JP2011209245A - Radiographic image capturing system and program - Google Patents

Abstract

A radiation image capturing system and program capable of suppressing a decrease in image quality of a radiation image due to uneven temperature distribution in an imaging region while suppressing an increase in power consumption.
An operation is started when a difference between a maximum temperature and a minimum temperature at different positions in an imaging region in a radiation detector 60 provided in an electronic cassette 32 is equal to or greater than a predetermined threshold by a CPU 92A. As described above, the heater unit 64 that adjusts the temperature of the imaging region in the radiation detector 60 to a predetermined temperature is controlled.
[Selection] Figure 6

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. 12, 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 of the image quality of a radiographic image caused by temperature spots in an imaging region of a radiation detector, Patent Document 1 discloses one or more attached to a part of a detector case. The first constant temperature heater, one or more first temperature sensors disposed at positions near the outside of the detector case, and the first temperature sensor according to the measured value of the ambient temperature around the detector. A first temperature control unit configured to increase / decrease the detector case temperature to a first set temperature by controlling on / off the power supplied to the constant temperature heater, and one or more first units attached to a part of the detector case; 2 constant temperature heater, one or more second temperature sensors attached to a part of the detector case, and the detector case temperature by the second temperature sensor in the second constant temperature heater according to the measured value Supply power An X-ray detector isothermal apparatus comprising a second temperature control unit that performs on / off control to maintain a detector case temperature within a range between a first set temperature and a second set temperature is disclosed. ing.

  Further, in Patent Document 2, in a radiation detection apparatus including a radiation detection unit having a scintillator and a photodiode and a signal processing circuit unit, at least a temperature control mechanism for keeping the temperature of the radiation detection unit constant is provided. A radiation detection apparatus characterized by this is disclosed.

  Furthermore, in Patent Document 3, 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 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.

Japanese Patent Laid-Open No. 10-73668 Japanese Patent Laid-Open No. 3-95479 Japanese Patent Application Laid-Open No. 11-231055

  By the way, as described above, the occurrence of spots in the radiographic image obtained by imaging is caused by the occurrence of temperature distribution spots in the imaging area of the electronic cassette. Radiation image spots are less likely to occur. Therefore, when there are relatively few spots in the temperature distribution in the imaging region, it is often unnecessary to take measures against spots in the radiation image.

  However, the techniques disclosed in Patent Documents 1 to 3 do not take into account the unevenness of the temperature distribution in the imaging region, and may perform temperature control more than necessary. There was a problem that the power consumption was increased.

  The present invention has been made to solve the above-described problem, and can suppress a decrease in image quality of a radiation image due to uneven temperature distribution in an imaging region while suppressing an increase in power consumption. An object is to provide a photographing system and a program.

  In order to achieve the above object, a radiographic image capturing system according to claim 1 includes a radiographic image capturing apparatus including a radiographic image capturing unit configured to capture a radiographic image, and a temperature of an imaging region in the radiographic image capturing unit. Detecting by adjusting means for adjusting to a predetermined temperature, a plurality of temperature detecting means for individually detecting temperatures at different positions of the radiographing region in the radiographic imaging unit, and a plurality of temperature detecting means Control means for controlling the adjusting means so that the operation is started when the difference between the maximum temperature and the minimum temperature of the plurality of temperatures is not less than a predetermined threshold value.

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

  Here, in the present invention, a plurality of temperature detection units individually detect temperatures at different positions in the radiographic image capturing unit in the radiographic image capturing unit, and a plurality of temperature detection units detected by the control unit. In order that the operation is started when the difference between the maximum temperature and the minimum temperature is equal to or greater than a predetermined threshold, the temperature of the imaging region in the radiographic image capturing unit is set to a predetermined temperature. The adjusting means for adjusting is controlled.

  Thus, according to the radiographic image capturing system of claim 1, the difference between the maximum temperature and the minimum temperature at different positions of the imaging regions in the radiographic image capturing unit provided in the radiographic image capturing apparatus is determined in advance. Since the adjustment means for adjusting the temperature of the imaging region in the radiographic image capturing unit to be a predetermined temperature is controlled so that the operation is started when the threshold value is equal to or greater than a predetermined threshold, power consumption The deterioration of the image quality of the radiation image due to the uneven temperature distribution in the imaging region can be suppressed.

