JP5635894B2 - Radiation imaging apparatus and power supply method for radiation imaging apparatus - Google Patents

Description

The present invention relates to a power supply method of the radiation image capturing instrumentation 置及 beauty radiographic imaging device, for example, an operator using the portable radiographic imaging apparatus capable portable outdoor suitable radiographic imaging instrumentation 置及 beauty radiographic image The present invention relates to a power supply method for an imaging apparatus.

  2. Description of the Related Art In the medical field, radiation image capturing apparatuses that irradiate a subject with radiation and guide the radiation transmitted through the subject to a radiation conversion panel (radiation detector) to capture a radiation image are widely used. As the radiation conversion panel, a conventional radiation film in which the radiation image is exposed and recorded, or radiation energy as the radiation image is accumulated in a phosphor and irradiated with excitation light, thereby stimulating the radiation image. A storage phosphor panel that can be extracted as light is known. These radiation conversion panels supply the radiation film on which the radiation image is recorded to the developing device to perform development processing, or supply the storage phosphor panel to the reading device to perform reading processing, A visible image can be obtained.

  On the other hand, in an operating room or the like, it is necessary to be able to immediately read out and display a radiation image from a radiation detector after imaging in order to perform a quick and accurate treatment on a patient. As a radiation detector capable of meeting such demands, a direct conversion type radiation detection apparatus (electronic cassette) using a solid detection element that directly converts radiation into an electrical signal, or a scintillator that temporarily converts radiation into visible light An indirect conversion type radiation detection apparatus (electronic cassette) using the solid-state detection element that converts the visible light into an electric signal has been developed (see Patent Document 1).

  Such a conventional radiographic imaging device has been developed on the premise of imaging of a patient in a medical institution.

  On the other hand, there is a potential demand for imaging outside a medical institution, and for example, an in-vehicle radiographic imaging device for the purpose of health examination using a medical examination vehicle has been proposed. However, such a radiographic imaging device is a relatively large size mounted on the examination car. Therefore, for example, even if it is attempted to take a picture of a subject at a disaster site such as a natural disaster or home nursing, in the case of a disaster site, the examination vehicle cannot be moved to the disaster site. In the case of home nursing, the examination car can be moved to the home of the subject (home person) serving as the home nursing site, but the home person can be brought into the examination car at the time of photographing. Since it is necessary to guide, the burden on the home-stayer involved in the shooting is increased. Therefore, an ultra-compact and portable radiographic imaging device is required at the disaster site and the home nursing site.

Therefore, in recent years, portable radiographic imaging devices (see Patent Document 2) that can accommodate the entire system in a compact manner and field electron emission type radiation sources using carbon nanotubes (CNT) have been developed. (Refer to patent document 3 and non-patent document 1) The miniaturization and weight reduction of a radiographic imaging apparatus including the radiation source are expected. In addition, a compact high-energy X-ray source using LiTaO ₃ crystal, which is a typical pyroelectric crystal, has been developed (see Non-Patent Document 2).

  Note that Non-Patent Document 3 and Non-Patent Document 4 are known as methods for wirelessly transmitting power. The method described in Non-Patent Document 3 transmits power by electromagnetic induction from a primary coil embedded in a non-contact power transmission sheet. The method described in Non-Patent Document 4 includes a magnetic field between two LC resonators. This is a wireless power transmission technology that uses the resonance.

US Pat. No. 5,514,873 Special table 2007-530979 gazette JP 2007-103016 A

AIST: Press release, “Development of portable X-ray source using carbon nanostructures”, [online], March 19, 2009, National Institute of Advanced Industrial Science and Technology, [July 2009] Search 8th of May], Internet <URL: http://www.aist.go.jp/aist_j/press_release/pr2009/pr20090319/pr20090319.html> Advances in X-ray analysis No. 41 (2010) Reprint p. 195-p. 200 “Application of pyroelectric crystals to small high-energy X-ray sources” IEDM pre “Non-contact power transmission sheet for embedding in walls and floors, developed by the University of Tokyo”, [online], December 4, 2006, [December 21, 2007 search], Internet < URL: http: // techon. nikkeibp. co. jp / article / NEWS / 20061204/1244943 /> Nikkei Electronics 2007.12.3 p. 117-128 “Development of technology to transmit power wirelessly Turn on 60W light bulb in experiment”

  If the radiation source can be miniaturized as in Patent Documents 2 and 3 and Non-Patent Documents 1 and 2 described above, the entire radiographic imaging apparatus including the radiation source and the electronic cassette is combined with the electronic cassette shown in Patent Document 1 and the like. Is reduced in size and weight, and the radiographic imaging apparatus can be easily moved. That is, a portable radiographic imaging device can be realized.

