JP7003647B2 - Radiography equipment and radiography system - Google Patents

Description

The present invention relates to a radiographic apparatus and a radiological imaging system including the apparatus.

Among the radiographing devices that generate image data by receiving radiation, there is a so-called indirect type equipped with a flat plate scintillator and a flat plate sensor substrate arranged in parallel with the scintillator. .. In such an indirect radiography device, the scintillator emits light according to the intensity of the radiation received from the outside, and each pixel of the sensor substrate accumulates a charge according to the intensity of the light received from the scintillator, and the amount of charge of each pixel. Is converted into a signal value to generate image data.
On the other hand, among the radiographic imaging devices, there is a portable device called an FPD (Flat Panel Detector). Such a portable radiographic imaging device is often equipped with a wireless module for wireless communication with the outside, and can wirelessly transmit the generated image data to the image display device.

However, in an indirect radiography device that performs such wireless communication, heat is generated when the wireless module transmits data, which causes the temperature of the scintillator to partially rise and the sensitivity of some pixels to fluctuate, resulting in generation. There was a problem that density unevenness occurred in the image data.
Therefore, conventionally, a technique has been proposed in which the temperature of a wireless module during communication is monitored and the data to be transmitted is changed according to whether or not the temperature exceeds a threshold value (see Patent Document 1). Specifically, when the temperature is above the threshold value, only the preview data having a small amount of data is transmitted, and when the temperature is below the threshold value, the preview and the image data are transmitted.
By using this technique, it is possible to prevent image data having uneven density from being used for diagnosis.

Japanese Unexamined Patent Publication No. 2014-44179

In photography using the technique described in Patent Document 1, as described above, image data is not transmitted when the temperature of the wireless module exceeds the threshold value, but the scintillator may be housed in a housing. Yes, once the temperature rises, it takes some time to return to the original temperature. Therefore, once the temperature of the wireless module exceeds the threshold value and the transmission of the image data is stopped, the state in which the image data cannot be transmitted continues for a relatively long time.
For this reason, it takes time from shooting until the image is displayed on the external image display device, which may delay the diagnosis.

The present invention has been made in view of the above problems, and in a radiographic apparatus capable of transmitting generated image data to the outside by wireless communication, the heat generation of the wireless module is suppressed without stopping the transmission of the image data. The purpose is.

In order to solve the above problems, the radiography apparatus of the present invention is used.
A sensor panel having a sensor substrate on which a plurality of pixels capable of accumulating charges according to the irradiated radiation are arranged , and a sensor panel.
An image generation means that generates image data based on the electric charge accumulated by each pixel of the sensor substrate.
A wireless module equipped with a plurality of antennas and capable of transmitting image data generated by the image generation means to the outside by wireless communication.
A first temperature sensor that measures the temperature of a portion of the sensor panel near the wireless module, and
It is characterized by comprising a communication control means for controlling the number of antennas used by the wireless module for transmitting image data based on the measured value of the temperature sensor.
Further, the radiography apparatus of the present invention is
A sensor board on which multiple pixels capable of accumulating electric charges according to the irradiated radiation are arranged, and
An image generation means that generates image data based on the electric charge accumulated by each pixel of the sensor substrate.
A wireless module equipped with a plurality of antennas and capable of transmitting image data generated by the image generation means to the outside by wireless communication.
A shooting mode setting means for setting a shooting mode that defines the operation of the image generation means to one of a plurality of shooting modes in which the amount of image data to be generated is different.
It is characterized by comprising a communication control means for controlling the number of antennas used by the wireless module for transmitting image data based on the shooting mode set by the shooting mode setting means.

According to the present invention, it is possible to suppress heat generation of the wireless module without stopping the transmission of image data.

