WO2014188795A1

WO2014188795A1 - Diagnostic medical imaging system and radiography apparatus

Info

Publication number: WO2014188795A1
Application number: PCT/JP2014/059738
Authority: WO
Inventors: 裕一西島; 智紀儀同; 修吾石阪; 孝夫椎橋; 志行金子; 陽廣重; 兼六生方; 幸大贄川
Original assignee: コニカミノルタ株式会社
Priority date: 2013-05-24
Filing date: 2014-04-02
Publication date: 2014-11-27

Abstract

Provided is a diagnostic medical imaging system capable of accurately preventing the occurrence of deterioration in image quality of diagnostic medical images generated even when imaging is performed using a radiography apparatus capable of transitioning the imaging mode from a sleep mode to a wake-up mode. In the diagnostic medical imaging system (50), the control means (22) of the radiography apparatus (1): performs, after imaging, an offset data (O) read-out processing, which repeats the same processing sequence as the processing sequence of resetting each radiation detecting element (7), continuing the charge accumulation state for an accumulation time (τ) and performing image data (D) read-out processing; and when the time (t) elapsed from when the imaging mode transitions to the wake-up mode reaches a waiting time (WT), transmits a signal to a notification device (58). When a signal is received, the notification device (58) issues a notice that radiation can be irradiated from the radiation-generating device (55) and imaging can be performed. The waiting time (WT) can be changed according to the accumulation time (τ).

Description

Medical imaging system for providing diagnosis and radiographic imaging apparatus

The present invention relates to a diagnostic providing medical image system and a radiographic imaging apparatus that generate a diagnostic providing medical image based on image data read by a radiographic imaging apparatus.

In the field of X-ray photography, the shift from the conventional silver salt photography method using screens / films to CR (computed radiography) cassettes using photostimulable phosphor sheets, etc. has made digitization from analog photography methods possible. It is illustrated. In recent years, a radiation imaging device (Flat Panel Detector, hereinafter) in which radiation detection elements that generate charges (electron-hole pairs) in accordance with radiation irradiated from a radiation generator and transmitted through a subject are arranged in a two-dimensional manner. Various types of FPDs) have been developed and are used for taking medical images for diagnosis provision in medical sites such as hospitals. In recent years, a portable FPD in which a sensor panel or the like on which a radiation detection element or the like is formed is housed in a casing and can be carried has been developed and put into practical use (for example, see Patent Document 1).

In such an FPD, for example, as shown in FIG. 2 and the like to be described later, normally, a plurality of radiation detection elements 7 are arranged in a two-dimensional form (matrix form) on the detection part P4 of the sensor panel SP, and each radiation detection element is detected. Each element 7 is configured by being connected to a switch element formed by a thin film transistor (Thin Film Transistor, hereinafter referred to as TFT) 8. When imaging is performed by irradiating the FPD with radiation from the radiation generator through the subject, all the TFTs 8 are turned off for a predetermined time and generated in each radiation detection element 7 by radiation irradiation. The charged charges are accumulated in each radiation detection element 7. Hereinafter, the “predetermined time” set for accumulating charges in each radiation detection element 7 is referred to as an accumulation time τ. A state in which all TFTs 8 are turned off and charges are accumulated in each radiation detection element 7 is referred to as a charge accumulation state. That is, the accumulation time τ means the duration of this charge accumulation state.

Then, after the accumulation time τ elapses, the reading process of the image data D from each radiation detection element 7 is performed. In the reading process, an ON voltage is sequentially applied from the gate driver 15b to each of the lines L1 to Lx of the scanning line 5 so that the TFTs 8 are sequentially turned on, and are generated and accumulated in each radiation detecting element 7 by radiation irradiation. The charges are sequentially discharged to the signal lines 6 and read out as image data D by the readout circuits 17, respectively.

By the way, as described above, in order to accurately accumulate the charges generated by the irradiation of radiation in each of the radiation detection elements 7, at the same time as the irradiation of the radiation to the FPD is started from the radiation generating apparatus, or Before starting, it is necessary that each TFT 8 which is a switching element of the FPD is in an OFF state. As one method for realizing this, for example, there is a case where imaging is performed while synchronizing between the radiation generation apparatus and the FPD. Such a photographing method is hereinafter referred to as a synchronous method.

In the case of this synchronization method, for example, the FPD receives a wake-up signal (also referred to as a wake up signal) from a console 58 (see FIGS. 3 and 4 described later) or an exposure described later from the radiation generator. When a signal indicating that the first-stage operation of the shooting switch 56 (ie, a so-called half-pressing operation) has been received, etc., reset processing of each radiation detection element 7 for removing the charge remaining in each radiation detection element 7 To start. When the reset processing of each radiation detection element 7 is performed, for example, as shown in the left part of FIG. 28, an ON voltage is applied to each line L1 to Lx of the scanning line 5 from the gate driver 15b (see FIG. 2 described later). It may be configured to be applied sequentially, and although not shown, it may be configured to apply the on-voltage to the lines L1 to Lx of the scanning line 5 from the gate driver 15b all at once. Is possible. Further, Tac in FIG. 28 will be described later.

Then, when an operator such as a radiologist performs the second stage operation of the exposure switch 56 (that is, a so-called full-press operation), an irradiation start signal is transmitted from the radiation generator to the FPD. Then, when the FPD receives the irradiation start signal, as shown in FIG. 28, the reset processing of each radiation detection element 7 is ended and an interlock release signal is transmitted to the radiation generation apparatus. And a radiation generator irradiates radiation at the time of receiving an interlock release signal. Further, when the reset process of each radiation detection element 7 is finished, the FPD transmits the interlock release signal as described above, and at the same time, turns off the TFT 8 and shifts to the charge accumulation state. Then, radiation is irradiated during the accumulation time τ. Note that the hatched portion in FIG. 28 represents a period during which radiation is applied from the radiation generation apparatus. Then, after the accumulation time τ elapses, the FPD sequentially applies on-voltages to the lines L1 to Lx of the scanning line 5 from the gate driver 15b as described above, so that the image data D from each radiation detection element 7 is transferred. It is configured to perform a read process.

On the other hand, when the manufacturers of the FPD and the radiation generator are different from each other, there is a case where an interface cannot be constructed between the two. Such an imaging method performed without synchronizing the FPD and the radiation generating apparatus is hereinafter referred to as an asynchronous method. Also in this asynchronous system, it is necessary to turn off each TFT 8 that is a switching element of the FPD when radiation irradiation to the FPD is started from the radiation generating device. For this reason, when imaging is performed in an asynchronous manner, normally, the FPD itself detects that radiation has been emitted without exchanging signals with the radiation generator.

In order to realize this, an X-ray detection means such as an X-ray sensor is attached to the FPD (see Patent Document 2), or predetermined radiation detection among the radiation detection elements 7 arranged in a two-dimensional manner as described above. The element 7 is configured to be used as a sensor (see Patent Document 3), or the current detection means is provided on a bias line 9 (see FIG. 2 and the like described later) connected to each radiation detection element 7. Is also possible (see Patent Document 4). In addition, before the start of radiation irradiation, the readout circuit 17 is caused to perform a readout operation in a state in which each TFT 8 is turned off by applying an off voltage to all the scanning lines 5 from the gate driver 15b of the scanning drive unit 15. It is also possible to perform a read process of the leak data dleak that reads out the charges leaked from the radiation detection element 7 as leak data dleak via the (see Patent Document 5). Furthermore, as described in Patent Document 6 and the like, it is also possible to perform a configuration in which image data reading processing is performed before the start of radiation irradiation. In this case, the image data read out in this case is referred to as image data d for irradiation start detection, in distinction from the image data D as the main image read out after photographing as described above.

If the inventions described in

Patent Documents

5 and 6 are employed, when radiation irradiation to the FPD is started, the values of the leak data dleak read out as described above and the image data d for irradiation start detection are as follows: It becomes much larger than before the start of irradiation. For this reason, it is possible to detect the start of radiation irradiation when, for example, the read leak data dleak or image data d for detection of irradiation start is equal to or greater than a threshold value. Even if any of the above detection methods in the asynchronous method is employed, when the FPD detects the start of irradiation of radiation from the radiation generator, all the TFTs 8 are turned off and the charge accumulation state is entered. Then, after the accumulation time τ elapses, the image data D is read from each radiation detection element 7 as described above.

Japanese Patent Laid-Open No. 6-342099 JP 2007-151761 A JP 2011-174908 A JP 2009-219538 A International Publication No. 2011/13517 Pamphlet International Publication No. 2011-152093 Pamphlet

Incidentally, in each radiation detection element 7, so-called dark charges (also referred to as dark current) are constantly generated due to thermal excitation or the like due to heat (temperature) of the radiation detection element 7 itself. For this reason, when the TFT 8 serving as the switch element is turned off, the dark charge continues to accumulate in the radiation detection element 7. For example, when the reading process of the image data D as the main image is performed according to the processing sequence shown in FIG. 28, the reading of the image data D is performed after the on-voltage is applied in the reset process before the reading process. Until the on-voltage is applied during processing, the TFT 8 is in an off state, and thus dark charges generated in each radiation detection element 7 during that time are accumulated in each radiation detection element 7.

Therefore, in the image data D read out by the reading process, as described above, the data resulting from the charge generated by the irradiation of radiation (that is, the so-called true image data D ^* ) is superimposed with the offset o due to the dark charge. It has become. More precisely, the image data D has a voltage applied in the read process of the image data D after the voltage applied in the reset process before the read process is switched from the on voltage to the off voltage. An offset o due to dark charges generated in each radiation detection element 7 is superimposed during a time Tac (hereinafter, this time Tac is referred to as an effective accumulation time Tac) until switching from the on voltage to the off voltage. That is, between the image data D, the true image data D ^*, and the offset o due to the dark charge,
D = D ^* + o (1)
The relationship is established.

Then, the offset data O reading process for reading the offset o due to the dark charge as the offset data O is normally performed after photographing. The amount of dark charge accumulated in each radiation detection element 7, that is, the offset o due to the dark charge superimposed on the image data D changes according to the length of the effective accumulation time Tac. Further, if the length of the effective accumulation time Tac is the same, the value of the offset o due to the dark charge is the same. Therefore, in the offset data O reading process, the effective accumulation time Tac for each of the lines L1 to Lx of the scanning line 5 is set to the same time interval as the effective accumulation time Tac (see FIG. 28) in the image data D reading process. The offset data O and the offset o due to the dark charge superimposed on the image data D can be made the same size. In this case, since O = o, if this is substituted into the above equation (1) and transformed,
D ^* = D−o
= DO (2)
Thus, by subtracting the offset data O read by the offset data O reading process from the image data D read by the image data D reading process, each radiation detecting element 7 is irradiated with radiation. It is possible to easily and accurately calculate true image data D ^* resulting from only the generated charges.

In order to realize this, as described above, it is necessary to set the effective accumulation time Tac in the reading process of the offset data O to the same time interval as the effective accumulation time Tac in the reading process of the image data D. Become. Therefore, for example, as shown in FIG. 29, the offset data O reading process is often configured to repeat the same processing sequence as the processing sequence up to the image data D reading process shown in FIG. By configuring so that the same processing sequence is repeated in this way, the timing of applying the ON voltage to each of the lines L1 to Lx of the scanning line 5 is the case of the reading process of the image data D and the case of the reading process of the offset data O The effective accumulation time Tac becomes the same time interval for each of the lines L1 to Lx of the scanning line 5. Note that the offset data O is read out in a state in which the FPD is not irradiated with radiation. In this case, the accumulation time τ (see FIG. 28), which is the duration of the charge accumulation state before the image data D reading process, and the accumulation time τ before the offset data O reading process (see FIG. 29) are also completely different. Set to the same time interval.

In this way, if the offset data O is read out by repeating the same processing sequence as the processing sequence up to the reading processing of the image data D (see FIG. 28), the reading processing of the image data D is performed. The effective accumulation time Tac and the effective accumulation time Tac at the time of the reading process of the offset data O are the same time interval, and the offset o due to the dark charge superimposed on the image data D and the offset data O have the same size. . Therefore, when the image processing is performed, the offset amount o due to the dark charge superimposed on the image data D and the offset data O are canceled by performing the calculation of the above equation (2), so that the true image data D ^* Can be calculated accurately.

However, in theory, it should be as described above, but actually, the offset data O is read out as described above, and the read offset data O and image data D are substituted into the above equation (2). It has been found that when the image data D ^* is calculated, the offset o due to the dark charge superimposed on the image data D and the offset data O may not be offset. In such a situation, the reading process of the image data D and the reading process of the offset data O are performed as described above, and a true image is obtained according to the above equation (2) based on the read image data D and the offset data O. When the data D ^* is calculated, the image quality of the diagnostic-provided medical image generated based on the calculated true image data D ^* may be deteriorated.

As a result of the inventors' researches on the cause of the phenomenon as described above, in particular, the FPD has a photographing mode including at least a control unit 22, a scanning drive unit 15, and a readout IC 16 ( (See FIG. 2 to be described later) and the like, a power is supplied to each functional unit such as a wake up mode in which imaging can be performed, and power is supplied only to necessary functional units such as the communication unit 30 to perform imaging. It has been found that the above phenomenon appears when it is configured to be able to transition to a sleep mode that cannot be performed.

The present invention has been made in view of the above-described problems, and is generated even when imaging is performed using an FPD (radiation imaging apparatus) capable of changing the imaging mode from the sleep mode to the awakening mode. It is an object of the present invention to provide a diagnostic providing medical image system and a radiographic imaging apparatus capable of accurately preventing deterioration of the image quality of a diagnostic providing medical image.

In order to solve the above problems, a medical image system for diagnosis provision and a radiographic imaging apparatus of the present invention include:
A plurality of scanning lines and a plurality of signal lines;
A plurality of radiation detection elements arranged two-dimensionally;
Scanning drive means for switching a voltage applied to each scanning line between an on-voltage and an off-voltage,
A switch element connected to each of the scanning lines, and discharging a charge accumulated in the radiation detection element to the signal line when an on-voltage is applied;
A readout circuit for reading out the electric charge emitted to the signal line as image data;
Control means for controlling at least the scanning drive means and the readout circuit to perform the readout processing of the image data;
A radiographic imaging device comprising:
A radiation generator for irradiating the radiation imaging apparatus with radiation through a subject; and
A notification device;
With
The radiographic image capturing apparatus supplies an imaging mode, an awakening mode capable of performing imaging by supplying power to each functional unit including at least the control unit, and supplying power only to necessary functional units to perform imaging. Is configured to be able to transition between sleep modes that cannot be performed,
The control means of the radiographic image capturing apparatus includes:
At the time of imaging, after performing reset processing of each radiation detection element, the scanning drive means applies an off voltage to each scanning line, and the switch element is turned off by irradiation of radiation. The charge accumulation state in which charges generated in each radiation detection element are accumulated in each radiation detection element is continued for a set accumulation time, and then at least the scanning drive unit and the readout circuit are controlled to Have the image data read out,
Read offset data to read offset data instead of the image data by repeating the same processing sequence as the processing sequence from the reset processing of each radiation detection element to the reading processing of the image data in a state where no radiation is irradiated after imaging. As well as processing
Counting the elapsed time since the shooting mode is changed from the sleep mode to the wake-up mode, and when the elapsed time has elapsed by a waiting time, a signal is sent to the notification device,
The notification device is configured to notify that it is possible to perform imaging by irradiating radiation from the radiation generation device when receiving the signal from the radiographic imaging device,
The waiting time is switched according to the accumulation time.

According to the medical imaging system for diagnosis providing and the radiographic imaging apparatus of the system as in the present invention, imaging is performed in a short time after the imaging mode of the radiographic imaging apparatus (FPD) is changed from the sleep mode to the awakening mode. Even when the image data D is read by the FPD and the offset data O is subsequently read out, the read image data D and the offset can be changed by appropriately switching the waiting time according to the set accumulation time. It is possible to accurately prevent deterioration in the image quality of the medical image for diagnosis providing generated based on the data O.

