JP2012047507A - Radiation image photographing device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To reduce the size and weight of a device, while making it possible to photograph a radiation still image and a radiation moving image.SOLUTION: A radiation image photographing device 1 includes a housing 2 having a radiation incident surface R and a detection part P which is stored in the housing and has a plurality of radiation detection elements two-dimensionally arranged. In the radiation image photographing device 1, a module for a still image 40 having a functional part suitable for photographing a still image and a module for a moving image 50 having a functional part suitable for photographing a moving image can be attached and detached to and from the housing and only one of the modules can be connected by replacement.

Description

  The present invention relates to a radiographic image capturing apparatus capable of capturing radiographic images of still images and moving images as necessary.

  2. Description of the Related Art Conventionally, as a means for acquiring a medical radiation image, a radiation image forming apparatus in which radiation detection elements called a so-called flat panel detector (FPD) are two-dimensionally arranged is known. In such a radiation image forming apparatus, radiation energy is directly converted into charges using a photoconductive substance as a radiation detection element, and the charges are converted into pixels by a switch element for signal readout arranged two-dimensionally. What is read as an electrical signal is known. The FPD is easy to carry because of its thinness, and there are no restrictions on the arrangement and orientation during use compared to the stationary type, and it is possible to perform a variety of shootings.

By the way, as described above, the FPD can take various images. However, in recent years, there has been an increasing demand for capturing radiographic images by moving images. If necessary, radiographic images for still images and moving images can be obtained. A radiographic imaging apparatus capable of performing the above imaging has been developed.
This conventional radiographic image capturing apparatus is capable of capturing a radiographic image by a still image in the basic configuration, and further enabling moving image capturing by additionally providing an additional function module (for example, Patent Documents). 1).

JP 2008-083031 A

However, the conventional radiographic image capturing apparatus has a configuration for still image capturing as a basic configuration, and additionally includes an additional function module for capturing moving images. There is also a problem that the apparatus is increased in size and weight.
On the other hand, in order to reduce the size and weight, it may be possible to use a small device for each component of the device, but when shooting a movie, the processing speed, the amount of data transmission, the increase in power consumption, etc. There are various problems, and there is a problem that the performance required for moving image shooting cannot be maintained with a small configuration.
In addition, when a method for additionally installing a moving image additional function module is used with a configuration for still image shooting as a basic configuration, at least a part of the configuration for still images is not used. There has been a problem that an unnecessary configuration may occur at the time of shooting.

  An object of the present invention is to provide a radiographic image capturing apparatus that can capture a moving image and a still image as required, and can be reduced in size and weight.

In order to solve the above-described problem, the radiographic imaging device of the present invention includes:
A housing having a radiation incident surface;
In a radiographic imaging apparatus comprising: a detection unit including a plurality of radiation detection elements housed in the housing and arranged two-dimensionally;
A still image module having a function unit suitable for still image shooting and a moving image module having a function unit suitable for moving image shooting can be attached to and detached from the housing, and only one of them can be replaced by replacement. It can be mounted.

In the above-described invention, the radiographic image capturing device can selectively mount the still image module and the moving image module on the housing, and these modules can be exchanged and connected. It is possible to select and capture a radiographic image of a moving image.
Since only one of the still image module and the moving image module is selectively mounted, the camera has a configuration suitable for still image shooting when shooting a still image. In this case, since the configuration suitable for moving image shooting is achieved, the radiographic image capturing apparatus can avoid the installation of a configuration in which still image capturing and moving image capturing overlap, and the size and weight of the apparatus can be reduced. Can be achieved.
Note that the moving image module is more suitable for moving image shooting, but its configuration is generally capable of shooting still images, and does not distribute still image shooting when the moving image module is installed.

1 is an external perspective view of a radiographic image capturing apparatus according to an embodiment of the invention. It is a block block diagram of the radiographic imaging apparatus equipped with the still image module. It is a block block diagram of the radiographic imaging apparatus equipped with the moving image module. It is sectional drawing which follows the XX line of FIG. It is a top view which shows the structure of the board | substrate surface with which a radiographic imaging apparatus is provided. It is an enlarged view which shows the structure of the photoelectric conversion element, thin film transistor, etc. which were formed in the small area | region on the board | substrate of FIG. It is a figure explaining the board | substrate with which COF, a PCB board | substrate, etc. were attached. FIG. 8A is a diagram illustrating a mounting state of the COF on which the gate IC is mounted, and FIG. 8B is a diagram illustrating a mounting state of the COF on which the reading IC is mounted. It is a block diagram showing the equivalent circuit of the radiographic imaging apparatus in the mounting state of the still image module. It is a block diagram showing the equivalent circuit of the radiographic imaging apparatus in the mounting state of the moving image module. It is a block diagram showing the equivalent circuit about 1 pixel which comprises the detection part in the mounting state of the module for still images. It is a block diagram showing the equivalent circuit about 1 pixel which comprises the detection part in the mounting state of the module for moving images. It is a block diagram which shows the system configuration | structure of a radiographic imaging system.

