Radiographic apparatus, radiographic system, and control method of radiographic apparatus

Abstract

To provide a radiographic apparatus capable of reducing an influence of noise of a voltage conversion circuit.SOLUTION: A radiographic apparatus includes: a plurality of pixels for generating an image signal based on a radioactive ray; a voltage conversion circuit 401 for converting an input voltage and outputting the converted voltage; a first battery 403 for outputting the voltage; and a power source control part 309 for supplying either the voltage output by the voltage conversion circuit or the voltage output by the first battery as a power source voltage according to an operation state of the radiographic apparatus.SELECTED DRAWING: Figure 5

Description

[Technical field]

[0001] The present disclosure relates to a radiation imaging apparatus, a radiation imaging system, and a method for controlling a radiation imaging apparatus. [Background technology]

[0002] In recent years, radiography devices using flat panel detectors (FPDs) made of semiconductor materials have been used as imaging devices for medical image diagnosis and non-destructive testing using X-rays, etc. This FPD has a pixel array in which multiple pixels that convert radiation into electrical signals are arranged in a two-dimensional matrix, and the FPD converts the electrical signals from the pixel array into digital data to output a digital radiography image for one image (frame). For example, in medical image diagnosis, such radiography devices are used as digital imaging devices for still image capture such as general imaging and video capture such as fluoroscopy. In such imaging devices, in order to further reduce invasiveness and improve the quality of diagnosis, sensors with high sensitivity and high signal-to-noise ratio are required to capture clear images even with low radiation doses.

[0003] On the other hand, a radiation imaging device includes a switching power supply such as a DC / DC power supply that supplies voltage to each circuit board inside. The switching power supply generates high-frequency radiation noise when switched at high frequency. The radiation sensor inside the radiation image detector, which has a sensor array in which photoelectric conversion elements are arranged in a two-dimensional array, handles small signals and is therefore susceptible to the effects of radiation noise, which causes an increase in noise in the captured image.

[0004] Patent Document 1 discloses a method of reducing the noise that is radiated from the power supply circuit and affects the radiation sensor by using a configuration in which the housing has a partition and the radiation sensor and power supply circuit are housed in different compartments.

[0005] Moreover, Patent Document 2 discloses a method for reducing the influence of noise by controlling the driving cycle of a switching power supply and the scanning cycle of a sensor. [Prior art documents] [Patent documents]

[0006] [Patent Document 1] JP 2002-214729 A [Patent Document 2] JP 2005-87254 A Summary of the Invention [Problem to be solved by the invention]

[0007] However, in the method described in Patent Document 1, the radiation sensor and the power supply circuit unit are arranged separately by a partition formed by the housing and the cover, which poses a problem that the size of the horizontal surface of the panel of the radiation image detector becomes large.

[0008] Furthermore, in the method described in Patent Document 2, it is necessary to strictly match the driving cycle of the switching power supply and the scan timing of the sensor for each scan line. Also, when the amount of noise changes, noise reduction may not be sufficient.

[0009] An object of the present disclosure is to provide a radiation imaging apparatus capable of reducing the influence of noise in a voltage conversion circuit. [Means for solving the problem]

[0010] The radiographic imaging device includes a plurality of pixels that generate image signals based on radiation, a voltage conversion circuit that converts an input voltage and outputs the converted voltage, a first battery that outputs a voltage, and a power supply control unit that supplies either the voltage output by the voltage conversion circuit or the voltage output by the first battery as a power supply voltage depending on the operating state of the radiographic imaging device. Effect of the Invention

[0011] According to the present disclosure, it is possible to provide a radiation imaging apparatus capable of reducing the influence of noise in a voltage conversion circuit. [Brief description of the drawings]

[0012] [Figure 1] FIG. 1 is a diagram illustrating an example of the configuration of a radiation imaging system. [Diagram 2] FIG. 2 is a diagram illustrating an example of the configuration of a sensor unit of a radiation imaging apparatus. [Diagram 3] FIG. 2 is a block diagram showing a control signal and an image signal of the radiation imaging apparatus. [Figure 4] 2 is a block diagram showing an example of the configuration of a power supply circuit of a radiation imaging apparatus; [Diagram 5] FIG. 2 is a block diagram showing an example of the configuration of a small power supply unit of a radiation imaging apparatus. [Figure 6] 4 is a timing chart showing an example of a drive sequence of the radiation imaging apparatus. [Figure 7] 2 is a block diagram showing an example of the configuration of a power supply circuit of a radiation imaging apparatus; [Figure 8] 11 is a flowchart showing an operation example. [Figure 9] 4 is a timing chart showing an example of a drive sequence of the radiation imaging apparatus. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0013] Hereinafter, a specific embodiment of the radiation imaging system will be described with reference to the drawings. In the following description and drawings, common components are assigned common symbols across multiple drawings. Therefore, the common components will be described with mutual reference to multiple drawings, and the description of the components assigned common symbols will be omitted as appropriate. In addition, radiation in this specification may include α-rays, β-rays, γ-rays, etc., which are beams created by particles (including photons) emitted by radioactive decay, as well as beams having the same or higher energy, such as X-rays, particle beams, and cosmic rays.

[0014] (First embodiment) 1 is a diagram showing an example of the configuration of a radiation imaging system 100 according to the first embodiment. The radiation imaging system 100 includes a radiation imaging apparatus 101, a console 102, a communication network 103, a power supply device 104, an access point (AP) 105, a radiation tube 106, and a radiation generation apparatus console 107. The radiation imaging system 100 further includes a radiation generation apparatus 108, a connector 109, a gantry 111 for imaging, a bed 112, and a cradle 113.

[0015] The radiation imaging device 101 includes a sensor unit for acquiring a radiation image, and has a wired or wireless communication function, or both wired and wireless communication functions, and is capable of transmitting and receiving data to and from the console 102 via a communication path.

[0016] The console 102 is constructed of a PC having a display function such as a monitor and an input function from the user, and is capable of transmitting instructions from the user to the radiation imaging apparatus 101, receiving images acquired by the radiation imaging apparatus 101 and displaying them to the user. The console 102 also has a wired or wireless communication function, or both wired and wireless communication functions. In the configuration shown in FIG. 1, a stationary type console is illustrated as the console 102, but there are no particular restrictions in the actual operation of the radiation imaging system 100, and a portable notebook PC, tablet device, or the like may be used as the console 102.

[0017] The radiation imaging apparatus 101 may send image data to the console 102 via any one of a communication network 103, a power supply device 104, and an access point (AP) 105 that configure a communication path depending on the configuration status of the radiation imaging system 100. The radiation imaging apparatus 101 may also send image data directly to the console 102. The communication network 103 is, for example, a LAN network, and data can be transmitted and received by connecting the radiation imaging apparatus 101 and the console 102 to the communication network 103 via a wired cable.

[0018] The radiation imaging apparatus 101 has a function capable of receiving power, and by connecting a power supply device 104 capable of supplying power to the radiation imaging apparatus 101, it becomes possible for the power supply device 104 to supply power to the radiation imaging apparatus 101. Furthermore, if the radiation imaging apparatus 101 and the power supply device 104 have a communication function, a configuration may be provided for communication between the power receiving unit of the radiation imaging apparatus 101 and the power supply unit of the power supply device 104. In this way, by connecting the radiation imaging apparatus 101 and the power supply device 104, the radiation imaging apparatus 101 becomes able to receive power and communicate via the power supply device 104. Note that the power reception and communication may be performed by a method having electrical contact or a non-contact method.

[0019] 1, among the lines connecting the radiation imaging apparatus 101 and the power supply device 104, a line 150 is a connection line for communication (wired and / or wireless), and a line 151 is a connection line for power supply. In the configuration shown in Fig. 1, the power supply device 104 is connected to the console 102 via a communication network 103, but is not limited to this. The power supply device 104 and the console 102 may be directly and electrically connected to each other.