  Note that, as in the invention described in claim 2, the present invention further includes a supply state detection unit that detects a supply state of power for driving to the radiographic imaging unit, and the control unit includes the supply state. The operation is started when it is detected by the detection means that the supply of power for driving to the radiographic imaging unit is interrupted, and the difference between the maximum temperature and the minimum temperature is equal to or greater than a predetermined threshold. The adjusting means may be controlled so that As a result, unnecessary adjustment of the temperature of the imaging region in the radiation image capturing unit can be avoided, and as a result, power consumption can be further reduced.

  In particular, according to the second aspect of the present invention, as in the third aspect of the present invention, the driving power to the radiographic imaging unit is based on the driving time of the radiographic imaging unit during the previous imaging. And a derivation unit for deriving a standby time from when the supply of power is interrupted until the adjustment unit starts to operate, wherein the control unit is configured to interrupt the supply of driving power to the radiographic imaging unit. The adjustment means may be controlled so that the operation is started after waiting for the waiting time derived by the derivation means. Thereby, power consumption can be reduced more.

  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.

  Particularly, in the invention described in claim 6, as in the invention described in claim 7, the adjusting means may be provided in a housing that houses the radiographic image capturing unit in the radiographic image capturing apparatus. . As a result, it is possible to reduce the influence on the temperature distribution of the imaging region in the radiographic imaging unit due to the radiographic imaging device coming into contact with an external part such as a gantry. As a result, temperature adjustment can be performed more effectively.

  Further, according to the present invention, as in the invention described in claim 8, the radiographic imaging device is held by a holding device that holds the radiographic imaging device when the adjusting means captures a radiographic image. It may be provided so as to come into contact with the radiographic imaging apparatus in a state. Thereby, compared with the case where the said adjustment means is provided in a radiographic imaging device, a radiographic imaging device can be reduced in weight, As a result, the portability of the radiographic imaging device can be improved, and radiographic imaging can be performed. As a result of reducing the influence on the temperature distribution of the imaging region in the radiographic image capturing unit due to the contact of the apparatus with the holding device, temperature adjustment can be performed more effectively.

  In the present invention, as in the ninth aspect of the present invention, the control means may be provided in the radiation image capturing 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.

  Furthermore, in the present invention, as in the invention described in claim 10, the control means may be configured as a separate body 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, a program according to an eleventh aspect of the present invention is directed to a computer that causes a radiographic image capturing unit of a radiographic image capturing unit provided with a radiographic image capturing unit that captures a radiographic image to each other. The operation is started when the temperature detection means for individually detecting the temperatures at different positions and the difference between the maximum temperature and the minimum temperature of the plurality of temperatures detected by the temperature detection means is equal to or greater than a predetermined threshold value. As described above, the radiographic image capturing unit functions as a control unit that controls the adjusting unit that adjusts the temperature of the imaging region to be a predetermined temperature.

  Therefore, according to the present invention, since the computer can be operated in the same manner as the invention described in claim 1, as in the invention described in claim 1, an increase in power consumption is suppressed and an increase in power consumption is suppressed. It is possible to suppress deterioration of the image quality of the radiation image due to the temperature distribution spots.

  According to the radiographic image capturing system and program of the present invention, the difference between the maximum temperature and the minimum temperature at different positions in the radiographic region in the radiographic image capturing unit provided in the radiographic image capturing apparatus is equal to or greater than a predetermined threshold value. Since the adjustment means for adjusting the temperature of the imaging region in the radiographic image capturing unit to be a predetermined temperature is controlled so that the operation is started in the case of On the other hand, it is possible to suppress the deterioration of the image quality of the radiation image due to the temperature distribution spots in the imaging region.

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 rear view which shows the structure of the radiation detector 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 temperature control process program which concerns on 1st Embodiment. It is a flowchart which shows the flow of a process of the temperature control process program which concerns on 2nd 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 Embodiment]
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 the HDD 110 (see FIG. 6) 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 wired communication. Not limited to this, various types of information may be transmitted and received by wireless communication between at least one of the radiation generator 34 and the console 42 and between the electronic cassette 32 and the console 42.