It is a perspective view which shows the external appearance of FPD. It is a block diagram showing the equivalent circuit of FPD. It is a figure which shows the structural example of the medical image system for diagnosis provision constructed | assembled in the imaging | photography room etc. It is a figure showing the structural example of the medical image system for diagnosis provision constructed | assembled on the round-trip vehicle, and the portable terminal which an operator carries. It is a timing chart explaining the timing etc. which apply an ON voltage to each scanning line, when detecting the irradiation start of radiation based on leak data. 6 is a timing chart showing that offset data reading processing is performed by repeating the processing sequence shown in FIG. 5. It is a graph showing an example of the state which the electric charge amount per unit time which generate | occur | produces in a radiation detection element reduces gradually as time passes. FIG. 8 is a graph for explaining that an offset amount o and offset data O due to dark charges superimposed on image data D in the example of FIG. 7 are respectively expressed as areas of hatched areas. FIG. 8 is a graph for explaining that the amount of charge per unit time generated in each radiation detection element becomes a constant value and the offset amount o and the offset data O become equal after the time has elapsed in the example of FIG. 7. It is a timing chart explaining transmitting a signal to an alarm device etc. when the elapsed time after changing to a wake-up mode passes only waiting time. FIG. 8 is a graph for explaining a difference Δ between an offset amount o due to dark charges superimposed on image data D and offset data O in the example of FIG. FIG. 12 is a graph for explaining that the difference Δ becomes larger than the case of FIG. 11 when the effective accumulation time Tac becomes longer in the example of FIG. 7. 13 is a graph for explaining that the difference Δ is reduced by increasing the waiting time in the case of FIG. 12. It is a figure showing an example of the screen displayed on the display part of a console. It is a figure showing an example of the screen comprised so that the accumulation | storage time can be set simultaneously with setting an imaging | photography site | part and an imaging | photography direction. It is a figure showing an example of the screen at the time of comprising so that accumulation time can be set on the screen shown in FIG. It is a timing chart in an example in which the first shooting is performed after a short waiting time has elapsed since the transition to the awakening mode, and then the second shooting is performed after a long waiting time has elapsed. It is a graph explaining that the voltage Vb applied to each radiation detection element from a bias power supply changes so that it may approach 0 [V] gradually from the time of the transition to an awakening mode. It is a figure which shows an example of imaging | photography order information. It is a figure which shows an example of the selection screen which displays imaging | photography order information. It is a figure which shows an example of the screen which displays each icon etc. corresponding to each imaging | photography order information. 6 is a diagram for explaining an example of a method for extracting preview image data from image data D. FIG. It is a figure showing the state which displays a preview image in a wipe. It is a figure showing the state which displays a preview image in a wipe. It is a figure showing the state which displays a preview image in a wipe. FIG. 22 is a diagram illustrating that a preview image is displayed at a position of an icon I2 on the screen of FIG. It is a figure showing an example of the symbol showing that FPD is reading offset data. It is a figure showing an example of the table which matches the set accumulation | storage time and the content of the display process displayed on a display part. It is a figure explaining the order of processing of image data reading processing and offset data reading processing when performing offset data reading processing after shooting. It is a figure explaining the order of the process of the reading process of image data, and the reading process of offset data in the case of performing the reading process of offset data before imaging | photography. 6 is a timing chart for explaining the timing of applying an ON voltage to each scanning line when shooting is performed in a synchronous manner. FIG. 29 is a timing chart showing that offset data reading processing is performed by repeating the processing sequence shown in FIG. 28.

Hereinafter, embodiments of a medical image system for diagnosis provision and a radiographic imaging apparatus according to the present invention will be described with reference to the drawings.

In the following, the radiographic imaging device is also referred to as FPD. In the following, a so-called indirect FPD that includes a scintillator or the like as an FPD used in a medical image system for diagnosis provision and obtains image data by converting emitted radiation into electromagnetic waves of other wavelengths such as visible light. As will be described, the present invention can also be applied to a so-called direct FPD in which radiation is directly detected by a radiation detection element without using a scintillator or the like. Although the case where the FPD is a so-called portable type will be described, the present invention can also be applied to a so-called dedicated type FPD formed integrally with a support base or the like.

[About FPD]
Here, before explaining the medical image system for diagnosis provision according to the present invention, the FPD 1 used in the medical image system for diagnosis provision will be described. FIG. 1 is a perspective view showing the appearance of the FPD.

In this embodiment, the FPD 1 is configured by housing a sensor panel (not shown) in a housing 2 formed of a carbon plate or the like. On one side surface of the housing 2, a power switch 25, a changeover switch 26, a connector 27, an indicator 28, and the like are arranged. Although not shown, in the present embodiment, an antenna device 29 (see FIG. 2 to be described later) for performing wireless communication with the outside is provided on, for example, the opposite side surface of the housing 2. Note that the FPD 1 uses the antenna device 29 when communicating with the outside in a wireless manner, and communicates by connecting a cable (not shown) to the connector 27 when communicating with the outside in a wired manner. It has become.

FIG. 2 is a block diagram showing an equivalent circuit of FPD. As shown in FIG. 2, in the FPD 1, a plurality of radiation detection elements 7 are arranged in a two-dimensional shape (matrix shape) on a sensor substrate (not shown). Each of the radiation detection elements 7 generates charges in accordance with radiation irradiated from a radiation source 52 (see FIGS. 3 and 4) of a radiation generator 55 (described later) and transmitted through a subject (not shown). Each radiation detection element 7 is connected to a bias line 9, and the bias line 9 is connected to a bias power supply 14 through a connection 10. A reverse bias voltage is applied from the bias power source 14 to each radiation detection element 7 via the bias line 9 and the like. Each radiation detecting element 7 is connected to a thin film transistor (hereinafter referred to as TFT) 8 as a switching element, and the TFT 8 is connected to the signal line 6.

In the scanning drive means 15, an ON voltage and an OFF voltage are supplied from the power supply circuit 15a to the gate driver 15b via the wiring 15c, and applied to each line L1 to Lx of the scanning line 5 by the gate driver 15b. The voltage is switched between an on voltage and an off voltage. Each TFT 8 is turned on when an on-voltage is applied via the scanning line 5, and the radiation detection element 7 and the signal line 6 are brought into conduction, and the charge in the radiation detection element 7 is read out. . Further, each TFT 8 is turned off when an off voltage is applied via the scanning line 5, and the conduction between the radiation detection element 7 and the signal line 6 is cut off.

The control means 22 includes a CPU (Central Processing Unit), a ROM (Read Only Memory), a RAM (Random Access Memory), an input / output interface connected to the bus, an FPGA (Field Programmable Gate Array), etc. ing. It may be configured by a dedicated control circuit. The control means 22 is connected to a storage means 23 composed of SRAM (Static RAM), SDRAM (Synchronous DRAM) or the like, and performs an antenna device 29 for wireless communication with the outside or wired communication. A communication unit 30 to which a connector 27 is connected is connected. Further, a battery 24 that supplies necessary power to each functional unit such as the scanning drive unit 15, the readout circuit 17, the storage unit 23, and the bias power supply 14 is connected to the control unit 22.

For example, as shown in FIG. 28, the control unit 22 sequentially applies on-voltages to the lines L1 to Lx of the scanning line 5 from the gate driver 15b (see FIG. 2) when the image data D is read out. Each TFT 8 connected to the scanning line 5 is turned on. When each TFT 8 is turned on, each radiation detection element 7 and each signal line 6 are electrically connected, and the electric charge discharged from each radiation detection element 7 to the signal line 6 is read out in each readout IC 16. Read by the circuit 17.

Specifically, a voltage value is output from the amplification circuit 17 in accordance with the amount of charge flowing from the radiation detection element 7 to the amplification circuit 18 of the readout circuit 17. Then, the correlated double sampling circuit (described as “CDS” in FIG. 2) 19 converts the difference between the voltage values output from the amplifier circuit 18 before and after the charge flows from each radiation detection element 7 into an analog value. The image data D is output downstream. The output image data D is sequentially transmitted to the A / D converter 20 via the analog multiplexer 21, and is sequentially converted into digital image data D by the A / D converter 20, and is output to the storage means 23. Are stored sequentially.

In the present embodiment, the FPD 1 can perform shooting by supplying power to at least the functional units such as the reading IC 16 including the control unit 22, the scanning drive unit 15, and the reading circuit 17 in the shooting mode. Awake mode (also referred to as a shootable mode) and a sleep mode in which power is supplied only to necessary functional units such as the communication unit 30 that communicates with the outside, and imaging cannot be performed. Can be transitioned between.

The FPD 1 may be configured such that, for example, the shooting mode is set to the awakening mode when the power switch 25 is turned on, and the shooting mode is set to the sleep mode when the power switch 25 is turned on. It may be configured. Further, for example, when a wake-up signal is received from a console 58 (described later, see FIGS. 3 and 4), the photographing mode is changed from the sleep mode to the wake-up mode. In the present embodiment, the FPD 1 changes the shooting mode to the sleep mode when the shooting mode is changed to the awakening mode and no shooting is performed even after a predetermined time has elapsed.

[Medical imaging system for diagnosis provision]
Next, the configuration and the like of the diagnostic providing medical image system 50 according to the present embodiment will be described. FIG. 3 is a diagram illustrating a configuration example of the medical image system 50 for providing diagnosis according to the present embodiment. FIG. 3 shows a case where the diagnostic providing medical image system 50 is constructed in the imaging room R1 or the like.

In the photographing room R1, a bucky device 51 is installed, and the bucky device 51 can be used by loading the FPD 1 into a cassette holding portion (also referred to as a cassette holder) 51a. FIG. 3 shows a case where a bucky device 51A for standing position shooting and a bucky device 51B for standing position shooting are installed as the bucky device 51. For example, only one of the bucky devices 51 is provided. It may be done. In addition, as shown in FIG. 3, the imaging room R1 is provided with at least one radiation source 52A of a radiation generator 55 that irradiates the FPD 1 loaded in the Bucky device 51 via a subject.

The photography room R1 is provided with a repeater 54 for relaying communication between each device in the photography room R1 and each device outside the photography room R1. I have. The relay 54 is connected to the radiation generator 55 and the console 58. The relay 54 is connected to a signal for LAN (Local Area Network) communication transmitted from the FPD 1 or the console 58 to the radiation generator 55. Is converted into a signal or the like for the radiation generator 55, and vice versa.

In the present embodiment, the front room (also referred to as an operation room) R2 is provided with an operation console 57 of the radiation generating device 55. The operation panel 57 is operated by an operator such as a radiation engineer. An exposure switch 56 is provided for instructing the generator 55 to start radiation irradiation.
The exposure switch 56 is provided with a button (not shown).

As described above, when an operator such as a radiologist performs the first-stage operation (that is, so-called half-press operation) on the button of the exposure switch 56, the radiation generator 55 activates the radiation source 52. To be ready for radiation. Then, when the operator performs the second-stage operation (that is, so-called full-press operation) on the button of the exposure switch 56, the radiation generator 55 starts from the FPD 1 in the synchronous method as described above. When the interlock release signal is transmitted, the radiation source 52 emits radiation. Further, when imaging is performed in an asynchronous manner, the radiation generator 55 irradiates the radiation from the radiation source 52 when the operator performs the second stage operation on the exposure switch 56. The radiation generator 55 performs various controls such as setting a tube current and an irradiation time for the radiation source 52 so that an appropriate dose of radiation is emitted from the radiation source 52. .

As shown in FIG. 3, in the present embodiment, a console 58 formed of a computer or the like is provided in the front room R2. The console 58 can be configured to be provided outside the imaging room R1 and the front room R2, in a separate room, and the like, and is installed in an appropriate place. In addition, the console 58 is provided with a display unit 58a configured to include a CRT (Cathode Ray Tube), an LCD (Liquid Crystal Display), or the like, and also includes input means such as a mouse and a keyboard (not shown). Yes. In addition, the console 58 is connected to or has a built-in storage means 59 composed of an HDD (Hard DiskDrive) or the like. Although not shown, the console 58 is connected to the console 58 via a network such as a LAN, HIS (Hospital Information System), RIS (Radiology Information System), PACS (Picture Archiving and Communication). System) etc. are connected.

On the other hand, as shown in FIG. 4, the FPD 1 can be used in a so-called state without being loaded into the bucky device 51. FIG. 4 is a diagram illustrating a configuration example of the diagnostic providing medical image system 50 constructed on the round-trip wheel 60. For example, when the patient H cannot get up from the bed B of the patient room R3 and cannot go to the radiographing room R1 as shown in FIG. 3, the FPD 1 and the round-trip car 60 are moved to the patient room R3 as shown in FIG. It can be brought in and inserted between the bed B and the body of the patient H or applied to the body of the patient H. Further, when the FPD 1 is used in the hospital room R3 or the like, the radiation generator 55 is mounted on the round-trip wheel 60 and installed in the hospital room R3 as shown in FIG. 4 instead of the radiation generator 55 installed in the imaging room R1 described above. Brought in. Further, in this case, the roundabout wheel 60 is equipped with a portable radiation 52P that can appropriately change the radiation direction and the like. The roundabout wheel 60 is also equipped with a console 58 and the like. Although not shown in FIG. 4, the roundabout wheel 60 is configured to include the access point 53, the repeater 54, and the like shown in FIG. 3.

The same applies to the case where the photographing is performed in the photographing room R1 shown in FIG. 3. For example, as shown in FIG. 4, the operator E such as a radiologist carries the portable terminal 70 having the display unit 71 and the console. The image displayed on the 58 display units 58 a can also be configured to be displayed on the display unit 71 of the mobile terminal 70. If comprised in this way, it will become possible for operators, such as a radiographer, to confirm an image on the display part 71 of the portable terminal 70 which he carries, without going to the console 58 one by one. Therefore, it is convenient for the operator.

[Regarding normal processing during shooting]
Next, normal processing of the FPD 1 control means 22 and console 58 during shooting will be described. For example, when an instruction is input by an operator such as a radiographer before imaging, the console 58 transmits an awakening signal to the FPD 1 used for imaging, and changes the imaging mode of the FPD 1 to the awakening mode. When the imaging mode is changed to the awakening mode, the FPD 1 starts a reset process for each radiation detection element 7 that removes the charge remaining in each radiation detection element 7 as a pre-process for imaging. Then, when the operator such as a radiologist completes positioning of the FPD 1 and the patient H as the subject, the operator moves to the exposure switch 56 of the radiation generator 55 and operates the exposure switch 56 to generate radiation. Radiation is emitted from the radiation source 52 of the device 55.

In some cases, after the positioning of the FPD 1 and the patient H who is the subject is completed, a wake-up signal is transmitted from the console 58 to the FPD 1 so that the photographing mode of the FPD 1 is changed from the sleep mode to the wake-up mode. . In order to avoid exhaustion of the battery 24 of the FPD 1 (see FIG. 2 and the like), a wake-up signal is transmitted from the console 58 to the FPD 1 by using the first button operation of the exposure switch 56 as a trigger. In some cases, the photographing mode is changed from the sleep mode to the awakening mode.

When imaging is performed in a synchronous manner, when the second-stage operation of the exposure switch 56 (that is, a so-called full-press operation) is performed, as described above, irradiation from the radiation generator 55 to the FPD 1 is performed. A start signal is transmitted. Then, as shown in FIG. 28, an interlock release signal is transmitted from the FPD 1 that has completed the reset process of each radiation detection element 7 to the radiation generator 55. And the radiation generator 55 irradiates radiation at the time of receiving the interlock release signal. As shown in FIG. 28, the FPD 1 transmits the interlock release signal as described above, and at the same time, turns off the TFT 8 and shifts to the charge accumulation state. Then, radiation is irradiated during the accumulation time τ. Then, after the accumulation time τ has elapsed, the FPD 1 sequentially applies on-voltages to the lines L1 to Lx of the scanning line 5 from the gate driver 15b, and performs a process of reading the image data D from each radiation detection element 7. Configured as follows.

When imaging is performed in an asynchronous manner, the FPD 1 resets each radiation detection element 7 as imaging pre-processing as described above when the imaging mode is changed to the awakening mode as described above. After performing the above, as described above, in order to detect the start of the radiation irradiation by itself, it is configured to perform a radiation irradiation start detection process. For example, as described in Patent Document 5 described above, the leak data dleak is read before radiation irradiation, and the radiation irradiation start is detected based on the read leak data dleak. Is possible.

