JP2011196864A - Radiographic imaging system and program - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiographic imaging system and a program capable of suppressing deterioration in the image quality of a radiographic image caused by the spotty distribution of a temperature in an imaging area without increasing power consumption or extending a time until the start of imaging.SOLUTION: A CPU 92A controls a heater part 64 adjusting the temperature of an imaging area in an electronic cassette 32 at a predetermined temperature so that the operation is started at timing in which the preparation of the next imaging by the electronic cassette 32 is started.

Description

  The present invention relates to a radiographic image capturing system and program, and more particularly, to a radiographic image capturing system and program for capturing a radiographic image indicated by radiation emitted from a radiation source and transmitted through a subject.

  In recent years, radiation detectors such as flat panel detectors (FPDs) that can arrange radiation sensitive layers on TFT (Thin Film Transistor) active matrix substrates and convert radiation directly into digital data have been put into practical use. A portable radiographic image capturing apparatus (hereinafter also referred to as “electronic cassette”) that captures a radiographic image represented by irradiated radiation has been put into practical use. The radiation detectors used in the above-mentioned electronic cassettes include, as a method for converting radiation, an indirect conversion method in which radiation is converted into light by a scintillator and then converted into electric charges in a semiconductor layer such as a photodiode, or radiation is converted into amorphous selenium. There are direct conversion systems that convert charges into semiconductor layers, etc., and there are various materials that can be used for the semiconductor layer in each system.

  By the way, the electronic cassette may be provided so as to continuously capture a plurality of radiographic images by continuously providing one electronic cassette on a plurality of mounts such as a standing base and a stand. In this case, when the temperature of the electronic cassette main body and the newly provided frame are different, as a result of uneven temperature distribution (unevenness) occurring in the imaging area of the electronic cassette, the radiation image obtained by imaging is also uneven. There was a problem that it might occur.

  For example, as shown in FIG. 10 as an example, for the TFT, an offset value, which is image information obtained by imaging in a state where no radiation is incident, fluctuates depending on temperature, and an indirect conversion type radiation detector is used. In the case of the scintillator in particular, when cesium iodide (CsI) is used as the phosphor material, the sensitivity to radiation varies with temperature.

  Conventionally, as a technique that can be applied to suppress deterioration in the quality of a radiographic image caused by temperature spots in an imaging region of a radiation detector, Patent Document 1 discloses that electrodes are provided on the upper and lower surfaces and X-rays are used as charge signals. A radiation detector in which a flat X-ray conversion layer made of a semiconductor to be converted and a collimator formed of a collimator plate for removing scattered X-rays are arranged one-dimensionally or two-dimensionally, and holds the X-ray conversion layer There is disclosed a radiation detector characterized in that a heater and a temperature sensor are provided on a member, and temperature adjusting means for adjusting the X-ray conversion layer to a predetermined temperature is provided.

  In Patent Document 2, charges generated in the photoconductive layer according to the intensity of irradiated radiation are read and accumulated by a number of microplates arranged in a two-dimensional manner, and an image is obtained based on the accumulated charge amount. Based on an imaging panel that generates and reads data, a temperature sensor that measures the temperature of the imaging panel and outputs a sensor signal, temperature variable means that varies the temperature of the imaging panel, and a sensor signal from the temperature sensor There is disclosed a radiation image reading apparatus comprising temperature control means for controlling the temperature variable means to control the temperature of the imaging panel to be within a predetermined temperature range.

  Patent Document 3 discloses an image detection unit that records a predetermined image and outputs the recorded image as image information, and a cooling panel that is disposed on the surface of the image detection unit and cools the image detection unit. An image detector is disclosed, wherein the cooling panel is configured such that heat conduction characteristics are directed in a plane direction along a surface of the image detection unit.

  Patent Document 4 discloses a radiation solid detector that receives irradiation of radiation carrying image information, records the image information, and outputs an image signal representing the recorded image information, and the radiation solid detector. A radiation detection case having a housing for housing is disclosed, wherein at least a part of the space in the housing is filled with a heat-insulating filler.

  Further, Patent Document 5 discloses a sensor region including a plurality of pixels for detecting a subject image, a readout circuit for sequentially reading signals from the plurality of pixels to a common output unit, the sensor region, and the readout. There is disclosed an image photographing apparatus including a power supply unit that supplies power independently to each circuit.

  Further, Patent Document 6 discloses an imaging apparatus including an imaging unit that images a subject, a driving unit that drives the imaging unit, and a control unit that controls the driving unit. Receiving means for receiving the imaging request, and detecting means for detecting whether or not the imaging operation for the imaging request received by the receiving means is completed, based on the detection result of the detecting means, An imaging apparatus is disclosed in which the state of the driving means is set to a standby state or an imaging enabled state.

