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WO2013047069A1 - Système de capture d'image d'image radiographique, procédé et programme de commande de capture d'image d'image radiographique - Google Patents

Système de capture d'image d'image radiographique, procédé et programme de commande de capture d'image d'image radiographique Download PDF

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Publication number
WO2013047069A1
WO2013047069A1 PCT/JP2012/071896 JP2012071896W WO2013047069A1 WO 2013047069 A1 WO2013047069 A1 WO 2013047069A1 JP 2012071896 W JP2012071896 W JP 2012071896W WO 2013047069 A1 WO2013047069 A1 WO 2013047069A1
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WIPO (PCT)
Prior art keywords
unit
radiation
region
image
area
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English (en)
Japanese (ja)
Inventor
中津川　晴康
大田　恭義
西納　直行
北野　浩一
岩切　直人
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Fujifilm Corp
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Fujifilm Corp
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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
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • 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
    • A61B6/04—Positioning of patients; Tiltable beds or the like
    • A61B6/0407—Supports, e.g. tables or beds, for the body or parts of the body
    • A61B6/0414—Supports, e.g. tables or beds, for the body or parts of the body with compression means
    • 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
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A61B6/4233—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors

Definitions

  • the present invention relates to a radiographic image capturing system, method, and radiographic image capturing control program, and in particular, a radiographic image capturing system, method, and method for capturing a radiographic image indicated by radiation emitted from a radiation source and transmitted through a subject.
  • the present invention relates to a radiographic imaging control program.
  • radiography apparatus such as FPD (Flat Panel Detector) which can arrange radiation sensitive layer on TFT (Thin Film Transistor) active matrix substrate and convert radiation directly into digital data have been put into practical use.
  • FPD Fluor Deposition Detector
  • TFT Thin Film Transistor
  • a radiographic apparatus that captures a radiographic image represented by irradiated radiation has been put to practical use.
  • the radiography apparatus using this radiation detector can see images immediately, compared with conventional radiography apparatuses using X-ray film or imaging plate, and radiographic imaging (moving image) (Photographing) can also be performed.
  • radiation detectors of this type have been proposed.
  • radiation is once converted into light by a scintillator such as CsI: Tl, GOS (Gd 2 O 2 S: Tb), and converted light.
  • Materials that can be used for the semiconductor layer in each method such as an indirect conversion method that converts the charge into a charge using a sensor such as a photodiode, and a direct conversion method that converts radiation into a charge in a semiconductor layer such as amorphous selenium.
  • the electric charge accumulated in the radiation detector is read as an electric signal, and the read electric signal is amplified by an amplifier and then converted into digital data by an A / D (analog / digital) converter.
  • Pulsed irradiation has the advantage of increasing the irradiation amount per unit time because it can irradiate radiation only for the period required for imaging and can suppress the patient's exposure compared to continuous irradiation.
  • the image data In order to display the radiographic image obtained by fluoroscopy in real time, the image data must be transferred without delay from the radiation detector to the console. However, if the size of the image data to be transferred is large, display delay may occur. In order to prevent display delay, a method of irreversibly compressing the entire image data is conceivable. However, there is a possibility that the image data may be lost or the displayed image may be deteriorated, resulting in trouble.
  • the captured frame is divided into a plurality of small regions, the region of interest is specified based on the amount of change in the density feature value, and the shooting conditions such as the size of the region of interest are determined according to the frame rate and the like.
  • the shooting conditions such as the size of the region of interest are determined according to the frame rate and the like. Is also known (see Japanese Patent Laid-Open No. 6-209926).
  • a region where a tumor, a polyp, or the like exists is a region that is particularly desired to be displayed in real time without image deterioration, and is a region where image data should be transferred to the console without being compressed.
  • the size of the region of interest is set regardless of such a region, so that a region to be transferred without being compressed may be compressed before being transmitted.
  • the present invention has been made in order to solve the above-described problems.
  • image data of an area to be displayed in real time without deterioration in image quality is transmitted without being compressed reliably.
  • Another object of the present invention is to provide a radiographic imaging system and method capable of displaying in real time without deterioration in image quality.
  • the radiographic imaging system is a fluoroscopic imaging that continuously detects radiographic images by detecting the radiation irradiated in a pulse form from the radiation irradiating unit.
  • the image data of the radiographic image capturing unit that is enabled and the radiographic image non-compressed transfer region image data obtained by fluoroscopic imaging of the radiographic image capturing unit are transmitted without compression, and the image data of the remaining region is compressed Transmitting unit, receiving unit receiving the image data of the radiographic image transmitted from the transmitting unit, display unit displaying the radiographic image based on the image data received by the receiving unit, fluoroscopic imaging Specified as an area to be transferred in an uncompressed manner within the region of interest of the radiation image, which is below the upper limit of the amount of data that can be transferred without compression determined by the frame rate of The region containing the mandatory transfer area, and a, a transfer area setting unit that sets as the uncompressed transfer area.
  • a movement detection unit that detects the movement of the imaging region during fluoroscopic imaging is further provided, and the transfer region setting unit is detected by the motion detection unit within the region of interest.
  • the transfer region setting unit is detected by the motion detection unit within the region of interest.
  • a first changing unit that changes to be equal to or less than a frame rate that is an upper limit value, and a radiation irradiation period for each frame period for capturing each frame image according to the changed frame rate
  • a second changing unit that changes to be longer than the irradiation period before the frame rate is changed, and after the change of the frame rate and the irradiation period, according to the changed frame rate and the irradiation period,
  • An imaging control unit that controls the radiographic imaging unit to perform radiographic imaging in synchronization with the pulse irradiation while irradiating the radiographic imaging unit with radiation from the radiation irradiating unit; You may have.
  • the region in which the motion has occurred can be included in the uncompressed transfer region and transmitted. If the amount of data in the uncompressed transfer area that has been detected and the setting has been changed exceeds the upper limit of the amount of data that can be transferred without compression determined by the frame rate of fluoroscopic imaging, the frame rate is changed according to the amount of data. Therefore, it is possible to reliably transmit image data in an area to be displayed in real time without deterioration in image quality without being compressed, and display the image data in real time without deterioration in image quality. Furthermore, since the irradiation period is changed to become longer according to the change of the frame rate, a fluoroscopic image with smooth movement can be displayed.
  • the second changing unit sets the ratio of the irradiation period of radiation to each frame period for capturing each frame image corresponding to the changed frame rate to 12.5%. You may make it change so that it may become in the range of -80%.
  • the second changing unit has a ratio of the radiation irradiation period to each frame period corresponding to the changed frame rate within a range of 33% to 80%. You may make it change as follows.
  • the second changing unit when the frame rate after changing the fluoroscopic imaging is equal to or less than the first frame rate threshold, sets the ratio of the irradiation period to each frame period to 12.5. If the frame rate after changing the fluoroscopic imaging is less than or equal to the second frame rate threshold lower than the first frame rate threshold, the ratio of the irradiation period to each frame period is 33% to You may make it change so that it may exist in the range of 80%.
  • the first frame rate threshold may be 15 fps or more and 60 fps or less
  • the second frame rate threshold may be 5 fps or more and less than the first frame rate threshold.
  • the image processing apparatus further includes a gaze degree detection unit that detects a gaze degree with respect to a motion region in the radiographic image displayed on the display unit, and the transfer area setting unit is controlled by the gaze degree detection unit.
  • the gaze degree detection unit detects a gaze degree with respect to a motion region in the radiographic image displayed on the display unit.
  • the changed frame rate and irradiation period are changed to the state before the change.
  • the imaging control unit further includes a third changing unit that changes the frame rate and the irradiation period to the state before the change, and then changes the frame rate and the irradiation period according to the frame rate and the irradiation period that are returned to the state before the change.
  • the radiation image capturing unit may be controlled so that the radiation image capturing unit captures a radiation image in synchronization with the pulse irradiation while the radiation image capturing unit performs pulse irradiation of radiation.
  • the said radiographic imaging part arrange
  • the image data in the non-compressed transfer area of the radiographic image obtained by fluoroscopic imaging in the imaging unit is transmitted to the display unit without compression, and the image data in the remaining area of the radiographic image is compressed and the receiving unit
  • the transfer area setting unit may perform the setting based on a detection image detected by the detection unit.
  • the diaphragm unit that is provided between the radiation irradiation unit and the subject and adjusts the irradiation region of the radiation, and the region including at least the essential transfer region or the region of interest
  • An irradiation area setting unit that is set as an irradiation area of radiation and image data of the irradiation area set by the irradiation area setting unit are transmitted, and non-irradiation areas other than the irradiation area set by the irradiation area setting unit are transmitted.
  • a transmission control unit that controls the transmission unit so that image data is not transmitted.
  • a radiographic imaging system includes a radiographic imaging unit capable of performing radiographic imaging that continuously performs radiographic imaging, and radiation obtained by fluoroscopic imaging of the radiographic imaging unit.
  • the image data in the uncompressed transfer area of the image is transmitted uncompressed, and the image data in the remaining area is compressed and transmitted, and radiation is pulsed to the radiographic image capturing unit during fluoroscopic imaging
  • a radiation irradiating unit that radiates in a shape; a receiving unit that receives image data of a radiographic image transmitted from the transmitting unit; a display unit that displays a radiographic image based on the image data received by the receiving unit;
  • the region with the required transfer regions, and a, a transfer area setting unit that sets as the uncompressed transfer area.
  • the image data of the area to be displayed in real time without deterioration in image quality is reliably compressed in the radiographic image obtained by fluoroscopic imaging. Without being transmitted, and can be displayed in real time without deterioration in image quality.
  • the radiographic image capturing method is a radiographic image in which fluoroscopic imaging capable of continuously capturing radiographic images by detecting radiation irradiated in a pulse form from a radiation irradiating unit.
  • the image data of the uncompressed transfer area of the radiographic image obtained by fluoroscopic imaging of the imaging unit is transmitted without compression, the image data of the remaining area is compressed and transmitted, and the image data of the transmitted radiographic image is transmitted
  • an area that is equal to or less than the upper limit of the amount of data that can be transferred without compression determined by the frame rate of fluoroscopic radiography an area including an essential transfer area specified as an area to be transferred in an uncompressed area within the area of interest is set as the uncompressed transfer area.
  • the invention according to the twelfth aspect also operates in the same manner as the invention according to the first aspect, the image data of the area to be displayed in real time without deterioration in image quality is reliably compressed in the radiographic image obtained by fluoroscopic imaging. Without being transmitted, and can be displayed in real time without deterioration in image quality.
  • the radiological image capturing control program of the invention according to the thirteenth aspect causes a computer to function as a transfer area setting unit of the radiographic image capturing system according to any one of the first to tenth inventions.
  • a radiological moving image capturing control program comprising: a computer, a transfer area setting unit, a first changing unit, a second changing unit; It functions as a changing unit and a photographing control unit.
  • the present invention it is possible to reliably transmit image data of a region to be displayed in real time without deterioration in image quality in a radiographic image obtained by fluoroscopic imaging and display the image data in real time without deterioration in image quality.
  • the effect of being able to be obtained is obtained.
  • MIN1 to MAX1 are graphs showing the results of normalization processing so that the appropriate density ranges MIN2 to MAX2 are respectively obtained.
  • (3) is a graph showing an example of a conversion function used in the normalization processing. It is a flowchart which shows the flow of a process of the area
  • RIS Radiology Information System
  • 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 Healthcare Information System
  • the RIS 10 includes a plurality of radiography requesting terminal devices (hereinafter referred to as “terminal devices”) 12, a RIS server 14, and a radiographic imaging system (or an operating room) installed in a hospital. (Hereinafter referred to as “imaging system”) 18, which are connected to an in-hospital network 16 comprising a wired or wireless LAN (Local Area Network) or the like.
  • imaging system a radiography requesting terminal devices
  • imaging system or an operating room installed in a hospital.