In addition, when reading the leak data dleak, as described above, the off-voltage is applied to all the scanning lines 5 from the gate driver 15b (see FIG. 2) of the FPD 1 so that each TFT 8 is turned off. Leak data dleak is read by performing a read operation. However, if the TFTs 8 are kept in the OFF state, dark charges are continuously accumulated in the respective radiation detection elements 7 as described above. Therefore, as shown on the left side of FIG. The dleak read process (see “L” in FIG. 5) and the reset process of each radiation detection element 7 (see “R” in FIG. 5) are alternately performed.

When an operator such as a radiologist operates the exposure switch 56 to irradiate radiation from the radiation source 52P as described above, the FPD 1 sets, for example, the leak data dleak read in a certain read process. The start of radiation irradiation is detected when the threshold value is exceeded (see “Detection” in FIG. 5). Then, when the start of radiation irradiation is detected in this way, the control means 22 of the FPD 1 applies an off voltage to each scanning line 5 from the gate driver 15b, and keeps all the TFTs 8 for a predetermined time, that is, the accumulation time τ described above. In the meantime, the electric charge generated in each radiation detection element 7 by irradiation of radiation is accumulated in each radiation detection element 7. As in the case of the synchronous method, after the accumulation time τ elapses, the image data D is read out from each radiation detection element 7.

In FIG. 5, in order to ensure that the effective accumulation time Tac in each of the lines L1 to Lx of the scanning line 5 is the same time, in the reading process of the image data D, the time when the start of radiation irradiation is detected or From the scanning line 5 to which the ON voltage is to be applied next (the line L5 of the scanning line 5 in the case of FIG. 5) to the scanning line 5 to which the ON voltage is applied immediately before (the line L4 of the scanning line 5 in the case of FIG. 5). The case where the application of the on-voltage is started and the on-voltage is sequentially applied from the gate driver 15b to each of the lines L5 to Lx and L1 to L4 of the scanning line 5 to perform the reading process is shown. However, for example, as shown in FIG. 28, the application of the on-voltage is started from the first line L1 of the scanning line 5, and the on-voltage is sequentially applied to the lines L1 to Lx of the scanning line 5 from the gate driver 15b. It is also possible to configure to perform processing.

Further, when the image data D is read out as described above, for example, the control means 22 of the FPD 1 extracts the preview image data Dp from the read image data D and transmits it to the console 58. 58, a preview image p # pre may be generated based on the preview image data Dp or the like and displayed on the display unit 58a or the display unit 71 of the mobile terminal 70. .

On the other hand, the control means 22 of the FPD 1 completes the reading process of the image data D (see FIGS. 5 and 28) as described above, and then performs the reading process of the offset data O as shown in FIGS. The reset process of each radiation detection element 7 is started. Then, as described above, in order to set the effective accumulation time Tac (see FIG. 5) for each scanning line 5 to the same time interval between the reading process of the image data D and the reading process of the offset data O, FIG. As shown in FIG. 29 and FIG. 29, the same processing sequence as the processing up to the reading processing of the image data D shown in FIG. 5 and FIG. 28 is repeated, and the reading processing of the offset data O is performed. When the control unit 22 of the FPD 1 performs the offset data O reading process as described above, the read image data D and the offset data O are transmitted to the console 58 (see FIGS. 3 and 4).

The console 58 calculates the true image data D ^* according to the above equation (2) based on the transmitted image data D and offset data O, and performs gain correction and defective pixels based on the true image data D ^*. The medical image p for diagnosis provision is generated by performing precise image processing such as correction and gradation processing according to the imaging region. When the generated diagnostic providing medical image p is approved by an operator such as a radiographer, the console 58 determines the generated diagnostic providing medical image p, and information on the confirmed diagnostic providing medical image p is displayed. Etc. are configured to be transmitted to a necessary location such as the PACS described above.

[Phenomenon that can occur in normal processing]
As shown in FIGS. 6 and 29, if the offset data O is read out, the same processing sequence as the processing sequence up to the reading processing of the image data D (see FIGS. 5 and 28) is repeated. In the image processing, by performing the calculation of the above equation (2) as described above, the offset o due to the dark charge superimposed on the image data D and the offset data O are offset, and the true image data D ^* should be calculated accurately, but in reality, as described above, even if the true image data D ^* is calculated as described above, it depends on the dark charge superimposed on the image data D. The offset o and the offset data O may not be offset. Then, when the diagnostic providing medical image p is generated based on the true image data D ^* calculated in a state where the offset o due to the dark charge and the offset data O are not offset, the image quality of the generated diagnostic providing medical image p May deteriorate.

As a result of repeated researches on the cause of the occurrence of such a phenomenon by the present inventors, in particular, as described above, immediately after the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode, the imaging and reading of the offset data O are performed. It has been found that the above phenomenon appears when done. The major cause of such a phenomenon is that the charge amount dQ per unit time generated in the radiation detection element 7 immediately after the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode as follows. It is thought to be a major change.

For example, when the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode, as shown in FIG. 7, it occurs in the radiation detection element 7 at the time of the transition to the awakening mode (see the time point t = 0 in FIG. 7). The charge amount dQ per unit time becomes a large value, and from this point, the charge amount dQ per unit time generated in the radiation detection element 7 gradually decreases as time t elapses. FIG. 7 is a graph showing the relationship between the elapsed time t from when the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode and the charge amount dQ per unit time generated in each radiation detection element 7. It is. Note that FIG. 7 does not include charges generated in each radiation detection element 7 due to radiation irradiation (that is, charges corresponding to true image data D ^* (see the above equation (1))).

Further, as time t elapses, the amount of charge dQ per unit time generated in each radiation detection element 7 gradually decreases, and finally becomes constant equal to the amount of dark charge generated per unit time described above. Settling down in value. Then, in such a situation, as shown in FIG. 5 and FIG. 28, reset processing of each radiation detecting element 7 before imaging is performed (in the case of FIG. 5, readout processing of leak data dleak is performed alternately with reset processing). ) Each TFT 8 is turned off to be in a charge accumulation state (radiation is irradiated during this period), and after the accumulation time τ has elapsed, the reading process of the image data D is performed. Then, after the image data D reading process, as shown in FIGS. 6 and 29, the same processing sequence as the image data D reading process shown in FIGS. O reading processing is performed.

In this case, the offset o due to the dark charge superimposed on the image data D and the offset data O are respectively during the effective accumulation time Tac (see FIGS. 5 and 28) before the image data D read processing, and Calculated as an integral value of the charge amount dQ (see FIG. 7) per unit time generated in each radiation detection element 7 during the effective accumulation time Tac (see FIGS. 6 and 29) before the offset data O reading process. Is done. Therefore, the offset o due to the dark charge superimposed on the image data D and the offset data O are values represented as the area of the region indicated by hatching, as shown in FIG.

After a lapse of time after the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode, the charge amount dQ per unit time generated in each radiation detection element 7 is reduced as described above, and the above-described Since the constant value is equal to the amount of dark charge generated per unit time, the offset amount o and the offset data O due to the dark charge superimposed on the image data D are equal to each other as shown in FIG. Therefore, as described above, when the calculation process for subtracting the offset data O from the image data D is performed as shown in the above equation (2), the offset o and offset data due to the dark charge superimposed on the image data D are obtained. It is possible to calculate true image data D ^* resulting from only the electric charges generated in each radiation detection element 7 by irradiation of radiation by offsetting O.

However, as shown in FIG. 8, immediately after the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode, the charge amount dQ per unit time generated in each radiation detection element 7 increases as the time t elapses. It is in a state of decreasing. Therefore, when the reading process of the image data D and the reading process of the offset data O are performed as described above in this state, the offset o due to the dark charge superimposed on the image data D is displayed as shown in FIG. Is larger than the offset data O. That is, if the difference between the offset o due to the dark charge superimposed on the image data D and the offset data O is Δ, the offset o due to the dark charge superimposed on the image data D and the offset data O In between
o = O + Δ (3)
However, in the case of FIG. 8, that is, in a state immediately after the photographing mode of the FPD 1 is changed from the sleep mode to the awakening mode, the difference Δ takes a positive value that is not zero. Then, D ^* = D−o (4) obtained by modifying the above equation (1).
If the above equation (3) is substituted,
D ^* = D−O−Δ (5)
Is obtained.

This and the above equation (2), that is,
D ^* = DO (2)
As can be seen from the above, when the offset data O is subtracted from the image data D in accordance with the above equation (2) in the image processing for generating the medical image p for diagnosis provision, the calculated true image data D ^* is a large value only original true image data D ^* that is, the equation (4) (i.e., (5)) true image data to be calculated by D ^* difference Δ than. That is, when the true image data D ^* is calculated according to the above equation (2) as in normal image processing, the calculated true image data D ^* is the above equation (4) (ie, the equation (5). ), The original true image data D ^* to be calculated is a value in which the offset due to the dark charge is superimposed by the difference Δ.

As described above, when the reading process of the image data D or the reading process of the offset data O is performed immediately after the photographing mode of the FPD 1 is changed from the sleep mode to the awakening mode (see FIG. 8), the image data D is superimposed on the image data D. A positive difference Δ significantly different from 0 is generated between the offset o due to the dark charge and the offset data O. Then, during the subsequent image processing, (2) calculating the true image data D ^* in accordance with equation was calculated true image data D ^*, i.e. dark charge true that should not contain any offset by The image data D ^* has a value in which the offset due to the dark charge is superimposed by the difference Δ. Therefore, when the diagnostic-providing medical image p is generated based on such true image data D ^* , the image quality of the generated diagnostic-providing medical image p is dark charge by the difference Δ from the true image data D ^*. Therefore, the amount of offset due to the superimposition deteriorates.

In particular, in order to avoid depletion of the battery 24 (see FIG. 2 and the like), a wake-up signal is transmitted from the console 58 to the FPD 1 by using the first button operation of the exposure switch 56 as a trigger. In the case where the photographing mode is changed from the sleep mode to the awakening mode, it is likely to be deteriorated.

[Configurations Specific to the Present Invention]
Next, a configuration unique to the present invention in the medical image system 50 for diagnosis provision and the FPD 1 according to the present embodiment will be described. The operation of the diagnostic providing medical image system 50 and the FPD 1 according to the present invention will also be described.

As described above, in the state immediately after the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode, the amount of charge dQ per unit time generated in each radiation detection element 7 changes with time. A non-zero positive difference Δ between the offset o and the offset data O due to the dark charge superimposed on D causes the image quality of the generated diagnostic-provided medical image p to deteriorate. ing. As the difference Δ increases, the degree of deterioration of the image quality of the generated diagnostic providing medical image p increases. Conversely, if the difference Δ decreases, the generated diagnostic providing use If the degree of deterioration of the image quality of the medical image p is reduced and the difference Δ is made sufficiently small, it is possible to prevent the image quality of the generated medical image p for diagnosis providing from being deteriorated. That is, as shown in FIG. 9, the offset o and offset data due to the dark charge superimposed on the image data D after a sufficient amount of time has elapsed since the shooting mode of the FPD 1 was changed from the sleep mode to the awakening mode. When the medical image p for diagnosis providing is generated based on the image data D and the offset data O read out in a state equal to O, the high quality diagnostic providing medical image p is generated. If it can be made smaller, it is possible to generate a medical image p for diagnosis providing with a picture quality as high as this.

Therefore, in the diagnostic providing medical image system 50 according to the present embodiment, a predetermined time (hereinafter, this time is referred to as a waiting time WT) has elapsed since the imaging mode of the FPD 1 was changed from the sleep mode to the awakening mode. Shooting is allowed after the difference Δ is sufficiently small.

Specifically, in the present embodiment, as shown in FIG. 10, the control means 22 of the FPD 1 counts the elapsed time t after the shooting mode is changed from the sleep mode to the awake mode, and the elapsed time t is When the waiting time WT of elapses, a signal is transmitted to the notification device. The notification device is configured to notify an operator such as a radiologist that radiation can be emitted from the radiation generation device 55 when receiving the above signal from the FPD 1. Yes. In the present embodiment, the console 58 (see FIG. 3 and FIG. 4) functions as the above notification device. When the console 58 (hereinafter referred to as the notification device 58) as the notification device receives the above signal from the FPD 1, for example, the console 58 displays “Shooting can be performed” or the like on the display unit 58a or utters a voice. For example, it can be configured to notify that it is possible to perform imaging by irradiating radiation from the radiation generating device 55. Further, as the notification device, for example, the portable terminal 70 shown in FIG. 4 may be used, and the notification device may be configured as a separate device from the console 58. In addition, a plurality of devices including the console 58 can be configured to function as a notification device.

As described above, the “detection process” in FIG. 10 is as described above after the FPD 1 transitions to the awake mode and performs the reset process of each radiation detection element 7 when imaging is performed in an asynchronous manner. This represents a transition to detection processing of the start of irradiation with various radiations. In addition, when the imaging is performed in a synchronous manner, the reset process of each radiation detection element 7 is repeatedly performed after the FPD 1 transitions to the awakening mode. For example, a predetermined number of times for power saving or the like. It is also possible to configure such that the reset process is temporarily stopped after the reset process is performed and the reset process is restarted before the waiting time WT elapses.

If comprised as mentioned above, the control means 22 of FPD1 will transmit a signal to the alerting | reporting apparatus 58, and only the said waiting time WT will pass after imaging | photography mode is changed from sleep mode to awakening mode, and the alerting | reporting apparatus 58 However, it is notified that it is possible to perform imaging by irradiating radiation from the radiation generating device 55. Then, an operator such as a radiologist who has confirmed the notification by the notification device 58 operates the exposure switch 56 to irradiate radiation from the radiation generation device 55 and performs imaging. Therefore, as shown in FIG. 11, the offset o due to the dark charge superimposed on the image data D read out in this way, and the offset read out in the subsequent read-out process It is possible to make the difference Δ with the data O sufficiently small. Then, by reducing the difference Δ, the degree of deterioration of the image quality of the diagnostic providing medical image p generated by the subsequent image processing is sufficiently reduced, and the generated diagnostic providing medical image p is actually reduced. It is possible to prevent the image quality from deteriorating. In other words, in the waiting time WT, the difference Δ is sufficiently small, and the image quality of the medical image p for diagnosis providing generated based on the read image data D and offset data O is high. In practice, the time is set so that it does not appear to have deteriorated.

On the other hand, the difference Δ, that is, the difference Δ between the offset o due to the dark charge superimposed on the image data D and the offset data O increases as the effective accumulation time Tac (see FIGS. 5 and 28, etc.) changes. Changes. Therefore, as shown in FIG. 12, for example, the notification device 58 can take a picture when the same waiting time WT as the waiting time WT shown in FIG. 11 has elapsed after the shooting mode of the FPD 1 is changed from the sleep mode to the awakening mode. Even if it is notified that, as shown in FIG. 12, if the effective accumulation time Tac becomes longer, the difference Δ becomes larger than the case shown in FIG. Therefore, if the diagnostic providing medical image p is generated based on the image data D and the offset data O read in such a state, the image quality of the diagnostic providing medical image p may be deteriorated.

That is, in order to prevent the image quality of the medical image p for diagnosis providing from deteriorating, it is necessary to change the waiting time WT according to the effective accumulation time Tac. That is, when the effective accumulation time Tac is long, it is necessary to lengthen the waiting time WT as shown in FIG. 13, for example, in order to sufficiently reduce the difference Δ. As described above, when the FPD 1 is configured such that the irradiation of radiation to the FPD 1 is allowed after the waiting time WT has elapsed since the imaging mode of the FPD 1 has been changed from the sleep mode to the awakening mode, the image on the FPD 1 It is necessary to switch the waiting time WT according to the effective accumulation time Tac in the data D reading process or the offset data O reading process.

Therefore, the waiting time WT is set to be different according to the effective accumulation time Tac in the FPD 1, and the waiting time WT is switched according to the set effective accumulation time Tac. Yes. However, in actual control in the FPD 1, the effective storage time Tac is often set by the storage time τ (see FIG. 5, FIG. 28, etc.) that is the duration of the charge storage state.