JP 2002-202377 A Japanese Patent Application Laid-Open No. 11-231055 JP 2009-85630 A JP 2006-242702 A Japanese Patent Laid-Open No. 2002-165142 JP 2001-66720 A

  However, in the techniques disclosed in Patent Documents 1 and 2, the timing for performing the temperature control is not specified, and when the temperature control is always performed, the power consumption is large and the temperature control is performed in an abnormal temperature range. When it is performed, it is impossible to take a picture until the temperature is stabilized, and it takes time to take a picture.

  In addition, since the techniques disclosed in Patent Documents 3 to 6 do not adjust the temperature in the imaging region of the radiation detector, it is not always possible to sufficiently suppress the uneven temperature distribution. There was a problem of not.

  The present invention has been made to solve the above-described problems, and does not cause an increase in power consumption or a long period of time until the start of imaging, and the image quality of the radiation image resulting from the uneven temperature distribution in the imaging region. An object of the present invention is to provide a radiographic image capturing system and program capable of suppressing the decrease of the above.

  In order to achieve the above object, a radiographic imaging system according to claim 1 is a radiographic imaging apparatus that performs radiographic imaging, and a temperature of an imaging region in the radiographic imaging apparatus is a predetermined temperature. And adjusting means for controlling the adjusting means so that the operation is started at the timing when preparation for the next imaging by the radiographic imaging apparatus is started.

  According to the radiation image capturing system of the first aspect, a radiation image is captured by the radiation image capturing apparatus.

  Here, in the present invention, the temperature of the imaging region in the radiographic imaging device is determined in advance by the control means so that the operation is started at the timing when the preparation for the next imaging by the radiographic imaging device is started. The adjusting means for adjusting the temperature to be adjusted is controlled.

  As described above, according to the radiographic image capturing system of the first aspect, the imaging region of the radiographic image capturing apparatus is started so that the operation is started at the timing when the preparation for the next capturing by the radiographic image capturing apparatus is started. Controlling the adjustment means to adjust the temperature to be a predetermined temperature, so it does not increase power consumption or lengthen the period until the start of shooting, resulting in uneven temperature distribution in the shooting area The deterioration of the image quality of the radiation image can be suppressed.

  Note that, as in the invention described in claim 2, the present invention further includes a detection unit that detects a temperature of an imaging region in the radiographic image capturing device, and the control unit performs next imaging by the radiographic image capturing device. After the adjustment means is controlled so that the operation is started at the timing when the preparation for the start is started, the difference between the temperature detected by the detection means and the predetermined temperature is not more than a predetermined threshold value. In some cases, the adjusting means may be controlled so that the operation is stopped. Thereby, power consumption can be suppressed more.

  In particular, the invention according to claim 2 is indicated by image information obtained by imaging by the radiographic imaging apparatus in a state where no radiation is incident, as in the invention according to claim 3. The offset value is detected instead of the temperature, and the control unit controls the adjustment unit so that the operation is started at the timing when the preparation for the next imaging by the radiographic apparatus is started, and then the detection The adjusting means may be controlled so that the operation is stopped when a difference between the offset value detected by the means and the offset value at the predetermined temperature is equal to or less than a predetermined second threshold value. . Thereby, power consumption can be suppressed, without newly providing members, such as a sensor which detects temperature.

  Further, according to the present invention, as in the invention described in claim 4, the temperature may be increased by operating the adjusting means. As a result, the temperature can be adjusted only by starting and stopping the operation, so that the temperature can be adjusted more easily.

  Further, according to the present invention, as in the fifth aspect of the present invention, the adjusting means may be capable of controlling temperature rise and fall. Thereby, temperature adjustment can be performed finely.

  In the present invention, as in the invention described in claim 6, the adjusting means may be provided in the radiographic imaging apparatus. Thereby, compared with the case where the said adjustment means is comprised separately from the radiographic imaging apparatus, since the temperature of the imaging area | region by a radiographic imaging apparatus can be controlled directly, more power consumption is possible. Can be suppressed.

  In the present invention, as in the invention described in claim 7, the adjusting means may be provided in a holding device that holds the radiographic image capturing apparatus when a radiographic image is captured. Thereby, compared with the case where the said adjustment means is provided in a radiographic imaging apparatus, a radiographic imaging apparatus can be reduced in weight, As a result, the portability of a radiographic imaging apparatus can be improved.

  In the present invention, as in the invention described in claim 8, the control means may be provided in the radiographic apparatus. Thereby, since the said adjustment means can be directly controlled by the said control means, compared with the case where the said control means is comprised separately from the radiographic imaging apparatus, the said adjustment means is simpler. Can be controlled.

  Further, according to the present invention, as in the invention described in claim 9, the control means may be configured separately from the radiographic image capturing apparatus. Thereby, compared with the case where the said control means is provided in a radiographic imaging apparatus, a radiographic imaging apparatus can be reduced in weight, As a result, the portability of a radiographic imaging apparatus can be improved.