It is a block diagram which shows the schematic structure of the radiological imaging system which concerns on 1st and 2nd Embodiment of this invention. It is a perspective view of the radiological imaging apparatus included in the radiological imaging system according to the first and second embodiments. FIG. 2 is a sectional view taken along line III-III of FIG. It is a top view of the sensor substrate provided in the radiography apparatus which concerns on 1st and 2nd Embodiment. It is a block diagram which shows the electric structure of a part of the radiographing apparatus which concerns on 1st Embodiment. It is a schematic diagram which shows the arrangement example of the 1st temperature sensor provided in the radiography apparatus which concerns on 1st Embodiment. It is a schematic diagram which shows the arrangement example of the 1st temperature sensor and the 2nd temperature sensor provided in the radiography apparatus which concerns on 1st Embodiment. It is a flowchart which shows the communication speed control process executed by the radiographing apparatus which concerns on 1st Embodiment.

<First Embodiment>
Hereinafter, the first embodiment of the present invention will be described with reference to the drawings. However, the present invention is not limited to those shown in the drawings.

[Configuration of radiography system]
First, a schematic configuration of the radiography system according to the present embodiment will be described. FIG. 1 is a block diagram showing the configuration of the radiography system 100 of the present embodiment.
As shown in FIG. 1, the radiography system 100 of the present embodiment is composed of a radiation irradiation device 1, a radiography device 2, an image display device 3, and the like.
Further, the radiography system 100 can be connected to a radiological information system (RIS), a picture archiving and communication system (PACS), etc. (not shown).

The radiation irradiation device 1 generates radiation, and includes a generator 11, an exposure switch 12, a radiation source 13, and the like.
The generator 11 applies a voltage corresponding to preset irradiation conditions (tube voltage, tube current, irradiation time (mAs value), etc.) to the radiation source 13 based on the operation of the exposure switch 12. It is configured to be possible.
The radiation source 13 (tube) has a rotating anode, a filament, and the like (not shown). Then, when a voltage is applied from the generator 11, the filament irradiates an electron beam corresponding to the applied voltage toward the rotating anode, and the rotating anode emits radiation X (X-rays or the like) having a dose corresponding to the intensity of the electron beam. ) Is to be generated.

Although FIG. 1 illustrates that the exposure switch 12 is connected to the generator 11, the exposure switch 12 may be provided in another device (for example, an operation console (not shown)).
Further, the radiation irradiation device 1 may be installed in the photographing room or may be configured to be movable by incorporating it into a round-trip vehicle or the like.

The radiological imaging device 2 is wirelessly connected to the image display device 3 so as to be able to communicate with each other.
Then, the radiography apparatus 2 can generate image data of a radiation image corresponding to the radiation received from the outside and transmit it to the image display apparatus 3.
The details of the radiological imaging apparatus 2 will be described later.

The image display device 3 is configured to have a display unit 3a by a PC, a mobile terminal, or a dedicated device, and is wirelessly connected to the radiographing device 2 and the like.
Then, the image display device 3 can wirelessly receive image data from the radiographic imaging device 2 and display a diagnostic image based on the image data on the display unit 3a.
In addition, for example, a console for setting various imaging conditions of the radiation irradiation device 1 and the radiation imaging device 2, a dedicated analysis device for performing predetermined image processing on the image data, and the like are connected to the radiation imaging system 100. They may be used as an image display device 3.

[Configuration of radiography equipment]
Next, the configuration of the radiography apparatus 2 included in the radiological imaging system 100 will be described. 2 is a perspective view of the radiography apparatus 2, FIG. 3 is a sectional view taken along line III-III of FIG. 2, FIG. 4 is a plan view of a sensor substrate included in the radiography apparatus 2, and FIG. It is a block diagram showing a target structure.
Although FIG. 2 illustrates a panel-type portable radiographic apparatus 2, the present invention relates to a so-called stationary radiological imaging apparatus integrally formed with a support base or the like. Is also applicable.

The radiographing apparatus 2 according to the present embodiment is a so-called indirect type that obtains an electric signal by converting the emitted radiation (X-rays or the like) into electromagnetic waves of other wavelengths such as visible light, and is shown in FIGS. As shown, in addition to the housing 21, the scintillator 22, the sensor board 23, the control board 24, the wireless module 25, the battery 26, the temperature sensors 27, 28, etc., which are housed in the housing 21, are provided. There is.