That is, for example, in the case of the synchronous method shown in FIG. 28, the timing for sequentially applying the ON voltage to each scanning line 5 in the reset processing of each radiation detecting element 7 before the charge accumulation state (that is, the ON voltage is applied to a certain scanning line 5). The time interval from the application to the application of the ON voltage to the next scanning line 5 (the same applies hereinafter) is determined in advance. In addition, the timing at which the ON voltage is sequentially applied to each scanning line 5 in the reading process of the image data D performed after the charge accumulation state is also determined in advance. Therefore, if the accumulation time τ is set, the effective accumulation time Tac is automatically determined. Also, for example, in the case of the asynchronous method shown in FIG. 5, the on-voltage is sequentially applied to each scanning line 5 in the reset processing of each radiation detection element 7 that is alternately performed with the reading processing of the leak data dleak before the charge accumulation state. The application timing is determined in advance. In addition, the timing at which the ON voltage is sequentially applied to each scanning line 5 in the reading process of the image data D performed after the charge accumulation state is also determined in advance. Therefore, even in the case of the asynchronous method, the effective accumulation time Tac is automatically determined by setting the accumulation time τ. Thus, setting the accumulation time τ is synonymous with determining the length of the effective accumulation time Tac. In this embodiment, as described above, in the actual control in the FPD 1, the accumulation time τ is set to The effective accumulation time Tac is determined by setting.

Therefore, in the present embodiment, the waiting time WT is set to a different time according to the accumulation time τ in the FPD 1. Specifically, as shown in FIG. 11 and FIG. The waiting time WT is set so that the waiting time WT becomes longer as the set accumulation time τ (that is, the effective accumulation time Tac) is longer. The waiting time WT is switched according to the set accumulation time τ.

It should be noted that the accumulation time τ can be set at any time interval, and what waiting time WT is associated with each set accumulation time τ is the performance of the FPD 1, that is, FIG. The charge amount dQ per unit time generated in the radiation detection element 7 shown in FIG. Further, for example, when the radiation source 52 of the radiation generating device 55 irradiates radiation, the dose rate of the irradiated radiation (that is, the dose per unit time) instantaneously rises to a prescribed dose rate, and when the irradiation ends. In some cases, there is an irradiation characteristic such that the dose rate of irradiated radiation falls instantaneously. In the case of such a radiation source 52, it is not necessary to set the accumulation time τ to a time longer than necessary. For example, when the radiation source 52 emits radiation, the dose rate of the irradiated radiation is It may take a long time to rise slowly and reach a prescribed dose rate, and may have an irradiation characteristic that the dose rate of the irradiated radiation gradually falls at the end of irradiation. In such a case, it is necessary to set the accumulation time τ to be long so as not to waste the radiation emitted from the radiation source 52. In this way, the accumulation time τ can be set at any time interval, and what waiting time WT is associated with each set accumulation time τ is determined by irradiating the FPD 1 with radiation. It can also vary depending on the irradiation characteristics of the radiation source 52 of the radiation generator 55.

Also, depending on the imaging region of the patient, which is the subject, the imaging method for the subject, etc., it may be necessary to perform imaging by irradiating the radiation from the radiation generator 55 for a longer time than usual. Therefore, when imaging is performed with such an imaging region or imaging method, it is necessary to set the accumulation time τ to be long. Therefore, based on the specifications of the FPD 1, the specifications of the diagnostic providing medical image system 50 in which the FPD 1 is used, the imaging conditions including the imaging region and the imaging method, etc., the settable accumulation time τ and each accumulation time τ The length of the waiting time WT associated with each is determined in advance as appropriate. In this case, the accumulation time τ can be set as a discrete time interval, or can be set as a time interval that can be continuously changed. For example, when the accumulation time τ is set as a time interval that can be continuously changed, the waiting time WT may be set in advance as a function of the accumulation time τ.

[effect]
As described above, according to the diagnostic providing medical image system 50 and the FPD (ie, radiographic imaging apparatus) 1 according to the present embodiment, the waiting time WT is set in advance according to the accumulation time τ as described above. Keep it. The waiting time WT is configured to be switched according to the accumulation time τ. At that time, the waiting time WT is a time from when the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode until irradiation of the radiation to the FPD 1 is permitted. When shooting is performed with irradiation, the difference Δ between the offset o due to the dark charge superimposed on the image data D and the offset data O becomes sufficiently small, and based on such image data D and offset data O. The time is set so that the image quality of the medical image p for diagnosis providing generated in this way can be prevented from deteriorating.

Then, when the imaging mode is changed from the sleep mode to the awakening mode by receiving an awakening signal from the console 58 or the like, the control means 22 of the FPD 1 counts an elapsed time t after the transition to the awakening mode. Then, when the elapsed time t has elapsed by the waiting time WT, a signal is transmitted to the notification device 58 (console 58 in the present embodiment), and the notification device 58 notifies the operator such as a radiologist to the radiation generation device 55. It is informed that it is possible to shoot with radiation. Then, an operator such as a radiologist who has confirmed the notification by the notification device 58 operates the exposure switch 56 to irradiate the FPD 1 with radiation from the radiation source 52 of the radiation generation device 55 through the subject to perform imaging.

Therefore, when the operator irradiates the FPD 1 with radiation through the subject, imaging is performed in this way, the image data D is read out, and then the processing sequence until the reading processing of the image data D is repeated to offset. When the data O is read to read the offset data O, and the medical image p for diagnosis providing is generated based on the read image data D or the offset data O, the offset o due to the dark charge superimposed on the image data D is generated. And the offset data O are sufficiently small, the deterioration of the image quality of the generated diagnostic-provided medical image p is accurately prevented.

In the present embodiment, in this way, after the shooting mode of the FPD 1 is changed from the sleep mode to the awakening mode, shooting is performed in a short time, the image data D is read by the FPD 1, and the offset data O reading process is subsequently performed. Even in this case, it is possible to accurately prevent the image quality of the medical image p for diagnosis providing generated based on the image data D and the offset data O read out in this way from being deteriorated. .

[How to set storage time etc. in FPD]
Next, how to set the accumulation time τ in the FPD 1 will be described. In the present embodiment, as described above, for example, as illustrated in FIG. 6, the offset data O reading process repeats the same processing sequence up to the image data D reading process illustrated in FIG. 5. Done. Therefore, the accumulation time τ is set to the same time interval in the charge accumulation state before the image data D reading process (see FIG. 5) and the charge accumulation state before the offset data O reading process (see FIG. 6). Therefore, in this embodiment, by setting the accumulation time τ (see FIG. 5 and FIG. 28) in the charge accumulation state before the reading process of the image data D, the charge accumulation before the offset data O reading process is automatically performed. The storage time τ in the state (see FIG. 6 and FIG. 29) is set.

As a method of setting the accumulation time τ to the FPD 1, for example, an operator such as a radiographer can input the accumulation time τ to the console 58 and transmit it from the console 58 to the FPD 1 to set it. It is. For example, in the center of the screen H1 (see FIG. 14) displayed on the display unit 58a of the console 58, there is a display space S in which the preview image p # pre generated by the console 58, the medical image p for providing diagnosis, and the like are displayed. Is provided. On the left side of the screen H1, an icon I corresponding to the imaging order information selected by the operator such as a radiographer from the imaging order information obtained by the console 58 from the RIS or the like (see FIG. 19 to be described later) is displayed. It has come to be. On the right side of the screen H1, a button icon for designating the size of the FPD 1 to be used and designating how to display the preview image p # pre, the medical image for diagnosis p, etc. in the display space S, etc. BI etc. are displayed.

For example, when a predetermined icon on the screen H1 is clicked or a mouse is right-clicked on the screen H1, a screen H2 as shown in FIG. 15 is displayed on the display unit 58a of the console 58. It has become. For example, on the screen H <b> 2, “AP (front)”, “PA (back)”, “LAT (side)”, etc. are taken with respect to an imaging region such as “Chest” or “Abdomen”. The direction can be specified. In the example shown in FIG. 15, for each imaging direction of each imaging region, either a normal accumulation time τ such as 1 second or a long accumulation time τ such as 10 seconds can be set. .

In the example shown in FIG. 15, the button icon BI without “LONG” is a button icon for setting the normal accumulation time τ simultaneously with the imaging region and imaging direction, and “LONG” is added. The button icon BI is a button icon for setting an accumulation time τ of a longer time simultaneously with an imaging region and an imaging direction. Further, as described above, instead of switching from the screen H1 (see FIG. 14) to the screen H2 (see FIG. 15) and setting the accumulation time τ, as shown in FIG. 16, for example, a button icon shown on the right side of the screen H1 Each button icon BI ^* representing a normal accumulation time τ and a long accumulation time τ may be displayed in the BI group or the like, and the accumulation time τ may be set on the screen H1. Further, in the examples shown in FIG. 15 and FIG. 16, a case is shown in which only one of a normal accumulation time and a longer accumulation time can be set as the accumulation time τ. However, when the button icons BI to be displayed are further increased to increase the number of accumulation times τ that can be set to three or more, or as described above, the accumulation time τ is set as a time interval that can be continuously changed. Can be configured such that an operator such as a radiologist inputs and sets the accumulation time τ on the screen H1 or the screen H2 using a keyboard or the like.

Although not shown in the drawings, an operator such as a radiographer can be configured by displaying information on the set accumulation time τ on the display space S in the center of the screen H1 shown in FIGS. Is preferable because it is possible to easily check the length of the set accumulation time τ by looking at the display space S of the screen H1. Further, as described above, the waiting time WT elapses after the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode, and a signal is transmitted from the FPD 1 to the console 58 that is a notification device. To notify the operator that radiation can be performed from the radiation generation device 55, for example, as described above, on the display space S of the screen H1 "can be photographed." It is possible to make a notification such as by displaying “ Also, until the above-described waiting time WT elapses, for example, “Starting” or “Preparing” is displayed on the display space S of the screen H1, and the FPD 1 is starting or preparing. It is also possible to configure so as to notify an operator such as a radiologist that the imaging is not yet possible.

As described above, when the accumulation time τ is set, the console 58 is configured to transmit and set information on the set accumulation time τ to the FPD 1. At that time, if the wake-up signal is not yet transmitted to the FPD 1, the console 58 transmits the wake-up signal to the FPD 1 as described above to change the photographing mode of the FPD 1 from the sleep mode to the wake-up mode. It is possible to configure the storage time τ to be transmitted to the FPD 1. If the wake-up signal is already transmitted to the FPD 1, the console 58 transmits the information on the accumulation time τ set to the FPD 1 when the accumulation time τ is set as described above. Configured to set.

When configured as described above, the FPD 1 is configured in advance to include a table that associates the accumulation time τ with the waiting time WT, a function that associates the waiting time WT as a function of the accumulation time τ, and the like. When the wake-up signal is received and the photographing mode of the FPD 1 is changed from the sleep mode to the wake-up mode, the control means 22 of the FPD 1 starts counting the elapsed time t. Further, the control means 22 of the FPD 1 calculates the waiting time WT from the above table, function, etc. based on the information of the accumulation time τ obtained from the console 58. A signal is transmitted to the notification device 58 when the elapsed time t has elapsed by the determined waiting time WT. When an operator such as a radiologist operates the exposure switch 56 to irradiate the radiation generating device 55 with radiation, the control means 22 of the FPD 1 stores the accumulated time τ transmitted from the console 58. Only the charge accumulation state is continued, and the image data D is read or the offset data O is read.

In this way, by configuring the console 58 to transmit the information of the accumulation time τ to the FPD 1, it is possible to accurately exhibit the beneficial effects in the above embodiment. As described above, instead of configuring the console 58 to transmit the storage time τ information to the FPD 1, it is possible to configure the console 58 to transmit the waiting time WT information to the FPD 1. In the case of such a configuration, for example, the console 58 is input by an operator such as a radiographer or specified in the imaging order information obtained from the RIS or the like. The waiting time WT is determined based on information such as the generation device 55 and the imaging conditions such as the imaging region and imaging method, and the information of the determined waiting time WT is transmitted to the FPD 1 and set. Then, when information on the waiting time WT is transmitted from the console 58, the control means 22 of the FPD 1 calculates the accumulation time τ from a table or function (or its inverse function) provided in advance based on the information. Thus, even if it is configured to transmit the waiting time WT information from the console 58 to the FPD 1, it is possible to accurately exhibit the beneficial effects described above in the present embodiment.

[Second and subsequent shots]
Here, for example, as shown in FIG. 17, after the short waiting time WT1 has elapsed since the shooting mode of the FPD 1 was changed from the sleep mode to the awakening mode, the first shooting is immediately performed under a short accumulation time τ1. Next, consider a case where the second imaging is performed under the long accumulation time τ2 after the long waiting time WT2 elapses. In FIG. 17, “D” is a process for reading image data D, “O” is a process for reading offset data O, and “R” is a reset process for each radiation detection element 7 (in the case of the asynchronous method, radiation irradiation start is performed). Including detection processing).

In such a case, as shown in FIG. 17, at the time t ^* when the reading process of the image data D is performed in the first shooting and the reading process of the offset data O is subsequently performed, the second process is still performed. There is a case where the long waiting time WT2 corresponding to the long accumulation time τ2 in photographing has not elapsed. As described above, after the shooting mode of the FPD 1 is changed from the sleep mode to the awakening mode, when the second and subsequent shootings are performed following the first shooting, the shooting mode is changed from the sleep mode to the awakening mode in the second and subsequent shootings. If the elapsed time t since the transition to is not the waiting time WT2 switched according to the accumulation time τ2 in the second and subsequent shootings, the control means 22 of the FPD 1 As shown in FIG. 17, when the offset data O reading process ends, a signal is transmitted to the notification device 58 when the waiting time WT2 in the second and subsequent shootings has elapsed, and the notification device 58 is notified. It is comprised so that it may alert | report that imaging | photography is possible.

With this configuration, it is possible to enable shooting after a sufficient waiting time WT2 has elapsed in the second and subsequent shootings, and the darkness superimposed on the image data D also in the second and subsequent shootings. The difference Δ between the offset o due to the charge and the offset data O can be set to a sufficiently small value, and is generated based on the read image data D and offset data O in the second and subsequent shootings. It is possible to accurately prevent the image quality of the diagnostic providing medical image p to be deteriorated.

Needless to say, the present invention is not limited to the above-described embodiment and the like, and can be appropriately changed without departing from the gist of the present invention. For example, in order to save energy (longer life) of the battery 24 (see FIG. 2 etc.) built in the FPD 1, the imaging mode is set to the sleep mode when the patient who is the subject is positioned, and the stage where the positioning is completed (ie, radiation) At the stage when the irradiation of the FPD 1 becomes possible, a method of changing the photographing mode of the FPD 1 from the sleep mode to the awakening mode is effective. Therefore, after the positioning of the FPD 1 and the patient H is completed, a wake-up signal is transmitted from the console 58 to the FPD 1 to change the imaging mode of the FPD 1 from the sleep mode to the wake-up mode. Aiming at effect, triggering first button operation of exposure switch 56 as trigger, sending wake-up signal from radiation generator 55 to FPD1 via console 58, wakes up FPD1 shooting mode from sleep mode It may be configured to transition to a mode.

In the above configuration, since the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode immediately before actual radiation irradiation, the FPD 1 is irradiated with radiation after the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode. Elapsed time t is likely to be shortened. At this time, when the FPD 1 is controlled in an asynchronous manner, the radiation generating device 55 is operated in the same manner as in the synchronous manner when the second stage operation of the exposure switch 56 is performed by an operator such as a radiation technician. Rather than irradiating the radiation for the first time after receiving the interlock release signal from the FPD 1, radiation irradiation can be started immediately when the second stage operation is performed. Therefore, the elapsed time t from when the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode until the radiation is applied to the FPD 1 is likely to be shorter, and the above-described problem of deterioration in the image quality of the medical image p for diagnosis provision Is more likely to occur.

On the other hand, when the FPD 1 is controlled in a synchronous manner, the waiting time until the interlock release signal is transmitted after the operator performs the second-stage operation on the button of the exposure switch 56 becomes longer. (That is, it becomes longer by the waiting time WT set in accordance with the accumulation time τ), and irradiation of radiation is not started until the interlock release signal is transmitted, so that the imaging mode of the FPD 1 is awakened from the sleep mode. The elapsed time t from when the mode is changed to when the FPD 1 is irradiated with radiation can be made sufficiently long, and there is no problem of deterioration of the image quality of the medical image p for diagnosis provision. Therefore, when the asynchronous FPD 1 is used, in order to prevent an operator such as a radiologist from performing the second button operation immediately after the first button operation, in other words, the operator waits. In order to perform the button operation of the second stage after the time WT has elapsed, as described in the above embodiment, the notification device is configured to accurately notify an operator such as a radiologist. It is preferable to do.