  On the other hand, in order to achieve the above object, the program according to claim 10 includes a timing detection unit that detects a timing at which preparation for next imaging by a radiographic imaging device that performs radiographic imaging is started. The temperature of the imaging region in the radiographic imaging device is set to a predetermined temperature so that the operation is started when the timing at which the preparation for the next imaging is started is detected by the timing detection unit. It is for functioning as a control means for controlling the adjusting means for adjusting the speed.

  Therefore, according to the present invention, the computer can be operated in the same manner as in the first aspect of the present invention. Therefore, as in the first aspect of the present invention, the increase in power consumption and the length of time until the start of photographing are increased. Without incurring a period, it is possible to suppress the deterioration of the image quality of the radiation image due to the uneven temperature distribution in the imaging region.

  According to the radiographic imaging system and program of the present invention, the temperature of the imaging region in the radiographic imaging device is determined in advance so that the operation starts at the timing when the preparation for the next imaging by the radiographic imaging device is started. Therefore, the image quality of the radiation image caused by the unevenness of temperature distribution in the imaging area is avoided without increasing the power consumption or lengthening the period until the start of imaging. The effect that the fall of can be suppressed is acquired.

It is a block diagram which shows the structure of the radiation information system which concerns on embodiment. It is a side view which shows an example of the arrangement | positioning state of each apparatus in the radiography room of the radiographic imaging system which concerns on embodiment. It is a permeation | transmission perspective view which shows the internal structure of the electronic cassette concerning embodiment. It is a front view which shows the structure of the heater part which concerns on embodiment. It is a block diagram which shows the principal part structure of the electrical system of the radiographic imaging system which concerns on embodiment. It is a flowchart which shows the flow of a process of the radiographic imaging processing program which concerns on embodiment. It is the schematic which shows an example of the initial stage information input screen which concerns on embodiment. It is a flowchart which shows the flow of a process of the imaging | photography preparation processing program which concerns on embodiment. It is a side view which shows an example of the arrangement | positioning state of each apparatus in the radiography room of the radiographic imaging system which concerns on other embodiment. It is a graph with which the problem of a prior art is demonstrated.

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

  First, the configuration of a radiation information system (hereinafter referred to as “RIS (Radiology Information System)”) 10 according to the present embodiment will be described with reference to FIG.

  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)”). .

  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 radiography room (or operating room) in a hospital. (Hereinafter referred to as “imaging system”) 18, which are connected to an in-hospital network 16, such as a wired or wireless LAN (Local Area Network). 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 made 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.

  On the other hand, the RIS server 14 receives an imaging request from each terminal device 12 and manages a 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 related to the patient, identification number (ID information) of the electronic cassette 32 (to be described later) used in the imaging system 18, model, size, sensitivity, usable imaging part (content of imaging request that can be supported), date of start of use , 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. Electrons that incorporate a radiation detector 60 (see also FIG. 3) that absorbs radiation X transmitted through the imaging region of the person and generates charges and generates image information indicating a radiation image based on the amount of generated charges. A cassette 32, a cradle 40 that charges a battery built in the electronic cassette 32, and an electronic cassette 32, a radiation generator 34, and a console 42 that controls the cradle 40 are provided.

  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. 5) 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.

  As shown in the figure, the radiation imaging room 44 has a standing table 45 used when performing radiography in a standing position and a prone table 46 used when performing radiography 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.

  The standing base 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. Similarly, 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.

  Further, in the radiation imaging room 44, 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, and a support moving mechanism 52 is provided which can be rotated in the vertical direction (arrow B direction in FIG. 2) and supported so as to be movable in the horizontal direction (arrow C direction in FIG. 2). It has been. Here, 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).

  On the other hand, the cradle 40 is formed with an accommodating portion 40 </ b> A capable of accommodating the electronic cassette 32.

  When the electronic cassette 32 is not in use, the built-in battery is charged in a state of being accommodated in the accommodating portion 40A of the cradle 40. When a radiographic image is captured, 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.

  Here, in the imaging system 18 according to the present embodiment, various types of information are transmitted and received between the radiation generator 34 and the console 42 and between the electronic cassette 32 and the console 42 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 an internal configuration of the electronic cassette 32 according to the present exemplary embodiment.

  As shown in the figure, the electronic cassette 32 includes a housing 54 made of a material that transmits the radiation X, and has a waterproof and airtight structure. When the electronic cassette 32 is used in an operating room or the like, there is a risk that blood and other germs may adhere. Therefore, one electronic cassette 32 can be used repeatedly by sterilizing and cleaning the electronic cassette 32 as necessary with a waterproof and hermetic structure.