[0020] When the radiation imaging apparatus 101 is provided with a wireless communication function, the radiation imaging apparatus 101 may transmit and receive data to and from the console 102 via the AP 105. In the configuration shown in Fig. 1, the AP 105 is connected to the console 102 via the communication network 103, but the AP 105 may be directly and electrically connected to the console 102, similar to the power supply device 104 described above.

[0021] Furthermore, if the radiation imaging apparatus 101, the console 102, the power supply apparatus 104, and the AP 105 have a function for directly transmitting and receiving data to and from each other, they may transmit and receive data to and from each other directly via wires or wirelessly.

[0022] The above is an explanation of an example of a path for transmitting and receiving data between the radiation imaging apparatus 101 and the console 102.

[0023] Here, a description will be given of the cradle 113 which is a charger for the radiation imaging apparatus 101. The internal configuration of the radiation imaging apparatus 101 will be described later, but the radiation imaging apparatus 101 has an internal power source such as a battery, and the internal power source can be charged by supplying power to the radiation imaging apparatus 101 from an external source. Charging is also possible by receiving power from the power supply device 104 described above, but the radiation imaging system 100 may be provided with the cradle 113 as a device that can be charged by installing the radiation imaging apparatus 101 therein, for example, when radiation image capture is not performed.

[0024] 1 shows an example in which the cradle 113 is disposed independently without communicating with other components of the radiation imaging system 100, but is not limited thereto. A plurality of cradles 113 may have a communication function and be connectable to other components of the radiation imaging system 100 via the communication network 103 or the like. For example, while the radiation imaging apparatus 101 is attached to the cradle 113, communication may be possible between the radiation imaging apparatus 101 and components such as the console 102 via the cradle 113.

[0025] Next, an overview of imaging of the subject 110 using radiation will be described. When imaging the subject 110, the radiation imaging device 101 is placed at a position where it receives radiation that is irradiated from the radiation tube 106 and transmitted through the subject 110.

[0026] In one example of the flow of imaging, a user such as a technician starts up the radiation imaging apparatus 101, and then the user operates the console 102 to put the radiation imaging apparatus 101 into a state in which imaging is possible. Next, the user operates the radiation generator console 107 to set imaging conditions for irradiating radiation (such as the tube voltage, tube current, and irradiation time of the radiation tube 106). After the above processing is completed, the user confirms that imaging preparations including the subject 110 are complete, and presses an exposure switch provided on the radiation generator console 107 to irradiate radiation from the radiation tube 106 via the radiation generator 108. The radiation tube 106 is a radiation source that irradiates radiation.

[0027] When irradiating radiation, the radiation generating device 108 notifies the radiation imaging device 101 of a signal indicating that radiation is about to be irradiated via the connector 109 and the communication network 103. In the configuration shown in Fig. 1, the radiation imaging device 101 and the radiation generating device 108 are connected via the connector 109 and the communication network 103, but the connection is not limited to this form and may be directly connected in the same manner as described above.

[0028] When the radiation imaging apparatus 101 receives a signal to irradiate radiation, the radiation imaging apparatus 101 checks whether preparations for radiation irradiation are complete, and if there are no problems, returns permission for irradiation to the radiation generation apparatus 108. As a result, radiation is irradiated.

[0029] When the radiation imaging apparatus 101 detects the end of radiation irradiation by various methods, such as by receiving a notification from the radiation generation apparatus 108 or by referring to a prearranged set time, the radiation imaging apparatus 101 starts generating image data of a radiation image. The generated image data is sent to the console 102 through the above-mentioned communication path. The image data sent to the console 102 can be displayed as a radiation image on a display unit included in the console 102, for example.

[0030] Fig. 2 is a diagram showing an example of an equivalent circuit of a sensor unit of a radiation imaging apparatus 101 according to this embodiment. For ease of explanation, Fig. 2 shows the radiation imaging apparatus 101 having pixels of 3 rows x 3 columns. However, an actual radiation imaging apparatus 101 has more pixels, and for example, a 17-inch radiation imaging apparatus 101 has pixels of about 4000 rows x about 4000 columns.

[0031] The radiation imaging apparatus 101 includes a bias power supply 203 , a detection unit 212 , a drive circuit 304 , and a readout circuit 305 .

[0032] The detection unit 212 is a two-dimensional detector having a plurality of pixels arranged in a matrix. Each pixel has a conversion element 202 that converts radiation or light into an electric charge, and a switch element 201 that outputs an electric signal according to the electric charge. In this embodiment, a PIN type photodiode arranged on an insulating substrate such as a glass substrate and made mainly of amorphous silicon is used as a photoelectric conversion element that converts light irradiated on the conversion element 202 into an electric charge, but a MIS type photodiode may also be used.

[0033] As the conversion element 202, an indirect type conversion element having a wavelength converter on the radiation incident side of the above-mentioned photoelectric conversion element for converting radiation into light in a wavelength band detectable by the photoelectric conversion element, or a direct type conversion element for directly converting radiation into electric charges is preferably used.

[0034] A transistor having a control terminal and two main terminals is preferably used as the switch element 201, and in this embodiment, a thin film transistor (TFT) is used. One electrode of the conversion element 202 is electrically connected to one of the two main terminals of the switch element 201, and the other electrode is electrically connected to a bias power supply 203 via a common bias wiring.

[0035] A control terminal of each of the switch elements 201 in the row direction, for example, switch elements T11 to T13, is electrically connected in common to the drive wiring Vg1 in the first row. A drive signal for controlling the conductive state of the switch elements 201 is supplied from the drive circuit 304 to the switch elements 201 on a row-by-row basis via the drive wirings Vg1 to Vg3.

[0036] The other main terminal of each of the multiple switch elements 201 in the column direction, for example, switch elements T11 to T31, is electrically connected to the signal wiring Sig1 in the first column. While the switch element 201 is in a conductive state, the switch element 201 outputs an electrical signal corresponding to the charge of the conversion element 202 to the readout circuit 305 via the signal wirings Sig1 to Sig3. The signal wirings Sig1 to Sig3 arranged in the column direction transmit the electrical signals output from the multiple pixels in parallel to the readout circuit 305.

[0037] The readout circuit 305 is provided with amplifier circuits 206 for amplifying the electrical signals output in parallel from the detection unit 212, corresponding to each of the signal wirings Sig1 to Sig3. Each amplifier circuit 206 includes an integral amplifier 205 for amplifying the output electrical signal, a variable amplifier 204 for amplifying the electrical signal from the integral amplifier 205, a sample hold circuit 207 for sampling and holding the amplified electrical signal, and a buffer amplifier 213.

[0038] The integral amplifier 205 has an operational amplifier that amplifies and outputs the read electrical signal, an integral capacitance, and a reset switch. The integral amplifier 205 can change the amplification factor by changing the value of the integral capacitance. The output electrical signal is input to the inverting input terminal of the operational amplifier, a reference voltage Vref is input from a reference power supply 211 to the non-inverting input terminal of the operational amplifier, and the amplified electrical signal is output from the output terminal. In addition, an integral capacitance is disposed between the inverting input terminal and the output terminal of the operational amplifier.

[0039] The sample-and-hold circuits 207 are provided corresponding to the respective amplifier circuits 206, and are composed of a sampling switch and a sampling capacitor.

[0040] The readout circuit 305 also has a multiplexer 208 that sequentially outputs the electrical signals read out in parallel from each amplifier circuit 206 as a serial image signal, and a buffer amplifier 209 that outputs the image signal after impedance conversion. The image signal, which is an analog electrical signal output from the buffer amplifier 209, is converted into digital image data by an A / D converter 210 and output to the image information processing unit 303 in FIG. 3.

[0041] The reference power supply 211 supplies a reference voltage Vref to the non-inverting input terminal of the operational amplifier in each of the integrating amplifiers 205. The bias power supply 203 supplies a bias voltage in common to the other electrode of each of the conversion elements 202 via a bias line Bs.