At this time, an operator such as a radiologist is present in the vicinity of the exposure switch 56, and it is assumed that the screen displayed on the display unit 58a of the console 58 cannot be visually recognized. The display unit 58a displays that it is possible to shoot and informs that it is possible to shoot with sound such as a beep sound (that is, the second-stage button operation on the exposure switch 56 is possible). It is preferable to configure.

[Configuration for Reducing Charge Quantity dQ per Unit Time Generated in Radiation Detecting Element]
By the way, the reason why the waiting time WT is switched according to the accumulation time τ in the medical image system for diagnosis providing 50 according to the present embodiment is that the imaging mode of the FPD 1 is changed from the sleep mode as shown in FIG. At the time of transition to the awakening mode (see the time t = 0 in FIG. 7), the charge amount dQ per unit time generated in the radiation detection element 7 becomes a large value, and as time t elapses from there. This is because the charge amount dQ per unit time generated in the radiation detection element 7 gradually decreases. Therefore, if the charge amount dQ per unit time generated in the radiation detection element 7 can be further reduced, the waiting time WT set according to the accumulation time τ can be further shortened.

As a result of repeated studies by the present inventors, when the photographing mode of the FPD 1 is the sleep mode, the scanning line 5, the signal line 6, the radiation detection element 7, and the TFT 8 described above are set at certain time intervals. Is generated in the radiation detection element 7 when the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode (refer to the time t = 0 in FIG. 7). It has been found that the charge amount dQ per unit time can be made smaller.

The reason why such a phenomenon occurs is considered as follows. That is, when the imaging mode of the FPD 1 is the awakening mode, as described above, for example, −5 [V] or the like is supplied to each radiation detection element 7 from the bias power source 14 (see FIG. 2 etc.) via the bias line 9. A reverse bias voltage is applied. When the imaging mode of the FPD 1 transitions from the awakening mode to the sleep mode, the application of the reverse bias voltage to each radiation detection element 7 is stopped. However, at that time, as shown in FIG. 18, the voltage Vb applied from the bias power supply 14 to each radiation detection element 7 is actually 0 [V] instantaneously from the reverse bias voltage of the predetermined voltage value Vbias. However, it changes so as to gradually approach 0 [V] in a state having a predetermined time constant. In FIG. 18, Mw represents the period of the awakening mode, and Ms represents the period of the sleep mode.

While the above phenomenon occurs in the sleep mode, as described above, the panel unit is energized for a predetermined time at certain time intervals, and the reverse bias voltage is applied from the bias power source 14 to each radiation detection element 7. When Vbias is applied, the voltage Vb that has gradually increased toward 0 [V] as shown in FIG. 18 decreases to a reverse bias Vbias such as −5 [V]. When the application of the reverse bias voltage Vbias from the bias power supply 14 to each radiation detection element 7 is stopped after a predetermined time has elapsed, the voltage Vb applied from the bias power supply 14 to each radiation detection element 7 is gradually increased. Change to approach 0 [V]. Therefore, as described above, the voltage Vb applied to each radiation detection element 7 from the bias power supply 14 is returned to 0 [V] by repeatedly energizing the panel unit for a predetermined time at certain time intervals. Instead, the state of taking a negative voltage value between the reverse bias voltage Vbias and a predetermined negative voltage is maintained.

On the other hand, in a state where the voltage Vb applied to each radiation detection element 7 from the bias power supply 14 of the FPD 1 in the sleep mode is in the above-described state, an operator such as a radiographer takes an image from the console 58 for imaging. Consider a case where the shooting mode of the FPD 1 is changed from the sleep mode to the awake mode by transmitting a wake-up signal to the FPD 1. Then, when the operation as described above in the sleep mode is not performed, the voltage Vb applied to each radiation detection element 7 from the bias power supply 14 during the sleep mode returns to 0 [V]. At the time of transition, the voltage Vb applied to each radiation detection element 7 decreases from 0 [V] to a predetermined reverse bias voltage Vbias such as −5 [V]. That is, the change amount of the voltage Vb applied to each radiation detection element 7 in this case is, for example, 5 [V].

On the other hand, in the sleep mode, when the operation of energizing the panel portion of the FPD 1 for a predetermined time is performed at certain time intervals as described above, each radiation detection is performed from the bias power source 14 during the sleep mode. The voltage Vb applied to the element 7 does not return to 0 [V], and takes a negative voltage value between the reverse bias voltage Vbias and a predetermined negative voltage as described above. Therefore, the change amount of the voltage Vb applied to each radiation detection element 7 at the time of transition to the awakening mode is a change amount smaller than the above 5 [V].

The magnitude of the charge amount dQ per unit time generated in the radiation detection element 7 at the time when the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode (see the time t = 0 in FIG. 7) is This is determined depending on the amount of change in the voltage Vb applied to each radiation detection element 7 at the time of transition to the awakening mode. That is, the magnitude of the charge amount dQ per unit time generated in the radiation detection element 7 at the time when the imaging mode of the FPD 1 is changed from the sleep mode to the awake mode is the detection of each radiation at the transition to the awake mode. If the change amount of the voltage Vb applied to the element 7 is large, the charge amount dQ increases, and if the change amount of the voltage Vb is small, the charge amount dQ also decreases.

Therefore, as described above, when the shooting mode of the FPD 1 is the sleep mode, the FPD 1 shooting mode is awakened from the sleep mode by energizing the panel unit for a predetermined time at certain time intervals. The amount of charge dQ per unit time generated in the radiation detection element 7 at the time of transition to the mode (refer to the time t = 0 in FIG. 7) can be made smaller.

Therefore, in the FPD 1, the control means 22 can be configured to energize the panel unit for a predetermined time at predetermined time intervals when the photographing mode of the FPD 1 is in the sleep mode. With this configuration, as described above, the amount of charge dQ per unit time generated in the radiation detection element 7 is changed to the time when the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode (t in FIG. 7). It is possible to reduce the size at = 0). Then, by reducing the size at the time of transition to the awakening mode, the subsequent charge amount dQ per unit time can be reduced.

That is, it is possible to further reduce the amount of charge dQ per unit time generated in the radiation detection element 7 at each time t as compared with FIG. 7 or the like when not configured as described above. With this configuration, the charge amount dQ per unit time generated in the radiation detection element 7 can be reduced as a whole. Therefore, for example, compared with the case shown in FIG. 13 in which the waiting time WT is set based on the graph of FIG. 7, even if the waiting time WT is made shorter, the offset o due to the dark charge superimposed on the image data D is obtained. And the difference Δ between the offset data O and the offset data O can be sufficiently reduced. Therefore, by configuring as described above and further reducing the charge amount dQ per unit time generated in the radiation detection element 7, the waiting time WT set according to the above-described accumulation time τ is further shortened. It becomes possible.

Further, as described above, when the imaging mode of the FPD 1 is the sleep mode, instead of the configuration in which the reverse bias voltage Vbias is periodically applied from the bias power source 14 to each radiation detection element 7, the imaging mode of the FPD 1 Is in the sleep mode, every time the voltage applied from the bias power supply 14 to each radiation detection element 7 rises and reaches a threshold value, the bias power supply 14 applies a predetermined voltage value to each radiation detection element 7 for a predetermined time. It is also possible to apply a reverse bias voltage Vbias.

That is, as shown in FIG. 18, after the reverse bias voltage Vbias is applied from the bias power supply 14 to each radiation detection element 7 in the awakening mode, the voltage Vb applied from the bias power supply 14 to each radiation detection element 7 is predetermined. The reverse bias voltage of the voltage value Vbias is not instantaneously 0 [V], but gradually approaches 0 [V] in a state having a predetermined time constant.

Therefore, even in the sleep mode, the control unit 22 is configured to monitor the voltage Vb applied to each radiation detection element 7 from the bias power supply 14, and the voltage Vb increases as shown in FIG. When a threshold (not shown) is reached, a reverse bias voltage having a predetermined voltage value Vbias is applied from the bias power supply 14 to each radiation detection element 7 for a predetermined time. Then, the voltage Vb applied from the bias power supply 14 to each radiation detection element 7 falls to the reverse bias voltage of the predetermined voltage value Vbias.

Then, when a predetermined time elapses, the application of the reverse bias voltage of the predetermined voltage value Vbias is stopped. Then, the voltage Vb applied from the bias power supply 14 to each radiation detection element 7 increases, and when the voltage Vb reaches a threshold value, the bias power supply 14 applies a predetermined voltage value to each radiation detection element 7 for a predetermined time. A reverse bias voltage of Vbias is applied.

Thus, every time the voltage Vb applied from the bias power supply 14 to each radiation detection element 7 rises and reaches a threshold value, the reverse bias of the predetermined voltage value Vbias from the bias power supply 14 to each radiation detection element 7 for a predetermined time. It is also possible to configure to apply a voltage. With this configuration, as described above, the imaging of the FPD 1 is performed as in the case where the reverse power supply voltage Vbias is periodically applied to each radiation detection element 7 from the bias power supply 14 in the sleep mode. The charge amount dQ per unit time generated in the radiation detection element 7 at the time when the mode is changed from the sleep mode to the awakening mode (refer to the time t = 0 in FIG. 7) can be set to a smaller value. .

On the other hand, as described above, when the imaging mode of the FPD 1 is the sleep mode, the panel portion of the FPD 1 is energized for a predetermined time at regular time intervals, and the reverse bias voltage is applied from the bias power source 14 to each radiation detection element 7 during that period. By applying Vbias or by applying a reverse bias voltage Vbias from the bias power supply 14 to each radiation detection element 7 every time the voltage Vb applied from the bias power supply 14 to each radiation detection element 7 rises and reaches a threshold value. The charge amount dQ per unit time generated in the radiation detection element 7 at the time when the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode (refer to the time t = 0 in FIG. 7) is set to a smaller value. If it can, the bias power supply 14 can be advanced one step further while the shooting mode of the FPD 1 is in the sleep mode. It is also possible to configure to continue to apply a continuously to reverse-bias voltage Vbias Luo each radiation detection element 7.

That is, when the imaging mode of the FPD 1 is the awakening mode, the reverse bias voltage Vbias is applied from the bias power supply 14 to each radiation detection element 7 via the bias line 9, but after the imaging mode is switched to the sleep mode. Alternatively, the reverse bias voltage Vbias can be continuously applied from the bias power source 14 to each radiation detection element 7.

With this configuration, the charge amount dQ per unit time generated in the radiation detection element 7 at the time when the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode can be further reduced. It is possible to further reduce the waiting time WT set in accordance with the accumulation time τ described above. Therefore, it is possible to perform imaging by irradiating the FPD 1 with radiation more quickly after the imaging mode of the FPD 1 is changed from the sleep mode to the awakening mode.

[Effects of vibration, etc. applied to FPD]
By the way, in the above-described embodiment and the like, since the offset o due to the dark charge superimposed on the image data D and the offset data O have the same size (that is, o = O), no radiation is irradiated after imaging. Thus, the offset data O is read out by repeating the same processing sequence as the processing sequence from the reset process of each radiation detection element 7 to the readout process of the image data D at the time of imaging. However, as shown in FIG. 7, when the charge amount dQ per unit time generated in the radiation detection element 7 changes the imaging mode of the FPD 1 from the sleep mode to the awakening mode (t = 0 in FIG. 7 and the like). Since the phenomenon becomes a large value at the time of (3) and then gradually decreases as the time t elapses, imaging is performed immediately after the imaging mode is changed to the awakening mode, and the offset data O is read out. The offset o due to the dark charge superimposed on the image data D and the offset data O are not the same size. Therefore, by switching the waiting time WT after changing the photographing mode of the FPD 1 from the sleep mode to the awakening mode according to the accumulation time τ in the charge accumulation state, the offset o due to the dark charge superimposed on the image data D is obtained. As described above, the offset data O and the offset data O are configured to have substantially the same size.

In this way, by subtracting the offset data O from the image data D in the subsequent image processing, the offset amount o due to the dark charge superimposed on the image data D and the offset data O are offset, It is possible to calculate the true image data D ^* resulting from the electric charge generated in each radiation detection element 7 due to the irradiation of radiation, and the image quality of the medical image p for diagnosis providing generated based on this is deteriorated. It becomes possible to prevent accurately.

However, as a result of further research by the present inventors, the image data D is read out and the offset data O is read out as described above, and the read offset data O and the image data D are read out as described above. When the true image data D ^* is calculated by substituting into the equation (2), and the diagnostic providing medical image is generated based on the calculated true image data D ^* , the generated diagnostic providing medical image (so-called definite image) ) It has been found that artifacts may appear inside.

As a result of repeated researches on the cause of the occurrence of such a phenomenon by the present inventors, in particular, a so-called microphonic phenomenon (for example, the United States) caused by an impact or vibration applied to the FPD during the offset data O reading process. (See Japanese Patent No. 6707818, for example), artifacts appear in the offset data O to be read. Therefore, even if no artifact appears in the image data D, the artifact component in the offset data O remains in the calculated true image data D ^* by performing the calculation of the above equation (2). It has been found that artifacts appear in the diagnostic-provided medical image generated based on the true image data D ^* .

In view of such a problem, a diagnosis capable of accurately preventing vibrations and the like from being applied to the FPD during the offset data O reading process and preventing the offset data O to be read from including artifacts will be described below. The providing medical image system will be described.

Even in the medical image system 50 for diagnosis providing constructed in the imaging room R1 and the front room R2 as shown in FIG. 3, the patient as the subject collides with the Bucky device 51 loaded with the FPD1, and the like, the offset data. There is a possibility that a vibration or the like is applied to the FPD 1 during the O reading process. Such a situation occurs in the medical image system 50 for providing diagnosis constructed on the round wheel 60 as shown in FIG. Since it is easy, below, the case where the medical image system 50 for diagnosis provision constructed | assembled on the round-wheel 60 is brought in to the hospital room R3 and imaging | photography is demonstrated. In this case, it is possible to construct an interface between the FPD 1 and the radiation generator 55 and perform imaging in a synchronous manner, but in the following, a case in which imaging is performed in an asynchronous manner. explain. The same applies to the case of the diagnostic providing medical image system 50 constructed in the imaging room R1 or the like or the case where imaging is performed in a synchronous manner.

[Regarding normal processing procedures during shooting]
Here, first, a normal processing procedure of the control means 22 of the FPD 1 and the console 58 at the time of shooting will be briefly described.

Prior to imaging, an operator such as a radiographer operates the console 58 and obtains imaging order information relating to imaging to be performed, for example, from the RIS described above. For example, as illustrated in FIG. 19, the imaging order information includes “patient ID” P2, “patient name” P3, “sex” P4, “age” P5, “clinical department” P6, and imaging conditions as patient information. "Imaging part" P7, "imaging direction" P8, and the like. Then, the “shooting order ID” P1 is automatically assigned to each shooting order information in the order in which the shooting orders are received. Further, the imaging order information further includes a “modality ID” P9 indicating modality identification information such as the used Bucky device 51 (see FIG. 3) and the roundabout car 60 (see FIG. 4), and the “cassette ID” of the cassette to be used. "Items such as P10 are provided.

When the console 58 obtains the shooting order information as described above, the console 58 displays a list of each shooting order information in a list format on the selection screen H3 of the display unit 58a as shown in FIG. The selection screen H3 is provided with a shooting order information display field h11 for displaying a list of each shooting order information. On the left side of the shooting order information display field h11, shooting order information scheduled to be shot is displayed. A selection button h12 for selecting is provided. Further, an enter button h13 and a return button h14 are provided below the shooting order information display field h11. Then, the operator clicks the selection button h12 to select one or a plurality of shooting order information, and clicks the decision button h13. In addition, when one order information is selected, all the other imaging | photography order information with respect to the same patient as the said order information can also be comprised so that it can select automatically.

Then, for example, when an operator such as a radiologist selects four pieces of imaging order information regarding the patient “A” from the imaging order information of FIG. 20 and clicks the decision button h13, the console 58 is displayed on the display unit 58a. A screen H4 as shown in FIG. 21 is displayed. In the following, the case where the screen H4 is configured as shown in FIG. 21 and the like will be described. However, the screen H4 is the same screen as the screen H1 described above (see FIG. 14 and FIG. 16), and FIG. It is also possible to configure as shown in FIG.

