WO2013042514A1 - Appareil de radioscopie, procédé de détermination d'une région d'intérêt pour appareil de radioscopie, système de radiographie, et programme de contrôle de radioscopie - Google Patents

Appareil de radioscopie, procédé de détermination d'une région d'intérêt pour appareil de radioscopie, système de radiographie, et programme de contrôle de radioscopie Download PDF

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Publication number
WO2013042514A1
WO2013042514A1 PCT/JP2012/071895 JP2012071895W WO2013042514A1 WO 2013042514 A1 WO2013042514 A1 WO 2013042514A1 JP 2012071895 W JP2012071895 W JP 2012071895W WO 2013042514 A1 WO2013042514 A1 WO 2013042514A1
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Prior art keywords
radiation
exposure
region
moving image
interest
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PCT/JP2012/071895
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English (en)
Japanese (ja)
Inventor
西納　直行
北野　浩一
岩切　直人
大田　恭義
中津川　晴康
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富士フイルム株式会社
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Publication of WO2013042514A1 publication Critical patent/WO2013042514A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/46—Arrangements for interfacing with the operator or the patient
    • A61B6/467—Arrangements for interfacing with the operator or the patient characterised by special input means
    • A61B6/469—Arrangements for interfacing with the operator or the patient characterised by special input means for selecting a region of interest [ROI]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/48—Diagnostic techniques
    • A61B6/486—Diagnostic techniques involving generating temporal series of image data
    • A61B6/487—Diagnostic techniques involving generating temporal series of image data involving fluoroscopy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • A61B6/542—Control of apparatus or devices for radiation diagnosis involving control of exposure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
    • A61B6/4464—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit or the detector unit being mounted to ceiling

Definitions

  • the present invention generates a moving image of a subject by continuously radiating radiation toward the subject and continuously capturing still images obtained by receiving a radiation amount passing through the subject with a radiation detector.
  • the present invention relates to a radiation moving image capturing apparatus, a region of interest setting method for a radiation moving image capturing apparatus, a radiation image capturing system, and a radiation moving image capturing control program.
  • radiation detectors such as FPD (Flat Panel Detector) that can arrange radiation sensitive layers on TFT (Thin Film Transistor) active matrix substrates and convert radiation dose into digital data (electrical signals) (referred to as “electronic cassettes”)
  • FPD Fluor Deposition Detector
  • TFT Thin Film Transistor
  • electrospray cassettes a radiation image capturing apparatus that captures a radiation image represented by the amount of radiation that has been exposed using this radiation detector has been put into practical use.
  • the radiation dose is, for example, interchangeably converted into a light emission amount and then converted into an electric signal, and then a direct conversion method in which the radiation dose is directly converted into an electric signal, and is selected as appropriate. Adopted.
  • the radiographic imaging apparatus As described above, it is considered to display a so-called moving image by continuously reproducing image information detected by a radiation detector at regular intervals. Note that the shorter the time interval, the better the continuity and the better the image quality as a moving image. However, the amount of image information is increased by using a general CCD or CMOS. It is the same as an imaging device (image sensor). In the radiographic image capturing apparatus, if the number of image frames to be captured increases, the radiation dose to the subject increases. Therefore, it is preferable to select an appropriate number of image frames.
  • the “appropriate number of image frames” refers to whether the movement of the imaging target (image in the region of interest (ROI) in the subject) is fast or slow, whether or not the change amount of the movement is important, etc. This is the number of image frames decided according to the purpose.
  • Japanese Patent Laid-Open No. 2010-273434 discloses an X-ray diagnostic imaging apparatus that displays a fluoroscopic image of a contrasted blood vessel and a DA (Digital Angiography) image.
  • Japanese Patent Laid-Open No. 9-266901 discloses an image processing condition setting device for radiographic images.
  • Japanese Patent Application Laid-Open No. 2010-27383 discloses an X-ray diagnostic imaging apparatus that performs ABC control based on an image level in a region of interest by appropriately canceling ABC control according to a user operation, and the X-ray condition at that time A technique that can fix the above is disclosed.
  • the radiation dose emitted from the radiation generating device may be reduced.
  • the ABC control is executed before the region of interest is determined.
  • the radiation dose may be controlled to increase in spite of the so-called pre-photographing image.
  • Patent Document 1 cancels ABC control according to a user operation, and there is no causal relationship between ABC control and a region of interest.
  • Japanese Patent Laid-Open No. 2009-101208 does not perform ABC control, but performs normal shooting at the time of the first exposure for setting a region of interest. After setting the region of interest, a technique for controlling the collimator so that only the region of interest is exposed to radiation is disclosed.
  • the present invention mainly provides a moving image radiographing apparatus and a radiographic moving image capable of reducing the radiation exposure dose to a subject without adversely affecting the identification of a region of interest when capturing a moving image. It is an object to obtain a region-of-interest setting method for an image capturing apparatus, a radiation image capturing system, and a radiation moving image capturing control program.
  • a plurality of pixels are used to determine the amount of radiation that has been emitted from radiation exposure means that exposes radiation of radiation energy in a set steady range toward a subject and has passed through the subject.
  • a radiation image capturing unit that receives a radiation signal in accordance with the amount of radiation received for each pixel received by the radiation detector provided, and obtains the gradation signal from the radiation image capturing unit, and has a predetermined dynamic range.
  • Reading the gradation signal Reading the gradation signal, generating still image information for each frame, and moving image information generating means for generating a moving image of the subject by continuously capturing the still images;
  • Control means for feedback controlling the set value of the radiation energy of the radiation to be emitted from the radiation exposure means at a predetermined control cycle, instructing prohibition of feedback control by the control means, and instructing the radiation exposure means Then, pre-exposure for a still image is performed, and a gradation signal corresponding to a still image for at least one frame based on the pre-exposure is acquired from the radiation image capturing unit, and generated from the gradation signal.
  • a region of interest setting means for setting a partial region of the still image as a region of interest.