  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.

  Here, in the electronic cassette 32 according to the present exemplary embodiment, the surface of the heater portion 64 is in close contact with the inner surface of the surface opposite to the irradiation surface 56 of the housing 54. In the electronic cassette 32 according to the present embodiment, the heater portion 64 is adhered to the housing 54 by being bonded with an adhesive, but is not limited thereto, and the heater portion 64 is attached by a holding member such as a screw. It is good also as a form etc. which hold | maintain so that it may closely_contact | adhere to the housing | casing 54.

  On the other hand, a case 31 that houses an electronic circuit including a microcomputer and a rechargeable and detachable battery 96 </ b> A is disposed on one end side inside the housing 54. 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.

  FIG. 5 shows the configuration of the radiation detector 60 according to the present exemplary embodiment.

  As shown in the figure, the radiation detector 60 according to the present embodiment is provided with a plurality (13 in the present embodiment) of temperature sensors 60A at different positions. In the electronic cassette 32 according to the present embodiment, each temperature sensor 60A is adjacent to the entire region corresponding to the imaging region on the surface opposite to the radiation X incident surface of the radiation detector 60. It is arranged in a staggered manner so that the distance to 60A is substantially the same (so that the density is substantially uniform).

  Next, with reference to FIG. 6, the configuration of the main part 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. 5) 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 and each temperature sensor 60A. The operation of the heater unit 64 is controlled by the CPU 92A provided in the cassette control unit 92, while the CPU 92A The temperature detected by the temperature sensor 60A can be grasped.

  The cassette control unit 92 is connected to the connection terminal 32 </ b> A and is a communication interface (I / F) unit that transmits and receives various information to and from the console 42 while being connected to the console 42 via the communication cable 120. 94 is connected.

  The electronic cassette 32 is provided with a power supply unit 96. The power supply unit 96 incorporates the battery (secondary battery) 96A described above so as not to impair the portability of the electronic cassette 32, and supplies power from the charged battery 96A to a predetermined portion. In FIG. 6, illustration of wirings that connect the power supply unit 96 and each unit of the power supply destination is omitted.

  As described above, in the imaging system 18 according to the present embodiment, the electronic cassette 32 and the console 42 are connected by the communication cable 120 to transmit and receive various types of information, but the communication cable 120 also has a power supply line. The driving power for each part of the electronic cassette 32 is supplied from the console 42 via the communication cable 120.

  The electronic cassette 32 according to the present embodiment is always supplied from the console 42 when connected to the console 42 via the communication cable 120 so that radiographic imaging can be started in a short time. The driving power is supplied to the parts used for radiographic imaging such as the radiation detector 60 and the cassette controller 92.

  However, in order to improve the portability of the electronic cassette 32, the communication cable 120 is configured to be detachable from the electronic cassette 32. When the electronic cassette 32 is moved, the communication cable 120 is removed from the electronic cassette 32. become. In order to prevent the communication cable 120 from being lost, the communication cable 120 is always connected to the console 42 in the imaging system 18 according to the present embodiment.

  The battery 96A supplies driving power to the minimum necessary part of the electronic cassette 32 when the electronic cassette 32 is not connected to the console 42 by the communication cable 120. In this case, the electronic cassette 32 supplies driving power to the cassette control unit 92 and supplies driving power to the heater unit 64 and each temperature sensor 60A as necessary.

  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.

  The console 42 is connected to the connection terminal 42A and is connected to the radiation generator 34 via the communication cable 122. The console 42 transmits and receives various information to and from the radiation generator 34. The communication I / F unit 118 is connected to the connection terminal 42B and transmits / receives various information to / from the electronic cassette 32 while being connected to the electronic cassette 32 via the communication cable 120.

  CPU 104, ROM 106, RAM 108, HDD 110, display driver 112, operation input detection unit 114, communication I / F unit 116, and communication I / F 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, and controls the display of various information on the display 100 via the display driver 112, the communication I / F unit 116 and the communication I / F unit 118. Control of transmission and reception of various types of information with the radiation generator 34 and 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 is connected to the radiation source 130 and the connection terminal 34A, and transmits and receives various information such as exposure conditions to and from the console 42 while being connected to the console 42 via the communication cable 122. A communication I / F unit 132 to perform, and a radiation source control unit 134 that controls the radiation source 130 based on the received exposure conditions.