[0042] The drive circuit 304 outputs drive signals having a conductive voltage Vcom for turning on the switch element 201 and a non-conductive voltage Vss for turning on the switch element 201 to a non-conductive state to the drive wirings Vg1 to Vg3 in response to the control signals D-CLK, OE, and DIO input from the drive control unit 302 shown in Fig. 3. In this way, the drive circuit 304 controls the conductive state and non-conductive state of the switch element 201 to drive the detection unit 212.

[0043] The control signal D-CLK is a shift clock for the shift register used as the driving circuit 304. The control signal DIO is a pulse for transferring the shift register. The control signal OE is a signal for controlling the output terminal of the shift register. In this way, the driving circuit 304 sets the required driving time and the scanning direction.

[0044] 3 controls the operation of each component of the readout circuit 305 by providing a control signal RC, a control signal SH, and a control signal CLK to the readout circuit 305. Here, the control signal RC controls the operation of the reset switch of the integral amplifier 205. The control signal SH controls the operation of the sample-and-hold circuit 207. The control signal CLK controls the operation of the multiplexer 208.

[0045] 3 is a block diagram showing an example of the flow of control signals and image signals in the radiation imaging apparatus 101 according to this embodiment. The radiation imaging apparatus 101 has a detection unit 212, an image capture control unit 301, a drive circuit 304, a readout circuit 305, a storage unit 306, a wireless communication unit 307, an antenna 308, a power supply control unit 309, an external connection I / F 311, a display unit 312, and an operation unit 313. The image capture control unit 301 has a drive control unit 302 and an image information processing unit 303. The operation unit 313 has an image capture ready state switch 310.

[0046] The image capturing control unit 301 controls the overall operation of the radiation imaging apparatus 101 , and includes a drive control unit 302 and an image information processing unit 303 .

[0047] The drive control unit 302 has a function of controlling the drive circuit 304 .

[0048] The image information processing unit 303 performs various processes on the radiation image data input from the readout circuit 305. The processes performed here may include, for example, defect correction for correcting defects in the image, offset correction for correcting offset data of the image, and noise reduction processing for reducing various noises. Note that the image information processing unit 303 does not need to perform all of the processes for creating a diagnostic image, and some of the processes can be performed by the console 102.

[0049] Offset correction is a process for subtracting unnecessary data such as dark current components that occur during accumulation of a radiation image, and is performed by subtracting offset correction image data obtained without radiation exposure from radiation image data obtained while irradiating radiation. Gain correction is a type of process for correcting image defects caused by individual characteristic differences of pixels arranged in a two-dimensional matrix, and is used to correct the gain difference for each pixel based on gain correction information data obtained by irradiating a uniform dose in the absence of a subject.

[0050] The storage unit 306 stores the radiation image data processed by the image information processing unit 303 in association with the imaging information. The storage unit 306 also stores imaging unit information. The storage unit 306 is implemented by a non-volatile memory such as a flash memory.

[0051] Here, the imaging information includes information on the patient who was imaged, information on the photographer, information on the part imaged, information on the date and time of imaging, a unique ID for identifying the image, etc. Furthermore, when imaging is performed in an imaging mode in which the radiation imaging apparatus 101 detects the start of irradiation of radiation and starts imaging, the imaging information includes information used for radiation detection determination, etc. The imaging unit information includes information such as the name of the imaging unit itself, the sensor size, the connection method (wireless, wired, etc.), etc.

[0052] The storage unit 306 can store one or more pieces of imaging information in association with radiation image data. The storage unit 306 may further store defect information for use in image correction, gain information for gain correction, and an operation history of the radiation imaging apparatus 101.

[0053] The wireless communication unit 307 transmits the radiation image data and imaging information stored in the storage unit 306 to the console 102. The wireless communication unit 307 is connected to an antenna 308, and includes a circuit for transmitting and receiving radio waves via the antenna 308. The wireless communication unit 307 may transmit the radiation image data processed by the image information processing unit 303 to the control device. At this time, the wireless communication unit 307 may transmit the radiation image data and store it in the storage unit 306. The transmission to the console 102 may be performed by wired communication via an external connection interface (represented as external connection I / F in the figure) 311.

[0054] The power supply control unit 309 is a unit for controlling the power supply of the radiation imaging apparatus 101. A specific operation will be described later.

[0055] The display unit 312 is equipped with a display device for indicating the state of the radiation imaging apparatus 101. The display device indicates the state of the imaging unit (standby state or imaging possible state) and the charge level of the main battery 314 in Fig. 4 with an LED. Note that the display device is not limited to an LED, and may be a liquid crystal display or a touch-operable display.

[0056] The operation unit 313 has a plurality of switches that can be input from the outside, and is equipped with an image capture ready state switch 310 that serves as a trigger for transition to an image capture ready state.

[0057] 4 is a block diagram showing an example of power supply to the radiation imaging apparatus 101. The radiation imaging apparatus 101 includes an image capture control unit 301, a main battery 314, a power supply unit 400, a voltage conversion circuit 401, a readout unit 411, and a drive unit 412.

[0058] The image capture control unit 301 includes a drive control unit 302 , an image information processing unit 303 , and a voltage conversion circuit 401 .

[0059] The readout unit 411 includes a readout circuit 305 and a small power supply unit 404. The small power supply unit 404 includes a voltage conversion circuit 401, a switching circuit 402, and a sub-battery 403. The drive unit 412 includes the drive circuit 304 and the voltage conversion circuit 401.

[0060] The power supply unit 400 is connected to an external connection I / F 311 and a main battery 314 that is detachable from the radiation imaging apparatus 101 .

[0061] A lithium ion battery is preferably used as the main battery 314, but other types of batteries may be used. For example, the main battery 314 may be a secondary battery such as a lithium ion capacitor battery, a lithium polymer battery, an all-solid-state battery, or a nickel-metal hydride battery, or may be a non-rechargeable primary battery. The main battery 314 may be either detachable or non-detachable.

[0062] In this embodiment, both the external connection I / F 311 and the main battery 314 are connected to the power supply unit 400, but only one of them may be connected.

[0063] The power supply unit 400 supplies power from the power supply device 104 and main battery 314 connected to the external connection I / F 311 to a voltage conversion circuit 401 of each functional unit such as a drive unit 412 and a readout unit 411 .

[0064] The voltage conversion circuit 401 is a circuit configured with, for example, a switching regulator. The voltage conversion circuit 401 converts the voltage supplied from the power supply unit 400 into a voltage required by each functional unit.

[0065] 4, in the readout section 411, a switching circuit 402 is connected to the output destination of a voltage conversion circuit 401. A sub-battery 403 is also connected to this switching circuit 402. Hereinafter, for the sake of simplicity, the combination of the voltage conversion circuit 401, the switching circuit 402, and the sub-battery 403 will be referred to as a small power supply unit 404.

[0066] 4, the small power supply unit 404 is disposed in the readout section 411, and the readout circuit 305 is connected to the small power supply unit 404, but it may be disposed in another location. For example, the small power supply unit 404 may be disposed in the drive section 412, and the output destination of the small power supply unit 404 may be connected to the drive circuit 304. Also, for example, if the readout circuit 305 and the drive circuit 304 operate at the same voltage, the power output from one small power supply unit 404 may be used by the readout circuit 305 and the drive circuit 304.

[0067] Fig. 5 is a block diagram showing an example of the configuration of the small power supply unit 404 in Fig. 4. The small power supply unit 404 has a voltage conversion circuit 401, a switching circuit 402, and a sub-battery 403.

[0068] 4, is non-detachable, and is configured to store power at a voltage converted by the voltage conversion circuit 401. That is, the voltages of the main battery 314 and the sub-battery 403 are different.

[0069] The switching circuit 402 is configured to be able to switch the power supply to each unit connected in the subsequent stage by changing the switch. Specifically, the switching circuit 402 can switch between supplying power supplied from the power supply unit 400 and voltage-converted by the voltage conversion circuit 401, or supplying power stored in the sub-battery 403.