  However, since such a portable radiographic imaging apparatus is mainly used by taking it outdoors, there is a problem of how to secure power supply. Thus, it is conceivable to prepare a separate battery and carry the battery together with a portable radiographic imaging device. In this case, it is necessary to prepare a dedicated battery for the radiation source, a dedicated battery for the electronic cassette, and a dedicated battery for the controller (such as a personal computer). Will be prepared. As a result, there are problems that the carrying size and weight increase, and usability (including portability) deteriorates.

The present invention has been made in order to solve the above-described problems, and can secure power supply to a radiation source and a radiation detection device even outdoors, and can reduce power consumption. Moreover, it is possible to suppress the battery to provide a minimum, usability outdoors such as an object to provide a power supply method of the radiation image capturing instrumentation 置及 beauty radiographic imaging apparatus becomes excellent.

[1] A radiographic imaging apparatus according to a first aspect of the present invention includes a radiation source main body that houses a radiation source that outputs radiation, and the radiation source that has passed through the subject when the radiation is applied to the subject. A portable radiographic imaging device having a detector main body that houses a radiation detector that detects radiation and converts it into a radiographic image, wherein at least one of the radiation source main body and the detector main body is A power supply restricting unit that restricts and controls power supply, and the power supply restricting unit controls bidirectional power supply between the battery in the radiation source body and the battery in the detector body. A power control unit; and a power supply limiting unit that limits power supply between the radiation source main body and the detector main body by the power control unit during a period during which radiographing is performed. And

[ 2 ] The power supply method of the radiographic imaging apparatus according to the second aspect of the present invention includes a radiation source main body that houses a radiation source that outputs radiation, and the radiation source irradiates a subject with the radiation. A power supply method for a portable radiographic imaging device having a detector main body housing a radiation detector that detects radiation that has passed through a subject and converts it into a radiographic image , the battery in the source main body wherein the step of controlling the two-way power supply with the battery in the detector main body, the period during which the imaging by radiation is being performed, the line source body portion and the power between the detector main unit mutual and And limiting the supply.

  According to the present invention, it is possible to secure power supply to a radiation source and a radiation detection apparatus even outdoors, to reduce power consumption and to minimize the number of batteries to be prepared. It is easy to use outdoors.