  • the radiation amount irradiated from the radiation exposure means and passed through the subject is received by a radiation detector having a plurality of pixels, and a gradation signal corresponding to the radiation amount received for each pixel Is output.
  • the moving image information generating means acquires the gradation signal from the radiation image photographing means, reads the gradation signal under a predetermined steady dynamic range, and generates still image information for each frame. Then, a moving image of the subject is generated by continuously capturing still images.
  • control means feedback-controls the set value of the radiation energy of the radiation exposed from the radiation exposure means at a predetermined control cycle.
  • the region of interest setting means sets the region of interest from the moving images to be photographed.
  • the region-of-interest setting unit prohibits feedback control by the control unit and captures a still image by pre-exposure prior to moving image capturing. Based on this still image, a part of the image is set as a region of interest.
  • the subject is exposed only during still image shooting, and the exposure dose of the subject is suppressed from the normal range. can do. Moreover, the state which was suppressed can be maintained by prohibiting feedback control.
  • the prohibition of feedback control by the control means is canceled and the generation of the moving image is started.
  • the exposure dose due to still image shooting during the pre-exposure by the radiation exposure means is suppressed to be less than the exposure dose during generation of a still image for one frame during shooting of the moving image.
  • the still image by pre-exposure is applied only to setting the region of interest, for example, an image having high image quality (high-quality still image) enough to accurately observe the affected area of the subject is unnecessary.
  • the amount of exposure can be suppressed by the difference in application purpose.
  • the suppression of the exposure dose is to make the radiation energy instructed to the radiation exposure means lower than a steady range.
  • the exposure dose to the subject can be reduced by making the radiation energy of the radiation source itself lower than the steady range.
  • the rate of change of the image information with respect to the gradation signal which is a parameter of compression of the dynamic range is being feedback controlled. Adjust to make it larger.
  • the radiation energy instructed to the radiation exposure means is set lower than the steady range, the radiation amount itself detected for each pixel decreases, and a gradation signal may not be obtained properly.
  • the dynamic range compression parameter is made larger than the dynamic range compression parameter during feedback control.
  • the dynamic range compression parameter is the rate of change of the image information with respect to the gradation signal.
  • the radiation dose received by the radiation detector is small because the radiation energy is low, and the gradation signal tends to be biased toward the low level. Tonal change (density change) is low.
  • Appropriate image information can be obtained from a so-called underimage by increasing the dynamic range compression parameter, that is, the rate of change of the image information with respect to the gradation signal, in accordance with this biased region.
  • the range of the still image applied when the region of interest is set by the region of interest setting means is wider than the range of the moving image captured after the region of interest is set.
  • the range of the still image that is the target of the region of interest is made wider than the range of moving images that are captured after the region of interest is set. As a result, it is possible to prevent the region of interest from being overlooked or misidentified.
  • the target of feedback control by the control means is an image in the region of interest set by the region of interest setting means.
  • the radiation dose can be adjusted separately inside and outside the region of interest, feedback correction is performed so that appropriate radiation energy is obtained within the region of interest, and the radiation dose is reduced outside the region of interest, thereby exposing the subject.
  • the amount of radiation emitted can be reduced.
  • the exposure surface of the radiation exposure means is partitioned and controlled independently, or between the radiation exposure means and the subject.
  • means such as arranging an aperture can be considered, and in the case of a moving image, the movement of the region of interest may be followed.
  • pre-exposure for a still image is performed toward a subject prior to moving image capturing by continuous exposure of radiation energy, and based on radiation energy passing through the subject by the pre-exposure.
  • the second aspect of the invention for example, as a normal moving image capturing procedure, radiation of radiation energy in a set steady range is exposed toward the subject and the amount of radiation that has passed through the subject. A corresponding gradation signal is read under a predetermined dynamic range to generate still image information for each frame, and a moving image of the subject is generated by continuously capturing still images.
  • the set value of the radiation energy of the radiation to be exposed is feedback-controlled at a predetermined control cycle.
  • the region of interest is set from the moving images to be shot.
  • feedback control is prohibited and a part of the image is set as the region of interest while the exposure dose of the subject is suppressed from the steady range.
  • the subject is exposed only during still image shooting, and the exposure dose of the subject is suppressed from the normal range. can do. Moreover, the state which was suppressed can be maintained by prohibiting feedback control.
  • the radiation energy of the radiation at the time of the pre-exposure is set lower than that at the time of moving image shooting.
  • the radiation dose to the subject can be reduced by making the radiation energy of the radiation source itself lower than the steady range.
  • the compression ratio of the dynamic range is adjusted so that the change amount of the gradation signal with respect to the radiation energy is increased by the amount that the radiation energy is set low.
  • the amount of radiation detected for each pixel decreases, and a gradation signal may not be obtained properly.
  • the dynamic range compression parameter is made larger than the dynamic range compression parameter during feedback control.
  • the dynamic range compression parameter is the rate of change of the image information with respect to the gradation signal.
  • the radiation dose received by the radiation detector is small because the radiation energy is low, and the gradation signal tends to be biased toward the low level. Tonal change (density change) is low.
  • Appropriate image information can be obtained from a so-called underimage by increasing the dynamic range compression parameter, that is, the rate of change of the image information with respect to the gradation signal, in accordance with this biased region.
  • the radiological moving image capturing apparatus according to any one of the first to sixth aspects of the present invention, a terminal apparatus that inputs and browses diagnostic information and facility reservations, and requests radiographic image capturing and reservations.
  • a radiographic imaging system comprising: a server that accepts an imaging request from the terminal device, manages a radiographic imaging schedule in the radiographic video imaging device, and collectively manages radiographic images taken.
  • the third aspect of the invention can be applied as a system for managing information such as medical appointment reservations and diagnostic records, particularly in a radiology department in a hospital, and can be a part of a hospital information system.
  • the radiation energy suppression rate at the time of setting the region of interest is determined for each subject. Can be adjusted.