In the screen H4, as shown in FIG. 21, each icon I corresponding to each shooting order information is displayed. Note that the icon I has a schematic diagram indicating the modality. The perspective view of the FPD described in each icon I in FIG. 21 shows that the FPD 1 is not loaded into the Bucky device. It shows that it is used in a single state. In addition, by clicking each button on the display Ia for setting the imaging condition displayed on the right side of the screen H4, the operator can set the tube voltage and tube current set by the radiation irradiation device 55 to the radiation source 52, The photographing conditions such as the irradiation time can be finely adjusted and set. Further, on the left side of the screen H4, the human body model Ib is shown so that the imaging part P7 (see FIGS. 19 and 20) designated by the imaging order information corresponding to the icon I displayed in focus can be seen. Is displayed.

The console 58 automatically selects one of the icons I1 to I4 displayed on the screen H4 (the icon I2 in the case of FIG. 21) so that the selected icon I stands out. Display in focus. Then, photographing based on photographing order information corresponding to the focused icon I is performed. When the operator wants to perform shooting based on different shooting order information, the focus can be changed by clicking and selecting another icon I corresponding to the shooting order information. .

On the other hand, as shown in FIG. 21, for example, when the console 58 selects and focuses on the icon I2 corresponding to the next shooting, the “cassette ID” P10 (specified in the shooting order information corresponding to the icon I2) A wake-up signal is transmitted to the FPD 1 in FIGS. 19 and 20, and the photographing mode of the FPD 1 is switched to the wake-up mode. In this case, an operator such as a radiographer loads the FPD 1 having the cassette ID “FPD-001” (see FIG. 19 and FIG. 20) on the round wheel 60 in advance, and the patient room R3 (see FIG. 4) together with the round wheel 60. It is carried in. Note that, as described above, instead of setting the timing at which the wake-up signal is transmitted from the console 58 to the FPD 1 as described above, for example, from the radiation generator 55, the first-stage operation of the exposure switch 56 (ie, so-called half-press The timing at which the signal indicating that the operation is performed may be received, and the timing for switching the imaging mode of the FPD 1 to the awakening mode is appropriately determined.

When the imaging mode is switched to the awakening mode, the FPD 1 starts a reset process for each radiation detection element 7 as a pre-process for imaging as described above. Then, an operator such as a radiologist positions the FPD 1 with respect to the patient H who is the subject, then moves to the round wheel 60 and operates the exposure switch 56 to operate the radiation source 52P of the radiation generator 55. Radiation. In the case of the asynchronous system, as described above, the FPD 1 detects the start of radiation irradiation based on, for example, the read leak data dleak, image data d for detection of irradiation start (see FIG. 5 and the like).

When an operator such as a radiologist operates the exposure switch 56 to irradiate radiation from the radiation source 52P as described above, the FPD 1 sets, for example, the leak data dleak read in a certain read process. The radiation start is detected when the threshold value is exceeded (see “detection” in FIG. 5 described above). Then, when the control means 22 of the FPD 1 detects the start of radiation irradiation, as described above, the gate driver 15b applies an off voltage to each scanning line 5 to turn off all the TFTs 8 during the accumulation time τ. Thus, the charge generated in each radiation detection element 7 due to radiation irradiation is accumulated in each radiation detection element 7, and after the accumulation time τ has elapsed, the image data D is read from each radiation detection element 7. Then, the image data D is read out.

Subsequently, when the control unit 22 of the FPD 1 performs the reading process of the image data D as described above, the preview image data Dp is extracted from the read image data D at a predetermined ratio and extracted as described above. The preview image data Dp is transmitted to the console 58. The extraction process of the preview image data Dp is performed as shown in FIG. 22, for example. As shown in FIG. 22, image data D read from the radiation detection elements 7 (n, m) in the n-th row and the m-th column among the radiation detection elements 7 arranged in a two-dimensional form of the FPD 1 is represented by D. If represented by (n, m), the control means 22 of the FPD 1 predetermines a predetermined number (FIG. 22) from the read image data D (n, m), for example, as shown by hatching in FIG. In this case, image data D (n, m) read out from each radiation detection element 7 connected to the designated scanning line 5 is extracted for every four scanning lines 5. The preview image data is Dp.

Then, the control means 22 of the FPD 1 extracts the preview image data Dp and transmits it to the console 58. When the preview image data Dp is transmitted from the FPD 1 as described above, the console 58 generates a preview image p # pre based on the transmitted data. The console 58 generates the preview image p # pre as described above every time the preview image data Dp is transmitted from the FPD 1, and the original icon of the screen H4 displayed on the display unit 58a. The preview image p # pre generated as shown in FIGS. 23A to 23C is wiped on I2.

For example, when imaging is performed using the FPD 1 having a size of 17 × 17 inches, if an operator such as a radiographer misplaces the FPD 1 vertically or horizontally when positioning the FPD 1, for example, FIG. 23A to FIG. As shown in 23C, a preview image p # pre or the like that is shifted by 90 ° from the original position is generated. However, in such a case, for example, the imaging region (the chest in this case) is automatically recognized from the luminance distribution of each pixel of the preview image p # pre shown in FIG. 23C, for example, as shown in FIG. 23C. As shown in FIG. 24, the preview image p # pre that has been rotated by 90 ° is rotated and corrected to the original display direction (that is, the direction used by the doctor for interpretation), as shown in FIG. Overwrite display. If the positioning of the FPD 1 is normal, the display direction does not change before and after the execution of the automatic part recognition process.

When the operator who has viewed the preview image p # pre clicks the “OK” button icon or displays the preview image p # pre for a predetermined time, the console 58 determines that the “NG” button icon is not clicked. (The same applies to a case where the mobile terminal 70 can be operated.) It is determined that the preview image p # pre has been approved by the operator. When the operator who has viewed the preview image p # pre clicks the “NG” button icon during the predetermined time, the console 58 displays the preview image data Dp transmitted from the FPD 1 so far. The FPD 1 is instructed to stop the processing being performed at that time and to start preprocessing such as reset processing of each radiation detection element 7 for re-imaging.

When the console 58 is configured to function as an image processing apparatus, the console 58 receives the remaining image data D, offset data O, or true image data D ^* from the FPD 1 as will be described later. When transmitted, precise image processing such as gain correction, defective pixel correction, and gradation processing according to the imaging region is performed based on these, and the diagnostic providing medical image p is generated. When an image processing apparatus separate from the console 58 is provided, the image processing apparatus performs the image processing described above. And although illustration is abbreviate | omitted, when the console 58 produces | generates the medical image p for diagnosis provision, it will display on the preview image p # pre currently displayed on the position of the original icon I2 on the screen H4 shown, for example in FIG. The generated diagnostic-provided medical image p is overwritten and displayed.

When the diagnostic providing medical image p is approved by an operator such as a radiologist clicking the “OK” button icon or the like, the console 58 displays information on the generated diagnostic providing medical image p or the like. The imaging order information corresponding to the imaging (that is, imaging order information corresponding to the icon I2) is determined and confirmed, and the confirmed medical image p for diagnosis providing and the imaging order information are transmitted to the necessary places such as the PACS described above. To do.

On the other hand, the control means 22 of the FPD 1 extracts the preview image data Dp from the read image data D as described above and transmits it to the console 58, that is, the read processing of the image data D (see FIG. 5). At the same time as the process ends, the reading process of the offset data O is started. This point is as described above. When the reading process of the offset data O is completed, the control unit 22 of the FPD 1 transmits the read image data D and the offset data O to the console 58.

[Configuration etc. to prevent vibrations and the like from being applied to FPD during offset data O read processing]
Next, a configuration for preventing vibration or the like from being applied to the FPD during the offset data O reading process will be described below with some configuration examples.

[Configuration example 1]
As described above, if an impact or vibration is applied to the FPD during the reading process of the offset data O, an artifact may appear in the read offset data O due to a microphonic phenomenon. Then, when the operation in this state of the above equation (2) will be components of artifacts in the offset data O to the true image data D ^* calculated remains and generated based on the true image data D ^* Artifacts appear in the diagnosis-provided medical image.

On the other hand, when an operator such as a radiologist operates the exposure switch 56 (see FIGS. 3 and 4) of the radiation generating device 55 to irradiate the subject and the FPD 1 with radiation, The display unit 58a and the display unit 71 of the mobile terminal 70 are viewed, and the process waits for the preview image p # pre to be displayed. The preview image p # pre is generated only when the preview image data Dp is transmitted from the FPD 1 to the console 58 after the image data D reading process (see FIG. 5). As described above, an operator such as a radiologist does not move the FPD 1 until at least the preview image p # pre is displayed. Therefore, unless the patient as a subject moves greatly, the image data D is read out. No vibration or the like is applied to the FPD 1 until the processing.

An operator such as a radiologist wipes the preview image p # pre on the display unit 58a of the console 58 (or the display unit 71 of the portable terminal 70; the same applies hereinafter) (see FIGS. 23A to 23C), or When the preview image p # pre whose rotation is corrected (see FIG. 24) is displayed, it is determined whether or not re-shooting is necessary. In preparation for the imaging, the operation of positioning the FPD 1 with respect to the body of the patient H (for example, see FIG. 4) as the subject is started. Also, even in the radiographing in the radiographing room R1 (see FIG. 3), when an operator such as a radiographer determines that re-imaging is unnecessary by looking at the preview image p # pre, the operator immediately proceeds to the next radiographing. The FPD 1 is pulled out from the Bucky device 51, and the FPD 1 is loaded into the Bucky device 51 used for the next shooting.

From the above situation, if the offset data O reading process (see FIG. 6) performed in the FPD 1 is completed before the preview image p # pre is displayed on the display unit 58a of the console 58, then As described above, an operator such as a radiologist performs positioning work of the FPD 1, pulls out the FPD 1 from the Bucky device 51, or loads it into the Bucky device 51 used for the next photographing, and vibrates the FPD 1. Etc., it is considered that no artifacts appear in the offset data O, and no artifacts appear in the diagnosis providing medical image p.

As described above, the time from the end of the image data D reading process (see FIGS. 5 and 28) to the end of the offset data O reading process (see FIGS. 6 and 29), that is, offset data. As shown in FIGS. 6 and 29, the time required for the O reading process is determined by the duration of the charge accumulation state, that is, the accumulation time τ. Therefore, for example, after the imaging, the FPD 1 keeps the charge accumulation state for a predetermined time, that is, accumulation so that an operator such as a radiographer does not move the FPD 1 while the FPD 1 performs the reading process of the offset data O. Depending on the time τ (see FIGS. 5, 6, 28, and 29), the preview image p # pre is displayed on the display unit 58 a of the console 58 (including the case where it is displayed on the display unit 71 of the portable terminal 70. It is possible to configure to change the content of the display process when displaying.

In particular, when the accumulation time τ is set to a long time, a timing when an operator such as a radiographer determines that re-imaging is unnecessary by looking at the preview image p # pre displayed on the display unit 58a of the console 58 By changing the content of the display process displayed on the display unit 58a of the console 58 so as to delay the operation, an operator such as a radiologist moves the FPD 1 while the FPD 1 is performing the reading process of the offset data O after imaging. It becomes possible not to be.

[How to change the contents of display processing 1]
For example, when the accumulation time τ is set to a short time such as 1 second, as described above, there is no possibility that the FPD 1 is moved by an operator such as a radiologist before the offset data O reading process is completed. In this case, in this case, the console 58 can display the preview image p # pre on the display unit 58a by the normal display processing procedure described in the normal processing procedure at the time of shooting or the like. is there. That is, the console 58 generates a preview image p # pre based on the preview image data Dp transmitted from the FPD 1, and as shown in FIG. 23A to FIG. 23C and FIG. The generated preview image p # pre is displayed in the normal display processing procedure by wiping or correcting the rotation.

In this way, even if the operator who viewed the preview image p # pre displays the preview image p # pre in the normal processing procedure and moves the FPD1 for the next photographing, the offset data is already stored in the FPD1. This is because since the O reading process has been completed, artifacts due to microphonic phenomena do not appear in the offset data O even if the FPD 1 is moved.

When the accumulation time τ is set to a long time such as 2 seconds or more, an operator such as a radiologist re-photographs by looking at the preview image p # pre displayed on the display unit 58a of the console 58. When the FPD 1 is determined to be unnecessary and the FPD 1 is moved, there is a possibility that the reading process of the offset data O has not yet been completed in the FPD 1. In this case, the operator re-photographs by looking at the preview image p # pre. It is necessary to change the content of the display process so as to delay the timing for determining that it is unnecessary. In order to realize this, for example, when the accumulation time τ is set to a long time such as 2 seconds or more, the console 58 changes the order in which the preview image p # pre is displayed on the display unit 58a. It is possible to configure.

Specifically, the console 58 does not perform the wipe display of the preview image p # pre as shown in FIGS. 23A to 23C, and during that time, for example, at the position of the icon I2, the original icon I2 shown in FIG. It can be configured to continue to display. Then, after a certain amount of time has elapsed, a preview image p # pre that has been rotationally corrected is displayed in the state shown in FIG. That is, the display on the display unit 58a of the console 58 suddenly switches to the state shown in FIG. 24 when a certain amount of time has elapsed from the state shown in FIG.

With this configuration, an operator such as a radiologist cannot see the preview image p # pre displayed in wipe, and the preview image displayed in the state shown in FIG. 24 after a certain amount of time has passed. Only when p # pre is seen, the necessity of re-shooting is judged. For this reason, the timing at which the operator views the preview image p # pre and determines that re-shooting is unnecessary is delayed, and the timing at which the FPD 1 is moved toward the next shooting is delayed. The reading process is completed.

[How to change the contents of display processing 2]
Further, in order to delay the timing at which an operator such as a radiologist views the preview image p # pre and determines that re-imaging is unnecessary, for example, the console 58 has a long accumulation time τ such as 2 seconds or more. When the time is set, the timing for starting the wipe display of the preview image p # pre may be changed.

In the normal processing procedure at the time of shooting or the like, the console 58 generates a preview image p # pre as needed based on the transmitted preview image data Dp every time the preview image data Dp is transmitted from the FPD 1. Each time the preview image p # pre is generated, the portion of the preview image p # pre to be displayed is increased, and the preview image p # pre is wiped and displayed. That is, in a normal processing procedure at the time of shooting or the like, transmission of the preview image data Dp from the FPD 1 to the console 58 and wipe display of the preview image p # pre on the display unit 58a of the console 58 are performed almost simultaneously. .

Then, in order to delay the timing at which an operator such as a radiologist views the preview image p # pre and determines that re-imaging is unnecessary, the preview image data Dp is transmitted from the FPD 1 to the console 58. The console 58 can be configured to display the preview image p # pre generated for that portion, instead of immediately displaying it on the display unit 58a, by delaying it by a predetermined timing. A time width for delaying the display of the preview image p # pre is set in the console 58 in advance.

With this configuration, the timing for starting the wipe display of the preview image p # pre on the display unit 58a of the console 58 is delayed, so that an operator such as a radiologist can delay the preview image p # displayed by the wipe display. Only after pre sees whether or not re-shooting is necessary. For this reason, the timing at which the operator views the preview image p # pre and determines that re-shooting is unnecessary is delayed, and the timing at which the FPD 1 is moved toward the next shooting is delayed. The reading process is completed.

Then, if the

method

1 or 2 for changing the contents of the display processing described above or a method combining the

methods

1 and 2 is adopted, the operator who has determined that re-photographing is unnecessary by looking at the preview image p # pre However, even if the FPD 1 is moved for the next shooting, since the offset data O reading process has already been completed, it is possible to accurately prevent the occurrence of artifacts due to the microphonic phenomenon in the offset data O. Become. Therefore, it is possible to prevent vibrations and the like from being applied to the FPD 1 during the offset data O reading process, and to prevent the offset data O to be read from including artifacts, so that the diagnostic providing medical image p is included. It becomes possible to accurately prevent the appearance of artifacts.

[How to change the contents of display processing 3]
In addition, the console 58 displays the preview image p # pre on the display unit 58a by wiping the preview image p # pre (see FIGS. 23A to 23C) or rotating the image according to the normal processing procedure at the time of shooting. (See FIG. 24), for example, until the FPD1 finishes reading the offset data O, the display unit 58a displays that the FPD1 is in the process of reading offset data. It is also possible to change the content of the display process displayed on the display unit 58a. In this case as well, it is possible to configure whether or not to perform the above display depending on whether the accumulation time τ is set to a short time or a long time.