[0070] Since the sub-battery 403 stores power at a voltage converted by the voltage conversion circuit 401, power can be supplied to the subsequent stage at approximately the same voltage whether from the voltage conversion circuit 401 or from the sub-battery 403.

[0071] The power supply control unit 309 controls the operation of the voltage conversion circuit 401 and the switching of the switching circuit 402. The power supply control unit 309 also monitors the voltage of the sub-battery 403. For example, when the power supply control unit 309 detects that the voltage of the sub-battery 403 has dropped and the remaining power is low, it switches the switching circuit 402 and performs control such as starting charging the sub-battery 403.

[0072] The sub-battery 403 can be selected from various types of batteries, such as secondary batteries such as a lithium ion battery, a lithium ion capacitor battery, a lithium polymer battery, an all-solid-state battery, a nickel-metal hydride battery, and the like, and primary batteries. The sub-battery 403 may also be in a removable form. The sub-battery 403 can be optimally configured by arbitrarily changing the type of the sub-battery 403 according to the voltage, current, capacity, and the like required for each functional unit.

[0073] 6 is a timing chart showing an example of the drive timing of the radiation imaging apparatus 101. When power is applied to the sensor unit, the radiation imaging apparatus 101 performs preparatory drive to stabilize the conversion elements 202. In the preparatory drive, a reset operation is performed to remove electric charges generated by accumulation of dark current, and the characteristics of the conversion elements 202 are stabilized. The reset operation resets the dark current component flowing through the conversion elements 202 by turning on / off the switch elements 201 row by row. After a certain period of time has passed, the radiation imaging apparatus 101 issues a notification permitting irradiation of radiation.

[0074] At this time, the power supply control unit 309 operates the voltage conversion circuit 401 in the small power supply unit 404. Power is supplied to each functional unit of the radiation imaging apparatus 101 from the voltage conversion circuit 401. Note that the sub-battery 403 may be charged during the preparatory driving period. At time t1, when the exposure switch of the radiation generator console 107 is pressed, radiation is emitted from the radiation tube 106.

[0075] When the radiation imaging apparatus 101 detects irradiation of radiation through communication with the radiation generation apparatus 108 or various detection methods, the radiation imaging apparatus 101 transitions from preparatory driving to imaging operation. First, the radiation imaging apparatus 101 performs an accumulation operation. When radiation hits the radiation imaging apparatus 101, electric charge is accumulated in the detection unit 212.

[0076] The radiation imaging apparatus 101 transitions to imaging operation. Then, the power supply control unit 309 stops the operation of the voltage conversion circuit 401 in the small power supply unit 404, and controls the switching circuit 402 so that power is supplied to each functional unit of the radiation imaging apparatus 101 from the sub-battery 403. During the imaging operation, the power supply control unit 309 continues the power supply from the sub-battery 403. At this time, the operation of the voltage conversion circuits 401 other than the small power supply unit 404 does not need to be stopped.

[0077] At time t2, when the end of radiation irradiation is detected by various methods, such as by notification from the radiation generation device 108 or by referring to a prearranged set time, the radiation imaging device 101 transitions from the accumulation operation to the readout operation. In the readout operation, the switch elements 201 are turned on row by row to read out the charges accumulated in the detection units 212.

[0078] Between times t3 and t4, the radiation imaging apparatus 101 causes the detection unit 212 to accumulate electric charges for a predetermined time in order to correct the dark current component by offset correction.

[0079] At time t4, the radiation imaging apparatus 101 performs an operation of reading out a signal corresponding to the charge accumulated in the detection unit 212.

[0080] When the second readout operation is completed, at time t5, the radiation imaging apparatus 101 ends the imaging operation. Thereafter, the radiation imaging apparatus 101 continues preparatory driving in preparation for the next imaging.

[0081] When the preparatory driving is started, the power supply control unit 309 may operate the voltage conversion circuit 401 in the small power supply unit 404 and control the supply of power to each functional unit of the radiation imaging apparatus 101 to be performed from the voltage conversion circuit 401 .

[0082] By irradiating radiation in either the first imaging operation or the second imaging operation, image data for offset correction is obtained in the imaging operation in which radiation is not irradiated.

[0083] In this embodiment, in the first imaging operation, a signal corresponding to the charge accumulated by irradiation with radiation is read out. Next, the radiation imaging apparatus 101 performs preparatory driving for a predetermined time, performs the second imaging operation without irradiating radiation, and reads out the signal. In order to correct the dark current component, it is desirable that the accumulation time of the second imaging operation is the same as that of the first imaging operation as much as possible. Also, in the first imaging operation, image data for correcting the dark current component may be obtained without irradiating radiation, and in the second imaging operation, image data may be obtained by irradiating radiation.

[0084] As described above, in this embodiment, during imaging operation, the radiation imaging apparatus 101 stops the operation of the voltage conversion circuit 401 in the small power supply unit 404 and supplies power from the sub-battery 403. As described above, the switching regulator used in the voltage conversion circuit 401 generates high-frequency radiation noise and conduction noise. In particular, when the detection unit 212, the drive circuit 304, and the readout circuit 305 receive these noises during image readout, the noise is superimposed on the image.

[0085] During imaging operation, the generation of noise is suppressed by stopping the operation of the voltage conversion circuit 401 in the small power supply unit 404. In addition, in order to continue the operation of the radiation imaging apparatus 101 even if the operation of the voltage conversion circuit 401 is stopped, the sub-battery 403 is used to supply power from the sub-battery 403 during readout operation.

[0086] Noise generated from the secondary battery used in the sub-battery 403 is generally less than noise generated from the voltage conversion circuit (switching regulator) 401. By using power supply from the sub-battery 403, the readout circuit 305 can perform a readout operation, thereby reducing noise superimposed on the image.

[0087] In FIG. 4, the small power supply unit 404 is disposed within the readout section 411. However, it is preferable to place the small power supply unit 404 in a section that supplies power to functional sections that handle analog signals such as the readout section 411, as this provides a high noise reduction effect.

[0088] In addition, in this embodiment, the operation of the voltage conversion circuit 401 in the small power supply unit 404 is stopped during the shooting operation, but the period during which the operation of the voltage conversion circuit 401 is stopped may be only for at least one readout operation during the shooting operation.

[0089] As described above, the detection unit 212 has a plurality of pixels. The plurality of pixels generate image signals based on radiation. The readout circuit 305 reads out the image signals generated by the plurality of pixels of the detection unit 212.

[0090] The voltage conversion circuit 401 converts an input voltage and outputs the converted voltage. The sub-battery 403 outputs a voltage. The power supply control unit 309 supplies either the voltage output by the voltage conversion circuit 401 or the voltage output by the sub-battery 403 as a power supply voltage to each functional unit according to the operating state of the radiation imaging apparatus 101. When the power supply control unit 309 supplies the voltage output by the sub-battery 403 as the power supply voltage, it stops the operation of the voltage conversion circuit 401.

[0091] The voltage conversion circuit 401 is, for example, a switching regulator. The sub-battery 403 is charged by the voltage output by the voltage conversion circuit 401.

[0092] As shown in FIG. 6, during the preparatory driving period, the power supply control unit 309 supplies the voltage output by the voltage conversion circuit 401 as the power supply voltage, and during the storage operation period and the readout operation period, the power supply control unit 309 supplies the voltage output by the sub-battery 403 as the power supply voltage.

[0093] The preparatory driving period is a period during which a reset operation is performed on the multiple pixels of the detection unit 212. The accumulation operation period is a period during which image signals of the multiple pixels of the detection unit 212 are accumulated. The readout operation period is a period during which the readout circuit 305 reads out image signals.

[0094] Note that the power supply control unit 309 only needs to supply the voltage output by the sub-battery 403 as the power supply voltage and stop the operation of the voltage conversion circuit 401 at least during all or part of the period during which the readout circuit 305 reads out the image signal. During the other periods, the power supply control unit 309 operates the voltage conversion circuit 401 and supplies the voltage output by the voltage conversion circuit 401 as the power supply voltage.