It is a perspective view which shows the radiographic imaging apparatus (1st radiographic imaging apparatus) which concerns on 1st Embodiment. It is explanatory drawing which shows the conveyance state of a 1st radiographic imaging apparatus. It is sectional drawing which looked at the cross section along the horizontal surface of the 1st radiographic imaging apparatus in FIG. 1 in the direction of III-III. It is a top view which shows the state which isolate | separated the radiation source main-body part from the cassette main-body part of FIG. It is sectional drawing which shows the inside of the radiation source main-body part of FIG. It is sectional drawing which shows imaging | photography by the 1st radiographic imaging apparatus. It is a perspective view which shows the imaging preparation of a 1st radiographic imaging apparatus. It is a perspective view which shows imaging | photography by the 1st radiographic imaging apparatus. It is explanatory drawing which shows typically the arrangement | sequence of the pixel in a radiation detector. It is a circuit diagram of a cassette body part. It is a block diagram of the 1st radiographic imaging device. It is a top view which shows an example of the radiographic image displayed on the display part of a portable terminal after imaging | photography. It is a block diagram which shows the structure of a battery part. It is a block diagram which shows the structure of a battery control part. It is a block diagram which shows the 1st specific example of an electric power control part. It is a block diagram which shows the 2nd specific example (a power management part is included) of a power control part. It is a block diagram which shows the structure of a cassette selection starting part and a cassette selection part. It is a block diagram which shows the structure of an integrated supply starting part and an integrated supply part. It is a block diagram which shows the structure of a power management part. It is a flowchart (the 1) which shows operation | movement of a 1st radiographic imaging apparatus in case supply timing conditions are no timing restrictions. It is a flowchart (the 2) which shows operation | movement of a 1st radiographic imaging apparatus in case supply timing conditions are no timing restrictions. It is a flowchart (the 1) which shows operation | movement in case supply timing conditions are supply before imaging | photography. It is a flowchart (the 2) which shows operation | movement in case supply timing conditions are supply before imaging | photography. 12 is a flowchart (part 3) illustrating an operation in a case where a supply timing condition is supply before photographing. It is a flowchart (the 1) which shows operation | movement in case supply timing conditions are supply after imaging | photography. It is a flowchart (the 2) which shows operation | movement in case supply timing conditions are supply after imaging | photography. It is a perspective view which shows the modification of a 1st radiographic imaging apparatus. It is a perspective view which shows the modification of a 1st radiographic imaging apparatus. It is a perspective view which shows the modification of a 1st radiographic imaging apparatus. It is a perspective view of the radiographic imaging device (2nd radiographic imaging device) which concerns on 2nd Embodiment. It is explanatory drawing which shows the conveyance state of a 2nd radiographic imaging apparatus. FIG. 31 is a cross-sectional view taken along line XXXII-XXXII in FIG. 30. It is a top view which shows the state which isolate | separated the radiation source main-body part from the cassette main-body part of FIG. It is sectional drawing which shows imaging | photography by the 2nd radiographic imaging apparatus. It is explanatory drawing for demonstrating SID of FIG. 34 in detail. It is a perspective view which shows the imaging preparation of a 2nd radiographic imaging apparatus. It is a perspective view which shows imaging | photography by the 2nd radiographic imaging apparatus. It is a perspective view of the radiographic imaging apparatus (3rd radiographic imaging apparatus) which concerns on 3rd Embodiment. It is a perspective view of a 3rd radiographic imaging device. It is a side view of a 3rd radiographic imaging device. It is explanatory drawing which shows the conveyance state of a 3rd radiographic imaging apparatus. It is a block diagram which shows the structure of a part of PC. It is a block diagram which shows the structure of a current collection part. It is a flowchart which shows operation | movement of a current collection part. It is a figure which shows roughly the structure for 3 pixels of the radiation detector which concerns on a modification. FIG. 46 is a schematic configuration diagram of a TFT and a charge storage section shown in FIG. 45.

  As shown in FIGS. 1 and 2, the portable radiographic image capturing apparatus according to the first embodiment (hereinafter referred to as the first radiographic image capturing apparatus 10 </ b> A) has a substantially rectangular casing and radiation 46. The cassette body 12 is held by the cassette body 12 by means of a cassette body 12 made of a material that can permeate (see FIG. 5) and holding members 16a and 16b that project outward from both ends of the side surface 14a of the cassette body 12. A cylindrical radiation source body 18.

  In this case, a guide line 22 serving as a reference for an imaging region and an imaging position is formed on one surface (irradiation surface 20) of the cassette body 12. A handle 24 is provided on the side surface 14b opposite to the side surface 14a on which the holding members 16a and 16b are formed. Further, of the remaining two side surfaces 14c and 14d of the cassette body 12, one side surface 14c has a USB (Universal Serial Bus) terminal 28 as an interface means capable of transmitting / receiving information to / from an external device, A card slot 32 for loading the memory card 30 and a lock release button 34 to be described later are provided. In addition, the side surface 14c is removable from the cassette body 12 and includes a display unit 36 and an operation unit 40 operated by a doctor or a radiographer (hereinafter also referred to as an operator 38). A terminal 42 is attached. On the other hand, the radiation source body 18 is provided with an exposure switch 48 for starting output of radiation 46 (see FIG. 5) from a radiation source 44 described later.