  • a fourth aspect of the present invention is a radiation moving image photographing control that causes a computer to function as moving image information generating means, control means, and region of interest setting means of any one of the first to sixth inventions. It is a program. Note that the radiation moving image capturing control program can be stored in a storage medium.
  • the present invention has an excellent effect that the radiation exposure dose to the subject can be reduced without adversely affecting the identification of the region of interest.
  • FIG. 10 (2) is in FIG. 11 (1). It is a histogram of the QL value when the dynamic range is compressed.
  • FIG. 6 is a characteristic diagram showing a radiation moving image photographing process-radiation exposure dose cumulative value characteristic curve. It is the block diagram which showed the flow of imaging
  • FIG. 1 is a schematic configuration diagram of a radiation information system (hereinafter referred to as “RIS” (Radiology Information System)) 10 according to the present embodiment.
  • the RIS 10 can capture a moving image in addition to a still image.
  • the definition of a moving image means that still images are displayed one after another at a high speed and recognized as a moving image.
  • the still image is photographed, converted into an electric signal, transmitted, and the still image is converted from the electric signal.
  • the process of replaying is repeated at high speed. Accordingly, the so-called “frame advance” in which the same area (part or all) is photographed a plurality of times within a predetermined time and continuously reproduced in accordance with the degree of the “high speed” is also included in the moving image.
  • frame advance in which the same area (part or all) is photographed a plurality of times within a predetermined time and continuously reproduced in accordance with the degree of the “high speed” is also included in the moving image.
  • the RIS 10 is a system for managing information such as medical appointments and diagnosis records in the radiology department, and constitutes a part of a hospital information system (hereinafter referred to as “HIS” (Hospital Information System)).
  • HIS Hospital Information System
  • the RIS 10 includes a plurality of radiographic imaging systems installed individually in a plurality of imaging request terminal devices (hereinafter referred to as “terminal devices”) 12, a RIS server 14, and a radiographic room (or operating room) in a hospital.
  • terminal devices hereinafter referred to as “terminal devices”
  • RIS server a radiographic room (or operating room) in a hospital.
  • imaging system which are connected to an in-hospital network 18 composed of a wired or wireless LAN (Local Area Network) or the like.
  • the hospital network 18 is connected to an HIS server (not shown) that manages the entire HIS.
  • the radiographic image capturing system 16 may be a single unit or three or more facilities. In FIG. 1, the radiographic image capturing system 16 is installed for each radiographing room. An imaging system 16 may be arranged.
  • the terminal device 12 is used by doctors and radiographers to input and view diagnostic information and facility reservations, and radiographic image capturing requests and imaging reservations are performed via the terminal device 12.
  • Each terminal device 12 includes a personal computer having a display device, and is capable of mutual communication via the RIS server 14 and the hospital network 18.
  • the RIS server 14 receives an imaging request from each terminal device 12 and manages a radiographic imaging schedule in the imaging system 16, and includes a database 14A.
  • the database 14A includes attribute information (name, sex, date of birth, age, blood type, weight, patient ID (Identification), etc.), medical history, Medical history, information about the patient such as radiation images taken in the past, identification number (ID information) of the electronic cassette 20 (model information) used in the imaging system 16, model, size, sensitivity, start date of use, number of uses, etc.
  • ID information information about the electronic cassette 20 and environmental information indicating an environment in which a radiographic image is taken using the electronic cassette 20, that is, an environment in which the electronic cassette 20 is used (for example, a radiographic room or an operating room).
  • medical-related data managed by medical institutions is stored almost permanently, and when necessary, a system (sometimes referred to as a “medical cloud”) that instantly retrieves data from the required location can be used outside the hospital. You may make it acquire the past personal information etc. of a patient (subject) from a server.
  • a system sometimes referred to as a “medical cloud”
  • the imaging system 16 captures a radiographic image by an operation of a doctor or a radiographer according to an instruction from the RIS server 14.
  • the imaging system 16 exposes the subject to the radiation X having a dose according to the exposure conditions from the radiation exposure source 22A that exposes the radiation X under the control of the radiation exposure control unit 22 (see FIG. 4).
  • a radiation generating device 24 that emits radiation
  • a radiation detector 26 that generates radiation by absorbing the radiation X transmitted through the imaging target region of the subject and generates image information indicating a radiation image based on the amount of the generated charge ( 3), a cradle 28 for charging a battery built in the electronic cassette 20, and a console 30 for controlling the electronic cassette 20 and the radiation generator 24.
  • the console 30 acquires various types of information included in the database 14A from the RIS server 14 and stores them in an HDD 88 (see FIG. 4) described later. If necessary, the console 30 uses the information to store the electronic cassette 20 and the radiation generator 24. Take control.
  • FIG. 2 shows an example of the arrangement state of each device in the radiation imaging room 32 of the imaging system 16 according to the present embodiment.
  • the radiation imaging room 32 there are a standing table 34 used when performing radiography in a standing position and a prone table 36 used when performing radiation imaging in a lying position.
  • the space in front of the standing table 34 is set as the imaging position of the subject 38 when performing radiography in the standing position, and the upper space of the prone table 36 is used in performing radiography in the prone position. This is the imaging position of the subject 40.
  • the standing table 34 is provided with a holding unit 42 that holds the electronic cassette 20, and the electronic cassette 20 is held by the holding unit 42 when a radiographic image is taken in the standing position.
  • a holding unit 44 that holds the electronic cassette 20 is provided in the lying position table 36, and the electronic cassette 20 is held by the holding unit 44 when a radiographic image is taken in the lying position.
  • the radiation exposure source 22A is installed in a horizontal position in order to enable radiography in the standing position and in the prone position by the radiation from the single radiation exposure source 22A.
  • Support movement that can rotate around the axis (in the direction of arrow A in FIG. 2), move in the vertical direction (in the direction of arrow B in FIG. 2), and further move in the horizontal direction (in the direction of arrow C in FIG. 2).
  • a mechanism 46 is provided.