[0095] As described above, according to this embodiment, the radiation imaging apparatus 101 can be used for still image capture such as general imaging in medical diagnosis and for video capture such as fluoroscopy. The voltage conversion circuit 401 can be a noise source like a switching power supply. By using the sub-battery 403 instead of the voltage conversion circuit 401, the radiation imaging apparatus 101 can acquire an image while reducing the influence of noise from the voltage conversion circuit 401.

[0096] Second embodiment Next, a second embodiment will be described. A radiation imaging apparatus 101 in the second embodiment is equipped with a plurality of small power supply units 404 therein. This makes it possible to reduce noise superimposed on an image. Note that explanations of the second embodiment and the first embodiment that overlap will be omitted.

[0097] The second embodiment is similar to the first embodiment with respect to the configuration example of the radiation imaging system 100 in FIG. 1, an example of an equivalent circuit diagram of the sensor unit in FIG. 2, an example of a block diagram showing the flow of control signals and image signals in FIG. 3, and a block diagram of the small power supply unit 404 in FIG. 5.

[0098] Fig. 7 is a block diagram showing an example of power supply to a radiation imaging apparatus 101 according to the second embodiment. The radiation imaging apparatus 101 in Fig. 7 is provided with a small power supply unit 404 instead of the voltage conversion circuit 401 of the radiation imaging apparatus 101 in Fig. 4.

[0099] The radiation imaging apparatus 101 includes an image capture control unit 301 , a main battery 314 , a power supply unit 400 , a small power supply unit 404 , a readout unit 411 , and a drive unit 412 .

[0100] The image capture control unit 301 includes a drive control unit 302 , an image information processing unit 303 , and a small power supply unit 404 .

[0101] The readout unit 411 includes a readout circuit 305 and a small power supply unit 404. The small power supply unit 404 includes a voltage conversion circuit 401, a switching circuit 402, and a sub-battery 403. The drive unit 412 includes a drive circuit 304 and a small power supply unit 404.

[0102] The power supply unit 400 is connected to an external connection I / F 311 and a main battery 314 that is detachable from the radiation imaging apparatus 101. The power supply unit 400 supplies power from the power supply device 104 and the main battery 314 connected to the external connection I / F 311 to small power supply units 404 of each functional unit such as a drive unit 412 and a readout unit 411.

[0103] Although FIG. 7 shows the small power supply units 404 being distributed among the various functional sections, the small power supply units 404 may be arranged together in the vicinity of the power supply section 400, for example.

[0104] The voltage conversion circuits 401 in the small power supply units 404 each convert the voltage of the power supply section 400 into a voltage required at the connection destination. The sub-battery 403 is configured to store power at the voltage converted by the voltage conversion circuit 401. That is, the sub-battery 403 has a different voltage for each small power supply unit 404.

[0105] In addition to the voltage, the battery capacity may also be different for each sub-battery 403. For example, the capacity of the sub-battery 403 can be changed according to the power consumption of the circuit connected to the rear stage of the small power supply unit 404. Specifically, when a circuit with high power consumption is connected, the capacity of the sub-battery 403 is increased. More preferably, the capacity of the sub-battery 403 is set so that the capacity relative to the power consumption is the same for the multiple sub-batteries 403, which is efficient because the multiple sub-batteries 403 consume power at the same rate. In addition, the multiple sub-batteries 403 may be connected to each other so that they can share power.

[0106] Furthermore, when multiple sub-batteries 403 are charged simultaneously, there may be a limit to the charging current. In that case, the power supply control unit 309 can obtain information on the remaining power of the sub-battery 403 and the power consumption during use, and use this information to determine the priority order for charging the multiple sub-batteries 403. In this case, it is preferable for the power supply control unit 309 to control the charging of the sub-battery 403 so that the available shooting time using only the sub-battery 403 is maximized.

[0107] In this way, by arranging a plurality of small power supply units 404, it is possible to increase the number of voltage conversion circuits 401 that the power supply control unit 309 can stop operating during the imaging operation period, thereby enhancing the effect of noise reduction. It is most preferable to arrange the small power supply units 404 in all the functional units in the radiation imaging apparatus 101, as shown in Fig. 7. In particular, when the small power supply units 404 are arranged in the parts that supply power to the functional units such as the reference power supply 211, the drive circuit 304, and the readout circuit 305 in Fig. 2, it is possible to effectively reduce not only the radiation noise but also the conduction noise.

[0108] Next, the operation of the radiation imaging apparatus 101 in this embodiment will be described. The operation of the voltage conversion circuit 401 and the control of the switching circuit 402 connected to the power supply control unit 309 may be controlled according to the operating state of the radiation imaging apparatus 101 shown in Fig. 6, and may also be controlled according to the presence or absence of connection of the power supply device 104 and the main battery 314.

[0109] FIG. 8 is a flowchart showing a control method of the radiation imaging apparatus 101, and is a flowchart showing an example of the operation of the voltage conversion circuit 401 and the control of the switching circuit 402 in the small power supply unit 404.

[0110] In this embodiment, the power supply control unit 309 is configured to be able to check whether there is power supply from the outside via the external connection I / F 311, the connection state of the main battery 314, and the remaining power level of the main battery 314. Furthermore, the power supply control unit 309 is configured to be able to check the remaining power levels of all sub-batteries 403 in the radiation imaging apparatus 101.

[0111] In step S501, the power supply control unit 309 determines whether or not power is being supplied from the power supply device 104 to the power supply unit 400 via the external connection I / F 311. If power is being supplied from the power supply device 104 to the power supply unit 400, the process proceeds to step S504. If power is not being supplied from the power supply device 104 to the power supply unit 400, the process proceeds to step S502.

[0112] In step S502, the power supply control unit 309 determines whether or not the main battery 314 is connected to the power supply unit 400. If the main battery 314 is connected to the power supply unit 400, the process proceeds to step S503. If the main battery 314 is not connected to the power supply unit 400, the process proceeds to step S508.

[0113] In step S503, the power supply control unit 309 determines whether the remaining power of the main battery 314 is greater than the first threshold. If the remaining power of the main battery 314 is greater than the first threshold, the process proceeds to step S504. If the remaining power of the main battery 314 is not greater than the first threshold, the process proceeds to step S508.

[0114] In step S504, the power supply control unit 309 determines whether the remaining power of the sub-battery 403 is greater than the second threshold. If the remaining power of the sub-battery 403 is greater than the second threshold, the process proceeds to step S505. If the remaining power of the sub-battery 403 is not greater than the second threshold, the process proceeds to step S506.

[0115] In step S505, when shooting is in progress, the power supply control unit 309 stops the operation of the voltage conversion circuit 401 and supplies power from the sub-battery 403 to each functional unit via the switching circuit 402. When shooting is not in progress, the power supply control unit 309 operates the voltage conversion circuit 401 and supplies power from the voltage conversion circuit 401 to each functional unit via the switching circuit 402. The specific operations are the same as those described in FIG. 6.

[0116] In step S506, the power supply control unit 309 notifies the user of the possibility of an increase in noise. For example, the power supply control unit 309 controls the display unit 312 to display the possibility of an increase in noise. After that, the process proceeds to step S507.

[0117] In step S507, the power supply control unit 309 operates the voltage conversion circuit 401 regardless of the operating state of the radiation imaging apparatus 101, and supplies power from the voltage conversion circuit 401 via the switching circuit 402 to each functional unit.

[0118] In step S508, the power supply control unit 309 determines whether the remaining power of the sub-battery 403 is greater than the second threshold. If the remaining power of the sub-battery 403 is greater than the second threshold, the process proceeds to step S509. If the remaining power of the sub-battery 403 is not greater than the second threshold, the process proceeds to step S511.

