derived with high accuracy in the radiographic imaging system, and as a result, it is possible to more effectively prevent the subject from being exposed to excessive radiation.

  Further, when a column crystal of CsI is used as the scintillator 304 and the radiation detector 36 is built in the electronic cassette 20 so as to be a surface reading system, a high-quality image can be obtained. In addition, when an organic photoelectric conversion material is used for the photoelectric conversion film 314, radiation is hardly absorbed by the photoelectric conversion film 314, and more radiation reaches the scintillator 304, thereby improving sensitivity. As a result, when the aperture 44 is narrowed by the aperture 44 and the peripheral portion of the region of interest is irradiated with the radiation that has passed through the aperture 44, the radiographic image at the periphery may be slightly blurred but may be high. There is no problem because the image quality. Further, doctors and engineers can confirm whether or not the region unnecessary for diagnosis is irradiated by observing the degree of blurring of the radiation image at the peripheral portion of the region of interest.

  Further, as shown in FIG. 17, the sensitivity of CsI used as the scintillator 304 changes due to a temperature change. For example, the sensitivity decreases by about 0.3% when the temperature increases once. On the other hand, GOS hardly changes in sensitivity due to temperature change.

  When the electronic cassette 20 performs photographing, various circuits and elements such as the power supply unit 106, the gate line driver 88, and the signal processing unit 90 generate heat. In addition, when moving image shooting is performed with IVR or the like, the shooting time is long. For this reason, in the electronic cassette 20 using CsI as the scintillator 304, the sensitivity of the scintillator 304 may decrease due to heat from various circuits and elements in moving image shooting. An operator who performs IVR increases the dose of radiation to be irradiated when trying to maintain the image quality necessary for diagnosis, but when the dose is increased, the exposure dose to the patient also increases. Therefore, as in the present embodiment, the diaphragm is configured such that the transmitted dose of radiation decreases as it moves away from the peripheral edge of the opening region, thereby suppressing an increase in the exposure dose to the patient. Can do.

  Further, as shown in FIG. 18, the sensitivity of CsI decreases as the cumulative exposure dose increases and the sensitivity decreases, and the reduced sensitivity recovers when maintained without radiation. When taking a video with IVR or the like, it takes a long time to shoot, and when taking a still image frequently during movie shooting, the radiation dose of still image shooting is 10 to 1000 times that of one frame of movie shooting. Therefore, the sensitivity of the scintillator 304 decreases as the cumulative exposure dose increases. Even in such a case, the surgeon increases the dose of radiation to be irradiated when trying to maintain the image quality necessary for diagnosis, but when the dose is increased, the exposure dose to the patient also increases. Therefore, as in the present embodiment, the diaphragm is configured such that the transmitted dose of radiation decreases as it moves away from the peripheral edge of the opening region, thereby suppressing an increase in the exposure dose to the patient. Can do.

  In addition, according to the present embodiment, the diaphragm portion is configured such that the radiation transmission dose decreases with increasing distance from the peripheral portion of the opening region, so that irradiation is performed in accordance with a decrease in sensitivity of the scintillator 304. Even when the dose of the radiation X is increased, an increase in the exposure dose to the patient can be suppressed.

  As described above, the sensitivity of CsI decreases due to temperature change, cumulative exposure dose, and the like. For this reason, the cumulative exposure dose may be calculated in consideration of a decrease in sensitivity of the scintillator 304.

  Specifically, for example, the temperature change of the scintillator 304 may be predicted in advance from the radiation dose according to the imaging conditions, and the cumulative exposure dose may be calculated after taking into account the decrease in sensitivity of the scintillator 304 due to the temperature change. Regarding the temperature change of the scintillator 304 during photographing, for example, a temperature sensor may be provided in the scintillator 304 and the temperature of the scintillator 304 may be monitored by the temperature sensor during photographing.

  The cumulative exposure dose is determined by positioning the region of interest in the central portion of the imaging region, and measuring the total exposure dose in the central portion so far.