  Hereinafter, an embodiment of a radiographic imaging apparatus 1 according to the present invention will be described with reference to the drawings.

  In the following description, the radiographic image capturing apparatus 1 is a so-called indirect radiographic image capturing apparatus that includes a scintillator or the like and converts irradiated radiation into electromagnetic waves of other wavelengths such as visible light to obtain electric signals. Although a case will be described, the present invention can also be applied to a direct type radiographic imaging apparatus. Moreover, although the case where the radiographic imaging device 1 is a portable type is demonstrated, it is possible to apply also to the radiographic imaging device integrally formed with the support stand etc.

  FIG. 1 is an external perspective view of a radiographic image capturing apparatus according to the present embodiment, FIG. 2 is a block configuration diagram in a state where a still image module 40 described later is mounted, and FIG. 3 is mounted a moving image module 50 described later. FIG. 4 is a cross-sectional view taken along line XX in FIG. 1.

(Schematic configuration of radiographic imaging device)
The radiographic imaging apparatus 1 includes a housing 2 having a radiation incident surface R and a substrate on which a detection unit P including a plurality of radiation detection elements 7 housed in the housing 2 and arranged two-dimensionally is formed. 4, a still image module 40 having a function unit suitable for still image shooting, and a moving image module 50 having a function unit suitable for moving image shooting, and the still image module 40 and the moving image module 50. Can be mounted alternatively to the mounting portion 2C of the housing 2.

  The casing 2 has a substantially rectangular shape in plan view, and the upper surface thereof is a radiation incident surface R. A rectangular recess is formed at one corner of the lower surface, and the recess is a still image module 40 or This is the mounting portion 2C of the moving image module 50. The mounting portion 2C is provided with a latch mechanism (not shown) for mounting and holding the still image module 40 or the moving image module 50. The crimp-type first and second connectors 26, 26 shown in FIGS. 27, the still image module 40 or the moving image module 50 is held so as to be in pressure contact therewith. In addition, this latch mechanism can attach or detach the still image module 40 or the moving image module 50 with respect to the mounting portion 2C by manual operation.

As illustrated in FIG. 2, the still image module 40 performs radiographic image capturing control of a still image on the rectangular module housing 41 sized to fit into the mounting portion 2 </ b> C and the entire radiographic image capturing apparatus 1. In order to control the control board 42 as a still picture control section to be performed, the still picture power supply board 44 that supplies power to each part of the radiographic imaging apparatus 1 using the battery 43 as a power storage unit as a power source, and the detection section P The first module connector 45 connected to the first connector 26 described above and the second module connector 46 connected to the second connector 27 described above for receiving the detection output from the detection unit P. And connection boards 45A and 46A for holding the first module side connector 45 and the second module side connector 46, respectively, and still image captured image data via the antenna 47A. A wireless module 47 as a wireless communication unit for wirelessly output section, supplying power from a not-shown charging unit to the battery 41 and a connection terminal 48 at the time of charging the battery 41.
The control board 42, the battery 43, the still image power supply board 44, and the wireless module 47 have a configuration corresponding to a functional unit suitable for taking a still image.

As shown in FIG. 3, the moving image module 50 has a rectangular module housing 51 sized to fit in the mounting portion 2 </ b> C, and a moving image that performs shooting control of moving image radiographic images on the entire radiographic image capturing apparatus 1. A control board 52 as a control unit, a moving image processing unit 53 that performs image processing on image data obtained by imaging control, and a power cable 54A from the outside to supply power to each unit of the radiographic image capturing apparatus 1 In order to receive the detection output from the moving image power supply board 54 for supplying power, the first module-side connector 55 connected to the first connector 26 described above for controlling the detection portion P, and the detection portion P. The second module side connector 56 connected to the second connector 27, the first module side connector 55, and the second module side connector 56 are respectively connected to hold the second module side connector 56. High-speed communication processing unit 57 as a wired communication unit that outputs captured image data of moving images to the outside via communication cable 57A, and second A / D that digitizes analog output from detection unit P And a high-speed A / D converter 58 as a D converter.
The control board 52, the moving image processing unit 53, the moving image power supply board 54, the high-speed communication processing unit 57, and the high-speed A / D converter 58 have a configuration corresponding to a functional unit suitable for moving image shooting.

Next, each part will be described in detail.
The housing 2 is formed of a material such as a carbon plate or plastic that at least the radiation incident surface R transmits radiation. 1 and 4 show a case in which the casing 2 is a so-called lunch box type formed by a frame plate 2A and a back plate 2B. However, the casing 2 is integrally formed in a rectangular tube shape. It is also possible to use a so-called monocoque type.