As shown in FIG. 2, a power switch 21a, an operation switch 21b, an indicator 21c, a connector 21d, and the like are provided on the side surface of the housing 21.
Further, one of the plurality of surfaces of the housing 21 is the radiation incident surface 21e.

The scintillator 22 is formed in a flat plate shape with, for example, a columnar crystal of CsI, and emits light when it receives radiation, that is, it emits an electromagnetic wave having a wavelength longer than that of radiation (for example, visible light) with an intensity corresponding to a dose. It has become.
Further, as shown in FIG. 3, the scintillator 22 is arranged in the housing 21 so as to spread in parallel with the radiation incident surface 21e.

In the sensor substrate 23, a plurality of pixels P capable of accumulating electric charges are arranged two-dimensionally and are arranged so as to spread in parallel with the radiation incident surface 21e and the scintillator 22.
In the case of this embodiment, as shown in FIG. 4, it is composed of a substrate 23a, a plurality of scanning lines 23b, a plurality of signal lines 23c, a plurality of radiation detection elements 23d, a plurality of TFTs 23e, a plurality of bias lines 23f, and the like. ing. Then, a rectangular region surrounded by the adjacent scanning lines 23b and the adjacent signal lines 23c becomes one pixel P.
Further, the gate of each TFT 23e is connected to the scanning line 23b, the source is connected to the signal line 23c, and the drain is connected to the radiation detection element 23d.
Further, the end (terminal) of each scanning line 23b is connected to a gate driver (not shown), the end (terminal) of each signal line 23c is connected to a read circuit (not shown), and the bias line 23f is connected to a power supply circuit (not shown). There is.
Hereinafter, the combination of the scintillator 22 and the sensor substrate 23 described above may be referred to as a sensor panel 2a.

As shown in FIGS. 3 and 5, the control board 24 is arranged on the surface of the sensor board 23 opposite to the surface facing the scintillator 22.
The control board 24 is connected to a gate driver (not shown), a readout circuit, a power supply circuit, and the like by wiring (not shown).
Further, the control board 24 includes a RAM, a ROM, and the like (not shown) in addition to the CPU 24a.
The CPU 24a is configured to comprehensively control the operation of each part of the radiography apparatus 2. Specifically, various programs stored in the ROM are read out and expanded in the RAM, and various processes for operating each part are executed according to the programs.

Similar to the control board 24, the wireless module 25 is also arranged on the surface of the sensor board 23 opposite to the surface facing the scintillator 22.
The wireless module 25 includes a plurality of amplifier circuits 25a and a plurality of antennas 25b connected to each amplifier circuit 25a.
Note that FIG. 5 illustrates a wireless module 25 including three sets of an amplifier circuit 25a and an antenna 25b, but two sets or four or more sets may be provided.
Each amplifier circuit 25a is connected to the control board 24 by a command line.

The wireless module 25 configured in this way can transmit various data generated by the CPU 24a to the outside by wireless communication.
Further, the wireless module 25 is capable of communication using MIMO (multiple-input and multiple-output). Specifically, it is possible to increase or decrease the number of antennas 25b (the number of amplifier circuits 25a to be driven) used for data transmission according to the control signal from the CPU 24a of the control board 24.

〔Temperature sensor〕
Next, the temperature sensor included in the radiography apparatus 2 will be described. FIG. 6 is a schematic diagram showing an arrangement example of the first temperature sensor, and FIG. 7 is a schematic diagram showing an arrangement example of the first temperature sensor and the second temperature sensor.

The first temperature sensor 27 is connected to the CPU 24a of the control board 24 and is attached in the vicinity of the sensor panel 2a and the wireless module 25. That is, the temperature of the portion near the wireless module 25 in the sensor panel 2a is measured.
The mounting position of the first temperature sensor 27 is the surface of the sensor panel 2a where the heat generated by the wireless module 25 is greatly affected, that is, the temperature rises to a temperature at which density unevenness occurs in a short time due to the heat generated by the wireless module 25. It is preferable to do. Specifically, for example, as shown in FIGS. 6 (a) and 6 (b), between the sensor panel 2a and the wireless module 25, or as shown in FIG. 6 (c), with the radiation incident surface 21e. It is preferable that the location is in contact with the contour line of the radio module when viewed from an orthogonal direction, the location where the contour line passes, or the location where the contour line is separated from the contour line by a predetermined distance d.