  • the drive source that moves (including rotation) in the directions of arrows A to C in FIG. 2 is built in the support moving mechanism 46, and is not shown here.
  • the cradle 28 is formed with an accommodating portion 28A capable of accommodating the electronic cassette 20.
  • the built-in battery is charged in a state of being accommodated in the accommodating portion 28A of the cradle 28.
  • the electronic cassette 20 is taken out of the cradle 28 by a radiographer or the like, and the photographing posture is established. If it is in the upright position, it is held in the holding part 42 of the standing table 34, and if it is in the upright position, it is held in the holding part 44 of the standing table 36.
  • various kinds of information are transmitted by wireless communication between the radiation generator 24 and the console 30 and between the electronic cassette 20 and the console 30. Send and receive (details will be described later).
  • the electronic cassette 20 is not used only in the state of being held by the holding portion 42 of the standing base 34 or the holding portion 44 of the prone position base 36. When photographing, it can be used in a state where it is not held by the holding unit.
  • FIG. 3 is a schematic cross-sectional view schematically showing the configuration of the three pixel portions of the radiation detector 26 provided in the electronic cassette 20.
  • the radiation detector 26 includes a signal output unit 52, a sensor unit 54 (TFT substrate 74), and a scintillator 56 that are sequentially stacked on an insulating substrate 50.
  • the sensor unit 54 is provided with a pixel group of the TFT substrate 74. That is, the plurality of pixel groups are arranged in a matrix on the substrate 50, and the signal output unit 52 and the sensor unit 54 in each pixel are configured to overlap each other.
  • An insulating film 53 is interposed between the signal output unit 52 and the sensor unit 54.
  • the scintillator 56 is formed on the sensor unit 54 via a transparent insulating film 58, and forms a phosphor that emits light by converting radiation incident from above (opposite side of the substrate 50) or below into light. It is what. Providing such a scintillator 56 absorbs radiation transmitted through the subject and emits light.
  • the wavelength range of light emitted by the scintillator 56 is preferably in the visible light range (wavelength 360 nm to 830 nm), and in order to enable monochrome imaging by the radiation detector 26, the wavelength range of green is included. Is more preferable.
  • the phosphor used in the scintillator 56 preferably contains cesium iodide (CsI) when imaging using X-rays as radiation, and has an emission spectrum of 400 nm to 700 nm upon X-ray exposure. It is particularly preferred to use some CsI (Tl) (cesium iodide with thallium added). Note that the emission peak wavelength of CsI (Tl) in the visible light region is 565 nm.
  • CsI cesium iodide
  • the sensor unit 54 includes an upper electrode 60, a lower electrode 62, and a photoelectric conversion film 64 disposed between the upper and lower electrodes.
  • the photoelectric conversion film 64 absorbs light emitted from the scintillator 56 and generates electric charges. It is composed of an organic photoelectric conversion material.
  • the upper electrode 60 Since it is necessary for the upper electrode 60 to cause the light generated by the scintillator 56 to enter the photoelectric conversion film 64, it is preferable that the upper electrode 60 be made of a conductive material that is transparent at least with respect to the emission wavelength of the scintillator 56. It is preferable to use a transparent conductive oxide (TCO “Transparent Conductive Oxide”) having a high transmittance for visible light and a small resistance value. Although a metal thin film such as Au can be used as the upper electrode 60, the TCO is preferable because it tends to increase the resistance when it is desired to obtain a transmittance of 90% or more.
  • TCO Transparent Conductive Oxide
  • the upper electrode 60 may have a single configuration common to all pixels, or may be divided for each pixel.
  • the photoelectric conversion film 64 includes an organic photoelectric conversion material, absorbs light emitted from the scintillator 56, and generates electric charge according to the absorbed light.
  • the photoelectric conversion film 64 including the organic photoelectric conversion material has a sharp absorption spectrum in the visible region, and electromagnetic waves other than light emitted by the scintillator 56 are hardly absorbed by the photoelectric conversion film 64, and X-rays are obtained.
  • the noise generated by the radiation such as being absorbed by the photoelectric conversion film 64 can be effectively suppressed.
  • the organic photoelectric conversion material constituting the photoelectric conversion film 64 is preferably such that its absorption peak wavelength is closer to the emission peak wavelength of the scintillator 56 in order to absorb light emitted by the scintillator 56 most efficiently.
  • the absorption peak wavelength of the organic photoelectric conversion material matches the emission peak wavelength of the scintillator 56, but if the difference between the two is small, the light emitted from the scintillator 56 can be sufficiently absorbed.
  • 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 56 is preferably within 10 nm, and more preferably within 5 nm.
  • Examples of the organic photoelectric conversion material that can satisfy such conditions include quinacridone organic compounds and phthalocyanine organic compounds.
  • quinacridone organic compounds since the absorption peak wavelength in the visible region of quinacridone is 560 nm, if quinacridone is used as the organic photoelectric conversion material and CsI (Tl) is used as the material of the scintillator 56, the difference in peak wavelength can be made within 5 nm. Thus, the amount of charge generated in the photoelectric conversion film 64 can be substantially maximized.
  • the sensor unit 54 constituting each pixel only needs to include at least the lower electrode 62, the photoelectric conversion film 64, and the upper electrode 60.
  • the electron blocking film 66 and the hole blocking film are used. It is preferable to provide at least one of 68, and it is more preferable to provide both.
  • the electron blocking film 66 can be provided between the lower electrode 62 and the photoelectric conversion film 64.
  • a bias voltage is applied between the lower electrode 62 and the upper electrode 60, electrons are transferred from the lower electrode 62 to the photoelectric conversion film 64. 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 66.
  • the hole blocking film 68 can be provided between the photoelectric conversion film 64 and the upper electrode 60. When a bias voltage is applied between the lower electrode 62 and the upper electrode 60, the hole blocking film 68 is transferred from the upper electrode 60 to the photoelectric conversion film 64. 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 68.