  Inside the housing 54, a grid 58 for removing scattered radiation of the radiation X by the subject and the radiation X transmitted through the subject are detected from the irradiation surface 56 side of the housing 54 to which the radiation X is irradiated. A radiation detector 60, a lead plate 62 that absorbs the back scattered radiation of the radiation X, and a heater unit 64 that uniformly heats the imaging region of the radiation detector 60 are arranged in this order. Note that the irradiation surface 56 of the housing 54 may be configured as a grid 58.

  In addition, an electronic circuit including a microcomputer and a chargeable and detachable battery 96 </ b> A are arranged on one end side inside the housing 54. The radiation detector 60, the heater unit 64, and the electronic circuit are operated by electric power supplied from the battery 96 </ b> A disposed in the case 31. In order to avoid various circuits housed in the case 31 from being damaged by the radiation X irradiation, it is desirable to arrange a lead plate or the like 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.

  Further, at a predetermined position on the outer wall of the housing 54, 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. Is provided. In the electronic cassette 32 according to the present embodiment, a light emitting diode is applied as the display unit 56A. However, 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.

  Further, a handle 54 </ b> B that is gripped when the electronic cassette 32 is moved is provided at a predetermined position on the outer wall of the housing 54. In the electronic cassette 32 according to the present exemplary embodiment, the handle 54B is provided at the central portion of the side wall of the casing 54 that extends in the longitudinal direction of the irradiation surface 56. It may be provided at other positions such as the central portion of the side wall extending in the short direction of the surface 56, a position deviated by a distance considering the deviation of the center of gravity of the electronic cassette 32 from the central portion of these side walls, etc. Needless to say.

  On the other hand, FIG. 4 shows the configuration of the heater section 64 according to the present embodiment.

  As shown in the figure, the heater section 64 according to the present embodiment has heating wires 64A on the surface of a plate-like member 64B made of a material having high thermal conductivity at substantially equal intervals in a predetermined direction. The one laid back is applied. In addition, although illustration is abbreviate | omitted, the application and interruption | blocking of the electric power supplied from battery 96A can be switched to the both ends of the heating wire 64A.

  Next, with reference to FIG. 5, the main configuration of the electrical system of the imaging system 18 according to the present embodiment will be described.

  As shown in the figure, the radiation detector 60 built in the electronic cassette 32 is configured by laminating a photoelectric conversion layer that absorbs radiation X and converts it into charges on a TFT active matrix substrate 66. The photoelectric conversion layer is made of amorphous a-Se (amorphous selenium) containing, for example, selenium as a main component (for example, a content rate of 50% or more), and when irradiated with radiation X, a charge corresponding to the amount of irradiated radiation. By generating a certain amount of charge (electron-hole pairs) internally, the irradiated radiation X is converted into a charge. The radiation detector 60 is indirectly charged using a phosphor material and a photoelectric conversion element (photodiode) instead of a radiation-charge conversion material that directly converts the radiation X such as amorphous selenium into an electric charge. May be converted to As phosphor materials, gadolinium sulfate (GOS) and cesium iodide (CsI) are well known. In this case, radiation X-light conversion is performed using a phosphor material, and light-charge conversion is performed using a photodiode of a photoelectric conversion element.

  Further, on the TFT active matrix substrate 66, a pixel portion 74 (in FIG. 4) provided with a storage capacitor 68 for storing the charge generated in the photoelectric conversion layer and a TFT 70 for reading out the charge stored in the storage capacitor 68. A number of photoelectric conversion layers corresponding to the individual pixel portions 74 are schematically shown as the photoelectric conversion portions 72.) A large number of photoelectric conversion layers are arranged in a matrix, and photoelectric conversion occurs as the electronic cassette 32 is irradiated with the radiation X. The charges generated in the layers are stored in the storage capacitors 68 of the individual pixel portions 74. As a result, 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.

  The TFT active matrix substrate 66 is extended in a certain direction (row direction), a plurality of gate wirings 76 for turning on / off the TFTs 70 of the individual pixel portions 74, and a direction orthogonal to the gate wirings 76. A plurality of data wirings 78 are provided so as to read the stored charge from the storage capacitor 68 via the TFT 70 which is extended in the (column direction) and turned on. Individual gate lines 76 are connected to a gate line driver 80, and individual data lines 78 are connected to a signal processing unit 82. When charges are accumulated in the storage capacitors 68 of the individual pixel portions 74, the TFTs 70 of the individual pixel portions 74 are sequentially turned on in units of rows by a signal supplied from the gate line driver 80 via the gate wiring 76. The charge stored in the storage capacitor 68 of the pixel unit 74 for which is turned on is transmitted as an analog electrical signal through the data wiring 78 and input to the signal processing unit 82. Accordingly, the charges accumulated in the storage capacitors 68 of the individual pixel portions 74 are sequentially read out in units of rows.