As shown in FIG. 4, a base 31 is arranged inside the housing 2 via a lead thin plate (not shown) on the lower side of the substrate 4. A gate IC connection substrate 32 and a readout IC connection substrate 33 (see FIG. 8B) are attached. In the present embodiment, a glass substrate 35 for protecting the substrate 4 and the radiation incident surface R of the scintillator 3 is disposed.
The still image module 40 or the moving image module 50 is disposed below the substrate 4 in the mounted state.

  The scintillator 3 is attached to a detection unit P, which will be described later, of the substrate 4. As the scintillator 3, for example, a scintillator 3 that has a phosphor as a main component and converts it into an electromagnetic wave having a wavelength of 300 to 800 nm, that is, an electromagnetic wave centered on visible light when it receives incident radiation, is used.

  In the present embodiment, the substrate 4 is formed of a glass substrate. As shown in FIG. 5, a plurality of scanning lines 5 and a plurality of signal lines are provided on a surface 4 a of the substrate 4 facing the scintillator 3. 6 are arranged so as to cross each other. In each small region r defined by the plurality of scanning lines 5 and the plurality of signal lines 6 on the surface 4 a of the substrate 4, radiation detection elements 7 are respectively provided.

  Thus, the entire region r in which the plurality of radiation detection elements 7 arranged in a two-dimensional manner are provided in each small region r partitioned by the scanning line 5 and the signal line 6, that is, shown by a one-dot chain line in FIG. The region is a detection unit P.

  In the present embodiment, a photodiode is used as the radiation detection element 7, but other than this, for example, a phototransistor or the like can also be used. Each radiation detection element 7 is connected to a source electrode 8s of a TFT 8 as a switch element, as shown in the enlarged views of FIGS. The drain electrode 8 d of the TFT 8 is connected to the signal line 6.

  The TFT 8 is turned on when a turn-on voltage is applied to the connected scanning line 5 by the scanning drive means 15 described later and applied to the gate electrode 8g, and is generated and accumulated in the radiation detection element 7. The charged electric charge is discharged to the signal line 6. Further, the TFT 8 is turned off when the off voltage is applied to the connected scanning line 5 and the off voltage is applied to the gate electrode 8g, and the emission of the charge from the radiation detecting element 7 to the signal line 6 is stopped. The charges generated in the radiation detection element 7 are held and accumulated in the radiation detection element 7.

  Here, the structure of the radiation detection element 7 and the TFT 8 in this embodiment will be briefly described with reference to a cross-sectional view shown in FIG. 7 is a cross-sectional view taken along line YY in FIG.

A gate electrode 8g of a TFT 8 made of Al, Cr or the like is formed on the surface 4a of the substrate 4 so as to be integrally laminated with the scanning line 5, and silicon nitride (laminated on the gate electrode 8g and the surface 4a). The first electrode 74 of the radiation detecting element 7 is connected to the upper portion of the gate electrode 8g on the gate insulating layer 81 made of SiN _x ) or the like via the semiconductor layer 82 made of hydrogenated amorphous silicon (a-Si) or the like. The formed source electrode 8s and the drain electrode 8d formed integrally with the signal line 6 are laminated.

The source electrode 8s and the drain electrode 8d are divided by a first passivation layer 83 made of silicon nitride (SiN _x ) or the like, and the first passivation layer 83 covers both the electrodes 8s and 8d from above. In addition, ohmic contact layers 84a and 84b formed in an n-type by doping hydrogenated amorphous silicon with a group VI element are laminated between the semiconductor layer 82 and the source electrode 8s and the drain electrode 8d, respectively. The TFT 8 is formed as described above.

  In the radiation detecting element 7, an auxiliary electrode 72 is formed by laminating Al, Cr, or the like on the insulating layer 71 formed integrally with the gate insulating layer 81 on the surface 4 a of the substrate 4. A first electrode 74 made of Al, Cr, Mo or the like is laminated on the auxiliary electrode 72 with an insulating layer 73 formed integrally with the first passivation layer 83 interposed therebetween. The first electrode 74 is connected to the source electrode 8 s of the TFT 8 through the hole H formed in the first passivation layer 83.

  On the first electrode 74, an n layer 75 formed in an n-type by doping a hydrogenated amorphous silicon with a group VI element, an i layer 76 which is a conversion layer formed of hydrogenated amorphous silicon, and a hydrogenated amorphous A p layer 77 formed by doping a group III element into silicon and forming a p-type layer is formed by laminating sequentially from below.