  1 and 2 show the state of the first radiographic imaging apparatus 10A when the operator 38 transports the first radiographic imaging apparatus 10A. In this case, the cassette main body 12 and the radiation source main body 18 are integrally connected and fixed. Accordingly, the operator 38, while holding the handle 24, transports the first radiographic imaging apparatus 10A to, for example, an accident site, disaster site, health checkup or home nursing site outside the medical institution, so that the operator 38 Using the first radiographic image capturing apparatus 10A, for example, radiographic imaging for accident victims and disaster victims, radiographic imaging for those who undergo medical examinations (examiners), home nursing It is possible to take a radiographic image for a required person at home. In the following description, the victim, the victim, the examinee, the home-stayed person, and the like, which are radiographic images, are also referred to as a subject 50 (see FIG. 6).

  Here, the integrally connected and fixed state of the cassette body 12 and the radiation source body 18 is such that the cassette can be transported by the first radiographic imaging apparatus 10A by a connection mechanism 82 (see FIG. 3) described later. This means a state in which the main body 12 and the radiation source main body 18 are integrally connected.

  Next, refer to FIGS. 3 to 8 for the state of the first radiographic imaging device 10A when the portable radiographic imaging device 10A is brought into a disaster site or home nursing site outside the medical institution. While explaining.

  As shown in FIG. 3, among the side walls 52a to 52d constituting the side surfaces 14a to 14d of the cassette body 12, the USB terminal 28, the card slot 32, and the lock release button 34 are arranged on the side wall 52c. A portion of the side wall 52c between the card slot 32 and the lock release button 34 is a concave portion 54 that is recessed inward, and the portable terminal 42 can be attached to the concave portion 54.

  The unlock button 34 can be displaced toward the side wall 52d along the side wall 52a due to the pressing operation by the operator 38 (see FIG. 2). In this case, a slide portion 56 is formed along the side wall 52a on the side of the side wall 52d of the lock release button 34. A protrusion 58 is formed between the slide portion 56 and the protrusion 58 protruding inward from the side wall 52a. A spring member 60 is inserted that springs from the side toward the side wall 52c. Further, a hole 62 is formed in a part of the side wall 52a with which the slide portion 56 comes into contact, and the inside of the cassette body 12 is communicated with the outside. A hook that passes through the hole 62 is formed on the side portion of the slide portion 56. A portion 64 is formed.

  On the other hand, as shown in FIGS. 3 and 4, when the radiation source main body 18 is held by the cassette main body 12 by the holding members 16 a and 16 b, the radiation source main body 18 is opposed to the hole 62. Is formed with a hole 66 having substantially the same size as the hole 62. Accordingly, when the hook portion 64 is displaced toward the side wall 52c by the elastic force of the spring member 60, the hook portion 64 and the hole 66 (see FIG. 3) engage with each other. As a result, radiation is applied to the cassette body portion 12. The source body 18 can be integrally connected and fixed (see FIG. 3).

  In addition, a conductive connection terminal (first radiation source side connection terminal 68a) is attached to one end of the radiation source body 18 on the holding member 16a side, and the other end on the holding member 16b side is attached to the other end on the holding member 16b side. A conductive connection terminal (second radiation source side connection terminal 68b) is mounted. In this case, the first radiation source side connection terminal 68a is convex toward the holding member 16a, while the second radiation source side connection terminal 68b is concave toward the holding member 16b. In addition, the radiation source body 18 is provided with a first energy input / output unit 300 or a second energy input / output unit 302 (see FIG. 13) that performs input and output of, for example, wired or wireless power. For example, the first energy input / output unit 300 or the second energy input / output unit 302 is configured by the first source side connection terminal 68a and the second source side connection terminal 68b. Of course, the structure electrically connected by radio | wireless may be sufficient. Moreover, the 2nd energy input / output part 302 or the 1st energy input / output part 300 in which the input / output of the electric power etc. by a wire or radio | wireless is performed is installed in the side surface of the radiation source main-body part 18 (refer FIG. 1).

  On the other hand, a conductive connection terminal (first cassette side connection terminal) 70a is mounted on the radiation source body 18 side of the holding member 16a of the cassette body 12 and the radiation source body 18 of the holding member 16b. On the side, a conductive connection terminal (second cassette side connection terminal) 70b is mounted. In this case, the first cassette side connection terminal 70a has a concave shape corresponding to the first radiation source side connection terminal 68a, while the second cassette side connection terminal 70b corresponds to the second radiation source side connection terminal 68b. It is convex. Also in the cassette body 12, for example, a first energy input / output unit 300 or a second energy input / output unit 302 (see FIG. 13) that performs input / output of electric power or the like by wire or wireless is installed. For example, the first energy input / output unit 300 or the second energy input / output unit 302 is configured by the first cassette side connection terminal 70a and the second cassette side connection terminal 70b. Of course, the structure electrically connected by radio | wireless may be sufficient. In addition, a second energy input / output unit 302 or a first energy input / output unit 300 that performs input / output of power or the like by wire or wireless is installed on one side surface 14 c of the cassette body 12.