  On the other hand, the signal processing unit 82 includes an amplifier and a sample and hold circuit provided for each data line 78, and the charge signal transmitted through the individual data line 78 is amplified by the amplifier and then supplied to the sample and hold circuit. Retained. Further, a multiplexer and an A / D (analog / digital) converter are sequentially connected to the output side of the sample and hold circuit, and the charge signals held in the individual sample and hold circuits are sequentially (serially) input to the multiplexer. The digital image data is converted by an A / D converter.

  An image memory 90 is connected to the signal processing unit 82, and image data output from the A / D converter of the signal processing unit 82 is sequentially stored in the image memory 90. 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.

  The cassette control unit 92 is connected to the heater unit 64 described above, and the operation of the heater unit 64 is controlled by a CPU 92 </ b> A provided in the cassette control unit 92.

  A wireless communication unit 94 is connected to the cassette control unit 92. The wireless communication unit 94 according to the present embodiment corresponds to a wireless LAN (Local Area Network) standard represented by IEEE (Institute of Electrical and Electronics Engineers) 802.11a / b / g and the like. 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.

  Further, the electronic cassette 32 is provided with a power supply unit 96, and the various circuits and elements described above (heater unit 64, gate line driver 80, signal processing unit 82, image memory 90, wireless communication unit 94, cassette control unit). 92 and the like) is operated by the electric power supplied from the power supply 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. In FIG. 5, illustration of wirings connecting the power supply unit 96 to various circuits and elements is omitted.

  On the other hand, the console 42 is configured as a server computer, and includes a display 100 that displays an operation menu, captured radiographic images, and the like, and a plurality of keys, and inputs various information and operation instructions. An operation panel 102.

  The console 42 according to the present embodiment 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. In addition, the console 42 transmits and receives various types of information such as an exposure condition, which will be described later, to and from the radiation generator 34 and also transmits and receives various types of information such as image data to and from the electronic cassette 32 by wireless communication. A wireless communication unit 118 is provided.

  The CPU 104, the ROM 106, the RAM 108, the HDD 110, the display driver 112, the operation input detection unit 114, and the wireless communication unit 118 are connected to each other via a system bus BUS. Therefore, the CPU 104 can access the ROM 106, the RAM 108, and the HDD 110, controls the display of various information on the display 100 via the display driver 112, and the radiation generator 34 via the wireless communication unit 118. Control of transmission and reception of various types of information with the electronic cassette 32 can be performed. 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.

  On the other hand, the radiation generator 34 includes a radio communication unit 132 that transmits and receives various types of information such as an exposure condition between the radiation source 130 and the console 42, and a line that controls the radiation source 130 based on the received exposure condition. A source control unit 134.

  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 such as tube voltage, tube current, and exposure period. The radiation source controller 134 irradiates the radiation X from the radiation source 130 based on the received exposure conditions.

  Next, the operation of the imaging system 18 according to the present embodiment will be described.

  First, with reference to FIG. 6, the operation of the console 42 when radiographic images are taken will be described. FIG. 6 is a flowchart showing the flow of processing of the radiographic image capturing processing program executed by the CPU 104 of the console 42 at this time, and the program is stored in a predetermined area of the ROM 106 in advance.

  In step 300 in the figure, the display driver 112 is controlled so that a predetermined initial information input screen is displayed on the display 100, and in step 302, input of predetermined information is waited.

  FIG. 7 shows an example of an initial information input screen displayed on the display 100 by the processing in step 300 described above. As shown in the figure, in the initial information input screen according to the present embodiment, the name of the subject who is going to capture a radiographic image, the region to be imaged, and the posture at the time of capturing (in this embodiment, lying down, standing , And a message prompting the user to input radiation X exposure conditions at the time of imaging (in this embodiment, tube voltage, tube current, and exposure period when radiation X is exposed), and these The information input area is displayed.

  When the initial information input screen shown in the figure is displayed on the display 100, the photographer can input the name of the subject to be imaged, the imaging region, the posture at the time of imaging, and the exposure conditions corresponding to each of the input areas. And the electronic cassette 32 is held by the holding unit 150 of the standing table 45 or the holding unit 152 of the prone table 46 in accordance with the input posture at the time of imaging, and the subject. Is positioned at a predetermined photographing position, and then an end button displayed near the lower end of the initial information input screen is designated via the operation panel 102. When an end button is designated by the photographer, step 302 is affirmative and the process proceeds to step 304.

  In step 304, the exposure conditions input on the initial information input screen are transmitted to the radiation generator 34 and the electronic cassette 32 via the wireless communication unit 118, thereby setting the explosion conditions. In response to this, the radiation source controller 134 of the radiation generator 34 prepares for exposure under the received exposure conditions, while the cassette controller 92 of the electronic cassette 32 uses the heater unit 64 to detect the radiation detector 60. A shooting preparation processing program (see also FIG. 8) that adjusts the temperature of the shooting area to be within a predetermined range is executed, and preparation for shooting is completed when the shooting preparation processing program ends. Preparation completion information indicating this is transmitted to the console 42.