  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. 7, the operation of the console 42 when radiographic images are taken will be described. FIG. 7 is a flowchart showing a 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. 8 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 with the communication cable 120 removed, the holding unit 150 of the standing platform 45 or the holding unit of the prone platform 46 depending on the input posture at the time of photographing. After the communication cable 120 is connected after being held at 152 and the subject is positioned at a predetermined imaging position, an end button displayed near the lower end of the initial information input screen is displayed via the operation panel 102. Specify. 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 condition input on the initial information input screen is transmitted to the radiation generator 34 and the electronic cassette 32 via the communication I / F unit 116 and the communication I / F unit 118, respectively. Set. In response to this, the radiation source controller 134 of the radiation generator 34 prepares for exposure under the received exposure conditions.

  In the next step 306, instruction information for instructing the start of exposure is transmitted to the radiation generator 34 and the electronic cassette 32 via the communication I / F unit 116 and the communication I / F unit 118, respectively.

  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 via the communication I / F unit 94 after the photographing is completed.

  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.

  By the way, when the radio cassette is taken by moving the electronic cassette 32 on which the radiographic image has been taken to a base that is not the base on which the radiographing has been performed, and the radiograph is continuously taken, the photographer disconnects the communication cable 120 from the electronic cassette 32. The communication cable 120 is connected after removing and moving to the gantry and holding it on a holding portion provided on the gantry, and radiographic images are taken in the same manner as described above.

  On the other hand, in the electronic cassette 32 according to the present embodiment, when the communication cable 120 is removed and the difference between the maximum temperature and the minimum temperature detected by each temperature sensor 60A is equal to or greater than a predetermined threshold value. Is provided with a temperature adjusting function for adjusting the temperature by the heater section 64.

  Next, with reference to FIG. 9, the effect | action of the electronic cassette 32 at the time of performing the said temperature control function is demonstrated. FIG. 9 is a flowchart showing a flow of processing of the temperature adjustment processing program executed by the CPU 92A in the cassette control unit 92 of the electronic cassette 32 every predetermined period (in this embodiment, 1 second). The program is stored in advance in a predetermined area of the ROM of the memory 92B.

  In step 400 of the figure, it is determined whether or not the communication cable 120 has been removed. If a negative determination is made, the temperature adjustment processing program is terminated. If an affirmative determination is made, the process proceeds to step 402. To do.

  In step 402, the temperature detected by each temperature sensor 60A is received by receiving a signal indicating the temperature detected from each temperature sensor 60A. In the next step 404, the maximum temperature and the minimum temperature acquired. (Hereinafter referred to as “maximum temperature difference”).

  In the next step 406, it is determined whether or not the maximum temperature difference calculated by the processing in step 404 is equal to or greater than a predetermined threshold value TH. If the determination is negative, the temperature adjustment processing program is terminated. If the determination is affirmative, the process proceeds to step 412.

  In step 412, the operation of the heater unit 64 is started by controlling power supply from the battery 96 </ b> A to the heater unit 64, and in the next step 414, each temperature sensor 60 </ b> A is processed in the same manner as in step 402. In step 416, the maximum temperature difference is calculated in the same manner as in step 404.

  In the next step 418, it is determined whether or not the maximum temperature difference calculated by the process in step 416 is less than the threshold TH. If a negative determination is made, the process returns to step 414, but an affirmative determination is made. At this point, the process proceeds to step 420.

  In step 420, the operation of the heater unit 64 is stopped by controlling the power supply from the battery 96A to the heater unit 64, and then the temperature control processing program is terminated.

  The threshold value TH may be set as a fixed value in advance, but may be set as appropriate by a photographer or the like according to the required quality of the radiographic image.