  Therefore, as shown in FIG. 3, in a state where the hook portion 64 and the hole 66 are engaged by the elastic force of the spring member 60 and the cassette body portion 12 and the radiation source body portion 18 are integrally connected and fixed. The convex first source side connection terminal 68a and the concave first cassette side connection terminal 70a are engaged, and the concave second source side connection terminal 68b and the convex second cassette side connection terminal 70b are engaged. And the cassette main body 12 and the radiation source main body 18 can be reliably maintained in an integrally connected and fixed state. That is, these connection terminals 68a, 68b, 70a, 70b are also members for assisting in maintaining an integrally connected and fixed state of the cassette body 12 and the radiation source body 18 by the hook 64 and the hole 66. Function.

  On the other hand, as shown in FIG. 4, when the operator 38 pushes the unlock button 34 and moves the unlock button 34 to the side wall 52d against the elastic force of the spring member 60, the hook portion 64 and the slide portion 56 are moved. Is displaced toward the side wall 52d, and the engagement state between the hook portion 64 and the hole 66 is released. Therefore, the operator 38 removes the radiation source body 18 from the cassette body 12 (separation) in a state where the engagement state between the hook portion 64 and the hole 66 is released (the operator 38 is pressing the lock release button 34). By doing so, the integrally connected and fixed state of the cassette body 12 and the radiation source body 18 is released.

  A measure 72 is also arranged in the cassette body 12. The measure 72 is, for example, a measure that winds the band member 76 with the scale 74 swung in a roll shape by the action of a spring member (not shown), and the side of the measure 72 has a band member 76 from the measure 72 on the side. A rotary encoder 78 for detecting the pull-out amount is attached. The distal end portion of the band member 76 drawn out from the measure 72 is inserted through a hole 80 formed at a location facing the measure 72 in the side wall 52a and in the vicinity of the second radiation source side connection terminal 68b of the radiation source main body portion 18. It is fixed.

  Therefore, as shown in FIG. 3, in the state where the radiation source main body 18 is integrally connected and fixed to the cassette main body 12, most of the band member 76 is caused by the action of the spring member inside the measure 72. In 72, it is wound up in roll shape. On the other hand, as shown in FIGS. 4 to 8, the cassette body portion 12 is resisted against the action of the spring member as long as the integral connection and fixing state of the cassette body portion 12 and the radiation source body portion 18 is released. The strip member 76 can be pulled out from the measure 72 through the hole 80 by separating the radiation source main body 18 from the main body 72.

  The above-described lock release button 34, slide portion 56, spring member 60, hook portion 64, connection terminals 68a, 68b, 70a, 70b, and measure 72 are connected to the cassette body 12 when the first radiographic image capturing apparatus 10A is transported. On the other hand, a coupling mechanism 82 is configured to integrally connect and fix the radiation source body 18 while separating the cassette body 12 and the radiation source body 18 during imaging.

  Further, in the above description, the measure 72 can wind the band member 76 with the scale 74 swung, but instead of the band member 76, the measure 72 is a string member (string) with the scale 74 swung. Of course, the same function as that of the belt member 76 can be achieved.

  Further, as shown in FIG. 3 and FIG. 6, a grid 84 that removes scattered rays of the radiation 46 by the subject 50 when the subject 46 is irradiated with the radiation 46 from the radiation source 44, as shown in FIGS. A radiation detector 86 that detects the radiation 46 that has passed through the subject 50 and a lead plate 88 that absorbs backscattered rays of the radiation 46 are arranged in order on the irradiation surface 20 on the subject 50 side. Note that the irradiation surface 20 may be configured as a grid 84.