  • the signal output unit 52 corresponds to the lower electrode 62, a capacitor 70 that accumulates the electric charge transferred to the lower electrode 62, and a field effect thin film transistor (Thin) that converts the electric charge accumulated in the capacitor 70 into an electric signal and outputs it.
  • Film-Transistor (hereinafter sometimes simply referred to as a thin film transistor) 72 is formed.
  • the region in which the capacitor 70 and the thin film transistor 72 are formed has a portion that overlaps the lower electrode 62 in plan view. With this configuration, the signal output unit 52 and the sensor unit 54 in each pixel are thick. There will be overlap in the vertical direction. In order to minimize the plane area of the radiation detector 26 (pixel), it is desirable that the region where the capacitor 70 and the thin film transistor 72 are formed is completely covered with the lower electrode 62.
  • FIG. 4 is a control block diagram of the imaging system 16 according to the present embodiment.
  • the console 30 functions as a server computer, and includes a display 80 for displaying an operation menu, a captured radiographic image, and the like, and an operation panel 82 for inputting various information and operation instructions. I have.
  • the console 30 includes a CPU 84 that controls the operation of the entire apparatus, a ROM 86 that stores various programs including a control program in advance, a RAM 87 that temporarily stores various data, and various data.
  • An HDD (Hard Disk Drive) 88 that stores and holds, a display driver 92 that controls display of various types of information on the display 80, and an operation input detector 90 that detects an operation state of the operation panel 82 are provided. .
  • the console 30 transmits and receives various information such as an exposure condition described later between the image processing device 23 and the radiation generation device 24 by wireless communication, and various types of image data and the like with the electronic cassette 20.
  • An I / F (for example, a wireless communication unit) 96 and an I / O 94 that transmit and receive information are provided.
  • the image processing device 23 may be included in the console 30.
  • the CPU 84, ROM 86, RAM 87, HDD 88, display driver 92, operation input detection unit 90, I / O 94, and wireless communication unit 96 are connected to each other via a bus 98 such as a system bus bus or a control bus. Therefore, the CPU 84 can access the ROM 86, RAM 87, and HDD 88, controls display of various information on the display 80 via the display driver 92, and the radiation generator 24 via the wireless communication unit 96. Control of transmission and reception of various types of information with the electronic cassette 20 can be performed. Further, the CPU 84 can grasp the operation state of the user with respect to the operation panel 82 via the operation input detection unit 90.
  • the image processing apparatus 23 includes an I / F (for example, a wireless communication unit) 100 that transmits and receives various types of information such as an exposure condition to and from the console 30, and the electronic cassette 20 and the radiation generation apparatus based on the exposure condition. 24, an image processing control unit 102 for controlling 24.
  • the radiation generator 24 includes a radiation exposure control unit 22 that controls radiation exposure from the radiation exposure source 22A.
  • the image processing control unit 102 includes a system control unit 104, a panel control unit 106, and an image processing control unit 108, and exchanges information with each other via a bus 110.
  • the panel control unit 106 receives information from the electronic cassette 20 wirelessly or by wire, and the image processing control unit 108 performs image processing.
  • the system control unit 104 receives information such as a tube voltage and a tube current as an exposure condition from the console 30 and, based on the received exposure condition, the radiation X from the radiation exposure source 22A of the radiation exposure control unit 22. Control to expose.
  • the imaging system 16 in the present embodiment has a function of automatically setting a region of interest.
  • control for setting the region of interest after radiographic imaging preparation control is performed. Is to be executed.
  • appropriate image information is obtained by performing feedback correction on the radiation dose of radiation exposed to the subject by ABC “Auto Brightness Control” control.
  • the principle of ABC control is that radiation exposure is performed so that the average value of one frame of the QL value generated based on the gradation signal received from the electronic cassette 20 converges to a predetermined threshold value (reference value). This is for adjusting the amount of radiation exposed from the radiation source 22A, for example, the same as the light amount adjustment by a digital camera or a movie camera.
  • the completion of the ROI setting is before the so-called main imaging, and particularly in the case of moving image shooting, it is preferable to suppress the radiation exposure dose to the subject until the ROI is determined after the ROI has been set.
  • FIG. 5 is a block diagram specialized in a control system for radiographic image capturing (including ROI setting) in the imaging system 16 (mainly the console 16, the image processing device 23, and the radiation generating device 24). Note that this block diagram categorizes radiographic image capturing control by function, and does not limit the hardware configuration. Therefore, the respective functional blocks may be distributed to the console 16, the image processing device 23, and the radiation generation device 24.
  • the radiation exposure control unit 22 exposes radiation from the radiation exposure source 22A based on the radiation dose adjusted by the radiation dose adjustment unit 120.
  • the radiation dose adjustment unit 120 adjusts the output radiation dose (energy), and details will be described later.
  • the radiation exposed from the radiation exposure source 22A passes through the subject 40 lying on the prone position table 36 and reaches the radiation detector 26 (see FIG. 3) of the electronic cassette 20.
  • the radiation detector 26 the phosphor film 56 (see FIG. 3) emits light having a light amount corresponding to the radiation amount and is photoelectrically converted by the TFT substrate 74.
  • the TFT substrate 74 of the electronic cassette 20 is connected to the signal acquisition unit 122.
  • the signal acquisition unit 122 acquires a signal photoelectrically converted based on the radiation exposed from the radiation exposure source 22 ⁇ / b> A and sends it to the gradation signal analysis unit 124.
  • the photoelectric conversion signal may be an analog signal or may be converted into a digital signal by the control unit in the electronic cassette 20.
  • a dynamic range adjustment unit 126 is connected to the gradation signal analysis unit 124.
  • the gradation signal analysis unit 124 based on the dynamic range compression parameter received from the dynamic range adjustment unit 126 (hereinafter referred to as "compression rate", the compression rate DRN in the normal state), the photoelectric conversion signal. Histogram analysis is performed. As a result, for example, as shown in FIG. 10A, a data count number (gradation signal) for each gradation (density) is obtained.