  Since the degree of decrease in sensitivity due to the cumulative exposure dose of CsI depends on the operating temperature and storage temperature of the panel, the change in the sensitivity of the scintillator 304 is, for example, that the imaging system 10 first outputs a predetermined amount of radiation every imaging day. When the calibration is performed to calibrate the apparatus state by irradiating the cassette 20, the sensitivity of the scintillator 304 for each shooting date is detected during the calibration of each shooting date, and the curve shown in FIG. After grasping, the temperature change of the scintillator 304 is predicted in advance from the radiation dose according to the imaging conditions, and the cumulative exposure dose may be calculated after taking into account the decrease in the sensitivity of the scintillator 304 due to the temperature change.

  Further, since the region of interest is a surgical site, it is necessary to maintain the image quality. However, the region other than the region of interest has little influence even if the captured image is somewhat noisy. Therefore, when it is determined that the cumulative exposure dose R reaches a predetermined exposure dose, if a restriction is imposed on the exposure dose to the irradiation field excluding the region of interest, a sample hold is read out an image of the restricted region. The operational amplifier 92A of the circuit 92 may be expanded to a range not normally used, and control may be performed to reduce exposure to the maximum.

[Second Embodiment]
In the second embodiment, a description will be given of an example in the case of calculating and applying the cumulative exposure dose to the irradiation field up to the time point when the moving image shooting is finished. In addition, since the configuration of the imaging system 10 according to the second embodiment is the same as that according to the first embodiment, description thereof will be omitted, and radiation will be described with reference to FIG. The operation of the console 26 according to the second embodiment at the time of executing the image capturing process will be described. FIG. 19 is a flowchart showing the flow of processing of the radiographic image capturing processing program executed by the CPU 114 of the console 26 at this time. Steps for executing the same processing as FIG. 14 in FIG. The same step number is assigned and its description is omitted. Here, a case where a lesion site to be treated and a treatment time are set in advance will be described.

  In step 221 of the figure, it is determined whether or not the distal end of the catheter 60 has reached the lesion to be treated. If the determination is negative, the process proceeds to step 222, while the determination is affirmative. Goes to step 250.

  In step 250, based on the cumulative exposure dose R at this time point, the cumulative exposure dose R 'in the radiation X irradiation field up to the time point when the moving image capturing is completed is calculated as follows.

  First, the cumulative exposure dose R up to this point is calculated by the same processing as in step 222, and the time from this point to the end of the treatment time (hereinafter referred to as “remaining treatment time”) is calculated. . Then, assuming that the exposure conditions at this time are maintained, the cumulative exposure dose for each rectangular area 64 during the remaining treatment time elapses is calculated, and the cumulative exposure is calculated for each corresponding rectangular area 64. The cumulative exposure amount R ′ is calculated by adding the amount R.

  In the next step 252, a position corresponding to the cumulative exposure dose R ′ for each rectangular region 64 included in the region (non-region of interest irradiation field) excluding the region of interest in the fully open irradiation field calculated by the processing in step 250 is set at a position corresponding to the cumulative exposure dose R ′. It is determined whether there is an organ that reaches the exposure dose threshold value of the organ to be determined. If the determination is negative, the process proceeds to step 236, whereas if the determination is affirmative, the process proceeds to step 254.

  At this time, in step 252 above, the names of organs included in the coordinate range corresponding to the non-region of interest irradiation field are specified based on the organ coordinate information and organ name information stored in the IVR preparation stage described above. Then, the exposure dose threshold value (see also FIG. 7) corresponding to the specified organ is read from the HDD 120.

  In step 252, it is determined whether or not there is a cumulative exposure dose R ′ of the rectangular region 64 included in the non-interesting region irradiation field that reaches the exposure dose threshold value of the organ located at the corresponding position. At this time, if there is no organ located at the corresponding position, applying a threshold preset by the operator or the like as the exposure dose threshold in the region other than the organ is the same as the processing in step 224. .

  In step 254, the shape and area of the opening region 51 of the diaphragm 44 are set such that at least the region of interest is irradiated with a direct line, and the non-region of interest irradiation field is the rectangular region 64 included in the non-region of interest irradiation field. Of these, the cumulative exposure dose R ′ is derived such that the sum of the exposure doses for the rectangular region 64 that reaches the corresponding exposure dose threshold value has a shape and area that minimizes the cumulative exposure dose R ′.

  In the next step 256, information indicating the shape and area of the opening region 51 derived by the processing in step 254 is transmitted to the radiation irradiation device 18 together with change instruction information for instructing a change in the opening state of the aperture 44, and thereafter Step 236 follows.