Specifically, for example, when the accumulation time τ is set to a short time such as 1 second, as described above, the offset is set when the FPD 1 is moved toward the next imaging by an operator such as a radiologist. Since the reading process of the data O is completed, the console 58 does not need to display on the display unit 58a that the FPD 1 is in the process of reading the offset data as described above. Therefore, when the accumulation time τ is set to a short time, the console 58 does not display as described above.

On the other hand, when the accumulation time τ is set to a long time such as 2 seconds or more, an operator such as a radiologist re-photographs the preview image p # pre displayed on the display unit 58a of the console 58. When the FPD 1 is determined to be unnecessary and the FPD 1 is moved, there is a possibility that the FPD 1 has not yet finished reading the offset data O. Therefore, in this case, for example, the console 58 displays on the screen H4 shown in FIG. 24 on the wiped preview image p # pre or in the vicinity thereof or on the right side of the screen H4 for setting the shooting conditions. For example, as shown in FIG. 25, a prominent symbol indicating that the FPD 1 is in the process of reading offset data can be displayed on any part of the screen H4 such as the part Ia. Alternatively, on the screen H4, for example, a display such as “data is being read. Do not move the cassette” can be configured to be displayed in a manner that is easy for a radiographer or other operator to understand. is there. Further, when the operator is looking at another screen, it is also possible to configure the display as described above on the screen.

With this configuration, while the FPD 1 is reading the offset data O, the display as described above is performed on the display unit 58a of the console 58, so an operator such as a radiologist moves the FPD 1 This can be prevented. When the offset data O reading process is completed, the display as described above disappears from the display unit 58a. Therefore, after the offset data O reading process is completed, the operator performs FPD1 for the next shooting. Will move. Therefore, it is possible to prevent vibrations and the like from being applied to the FPD 1 during the offset data O reading process, and to prevent the offset data O to be read from including artifacts, so that the diagnostic providing medical image p is included. It becomes possible to accurately prevent the appearance of artifacts.

[Setting of accumulation time τ]
Next, how to set the accumulation time τ (that is, the duration of the charge accumulation state) will be described. As described above, for example, as illustrated in FIG. 6, the offset data O reading process is performed by repeating the same processing sequence as the processing sequence up to the image data D reading process illustrated in FIG. 5. Therefore, the accumulation time τ is set to the same time interval in the charge accumulation state before the image data D reading process (see FIG. 5) and the charge accumulation state before the offset data O reading process (see FIG. 6). Therefore, by setting the accumulation time τ (see FIG. 5) in the charge accumulation state before the reading process of the image data D, the accumulation time τ (see FIG. 6) in the charge accumulation state before the reading process of the offset data O is automatically performed. Reference) is set.

As described above, the accumulation time τ can be set, for example, by an operator such as a radiologist on the console 58 or automatically by the console 58. And the console 58 is comprised so that the content of the display process displayed on the display part 58a as mentioned above may be changed according to the set accumulation | storage time (tau). Note that the console 58 has a table (for example, see FIG. 26) instructing how to change the content of the display process displayed on the display unit 58a according to the set accumulation time τ. When the accumulation time τ is set, the display processing content displayed on the display unit 58a can be changed based on the table.

[Requirement 1 for setting accumulation time τ]
One of the factors that makes it necessary to set the accumulation time τ to be long is, for example, imaging in which the irradiation time of radiation from the radiation generation device 55 to the FPD 1 becomes long. In this case, the console 58 can recognize the irradiation time of radiation by referring to the irradiation time set in the radiation generator 55, for example. Therefore, for example, the console 58 performs the shooting corresponding to the icon I when the icon I corresponding to the next shooting to be performed (see FIG. 21) is focused on the screen H4 as described above. With reference to the irradiation time set in the radiation generator 55 (see display of each icon I in FIG. 21 such as “300 ms”), whether or not it is necessary to increase the accumulation time τ, and the accumulation time τ In the case of lengthening, it is possible to determine and set how long the length is.

[Requirement 2-1 for setting accumulation time τ]
As a second factor that makes it necessary to set the accumulation time τ to be long, for example, radiation irradiation characteristics of the radiation source 52 (see FIGS. 3 and 4) of the radiation generator 55 that irradiates the FPD 1 with radiation. be able to. That is, for example, when the radiation source 52 emits radiation, the dose rate of the irradiated radiation (that is, the dose per unit time) instantaneously rises to a prescribed dose rate, and at the end of irradiation In some cases, there is an irradiation characteristic such that the dose rate of the irradiated radiation falls instantaneously. When the next imaging is performed using the radiation source 52 having such radiation irradiation characteristics, the console 58 sets the accumulation time τ to be slightly longer than the radiation irradiation time set in the radiation generator 55. A long time can be set. Therefore, the accumulation time τ is generally a short time interval, and at least the accumulation time τ need not be set longer than necessary.

On the other hand, for example, when the radiation source 52 emits radiation, the dose rate of the irradiated radiation rises slowly, and it takes time to reach a prescribed dose rate. There may be an irradiation characteristic in which the dose rate of the irradiated radiation gradually falls and it takes time until the dose rate of the irradiated radiation is reduced to 0 or a predetermined dose rate. Accordingly, in order to effectively convert radiation image information without wasting radiation on the subject, it is necessary to set the accumulation time τ in consideration of the characteristics of the radiation source (that is, to set a relatively long accumulation time τ). Become.

In addition, one radiation source 52 is usually associated with one modality. That is, when the modality is the rounding wheel 60 (see FIG. 4), the rounding wheel 60 is normally equipped with one radiation source 52P. Even when the modality is the bucky device 51 (see FIG. 3), the bucky device 51 is usually associated with one radiation source 52A for irradiating the FPD 1 loaded therein with radiation. For example, in FIG. 3, by changing the irradiation direction of one radiation source 52A, it is possible to irradiate both the standing-up imaging device 51A and the standing-up imaging device 51B. Even in such a case, one radiation source 52A is associated with the standing-up imaging device 51A, and the same radiation source 52A is used. One radiation source 52A is also associated with the bucky device 51B for position photographing.

Thus, in many cases, one radiation source 52 is associated with one modality. Therefore, for example, the console 58 is configured to include a table or the like that associates “modality ID” that is identification information of each modality with the identification information of the radiation source 52, and the radiation irradiation characteristics of each radiation source 52. Accordingly, the accumulation time τ to be set is set in advance for each radiation source 52. When the console 58 focuses and displays the icon I (see FIG. 21) corresponding to the next shooting on the screen H4 as described above, the “58” of the shooting order corresponding to the icon I is displayed. With reference to the modality ID “P9” (see FIGS. 19 and 20), the radiation source 52 corresponding to the modality is specified based on the above table. Then, an accumulation time τ set in advance for the specified radiation source 52 is determined. Then, it is possible to transmit the calculated accumulation time τ to the FPD 1 or to change the content of the display process to be displayed on the display unit 58a based on the table as shown in FIG. In addition, you may comprise so that ID etc. of the radiation source 52 used by the said imaging | photography may be previously specified to imaging | photography order information. If comprised in this way, it will become possible for the console 58 to calculate the preset accumulation time τ for the radiation source 52 by referring to the ID of the radiation source 52 in the imaging order.

[Requirement 2-2 for setting accumulation time τ]
In this case, the radiation source 52 information can be notified from the FPD 1 to the console 58. That is, when the FPD 1 is brought into the radiographing room R1 (see FIG. 3) or mounted in the roundabout car 60 (see FIG. 4), the access point 53 of the radiographing room R1 or the roundabout car 60 (in FIG. 4). In order to be able to communicate with the access points 53 of the roundabout car 60, the SSIDs of these access points 53 are acquired. In many cases, the radiation room 52 is usually provided in the radiographing room R1 and the round-trip wheel 60.

Therefore, when the FPD 1 acquires the SSID of the access point 53 as described above, information such as identification information of the radiation source 52A installed in the imaging room R1 and the radiation source 52 provided in the round-the-wheel 60 In addition, it is configured so that it is also acquired. The acquired information such as the identification information of the radiation source 52 can be notified from the FPD 1 to the console 58. In this case, the console 58 calculates a preset accumulation time τ for the radiation source 52 based on the information of the radiation source 52 notified from the FPD 1. Then, it is possible to transmit the calculated accumulation time τ to the FPD 1 or change the content of the display process to be displayed on the display unit 58a based on the table as shown in FIG.

[Variation of setting requirement 2-2 for accumulation time τ]
In the case of [accumulation time τ setting requirement 2-2] described above, for example, when the FPD 1 acquires the SSID of the access point 53, the FPD 1 itself determines the radiation source 52 from the SSID of the access point 53. It is also possible to determine the identification information and set the accumulation time τ. In this case, the set accumulation time τ is notified from the FPD 1 to the console 58.

As described above, the control unit 22 of the FPD 1 performs the reading process of the offset data O by repeating the same processing sequence as the processing sequence from the reset process of each radiation detection element to the reading process of the image data D. If the content of the display process displayed on the display unit 58a is changed in accordance with a predetermined time during which the charge accumulation state is continued in the FPD 1, that is, the accumulation time τ, the preview image displayed on the display unit 58a of the console 58 is displayed. Even if an operator such as a radiologist who judges that re-imaging is unnecessary by looking at an image such as p # pre moves the FPD 1 for the next imaging, the FPD 1 has already finished reading the offset data O. Since it is in a state, artifacts due to microphonic phenomenon appear in the offset data O It becomes possible to accurately prevent.

Therefore, it is possible to prevent vibrations and the like from being applied to the FPD 1 during the offset data O reading process, and to prevent the offset data O to be read from including artifacts, so that the diagnostic providing medical image p is included. It becomes possible to accurately prevent the appearance of artifacts.

FIG. 3 shows a case where only one shooting room R1 is provided. However, for example, the above-described configuration can be applied to a case where a plurality of shooting rooms R1 are provided. . In this case, a different modality ID is assigned to each Buckie device 51 installed in each imaging room R1, and a radiation source 52 is provided for each imaging room R1. Therefore, for example, if the ID of the bucky device 51 is specified as the modality ID in the imaging order information, the radiation source 52 in the imaging room R1 in which the bucky device 51 is provided can be specified.

In this case, instead of specifying the modality ID in the imaging order information, it is possible to specify the identification information of the radiation source 52 of the radiation generator 55 used for imaging. Further, it is also possible to configure so that the identification information of the photographing room R1 used for photographing is designated by the photographing order information.

On the other hand, the same applies to each of the following configurations, but in the above configuration, the description has been made on the assumption that once the accumulation time τ is set, the accumulation time τ is not changed. However, even after the irradiation of radiation from the radiation generator 55 to the FPD 1 is completed, the irradiation time is completed by shortening the accumulation time τ rather than continuing the charge accumulation state until the set accumulation time τ elapses. When the image data D reading process is started immediately, the image data D reading process can be started earlier, and the offset data O reading process is also started earlier. Is possible. For example, as shown in FIG. 6, the offset data O reading process is performed by repeating the same processing sequence as the processing sequence up to the image data D reading process shown in FIG. 5. If the accumulation time τ in the reading process of the image data D is shortened, the accumulation time τ in the reading process of the offset data O can also be shortened.

Therefore, the time required for the offset data O reading process can be shortened, and the timing for starting the offset data O reading process can be advanced as described above. Therefore, it becomes possible to advance the timing at which the operator such as a radiologist can move the FPD 1 for the next imaging, and the operator can perform a series of imaging more quickly.

For example, if configured as follows, it is possible to configure to start reading processing of the image data D promptly when radiation irradiation to the FPD 1 is completed. That is, when the medical image system 50 for providing diagnosis is configured to perform imaging in the above-described synchronization method, for example, radiation that has fully pressed the button of the exposure switch 56 of the radiation generator 55 An operator such as an engineer (radiation is being irradiated in this state) gives a signal representing that the button of the exposure switch 56 has been fully pressed (in this state, radiation irradiation ends). The generation device 55 notifies the FPD 1. Then, when the control means 22 of the FPD 1 receives this signal, the processing content can be switched from the charge accumulation state (see FIG. 28) to the reading processing of the image data D.

In the subsequent offset data O reading process, it is necessary to repeat the same processing sequence as that until the image data D reading process. In this case, the control means 22 of the FPD 1 The count of the duration of the charge accumulation state is started at the time when the state of resetting each radiation detection element 7 is shifted to the charge accumulation state before the D reading process, and the time τreal when the charge accumulation state is actually continued is calculated. Configured to measure. In this case, the control means 22 of the FPD 1 does not measure the set accumulation time τ but the measured actual duration τreal in the charge accumulation state after the image data D readout process and before the offset data O readout process. Only after the charge accumulation state is continued, the offset data O is read out.

Further, in the case where the diagnosis providing medical image system 50 is configured to perform imaging by the asynchronous method described above, for example, as described above, the image data D is promptly obtained when the irradiation of the radiation to the FPD 1 is completed. In order to configure to start the reading process, it is necessary for the control means 22 of the FPD 1 to recognize that the irradiation of radiation from the radiation generating device 55 to the FPD 1 has been completed by some method. For this purpose, for example, a device capable of detecting that the button of the exposure switch 56 of the radiation generating device 55 is pressed or released is described, as described in JP 2010-104398 A. The exposure switch 56 can be externally attached, and the FPD 1 can be configured to receive a signal from the apparatus indicating that the operator has depressed the button of the exposure switch 56.

Further, as described in, for example, Patent Document 5 described above, if the read processing of the leak data dleak is performed in the charge accumulation state before the read processing of the image data D (see, for example, FIG. 5), The value of leak data dleak read out at the time when irradiation ends is decreased. Therefore, by using this phenomenon, the FPD 1 is configured to read out the leak data dleak while the charge accumulation state is continued. For example, when the read out leak data dleak becomes less than a set threshold value, radiation is emitted. It is also possible to configure so as to detect the end of irradiation.

In addition, it can be configured to detect the end of radiation irradiation when the output value from the X-ray sensor has decreased, and can be configured to detect the end of radiation irradiation by various methods. Is possible.

By the way, in the above configuration, it has been described that the content of the display process displayed on the display unit 58a of the console 58 is changed according to the length of the accumulation time τ that is the duration of the charge accumulation state in the FPD 1. With this configuration, when the accumulation time τ is long, the content of the display process is changed so that an operator such as a radiographer delays the timing for moving the FPD 1 for the next imaging. The FPD 1 is prevented from being subjected to vibration while the offset data O is being read out (including the charge storage state immediately before, and the same applies hereinafter), and the offset data O to be read is free from artifacts. .

However, if the operator such as a radiologist does not move the FPD 1 while the FPD 1 is performing the offset data O reading process (including the charge accumulation state immediately before), for example, The FPD 1 transmits a completion signal to the console 58 when the reading process of the offset data O is completed, and the console 58 displays the preview image p # pre and the like on the display unit 58 a for the first time when the completion signal is received from the FPD 1. It is possible to make it constitute.

In this case, until the console 58 receives a completion signal from the FPD 1, an operator such as a radiographer such as the preview image p # pre determines whether or not re-imaging is necessary on the display unit 58 a. The possible images are not displayed. Note that, for example, on the display unit 58a, the FPD 1 is in the process of reading the offset data as shown in FIG. 25 until the preview image p # pre is displayed on the display unit 58a after the completion signal is received. It can be configured to display a symbol indicating that it is, or to display a wording such as “Data is being read. Do not move the cassette”.

With this configuration, the preview image p # pre or the like is not displayed on the display unit 58a of the console 58 until the FPD 1 completes the reading process of the offset data O. The necessity of re-shooting cannot be determined. Then, since there is a possibility that re-photographing is necessary, the operator does not move the FPD 1. Therefore, it is possible to accurately prevent an operator such as a radiologist from moving the FPD 1 while the FPD 1 is performing the offset data O reading process.

On the other hand, each of the above configurations has been described on the premise that the offset data O is read out by the FPD 1 after imaging (that is, after irradiation of radiation). However, the offset data O can be read out before photographing. In this case, the offset data O can be read at various timings as to which timing before imaging is performed by irradiating the FPD 1 with radiation.