  When radiation enters from the radiation incident surface R of the housing 2 of the radiographic imaging apparatus 1 and is converted into an electromagnetic wave such as visible light by the scintillator 3, and the converted electromagnetic wave is irradiated from above in the figure, the electromagnetic wave is detected by radiation. The electron hole pair is generated in the i layer 76 by reaching the i layer 76 of the element 7. In this way, the radiation detection element 7 converts the electromagnetic waves irradiated from the scintillator 3 into electric charges.

  On the p layer 77, a second electrode 78 made of a transparent electrode such as ITO is laminated and formed so that the irradiated electromagnetic wave reaches the i layer 76 and the like. In the present embodiment, the radiation detection element 7 is formed as described above. The order of stacking the p layer 77, the i layer 76, and the n layer 75 may be reversed. Further, in the present embodiment, a case where a so-called pin-type radiation detection element formed by sequentially stacking the p layer 77, the i layer 76, and the n layer 75 as described above is used as the radiation detection element 7. However, it is not limited to this.

A bias line 9 for applying a bias voltage to the radiation detection element 7 is connected to the upper surface of the second electrode 78 of the radiation detection element 7 via the second electrode 78. The second electrode 78 and the bias line 9 of the radiation detection element 7, the first electrode 74 extended to the TFT 8 side, the first passivation layer 83 of the TFT 8, that is, the upper surfaces of the radiation detection element 7 and the TFT 8 are A second passivation layer 79 made of silicon nitride (SiN _x ) or the like is covered from above.

  As shown in FIGS. 5 and 6, in the present embodiment, one bias line 9 is connected to a plurality of radiation detection elements 7 arranged in rows, and each bias line 9 is connected to a signal line 6. Are arranged in parallel with each other. Further, each bias line 9 is bound to the connection 10 at a position outside the detection portion P of the substrate 4.

In the present embodiment, as shown in FIG. 5, each scanning line 5, each signal line 6, and connection 10 of the bias line 9 are input / output terminals (also referred to as pads) provided near the edge of the substrate 4. 11 is connected. As shown in FIG. 8A, one end portion of a COF (Chip On Film) 12 in which a chip such as a gate IC 15c described later is incorporated on the film is provided at the input / output terminal 11 of each scanning line 5 and connection 10. They are connected via an anisotropic conductive adhesive material 13 such as an anisotropic conductive adhesive film or an anisotropic conductive paste.
The COF 12 is routed to the back surface 4b side of the substrate 4 and connected to the gate IC connection substrate 32 described above on the back surface 4b side.

Further, as shown in FIG. 8B, the input / output terminal 11 of each signal line 6 has an end portion of a COF 23 in which a chip of a readout IC 16 described later is incorporated on the film. They are connected via an anisotropic conductive adhesive material 13 such as a anisotropic conductive paste.
The COF 23 is routed to the back surface 4b side of the substrate 4 and is connected to the read IC connection substrate 33 described above on the back surface 4b side. Thus, the board | substrate 4 part of the radiographic imaging apparatus 1 is formed.

  2 and 3, the gate IC connection board 32 is connected to a first connector 26 provided on one inner wall of the mounting portion 2C of the housing 2 by a cable 24 in which wirings are bundled. ing. As a result, it is possible to apply a bias voltage from the still image module 40 or the moving image module 50 to each radiation detection element 7 on the substrate 4 and to apply a voltage to the gate electrode 8 g of the TFT 8.

  The read IC connection board 33 is connected to a second connector 27 provided on the other inner wall of the mounting portion 2C of the housing 2 by a cable 25 in which wirings are bundled. Thereby, in the still image module 40 or the moving image module 50, it is possible to detect charges according to the radiation amount by the radiation detection elements 7 on the substrate 4.

Here, the circuit configuration of the radiation image capturing apparatus 1 will be described. FIG. 9 is a block diagram showing an equivalent circuit of the radiographic image capturing apparatus 1 when the still image module 40 is mounted. FIG. 10 shows an equivalent circuit of the radiographic image capturing apparatus 1 when the moving image module 50 is mounted. FIG. 11 is a block diagram illustrating an equivalent circuit for one pixel constituting the detection unit P when the still image module 40 is mounted, and FIG. 12 is a block diagram when the moving image module 50 is mounted. 3 is a block diagram illustrating an equivalent circuit for one pixel constituting a detection unit P. FIG.
In the following description, the case where the still image module 40 is mounted is described as an example in principle, and the configuration of the moving image module 50 that functions in the same manner as the configuration of the still image module 40 is shown in parentheses. To do.

  As described above, each radiation detection element 7 of the detection unit P of the substrate 4 has the bias electrode 9 connected to the second electrode 78, and each bias line 9 is bound to the connection 10 to be connected to the bias power supply 44B ( 54B). The bias power supply 44B (54B) applies a bias voltage to the second electrode 78 of each radiation detection element 7 via the connection 10 and each bias line 9, respectively. The bias power supply 44B (54B) is connected to a control board 42 (52) described later, and the control board 42 (52) applies a bias voltage to be applied to each radiation detection element 7 from the bias power supply 44B (54B). It comes to control.