  When the change instruction information is received, the radiation irradiating apparatus 18 causes the irradiation apparatus control unit 140 to position the slit plates 44A to 44D so as to have the shape and area indicated by the information received together with the change instruction information. Control.

  As described above in detail, in the present embodiment, in addition to the effects of the first embodiment, as the cumulative exposure dose, the cumulative exposure dose for the irradiation field up to the time when the moving image shooting is completed is calculated. As a result, it is possible to reduce the cumulative exposure up to the time when video shooting is completed in the irradiation field excluding the region of interest to be equal to or less than the predetermined exposure, resulting in more effective radiation exposure to the subject. Can be prevented.

  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. Not exclusively. 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, a case has been described in which the cumulative exposure dose of the radiation field excluding the region of interest is compared with the exposure dose threshold, but the present invention is not limited to this, For example, the cumulative exposure dose and the exposure dose threshold value including the region of interest may be compared.

  In each of the above-described embodiments, the case where the throttle unit 44 is controlled to be throttled when the cumulative dose reaches the dose threshold has been described, but the present invention is not limited to this, and in this case In addition to the control, a control may be performed to reduce the dose of the radiation X emitted from the radiation source 42.

  Further, in each of the above embodiments, as a condition for narrowing down the diaphragm 44, the shape and area of the opening region 51 are such that a direct line is irradiated at least for the region of interest, and the non-region of interest region is the non-region of interest. A description will be given of a case in which the condition that the total value of the exposure dose for the rectangular region 64 in which the cumulative exposure dose reaches the corresponding exposure dose threshold among the rectangular regions 64 included in the irradiation field is the minimum is the shape and area. However, the present invention is not limited to this. For example, at least the region of interest is directly irradiated with a line, such as a condition that the shape and area are directly irradiated with the region of interest. It is good also as a form which applies these conditions.

  In each of the above embodiments, the case where the position of each organ of the patient 14 to be treated is specified by inputting organ coordinate information in advance has been described, but the present invention is not limited to this, For example, there is a pattern between an image indicated by image information obtained by imaging the patient 14 to be treated by the electronic cassette 20 and an image indicated by image information obtained by imaging the human body in advance by the electronic cassette 20. It is good also as a form which specifies the position of each organ of the patient 14 made into a treatment target by performing a matching.

  Further, in each of the above-described embodiments, the embodiment has been described with reference to an example in which the position of the distal end portion of the catheter 60 in the body of the patient 14 is specified using the amount of entry of the catheter 60 in the body of the patient 14. The invention is not limited to this, and may be other forms such as a form specified using an image recognition technology, a form specified using an IC tag, a form specified using a magnetic material, and the like.

  As a form in the case of specifying using the image recognition technology, the image indicated by the image information acquired from the electronic cassette 20 when the specification is performed, and obtained by photographing the distal end portion of the catheter 60 with the electronic cassette 20 in advance. By performing pattern matching with the image indicated by the image information, it is possible to exemplify a form for specifying the position of the distal end portion of the catheter 60 in the image indicated by the image information acquired when performing the specification. .

  In addition, as a form in the case of specifying using an IC tag, an IC tag that transmits a predetermined signal is attached to the distal end portion of the catheter 60, and a plurality of antennas are provided in the operating room, and the antenna is received by the antenna. A mode in which the position of the distal end portion of the catheter 60 is specified by specifying the position of the source IC tag by the triangulation technique based on the received intensity of the signal can be exemplified.

  Furthermore, as a form when specifying using a magnetic body, while attaching a magnet to the front-end | tip part of the catheter 60, the position which does not overlap with the radiation detector 36 of the irradiation surface 32 of the electronic cassette 20 (for example, position of case 40) Is provided with a measuring device for measuring the magnitude of the magnetic force of the magnet attached to the tip of the catheter 60, and the magnet attached to the tip of the catheter 60 from the measuring device based on the magnitude of the magnetic force measured by the measuring device. And the position of the distal end of the catheter 60 on the touch panel of the UI panel 110 can be exemplified based on the distance and the coordinate information of the planned entry route.