  Accordingly, in the next step 305, the preparation completion information is waited for reception, and in the next step 306, the instruction information for instructing the start of exposure is sent to the radiation generator 34 and the electronic cassette 32 via the wireless communication unit 118. Send.

  In response to this, the radiation source 130 generates and emits radiation at a tube voltage, a tube current, and an exposure period corresponding to the exposure conditions received by the radiation generator 34 from the console 42. The radiation X exposed from the radiation source 130 reaches the electronic cassette 32 after passing through the subject.

  On the other hand, when the cassette control unit 92 of the electronic cassette 32 receives the instruction information instructing the start of exposure, the cassette control unit 92 starts accumulating charges in the storage capacitors 68 of the pixel units 74 of the built-in radiation detector 60, The gate line driver 80 is controlled after the exposure period specified by the above exposure conditions, and the gate line driver 80 sequentially outputs an ON signal to each gate line 76 one line at a time. Each TFT 70 is turned on one line at a time.

  In the radiation detector 60, when the TFTs 70 connected to the gate wirings 76 are sequentially turned on line by line, the charges accumulated in the storage capacitors 68 sequentially line by line flow out to the data wirings 78 as electric signals. The electric signal flowing out to each data wiring 78 is converted into digital image data by the signal processing unit 82 and stored in the image memory 90.

  The cassette control unit 92 transmits the image data stored in the image memory 90 to the console 42 by wireless communication after the end of shooting.

  Therefore, in the next step 308, the process waits until the image data is received from the electronic cassette 32, and in the next step 310, image processing for performing various corrections such as shading correction on the received image data is executed. To do.

  In the next step 312, the image data subjected to the above image processing (hereinafter referred to as “corrected image data”) is stored in the HDD 110, and in the next step 314, the radiation image indicated by the corrected image data is stored. The display driver 112 is controlled so as to be displayed on the display 100 for confirmation and the like, and in the next step 316, the corrected image data is transmitted to the RIS server 14 via the in-hospital network 16, and then the radiographic imaging is performed. Terminate the processing program. The corrected image data transmitted to the RIS server 14 is stored in the database 14A, so that a doctor can perform radiogram interpretation, diagnosis, and the like.

  Next, with reference to FIG. 8, the operation of the electronic cassette 32 when the explosion condition is set from the console 42 will be described. FIG. 8 is a flowchart showing a flow of processing of the photographing preparation processing program executed by the CPU 92A provided in the cassette control unit 92 of the electronic cassette 32 at this time, and the program is stored in a predetermined area of the memory 92B in advance. It is remembered.

  In step 400 of the figure, the operation of the heater unit 64 is started by controlling power supply from the battery 96A to the heater unit 64, and in the next step 402, radiation detection is performed without radiation X being incident. The image data obtained by controlling to perform imaging by the device 60 is acquired as an offset value, and in the next step 404, the offset value acquired by the processing of step 402 and the imaging region of the radiation detector 60 are acquired. The offset value (hereinafter referred to as “reference” in a state where the temperature of the image is stable at the temperature at the time of normal imaging (in the present embodiment, as a result, no visible spot appears in the radiographic image obtained by imaging). The difference from the value is calculated for each pixel of the radiation detector 60.

  In the next step 406, it is determined whether or not the maximum value of the difference for each pixel calculated by the processing in step 404 is larger than a predetermined threshold value TH. If the determination is affirmative, the process proceeds to step 408. Then, based on the maximum value of the difference, the operation duration time of the heater unit 64 until the temperature of the imaging region of the radiation detector 60 reaches the above-described normal imaging temperature is derived, and in the next step 410, After waiting for the elapse of the derived operation continuation time, the routine proceeds to step 412. On the other hand, if a negative determination is made in step 406, the process proceeds to step 412 without executing the processing of steps 408 and 410.

  In step 412, control is performed so as to stop power supply from the battery 96 </ b> A to the heater unit 64, so that the operation of the heater unit 64 started by the processing in step 400 is stopped, and in the next step 414. After the above-described preparation end information is transmitted to the console 42 via the wireless communication unit 94, the main photographing preparation processing program is ended.

  As described above in detail, according to the present embodiment, the operation is started at the timing when the preparation for the next imaging by the radiographic image capturing apparatus (in this embodiment, the electronic cassette 32) is started. Since the adjustment means (the heater unit 64 in the present embodiment) that adjusts the temperature of the imaging region in the radiographic imaging device to a predetermined temperature is controlled, power consumption increases and imaging starts. The deterioration of the image quality of the radiation image due to the uneven temperature distribution in the imaging region can be suppressed without incurring a long period of time.