  • This gradation signal may be referred to as a QL value.
  • the QL value is the gradation signal itself (raw data), it is not the gradation signal itself, but, for example, the capacitor 70 (see FIG. 3) of the electronic cassette 20 or other circuit system capacitance. A value after correcting the noise component may be used as the QL value.
  • the gradation signal analysis unit 124 is connected to the purpose-specific still image generation instruction unit 125. In the gradation signal analysis unit 124, when the gradation signals for one frame have been prepared, the gradation signal analysis unit 124 sends them to the still image generation unit 128 via the purpose-specific still image generation instruction unit 125.
  • the purpose-specific still image generation instruction unit 125 determines whether it is generation of a still image for ROI setting or generation of a still image that is a basis for generating a moving image, and either instruction signal is stopped. The image is sent to the image generation unit 128. That is, the purpose-specific still image generation instruction unit 125 receives a ROI setting start signal or completion signal from a region-of-interest setting unit 138 described later. When the start signal is received, the still image generation unit 128 is instructed to generate a ROI setting still image. On the other hand, when the completion signal is received, the still image generation unit 128 is instructed to generate a still image for moving image editing.
  • the still image generation unit 128 generates a still image based on the gradation signals of the entire captured region in the case of ROI setting, and in the region of the set ROI (or in the ROI in the case of moving image editing). A still image is generated based on the gradation signal (including a part of the periphery in the region).
  • the still image generation unit 128 generates image data for each frame based on the received gradation signal.
  • the still image for moving image editing and the still image shooting for ROI setting differ in the photoelectric conversion signal itself sent from the electronic cassette 20, for example, as in this embodiment, the moving image editing
  • a binning process may be performed to give priority to the transfer rate.
  • image data based on the maximum number of pixels on the TFT substrate 74 is generated in order to prioritize image quality.
  • the still image generating unit 128 is connected to the moving image editing unit 130 and the region of interest setting unit 138.
  • the moving image editing unit 130 combines the image data for each frame sequentially transmitted from the still image generating unit 128 to edit the moving image.
  • the edited moving image is displayed on the display 80 via the display driver 92.
  • the still image generation unit 128 is connected to the display driver 92, and can display a still image on the display 80.
  • the moving image editing unit 130 is connected to the average QL value calculation unit 132.
  • the average QL value calculation unit 132 calculates the average value of the QL values of each frame (or one frame appropriately extracted) of the moving image.
  • the calculation result in the average QL value calculation unit 132 is sent to the ABC control unit 134.
  • a reference QL value memory 136 is connected to the ABC control unit 134.
  • the ABC control unit 134 compares the QL average value received from the average QL value calculation unit 132 with the reference QL value received from the reference QL value memory 136, and converges the QL average value to the reference QL value.
  • Correction information ⁇ X is generated. This correction information ⁇ X is applied as a correction coefficient for increasing or decreasing the radiation dose (energy) exposed from the radiation exposure source 22A.
  • the correction information ⁇ X generated by the ABC control unit 134 is sent to the radiation dose adjustment unit 120.
  • the radiation dose XN is increased or decreased (XN ⁇ XN ⁇ ⁇ X).
  • the radiation dose adjustment unit 120 stores an initial value of the radiation dose XN, and when the exposure instruction is given, the exposure is started from the initial value.
  • the photoelectric conversion signal that is the basis for generating the moving image can be within an appropriate range without excess or deficiency for obtaining the gradation signal. This means that it is a region where the rate of change in the characteristic diagram showing the correlation between the photoelectric conversion signal and the image density is large (for example, an intermediate region of the ⁇ curve in the case of a photosensitive material).
  • the correction information ⁇ X is used as a multiplication (division) coefficient when correcting the radiation dose XN, but an addition (subtraction) coefficient (XN ⁇ XN + ⁇ XN) may be used.
  • the region of interest setting unit 138 sets a region of interest (ROI) based on the ROI setting still image data received from the still image generating unit 128.
  • ROI region of interest
  • a general method is a method of surrounding pixels having a pixel value equal to or greater than a certain value, and is suitable for surrounding an organ or a lesion where radioactivity is accumulated.
  • an ROI is defined in advance in a standard image and is matched with a target image. Furthermore, in the case of a moving image, a portion with a large change amount may be extracted.
  • the region-of-interest setting unit 138 sets at least a start signal indicating the start of setting of the ROI and the setting completion to the still image generation instruction unit 125 for each purpose and the exposure control unit 140 before ROI determination
  • a completion signal indicating the time is output.
  • the purpose-specific still image generation instruction unit 125 recognizes the purpose of the still image based on the start signal or the completion signal.
  • the pre-ROI determination exposure control unit 140 is connected to the radiation dose adjustment unit 120, the ABC control unit 134, and the dynamic range adjustment unit 126, respectively.
  • the control prohibition signal for instructing prohibition of the ABC control is output from the pre-ROI determination exposure control unit 140 to the ABC control unit 134.
  • An instruction signal is output (XROI ⁇ XN).
  • the result of the histogram analysis of the photoelectric conversion signal in the modulation signal analysis unit 124 is a part of the set dynamic range (region with a low QL value). ) Only.
  • the compression rate of the dynamic range is the ROI whose compression rate is higher than the compression rate DRN from the compression rate DRN at the steady state.
  • a dynamic range compression ratio instruction signal that is an instruction for setting the compression ratio DRROI for setting is output (DRROI> DRN).
  • the result of the histogram analysis of the photoelectric conversion signal covers the entire dynamic range.
  • the radiation dose (energy) exposed from the radiation exposure source 22A is lowered (from the radiation dose XN to the radiation dose XROI), and the amount of the dynamic range is reduced.
  • the compression rate from the compression rate DRN to DRROI
  • a completion signal is sent to the still image generation instruction unit 125 for each purpose and the exposure control unit 140 before ROI determination, so that the captured still image is a moving image.