  As a modification, the magnetic force of a magnet attached to the distal end portion of the catheter 60 is measured, and the position of the distal end portion of the catheter 60 is estimated by acquiring the direction of the magnetic force generation source. It is good. In this case, the coordinate information of the planned entry route is not necessary. In addition, an ultrasonic transmitter or a γ-ray transmitter may be used instead of the magnet. In this case, the distance from the measuring device to the transmitter by measuring the size of the physical quantity transmitted from the transmitter. And the position of the distal end portion of the catheter 60 is estimated using the distance. As described above, any method may be used for estimating the position of the distal end portion of the catheter 60 inserted into the body of the patient 14 in the body of the patient 14.

  Further, in each of the above-described embodiments, a description has been given of an example in which the position of the distal end portion of the catheter 60 inserted into the body of the patient 14 is estimated in the body of the patient 14. It is good also as a form which estimates the position in the body of the patient 14 of parts other than the front-end | tip part of the catheter 60 inserted in the inside of the patient.

  Further, in each of the above embodiments, the case where the diaphragm 44 is configured to be able to change all the area, shape, and position of the opening region 51 has been described, but the present invention is not limited to this, Any one of these or a combination of the two may be configured to be changeable.

  Further, in each of the above-described embodiments, the description has been given of the case where the direction in which each slit plate in the diaphragm portion 44 is movable is a direction orthogonal to the direction in which the radiation X passes, but the present invention is limited to this. However, it may be configured to be movable in the intersecting direction excluding the direction orthogonal to the direction in which the radiation X passes.

  In each of the above embodiments, the slit plate provided in the diaphragm 44 has a rectangular plate shape in plan view in which the thickness in the height direction gradually increases in a straight line shape in cross section from the front end portion to the rear end portion. Although the case where what was comprised with the member was applied was demonstrated, this invention is not limited to this, It is good also as a form which applies the slit plate of the other shape shown by FIGS. 20-22.

  In the example shown in FIG. 20, each of the slit plates 46 </ b> A to 46 </ b> D provided in the diaphragm portion 46 gradually increases in thickness in a straight line shape in a sectional view from the front end portion to the intermediate portion, and has a rectangular shape in plan view. The slit plate 46A and the slit plate 46B are opposed to each other, the slit plate 46C and the slit plate 46D are opposed to each other, and each of the slit plates 46A to 46D. The slit plates 46 </ b> A to 46 </ b> D are arranged so that an opening region 51 having a rectangular shape in a plan view is formed by the front end portion.

  On the other hand, in the example shown in FIG. 21, as the slit plates 48 </ b> A to 48 </ b> D provided in the diaphragm portion 48 are separated from the peripheral portion of the opening region 51, the thickness becomes stepwise in cross section, that is, gradually increases. The slit plate 48A and the slit plate 48B are opposed to each other, and the slit plate 48C and the slit plate 48D are opposed to each other. The slit plates 48A to 48D are arranged so that the opening regions 51 having a rectangular shape in plan view are formed by the tip portions of the slit plates 48A to 48D.

  Furthermore, in the example shown in FIG. 22, each slit plate group 50A (slit plates 50A1 and 50A2), slit plate group 50B (slit plates 50B1 and 50B2), and slit plate group 50C (slit plates 50C1 and 50C1) provided in the diaphragm unit 50 are provided. 50C2), each slit plate constituting the slit plate group 50D (slit plates 50D1, 50D2) is formed of a flat plate member, and the end faces of the slit plates of the slit plate group 50A and the slit plate group 50B are opposed to each other. In addition, the end faces of the slit plates of the slit plate group 50C and the slit plate group 50D face each other, and an opening region 51 having a rectangular shape in plan view is formed by the end portions of the slit plate groups 50A to 50D. Each slit board group 50A-50D is arrange | positioned.

  In addition, the slit plate of each aperture | diaphragm | squeeze part shown by FIGS. 20-22 is comprised with the material which shields radiation X, such as lead and tungsten, and one slit board group which an edge part opposes is an x direction. A slit that is configured to be movable, and that the other slit plate group is configured to be movable in the y direction, which is a direction orthogonal to the x direction. From the state in which the end portions of the plates are in contact, that is, the state in which the opening region 51 is in a fully closed state to the state in which the opening region 51 has a rectangular shape in plan view and has the maximum area (fully open state). The point set as the range and the point that each slit plate can be moved by the motor are the same as those of the diaphragm unit 44 according to the above embodiment.