  • imaging system an in-hospital network 16 comprising a wired or wireless LAN (Local Area Network) or the like.
  • the RIS 10 constitutes a part of the HIS provided in the same hospital, and an HIS server (not shown) that manages the entire HIS is also connected to the in-hospital network 16.
  • the terminal device 12 is used by doctors and radiographers to input and browse diagnostic information and facility reservations, and radiographic image capturing requests and imaging reservations are also performed via the terminal device 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 16.
  • the RIS server 14 receives an imaging request from each terminal device 12, manages the radiographic imaging schedule in the imaging system 18, and includes a database 14A.
  • Database 14A includes patient (subject) attribute information (name, sex, date of birth, age, blood type, weight, patient ID (Identification), etc.), medical history, medical history, radiation images taken in the past, etc.
  • Information on the electronic cassette 32 such as the number of times of use, and environment information indicating an environment in which a radiographic image is taken using the electronic cassette 32, that is, an environment in which the electronic cassette 32 is used (for example, a radiographic room or an operating room) It is comprised including.
  • the imaging system 18 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 18 includes a radiation generator 34 that irradiates a subject with radiation X (see also FIG. 3) that is a dose according to the exposure conditions from a radiation source 130 (see also FIG. 2), and a subject.
  • the console 42 acquires various types of information included in the database 14A from the RIS server 14 and stores them in an HDD 110 (see FIG. 10) described later. Based on the information, the electronic cassette 32, the radiation generator 34, and the cradle 40 are stored. Control.
  • FIG. 2 shows an example of the arrangement state of each device in the radiation imaging room 44 of the imaging system 18 according to the present embodiment.
  • the radiation imaging room 44 has a standing table 45 used when performing radiation imaging in a standing position and a prone table 46 used when performing radiation imaging in a lying position.
  • the space in front of the standing base 45 is set as a subject imaging position 48 when performing radiography in the standing position, and the upper space of the prong position 46 is used in performing radiography in the prone position.
  • the imaging position 50 of the subject is set as a subject imaging position 48 when performing radiography in the standing position, and the upper space of the prong position 46 is used in performing radiography in the prone position.
  • the standing stand 45 is provided with a holding unit 150 that holds the electronic cassette 32, and the electronic cassette 32 is held by the holding unit 150 when a radiographic image is taken in the standing position.
  • a holding unit 152 that holds the electronic cassette 32 is provided in the prone position table 46, and the electronic cassette 32 is held by the holding unit 152 when radiographic images are taken in the prone position.
  • the radiation source 130 is arranged around a horizontal axis (see FIG. 5) in order to enable radiation imaging in a standing position and in a standing position by radiation from a single radiation source 130.
  • 2 is provided that can be rotated in the vertical direction (arrow B direction in FIG. 2) and supported in a horizontal direction (in the arrow C direction in FIG. 2).
  • the support moving mechanism 52 includes a drive source that rotates the radiation source 130 about a horizontal axis, a drive source that moves the radiation source 130 in the vertical direction, and a drive source that moves the radiation source 130 in the horizontal direction. Each is provided (not shown).
  • the cradle 40 is formed with an accommodating portion 40A capable of accommodating the electronic cassette 32.
  • the built-in battery is charged in a state of being accommodated in the accommodating portion 40A of the cradle 40.
  • the electronic cassette 32 is taken out from the cradle 40 by a radiographer or the like, and the imaging posture is established. If it is in the upright position, it is held in the holding part 150 of the standing table 45, and if it is in the upright position, it is held in the holding part 152 of the standing table 46.
  • the radiation generator 34 and the console 42 are connected by cables and various types of information are transmitted and received by wired communication.
  • the cable connecting 42 is omitted.
  • Various information is transmitted and received between the electronic cassette 32 and the console 42 by wireless communication.
  • the communication between the radiation generator 34 and the console 42 may be performed by wireless communication.
  • the electronic cassette 32 is not used only in the state of being held by the holding portion 150 of the standing base 45 or the holding portion 152 of the standing base 46, and is not held by the holding portion because of its portability. It can also be used in the state.
  • FIG. 3 shows the internal configuration of the electronic cassette 32 according to the present embodiment.
  • the electronic cassette 32 includes a housing 54 made of a material that transmits the radiation X, and has a waterproof and airtight structure.
  • a housing 54 made of a material that transmits the radiation X, and has a waterproof and airtight structure.
  • one electronic cassette 32 can be used repeatedly by sterilizing and cleaning the electronic cassette 32 as necessary with a waterproof and airtight structure.
  • a radiation detector 60 for taking a radiation image of the radiation X transmitted through the subject from the irradiation surface 56 side of the housing 54 to which the radiation X is irradiated, A radiation detection unit 62 that performs detection is disposed in order.
  • an electronic circuit including a microcomputer and a chargeable and detachable battery 96A are disposed on one end side inside the housing 54.
  • the radiation detector 60 and the electronic circuit are operated by electric power supplied from the battery 96 ⁇ / b> A disposed in the case 31.
  • a lead plate or the like is arranged on the irradiation surface 56 side of the case 31.
  • the electronic cassette 32 according to the present embodiment is a rectangular parallelepiped whose irradiation surface 56 has a rectangular shape, and a case 31 is disposed at one end in the longitudinal direction.
  • a display unit 56A that displays an operation mode of the electronic cassette 32 such as an operation mode such as “ready state” and “data transmitting” and a remaining capacity of the battery 96A.
  • an operation mode such as “ready state” and “data transmitting” and a remaining capacity of the battery 96A.
  • a light emitting diode is applied as the display unit 56A.
  • the present invention is not limited to this, and other light emitting elements other than the light emitting diode, a liquid crystal display, an organic EL display, and the like are used. It may be a display means.
  • FIG. 4 is a cross-sectional view schematically showing configurations of the radiation detector 60 and the radiation detection unit 62 according to the present embodiment.
  • the radiation detector 60 includes a TFT active matrix substrate (hereinafter referred to as “TFT substrate”) 66 in which a thin film transistor (TFT: Thin Film Transistor, hereinafter referred to as “TFT”) 70 and a storage capacitor 68 are formed on an insulating substrate 64. I have.
  • TFT substrate TFT active matrix substrate
  • TFT Thin Film Transistor
  • a scintillator 71 that converts incident radiation into light is disposed.
  • the scintillator 71 for example, CsI: Tl, GOS can be used.
  • the scintillator 71 is not limited to these materials.
  • the insulating substrate 64 may be any substrate as long as it is light transmissive and absorbs little radiation.
  • a glass substrate, a transparent ceramic substrate, or a light transmissive resin substrate can be used.
  • the insulating substrate 64 is not limited to these materials.
  • the TFT substrate 66 is provided with a sensor portion 72 that corresponds to the first sensor portion of the present invention and generates charges when light converted by the scintillator 71 is incident thereon.
  • a flattening layer 67 for flattening the TFT substrate 66 is formed on the TFT substrate 66.
  • An adhesive layer 69 for bonding the scintillator 71 to the TFT substrate 66 is formed between the TFT substrate 66 and the scintillator 71 and on the planarizing layer 67.
  • the sensor unit 72 includes an upper electrode 72A, a lower electrode 72B, and a photoelectric conversion film 72C disposed between the upper and lower electrodes.
  • the photoelectric conversion film 72C absorbs the light emitted from the scintillator 71 and generates a charge corresponding to the absorbed light.
  • the photoelectric conversion film 72C may be formed of a material that generates charges when irradiated with light.
  • the photoelectric conversion film 72C may be formed of amorphous silicon, an organic photoelectric conversion material, or the like.
  • the photoelectric conversion film 72C containing amorphous silicon has a wide absorption spectrum and can absorb light emitted by the scintillator 71.
  • the photoelectric conversion film 72C includes an organic photoelectric conversion material, it has a sharp absorption spectrum in the visible range, and electromagnetic waves other than light emitted by the scintillator 71 are hardly absorbed by the photoelectric conversion film 72C, and radiation such as X-rays. Is effectively suppressed by the photoelectric conversion film 72C being absorbed.
  • the photoelectric conversion film 72C includes an organic photoelectric conversion material.
  • the organic photoelectric conversion material include quinacridone organic compounds and phthalocyanine organic compounds.
  • quinacridone organic compounds
  • phthalocyanine organic compounds For example, since the absorption peak wavelength in the visible region of quinacridone is 560 nm, if quinacridone is used as the organic photoelectric conversion material and CsI (Tl) is used as the material of the scintillator 71, the difference in peak wavelength can be made within 5 nm. Thus, the amount of charge generated in the photoelectric conversion film 72C can be substantially maximized. Since an organic photoelectric conversion material applicable as the photoelectric conversion film 72C is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, description thereof is omitted.
  • FIG. 5 schematically shows the configuration of the TFT 70 and the storage capacitor 68 formed on the TFT substrate 66 according to the present embodiment.
  • a storage capacitor 68 for storing the charge transferred to the lower electrode 72B, and a TFT 70 for converting the charge stored in the storage capacitor 68 into an electric signal and outputting it.
  • the region where the storage capacitor 68 and the TFT 70 are formed has a portion that overlaps with the lower electrode 72B in a plan view. With such a configuration, the storage capacitor 68 and the TFT 70 in each pixel portion, the sensor portion 72, and the like. Therefore, the storage capacitor 68, the TFT 70, and the sensor unit 72 can be arranged with a small area.
  • the storage capacitor 68 is electrically connected to the corresponding lower electrode 72B through a wiring made of a conductive material formed through an insulating film 65A provided between the insulating substrate 64 and the lower electrode 72B. Yes. Thereby, the charges collected by the lower electrode 72B can be moved to the storage capacitor 68.
  • the active layer 70B is formed of an amorphous oxide.
  • the amorphous oxide constituting the active layer 70B an oxide containing at least one of In, Ga, and Zn (for example, In—O-based) is preferable, and at least two of In, Ga, and Zn are used.
  • An oxide containing In (eg, In—Zn—O, In—Ga—O, or Ga—Zn—O) is more preferable, and an oxide containing In, Ga, and Zn is particularly preferable.
  • In—Ga—Zn—O-based amorphous oxide an amorphous oxide whose composition in a crystalline state is represented by InGaO 3 (ZnO) m (m is a natural number of less than 6) is preferable, and in particular, InGaZnO. 4 is more preferable.
  • the active layer 70B of the TFT 70 is formed of an amorphous oxide, it will not absorb radiation such as X-rays, or even if it absorbs it, it will remain extremely small, effectively suppressing the generation of noise. Can do.
  • the insulating substrate 64 is not limited to a highly heat-resistant substrate such as a semiconductor substrate, a quartz substrate, and a glass substrate, and a flexible substrate such as plastic, aramid, or bio-nanofiber can also be used.
  • flexible materials such as polyesters such as polyethylene terephthalate, polybutylene phthalate, and polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, and poly (chlorotrifluoroethylene).
  • a conductive substrate can be used. If such a plastic flexible substrate is used, it is possible to reduce the weight, which is advantageous for carrying around, for example.
  • the insulating substrate 64 includes 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 provided.
  • the transparent electrode material can be cured at a high temperature to lower its resistance, and can also be used for automatic mounting of a driver IC including a solder reflow process.
  • 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.
  • aramid can form a substrate thinner than a glass substrate or the like.
  • the insulating substrate 64 may be formed by stacking an ultrathin glass substrate and aramid.
  • Bionanofiber is a composite of cellulose microfibril bundle (bacterial cellulose) produced by bacteria (acetic acid bacteria, Acetobacter® Xylinum) and 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.
  • a transparent resin such as acrylic resin or epoxy resin into 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.
  • a thin insulating substrate 64 can be formed.
  • FIG. 6 is a plan view showing the configuration of the TFT substrate 66 according to this embodiment.