A plurality of temperature sensors may be provided. In that case, the second temperature sensor 28 attached is connected to the CPU 24a of the control board 24, and is a portion of the sensor panel 2a where the first temperature sensor 27 measures the temperature. Will measure the temperature of different parts.
The mounting position of the second temperature sensor 28 may be a position on the surface of the sensor panel 2a that is farther than the first temperature sensor 27 when viewed from the center of the wireless module 25, but the wireless module 25 on the sensor panel 2a. It is preferable that the surface is a portion where the influence of the heat generation is small, that is, a portion where the temperature does not rise so much even if the heat generation of the wireless module 25 continues for a predetermined time. Specifically, for example, as shown in FIG. 7, it is preferable that the outside of the contour line of the radio module (including the case where it touches the contour line) when viewed from a direction orthogonal to the radiation incident surface 21e. ..

The CPU 24a included in the control board 24 of the radiography apparatus 2 configured in this way has the following functions.
For example, the CPU 24a has a function of generating image data based on the electric charge accumulated by each pixel P of the sensor substrate. Specifically, the gate driver is made to turn off the TFT 23e to store the electric charge generated by the radiation detection element 23d in the pixel P, and then the gate driver is made to turn on the TFT 23e to store the accumulated electric charge via the signal line 23f. Is sent to the read circuit, and image data is generated from a plurality of signal values read by the read circuit.
That is, the CPU 24a serves as an image generation means in the present invention.

Further, the CPU 24a has a function of acquiring a measured value from the first temperature sensor 27.
When there are a plurality of temperature sensors, the function of calculating the temperature difference value by subtracting the other measured value from one of the acquired measured values is further provided.
Further, the CPU 24a has a function of comparing the acquired measured value or the difference value with a predetermined threshold value.
Further, the CPU 24a is used by the wireless module 25 for transmitting image data based on the measured value of the first temperature sensor 27 or the difference value between the measured value of the first temperature sensor 27 and the measured value of the second temperature sensor 28. It has a function of controlling the number of antennas 25b.

The threshold value for comparison is the limit temperature of the measurement target part so that the difference between the sensitivity of the room temperature part in the sensor panel 2a and the sensitivity of the measurement target part of the first temperature sensor 27 is such that the density unevenness can be visually recognized. The values are as follows.
When using a plurality of temperature sensors, the threshold value is such that the difference between the sensitivity of the measurement target portion of the first temperature sensor 27 and the sensitivity of the measurement target portion of the second temperature sensor 28 is such that density unevenness can be visually recognized. The value shall be less than or equal to the limit difference value.
In particular, it is preferable to set the threshold value to a temperature several ° C. lower than the limit temperature or the limit difference value or a difference value from the viewpoint of preventing the occurrence of density unevenness.

[Communication speed control processing]
Next, the communication speed control process executed by the radiographing apparatus 2 will be described. FIG. 8 is a flowchart of the communication speed control process.
In addition to the above functions, the CPU 24a satisfies a predetermined condition (for example, a predetermined operation is performed by the user, the CPU 24a starts transmitting image data to the wireless module 25, power is supplied to the wireless module, and the like. ), It has a function to execute the communication speed control process.

In this communication speed control process, as shown in FIG. 8, first, the measured value of the temperature of the sensor panel 2a is acquired from the first temperature sensor 27 (step S1).
Here, when a plurality of temperature sensors are provided, in step S1, a process of acquiring the measured values of the temperature sensors 27 and 28 and subtracting the other measured values from one measured value to calculate the difference value is performed. conduct.
Next, the acquired measured value or difference value is compared with a predetermined threshold value, and it is determined whether or not the value is equal to or greater than the threshold value (step S2).