  The diaphragm 46 shown in FIG. 20 can achieve substantially the same effect as the diaphragm 44 according to the above embodiment, whereas the diaphragm 48 shown in FIG. Compared with the case where it is configured to be thicker, the diaphragm portion can be configured more easily. Further, in the case of the diaphragm portion 50 shown in FIG. 22, the degree of freedom such as the shape and area of the opening region 51 can be increased. Can be improved.

  In addition, in each aperture | diaphragm | squeeze part shown in FIG. 3, FIG.20-FIG. 22, it is not necessary to comprise all the slit plates so that a movement is possible, and it should just be a form which comprises at least one slit plate so that a movement is possible. . In this case, it goes without saying that the number of motors for moving the slit plate can be reduced.

  Moreover, in each aperture | diaphragm | squeeze part shown in FIG. 3, FIG.20-FIG. 22, although the shape of all the slit plates which comprise the said aperture | diaphragm | squeeze part is made into the same shape, it uses for these aperture | diaphragm | squeeze parts not only in this. It is good also as a form applied combining the slit board currently used. 23, the wedge-shaped slit plates (slit plates 44C and 44D) used in the diaphragm portion 44 and the flat slit plates (slit plates 50A1 and 50B1) used in the diaphragm portion 50 are applied. An example of the case is shown.

  Moreover, in each aperture | diaphragm | squeeze part shown in FIG. 3, FIG. 20-FIG. 23, although two pairs of slit plates or slit plate groups which each face each other are applied, not only this but FIG. 24 as an example As shown, a pair of slit plate 43A and slit plate 43B having an L shape in plan view may be applied in combination. In this case, the shape in the thickness direction (height direction) of each of the slit plates 43A and 43B is, for example, a wedge shape or a step shape as shown in FIGS.

  In this case, at least one of the slit plate 43A and the slit plate 43B is configured to be movable in at least one of the x direction and the y direction, and the movable range of each slit plate is such that the opening region 51 is in a fully closed state. The range from the open state to the state in which the opening region 51 has a rectangular shape in plan view and has a maximum area (fully open state), and the movable slit plate is moved by the motor. The point is the same as the other apertures.

  In this case, the number of slit plates can be reduced as compared with other diaphragm portions, and the cost can be further reduced.

  Moreover, in each aperture | diaphragm | squeeze part shown in FIG. 3, FIG. 20-FIG. 24, although each slit plate is comprised with the single material, not only this but each slit plate is comprised combining different materials. Thus, the configuration may be such that the transmitted dose of the radiation X decreases as the distance from the peripheral edge of the opening region 51 increases.

  As an example of the form in this case, the composition ratio of the element having the radiation shielding ability such as lead, tungsten, molybdenum and the like and the element not having the radiation shielding ability is blended, and the blending ratio is set to the periphery of the opening region 51. The form comprised by changing according to the distance from a part can be illustrated. In this case, the element may be constituted by kneading a single element of an element having radiation shielding ability or a compound thereof into a resin material not having radiation shielding ability. In this case, the moldability is improved and the weight can be reduced, which is preferable.

  Moreover, in the above-mentioned aperture | diaphragm | squeeze part, although the shape of planar view of the edge part which each slit plate opposes is made into a linear form, it is good also as a form which makes the said shape into a curvilinear form.

  In each of the above embodiments, the case where the elapsed period t is applied as a parameter for determining the weight value has been described. However, the present invention is not limited to this, and for example, in addition to the elapsed period t Alternatively, at least one of an exposure dose per unit time, an exposure dose per treatment, and a frame rate at the time of imaging may be applied.

  When applying the exposure amount per unit time, the weight value is set so as to increase as the exposure amount per unit time increases, and when applying the exposure amount per treatment, The weight value is set so as to increase as the exposure amount increases, and when the frame rate at the time of shooting is applied, the weight value is set so as to increase as the frame rate increases. At this time, regardless of which parameter is applied, the maximum value of the weight value is set to “1” so that the exposure amount obtained by multiplying the weight value does not exceed the exposure amount before the multiplication. To do.

  Note that when applying at least one of the exposure amount per unit time, the exposure amount per treatment, and the frame rate at the time of imaging as a parameter for determining the weight value, the value of the parameter to be applied is determined. Since the weight value can be determined at this time, the determined weight value may be stored in the exposure history information. In this case, weight value management information becomes unnecessary.