  • the TFT substrate 66 includes a pixel 74 including the sensor unit 72, the storage capacitor 68, and the TFT 70 described above in a certain direction (row direction in FIG. 6) and a crossing direction with respect to the certain direction (column direction in FIG. 6).
  • a pixel 74 including the sensor unit 72, the storage capacitor 68, and the TFT 70 described above in a certain direction (row direction in FIG. 6) and a crossing direction with respect to the certain direction (column direction in FIG. 6).
  • a pixel 74 including the sensor unit 72, the storage capacitor 68, and the TFT 70 described above in a certain direction (row direction in FIG. 6) and a crossing direction with respect to the certain direction (column direction in FIG. 6).
  • the radiation detection unit 62 has a size of 17 inches ⁇ 17 inches
  • 2880 pixels 74 are arranged in the row direction and the column direction.
  • the radiation detector 60 includes a plurality of gate wirings 76 extending in a certain direction (row direction) for turning on / off each TFT 70, and an on-state TFT 70 extending in a crossing direction (column direction).
  • a plurality of data wirings 78 are provided for reading out charges via the.
  • the radiation detector 60 is flat and has a quadrilateral shape with four sides on the outer edge in plan view. Specifically, it is formed in a rectangular shape.
  • the radiation detector 60 is formed by attaching a scintillator 71 to the surface of the TFT substrate 66 as shown in FIG.
  • the scintillator 71 is formed by vapor deposition on the vapor deposition substrate 73 when it is intended to be formed of a columnar crystal such as CsI: Tl.
  • the vapor deposition substrate 73 is often an Al plate in terms of X-ray transmittance and cost, handling properties during vapor deposition, prevention of warpage due to its own weight, and deformation due to radiant heat. Therefore, a certain thickness (about several mm) is required.
  • the radiation detector 62 is attached to the surface of the radiation detector 60 on the scintillator 71 side.
  • a wiring layer 142 and an insulating layer 144 in which a wiring 160 (FIG. 8) to be described later is patterned are formed on a resin support substrate 140.
  • a plurality of sensor units 146 corresponding to the two sensor units are formed, and a scintillator 148 made of GOS or the like is formed on the sensor unit 146.
  • the sensor unit 146 includes an upper electrode 147A, a lower electrode 147B, and a photoelectric conversion film 147C disposed between the upper and lower electrodes.
  • the photoelectric conversion film 147 ⁇ / b> C generates a charge when light converted by the scintillator 148 is incident thereon.
  • the photoelectric conversion film 147C is preferably a photoelectric conversion film containing the above-described organic photoelectric conversion material, rather than a PIN-type or MIS-type photodiode using amorphous silicon. Compared to the case of using a PIN type photodiode or MIS type photodiode, this is a method using a photoelectric conversion film containing an organic photoelectric conversion material in terms of reduction in manufacturing cost and flexibility. Is advantageous.
  • the sensor unit 146 of the radiation detector 62 does not need to be formed as finely as the sensor unit 72 provided in each pixel 74 of the radiation detector 60, and is formed with a size of tens to hundreds of pixels of the radiation detector 60. That's fine.
  • FIG. 7 is a plan view showing an arrangement configuration of the sensor unit 146 of the radiation detection unit 62 according to the present embodiment.
  • a large number of sensor units 146 are arranged in a certain direction (row direction in FIG. 7) and in an intersecting direction (column direction in FIG. 7) with respect to the certain direction.
  • the sensor unit 146 is arranged in the row direction and column. 16 pieces are arranged in a matrix in the direction.
  • FIG. 8 is a block diagram showing the main configuration of the electrical system of the electronic cassette 32 according to the present embodiment.
  • the radiation detector 60 includes a plurality of pixels 74 including the sensor unit 72, the storage capacitor 68, and the TFT 70 arranged in a matrix, and the sensor unit according to the irradiation of the radiation X to the electronic cassette 32.
  • the charges generated at 72 are stored in the storage capacitors 68 of the individual pixels 74.
  • the image information carried on the radiation X irradiated to the electronic cassette 32 is converted into charge information and held in the radiation detector 60.
  • each gate wiring 76 of the radiation detector 60 is connected to a gate line driver 80, and each data wiring 78 is connected to a signal processing unit 82.
  • the TFTs 70 of the individual pixels 74 are sequentially turned on in units of rows by a signal supplied from the gate line driver 80 through the gate wiring 76, and the TFTs 70 are turned on.
  • the charges stored in the storage capacitor 68 of the pixel 74 are transmitted through the data wiring 78 as an analog electric signal and input to the signal processing unit 82. Therefore, the charges accumulated in the accumulation capacitors 68 of the individual pixels 74 are read out in order in row units.
  • FIG. 9 shows an equivalent circuit diagram focusing on one pixel portion of the radiation detector 60 according to the present exemplary embodiment.
  • the source of the TFT 70 is connected to a data wiring 78, and the data wiring 78 is connected to a signal processing unit 82.
  • the drain of the TFT 70 is connected to the storage capacitor 68 and the photoelectric conversion unit 72, and the gate of the TFT 70 is connected to the gate wiring 76.
  • the signal processing unit 82 includes a sample hold circuit 84 for each data wiring 78.
  • the electric signal transmitted through each data wiring 78 is held in the sample hold circuit 84.
  • the sample hold circuit 84 includes an operational amplifier 84A and a capacitor 84B, and converts an electric signal into an analog voltage.
  • the sample hold circuit 84 is provided with a switch 84C as a reset circuit that shorts both electrodes of the capacitor 84B and discharges the electric charge accumulated in the capacitor 84B.
  • the operational amplifier 84A can adjust the gain amount by control from a cassette control unit 92 described later.
  • a multiplexer 86 and an A / D converter 88 are sequentially connected to the output side of the sample and hold circuit 84, and the electrical signals held in the individual sample and hold circuits are converted into analog voltages and sequentially supplied to the multiplexer 86 (serially). ) And converted into digital image information by the A / D converter 88.
  • An image memory 90 is connected to the signal processing unit 82 (see FIG. 8), and image data output from the A / D converter 88 of the signal processing unit 82 is stored in the image memory 90 in order.
  • the image memory 90 has a storage capacity capable of storing image data for a plurality of frames, and image data obtained by imaging is sequentially stored in the image memory 90 every time a radiographic image is captured.
  • the image memory 90 is connected to a cassette control unit 92 that controls the operation of the entire electronic cassette 32.
  • the cassette control unit 92 includes a microcomputer, and includes a CPU (Central Processing Unit) 92A, a memory 92B including a ROM (Read Only Memory) and a RAM (Random Access Memory), an HDD (Hard Disk Drive), and a flash memory.
  • a non-volatile storage unit 92 ⁇ / b> C is provided.
  • a wireless communication unit 94 is connected to the cassette control unit 92.
  • the wireless communication unit 94 according to the present embodiment is compatible with a wireless LAN (Local Area Network) standard represented by IEEE (Institute of Electrical and Electronics Electronics) (802.11a / b / g) and is based on wireless communication. Controls the transmission of various information to and from external devices.
  • the cassette control unit 92 can wirelessly communicate with the console 42 via the wireless communication unit 94, and can transmit and receive various information to and from the console 42.
  • the radiation detection unit 62 includes a large number of sensor units 146 arranged in a matrix.
  • the radiation detection unit 62 is provided with a plurality of wires 160 individually connected to the sensor units 146, and the wires 160 are connected to the signal detection unit 162.
  • the signal detection unit 162 includes an amplifier and an A / D converter provided for each wiring 160, and is connected to the cassette control unit 92.
  • the signal detection unit 162 performs sampling of each wiring 160 at a predetermined cycle by the control from the cassette control unit 92, converts the electrical signal transmitted through each wiring 160 into digital data, and sequentially converts the converted digital data, Output to the cassette control unit 92.
  • the electronic cassette 32 is provided with a power supply unit 96, and the various circuits and elements described above (gate line driver 80, signal processing unit 82, image memory 90, wireless communication unit 94, cassette control unit 92, signal detection).
  • the unit 162 and the like are operated by the electric power supplied from the power source unit 96.
  • the power supply unit 96 incorporates the above-described battery (secondary battery) 96A so as not to impair the portability of the electronic cassette 32, and supplies power from the charged battery 96A to various circuits and elements.
  • illustration of wirings connecting the power supply unit 96 to various circuits and elements is omitted.
  • FIG. 10 is a block diagram showing the main configuration of the electrical system of the console 42 and the radiation generator 34 according to the present embodiment.
  • the console 42 is configured as a server computer, and includes a display 100 that displays an operation menu, a captured radiation image, and the like, and a plurality of keys, and an operation panel on which various information and operation instructions are input. 102.
  • the console 42 includes a CPU 104 that controls the operation of the entire apparatus, a ROM 106 that stores various programs including a control program in advance, a RAM 108 that temporarily stores various data, and various data. It includes an HDD 110 that stores and holds, a display driver 112 that controls display of various types of information on the display 100, and an operation input detection unit 114 that detects an operation state of the operation panel 102.
  • the console 42 includes a communication interface (I / F) unit 116 that transmits and receives various types of information such as an exposure condition to be described later to and from the radiation generator 34 via the connection terminal 42A and the communication cable 35, and an electronic cassette.
  • a wireless communication unit 118 that transmits and receives various types of information such as image capturing conditions, exposure conditions, and image data by wireless communication.
  • CPU 104, ROM 106, RAM 108, HDD 110, display driver 112, operation input detection unit 114, communication interface unit 116, and wireless communication unit 118 are connected to each other via a system bus BUS. Therefore, the CPU 104 can access the ROM 106, RAM 108, and HDD 110, controls display of various information on the display 100 via the display driver 112, and the radiation generator 34 via the communication I / F unit 116. And control of transmission / reception of various information to / from the radiation generator 34 via the wireless communication unit 118. Further, the CPU 104 can grasp the operation state of the user with respect to the operation panel 102 via the operation input detection unit 114.
  • the radiation generator 34 controls the radiation source 130 based on the received radiation conditions and the communication I / F unit 132 that transmits and receives various information such as the radiation conditions between the radiation source 130 and the console 42.
  • a radiation source control unit 134 controls the radiation source 130 based on the received radiation conditions and the communication I / F unit 132 that transmits and receives various information such as the radiation conditions between the radiation source 130 and the console 42.
  • the radiation source control unit 134 is also configured to include a microcomputer, and stores the received exposure conditions and the like.
  • the exposure conditions received from the console 42 include information on tube voltage and tube current.
  • the radiation source controller 134 irradiates the radiation X from the radiation source 130 based on the received exposure conditions.
  • the imaging system 18 is capable of still image shooting in which shooting is performed once and fluoroscopic shooting in which continuous shooting is performed, and still image shooting or fluoroscopic shooting is selected as a shooting mode. It is possible.
  • fluoroscopic imaging with pulse irradiation can irradiate radiation only for the period required for imaging, and can reduce the patient's exposure compared to continuous irradiation, so the irradiation dose per unit time is increased.
  • fluoroscopic imaging is performed by pulse irradiation.
  • FIG. 12 shows a time chart showing the flow of imaging operation when performing fluoroscopic imaging with pulse irradiation.
  • the console 42 transmits a synchronization signal to the radiation generator 34 and the electronic cassette 32 at a cycle corresponding to the designated frame rate.
  • the radiation generator 34 Each time the radiation generator 34 receives a synchronization signal, it generates and emits radiation at a tube voltage, a tube current, and an irradiation period corresponding to the exposure conditions received from the console 42.
  • the cassette control unit 92 of the electronic cassette 32 controls the gate line driver 80 after the irradiation period specified by the exposure condition after receiving the synchronization signal, and sequentially sets each gate line 76 from the gate line driver 80 line by line.
  • An on signal is output to turn on the TFTs 70 connected to the gate wirings 76 one line at a time to read an image.
  • the electric signal flowing out to each data wiring 78 of the radiation detector 60 is converted into digital image data by the signal processing unit 82, stored in the image memory 90, and transmitted to the console 42 one image at a time.