When it is determined in step S2 that the measured value or the difference value is equal to or greater than the threshold value (step S2; Yes), it is determined whether or not the number of antennas used by the wireless module for transmitting image data is one. Determination (step S3).
If it is determined in step S3 that the number of antennas used is one (step S3; Yes), the process returns to step S1.
On the other hand, when it is determined in step S3 that the number of antennas used is not one, that is, two or more antennas (step S3; No), it is instructed to reduce the number of antennas used by one. The signal is transmitted to the wireless module (step S4), and the process proceeds to step S5.
When the wireless module 25 receives this signal, it uses one less antenna than before and continues communication.

In step S2, when it is determined that the measured value or the difference value acquired from the temperature sensors 27 and 28 is not equal to or more than the threshold value, that is, less than the threshold value (step S2; No), the number of antennas used is the maximum number. It is determined whether or not there is (step S6).
If it is determined in step S6 that the number of antennas used is the maximum number (step S6; Yes), the process returns to step S1.
On the other hand, when it is determined in step S6 that the number of antennas used is not the maximum number (step S6; No), a signal instructing to increase the number of antennas used is transmitted to the wireless module 25. (Step S7), the process proceeds to step S5.
When the wireless module 25 receives this signal, it uses one more antenna than before and continues communication.

In step S5, it is determined whether or not the user (CPU 24a) is in the process of transmitting image data to the wireless module 25.
If it is determined in step S5 that the image data is being transmitted (step S5; Yes), the process returns to step S1.
On the other hand, when it is determined in step S5 that the image data is not transmitted (step S5; No), the communication speed control process is terminated.
The CPU 24a forms the communication control means in the present invention by executing such a process.
Although the number of antennas used at the start of this process is not particularly specified, it is preferable to use the maximum number of antennas in order to speed up the transmission of image data as much as possible.

As described above, in the radiographing apparatus 2 according to the present embodiment, a flat plate-shaped scintillator 22 that emits light by receiving radiation and a plurality of pixels P capable of accumulating charges are arranged in a two-dimensional manner. A sensor panel 2a having a sensor substrate 23 arranged so as to be parallel to the scintillator 22, a CPU 24a (image generation means) that generates image data based on the charge accumulated by each pixel P of the sensor substrate 23, and a plurality of antennas. A wireless module 25 capable of transmitting image data generated by the CPU 24a to the image display device 3 (external) by wireless communication, and a first measuring the temperature of a portion of the sensor panel 2a in the vicinity of the wireless module 25. It is equipped with a temperature sensor 27 and a CPU 24a (communication control means) that controls the number of antennas 25b used by the wireless module 25 for transmitting image data based on the measured values of the first temperature sensor 27. There is.

Each amplifier circuit 25a of the wireless module 25 generates heat when data is transmitted. Further, as the number of antennas used for data transmission increases, the number of amplifier circuits used also increases, and the amount of heat generated increases accordingly. Then, the heat generated by this wireless module raises the temperature of the adjacent sensor panel 2a.
Since the wireless module 25 is smaller than the sensor panel 2a, it faces a part of the sensor panel 2a. Therefore, when the wireless module 25 generates heat, only a part of the temperature of the sensor panel 2a rises.
The sensitivity of the sensor panel 2a (the emission intensity of the scintillator 22 with respect to the dose of radiation or the amount of electric charge accumulated in the pixel P) changes depending on the temperature of the sensor panel. That is, when the temperature of a part of the sensor panel 2a rises with respect to the surroundings, the sensitivity of the pixel P varies (a state in which the sensitivity differs only in a part of the pixels P).

However, according to the radiography system according to the present embodiment, if the temperature of the portion near the wireless module in the sensor panel 2a exceeds the threshold value while the wireless module 25 is transmitting data, the wireless module 25 is used. Reduce the number of antennas. Therefore, the calorific value of the wireless module 25 decreases, and the temperature of a part of the sensor panel 2a whose temperature has exceeded the threshold value starts to decrease. As a result, uneven density is less likely to occur in the image data being transmitted.