  Moreover, although the said embodiment demonstrated the case where an exposure area | region, an exposure amount, and an exposure period were memorize | stored for every frame of a radiographic image, this invention is not limited to this, These information is stored. It is good also as a form memorize | stored for every some flame | frame, and it is good also as a form memorize | stored for every treatment.

  Further, in each of the above embodiments, alignment with the position of the corresponding rectangular region 64 at the time of past imaging of the patient 14 is performed with a predetermined reference portion (the top of the head in each of the above embodiments). However, the case where the patient 14 is laid on the mounting table 16A so as to be positioned at a reference position predetermined for each patient on the mounting table 16A has been described, but the present invention is limited to this. For example, as disclosed in Japanese Patent Application Laid-Open No. 2008-206962, the above-described alignment may be automatically performed based on anatomical features in a radiographic image obtained by imaging. . In this case, since it is possible to cope with a change in the body shape of the patient 14 with time, alignment can be performed with higher accuracy than in the above embodiments.

  Further, a marker that is made of a material that can be captured as a radiographic image and has a shape that can be identified by a conventionally known image recognition technique is determined in advance as a position where a radiographic image can be captured in the patient 14 before the operation. The position of the marker is specified by the image recognition technique at the time of radiographic image capturing, and coordinate information indicating the specified position is set for each frame of the radiographic image, for each frame, While being stored in the exposure dose history information for each treatment or the like, the above-mentioned alignment may be performed with the coordinate information indicating the same reference position. In this case, instead of the marker, another member or the like applicable as the reference position such as the reflective photosensor 62 may be applied.

  Further, in each of the above embodiments, the case where the present invention is applied to the treatment in which the catheter 60 is inserted into the body from the neck of the patient 14 has been described. However, the present invention is not limited to this. It goes without saying that the present invention may be applied to a treatment in which the catheter 60 is inserted into the body from other parts such as the base of the thigh or the armpit.

  Although not particularly mentioned in each of the above-described embodiments, in these embodiments, the exposure dose during treatment is continuously stored in the exposure dose history information in time series. Because it is possible to grasp a part that has been exposed to a large amount of exposure compared to other parts in the past, the part is considered to be more damaged by exposure than other parts. It is good also as a form etc. which control the aperture | diaphragm | squeeze part 44 so that the exposure amount of a radiation may be suppressed from the site | part. For example, a total value of the exposure dose in a predetermined period (for example, the latest three months) for each region of the patient to be imaged is obtained from the exposure history information, and the exposure dose is near the region to be imaged this time. When there is a region where the exposure dose exceeds a predetermined allowable threshold value, the radiation X is not irradiated to the region exceeding the threshold value, and the radiation X transmitted through the slit plates 48A to 48D is not irradiated. The diaphragm unit 44 may be controlled so as to be irradiated. As a result, it is possible to suppress further exposure of a part that has already been exposed to a large amount even in pre-imaging. This control may be performed in the main photographing such as IVR. Further, it may be performed in advance shooting in order to perform positioning before performing actual shooting such as IVR.

  Further, in each of the above embodiments, the case of storing all of the time point information, surgical exposure dose information, and frame rate information of the present invention has been described, but the present invention is not limited to this, and any of these One or a combination of the two may be stored.

  Moreover, although the said embodiment demonstrated the case where the aperture | diaphragm | squeeze part 44 restrict | limits the irradiation area | region of the direct line | wire of the radiation X to a region of interest, this invention is not limited to this. For example, female gonads and fetuses are susceptible to radiation and are vulnerable to exposure. In addition, a medical device used integrally with a human body, such as a pacemaker, uses a semiconductor, and it is preferable to suppress exposure because the specification deteriorates due to irradiation of radiation. Therefore, the irradiation apparatus control unit 140 acquires information on a region where exposure should be suppressed, such as a region susceptible to radiation, such as a female gonad or fetus, or a region embedded with a medical device used integrally with the human body. However, the diaphragm unit 44 may be controlled so that the radiation that has passed through the diaphragm unit 44 is irradiated to the region where exposure is to be suppressed. Information related to the area where exposure should be suppressed may be input from the operation panel 112, may be transferred from an external device via a network, or may be various types such as pattern matching from a captured radiographic image. It may be specified by image processing.