  • the image transmitted to the console 42 is subjected to various correction image processing such as shading correction in the console 42 and stored in the HDD 110, and is displayed on the display 100 for confirmation of the captured radiation image. , Transferred to the RIS server 14 and stored in the database 14A.
  • the terminal device 12 accepts an imaging request from a doctor or a radiographer when imaging a radiographic image.
  • an imaging request a patient to be imaged, an imaging region to be imaged, an imaging purpose, an imaging mode, a frame rate are specified, and a tube voltage, a tube current, and the like are specified as necessary.
  • the terminal device 12 notifies the RIS server 14 of the contents of the accepted imaging request.
  • the RIS server 14 stores the contents of the imaging request notified from the terminal device 12 in the database 14A.
  • the console 42 accesses the RIS server 14 to acquire the content of the imaging request and the attribute information of the patient to be imaged from the RIS server 14, and displays the content of the imaging request and the attribute information of the patient on the display 100 (see FIG. 10). .).
  • the radiographer starts radiographic image capturing based on the content of the radiography request displayed on the display 100.
  • the electronic cassette 32 when imaging the affected part of the subject lying on the prone table 46, the electronic cassette 32 is arranged on the holding unit 152 of the prone table 46.
  • the photographer designates still image photographing or fluoroscopic photographing as a photographing mode for the operation panel 102, and further designates a tube voltage, a tube current, and the like when the operation panel 102 is irradiated with the radiation X.
  • the radiation detection unit 62 detects the radiation, and when the radiation irradiation start is detected, each pixel 74 of the radiation detector 60 is detected. Imaging is started after a reset operation for taking out and removing the charges accumulated in the storage capacitor 68 is performed.
  • the console 42 transmits the tube voltage, the tube current, the frame rate in the pulse irradiation and the irradiation period to the radiation generator 34 and the electronic cassette 32 as the exposure conditions, and designates the designated imaging region, imaging purpose, imaging mode, tube voltage, The tube current and the allowable amount are transmitted to the electronic cassette 32 as photographing conditions.
  • the radiation source control unit 134 of the radiation generator 34 receives the exposure conditions from the console 42
  • the radiation control unit 134 stores the received exposure conditions
  • the cassette control unit 92 of the electronic cassette 32 receives the exposure conditions and imaging conditions from the console 42. Is received, the received exposure conditions and imaging conditions are stored in the storage unit 92C.
  • the photographer When the photographer completes preparation for photographing, the photographer performs a photographing instruction operation for instructing photographing on the operation panel 102 of the console 42.
  • the console 42 transmits instruction information for instructing the start of exposure to the radiation generator 34 and the electronic cassette 32, and starts an imaging operation.
  • the radiation detection unit 62 detects the radiation to acquire a radiographic image for density correction, and the radiographic image for density correction.
  • the gain amount of the operational amplifier 84A from which an image with an appropriate density is obtained is obtained, and the obtained gain amount is fed back to adjust the gain amount of the operational amplifier 84A and the radiation image is read from the radiation detector 60. ing.
  • the console 42 transmits instruction information for instructing the start of exposure to the radiation generator 34 and the electronic cassette 32, and then transmits a synchronization signal to the radiation generator 34 and the electronic cassette 32 in a cycle corresponding to the designated frame rate. .
  • the radiation generator 34 Each time the radiation generator 34 receives a synchronization signal, it generates and emits radiation at a tube voltage, a tube current, and an irradiation period corresponding to the exposure conditions received from the console 42.
  • the cassette control unit 92 of the electronic cassette 32 executes the shooting control program shown in FIG. 13 when a predetermined period elapses after receiving the synchronization signal.
  • the program is stored in advance in a predetermined area of the memory 92B (ROM).
  • step S ⁇ b> 24 the cassette control unit 92 arranges the detection values detected by the sensor units 146 provided in the radiation detection unit 62 in a two-dimensional manner corresponding to the arrangement of the sensor units 146. Is used as a pixel value to generate image data of a radiographic image detected by each sensor unit 146 of the radiation detection unit 62.
  • This radiation image is a thinned-out image captured by the radiation detector 60 because each sensor unit 146 of the radiation detection unit 62 is formed with a size of several tens to several hundreds of pixels of the radiation detector 60.
  • the cassette control unit 92 analyzes the image data generated in step S26 and derives an appropriate gain amount for the operational amplifier 84A.
  • a storage area for storing the cumulative value of the digital data detected by each sensor unit 146 is prepared. It is assumed that the storage area stores a cumulative value of digital data from shooting (shooting of the previous frame).
  • FIG. 14A shows an example of a radiographic image detected by each sensor unit 146 of the radiation detection unit 62
  • FIG. 14B shows a cumulative histogram of the radiographic image shown in FIG. 14A.
  • the cumulative histogram is a diagram in which the pixel value (luminance value) is represented on the horizontal axis and the appearance rate (frequency) of the pixel of the pixel value is represented on the vertical axis for all image data forming one radiation image.
  • the radiographic image has a large number of pixels in a subject region in which an image of the imaging region (a face in FIG. 14A) is shown and a so-called unexposed region in which the imaging region is not in image, the subject region and the non-existence region in the cumulative histogram
  • the cumulative value has a peak, and the subject region has a larger density change, so the width of the cumulative histogram is also widened.
  • ⁇ In this cumulative histogram, specify the range of data values based on the image of the imaging region.
  • a known technique can be used as this specifying method.
  • dynamic contour extraction processing such as a snakes algorithm, contour extraction processing using Hough transform or the like is performed, and a region surrounded by a line along the contour point is recognized as a subject region.
  • the subject area may be recognized by using the technique described in Japanese Patent Laid-Open No. 4-11242.
  • a pattern image showing a standard shape for each imaging region is stored in the memory 92B (ROM).
  • the pattern matching is performed to obtain the similarity between the radiographic image and the pattern image while changing the position and enlargement ratio of the pattern image in accordance with the imaging region in the radiographic image taken, and the highest similarity is obtained.
  • the area may be recognized as a subject area.
  • a cumulative histogram of the recognized subject area of the radiographic image is obtained. For example, in the cumulative histogram, the half value width of the peak value is set as the main density range of the subject area, and the center of the density range becomes the center of the predetermined appropriate density range.
  • the gain amount of the operational amplifier 84A is obtained. For this gain amount, an appropriate gain amount is stored in advance in the memory 92B (ROM) as gain amount information for each difference between the center of the density range and the center of the appropriate density range.
  • the gain amount corresponding to the difference from the center may be obtained from the gain amount information, and the calculation that defines the relationship between the difference between the center of the density range and the center of the predetermined appropriate density range and the appropriate gain amount
  • the equation may be stored in the memory 92B (ROM), and the gain amount may be calculated from the difference between the center of the density range and the center of the appropriate density range using an arithmetic expression.
  • the cassette control unit 92 adjusts the gain amount of the operational amplifier 84A to the gain amount derived in step S28.
  • the cassette control unit 92 controls the gate line driver 80 to output an ON signal to each gate line 76 in order from the gate line driver 80 line by line. This step is performed at the timing when the irradiation period of the exposure condition has elapsed since the reception of the synchronization signal.
  • the charges accumulated in the storage capacitors 68 line by line flow out to the data lines 78 as electric signals.
  • the electric signals flowing out to the respective data lines 78 are amplified by the operational amplifier 84A of the signal processing unit 82, and then sequentially input to the A / D converter 88 through the multiplexer 86, converted into digital image data, and image memory 90.
  • the density range of the subject region in the read out radiation image can be set to an appropriate density range.
  • the cassette control unit 92 transmits the image data of the radiation image stored in the image memory 90 to the console 42 at a predetermined transfer rate, and ends the process.
  • the image data of the non-compressed transfer area is not compressed among the image data of the radiographic image, and the image data of the compressed transfer area other than the non-compressed transfer area is irreversibly compressed and transmitted to the console 42.
  • the console 42 When the console 42 receives the image data from the electronic cassette 32, the compressed image data of the received image data is subjected to decompression processing (or decoding). Of course, it is not necessary to decode the uncompressed image data. Thereafter, various types of image processing such as shading correction are performed as necessary, and the image information after the image processing is stored in the HDD 110 and displayed on the display 100 for confirmation of the captured radiographic image.
  • the image information stored in the HDD 110 is transferred to the RIS server 14 and stored in the database 14A.
  • the gain amount of the operational amplifier 84A as a processing parameter from the image obtained from the detection result by the sensor unit 146 of the radiation detection unit 62, the image of the subject region is appropriately adjusted without being saturated by the A / D converter 88.
  • the concentration range can be adjusted.
  • the electrical signal amplified by the operational amplifier 84A of the signal processing unit 82 is converted into digital data of a predetermined number of bits (for example, 16 bits) by the A / D converter 88, and the cassette control unit In 92, the 16-bit image data may be converted into 12-bit image data in the normalization process.
  • a predetermined number of bits for example, 16 bits
  • the 16-bit image data may be converted into 12-bit image data in the normalization process.
  • the radiation detection unit 62 detects the radiation to acquire a density correction radiation image, analyzes the density correction radiation image, and determines the main density range of the subject region. Then, various parameters for normalization processing are obtained so that the appropriate density range is obtained, and normalization processing is performed on the image data of the 16-bit radiation image read from the radiation detector 60 using the obtained various parameters. To 12-bit image data.
  • the operational amplifier 84 ⁇ / b> A is configured so that the electric signal flowing out to each data wiring 78 is within a range that can be converted into 16-bit digital data without being saturated by the A / D converter 88. It is assumed that the gain amount is adjusted to a predetermined value.
  • FIG. 15 shows a flowchart showing the flow of processing of the photographing control program when standardization processing is performed. Note that the same processing parts as those in the above-described photographing control program (see FIG. 13) are denoted by the same reference numerals and description thereof is omitted.
  • step S29 the cassette control unit 92 analyzes the image data generated in step S26, and derives appropriate values for various parameters of the normalization process.
  • the main density range of the subject region is MIN0 to MAX0 in the cumulative histogram a of the radiographic image captured under a certain imaging condition, and the imaging condition is different from the above imaging condition.
  • the main density range of the subject region is MIN1 to MAX1 in the cumulative histogram b of the radiographic image taken below.
  • the 16-bit image data that becomes the cumulative histogram indicated by a or b is converted into 12-bit image data by the normalization process, and the main area of the subject area is converted into the 16-bit image data at the time of the conversion.
  • the density ranges MIN0 to MAX0 and MIN1 to MAX1 are converted so as to become appropriate density ranges MIN2 to MAX2 in 12-bit image data, respectively.
  • FIG. 16 (2) shows the cumulative histogram a when MIN0 to MAX0 and MIN1 to MAX1 are converted to the proper density range MIN2 to MAX2 in 12-bit image data in this way. , B are shown.
  • a known technique can be used as a standardization method from 16-bit image data to 12-bit image data.
  • 16-bit image data D0 as input data is converted into 12-bit image data D1 as output based on a predetermined conversion function.
  • FIG. The conversion is performed using a linear function as indicated by a and b in (3).
  • values of Gain and Offset in which the main density range (for example, MIN0 to MAX0) of the subject area becomes the appropriate density range MIN2 to MAX2 are derived.
  • step S33 the cassette control unit 92 performs normalization processing on the 16-bit image data stored in the image memory 90 using the parameters derived in step S29 to convert the image data into 12-bit image data.
  • the converted image data is stored in the image memory 90.
  • the concentration range can be set to an appropriate concentration range.
  • step S34 the cassette control unit 92 transmits the image data to the console 42 after the conversion in step S33 stored in the image memory 90, and ends the process. At this time, among the image data stored in the image memory 90, the image data in the non-compressed transfer area is not compressed, and the image data in the compressed transfer area is irreversibly compressed and transmitted to the console 42.