  As shown in FIGS. 9 to 12, in the present embodiment, it can be seen that the bias line 9 is connected to the p-layer 77 side (see FIG. 7) of the radiation detection element 7 via the second electrode 78. In addition, the bias power supply 44B (54B) supplies a voltage equal to or lower than a voltage applied to the second electrode 78 of the radiation detection element 7 via the bias line 9 as a bias voltage on the first electrode 74 side of the radiation detection element 7 (that is, so-called reverse). Bias voltage) is applied.

  The first electrode 74 of each radiation detection element 7 is connected to the source electrode 8s of the TFT 8 (indicated as S in FIGS. 9 to 12), and the gate electrode 8g of each TFT 8 (FIGS. 9 to 12). Are respectively connected to the lines L1 to Lx of the scanning line 5 extending from the gate driver 15b of the scanning driving means 15 to be described later. Further, the drain electrode 8d (denoted as D in FIGS. 9 to 12) of each TFT 8 is connected to each signal line 6.

  The scanning drive unit 15 includes a gate driver 15b that switches the voltage applied to each of the lines L1 to Lx of the scanning line 5 between an on voltage and an off voltage to switch between the on state and the off state of each TFT 8, and for still images. An on-voltage and an off-voltage are supplied from the power circuit 44A (54A) mounted on the still image power supply substrate 44 of the module 40 (or the moving image power supply substrate 54 of the moving image module 50) via the wiring 15d. ing. In the present embodiment, the gate driver 15b is configured by arranging a plurality of the aforementioned gate ICs 15c provided in the COF 12 in parallel.

  As shown in FIGS. 9 to 12, each signal line 6 is connected to each readout circuit 17 formed in the readout IC 16. In the present embodiment, a plurality of read ICs 16 are provided, and a single read IC 16 performs processing on a plurality of signal lines 6 (for example, 128 lines). Each read IC 16 has one read line 16 for each signal line 6. Read circuits 17 are provided one by one. In addition, since the readout IC 16 is provided with one readout IC 16 for each COF 23, the same number of COFs 23 as the readout ICs 16 are mounted on the radiographic imaging apparatus 1, but are simplified in FIGS. Only one is shown.

  The readout circuit 17 includes an amplification circuit 18 and a correlated double sampling circuit 19. In the reading IC 16, an analog multiplexer 21 and an A / D converter 20 as a first A / D converter are further provided. 9 to 12, the correlated double sampling circuit 19 is expressed as CDS. Further, in FIG. 11 and FIG. 12, the analog multiplexer 21 is omitted.

  In the present embodiment, the amplifier circuit 18 is configured by a charge amplifier circuit, and is configured by connecting a capacitor 18b and a charge reset switch 18c in parallel to the operational amplifier 18a and the operational amplifier 18a. Further, the amplifier circuit 18 is supplied with power for supplying power to the amplifier circuit 18 mounted on the still image power supply substrate 44 of the still image module 40 (or the moving image power supply substrate 54 of the moving image module 50). The part 44C (54C) is connected.

Further, the signal line 6 is connected to the inverting input terminal on the input side of the operational amplifier 18 a of the amplifier circuit 18, and the reference potential V ₀ is applied to the non-inverting input terminal on the input side of the amplifier circuit 18. ing. Note that the reference potential V ₀ is set to an appropriate value, and in this embodiment, for example, 0 [V] is applied.

  The charge reset switch 18c of the amplifier circuit 18 is connected to the control board 42 (52) and is controlled to be turned on / off by the control board 42 (52). When the image data D is read from each radiation detection element 7, if the charge reset switch 18c is turned off and the TFT 8 of the radiation detection element 7 is turned on, the charge discharged from each radiation detection element 7 is changed. A voltage value corresponding to the amount of accumulated charge is output from the output side of the operational amplifier 18a by flowing into the capacitor 18b via the signal line 6 and accumulated therein.

  In this way, the amplifier circuit 18 outputs a voltage value according to the amount of charge output from each radiation detection element 7 and converts the charge voltage. When the charge reset switch 18c is turned on, the input side and the output side of the amplifier circuit 18 are short-circuited, and the charge accumulated in the capacitor 18b is discharged to reset the amplifier circuit 18. ing. Note that the amplifier circuit 18 may be configured to output a current in accordance with the charge output from the radiation detection element 7.

  A correlated double sampling circuit (CDS) 19 is connected to the output side of the amplifier circuit 18. In this embodiment, the correlated double sampling circuit 19 has a sample and hold function. The sample and hold function in the correlated double sampling circuit 19 is turned on by a pulse signal transmitted from the control board 42 (52). / Off is controlled.