  In each of the above embodiments, the CPU 114 of the console 26 has been described with reference to an example in which the radiographic image capturing process and the position specifying process are performed. However, the present invention is not limited to this, for example, The irradiation device control unit 140 of the radiation irradiation device 18 or the cassette control unit 100 of the electronic cassette 20 may execute these processes.

  In addition, it is needless to say that the configuration (see FIGS. 1 to 6) of the imaging system 10 described in the above embodiments is an example, and can be changed without departing from the gist of the present invention.

  Further, the flow of the radiographic image capturing processing program (see FIGS. 14 and 19) and the position specifying processing program described in each of the above embodiments is also an example, and is unnecessary within the scope of the present invention. It goes without saying that steps can be deleted, new steps can be added, and the processing order can be changed.

  The data structure of various information described in the above embodiments (see FIGS. 7 to 9) is also an example, and unnecessary data is deleted or new data is used without departing from the gist of the present invention. Needless to say, you may add.

  Further, in each of the above-described embodiments, the catheter 60 in the IVR is described as an example as a surgical instrument and a medical instrument to be inserted into the body of the patient 14, but other surgical procedures and medical instruments (guidewire, fracture in the IVR) are described. Needless to say, the present invention can also be applied to screws, plates, intramedullary nails, etc. in treatment.

DESCRIPTION OF SYMBOLS 10 Radiographic imaging system 14 Patient 18 Radiation irradiation apparatus 20 Electronic cassette 22 Support member 26 Console 28 Display 28A Display surface 36 Radiation detector 36A Irradiation surface 42 Radiation sources 43, 44, 44 ', 46, 48, 50 44D Slit plates 46A-46D Slit plates 48A-48D Slit plates 50A-50D Slit plate group 51 Opening region 60 Catheter 114 CPU
120 HDD
146, 148, 150, 152 Motor

Claims (9)

A calculating means for calculating the exposure amount per unit time of the radiation irradiated to the subject from the radiation source for moving image capturing of the radiation image for each of the divided areas defined as a predetermined unit area; ,
Storage means for storing the exposure dose information indicating the exposure dose calculated by the calculation means in association with the corresponding segment area specifying information for specifying the corresponding segment area and the subject specifying information for specifying the subject;
Radiation imaging management device. At least one of time point information indicating the time point at which the subject is irradiated with the radiation, operation dose information indicating an exposure amount per one operation of the radiation, and frame rate information indicating a frame rate of the moving image photographing. It further comprises an acquisition means for acquiring,
The storage means further stores at least one of the time point information, the surgical exposure dose information, and the frame rate information acquired by the acquisition means in association with the corresponding subject specifying information. The radiation imaging management apparatus described. The exposure information is provided between the radiation source and the subject, and has an aperture region configured to allow a part of the radiation emitted from the radiation source to pass through and to change the area. The radiation imaging management apparatus according to claim 1, wherein the radiation exposure management apparatus indicates an exposure dose of radiation that reaches the subject in a state of being squeezed by a unit. The radiation imaging management apparatus according to any one of claims 1 to 3,
A radiographic imaging apparatus for capturing a moving image of a radiographic image emitted by a radiation source that emits radiation to be managed by the radiation imaging management apparatus and transmitted through the subject; and
Including radiographic imaging system. A radiographic imaging apparatus is configured by laminating a phosphor layer that generates light when irradiated with radiation, and a substrate on which a photoelectric conversion element that converts light generated in the phosphor layer into charges is formed. The radiographic image capturing system according to claim 4, further comprising: a radiation detector of an indirect conversion type, wherein moving image capturing is performed by the radiation detector. The radiographic imaging system according to claim 5, wherein the phosphor is CsI. The radiographic image capturing system according to claim 5, wherein the radiation detector is disposed in the radiographic image capturing unit so that radiation enters from the substrate side. The radiation imaging management apparatus according to any one of claims 1 to 3,
A radiation source for emitting radiation to be managed by the radiation imaging management device;
Including radiographic imaging system. The radiation imaging management apparatus according to any one of claims 1 to 3,
A radiographic imaging apparatus for capturing a moving image of a radiographic image emitted by a radiation source that emits radiation to be managed by the radiation imaging management apparatus and transmitted through the subject; and
The radiation source;
Including radiographic imaging system.