[0119] In step S509, since the capacity of the sub-battery 403 is smaller than the capacity of the main battery 314, the power supply control unit 309 notifies the user to prompt the user to connect the power supply device 104 or replace the main battery 314. For example, the power supply control unit 309 controls the display unit 312 to display a message prompting the user to connect the power supply device 104 or replace the main battery 314. After that, the process proceeds to step S510.

[0120] In step S510, the power supply control unit 309 stops the operation of the voltage conversion circuit 401 regardless of the operating state of the radiation imaging apparatus 101, and supplies power from the sub-battery 403 to each functional unit via the switching circuit 402. When the power supply device 104 or the main battery 314 cannot be used, power is supplied from the sub-battery 403. This allows the radiation imaging apparatus 101 to continue operating, for example, when the external power supply cable is accidentally disconnected, when the main battery 314 runs out of power, or when the main battery 314 is being replaced.

[0121] In step S511, the power supply control unit 309 notifies the user that all power sources of the radiation imaging apparatus 101 have been exhausted and that it is necessary to connect the power supply device 104 or replace the main battery 314, and stops the operation of the radiation imaging apparatus 101. For example, the power supply control unit 309 controls the display unit 312 to display that it is necessary to connect the power supply device 104 or replace the main battery 314.

[0122] As described above, the power supply control unit 309 controls the operation of the voltage conversion circuit 401 and the switching circuit 402 depending on the power supply state from the power supply device 104 and the states of the main battery 314 and the sub-battery 403 in addition to the operating state of the radiation imaging apparatus 101. This enables the power supply control unit 309 to limit power supply from the sub-battery 403 to situations where it is necessary, thereby suppressing deterioration of the sub-battery 403. Furthermore, by utilizing the sub-battery 403 depending on the power supply from the power supply device 104 and the state of the main battery 314, the power supply control unit 309 can reduce image noise and improve the usability of the radiation imaging apparatus 101.

[0123] Further examples can be given of the operation of the voltage conversion circuit 401 and the control of the switching circuit 402 by the power supply control unit 309. For example, the power supply control unit 309 may control the operation of the voltage conversion circuit 401 and the switching circuit 402 depending on the amount of radiation irradiated to the radiation imaging apparatus 101.

[0124] Fig. 9 is a timing chart showing an example of drive timing of the radiation imaging apparatus 101 according to the second embodiment. Fig. 9 shows an operation of detecting the amount of radiation irradiated to the radiation imaging apparatus 101 in real time by repeatedly reading out some pixels of the detection unit 212 during irradiation of radiation.

[0125] At this time, the power supply control unit 309 is configured to be able to receive information on the amount of radiation irradiated to the radiation imaging apparatus 101 from the image capturing control unit 301. The operation of the preparatory drive before and after the imaging operation in FIG. 9 is the same as that described in FIG. 6.

[0126] At time t1, when the exposure switch of the radiation generation device console 107 is pressed, radiation is emitted from the radiation tube 106. When the radiation imaging device 101 detects the irradiation of radiation, it transitions from the preparatory drive to the imaging operation. At this time, during the accumulation operation, the radiation imaging device 101 repeatedly performs a readout operation during radiation irradiation, for example, only for pixels connected to the drive wiring Vg2. The radiation imaging device 101 can detect the amount of radiation irradiated to the radiation imaging device 101 in real time from the read-out charges.

[0127] At time t2, when the end of radiation irradiation is detected by various methods, such as by notification from the radiation generation device 108 or by referring to a prearranged set time, the radiation imaging device 101 transitions from the accumulation operation to the readout operation. In the readout operation, the switch elements 201 are turned on row by row to read out the charges accumulated in the detection units 212.

[0128] The power supply control unit 309 determines, from the detected radiation amount, the operation of the voltage conversion circuit 401 and the control of the switching circuit 402 during the period from time t2 to time t5 when the imaging operation ends, by time t2 when the readout operation starts. Fig. 9 shows an example in which the power supply control unit 309 determines, from the detected radiation amount, to operate the voltage conversion circuit 401 and supply power from the voltage conversion circuit 401 during the period from time t2 to t5.

[0129] When capturing an image with a high radiation dose, quantum noise due to radiation becomes dominant as noise superimposed on the image compared to noise generated from the voltage conversion circuit 401 and superimposed on the image. In such a case, that is, under usage conditions where the noise generated from the voltage conversion circuit 401 and superimposed on the image is not an issue, the power supply control unit 309 operates the voltage conversion circuit 401 and supplies power from the voltage conversion circuit 401 even during the capturing operation.

[0130] When the radiation dose is higher than the third threshold, the power supply control unit 309 operates the voltage conversion circuit 401 regardless of the operating state of the radiation imaging apparatus 101, and supplies power from the voltage conversion circuit 401 to each functional unit via the switching circuit 402. When the radiation dose is not higher than the third threshold, the power supply control unit 309 performs control according to the flowchart in FIG.

[0131] In this way, in the case where noise generated from the voltage conversion circuit 401 and superimposed on the image is not an issue, the power supply from the sub-battery 403 can be kept to a minimum, thereby reducing deterioration of the sub-battery 403.

[0132] The method of detecting the amount of irradiated radiation is not limited to the above. For example, the detection unit 212 may be provided with a dedicated pixel for detecting the amount of radiation, or a separate sensor may be attached inside or outside the radiation imaging device 101. It is also possible to receive information on the amount of irradiated radiation from the console 102 or the radiation generation device 108 via the wireless communication unit 307 or the external connection I / F 311.

[0133] As described above, the main battery 314 has a larger capacity than the sub-battery 403. In step S501, if the external power supply device 104 is connected, the process proceeds to step S504, and if the external power supply device 104 is not connected, the process proceeds to step S502.

[0134] In step S502, if the main battery 314 is connected, the process proceeds to step S503, and if the main battery 314 is not connected, the process proceeds to step S508.

[0135] In step S503, if the remaining power of the main battery 314 is greater than the first threshold, the process proceeds to step S504, and if the remaining power of the main battery 314 is not greater than the first threshold, the process proceeds to step S508.

[0136] In step S504, if the remaining power of the sub-battery 403 is greater than the second threshold, the process proceeds to step S505, and if the remaining power of the sub-battery 403 is not greater than the second threshold, the process proceeds to step S506.

[0137] In step S505, during the preparatory driving period, the voltage conversion circuit 401 converts the voltage based on the main battery 314 or the power supply device 104. During the preparatory driving period, the power supply control unit 309 supplies the voltage output by the voltage conversion circuit 401 as the power supply voltage, and during the storage operation period and the read operation period, supplies the voltage output by the sub-battery 403 as the power supply voltage.

[0138] Note that the power supply control unit 309 may supply the voltage output by the sub-battery 403 as the power supply voltage and stop the operation of the voltage conversion circuit 401 at least during the entire or part of the period during which the readout circuit 305 reads out the image signal. During the other periods, the power supply control unit 309 operates the voltage conversion circuit 401 and supplies the voltage output by the voltage conversion circuit 401 as the power supply voltage.

[0139] In step S507, during the preparatory driving, the storage operation, and the readout operation, the voltage conversion circuit 401 converts the voltage based on the main battery 314 or the power supply device 104. During the preparatory driving, the storage operation, and the readout operation, the power supply control unit 309 supplies the voltage output by the voltage conversion circuit 401 as a power supply voltage to charge the sub-battery 403.

[0140] In step S510, the power supply control unit 309 supplies the voltage output by the sub-battery 403 as the power supply voltage during the preparatory driving, the storage operation, and the readout operation.

[0141] The radiation imaging apparatus 101 has a plurality of pairs of the voltage conversion circuit 401 and the sub-battery 403. The power supply control unit 309 supplies a plurality of power supply voltages based on the plurality of pairs. The plurality of power supply voltages may be different from each other.

[0142] The power supply control unit 309 determines the priority order for charging the multiple sub-batteries 403 based on information on the remaining power or power consumption of the multiple sub-batteries 403.

[0143] The power supply control unit 309 can supply either the voltage output by the voltage conversion circuit 401 or the voltage output by the sub-battery 403 as the power supply voltage depending on the amount of radiation.