  In this case, as the radiation detector 86, for example, the radiation 46 transmitted through the subject 50 is temporarily converted into visible light by a scintillator, and the converted visible light is made of a substance such as amorphous silicon (a-Si). An indirect conversion type radiation detector (including a front side reading method and a back side reading method) that converts an electric signal by (hereinafter also referred to as a pixel) can be used. An ISS (Irradiation Side Sampling) type radiation detector, which is a surface reading method, has a configuration in which a solid detection element and a scintillator are sequentially arranged along the irradiation direction of the radiation 46. A PSS (Penetration Side Sampling) type radiation detector, which is a back side reading method, has a configuration in which a scintillator and a solid state detection element are sequentially arranged along the irradiation direction of the radiation 46. Further, as the radiation detector 86, in addition to the above-described indirect conversion type radiation detector, the direct conversion in which the dose of the radiation 46 is directly converted into an electric signal by a solid detection element made of a substance such as amorphous selenium (a-Se). A type of radiation detector can also be employed.

  Further, inside the cassette body 12, as shown in FIG. 3, a battery unit 304 as a power source of the cassette body 12, and a battery control unit that regulates and controls power supply to the battery unit 304 ( A power supply regulation unit) 306, a cassette control unit 92 for driving and controlling the radiation detector 86 (see FIG. 6) by the power supplied from the battery unit 304, and a signal including information on the radiation 46 detected by the radiation detector 86. And a transmitter / receiver 94 for transmitting / receiving data to / from the outside. The cassette control unit 92 and the transmitter / receiver 94 are provided with a lead plate or the like on the irradiation surface 20 side of the cassette control unit 92 and the transmitter / receiver 94 in order to avoid damage due to the irradiation of the radiation 46. It is preferable.

  Here, the battery unit 304 supplies power to the rotary encoder 78, the radiation detector 86, the cassette control unit 92, and the transceiver 94 in the cassette body 12. The battery unit 304 can also charge the mobile terminal 42 when the mobile terminal 42 is mounted in the recess 54. In addition to the first energy input / output unit 300 and the second energy input / output unit 302 described above, the battery unit 304 includes a battery 308, a first energy conversion unit 310, and a second energy conversion unit, as shown in FIG. 312, and performs power supply (charging) from the outside via wired or wireless via the first energy input / output unit 300 and / or the second energy input / output unit 302, or power supply via wired or wireless to the outside. It is also possible. A first switching unit 314 a is connected between the first energy input / output unit 300 and the first energy conversion unit 310, and a second switching unit 314 b is connected between the second energy input / output unit 302 and the second energy conversion unit 312. Are connected, and the third switching unit 314c to the fifth switching unit 314e are connected between the first energy conversion unit 310, the second energy conversion unit 312 and the battery 308.

  The first energy conversion unit 310 includes a first input conversion unit 316 and a first output conversion unit 318, and the second energy conversion unit 312 includes a second input conversion unit 320 and a second output conversion unit 322. During power input through the first energy input / output unit 300, the first switching unit 314a electrically connects the first energy input / output unit 300 and the first input conversion unit 316, and the third switching unit 314c and the fifth The switching unit 314e electrically connects the first input conversion unit 316 and the battery 308. On the other hand, when power is output through the first energy input / output unit 300, the first switching unit 314a electrically connects the first energy input / output unit 300 and the first output conversion unit 318, and the third switching unit 314c The fifth switching unit 314e electrically connects the first output conversion unit 318 and the battery 308. Similarly, when power is input through the second energy input / output unit 302, the second switching unit 314b electrically connects the second energy input / output unit 302 and the second input conversion unit 320, and the fourth switching unit 314d. And the fifth switching unit 314e electrically connects the second input conversion unit 320 and the battery 308. On the other hand, at the time of power output through the second energy input / output unit 302, the second switching unit 314b electrically connects the second energy input / output unit 302 and the second output conversion unit 322, and the fourth switching unit 314d The fifth switching unit 314e electrically connects the second output conversion unit 322 and the battery 308. These switching controls are performed by a power supply control unit 374 described later.

  The first energy input / output unit 300, the second energy input / output unit 302, the first energy conversion unit 310, and the second energy conversion unit 312 have different configurations depending on the type of energy to be supplied (supply energy).