  Then, the control board 42 (52) controls the amplification circuit 18 and the correlated double sampling circuit 19 in the reading process of the image data D from each radiation detection element 7 after radiographic imaging, and each radiation detection element. 7, the charge discharged from each radiation detection element 7 during the readout process is subjected to charge-voltage conversion by the amplification circuit 18, and the voltage value after the charge-voltage conversion is sampled by the correlated double sampling circuit 19 to obtain image data. D is output downstream.

When the still image module 40 is mounted, the image data D of each radiation detection element 7 output from the correlated double sampling circuit 19 is transmitted to the analog multiplexer 21 (see FIG. 9), and the analog multiplexer 21 sequentially performs A / D. It is transmitted to the converter 20. The image data D of each radiation detection element 7 is sequentially converted into digital image data D by the A / D converter 20, output to the storage means 40, and sequentially stored.
The A / D conversion circuit 20 is a power-saving type in order to suppress the power consumption of the battery 43. The A / D conversion circuit 20 is mounted on the readout IC 16 provided in the COF 23. However, the present invention is not limited to this, and may be mounted on the connection board 46A in the still image module 40, for example.

  On the other hand, since higher speed data processing is required during moving image shooting than during still image shooting, the analog image data D is directly input to the moving image module 50 to the COF 23 without going through the A / D conversion circuit 20. A data path to be sent is prepared in advance. Further, the connection board 56A of the moving image module 50 has the same number of high-speed A / D converters 58 as the read ICs 16 that are larger in power consumption than the A / D conversion circuit 20 but faster in processing speed. It is possible to save data by performing A / D conversion at high speed.

Next, each configuration of the still image module 40 will be described.
As shown in FIGS. 1 and 2, the casing 41 of the still image module 40 has a monocoque structure made of the same material as the casing 2 described above, and one side thereof is open and a lid (not shown) is provided. ing. As a result, the internal configuration can be incorporated and the battery 43 can be replaced.
As shown in FIG. 1, an indicator 41 </ b> B composed of a power switch 41 </ b> A, an LED, and the like is provided on a side surface portion facing outward when the housing 41 is mounted.

The control board 42 includes a CPU (Central Processing Unit), a ROM (Read Only Memory), a RAM (Random Access Memory), an input / output interface connected to a bus, an FPGA (Field Programmable Gate Array), or the like (not shown). It is configured. It may be configured by a dedicated control circuit.
And the control board 42 performs imaging | photography control of the still image in a general radiographic image. That is, after the reset processing of each radiation detection element 7 is performed, the charge stored in each radiation detection element 7 is read out by irradiation of radiation, and the image data D input from each readout IC 16 is transferred to the control board 42. Is stored in a storage means 49 (see FIG. 9) composed of a DRAM (Dynamic RAM) or the like.
Further, the control board 42 compresses the image data in the storage means 49 and then controls the wireless module 47 to store the compressed image data on a console 101 (see FIG. 13) described later. Performs wireless transmission processing.

The still image power supply substrate 44 includes the power supply circuit 44A, the bias power supply 44B, the power supply unit 44C, and the like described above, and sets the output voltage of the battery 43 to an appropriate voltage for other configurations that require power supply. It has the function to convert and supply.
The still image power supply board 44 also incorporates a charging circuit that controls charging of the battery 43 when external power is supplied from the connection terminal 48.
The connection terminal 48 includes a connection terminal for a charging cable (not shown) and a connection terminal for a charging cradle (not shown).
The charging cradle can detachably hold only the still image module 40 alone. With the still image module 40 alone held, the charging terminal of the connection terminal 48 is connected to the charging cradle side. Connected to the charging terminal. Thereby, the battery 43 can be charged to the single still image module 40 through the still image power supply substrate 44 by the charging cradle.
When using a charging cable, the charging cable can be connected to the connection terminal 48 while the still image module 40 is still attached to the radiation image capturing apparatus 1 to charge the battery 43. Further, it is also possible to charge the battery 43 by connecting a charging cable to the connection terminal 48 in the state of the still image module 40 alone.

Next, each configuration of the moving image module 50 will be described.
As shown in FIGS. 1 and 3, the casing 51 of the video module 50 has the same structure as the casing 41 described above, and a power switch 51A and an indicator 51B are provided on the outer side surface portion. Yes.

The control board 52 is configured by a computer (not shown), a ROM, a RAM, an input / output interface or the like connected to a bus, an FPGA, or the like. The control board 52 may also be configured with a dedicated control circuit.
Then, the control board 52 performs continuous shooting control of a plurality of frames (for example, 30 frames / second) per unit time. At this time, the control in shooting of each frame is almost the same as the shooting control of still image. However, in order to reduce the data processing load, the shooting control is executed by reducing the resolution per frame by thinning-out control. It has become.