  As described in detail above, according to the present embodiment, the radiation image capturing unit (in this embodiment, the radiation detector 60) provided in the radiation image capturing apparatus (in this embodiment, the electronic cassette 32). ) In which the difference between the maximum temperature and the minimum temperature at different positions in the imaging region (in this embodiment, the maximum temperature difference) is equal to or greater than a predetermined threshold (in this embodiment, the threshold TH). The adjustment means (in this embodiment, the heater unit 64) is adjusted so that the temperature of the imaging region in the radiographic image capturing unit becomes a predetermined temperature so that the operation is started. In addition, it is possible to suppress deterioration in the image quality of the radiation image due to uneven temperature distribution in the imaging region while suppressing an increase in power consumption.

  Further, according to the present embodiment, it is detected that the supply of power for driving to the radiographic image capturing unit is cut off, and the difference between the maximum temperature and the minimum temperature is equal to or greater than a predetermined threshold value. Since the adjusting means is controlled so that the operation is started in a certain case, unnecessary adjustment of the temperature of the imaging region in the radiographic image capturing unit can be avoided, so that power consumption can be further reduced. .

  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.

  In particular, according to the present embodiment, the adjusting means is provided in a housing (in this embodiment, the housing 54) that houses the radiation image capturing unit in the radiation image capturing apparatus. As a result of reducing the influence on the temperature distribution of the imaging region in the radiographic image capturing unit due to the image capturing apparatus coming into contact with an external part such as a gantry, temperature adjustment can be performed more effectively.

  Furthermore, according to the present embodiment, since the control means for controlling the adjustment means (in this embodiment, the cassette control unit 92) is provided in the radiographic imaging apparatus, the control means performs the adjustment. Since the means can be directly controlled, the adjusting means can be controlled more easily than in the case where the control means is configured separately from the radiographic apparatus.

[Second Embodiment]
Next, a second embodiment of the present invention will be described. Note that the configuration of the imaging system 18 according to the second embodiment and the operation at the time of radiographic imaging are the same as those in the first embodiment, and a description thereof will be omitted.

  The electronic cassette 32 according to the second exemplary embodiment measures the driving time of the radiation detector 60 each time a radiographic image is taken, and stores driving time information indicating the driving time in the storage unit 92C. It is supposed to be.

  When the electronic cassette 32 on which the radiographic image has been taken is moved to a base that is not the base on which the radiographing has been performed and the radiographic image is subsequently taken, the photographer can connect the electronic cable 32 to the communication cable 120. This is the same as in the first embodiment in that a radiographic image is taken by connecting the communication cable 120 after detaching and moving the frame to the frame and holding it on the holding unit provided on the frame.

  Next, with reference to FIG. 10, the effect | action of the electronic cassette 32 at the time of performing a temperature control function is demonstrated. FIG. 10 shows a temperature adjustment processing program executed by the CPU 92A in the cassette control unit 92 of the electronic cassette 32 according to the second embodiment every predetermined period (one second in the present embodiment). FIG. 9 is a flowchart showing the flow of the process. Steps for performing the same processing as the temperature adjustment processing program shown in FIG. 9 are assigned the same step numbers as in FIG.

  In step 408 in the figure, drive time information indicating the drive time of the radiation detector 60 at the time of the previous radiographic image capturing is read from the storage unit 92C, and the communication cable is based on the drive time indicated by the read drive time information. The standby time from when the supply of driving power to the radiation detector 60 is cut off by removing 120 to the start of the operation of the heater unit 64 is derived so as to increase as the driving time increases. The waiting time may be derived by calculating using an arithmetic expression derived in advance by an experiment using an actual machine, or the driving time is set as an input value, and the waiting time is set as an output value. It may be derived using a conversion table such as a look-up table.

  In the next step 410, the elapsed time from the time when the determination in step 400 is affirmative, that is, the time when the supply of power for driving to the radiation detector 60 is cut off by removing the communication cable 120 is The process waits until the waiting time derived by the process of step 408 is reached, and then the process proceeds to step 412.

  As described above in detail, according to the present embodiment, the same effects as those of the first embodiment can be obtained, and the radiation image capturing unit is based on the driving time at the previous capturing. , A waiting time from when the supply of driving power to the radiographic imaging unit is interrupted until the operation of the adjusting unit is started is derived, and the supply of driving power to the radiographic imaging unit is shut off Since the adjustment means is controlled so that the operation is started after waiting for the derived waiting time, the power consumption can be further reduced.