  • the density range of the subject area can be set to an appropriate density range in the radiographic image subjected to the normalization process.
  • the electronic cassette 32 is the radiographic image data detected by the radiation detector 60 in step S34 described with reference to FIGS.
  • the image data in the non-compressed transfer area is sent to the console 42 without being compressed, and the image data in the compressed transfer area other than the non-compressed transfer area is irreversibly compressed and sent to the console 42. Yes.
  • the uncompressed transfer area is set based on a radiation image (hereinafter, referred to as a density correction radiation image) detected by the radiation detection unit 62 in the initial imaging of fluoroscopic imaging.
  • the electronic cassette 32 transmits the image data of the radiation image detected by the radiation detector 60 based on the setting.
  • FIG. 17 shows a flowchart showing a flow of processing of an area setting processing program executed by the CPU 92A of the cassette control unit 92 in the fluoroscopic imaging according to the first embodiment.
  • This processing program is stored in advance in a predetermined area of the memory 92B (ROM), and is executed at the time of initial imaging immediately after the start of fluoroscopic imaging.
  • step S200 the CPU 92A acquires the image data of the density correction radiation image detected by the radiation detection unit 62.
  • the CPU 92A specifies a region of interest based on the pixel value (luminance value) obtained by analyzing the density correction radiation image, information on the designated imaging region, and information on the imaging purpose.
  • the lung field region is a region of interest
  • the gastric wall region is used to detect polyps or the like generated in the stomach wall. It becomes an area of interest.
  • the distal end region of the catheter and its surrounding region are the regions of interest.
  • region as a region of interest.
  • step S202 will be described in detail.
  • a region where the luminance value is included in the range A determined in advance according to the imaging region and the imaging purpose is extracted (see also FIG. 22).
  • the range of the luminance value is determined in advance for each imaging region and each imaging purpose, and is stored in a storage unit such as the memory 92B (ROM).
  • the region extracted by the luminance value may include a region outside the region of interest. Therefore, for example, a pattern image indicating the shape of a standard region of interest for each imaging region and imaging purpose is stored in advance in a storage unit such as the memory 92B, and a radiographic image captured for the extracted region is stored.
  • the pattern matching for obtaining the similarity between the radiation image and the pattern image may be performed while changing the position and enlargement ratio of the pattern image according to the imaging region, and the region with the highest similarity may be identified as the region of interest.
  • a region surrounded by a line along the contour point may be specified as a region of interest using a known technique such as a dynamic contour extraction process such as a snakes algorithm or a contour extraction process using Hough transform. .
  • the region of interest is a lung field region
  • the threshold value the number of valleys from the maximum luminance value side as the threshold depends on the region of interest
  • Information indicating the region of interest thus identified (for example, information indicating the position, size, and shape of the region of interest) is stored in a predetermined region of storage means such as the storage unit 92C.
  • a value corresponding to the resolution of the radiation detector 62 may be stored, but it may be converted into a value corresponding to the resolution of the radiation detector 60 and stored.
  • the lung field region is exemplified here as the region of interest, the present invention is not limited to this, and the region of interest may be a soft tissue region or a bone tissue region depending on the imaging purpose.
  • the CPU 92A specifies the MUST area.
  • a diseased part where a tumor or the like exists is an area that must be displayed in real time without image deterioration, and is an area where image data should be transferred without being compressed regardless of the frame rate. In this embodiment, this area is called a MUST area.
  • a region having a predetermined position, size, and shape determined from the imaging region and the imaging purpose may be specified as the MUST region.
  • information on the position, size, and shape of a standard MUST region with respect to the region of interest is stored in advance in a storage unit such as the memory 92B for each imaging region and imaging purpose, and this is referred to. You may do it.
  • a doctor or the like may input information on the position and size of the predicted disease in advance to the console 42 as imaging conditions, and specify the area indicated by the information as the MUST area.
  • the region may be identified as a MUST region (FIG. 18). See also).
  • a feature amount such as a disease is determined in advance
  • information indicating the feature amount is stored in advance in storage means such as the memory 92B, and the similarity to the feature amount is determined in advance.
  • information indicating the pattern image is stored in a storage unit such as the memory 92B, and pattern matching for obtaining a similarity with the pattern image is performed.
  • An area having a similarity equal to or greater than a predetermined threshold may be specified as the MUST area.
  • the MUST area specified in this way may be modified according to circumstances. For example, when a radiographic image for density correction is transmitted from the electronic cassette 32 to the console 42, and a doctor visually confirms the subject image for density correction displayed on the display 100, and a disease such as a tumor is larger than expected. Alternatively, when there is another disease, a doctor or the like may directly operate the operation panel 102 to correct the MUST area.
  • Information indicating the MUST area finally obtained in this way (for example, information indicating the position, size, and shape of the MUST area) is stored in a predetermined area of the storage unit 92C.
  • the MUST region exists within the region of interest identified in step S202.
  • FIG. 19 shows an example of the identified region of interest and MUST region.
  • pixels corresponding to the respective sensor units 146 of the radiation detection unit 62 (hereinafter referred to as “areas” in order to be distinguished from the pixels 74 corresponding to the sensor unit 72 of the radiation detector 60) are 16.
  • areas pixels corresponding to the respective sensor units 146 of the radiation detection unit 62
  • any number from 1 to 256 is assigned to each area.
  • An area number may be used as information indicating the region of interest and the MUST region.
  • step S206 the CPU 92A determines an upper limit value S of the number of areas that can be transferred without compression based on the designated frame rate.
  • the upper limit value of the amount of data that can be transferred without compression when the radiographic image detected by the radiation detector 60 of the electronic cassette 32 is transferred at a predetermined transfer rate and displayed without display delay.
  • Each frame rate is stored in advance in the memory 92B, and this is determined.
  • FIG. 20 shows an example of the upper limit value stored in the memory 92B.
  • the information shown in FIG. 20 is assumed to be stored in the memory 92B of the electronic cassette 32. Therefore, in step S206, the maximum number of areas S corresponding to the designated frame rate is determined based on this information.
  • the upper limit value of the amount of data that can be transferred without compression is the upper limit value of the number of areas that can be transferred without compression, but it is sufficient that the data amount (size) of the area can be determined.
  • the number the number of pixels, the area, or the upper limit value of the data amount itself may be stored for each frame rate.
  • the CPU 92A (as a transfer area setting unit) sets a rectangular area including the identified MUST area and having the number of areas equal to or less than S as an uncompressed transfer area.
  • Information indicating the non-compressed transfer area (for example, information indicating the position, size, and shape of the non-compressed transfer area) is stored in a predetermined area of the storage unit 92C, similarly to the region of interest and the MUST area.
  • the area number of the radiation detection unit 62 may be stored as information indicating the uncompressed transfer area.
  • FIG. 21 and FIG. 22 an example of the uncompressed transfer area set according to the present embodiment is indicated by a broken line. Note that the rectangular area surrounded by the thick solid line in FIGS. 21 and 22 is an uncompressed transfer area when it is set to include all of the region of interest regardless of the frame rate.
  • the electronic cassette 32 corresponds to the uncompressed transfer area in the image data of the radiographic image detected by the radiation detector 60 in step S34 (see FIGS. 13 and 15) according to the uncompressed transfer area information.
  • the image data is transmitted to the console 42 without being compressed, and the image data in the area corresponding to the compressed transfer area other than the non-compressed transfer area is compressed and transmitted to the console 42.
  • step S208 the number of areas is determined. However, the number of areas is converted into the number of pixels 74 of the radiation detector 60, and the number of pixels 74 corresponding to the upper limit value S of the number of areas is determined based on the number of pixels 74.
  • the compression transfer area may be determined and set. The number of areas may be converted into an area, and the uncompressed transfer area may be determined and set based on the area of the area corresponding to the upper limit value S of the number of areas.
  • the radiographic image obtained by fluoroscopic imaging is real-time without deterioration in image quality.
  • An area to be displayed can be reliably displayed in real time without deterioration in image quality.
  • detection of the motion region is performed as follows.
  • a threshold value of a motion amount that is recognized as a motion amount as a moving image is stored in the memory 92B in advance, and digital data (radiation for density correction) sequentially input from the signal detection unit 162 during fluoroscopic imaging.
  • Motion detection is performed using the image data of the image, and when a region in which the amount of motion detected in the region of interest is greater than or equal to the above threshold is generated, the region is extracted as a motion region, Information indicating the position, size, and shape of the motion region is stored in the storage unit 92C. Note that in motion detection, when a change in luminance value that is greater than or equal to a threshold value occurs, a region in which the change has occurred may be used as a motion region.
  • the image data used when detecting the motion region in this manner may be the image data of the density correction radiation image detected by the radiation detection unit 62, but the resolution of the image data is reduced. Low resolution image data may be used. Further, information indicating the position, size, and shape of the detected motion region may be stored in the storage unit 92C as information indicating the area number of the radiation detection unit 62.
  • FIG. 23 is a flowchart showing the flow of processing of the area setting change processing program executed by the CPU 92A of the cassette control unit 92 in the second embodiment. This program is executed when a motion region having a large amount of motion outside the uncompressed transfer region is generated in the region of interest specified in step S202 of the region setting process described in the first embodiment during fluoroscopic imaging.
  • step S300 the CPU 92A (as the transfer area setting unit) changes the setting of the uncompressed transfer area so as to include the MUST area and the motion area.
  • the minimum rectangular area including the motion area and the MUST area in the region of interest is determined and changed as an uncompressed transfer area.
  • Information indicating the non-compressed transfer area after the change is stored in a predetermined area of the storage unit 92C.
  • the area number of the radiation detection unit 62 may be stored as information indicating the uncompressed transfer area after the change.
  • 24 and 25 show examples of changing the uncompressed transfer area with broken lines. As shown in FIG. 24, three areas are detected as motion areas in the region of interest described in the first embodiment, and one of the three areas is an uncompressed transfer area before the change. Not included. Therefore, in this example, the uncompressed transfer area is expanded so that the motion area not included in the uncompressed transfer area before the change is included in the uncompressed transfer area.
  • the motion area is an area that has undergone a large change, it is a natural area to be visually confirmed without deterioration in image quality.
  • the MUST area is an important area and is removed from the uncompressed transfer area. It is not possible. In particular, in a situation where a single person is not watching the display but a plurality of people (doctors, engineers, etc.) are watching the display, a person who keeps an eye on the MUST area, not the movement area that occurred during shooting. May be present. Therefore, in this embodiment, the non-compressed transfer area is changed so that the motion area is included in the non-compressed transfer area without removing the MUST area, which is an important area, from the non-compressed transfer area.
  • step S302 the CPU 92A determines whether or not the number of areas in the non-compressed transfer area after the change is greater than the upper limit value S of the number of areas that can be transferred without compression. If a negative determination is made here, the process proceeds to step S304, and imaging is continued without changing the frame rate and the irradiation period.
  • step S302 the process proceeds to step S320. If the number of non-compressed transfer areas after the change is greater than S, real-time display may not be possible unless the frame rate is reduced. Therefore, in step S320, the CPU 92A changes the frame rate and the irradiation period.
  • the memory 92B stores in advance information on the upper limit value of the number of areas that can be transferred without compression for each frame rate (see also FIG. 20). Based on this information, the CPU 92A obtains a frame rate whose upper limit is the number of non-compressed transfer areas after the change, and determines a frame rate equal to or lower than the frame rate as the changed frame rate. To do. As apparent from FIG. 20, since the number of areas in the non-compressed transfer area after the change exceeds S, the frame rate after the change is lower than the frame rate before the change.
  • each image may become a frame-feed image in which movement has stopped.
  • the CPU 92A (as the second changing unit) keeps the radiation dose per unit time low in one pulse irradiation, Within each frame period for capturing each frame image, the irradiation period is changed to a longer period than before the change.