Further, in the control board 52, the image data of the moving image acquired by the imaging control is stored in a storage unit 59 (see FIG. 10) configured by a DRAM or the like provided in the control board 52.
The moving image module 50 includes a high-speed communication processing unit 57 capable of transferring a large amount of data via the communication cable 57A. Therefore, the moving image image data acquired by the shooting control is transferred to the outside as it is. Alternatively, compression processing may be performed in advance.

  The moving image processing unit 53 performs filter processing such as noise removal on the image data acquired by the shooting control. For example, this filter processing may be executed in parallel with photographing. In that case, since high-speed processing is required, a plurality of integrators and product-sum calculators specialized for a predetermined filter are provided. You may use the hardware which we did.

As described above, the high-speed communication processing unit 57 performs data transfer via the communication cable 57A, and can transmit large-capacity image data at high speed.
The communication cable 57A of the high-speed communication processing unit 57 is connected to a repeater 113 (see FIG. 13) described later, and data transfer to the console 101 is possible through the repeater 113.

The moving picture power supply board 54 includes the power supply circuit 54A, the bias power supply 54B, the power supply section 54C, and the like described above, and converts an external supply voltage into an appropriate voltage for other configurations that require power supply. Thus, it has a function of supplying each component.
Further, as described above, the moving image module 50 saves power by providing a plurality of high-speed A / D converters 58 on the connection board 56A separately from the A / D conversion circuit 20 mounted on the COF 23. Therefore, a configuration is adopted in which power is supplied from the outside through the power cable 54A connected to the repeater 113 without using a battery. Even in such a configuration, the portability of the radiographic imaging apparatus 1 is not impaired as long as the power cable 54A is within reach.

Next, an example in which the radiographic image capturing apparatus 1 is arranged and used in a radiographic image capturing system 100 as shown in FIG. 13 will be described. Here, the radiographic image capturing apparatus equipped with the still image module 40 will be described as 1A, and the radiographic image capture apparatus equipped with the moving image module 50 will be described as 1B.
The radiographic image capturing system 100 includes, for example, radiographic image capturing apparatuses 1 </ b> A and 1 </ b> B and a console 101 that can communicate with the radiographic image capturing apparatus 1.

  As illustrated in FIG. 13, the radiographic imaging apparatuses 1A and 1B are provided in an imaging room R1 that performs imaging of a subject (an imaging target site of the patient M) that is a part of the patient M by irradiating radiation, for example. The console 101 is provided corresponding to the photographing room R1.

In the radiographing room R1, there are a bucky device 110 including a cassette holding unit 111 that can load and hold the radiographic imaging devices 1A and 1B, an X-ray tube that irradiates a subject (a subject to be imaged by the patient M), and the like. A radiation generator 112 comprising a radiation source (not shown) is provided. The cassette holding unit 111 is loaded with the radiographic imaging device 1A or 1B at the time of imaging.
FIG. 13 illustrates a case where one of the bucky devices 110a for standing position shooting and one of the bucky devices 110b for standing position shooting are provided in the shooting room R1, but in the shooting room R1. The number of the bucky devices 110 provided in is not particularly limited.
Further, in the present embodiment, the case where the radiographic imaging device 1A is loaded in the bucky device 110a and the radiographic imaging device 1B is loaded in the bucky device 110b is illustrated, but the present invention is not limited thereto. It is also good.

  In addition, since the radiographing room R1 is a room that shields radiation and radio waves for radio communication are blocked, the radiographic imaging apparatuses 1A and 1B communicate with external devices such as the console 101 in the radiographing room R1. In this case, a repeater 113 capable of relaying these communications by wire and wireless is provided.

  In the present embodiment, a front room R2 is provided adjacent to the photographing room R1. In the anterior chamber R2, a radiographer, a doctor, etc. (hereinafter referred to as an “operator”) control the tube voltage, tube current, irradiation field stop, etc. of the radiation generator 112 that irradiates the subject with radiation. An operation device 114 for operating the device 110 is disposed.

  A control signal for controlling the radiation irradiation condition of the radiation generating device 112 is transmitted from the console 101 to the operation device 114, and the radiation irradiation condition of the radiation generating device 112 is transmitted to the console 101. It is set according to the control signal from. Examples of radiation irradiation conditions include exposure start / end timing, radiation tube current value, radiation tube voltage value, filter type, and the like.

  An exposure instruction signal for instructing the exposure of radiation is transmitted from the operation device 114 to the radiation generation apparatus 112. The radiation generation apparatus 112 has a predetermined radiation set in advance according to the exposure instruction signal. Irradiation is performed at a predetermined timing for a time.

The console 101 is a computer including a control unit configured by a CPU (Central Processing Unit), a storage unit, an input unit, a display unit, a communication unit (all not shown), and the like.
The console 101 displays an image based on the image data sent from the radiation image capturing apparatus 1 on the display unit, and performs various image processing on the image data.
In the present embodiment, the console 101 is connected to external devices such as the HIS / RIS 121, the PACS server 122, and the imager 123 via the network N.