  In particular, according to the present embodiment, an offset value indicated by image information obtained by imaging by the radiographic image capturing apparatus in a state in which no radiation is incident is detected, and preparation for the next imaging by the radiographic image capturing apparatus is performed. After controlling the adjusting means so that the operation is started at the timing at which is started, when the difference between the detected offset value and the offset value at the predetermined temperature is equal to or less than a predetermined threshold value Since the adjustment means is controlled so that the operation is stopped, power consumption can be suppressed without newly providing a member such as a sensor for detecting the temperature.

  In addition, according to the present embodiment, since the heater unit 64 whose temperature rises when operated is applied as the adjusting means of the present invention, the temperature can be adjusted only by starting and stopping the operation, and is simpler. The temperature can be adjusted.

  Further, according to the present embodiment, since the adjustment unit is provided in the radiographic image capturing apparatus, compared with a case where the adjustment unit is configured separately from the radiographic image capturing apparatus, Since the temperature of the imaging region by the radiographic imaging device can be directly controlled, power consumption can be further suppressed.

  Further, according to the present embodiment, since the control means for controlling the adjusting means (in the present embodiment, the cassette control unit 92) is provided in the radiographic imaging apparatus, the control means controls the Since the adjusting means can be directly controlled, the adjusting means can be controlled more easily than when the control means is configured separately from the radiographic image capturing apparatus.

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

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

  For example, in the above-described embodiment, the case where the heater unit as the adjusting unit of the present invention is provided in the electronic cassette 32 has been described. However, the present invention is not limited to this, and the holding unit 150 of the standing platform 45 is not limited thereto. In addition, the electronic cassette 32 may or may not be provided in at least one of the holding portions 152 of the gantry base 46. In this case, the electronic cassette 32 may or may not be provided.

  FIG. 9 shows a configuration example in which the heater portion 65A is provided in the holding portion 150 of the standing base 45 and the heater portion 65B is provided in the holding portion 152 of the standing base 46. The configuration of the heater unit 65A and the heater unit 65B is the same as that of the heater unit 64.

  As shown in the figure, in this case, the heater unit 65A is provided on the side of the holding unit 150 where the electronic cassette 32 is held opposite to the side on which the radiation X is incident, and the heater unit 65B is provided on the holding unit 152. It is provided on the side opposite to the side on which the radiation X is incident at the position where the electronic cassette 32 is held.

  For example, when the electronic cassette 32 includes the heater unit 64, the heater unit 65 </ b> A is included in the holding unit 150 of the standing platform 45, and the heater unit 65 </ b> B is included in the holding unit 152 of the standing platform 46. As a method, the electronic cassette 32 starts the operation of the heater unit 64 provided in itself in step 400 in the above-described imaging preparation processing program (see FIG. 8), and is provided in the holding unit in which the electronic cassette 32 is installed. In the process of step 304 of the above-described radiographic image capturing processing program (see FIG. 6), the exposure condition is set and used for radiographic imaging in the process of step 304 of the above-described radiographic image capturing processing program (see FIG. 6). The heater unit 65A provided in the holding unit 150 of the standing table 45 or the holding unit 152 of the standing table 46 is provided. The form to initiate operation of the heater portion 65B which have can be exemplified.

  In addition, when providing a heater part in the holding | maintenance part 150 and the holding | maintenance part 152, it is not necessary to necessarily provide a heater part in the electronic cassette 32. In this case, the electronic cassette 32 can be reduced in weight.

  Moreover, although the said embodiment demonstrated the case where the control means of this invention was provided in the electronic cassette 32, this invention is not limited to this, For example, the console 42 or the radiation generator 34 It is good also as a form provided in.

  Moreover, although the case where the heater part 64 was applied as the adjusting means of the present invention has been described in the above embodiment, the present invention is not limited to this, for example, electrically heating and cooling a Peltier element or the like. However, it is possible to adopt a configuration in which a fan is applicable, a configuration in which a fan is applied for cooling, and a configuration in which these are used in combination. In the case where a cooling capable device is applied as the adjusting means, the temperature of the imaging region of the radiation detector 60 is abnormally compared with a predetermined normal imaging temperature at the timing when preparation for the next imaging is started. If it is high, the adjusting means is activated. In this case, the temperature can be adjusted more finely than in the above embodiment.

  Moreover, although the said embodiment demonstrated the case where what heated up the heating wire 64A and laid in the predetermined direction at substantially equal intervals was applied as the heater part 64, this invention is limited to this. Instead, for example, a configuration in which the heating wire 64A is folded in a plurality of directions may be applied, or a rubber heater described in JP-A-2002-202377 may be applied as an example. .

  In the above embodiment, the case where the offset value is detected instead of the temperature detecting sensor as the detecting means of the present invention has been described. However, the present invention is not limited to this, and the detection of the present invention is not limited thereto. As a means, a temperature sensor may be provided in the vicinity of the imaging region of the radiation detector 60 and applied.