  • the radiation dose adjustment unit 120 sets the radiation dose to the initial value XN
  • the dynamic range adjustment unit 126 sets the compression rate to DRN.
  • ABC control by the ABC control unit 134 can be executed.
  • FIG. 6 is a flowchart showing the radiographic imaging preparation control routine.
  • step 200 it is determined whether or not a shooting instruction has been issued. If a negative determination is made, this routine ends. If an affirmative determination is made, the routine proceeds to step 202.
  • step 202 an initial information input screen is displayed. That is, the display driver 92 is controlled to display a predetermined initial information input screen on the display 80, and the process proceeds to step 204.
  • step 204 input of predetermined information is waited.
  • the name of the subject who will take a radiographic image, the part to be imaged, the posture at the time of radiography, and the exposure condition of the radiographic X at the time of radiography (in this embodiment, the radiation X is exposed Message for prompting the input of the tube voltage and tube current) and an input area for such information are displayed.
  • the photographer When the initial information input screen is displayed on the display 80, the photographer displays the name of the subject to be imaged, the region to be imaged, the posture at the time of imaging, and the exposure conditions in the corresponding input areas. Input via 82.
  • the radiographer enters the radiography room 32 together with the subject.
  • the radio cassette 20A is supported while the electronic cassette 20 is held in the holding unit 44 of the corresponding prone position table 36.
  • the subject is positioned (positioned) at a predetermined imaging position.
  • the subject and the electronic cassette 20 are ready to capture the imaging target site.
  • the radiation exposure source 22A is positioned (positioned).
  • step 204 is affirmative and the process proceeds to step 206.
  • the negative determination in step 204 is an infinite loop, but it may be forcibly terminated by operating a cancel button provided on the operation panel 82.
  • step 206 information input on the initial information input screen (hereinafter referred to as “initial information”) is transmitted to the electronic cassette 20 via the wireless communication unit 96, and then the process proceeds to the next step 208.
  • the exposure condition is set by transmitting the exposure condition included in the initial information to the radiation generator 24 via the wireless communication unit 96.
  • the image processing control unit 102 of the radiation generator 24 prepares for exposure under the received exposure conditions.
  • step 210 the start of the ABC control is instructed, and then the process proceeds to step 212, where the instruction information instructing the start of radiation exposure is transmitted to the radiation generator 24 via the wireless communication unit 96.
  • step 212 the instruction information instructing the start of radiation exposure is transmitted to the radiation generator 24 via the wireless communication unit 96.
  • the routine ends. The details of the ABC control in step 210 will be described later using the flowchart of FIG.
  • step 250 it is determined whether or not an exposure start instruction has been issued. If a negative determination is made, this routine ends. If an affirmative determination is made, the routine proceeds to step 252.
  • step 252 the region-of-interest setting control is executed, and when the region-of-interest setting ends, the process proceeds to step 254. Details of the region-of-interest setting control in step 252 will be described later using the flowchart of FIG.
  • step 254 the steady-state radiation dose (initial value) XN is read, and then the process proceeds to step 256 where the radiation exposure control unit 22 performs the exposure received by the radiation generator 24 from the console 30.
  • the emission of the radiation X from the radiation exposure source 22A with the tube voltage and the tube current according to the irradiation conditions is started.
  • the radiation X emitted from the radiation exposure source 22A reaches the electronic cassette 20 after passing through the subject.
  • the currently stored radiation dose correction information is read out.
  • This radiation dose correction information is generated by ABC control and is stored as a correction coefficient ⁇ X.
  • correction processing based on ABC control is executed. That is, based on the gradation signal (QL value) obtained from the electronic cassette 20, an average value of the QL values of the region of interest image is calculated, and the average value of the QL values is compared with a predetermined threshold value. The radiation dose is feedback controlled so as to converge to the threshold value.
  • step 262 the moving image editing process is executed, and the edited moving image is displayed on the display 80 in step 264 (image display process).
  • step 266 image data (moving image data) is transmitted to the RIS server 14 (see FIG. 1) via the in-hospital network 18, and the process proceeds to step 268.
  • step 268 it is determined whether or not an instruction to end imaging is given. If an affirmative determination is made, exposure is terminated in step 270, and the radiographic image capturing control program is terminated.
  • the corrected image data transmitted to the RIS server 14 is stored in the database 14A, so that a doctor can perform radiogram image interpretation and diagnosis.
  • step 210 of FIG. 6 the flow of ABC control that is instructed and started in step 210 of FIG. 6 will be described with reference to FIG. Note that the ABC control routine of FIG. 8 may be executed independently of the flowcharts of FIGS.
  • step 300 it is determined whether or not the exposure control after the ROI is determined. This is determined based on an ABC control prohibition instruction in Step 320 and an ABC control prohibition release instruction in Step 338, which will be described later.
  • step 300 If a negative determination is made in step 300, it is determined that ROI is being set, and this routine ends. That is, ABC control is not executed.
  • step 300 If the determination in step 300 is affirmative, the process proceeds to step 302 to set the dynamic range compression ratio to the compression ratio DRN at the normal time, and then the process proceeds to step 304 to capture image data, and the process proceeds to step 306. .
  • step 306 the average QL value is calculated from the captured image data, and then the process proceeds to step 308 to read the reference QL value.
  • the average QL value from the captured image data is compared with the read reference QL value to determine whether correction is possible, and the process proceeds to step 312.
  • the determination as to whether correction is possible may be a so-called on / off determination in which a predetermined amount of correction is performed if the difference is greater than or equal to a predetermined value and no correction is made if the difference is less than a predetermined value.
  • the solution of the calculation by a predetermined arithmetic expression (for example, arithmetic expression based on PID control etc.) may be sufficient.
  • step 312 correction information ⁇ X of the radiation dose XROI is generated based on the comparison and determination results in step 310, and then the process proceeds to step 314 to store the correction information ⁇ X generated in step 312. Ends.