On the other hand, since the radiography apparatus 2 according to the present embodiment does not have a means for cooling the inside, the temperature drop of the sensor panel 2a is gradual. However, since the wireless module 25 continues to transmit image data while reducing the number of antennas used, it is a device that stops transmitting image data when the temperature of the wireless module rises as in the conventional case. In comparison, image data can be transmitted to an image display device such as a console more quickly.
That is, it is possible to suppress the heat generation of the wireless module without stopping the image data transmission, and as a result, it is possible to prevent the situation where the diagnosis is delayed due to the non-delivery of the image data.

Further, when a plurality of temperature sensors are used, the degree of density unevenness that occurs in the image is grasped by detecting the temperature of the part where the influence of heat generation of the wireless module 25 is large and the temperature of the part where the influence is small. You will be able to. Therefore, it is possible to control the number of antennas to be used more accurately than in the case of only one first temperature sensor 27. As a result, image data can be efficiently transmitted without wastefully reducing the number of antennas used for data transmission.

In the communication speed control process, the power consumption per antenna 25b may be controlled according to the number of antennas 25b used by the wireless module 25 for transmitting image data. Specifically, each amplifier circuit 25a is made to increase the power consumption when transmitting a signal instructing to increase the number of antennas to be used, and to reduce the power consumption when reducing the number of antennas.
By doing so, the power control means in the present invention can be achieved, and the heat generation of the wireless module 25 can be suppressed as compared with the case where only the number of antennas to be used is controlled.

<Second embodiment>
Hereinafter, the second embodiment of the present invention will be described. Here, the same reference numerals are given to the same configurations as those of the first embodiment, and the description thereof will be omitted.

In the radiography apparatus 2 included in the radiography system 100 according to the first embodiment, the number of antennas used by the radio module 25 for transmitting image data is controlled based on the measured value of the temperature sensor. The radiological imaging device 2A included in the radiological imaging system 100A according to the present embodiment controls the number of antennas based on the set imaging mode.
Therefore, in the radiography apparatus 2A of the present embodiment, the processing executed by the CPU 24a is different from that of the first embodiment.

The photographing mode defines the photographing operation of the radiation photographing apparatus 2A, and in the present embodiment, there are two types, a still image photographing mode and a moving image photographing mode.
The still image shooting mode is a shooting mode in which one image is shot by operating the exposure switch once. The moving image shooting mode is a shooting mode in which a plurality of frame images are repeatedly shot during one operation of the exposure switch.
Since a moving image is composed of a plurality of frame images, the amount of data is generally larger than that of a still image. That is, the still image shooting mode and the moving image shooting mode are shooting modes in which the amount of image data to be generated is different from each other.

The CPU 24a of the radiography apparatus 2A of the present embodiment receives, for example, a control signal from a console connected to the radiography imaging apparatus 2A, and the operation switch 21b provided in the radiography imaging apparatus 2 is operated. Based on this, it has a function to set the shooting mode to one of a plurality of shooting modes. That is, the CPU 24a serves as the shooting mode setting means in the present invention.
Further, the CPU 24a controls the number of antennas to be used as the shooting mode is set. Specifically, reduce the number of antennas used when the shooting mode is set to movie shooting mode (the number is not the maximum number), and increase the number of antennas used when the shooting mode is set to still image shooting mode (multiple antennas). ). That is, the CPU 24a serves as the communication control means in the present invention.

Since the CPU 24a of the present embodiment does not use temperature for controlling the number of antennas used, the function of acquiring measured values from the temperature sensors 27 and 28 possessed by the CPU 24a of the first embodiment and the temperature It does not have a function to calculate a difference value, a function to compare a measured value or a difference value with a predetermined threshold value, and a function to execute a communication speed control process.