  In this case, after controlling the heater 64 so that the operation is started at the timing when preparation for the next shooting by the electronic cassette 32 is started, the temperature detected by the temperature sensor and the temperature during the normal shooting are The heater unit 64 is controlled so that the operation is stopped when the difference is equal to or less than a predetermined threshold value.

  Moreover, although the said embodiment demonstrated the case where the heater part 64 was provided in the vicinity of the radiation detector 60 across the lead plate 62, this invention is not limited to this, For example, a radiation detection The heater portion 64 may be provided between the vessel 60 and the lead plate 62.

  In the above-described embodiment, the case where the operation of the heater unit 64 is started at the timing when the exposure condition is set has been described. However, the present invention is not limited to this, and for example, a photographer or the like can take an image. At other timings when it can be considered that the preparation for the next shooting has started, such as the timing when the information indicating that the camera starts is input, the timing when the photographer has finished inputting various information on the initial information input screen, etc. The operation of the unit 64 may be started.

  Moreover, although the said embodiment demonstrated the case where it communicated by radio | wireless between the electronic cassette 32 and the console 42, and between the radiation generator 34 and the console 42, this invention is limited to this. For example, at least one of these may be configured to perform wired communication.

  In addition, the configuration of the RIS 10 described in the above embodiment (see FIG. 1), the configuration of the radiation imaging room (see FIG. 2), the configuration of the electronic cassette 32 (see FIG. 3), and the configuration of the heater unit 64 (see FIG. 4), and the configuration of the imaging system 18 (see FIG. 5) is an example, and unnecessary parts are deleted, new parts are added, and the connection state is within a range not departing from the gist of the present invention. Needless to say, it can be changed.

  Furthermore, the processing flow of the various programs described in the above embodiment (see FIGS. 6 and 8) is also an example, and unnecessary steps may be deleted or new within the scope of the gist of the present invention. It goes without saying that steps can be added and the processing order can be changed.

10 RIS
18 Radiation imaging system 32 Electronic cassette 34 Radiation generator 42 Console 60 Radiation detector 64 Heater 64A Heating wire 64B Plate members 65A, 65B Heater 92 Cassette control unit 92A CPU
94 Wireless communication unit 100 Display 102 Operation panel 104 CPU
106 ROM
110 HDD
118 Wireless communication unit 130 Radiation source

Claims (10)

A radiographic imaging device for radiographic imaging;
Adjusting means for adjusting the temperature of the imaging region in the radiographic imaging device to be a predetermined temperature;
Control means for controlling the adjustment means so that the operation is started at the timing when preparation for the next imaging by the radiographic imaging apparatus is started;
Radiographic imaging system equipped with. Further comprising a detecting means for detecting the temperature of the imaging region in the radiographic imaging device,
The control means controls the adjustment means so that the operation is started at the timing when preparation for the next imaging by the radiographic imaging apparatus is started, and then the temperature detected by the detection means is determined in advance. The radiographic imaging system according to claim 1, wherein the adjustment unit is controlled so that the operation is stopped when a difference from the detected temperature is equal to or less than a predetermined threshold value. The detection means detects an offset value indicated by image information obtained by imaging by the radiographic imaging apparatus in a state where no radiation is incident instead of the temperature,
The control means controls the adjustment means so that the operation is started at the timing when preparation for the next imaging by the radiographic imaging apparatus is started, and then determines the offset value detected by the detection means and the predetermined value. The radiographic image capturing system according to claim 2, wherein the adjustment unit is controlled so that the operation is stopped when a difference from an offset value at a predetermined temperature is equal to or less than a predetermined second threshold value. The radiographic imaging system according to any one of claims 1 to 3, wherein the adjusting unit is configured to increase a temperature when operated. The radiographic imaging system according to any one of claims 1 to 3, wherein the adjustment unit is capable of controlling an increase and a decrease in temperature. The radiographic image capturing system according to claim 1, wherein the adjustment unit is provided in the radiographic image capturing apparatus. The radiographic image capturing system according to claim 1, wherein the adjusting unit is provided in a holding device that holds the radiographic image capturing device when capturing a radiographic image. The radiographic imaging system according to claim 1, wherein the control unit is provided in the radiographic imaging apparatus. The radiographic image capturing system according to claim 1, wherein the control unit is configured separately from the radiographic image capturing device. Computer
Timing detection means for detecting the timing at which preparation for the next imaging by the radiographic imaging device that performs radiographic imaging is started;
The temperature of the imaging region in the radiographic imaging device is set to a predetermined temperature so that the operation is started when the timing at which the preparation for the next imaging is started is detected by the timing detection means. Control means for controlling adjustment means for adjustment;
Program to function as.

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