  For example, if power energy is supplied by a wired connection such as a cable or a connection terminal, the first energy input / output unit 300 is a connector connected to the cable or the connection terminal, for example. The first input conversion unit 316 is, for example, a voltage converter that converts a voltage input from the first energy input / output unit 300 via the first switching unit 314a into an optimum voltage for battery charging. The unit 318 is, for example, a voltage converter that converts the voltage output from the battery via the fifth switching unit 314e and the third switching unit 314c into a voltage optimal for power transmission. The same applies to the second energy input / output unit 302 and the second energy conversion unit 312.

  As in Non-Patent Document 3, if the electromagnetic induction is performed by a coil (primary coil or secondary coil) embedded in a non-contact power transmission sheet, the first energy input / output unit 300 is a secondary coil or a primary coil. The first input conversion unit 316 is, for example, a voltage converter that converts the voltage generated by the first energy input / output unit 300 (which functions as a secondary coil in this case) into a voltage optimal for battery charging. The output conversion unit 318 converts the voltage output from the battery 308 through the fifth switching unit 314e and the third switching unit 314c into a current that flows to the first energy input / output unit 300 (in this case, functions as a primary coil). For example, a voltage-current converter for conversion. The same applies to the second energy input / output unit 302 and the second energy conversion unit 312.

  As in Non-Patent Document 4, if the wireless power transmission technology uses magnetic field resonance, the first energy input / output unit 300 is installed corresponding to the first LC resonator or the second LC resonator on the power transmission side. The first LC converter or the first LC resonator, and the first input conversion unit 316 uses the electromagnetic energy generated by the first energy input / output unit 300 (which functions as the second LC resonator in this case) as electric power by electromagnetic induction. A coil that converts energy (secondary coil when the coil of the second LC resonator is used as a primary coil), and the like. Via the first energy input / output unit 300 (which functions as the first LC resonator in this case) as electromagnetic energy (coil of the first LC resonator). A primary coil) and the like in the case of the Le was secondary coil. The same applies to the second energy input / output unit 302 and the second energy conversion unit 312.

  Of course, the supply energy may be light energy or heat energy. In the case of light energy, the energy receiving unit is a light energy receiving unit, and the energy conversion unit corresponds to a photoelectric conversion unit that converts the received energy into electric power. In the case of thermal energy, the energy receiving unit is a heat receiving unit that receives thermal energy, and the energy conversion unit corresponds to a thermoelectric conversion element (for example, a thermoelectric conversion element using the Seebeck effect) that converts received heat into electric power. .

  As the battery 308, a secondary battery (nickel metal hydride, nickel-cadmium, lithium, etc.) and a capacitor (electric field capacitor, electric double layer capacitor, lithium ion capacitor, etc.) can be used. In this case, you may comprise so that attachment or detachment with respect to an apparatus is possible. Further, the battery 308 may be constituted by a small built-in capacitor capable of storing the amount of power required for at least one image capturing.

  Since the transmitter / receiver 94 can transmit / receive signals to / from the outside, for example, transmission / reception of signals to / from the transmitter / receiver 98 (see FIG. 11) of the mobile terminal 42 removed from the recess 54, or the cassette body Signals can be transmitted / received to / from the transmitter / receiver 100 of the radiation source body 18 that is separated from the unit 12. Of course, even when the cassette body 12 and the radiation source body 18 are integrally connected and fixed and / or the portable terminal 42 is mounted in the recess 54, each of the transceivers 94, 98, 100 Signals can be transmitted and received between them.

  As shown in FIG. 5, the radiation source main body 18 controls the radiation source 44, the battery unit 304, the battery control unit 306 that controls the battery unit 304, the transceiver 100, and the radiation source 44. The radiation source control unit 102 and the laser pointer 104 are arranged, and a first energy input / output unit 300 or a second energy input / output unit 302 similar to the cassette body 12 is provided on a side surface of the casing.

  The radiation source 44 is a field electron emission type radiation source similar to that of Patent Document 3.

  That is, in the radiation source 44, a disk-shaped rotating anode 110 is attached to a rotating shaft 108 rotated by a rotating mechanism 106, and an annular target whose main component is a metal element such as Mo is formed on the surface of the rotating anode 110. Layer 112 is formed. On the other hand, a cathode 114 is disposed facing the rotating anode 110, and a field electron emission electron source 116 is disposed on the cathode 114 so as to face the target layer 112.