For example, the offset data O can be read out at the timing in each of the above-described configurations, that is, the timing immediately after the reading processing of the image data D is completed. In this case, however, in each of the above-described configurations, as shown in FIG. 27A, the reading process of the image data D and the reading process of the offset data O immediately after that relate to the same shooting (see “ D1 ”and“ O1 ”,“ D2 ”and“ O2 ”), and when the offset data O is read before shooting as described above, as shown in FIG. 27B, the image data D The read processing of the offset data O performed immediately after the read processing is performed is the read processing of reading the offset data O for the next shooting performed thereafter (“D1” and “D” in FIG. 27B). O2 "). In FIG. 27A and FIG. 27B, “D” represents the reading process of the image data D, “O” represents the reading process of the offset data O, and “1” and “2” represent the first and second imaging, respectively. Represents that

In this case, the reading process of the offset data O is not the reading process of the image data D performed immediately before, but the reading process of the image data D in the next photographing performed after the reading process of the offset data O. It is comprised so that it may be performed by the process sequence of. Therefore, the accumulation time τ in the offset data O readout process in this case is set to the same time as the accumulation time τ in the subsequent readout process of the image data D in the next shooting.

In this respect, the present configuration is different from the above-described configurations, but other points can be configured in the same manner as the above-described configurations. That is, the content of the display process displayed on the display unit 58a of the console 58 is changed according to the accumulation time τ in the next reading process of the offset data O for photographing, or the FPD 1 performs the offset data O reading process. When the completion is completed, a completion signal is transmitted to the console 58. The console 58 does not display the preview image p # pre or the like on the display unit 58a until the completion signal is received from the FPD1, and the completion signal is received from the FPD1. The preview image p # pre or the like can be displayed on the display unit 58a for the first time when it is received.

With this configuration, it is possible to accurately prevent vibrations and the like from being applied to the FPD 1 during the offset data O reading process, and to prevent the offset data O being read from including artifacts. It is possible to accurately prevent an artifact from appearing in the medical image p.

In addition, the offset data O read processing performed before imaging is performed by, for example, the first operation (that is, half-pressing) and the second operation (ie, half-pressing) on the exposure switch 56 of the radiation generating device 55 by an operator such as the above-described radiographer. In other words, it can be configured to be performed during the full press). That is, in this case, when the medical image system 50 for providing diagnosis is configured to perform imaging in the synchronous method described above, for example, when the first operation is performed on the exposure switch 56. The radiation generator 55 is configured to transmit a signal indicating that the first operation on the exposure switch 56 has been performed to the FPD 1.

Further, when the diagnosis providing medical image system 50 is configured to perform imaging in, for example, the asynchronous method described above, for example, it is detected that the button of the exposure switch 56 described above has been pressed. When the first operation is performed on the exposure switch 56, the apparatus that has detected that the first operation has been performed is connected to the console 58. A signal indicating that the first operation on the exposure switch 56 has been performed is transmitted from the console 58 that has received the signal to the FPD 1.

When the control means 22 of the FPD 1 receives the above signal when the first stage operation is performed on the exposure switch 56, as described above, after performing reset processing of each radiation detection element, the charge accumulation state Is continued for a predetermined time, that is, the accumulation time τ, and then the offset data O is read (see FIG. 6 and FIG. 29). Then, the same processing sequence is repeated again to reset each radiation detection element 7 and then shift to the charge accumulation state. Then, while the FPD 1 continues in the charge accumulation state, a second operation is performed on the exposure switch 56 by an operator such as a radiologist, and the FPD 1 is irradiated with radiation through the subject. The FPD 1 is configured to perform the reading process of the image data D after continuing the charge accumulation state for the accumulation time τ.

With this configuration, it is possible to read the offset data O while an operator such as a radiologist operates the exposure switch 56 of the radiation generator 55. Further, since an operator such as a radiologist does not move the FPD 1 while operating the exposure switch 56 in this way, the FPD 1 vibrates during the reading process of the offset data O performed during that time. It becomes possible to prevent the addition of etc. accurately.

In this case, when the medical image system 50 for providing diagnosis is configured to perform imaging in the synchronous method described above, for example, during the process of reading the offset data O by the FPD 1, for example. Even if the second operation is performed on the exposure switch 56, radiation is not irradiated from the radiation source 52 unless an interlock release signal is transmitted from the FPD 1 to the radiation generator 55 as described above. For this reason, the FPD 1 is configured to transmit an interlock release signal from the FPD 1 to the radiation generator 55 when the offset data O reading process is completed, so that the FPD 1 can perform the offset data O reading process. It is possible to accurately prevent the radiation from being irradiated.

On the other hand, when the medical image system 50 for providing diagnosis is configured to perform imaging by the asynchronous method described above, for example, the radiation generator 55 is not interlocked, so that the offset data O is read by the FPD 1. There is a possibility that the FPD 1 is irradiated with radiation by performing a second operation on the exposure switch 56 during the processing.

Therefore, when the diagnosis providing medical image system 50 is configured to perform imaging in an asynchronous manner, when configured as described above, for example, an operator such as a radiologist is exposed to the radiation generator 55. When the first operation is performed on the shooting switch 56 and a signal indicating that is transmitted from the device that has detected that the first operation has been performed to the console 58, the console 58 At the same time as transmitting a signal to the FPD 1, it may be configured to alert an operator such as a radiographer not to perform the second operation on the exposure switch 56 by uttering sound or playing music. Is possible.

At the time of receiving a signal indicating that the offset data O reading process has been completed from the FPD 1, the console 58 stops voice utterance and music playback. Then, an operator such as a radiologist confirms that the voice utterance has been stopped and performs the second operation on the exposure switch 56 of the radiation generator 55. At the same time as the voice utterance or the like, it is possible to display on the display unit 58a of the console 58 a content for calling attention so as not to perform the second operation on the exposure switch 56.

With this configuration, an operator such as a radiologist does not move the FPD 1 while operating the exposure switch 56. For this reason, it is possible to accurately prevent the FPD 1 from being vibrated during the process of reading the offset data O by performing the process of reading the offset data O during that time.

Therefore, if the diagnosis providing medical image system 50 is configured as described above, it is possible to accurately prevent vibrations and the like from being applied to the FPD 1 during the reading process of the offset data O, and the offset data O to be read does not include artifacts. As a result, it is possible to accurately prevent an artifact from appearing in the medical image p for providing diagnosis.

For example, when the operator such as a radiographer is a chief engineer or the like and is a high-level radiographer who understands the characteristics and system configuration of the FPD 1, for example, the accumulation time τ is long. It is understood that the FPD 1 is not moved immediately, but the preview image p # pre may want to be confirmed early. In such a case, even if the accumulation time τ is long, the content of the display process for displaying the preview image p # pre on the display unit 58a of the console 58 is not changed, that is, according to the present invention. It is configured so that the preview image p # pre can be displayed as usual (ie, as shown in FIGS. 23A to 23C, FIG. 24, etc.) by performing a cancel process so as not to change the contents of the display process. It is also possible to do.

That is, in this case, when the preview image data Dp is transmitted from the FPD 1, the preview image p # pre is wiped and displayed at the same time as usual, and the preview image p # pre is quickly displayed. In this case, for example, an operator who can perform the canceling process is designated in advance according to the level of the skill, and the console 58 performs the canceling process based on the input operator ID of the operator, for example. It is also possible to configure so that the cancel process is accepted only when the operator is permitted to perform the operation.

It may be used in the field of radiographic imaging (especially in the medical field).

1 FPD (radiological imaging equipment)
5 Scanning line 6 Signal line 7 Radiation detection element 8 TFT (switch element)
DESCRIPTION OF SYMBOLS 15 Scan drive means 17 Read-out circuit 22 Control means 50 Medical image system 52 for diagnosis provision Radiation source 55 Radiation generator 56 Exposure switch 58 Console (console, alerting | reporting apparatus)
58a Display unit D Image data D ^* True image data Dp Preview image data (extracted image data)
H Patient (subject)
O Offset data p # pre Preview image (image)
t Elapsed time WT Wait time τ Accumulation time (predetermined time)

Claims

A plurality of scanning lines and a plurality of signal lines;
A plurality of radiation detection elements arranged two-dimensionally;
Scanning drive means for switching a voltage applied to each scanning line between an on-voltage and an off-voltage,
A switch element connected to each of the scanning lines, and discharging a charge accumulated in the radiation detection element to the signal line when an on-voltage is applied;
A readout circuit for reading out the electric charge emitted to the signal line as image data;
Control means for controlling at least the scanning drive means and the readout circuit to perform the readout processing of the image data;
A radiographic imaging device comprising:
A radiation generator for irradiating the radiation imaging apparatus with radiation through a subject; and
A notification device;
With
The radiographic image capturing apparatus supplies an imaging mode, an awakening mode capable of performing imaging by supplying power to each functional unit including at least the control unit, and supplying power only to necessary functional units to perform imaging. Is configured to be able to transition between sleep modes that cannot be performed,
The control means of the radiographic image capturing apparatus includes:
At the time of imaging, after performing reset processing of each radiation detection element, the scanning drive means applies an off voltage to each scanning line, and the switch element is turned off by irradiation of radiation. The charge accumulation state in which charges generated in each radiation detection element are accumulated in each radiation detection element is continued for a set accumulation time, and then at least the scanning drive unit and the readout circuit are controlled to Have the image data read out,
Read offset data to read offset data instead of the image data by repeating the same processing sequence as the processing sequence from the reset processing of each radiation detection element to the reading processing of the image data in a state where no radiation is irradiated after imaging. As well as processing
Counting the elapsed time since the shooting mode is changed from the sleep mode to the wake-up mode, and when the elapsed time has elapsed by a waiting time, a signal is sent to the notification device,
The notification device is configured to notify that it is possible to perform imaging by irradiating radiation from the radiation generation device when receiving the signal from the radiographic imaging device,
The medical image system for diagnosis provision, wherein the waiting time is switched according to the accumulation time.
The control means of the radiographic image capturing apparatus may be configured such that, in the second and subsequent imaging performed following the first imaging after the imaging mode is changed from the sleep mode to the awakening mode, the imaging mode is the sleep mode. If the elapsed time from the transition to the awakening mode is not the waiting time switched according to the accumulation time in the second and subsequent shootings, the waiting time in the second and subsequent shootings 2. The medical image system for providing diagnosis according to claim 1, wherein a signal is transmitted to the notification device at the time when elapses.
A display unit, a console that generates an image based on at least the extracted image data transmitted from the radiographic imaging device and displays the image on the display unit;
The said console changes the content of the display process displayed on the said display part according to the said accumulation time which continues the said electric charge accumulation state in the said radiographic imaging apparatus, The Claim 1 or Claim 2 characterized by the above-mentioned. The medical image system for providing diagnosis as described.
4. The diagnosis provision according to claim 3, wherein the console changes an order in which the image is displayed on the display unit according to the accumulation time during which the charge accumulation state is continued in the radiographic imaging device. Medical imaging system.
The said console changes the timing which displays the said image on the said display part according to the said accumulation time which continues the said charge accumulation state in the said radiographic imaging apparatus. Medical imaging system for providing diagnosis.
Whether the console displays on the display unit that the radiographic image capturing apparatus is in the process of reading offset data, according to the accumulation time during which the charge accumulation state is continued in the radiographic image capturing apparatus. 6. The medical image system for providing diagnosis according to any one of claims 3 to 5, characterized in that:
A display unit, a console that generates an image based on at least the extracted image data transmitted from the radiographic imaging device and displays the image on the display unit;
The control means of the radiographic imaging device is configured to transmit a completion signal to the console when the offset data reading process is completed,
5. The diagnosis providing device according to claim 1, wherein the console displays the image on the display unit when the completion signal is received from the radiographic imaging device. 6. Medical imaging system.
A display unit, a console that generates an image based on at least the extracted image data transmitted from the radiographic imaging device and displays the image on the display unit;
The radiation generation apparatus includes a radiation source that irradiates the radiation imaging apparatus with radiation through a subject, and an exposure switch that instructs the start of radiation irradiation. Is activated, the radiation source is activated, and the radiation switch is configured to emit radiation when a second stage operation is performed on the exposure switch,
The control means of the radiographic image capturing apparatus includes:
When the first stage operation is performed on the exposure switch of the radiation generating device, the radiation detection elements are reset, and the off-voltage is applied to the scanning lines from the scanning driving unit in a state where no radiation is irradiated. The charge accumulation state in which charges are accumulated in each radiation detection element is continued for the accumulation time in a state where the switch element is in an OFF state by applying N, and then at least the scanning drive means and the readout circuit are controlled. To perform the offset data read process,
The same processing sequence as the processing sequence from the reset processing of each radiation detection element to the readout processing of the offset data through the charge accumulation state is repeated, and the exposure of the radiation generating device is performed during the charge accumulation state. After accumulating charges generated in each radiation detection element by being operated from the radiation source of the radiation generation device by performing a second stage operation on the switch, at least the 5. The image data reading process for reading the image data instead of the offset data by controlling a scanning drive unit and the reading circuit is performed. The medical image system for diagnosis provision according to any one of the above.
The control means of the radiographic imaging apparatus performs a process of calculating true image data by subtracting the offset data from the image data for each of the radiation detection elements after completion of the offset data reading process, The medical image system for providing diagnosis according to any one of claims 3 to 8, wherein the calculated true image data is transmitted to the console.
A plurality of scanning lines and a plurality of signal lines;
A plurality of radiation detection elements arranged two-dimensionally;
Scanning drive means for switching a voltage applied to each scanning line between an on-voltage and an off-voltage,
A switch element connected to each of the scanning lines, and discharging a charge accumulated in the radiation detection element to the signal line when an on-voltage is applied;
A readout circuit for reading out the electric charge emitted to the signal line as image data;
Control means for controlling at least the scanning drive means and the readout circuit to perform readout processing of the image data, extracting predetermined image data from the read image data, and transmitting the image data to a console;
A radiographic imaging device comprising:
A radiation generator for irradiating the radiation imaging apparatus with radiation through a subject; and
A console that includes a display unit, generates an image based on at least the extracted image data transmitted from the radiographic imaging device, and displays the image on the display unit;
With
The control means of the radiographic image capturing apparatus includes:
At the time of imaging, after performing reset processing of each radiation detection element, the scanning drive means applies an off voltage to each scanning line, and the switch element is turned off by irradiation of radiation. The charge accumulation state in which the charges generated in each radiation detection element are accumulated in each radiation detection element is continued for a predetermined time, and thereafter, at least the scanning drive unit and the readout circuit are controlled to read out the image data. Let the process do
An offset for reading offset data instead of the image data by repeating the same processing sequence as the processing sequence from the reset processing of each radiation detection element to the reading processing of the image data in a state where radiation is not irradiated before or after imaging. It is configured to perform data read processing,
The diagnostic providing medical image system, wherein the console changes a content of display processing displayed on the display unit according to the predetermined time during which the charge accumulation state is continued in the radiographic imaging apparatus.
A plurality of scanning lines and a plurality of signal lines;
A plurality of radiation detection elements arranged two-dimensionally;
Scanning drive means for switching a voltage applied to each scanning line between an on-voltage and an off-voltage,
A switch element connected to each of the scanning lines, and discharging a charge accumulated in the radiation detection element to the signal line when an on-voltage is applied;
A readout circuit for reading out the electric charge emitted to the signal line as image data;
Control means for controlling at least the scanning drive means and the readout circuit to perform the readout processing of the image data;
A bias power supply for applying a reverse bias voltage to the radiation detection element via a bias line;
With
The shooting mode includes at least an awakening mode in which power can be supplied to each function unit including the control means and a sleep mode in which power is supplied only to the necessary function unit and shooting cannot be performed. And can be transitioned between and
The radiographic imaging apparatus characterized in that the control means applies a reverse bias voltage from the bias power source to each of the radiation detection elements when the imaging mode is the sleep mode.
The control means applies a reverse bias voltage from the bias power source to each radiation detection element for a predetermined time at predetermined time intervals when the imaging mode is the sleep mode. The radiographic imaging apparatus according to claim 11.
The radiographic imaging apparatus according to claim 11, wherein the control unit continuously applies a reverse bias voltage from the bias power source to the radiation detection elements while the imaging mode is the sleep mode. .
When the imaging mode is the sleep mode, the control means increases the voltage applied to each radiation detection element from the bias power source and reaches the set threshold value from the bias power source. The radiographic imaging apparatus according to claim 11, wherein a reverse bias voltage having a predetermined voltage value is applied to each radiation detection element for a predetermined time.