  In such a radiographic imaging system 100, the radiographic imaging apparatus 1A performs radiographic imaging of still images, and the radiographic imaging apparatus 1B performs radiographic imaging of moving images. Then, the image data obtained by each of the radiographic image capturing apparatuses 1A and 1B is transmitted to the repeater 113 wirelessly or by wire, and is transmitted to the console 101.

As described above, in the radiographic imaging apparatus 1, the housing 2 is provided with the mounting portion 2 </ b> C capable of selectively mounting the still image module 40 and the moving image module 50, and the modules 40 and 50 are exchanged and connected. Since it was made possible, it is possible to select and shoot still images and moving image radiation images as necessary.
Since only one of the still image module 40 and the moving image module 50 is selectively mounted, the camera has a configuration suitable for still image shooting when shooting a still image. At the time of shooting, since the configuration suitable for moving image shooting is provided, the radiographic image shooting device 1 can avoid the installation of a configuration in which still images and moving images are shot repeatedly, and the size of the device can be reduced. In addition, the weight can be reduced.

The still image module 40 of the radiographic image capturing apparatus 1 includes a control board 42 that controls reading of a radiographic image still image, a wireless module 47 that transmits image data to the outside, and a battery that supplies power to each unit. 43 and the still image power supply substrate 44 and the like, it is not necessary to share these configurations with the moving image module 50, and it is possible to mount each of them specialized for the purpose of use.
For example, since the still image module 40 handles less data than the moving image module 50, it is possible to select a low power consumption amount for each configuration. Can be used for a long time.

  The moving image module 50 is powered by the power supply cable 54A from the control board 52 that controls moving image reading, the high-speed communication processing unit 57 that transmits image data based on moving image reading to the outside by wire, and the repeater 113. Since the moving image power supply board 54 for supplying power to each part of the apparatus is provided, the processing speed can be increased by specializing when the amount of data processing such as moving image data is large. . In addition, as a result, the moving image power supply board 54 that is powered by wire is provided for an increase in power consumption, so that long-term use is possible while maintaining portability to some extent.

In addition, the moving image module 50 includes a high-speed A / D converter 58 corresponding to high-speed processing in addition to the A / D converter 20 provided in the COF 23, and therefore a large amount of data such as moving image data. Even when digital processing is performed, rapid processing is possible.
Further, the moving image module 50 is not optimized for shooting still images to the same extent as the still image module 40, but can also handle still image shooting.

DESCRIPTION OF SYMBOLS 1 Radiographic imaging apparatus 2 Case 7 Radiation detection element 20 A / D converter (1st A / D converter)
40 Still Image Module 42 Control Board (Still Image Control Unit, Function Unit)
43 battery (power storage unit, functional unit)
44 Power supply board for still images (functional part)
47 Wireless module (wireless communication unit, function unit)
50 Movie Module 52 Control Board (Functional Unit)
53 Moving Image Processing Unit (Functional Unit)
54 Video power supply board (wired power supply unit, functional unit)
54A Feeding cable 57 High-speed communication processing unit (wired communication unit, function unit)
58 High-speed A / D converter (second A / D converter, functional part)
100 Radiation Imaging System P Detector R Radiation Incident Surface

Claims (5)

A housing having a radiation incident surface;
In a radiographic imaging apparatus comprising: a detection unit including a plurality of radiation detection elements housed in the housing and arranged two-dimensionally;
A still image module having a function unit suitable for still image shooting and a moving image module having a function unit suitable for moving image shooting can be attached to and detached from the housing, and only one of them can be replaced by replacement. A radiographic imaging apparatus, characterized in that it can be attached. The still image module includes:
A still image control unit for controlling reading of a still image of a radiation image;
A wireless communication unit that transmits image data based on reading a still image to the outside;
The radiographic image capturing apparatus according to claim 1, further comprising a power storage unit that supplies power to each unit of the apparatus. The video module is
A moving image control unit that controls reading of moving images of radiation images;
A wired communication unit that transmits image data based on the reading of the video to the outside;
The radiographic imaging apparatus according to claim 1, further comprising: a wired power supply unit that supplies power to each unit of the apparatus while being fed with a cable from outside the apparatus.   The first A / D converter for converting the output of the detection unit at the time of shooting a still image from analog to digital is provided in a reading circuit of the detection unit or the still image module. The radiographic imaging apparatus as described in any one of Claims 1-3.   The moving image module is provided with a second A / D converter having a higher processing speed than the first A / D converter for converting the output of the detection unit at the time of shooting a moving image from analog to digital. The radiographic imaging apparatus according to claim 4, wherein

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