  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 each of the above-described embodiments, 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 of the stand 45 150 and at least one of the holding portions 152 of the prone table 46 may be provided. In this case, the electronic cassette 32 may or may not be provided.

  FIG. 11 shows a configuration example in which the heater unit 65 </ b> A is provided in the holding unit 150 of the standing base 45 and the heater unit 65 </ b> B is provided in the holding unit 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 disposed when the electronic cassette 32 is held on the side opposite to the side where the radiation X is incident on the holding unit 150 where the electronic cassette 32 is held. The heater 65B is provided so as to be in contact with the housing 54 of the electronic cassette 32, and the heater 65B is held by the electronic cassette 32 on the opposite side of the holding unit 152 from the side where the radiation X is incident. It is provided so as to come into contact with the casing 54 of the electronic cassette 32 when it is done.

  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, in addition to the heater unit 64, a heater unit to be controlled in the above-described temperature control processing program (see FIGS. 9 and 10) is provided by the electronic cassette 32 in the holding unit in which it is installed. The form which applies the heater part (heater part 65A or heater part 65B) which can be illustrated can be illustrated.

  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.

  In each of the above embodiments, the case where the control means of the present invention is provided in the electronic cassette 32 has been described. However, the present invention is not limited to this, for example, the console 42 or the radiation generating apparatus. 34 may be provided.

  Further, in each of the above embodiments, the case where the heater unit 64 is applied as the adjusting means of the present invention has been described. However, the present invention is not limited to this, for example, electrical heating and Peltier elements or the like A form that can be cooled may be applied, a fan may be applied for cooling, or a combination of these may be used. In the case where a cooling capable device is applied as the adjusting means, the adjusting means is operated when the temperature of the imaging region of the radiation detector 60 is abnormally higher than a predetermined normal imaging temperature. Become. In this case, temperature adjustment can be performed more finely than in the above embodiments.

  Further, in each of the above embodiments, the case where the heating part 64A in which the heating wire 64A is folded and laid in a predetermined direction at substantially equal intervals has been described, but the present invention is limited to this. For example, a configuration in which the heating wire 64A is folded and laid in a plurality of directions may be applied, or a rubber heater described in JP-A-2002-202377 may be applied as an example. Good.

  In each of the above embodiments, the case where the heater portion 64 is brought into close contact with the housing 54 has been described. However, the present invention is not limited to this, and for example, the radiation detector 60, the lead plate 62, It is good also as a form which provides the heater part 64 in between.

  In each of the above embodiments, the case where communication is performed by wired communication between the electronic cassette 32 and the console 42 and between the radiation generator 34 and the console 42 has been described, but the present invention is not limited thereto. For example, at least one of these may be configured to perform communication by wireless communication.

  In each of the above embodiments, the case where the plurality of temperature sensors 60A are arranged in a staggered manner with respect to the radiation detector 60 has been described. However, the arrangement state of the temperature sensors 60A is not particularly limited, and the radiation detector 60 is provided. When the occurrence state of the temperature distribution spot in the imaging region is known in advance, the temperature sensor 60A may be provided at a position where the highest temperature and the lowest temperature occur in the temperature distribution. In this case, since the number of temperature sensors 60A can be only two, it can contribute to cost reduction and power saving.

  Further, in each of the above embodiments, when the communication cable 120 is disconnected and the difference between the maximum temperature and the minimum temperature detected by each temperature sensor 60A is equal to or greater than the threshold value TH, power is supplied to the heater unit 64. Although the case of starting is described, the present invention is not limited to this. For example, the heater is used when the difference between the maximum temperature and the minimum temperature is equal to or greater than the threshold value TH regardless of the connection state of the communication cable 120. The power supply to the unit 64 may be started. In this case, the point that power supply to the heater unit 64 is stopped when the difference between the maximum temperature and the minimum temperature is less than the threshold value TH is the same as in each of the above embodiments.