[0144] If the radiation dose is not greater than the third threshold, in the first period, the power supply control unit 309 supplies the voltage output by the sub-battery 403 as the power supply voltage. If the radiation dose is greater than the third threshold, in the first period, the power supply control unit 309 supplies the voltage output by the voltage conversion circuit 401 as the power supply voltage. The first period is at least the entire or part of the period in which the readout circuit 305 reads out the image signal.

[0145] As described above, according to this embodiment, the radiation imaging apparatus 101 uses the sub-battery 403 instead of the voltage conversion circuit 401, thereby making it possible to reduce the influence of noise from the voltage conversion circuit 401 and acquire an image.

[0146] (Other embodiments) The present disclosure can also be realized by a process in which a program for implementing one or more functions of the above-described embodiments is supplied to a system or device via a network or a storage medium, and one or more processors in a computer of the system or device read and execute the program. It can also be realized by a circuit (e.g., ASIC) for implementing one or more functions.

[0147] It should be noted that the above-described embodiments are merely illustrative of specific examples of implementing the present disclosure, and the technical scope of the present disclosure should not be interpreted as being limited by these embodiments. In other words, the present disclosure can be implemented in various forms without departing from its technical concept or main features.

[0148] The disclosure of this embodiment includes the following configurations and methods. (Configuration 1) A radiography apparatus comprising: a plurality of pixels for generating image signals based on radiation; a voltage conversion circuit that converts an input voltage and outputs the converted voltage; a first battery that outputs a voltage; a power supply control unit that supplies, as a power supply voltage, either the voltage output by the voltage conversion circuit or the voltage output by the first battery in accordance with an operating state of the radiation imaging apparatus; A radiation imaging apparatus comprising: (Configuration 2) 2. The radiation imaging apparatus according to configuration 1, wherein the power supply control unit stops operation of the voltage conversion circuit when the voltage output by the first battery is supplied as the power supply voltage. (Configuration 3) 3. The radiation imaging apparatus according to claim 1, wherein the voltage conversion circuit is a switching regulator. (Configuration 4) 4. The radiographic imaging apparatus according to any one of configurations 1 to 3, wherein the first battery is charged by the voltage output from the voltage conversion circuit. (Configuration 5) The radiographic imaging apparatus according to any one of configurations 1 to 4, wherein the power supply control unit supplies the voltage output by the voltage conversion circuit as the power supply voltage during a first period, and supplies the voltage output by the first battery as the power supply voltage during a second period. (Configuration 6) a readout circuit for reading out image signals generated by the plurality of pixels; 6. The radiation imaging apparatus according to configuration 5, wherein the second period is the entirety or a part of the period during which the readout circuit reads out the image signal. (Configuration 7) 6. The radiation imaging apparatus according to configuration 5, wherein the first period is a period during which a reset operation of the plurality of pixels is performed. (Configuration 8) 7. The radiation imaging apparatus according to configuration 6, wherein the first period is a period during which a reset operation of the plurality of pixels is performed. (Configuration 9) a readout circuit for reading out image signals generated by the plurality of pixels; the first period is a period during which a reset operation of the plurality of pixels is performed, 6. The radiation imaging apparatus according to configuration 5, wherein the second period is a period during which the readout circuit reads out the image signal. (Configuration 10) a readout circuit for reading out image signals generated by the plurality of pixels; the first period is a period during which a reset operation of the plurality of pixels is performed, 6. The radiation imaging apparatus according to configuration 5, wherein the second period is a period during which image signals of the plurality of pixels are accumulated and a period during which the readout circuit reads out the image signals. (Configuration 11) When a second battery having a capacity larger than that of the first battery or an external power supply device is connected, during a period in which the reset operation of the plurality of pixels is performed, the voltage conversion circuit converts a voltage based on the second battery or the external power supply device, and the power supply control unit supplies the voltage output by the voltage conversion circuit as a power supply voltage; The radiographic imaging apparatus according to any one of configurations 1 to 10, characterized in that when a second battery having a capacity larger than that of the first battery is not connected and an external power supply device is not connected, during a period in which a reset operation of the plurality of pixels is performed, the power supply control unit supplies a voltage output by the first battery as a power supply voltage. (Configuration 12) when a second battery having a larger capacity than the first battery is connected and the remaining power of the second battery is greater than a first threshold, during a period in which the reset operation of the plurality of pixels is performed, the voltage conversion circuit converts a voltage based on the second battery, and the power supply control unit supplies the voltage output by the voltage conversion circuit as a power supply voltage; The radiation imaging device according to any one of configurations 1 to 11, characterized in that when a second battery having a larger capacity than the first battery is connected and the remaining power of the second battery is not greater than a first threshold, during a period in which a reset operation of the multiple pixels is performed, the power supply control unit supplies a voltage output by the first battery as a power supply voltage. (Configuration 13) a readout circuit for reading out image signals generated by the plurality of pixels; When the remaining power of the first battery is greater than a second threshold, the power supply control unit supplies a voltage output by the first battery as a power supply voltage during all or a part of a period during which the readout circuit reads out the image signal; A radiographic imaging device as described in any one of configurations 1 to 12, characterized in that when the remaining power of the first battery is not greater than a second threshold, during a period in which the readout circuit reads out the image signal, the power supply control unit supplies the voltage output by the voltage conversion circuit as the power supply voltage. (Configuration 14) The radiation imaging apparatus described in configuration 13, characterized in that when the remaining power of the first battery is not greater than a second threshold, during the period in which the readout circuit reads out the image signal, the power supply control unit supplies the voltage output by the voltage conversion circuit as a power supply voltage to charge the first battery. (Configuration 15) a plurality of pairs of the voltage conversion circuit and the first battery; 15. The radiation imaging apparatus according to any one of configurations 1 to 14, wherein the power supply control unit supplies a plurality of power supply voltages based on the plurality of combinations. (Configuration 16) 16. The radiation imaging apparatus according to configuration 15, wherein the plurality of power supply voltages are different from one another. (Configuration 17) The radiation imaging apparatus of configuration 15 or 16, characterized in that the power supply control unit determines a priority order for charging the multiple first batteries based on information on remaining power or power consumption of the multiple first batteries. (Configuration 18) a readout circuit for reading out image signals generated by the plurality of pixels; When the amount of radiation is not greater than a third threshold, the power supply control unit supplies the voltage output by the first battery as a power supply voltage during all or a part of a period during which the readout circuit reads out the image signal; A radiographic imaging device as described in any one of configurations 1 to 17, characterized in that when the radiation dose is greater than a third threshold, during a period in which the readout circuit reads out the image signal, the power supply control unit supplies the voltage output by the voltage conversion circuit as a power supply voltage. (Configuration 19) A radiography apparatus comprising: a plurality of pixels for generating image signals based on radiation; a voltage conversion circuit that converts an input voltage and outputs the converted voltage; a first battery that outputs a voltage; a power supply control unit that supplies, as a power supply voltage, either the voltage output by the voltage conversion circuit or the voltage output by the first battery in accordance with a radiation dose; A radiation imaging apparatus comprising: (Configuration 20) When the amount of radiation is not greater than a third threshold, during the first period, the power supply control unit supplies a voltage output by the first battery as a power supply voltage; The radiation imaging apparatus of configuration 19, characterized in that when the radiation dose is greater than a third threshold, during the first period, the power supply control unit supplies the voltage output by the voltage conversion circuit as the power supply voltage. (Configuration 21) a readout circuit for reading out image signals generated by the plurality of pixels; 21. The radiation imaging apparatus according to configuration 20, wherein the first period is all or a part of a period during which the readout circuit reads out the image signal. (Configuration 22) A radiographic imaging apparatus according to any one of configurations 1 to 21, A radiation source that emits radiation; A radiation imaging system comprising: (Method 1) a plurality of pixels for generating image signals based on radiation; a voltage conversion circuit that converts an input voltage and outputs the converted voltage; a first battery that outputs a voltage, A control method for a radiation imaging apparatus, comprising a power supply control step of supplying either the voltage output by the voltage conversion circuit or the voltage output by the first battery as a power supply voltage depending on an operating state of the radiation imaging apparatus. (Method 2) a plurality of pixels for generating image signals based on radiation; a voltage conversion circuit that converts an input voltage and outputs the converted voltage; a first battery that outputs a voltage, A control method for a radiographic imaging apparatus, comprising a power supply control step of supplying, as a power supply voltage, either the voltage output by the voltage conversion circuit or the voltage output by the first battery depending on a radiation dose. [Explanation of symbols]