  • the human eye has a time resolution of about 50 ms to 100 ms, and blinking of light shorter than this time is perceived as being continuously lit.
  • Table 1 shows the results of evaluation with the frame rate set to 5 fps and the ratio of the pulse irradiation period within one frame period (1/5 second) changed.
  • the frame period must include a reading period for reading out the accumulated charges.
  • This reading period needs about 20% of the frame period.
  • the upper limit of the period during which radiation can be irradiated within the frame period in pulse irradiation is about 80%.
  • the ratio of the irradiation period to the frame period needs to be within the range of 12.5% to 80% in order to suppress the frame drop feeling to an acceptable level, and 33% to 80%. More preferably, it is within the range.
  • the ratio of the radiation irradiation period to each frame period corresponding to the fluoroscopic frame rate is changed to 80% (here, the ratio of the irradiation period before the change is less than 80%).
  • Change the exposure conditions such as tube voltage and tube current, and change the radiation dose per unit time.
  • the minimum dose necessary for radiographic image capture may not be ensured. Therefore, by dividing the minimum irradiation amount by the changed irradiation period, the minimum irradiation amount per unit time necessary for radiographic image acquisition is obtained, and the radiation irradiation amount per unit time can be obtained.
  • Change exposure conditions such as tube voltage and tube current.
  • the electronic cassette 32 transmits the changed exposure condition to the console 42.
  • the console 42 transfers the transmitted exposure conditions to the radiation generator 34. Thereafter, the console 42 transmits a synchronization signal according to the changed exposure condition, the radiation generator 34 emits radiation according to the changed exposure condition, and the electronic cassette 32 changes to the changed exposure condition. Based on this, the image is read out as described above.
  • a radiographic image is not viewed by a single doctor but may be viewed simultaneously by a plurality of people such as doctors and engineers. Therefore, even when the uncompressed transfer area is changed according to the amount of movement as described above, there are people who want to check the area where the movement has occurred, and some people who want to keep an eye on the MUST area and its vicinity. . Therefore, changing the uncompressed transfer area regardless of the MUST area has a problem in a situation where a plurality of persons confirm the radiation image.
  • the MUST region is not removed and the uncompressed transfer region is changed.
  • the irradiation period when the frame rate is lowered is not limited to the above, and may be obtained as follows, for example.
  • the frame rate threshold value is stored in the memory 92B in advance, and when the fluoroscopic frame rate is equal to or lower than the threshold value, the irradiation period of the pulse irradiation within the frame period is changed.
  • two frame rate threshold values (first frame rate threshold value, second frame rate threshold value) are stored.
  • the first frame rate threshold may be a frame rate at which the majority of people do not feel flicker.
  • the first frame rate threshold may be 15 fps (Frame Per Second) or more and 60 fps or less, and more preferably 15 fps or more and 30 fps or less.
  • the second frame rate threshold may be a frame rate at which the majority of people feel flicker.
  • the second frame rate threshold may be 5 fps or more and less than the first frame rate threshold, and more preferably 5 fps or more and less than 15 fps.
  • the first frame rate threshold is, for example, 30 fps
  • the second frame rate threshold is, for example, 15 fps.
  • the first frame rate threshold is, for example, 24 fps
  • the second frame rate threshold is, for example, It may be 5 fps.
  • a radiographic image is captured in synchronization with the pulse irradiation while performing pulse irradiation during a predetermined irradiation period.
  • This irradiation period is determined as a time during which stable shooting can be performed even at the maximum frame rate that can be shot by the shooting system 18 and stored in the HDD 110 as an initial value of the irradiation period.
  • the ratio of the irradiation period to the frame period is changed to 50%, and the radiographic image is captured in synchronization with the pulse irradiation while performing the pulse irradiation.
  • the imaging frame rate is equal to or lower than the second frame rate threshold, the ratio of the irradiation period to the frame period is changed to 80%, and pulse irradiation is performed, and a radiographic image is acquired in synchronization with the pulse irradiation.
  • FIG. 26 is a flowchart showing the flow of processing of the irradiation period determination processing program executed by the CPU 92A (as the second changing unit).
  • step S410 in the figure the CPU 92A determines whether or not the frame rate after changing the fluoroscopic imaging is equal to or higher than a first frame rate threshold (for example, 30 fps). If the determination is affirmative, the process proceeds to step S412. If the determination is negative, the process proceeds to step S414.
  • a first frame rate threshold for example, 30 fps
  • step S412 the CPU 92A determines the irradiation period of each pulse irradiation as a period indicated by the irradiation period initial value.
  • step S414 the CPU 92A determines whether or not the frame rate after changing the fluoroscopic imaging is equal to or lower than a second frame rate threshold (for example, 15 fps). If the determination is affirmative, the process proceeds to step S416. When it becomes negative determination, it transfers to step S420.
  • a second frame rate threshold for example, 15 fps
  • step S416 the CPU 92A determines that the radiation period of each pulse irradiation is 50% of the frame period corresponding to the designated frame rate.
  • the exposure conditions such as tube voltage and tube current are also changed so as to reduce the radiation dose per unit time as the irradiation period is changed.
  • step S420 the CPU 92A determines the radiation period of each pulse irradiation as a period of 80% of the frame period corresponding to the designated frame rate.
  • the exposure conditions such as tube voltage and tube current are also changed so as to reduce the radiation dose per unit time as the irradiation period is changed.
  • step S422 the CPU 92A transmits the determined irradiation period and the changed frame rate, tube voltage, tube current, and the like as the exposure conditions to the console 42, and ends the irradiation period determination processing program.
  • the irradiation period program illustrated in FIG. 25 may be executed to obtain and use the irradiation period corresponding to the frame rate.
  • the changed non-compressed transfer area is changed to the original uncompressed transfer area before the change. You may make it return to.
  • the photographing system 18 is provided with detection means (gaze degree detection means) for detecting the line-of-sight direction of the people who are viewing the display 100, and the gaze area of the people viewing the display 100 is out of the movement region. Configure to be detectable.
  • the detection means analyzes imaging data such as a camera that captures a person who views the display 100 and eye region image data captured by the imaging means, and derives each of the gaze directions of the person viewing. And derivation means.
  • imaging data such as a camera that captures a person who views the display 100 and eye region image data captured by the imaging means, and derives each of the gaze directions of the person viewing.
  • derivation means for example, an IRED (infrared light emitting diode) is installed on the display 100, the eyeball of the detection target person is irradiated with infrared light with the IRED, and the anterior segment image of the detection target is imaged and received It may be a means for detecting by estimating the position of the IRED cornea reflection image and pupil circle from the output signal of the infrared sensor.
  • the detection means for detecting the line-of-sight direction is not limited to these, and various known techniques can be employed.
  • the gaze degree is calculated from the ratio of.
  • a program for calculating the gaze degree and executing the processing to be transmitted to the electronic cassette 32 may be included in the program executed by the CPU 104 of the console 42.
  • the detection result of the line-of-sight direction may be transmitted from the console 42 to the electronic cassette 32 and the gaze degree may be calculated by the electronic cassette 32.
  • FIG. 27 is a flowchart showing the flow of processing of the area setting change processing program using the gaze degree. As in FIG. 23, this program is executed when a motion region having a large motion amount outside the uncompressed transfer region is generated in the region of interest specified in step S202 during fluoroscopic imaging.
  • FIG. 27 the same processing parts as those in the area setting change processing program of FIG. On the other hand, it is assumed that the detection of the gaze direction and the calculation of the gaze degree are started at the time when the motion region occurs and are performed in parallel with this program.
  • the CPU 92A determines whether or not the gaze degree with respect to the motion region exceeds the threshold value in step S306.
  • the degree of gaze of the plurality of people is determined. If even one person's gaze degree exceeds the threshold, an affirmative determination is made here. Further, if all the gaze degrees of a plurality of people are below the threshold value, a negative determination is made.
  • a gaze degree for each of the motion areas newly added to the uncompressed transfer area is determined, and if even one gaze degree exceeds the threshold, An affirmative determination is made and a negative determination is made if all the gaze degrees are below the threshold.
  • step S306 the uncompressed transfer area is maintained unchanged.
  • step S306 the CPU 92A proceeds to step S308.
  • step S308 the CPU 92A (as the transfer area setting unit) changes the non-compressed transfer area to the area before change and continues shooting. Needless to say, the area before the change includes the MUST area.
  • step S320 the CPU 92A determines whether or not the gaze degree with respect to the motion area exceeds the threshold value in step S322, as in step S306. During the period in which an affirmative determination is made in step S322, the uncompressed transfer area is maintained unchanged.
  • step S322 the CPU 92A changes the uncompressed transfer area to the area before change. Further, the CPU 92A (as the third changing unit) returns the exposure conditions such as the frame rate changed in step S320 to the exposure conditions before the change, and transmits the exposure conditions to the console 42. The console 42 transfers the received exposure conditions to the radiation generator 34. Thereafter, the console 42 transmits a synchronization signal to the radiation generator 34 and the electronic cassette 32 at a period corresponding to the restored frame rate. In addition, the electronic cassette 32 reads an image as described above based on the restored exposure condition, and the radiation generator 34 emits radiation according to the exposure condition.
  • the uncompressed transfer area can be automatically restored, and the reduced frame rate can be restored to the original.
  • a smoother image can be displayed compared to a state in which the rate is lowered, and the MUST area is always included in the non-compressed transfer area, so that the image quality is not always deteriorated in real time regardless of the occurrence of the moving area. Can be displayed.
  • step S323 A step of determining whether or not the threshold value is greater than a threshold value (threshold value for detecting body movement and greater than the threshold value used in motion detection) is illustrated in FIG. 17 when an affirmative determination is made in step S323.
  • the region setting process may be re-executed.
  • a diaphragm mechanism that adjusts the irradiation region of the radiation X may be provided.
  • the radiation generator 34 is provided with a diaphragm device (collimator) 500 and a diaphragm controller 502.
  • the diaphragm device 500 is provided between the radiation source 130 and the subject, and adjusts the irradiation region of the radiation X.
  • the diaphragm control unit 502 includes a microcomputer, and controls the aperture state of the diaphragm device 500 based on the irradiation area information received from the console 42 (this control is referred to as diaphragm control).
  • the console 42 may control the non-irradiated region to display a radiation image (still image) obtained before performing aperture control.
  • a transfer stop request for image data in the non-irradiation area may be transmitted from the console 42 to the electronic cassette 32 together with information on the irradiation area (or non-irradiation area). Thereby, the amount of data to be transferred from the electronic cassette 32 can be reduced.
  • the radiation X irradiation area includes at least the MUST area. Therefore, the irradiation region may be a MUST region, or a MUST region and a peripheral region of the MUST region. Further, the irradiation region of the radiation X may be a region of interest or may be a region including a peripheral region of the region of interest. In addition, the irradiation region of radiation X also includes a region in which a lesion is suspected (this region is not necessarily a disease region; hereinafter, referred to as a lesion candidate region). It is good also as an irradiation area.
  • a specific example of an initial setting process for setting an irradiation area at the time of initial imaging will be described.
  • FIG. 31 shows a flowchart showing a flow of processing of an initial setting processing program related to aperture control, which is executed by the CPU 104 of the console 42.
  • this processing program is stored in advance in a predetermined area of the ROM 106 or the HDD 110, and is executed at the time of initial imaging immediately after the start of fluoroscopic imaging.
  • this processing program is started, it is assumed that reception of image data of a subject image from the electronic cassette 32 has already started and display based on the image data has started.
  • the aperture state of the aperture stop device 500 is an initial state with no aperture. Therefore, as shown in FIG. 35, the entire region to be imaged is imaged without limiting the irradiation area, and the imaged subject image is transmitted to the console 42.
  • step S600 the CPU 104 (as the irradiation region setting unit) executes a lesion candidate region setting process.
  • a lesion candidate area is set.
  • the lesion candidate area may not be set in this lesion candidate area setting process.