As described above, in the radiography apparatus 2A according to the present embodiment, a flat plate-shaped scintillator 22 that emits light by receiving radiation and a plurality of pixels P capable of accumulating data are arranged in a two-dimensional manner. The CPU 24a is provided with a sensor substrate 23 arranged so as to be parallel to the scintillator 22, a CPU 24a (image generation means) that generates image data based on the charge accumulated by each pixel P of the sensor substrate 23, and a plurality of antennas 25b. The amount of data of the image data generated differs between the wireless module 25 capable of transmitting the image data generated by The wireless module 25 controls the number of antennas 25b used for transmitting image data based on the CPU 24a (shooting mode setting means) set to either the still image shooting mode or the moving image shooting mode and the shooting mode set by the CPU 24a. The CPU 24a (communication control means) is provided.
By doing so, as in the first embodiment, the heat generation of the wireless module can be suppressed without stopping the image data transmission, and as a result, the diagnosis is delayed due to the non-delivery of the image data. It can be made difficult.

Needless to say, the present invention is not limited to each of the above-described embodiments and modifications, and can be appropriately changed as long as it does not deviate from the gist of the present invention.

100,100A Radiation Imaging Device 1 Radiation Irradiation Device 11 Generator 12 Radiation Switch 13 Radiation Source 2, 2A Radiation Imaging Device 21 Housing 21a Power Switch 21b Operation Switch 21c Indicator 21d Connector 21e Radiation Incident Surface 2a Sensor Panel 22 Scintillator 23 Sensor Board 23a Board 23b Scan line 23c Signal line 23d Radiation detection element 23f Bias line 24 Control board 25 Wireless module 25a Amplification circuit 25b Antenna 26 Battery 27 First temperature sensor 28 Second temperature sensor 3 Image display device 3a Display unit P pixel X Radiation

Claims (8)

A sensor panel having a sensor substrate on which a plurality of pixels capable of accumulating charges according to the irradiated radiation are arranged , and a sensor panel.
An image generation means that generates image data based on the electric charge accumulated by each pixel of the sensor substrate.
A wireless module equipped with a plurality of antennas and capable of transmitting image data generated by the image generation means to the outside by wireless communication.
A first temperature sensor that measures the temperature of a portion of the sensor panel near the wireless module, and
A radiography apparatus comprising: a communication control means for controlling the number of antennas used by the wireless module for transmitting image data based on a measured value of the first temperature sensor. The communication control means is
When the measured value of the first temperature sensor is equal to or higher than a predetermined threshold value, the number of antennas used by the wireless module for transmitting image data is reduced.
The radiography apparatus according to claim 1, wherein when the measured value of the first temperature sensor is less than the threshold value, the radio module increases the number of antennas used for transmitting the image data. A second temperature sensor for measuring the temperature of a part different from the part where the first temperature sensor in the sensor panel measures the temperature is provided.
The communication control means controls the number of antennas used by the wireless module to transmit the image data based on the difference value between the measured value of the first temperature sensor and the measured value of the second temperature sensor. The radiography apparatus according to claim 1. The radiography apparatus according to any one of claims 1 to 3, wherein the first temperature sensor is provided between the sensor panel and the wireless module. A sensor board on which multiple pixels capable of accumulating electric charges according to the irradiated radiation are arranged , and
An image generation means that generates image data based on the electric charge accumulated by each pixel of the sensor substrate.
A wireless module equipped with a plurality of antennas and capable of transmitting image data generated by the image generation means to the outside by wireless communication.
A shooting mode setting means for setting a shooting mode that defines the operation of the image generation means to one of a plurality of shooting modes in which the amount of image data to be generated is different.
A radiographic imaging apparatus comprising: a communication control means for controlling the number of antennas used by the wireless module for transmitting image data based on an imaging mode set by the imaging mode setting means. The communication control means is an antenna used by the wireless module to transmit the image data when the shooting mode setting means sets the shooting mode to a moving image shooting mode for shooting a moving image composed of a plurality of frame images. The radiographing apparatus according to claim 5, wherein the number of radiographs is increased. The communication control means includes claims 1 to 6 including power control means for controlling the power used per antenna according to the number of antennas used by the wireless module for transmitting the image data. The radiography apparatus according to any one of the above. A radiation irradiation device that generates radiation, and
The radiography apparatus according to any one of claims 1 to 7.
A radiographic imaging system comprising: an image display apparatus capable of wirelessly receiving image data from the radiographic imaging apparatus and displaying a radiographic image based on the image data.

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