  Further, in each of the above embodiments, the case where the temperature of the imaging region in the radiation detector 60 is uniformly heated by the heater unit 64 when performing the temperature adjustment function has been described, but the present invention is not limited thereto. For example, the heating wire 64 </ b> A laid on the heater unit 64 is provided at a position corresponding to a partial region in the imaging region of the radiation detector 60 where the temperature tends to decrease compared to other regions. The power supply to the heater unit 64 may be started when the difference between the maximum temperature and the minimum temperature becomes equal to or greater than the threshold value TH. In this case, power consumption can be further reduced as compared with the above embodiments.

  Further, in each of the above embodiments, the case where the temperature control by the heater unit 64 is started assuming that the power supply to the radiation detector 60 is interrupted when the communication cable 120 is removed has been described. The present invention is not limited to this. For example, although the communication cable 120 is connected, temperature control is started when it is detected that the power supply to the radiation detector 60 has been cut off for some reason. It is good also as a form to do.

  In addition, the configuration of the RIS 10 described in the above embodiments (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 section 64 (see FIG. 3). 4), the configuration of the radiation detector 60 (see FIG. 5), and the configuration of the imaging system 18 (see FIG. 6) are merely examples, and unnecessary portions are within the scope not departing from the gist of the present invention. Needless to say, it can be deleted, a new part can be added, or the connection state can be changed.

  Furthermore, the processing flow of the various programs described in the above embodiments (see FIGS. 7, 9, and 10) is also an example, and unnecessary steps are deleted without departing from the gist of the present invention. It goes without saying that new 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 60A Temperature sensor 64 Heater 64A Heating wire 64B Plate members 65A and 65B Heater 92 Cassette control unit 92A CPU
94 Communication I / F unit 100 Display 102 Operation panel 104 CPU
106 ROM
110 HDD
118 Communication I / F unit 130 Radiation source

Claims (11)

A radiographic image capturing apparatus including a radiographic image capturing unit that captures a radiographic image;
Adjusting means for adjusting the temperature of the imaging region in the radiation image capturing unit to be a predetermined temperature;
A plurality of temperature detecting means for individually detecting temperatures at different positions of the imaging region in the radiographic imaging unit;
Control means for controlling the adjustment means so that the operation is started when the difference between the maximum temperature and the minimum temperature detected by the plurality of temperature detection means is equal to or greater than a predetermined threshold;
Including radiographic imaging system. A supply state detection means for detecting a supply state of power for driving to the radiographic imaging unit;
The control unit detects that the supply of driving power to the radiographic imaging unit is interrupted by the supply state detection unit, and the difference between the maximum temperature and the minimum temperature is equal to or greater than a predetermined threshold value. The radiographic imaging system according to claim 1, wherein the adjustment unit is controlled so that the operation is started when Based on the driving time of the radiographic image capturing unit at the time of previous imaging, a standby time from when the supply of driving power to the radiographic image capturing unit is interrupted until the operation of the adjusting unit is started is derived. Further comprising a derivation means,
The control unit controls the adjustment unit so that the operation is started after waiting for the standby time derived by the deriving unit after the supply of driving power to the radiographic imaging unit is cut off. The radiation image capturing system according to claim 2. 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 6, wherein the adjusting unit is provided in a housing that houses the radiographic image capturing unit in the radiographic image capturing apparatus. The adjustment unit is provided in a holding device that holds the radiographic image capturing device when the radiographic image is captured so as to contact the radiographic image capturing device in a state where the radiographic image capturing device is held. The radiographic imaging system of any one of Claims 1-5. The radiographic image capturing system according to claim 1, wherein the control unit is provided in the radiographic image capturing apparatus. The radiographic image capturing system according to claim 1, wherein the control unit is configured separately from the radiographic image capturing apparatus. Computer
A temperature detecting means for individually detecting temperatures at different positions of the imaging region in the radiographic image capturing unit of the radiographic image capturing apparatus including the radiographic image capturing unit configured to capture a radiographic image;
The temperature of the imaging region in the radiographic image capturing unit is started so that the operation is started when the difference between the maximum temperature and the minimum temperature detected by the temperature detecting means is equal to or greater than a predetermined threshold. Control means for controlling adjusting means for adjusting to a predetermined temperature;
Program to function as.

Images