  • the CPU 104 sets the radiation X irradiation area.
  • the irradiation region can be, for example, a rectangular region including a MUST region or a region of interest and a lesion candidate region set by a lesion candidate region setting process.
  • the CPU 104 may acquire information indicating the position of the MUST region or the region of interest from the electronic cassette 32, or the CPU 104 itself may specify the MUST region or the region of interest.
  • the irradiation region is limited to only the MUST region (or the MUST region and the lesion candidate region), a real-time radiation image can be obtained only in the narrowed region. Since it is easier to check the MUST area itself for the area around the MUST area, it is preferable to set the irradiation area so that the area around the MUST area is included. Similarly, the irradiation area may be set so that the area around the lesion candidate area is included.
  • step S604 the CPU 104 transmits information on the set irradiation region to the radiation generator 34, and causes the diaphragm control unit 502 to perform diaphragm control.
  • the aperture control unit 502 irradiates the set irradiation region with the radiation X based on the irradiation region information transmitted from the console 42, and the region other than the set irradiation region receives the radiation X.
  • the diaphragm device 500 is controlled so as not to be irradiated.
  • step S606 the CPU 104 (as a transmission control unit) performs transfer control of image data. Specifically, the CPU 104 transmits to the electronic cassette 32 a request to stop transferring image data of the non-irradiation area together with information on the irradiation area (or non-irradiation area). Upon receiving this request, the electronic cassette 32 transfers the image data to the console 42 for the irradiation area, and stops transferring the image data for the non-irradiation area. When the irradiation area includes the non-compression transfer area and the compression transfer area, the electronic cassette 32 transmits the image data in the non-compression transfer area of the irradiation area without compression, and the image in the compression transfer area. Data is compressed before being sent.
  • step S608 the CPU 104 performs display control. Specifically, the CPU 104 displays an image in real time based on the image data transferred from the electronic cassette 32 for the irradiation area, and an image (still image) taken immediately before applying the aperture for the non-irradiation area.
  • the display driver 112 is controlled so that is displayed.
  • FIG. 32 is a flowchart illustrating an example of a lesion candidate area setting process.
  • step S610 the CPU 104 determines whether or not a region in the subject image displayed on the display 100 is designated by operating the operation panel 102 by a doctor or the like.
  • a region in the subject image displayed on the display 100 is designated by operating the operation panel 102 by a doctor or the like.
  • a plurality of areas may be designated.
  • the program may be configured so that the area can be specified in units of areas.
  • the area designation is accepted by the CPU 104 until a predetermined time (area designation waiting time) elapses after the execution of the initial setting process or the lesion candidate area setting process. That is, the CPU 104 does not shift from step S610 to the next step until the area designation waiting time elapses.
  • a predetermined time area designation waiting time
  • the candidate lesion region can be determined by observing the respiratory dynamics in several cycles. Therefore, for example, a time corresponding to a plurality of cycles that can be determined is set in advance as the designated waiting time, and the CPU 104 waits for the area designation by continuing the designated waiting time.
  • the heart rate per unit time of the subject may be measured in advance, and the designated waiting time may be calculated and set based on the heart rate.
  • step S610 If the CPU 104 makes an affirmative determination in step S610, it sets the designated region as a lesion candidate region in step S612. The CPU 104 displays the position of the set lesion candidate area on the display 100. If the CPU 104 makes a negative determination in step S610, it skips step S612.
  • step S614 the CPU 104 determines whether or not the operation panel 102 is operated by a doctor or the like and an instruction to cancel the designation of the lesion candidate area has been issued.
  • an affirmative determination is made in step S614 if a cancellation instruction is issued for at least one of them.
  • the cancellation instruction is accepted by the CPU 104 until a predetermined time (cancellation cancellation waiting time) elapses after the radiation image is displayed on the display 100. That is, the CPU 104 does not proceed from step S614 to the next step until the specified waiting time has elapsed.
  • the user can visually confirm the subject image after designating a certain region to be a lesion candidate region, and can cancel the designation if it is determined that it is unnecessary as a result of the confirmation.
  • step S614 If the CPU 104 makes an affirmative determination in step S614, it cancels the setting of the area instructed to be canceled in step S616. As a result, the cancel-instructed area is excluded from the lesion candidate area.
  • the lesion candidate area setting process ends.
  • the lesion candidate area setting process may be completed when a negative determination is made in step S610.
  • the CPU 104 sets a rectangular region including the lesion candidate region set as described above and the region of interest as an irradiation region in step S602 of FIG.
  • FIG. 36 shows an example of a radiation irradiation region. If no lesion candidate area is set (that is, the area is not specified or the area designation is canceled), for example, as shown in FIG. It is good. As described above, instead of the region of interest, a rectangular region including a MUST region may be used as the irradiation region.
  • FIG. 33 is a flowchart illustrating another example of a lesion candidate area setting process.
  • the lesion candidate area setting process shown in FIG. 33 is started until a predetermined time elapses after the acquisition of the image data of the subject image photographed by the electronic cassette 32 without the irradiation area being narrowed down. Shall not be.
  • the lesion candidate region can be determined by observing the respiratory dynamics in several cycles. Therefore, for example, a time corresponding to a plurality of cycles that can be determined is set in advance, and the CPU 104 acquires image data of a radiographic image for at least the set time, and then performs this lesion candidate region setting process. It is assumed that the process of step S620 is performed.
  • step S620 the CPU 104 determines whether or not there is an area where the luminance value is within the set range in each acquired subject image.
  • a range of luminance values to be extracted as a lesion candidate region is set in advance, and the set range is referred to as a setting range.
  • the brightness value of each of the subject images taken within the predetermined time is confirmed.
  • step S622 When the CPU 104 makes an affirmative determination in step S620, in step S622, it sets an area whose luminance value is within the setting range as a lesion candidate area. For example, if there is a subject image including a block having a luminance value within the set range among the subject images for the preset time, an affirmative determination is made in step S620, and in step S622, the block is determined as a lesion candidate region.
  • the program may be configured so that the area can be set in units of areas.
  • the luminance values of all the pixels included in the lesion candidate area may not be within the set range. For example, if there is an area where the luminance value of the number of pixels equal to or greater than a predetermined ratio is within the set range, an affirmative determination may be made in step S620. Further, the region set as the lesion candidate region may be a region having a size larger than a preset size.
  • step S620 if a negative determination is made in step S620, the process in step S622 is skipped, and the lesion candidate area setting process ends.
  • an example has been described in which an area in which the luminance value is within the setting range is set as a lesion candidate area, but the conditions for setting the lesion candidate area are not limited to this, and the imaging purpose, imaging site, etc. Can be determined according to
  • the irradiation region setting may be updated by performing a lesion candidate region setting process.
  • FIG. 34 is a flowchart showing an example of the shooting operation setting process performed after the initial setting process. This setting process during shooting operation is started when the initial setting process is completed.
  • step S650 the CPU 104 determines whether or not a predetermined time has elapsed. If the CPU 104 determines in step S650 that the predetermined time has elapsed, the CPU 104 proceeds to step S652.
  • step S652 the CPU 104 returns the aperture device 500 to the initial state. That is, as shown in FIG. 35, the diaphragm device 500 is reset so that an image is taken without narrowing the irradiation area.
  • step S654 the CPU 104 performs transfer control of image data. Specifically, the CPU 104 transmits a transfer request so that image data of the entire imaging region that is imaged without narrowing the irradiation area is transmitted.
  • the electronic cassette 32 transfers the image data to the console 42 in accordance with the transfer request. At that time, the electronic cassette 32 transmits the image data in the non-compressed transfer area without compression in the image data to be transmitted, and compresses and transmits the image data in the compressed transfer area.
  • step S656 the CPU 104 controls the display driver 112 so that the entire subject image when the aperture is not applied is displayed in real time based on the image data transmitted from the electronic cassette 32.
  • step S658 the CPU 104 performs a lesion candidate area setting process as described with reference to FIGS. As a result, a new lesion candidate region may be found, or a region already set as a lesion candidate region may be excluded from the lesion candidate region.
  • the CPU 104 resets the irradiation region in step S660 after the lesion candidate region setting process in step S658.
  • the method for resetting the irradiation area is the same as that in step S602, and thus the description thereof is omitted.
  • step S662 the CPU 104 transmits information on the newly set irradiation area to the radiation generation apparatus 34, and causes the diaphragm control unit 502 to perform diaphragm control.
  • step S664 the CPU 104 controls transfer of image data of the electronic cassette. Specifically, the CPU 104 transmits a transfer stop request for image data in the non-irradiation area to the electronic cassette 32 together with information on the irradiation area or the non-irradiation area.
  • step S666 the CPU 104 displays an image in real time based on the image data transferred from the electronic cassette 32 for the irradiation region, and an image (still image) taken immediately before the aperture is applied to the non-irradiation region.
  • the display driver 112 is controlled so as to be displayed.
  • step S668 the CPU 104 determines whether or not a predetermined time has elapsed. If the CPU 104 determines in step S668 that the predetermined time has not elapsed, the process proceeds to step S670. In step S670, CPU 104 determines whether or not shooting has ended.
  • step S670 determines in step S670 that shooting has not ended
  • the process returns to step S668.
  • the CPU 104 determines in step S670 that shooting has ended, it ends the setting process during shooting operation. Furthermore, when the CPU 104 determines in step S668 that the predetermined time has elapsed, the CPU 104 returns to step S652.
  • the lesion candidate area setting process by performing the lesion candidate area setting process at predetermined time intervals, for example, when it is determined that the area set as the lesion candidate area is not a lesion candidate area after the setting, the lesion Since the irradiation area not including the candidate area can be set, the exposure dose of the subject can be reduced.
  • the lesion candidate area for example, the radiation X irradiation area is changed from the area shown in FIG. 36 to the area shown in FIG.
  • a region that has not been set as a lesion candidate region in the initial setting process can be set as a lesion candidate region during imaging.
  • the exposure dose can be reduced by setting the irradiation region and performing aperture control.
  • the program may be configured to be executed while skipping the lesion candidate area setting process in step S658 and the irradiation area resetting in step S660. That is, although the lesion candidate area set in the lesion candidate area setting process of the initial setting process is not changed, the real-time display and the still image display of the non-irradiation area can be switched at predetermined time intervals.
  • the above embodiment does not limit the invention according to the claims (claims), and all the combinations of features described in the embodiment are essential for the solution means of the invention. Is not limited.
  • the embodiments described above include inventions at various stages, and various inventions can be extracted by appropriately combining a plurality of disclosed constituent elements. Even if some constituent requirements are deleted from all the constituent requirements shown in the embodiment, as long as an effect is obtained, a configuration from which these some constituent requirements are deleted can be extracted as an invention.
  • transfer of image data from the electronic cassette 32 to the console 42 is generally more time-consuming for wireless communication than wired communication that can realize high-speed communication such as an optical fiber.
  • the non-compressed transfer area setting process and the area setting changing process described in the above embodiments are performed, and the uncompressed transfer area is processed.
  • the configuration of transmitting without compression and transmitting the compressed transfer area with lossless compression is particularly effective.
  • switching means for switching between wired communication and wireless communication is provided so that the operator can change the communication method. If the communication method is switched to wireless communication when the switchable configuration is configured, one of the area setting process and the area setting change process described in each of the above embodiments is performed. If the non-compressed transfer area is transmitted without being compressed, and the compressed transfer area is reversibly compressed and transmitted, for example, regardless of the frame rate, it is switched to wired communication.
  • a rectangular area including a region of interest (for example, an area indicated by a thick frame line in FIG. 21) may be always set as an uncompressed transfer area.
  • the electronic cassette 32 is provided with a wireless communication unit 94 as an example of a transmission unit that transmits image data to the console 42, and the cassette control unit 92 (CPU 92A) of the electronic cassette 32 sets the area.