[0149] 301: Image capture control unit, 302: Drive control unit, 303: Image information processing unit, 304: Drive circuit, 305: Readout circuit, 306: Memory unit, 307: Wireless communication unit, 308: Antenna, 309: Power supply control unit, 310: Switch, 311: External connection I / F, 312: Display unit, 313: Operation unit, 314: Main battery, 400: Power supply unit, 401: Voltage conversion circuit, 402: Switching circuit, 403: Sub-battery, 404: Small power supply unit

Claims

1. A radiography apparatus comprising: a plurality of pixels for generating image signals based on radiation; a voltage conversion circuit that converts an input voltage and outputs the converted voltage; A first battery that outputs a voltage; a power supply control unit that supplies, as a power supply voltage, either the voltage output by the voltage conversion circuit or the voltage output by the first battery in accordance with an operating state of the radiation imaging apparatus; A radiation imaging apparatus comprising:

2. 2. The radiation imaging apparatus according to claim 1, wherein the power supply control unit stops the operation of the voltage conversion circuit when the voltage output by the first battery is supplied as the power supply voltage.

3. 2. The radiation imaging apparatus according to claim 1, wherein the voltage conversion circuit is a switching regulator.

4. 2. The radiation imaging apparatus according to claim 1, wherein the first battery is charged by the voltage output from the voltage conversion circuit.

5. 2. The radiation imaging apparatus according to claim 1, wherein the power supply control unit supplies the voltage output by the voltage conversion circuit as the power supply voltage during a first period, and supplies the voltage output by the first battery as the power supply voltage during a second period.

6. a readout circuit for reading out image signals generated by the plurality of pixels; 6. The radiation imaging apparatus according to claim 5, wherein the second period is the entirety or a part of the period during which the readout circuit reads out the image signal.

7. 6. The radiation imaging apparatus according to claim 5, wherein the first period is a period during which a reset operation of the plurality of pixels is performed.

8. 7. The radiation imaging apparatus according to claim 6, wherein the first period is a period during which a reset operation of the plurality of pixels is performed.

9. a readout circuit for reading out image signals generated by the plurality of pixels; the first period is a period during which a reset operation of the plurality of pixels is performed, 6. The radiation imaging apparatus according to claim 5, wherein the second period is a period during which the readout circuit reads out the image signal.

10. a readout circuit for reading out image signals generated by the plurality of pixels; the first period is a period during which a reset operation of the plurality of pixels is performed, 6. The radiation imaging apparatus according to claim 5, wherein the second period is a period during which image signals of the plurality of pixels are accumulated and a period during which the readout circuit reads out the image signals.

11. When a second battery having a capacity larger than that of the first battery or an external power supply device is connected, during a period in which the reset operation of the plurality of pixels is performed, the voltage conversion circuit converts a voltage based on the second battery or the external power supply device, and the power supply control unit supplies the voltage output by the voltage conversion circuit as a power supply voltage; 2. The radiation imaging apparatus according to claim 1, wherein when a second battery having a capacity larger than that of the first battery is not connected and an external power supply device is not connected, during a period in which a reset operation of the plurality of pixels is performed, the power supply control unit supplies a voltage output by the first battery as a power supply voltage.

12. when a second battery having a larger capacity than the first battery is connected and the remaining power of the second battery is greater than a first threshold, during a period in which the reset operation of the plurality of pixels is performed, the voltage conversion circuit converts a voltage based on the second battery, and the power supply control unit supplies the voltage output by the voltage conversion circuit as a power supply voltage; 2. The radiation imaging apparatus according to claim 1, wherein when a second battery having a larger capacity than the first battery is connected and the remaining power of the second battery is not greater than a first threshold, the power supply control unit supplies the voltage output by the first battery as the power supply voltage during a period in which a reset operation of the plurality of pixels is performed.

13. a readout circuit for reading out image signals generated by the plurality of pixels; When the remaining power of the first battery is greater than a second threshold, the power supply control unit supplies a voltage output by the first battery as a power supply voltage during all or a part of a period during which the readout circuit reads out the image signal; 2. The radiation imaging apparatus according to claim 1, wherein when the remaining power of the first battery is not greater than a second threshold, during a period in which the readout circuit reads out the image signal, the power supply control unit supplies the voltage output by the voltage conversion circuit as a power supply voltage.

14. 14. The radiation imaging apparatus according to claim 13, wherein, when the remaining power of the first battery is not greater than a second threshold, during a period in which the readout circuit reads out the image signal, the power supply control unit supplies the voltage output by the voltage conversion circuit as a power supply voltage to charge the first battery.

15. a plurality of pairs of the voltage conversion circuit and the first battery; The radiation imaging apparatus according to claim 1 , wherein the power supply control unit supplies a plurality of power supply voltages based on the plurality of combinations.

16. 16. The radiation imaging apparatus according to claim 15, wherein the plurality of power supply voltages are different from one another.

17. 16. The radiation imaging apparatus according to claim 15, wherein the power supply control unit determines a priority order for charging the first batteries based on information on remaining power or power consumption of the first batteries.

18. a readout circuit for reading out image signals generated by the plurality of pixels; When the amount of radiation is not greater than a third threshold, the power supply control unit supplies the voltage output by the first battery as a power supply voltage during all or a part of a period during which the readout circuit reads out the image signal; 2. The radiation imaging apparatus according to claim 1, wherein when the radiation dose is greater than a third threshold, the power supply control unit supplies the voltage output by the voltage conversion circuit as a power supply voltage during a period in which the readout circuit reads out the image signal.

19. A radiography apparatus comprising: a plurality of pixels for generating image signals based on radiation; a voltage conversion circuit that converts an input voltage and outputs the converted voltage; A first battery that outputs a voltage; a power supply control unit that supplies, as a power supply voltage, either the voltage output by the voltage conversion circuit or the voltage output by the first battery in accordance with a radiation dose; A radiation imaging apparatus comprising:

20. When the amount of radiation is not greater than a third threshold, during the first period, the power supply control unit supplies a voltage output by the first battery as a power supply voltage; 20. The radiation imaging apparatus according to claim 19, wherein, when the radiation amount is greater than a third threshold, during the first period, the power supply control unit supplies the voltage output by the voltage conversion circuit as the power supply voltage.

21. a readout circuit for reading out image signals generated by the plurality of pixels; 21. The radiation imaging apparatus according to claim 20, wherein the first period is the entirety or a part of the period during which the readout circuit reads out the image signal.

22. A radiographic imaging apparatus according to any one of claims 1 to 21, A radiation source that emits radiation; A radiation imaging system comprising:

23. a plurality of pixels for generating image signals based on radiation; a voltage conversion circuit that converts an input voltage and outputs the converted voltage; a first battery that outputs a voltage, a power supply control step of supplying, as a power supply voltage, either the voltage output by the voltage conversion circuit or the voltage output by the first battery depending on an operating state of the radiation imaging apparatus.

24. a plurality of pixels for generating image signals based on radiation; a voltage conversion circuit that converts an input voltage and outputs the converted voltage; a first battery that outputs a voltage, 13. A method for controlling a radiation imaging apparatus, comprising: a power supply control step of supplying, as a power supply voltage, either the voltage output by the voltage conversion circuit or the voltage output by the first battery in accordance with a radiation dose.

Images