  • FIG. 9 is a flowchart showing a region-of-interest setting control routine executed in step 252 of FIG. When execution of this region-of-interest setting control routine is started, a start signal is output to the exposure control unit 240 before ROI determination.
  • step 320 first, prohibition of ABC control is instructed. As a result, the radiation dose exposed from the radiation exposure source 22A is constant without feedback control.
  • the radiation dose XROI at the time of region of interest setting is read.
  • This region-of-interest setting radiation dose XROI is lower than the steady-state radiation dose N (XROI ⁇ XN).
  • the dynamic range compression ratio DRROI is read when the region of interest is set.
  • This region-of-interest setting dynamic range compression rate DRROI is a compression rate higher than a predetermined dynamic range compression rate DRN (hereinafter referred to as “steady-state dynamic range DRN”) (DRROI> DRN).
  • step 326 pre-exposure is started with the radiation dose XROI, and the process proceeds to step 328.
  • step 328 a still image for ROI setting is generated based on the photographing data (gradation signal) obtained by the pre-exposure in step 326, and the process proceeds to step 330.
  • step 330 the start of ROI setting is instructed, and the process proceeds to step 332. Since the pre-exposure in step 326 is an exposure for a still image, the radiation dose XROI is not accumulated except for a short time during the pre-exposure.
  • step 332 image display processing is executed, and the process proceeds to step 334.
  • step 334 it is determined whether or not the region of interest can be set from the moving image. If a negative determination is made, the process returns to step 332 and the image display is continued. If the determination in step 334 is affirmative, it is determined that the ROI setting has been completed, the process proceeds to step 338, the prohibition of ABC control is canceled, and this routine ends.
  • the histogram when the photoelectric conversion signal under the radiation dose XN in the steady state is converted into the gradation signal is almost the entire dynamic range compression rate DRN region in the steady state. It is distributed over. In other words, when setting the dynamic range compression ratio DRN at the normal time, the prediction is made based on the radiation dose XN at the normal time.
  • FIGS. 10 (2) and 11 (1) are the same characteristic diagram).
  • step 324 in FIG. 9 the dynamic range compression ratio is increased (DRROI).
  • DRROI dynamic range compression ratio
  • the radiation dose exposed from the radiation exposure source 22A is suppressed as much as possible (lower than the normal time), and the QL based on the lowered radiation dose is set.
  • the dynamic range compression rate was set higher than in the steady state to match the distribution of the value gramogram. For this reason, even if the distribution of the QL value is biased, the dynamic range can be used without waste, and both reduction of the exposure dose of the subject due to the radiation dose reduction and high-precision ROI setting can be achieved.
  • the radiation filter is temporarily (during pre-exposure) with the subject without changing the radiation dose from the radiation exposure source 22A. May be interposed.
  • the radiation filter includes, for example, a so-called diaphragm mechanism that can be installed on the radiation surface of the radiation radiation source 22A.
  • a so-called diaphragm mechanism that can be installed on the radiation surface of the radiation radiation source 22A.
  • attaching an ND (darkening) filter to the range and adjusting the aperture are the same in terms of the role of adjusting (reducing) exposure.
  • ND darkening
  • the diaphragm mechanism is a substitute for a case where the radiation filter cannot be practically used depending on the type of radiation. Applicable.
  • the radiation detector 26 in the electronic cassette 20 is a so-called area sensor in which detection pixels are two-dimensionally arranged, but only for a moving image that does not require a higher frame rate than a still image, Newly equipped with a line sensor in which pixels in the main scanning direction are arranged and a scanning mechanism unit that moves the line sensor in the sub-scanning direction, and a function of acquiring a two-dimensional image in time series by scanning of the scanning mechanism unit An electronic cassette may be manufactured. Further, a line sensor and a scanning mechanism unit may be built in the standing table 42 or the standing table 36 shown in FIG.
  • a line sensor for example, after a region of interest (ROI) is set, if a moving image is specified in the ROI region, at least the sub-scanning range can be reduced. Can be reduced.
  • ROI region of interest
  • FIG. 12 is a characteristic diagram in the case where the accumulated value of the exposure dose in the process of performing the examination by moving image for the subject in the radiographic imaging system 16 according to the present embodiment is compared with the conventional comparative example. It is.
  • the exposure amount is based on the inclination (change rate) of the present embodiment. It can be seen that a large slope (change rate) is accumulated in a so-called right-up direction (see the chain line in FIG. 12). Moreover, at the end of the inspection, ABC control increases in a quadratic curve in addition to a direct proportional (primary curve) increase, and a large gap occurs between the primary curve and the quadratic curve.
  • a still image is captured by pre-exposure prior to moving image capturing, and an ROI is set based on the still image generated by the pre-exposure, Until the ROI setting is completed, the ABC control is prohibited, so that the exposure dose can be significantly reduced as compared with the exposure dose during the ROI setting while always performing the moving image shooting and the ABC control. Furthermore, since the radiation energy in the pre-exposure for ROI setting is set low and the compression ratio of the dynamic range for converting to the gradation signal is increased accordingly, the ROI can be accurately and quickly performed even if the exposure dose is low. Can be set.

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Abstract

La présente invention concerne un système de radiographie, selon lequel une image fixe est capturée au moyen d'une pré-exposition avant imagerie par image animée, et sur la base de l'image fixe résultant de la pré-exposition, une région d'intérêt (ROI) est déterminée, le contrôle ABC étant interdit jusqu'à la fin de la détermination de la ROI. En outre, l'énergie de rayonnement dans la pré-exposition pour la détermination de la ROI est fixée à un bas niveau, et la vitesse de compression d'une gamme dynamique pour la conversion en signal de gradient est fixée à un niveau respectivement plus élevé.
PCT/JP2012/071895 2011-09-21 2012-08-29 Appareil de radioscopie, procédé de détermination d'une région d'intérêt pour appareil de radioscopie, système de radiographie, et programme de contrôle de radioscopie WO2013042514A1 (fr)

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