  • the wireless cassette 94 transmits the image data in the non-compressed transfer area to the console 42 without being compressed, and the image data in the compressed transfer area is reversible.
  • the imaging system 18 that compresses and transmits to the console 42 has been described, but is not limited thereto.
  • the imaging system 18 may have a mobile terminal device provided with a display unit separately from the console 42.
  • the electronic cassette 32 transmits not only the console 42 but also the portable terminal device to the console 42 without compressing the image data in the uncompressed transfer area by the wireless communication unit 94, and The image data can be reversibly compressed and transmitted to the console 42.
  • the radiation generating device 34 is provided with a diaphragm mechanism (a diaphragm device 500 and a diaphragm controller 502) that narrows the radiation irradiation region.
  • the image data transmitted from the electronic cassette 32 to the communication control device 700 or the console 42 after narrowing the irradiation area can be only the image data of the irradiation area.
  • FIG. 38 schematically shows a configuration example of the imaging system 181 including the communication control device.
  • components other than the wireless communication unit 118 and the display 100 of the console 42 are schematically shown as a console body 800.
  • the imaging system 181 also includes a radiation generator 34, which is not shown here.
  • the electronic cassette 32 is connected to the communication control device 700 by wire. The electronic cassette 32 transmits the entire image data of the subject image to the communication control device 700 without being compressed.
  • the CPU included in the communication control device 700 that has received the image data from the electronic cassette 32 by wired communication performs the region setting process and the region setting change process, and wirelessly communicates with the console 42 via the wireless communication unit 700A. Transfer image data by communication.
  • the communication control device 700 transmits the image data in the uncompressed transfer area to the console 42 without being compressed, and transmits the image data in the compressed transfer area to the console 42 after lossless compression.
  • the console 42 receives image data by the wireless communication unit 118 and displays a subject image on the display 100 based on the received image data.
  • the photographing system may further include a mobile terminal device provided with a display unit.
  • FIG. 39 schematically illustrates a configuration example of an imaging system 182 including the communication control device 700 and the mobile terminal device 900.
  • the imaging system 182 also includes a radiation generator 34, which is not shown here.
  • the mobile terminal device 900 includes a display unit 900A such as a touch panel display and a wireless communication unit 900B for performing wireless communication with an external device.
  • components other than the wireless communication unit 118 and the display 100 of the console 42 are schematically shown as a console body 800.
  • the communication control device 700 is connected to the electronic cassette 32 and the console 42 by wire.
  • the electronic cassette 32 transmits the entire image data of the subject image to the communication control device 700 without being compressed.
  • the CPU included in the communication control apparatus 700 that has received the image data from the electronic cassette 32 by wired communication performs the area setting process and the area setting change process.
  • the image data of the entire area is transmitted without compression without distinction of the transfer area, and is transmitted to the portable terminal device 900 without compression for the uncompressed transfer area of the image data of the subject image,
  • the compression transfer area is transmitted with lossless compression.
  • the portable terminal device 900 displays an image on the display unit 900A based on the received image data.
  • the communication control device 700 also transmits the non-compressed transfer area of the image data of the subject image without compression to the console 42 and transmits the compressed transfer area after lossless compression. Good.
  • the communication control device 700 illustrated with reference to FIGS. 38 and 39 may be built in or integrally provided in the electronic cassette 32.
  • FIG. 40 schematically illustrates a configuration example of the imaging system 183 when the console 42 receives image data from the electronic cassette 32 by wired communication and transfers image data from the console 42 to the mobile terminal device 900 by wireless communication.
  • the imaging system 183 also includes a radiation generator 34, which is not shown here.
  • the electronic cassette 32 and the console 42 are connected by wire.
  • the electronic cassette 32 transmits uncompressed image data of the entire subject image to the console 42.
  • the CPU 104 of the console main body 800 of the console 42 performs the region setting process and the region setting change process, and transmits image data to the mobile terminal device 900 via the wireless communication unit 118 by wireless communication.
  • the image data in the uncompressed transfer area is transmitted to the mobile terminal device 900 without being compressed, and the image data in the compressed transfer area is reversibly compressed and transmitted to the mobile terminal device 900.
  • the mobile terminal device 900 displays an image on the display unit 900A based on the received image data.
  • the diaphragm mechanism (the diaphragm device 500 and the diaphragm control) that narrows the radiation irradiation area.
  • the image data transmitted from the electronic cassette 32 to the communication control device 700 or the console 42 after narrowing the irradiation region may be only the image data of the irradiation region. it can.
  • the area setting process and the area setting changing process may be performed by any of the communication control device 700, the electronic cassette 32, and the console 42, and the apparatus that performs the process is not particularly limited.
  • the frame rate is reduced to a frame rate having the upper limit of the number of areas in the non-compressed transfer area, and the irradiation period is changed according to the frame rate to perform imaging. May be.
  • the present invention is applied to the electronic cassette 32 which is a portable radiation imaging apparatus.
  • the present invention is not limited to this, and a stationary radiation imaging apparatus. You may apply to.
  • the gain amount of the operational amplifier 84A is adjusted or the parameter of the normalization process is adjusted has been described.
  • the present invention is not limited to this.
  • both the gain amount of the operational amplifier 84A and the parameter of the normalization process may be adjusted, and further, the parameter of another process may be adjusted.
  • the linear function is used as the conversion function of the normalization processing
  • the present invention is not limited to this.
  • a conversion function represented by a high-order function such as a quadratic function or a cubic function
  • a plurality of assumed cumulative histograms and a lookup table corresponding to each of the cumulative histograms are prepared, and a lookup table corresponding to the one that is close to the obtained cumulative histogram from the assumed cumulative histograms. May be determined as the normalization processing characteristics, and the image data may be converted based on the lookup table.
  • the scintillator 148 is formed in the radiation detection unit 62
  • the present invention is not limited to this.
  • the radiation detector 60 detects the radiation without providing the scintillator 148 in the radiation detector 62 as shown in FIG. It is good also as what attaches to the surface on the opposite side to the TFT substrate 66 of the device 60 (surface on the scintillator 71 side), and each sensor part 146 of the radiation detection part 62 concerned detects the light of the scintillator 71.
  • the scintillator 148 becomes unnecessary, and thus the radiation detection unit 62 can be formed thinner.
  • the radiation detector 62 is provided on the surface opposite to the TFT substrate 66 of the scintillator 71. Since the radiation X passes through the radiation detector 60 after passing through the radiation detector 60, it is possible to prevent the radiation image taken by the radiation detector 60 from being affected by the provision of the radiation detector 62.
  • the radiation detector 62 may be attached to the surface of the radiation detector 60 on the TFT substrate 66 side.
  • the radiation X may be incident from above or below in FIG. 29.
  • the sensor unit 146 performs organic photoelectric conversion in order to suppress radiation absorption by the sensor unit 146 of the radiation detection unit 62. It is preferable to form with a photoelectric conversion film containing the material.
  • the radiation detector 60 has been described as having an indirect conversion method in which radiation is converted into light once, and the converted light is converted into electric charge by the sensor unit 72 and accumulated.
  • the present invention is not limited to this.
  • the radiation detector 60 may be a direct conversion system that converts radiation into electric charges in a semiconductor layer such as amorphous selenium.
  • the electronic cassette 32 may transfer the radiation image detected by each sensor unit 146 of the radiation detection unit 62 to the console 42 and cause the console 42 to display on the display 100. Thereby, it is possible to quickly check the blurring and positioning of the subject from the displayed radiation image.
  • the cassette control unit 92 of the electronic cassette 32 generates various parameters from the radiation images detected by the sensor units 146 of the radiation detection unit 62, and is generated from the radiation detector 60.
  • the radiographic image normalization processing is performed (see also the imaging control processing program described with reference to FIGS. 13 and 15 in the first embodiment), but the present invention is not limited to this. Absent.
  • the cassette control unit 92 may transmit the digital data input from the signal detection unit 162 to the console 42 as needed, and the console 42 may perform any processing.
  • the cassette control unit 92 of the electronic cassette 32 performs the region setting process and the region setting change process based on the radiation image detected by each sensor unit 146 of the radiation detection unit 62 .
  • the present invention is not limited to this (see also FIG. 17 of the first embodiment, and FIGS. 23 and 27 of the second embodiment).
  • digital data image data of density image for density correction
  • the cassette control unit 92 may be transmitted to the console 42 at any time, and any processing may be performed in the console 42.
  • the region setting process and the region setting change processing program are stored in the HDD 110 of the console 42 and executed by the CPU 104 of the console 42.
  • the image data of the radiographic image for density correction has a resolution that is much lower than the resolution of the radiographic image detected by the radiation detector 60 and is detected by the radiation detector 60 if there is some margin in the transfer rate. Even when the image data of the radiation image to be displayed is displayed in real time, it can be transmitted without any trouble.
  • the density correction radiographic image may be used for setting, and when motion detection is performed, the radiographic image captured and transmitted by the radiation detector 60 may be used for detection.
  • the radiation image detected by the radiation detector 60 is used not only as a density correction radiation image but also for region setting processing and region setting change processing.
  • the radiation image may not be used for density correction but may be used only for region setting processing or region setting change processing.
  • the console 42 transmits an instruction signal instructing the electronic cassette 32 and the radiation generator 34 to start exposure, and the radiation generator 34 uses the instruction signal as a trigger to trigger the exposure condition.
  • the electronic cassette 32 may be configured to detect radiation that is equal to or greater than a threshold value from the radiation generator 34 and to read out a radiation image after the irradiation period has elapsed, in accordance with the frame rate and the irradiation period.
  • the synchronization signal may be transmitted to one of the electronic cassette 32 and the radiation generator 34, and the synchronization signal may not be transmitted to the other. That is, the method of synchronizing during shooting is not limited to the above embodiment.
  • the present invention is not limited to this.
  • the radiation to be detected may be X-rays, visible light, ultraviolet rays, infrared rays, gamma rays, particle rays, or the like.
  • the present invention is not limited to this.
  • the present invention can be applied to imaging other parts, and can be used for angios. Is also applicable.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Engineering & Computer Science (AREA)
  • Radiology & Medical Imaging (AREA)
  • Molecular Biology (AREA)
  • Biophysics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
  • Pathology (AREA)
  • Physics & Mathematics (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Measurement Of Radiation (AREA)

Abstract

Selon la présente invention, lors de la transmission, dans un état non compressé, de données d'image de régions de transfert non compressées d'une image radiographique obtenue par capture d'image de transmission, et de la transmission des données d'image de régions restantes dans un état compressé, une région est réglée en tant que région de transfert de non-compression ; une telle région étant une région qui est à ou au- dessous de la valeur limite supérieure d'un volume de données qui peut être transmis dans un état non compressé déterminé par le taux de trame de capture d'image de transmission et qui comprend une région de transfert essentielle (région de base de données intégrée et système de gestion cognitif de la prochaine génération (MUST)) spécifiée en tant que région dans une région d'intérêt d'une image radiographique et qui est à transférer dans un état non compressé.
PCT/JP2012/071896 2011-09-26 2012-08-29 Système de capture d'image d'image radiographique, procédé et programme de commande de capture d'image d'image radiographique Ceased WO2013047069A1 (fr)

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JP2011-209536 2011-09-26

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EP3417785A1 (fr) * 2017-06-22 2018-12-26 Konica Minolta, Inc. Système de capture d'images radiographiques
CN118786676A (zh) * 2022-05-31 2024-10-15 飞睿设备株式会社 运动图像的收发系统、传送终端、程序及方法

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JP2002095640A (ja) * 2000-09-26 2002-04-02 Toshiba Corp 医用画像診断装置
JP2007097977A (ja) * 2005-10-07 2007-04-19 Ge Medical Systems Global Technology Co Llc Ｘ線ｃｔ装置
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JP2019005073A (ja) * 2017-06-22 2019-01-17 コニカミノルタ株式会社 放射線画像撮影システム
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