The radiation source control unit 102 controls the radiation source 44 to output the radiation 46 due to the operation of the exposure switch 48 by the operator 38. That is, in the radiation source 44, the rotating mechanism 106 rotates the rotating shaft 108 according to the control from the radiation source control unit 102, so that the rotating anode 110 rotates, and the power source unit 118 is based on the power supply from the battery unit 304. When a voltage (negative voltage) is applied to the field electron emission electron source 116 and the power supply unit 120 applies a voltage between the rotating anode 110 and the cathode 114 based on the power supply from the battery unit 304 (rotating anode). When a positive voltage is applied to 110 and a negative voltage is applied to the cathode 114), electrons are emitted from the field electron emission electron source 116, and the emitted electrons are applied between the rotating anode 110 and the cathode 114. It is accelerated by the voltage and collides with the target layer 112. From the electron collision surface (focal point 122) in the target layer 112, radiation 46 corresponding to the collided electrons is output to the outside. As the radiation source 44, a small high-energy X-ray source using crystals such as tourmaline, LiNbO ₃ , LiTaO ₃ , and ZnO shown in Non-Patent Document 2 can be used. In this case, for example, by using LiNbO ₃ with an axial length of 1 cm, a voltage of about 100 kV can be generated.

  Here, when a radiation image is taken by irradiating the subject 50 with the radiation 46, between the focal point 122 of the radiation source 44 and the position 124 (see FIG. 6) of the radiation detector 86 just below the focal point 122. Is set in advance as the distance (SID) between the source image and the image, and the center position of the irradiation range of the radiation 46 on the irradiation surface 20 and the center position 126 of the guide line 22 (crossed in a cross shape). It is necessary to perform a shooting preparation work including a work to match the intersection of the two guide lines 22).

  In this case, as shown in FIGS. 6 and 7, the operator 38 sets the pulling amount of the band member 76 from the measure 72 in accordance with the SID in a state where the radiation source main body 18 is separated from the cassette main body 12. The band member 76 is pulled out until it becomes l1. In addition, the laser pointer 104 projects the laser beam 128 onto the irradiation surface 20 according to the control from the radiation source control unit 102, thereby irradiating the irradiation surface 20 with the radiation 46. Is displayed on the irradiation surface 20 as a cross-shaped mark 130.

In addition, SID≈ is generally between the distance l2 between the position 124 and the center position 126 and the side surface 14a provided with the hole 80 through which the band member 76 is drawn, the amount of withdrawal l1 according to the SID, and the SID. The relationship of (l1 ² + l2 ² ) ^1/2 is established. Further, the distance l2 is constant.

  Therefore, after the band member 76 is pulled out from the measure 72 by the pull-out amount l1, the position of the radiation source body 18 is adjusted so that the position of the mark 130 displayed on the irradiation surface 20 and the center position 126 coincide with each other. Thereafter, as shown in FIG. 8, the radiation 46 is irradiated from the radiation source 44 to the subject 50 disposed on the irradiation surface 20 due to the operator 38 turning on the exposure switch 48, so that the radiation to the subject 50 is irradiated. It is possible to appropriately capture an image. Note that FIG. 8 illustrates a case where the hand of the subject 50 is photographed.

  As schematically shown in FIG. 9, the radiation detector 86 includes a plurality of pixels 132 arranged on a substrate (not shown), a plurality of gate lines 134 for supplying control signals to the pixels 132, and a plurality of gate lines 134. A large number of signal lines 136 for reading out electrical signals output from the pixels 132 are arranged.

  Next, as an example, a circuit configuration of the cassette body 12 when the indirect conversion type radiation detector 86 is employed will be described in detail with reference to FIG.

  The radiation detector 86 has a structure in which a photoelectric conversion layer 138 in which each pixel 132 made of a substance such as a-Si that converts visible light into an electrical signal is formed is arranged on an array of matrix-like TFTs 140. In this case, in each pixel 132, the charge generated by converting visible light into an electrical signal (analog signal) is accumulated, and the charge can be read out as an image signal by sequentially turning on the TFT 140 for each row. .

  The TFT 140 connected to each pixel 132 is connected to a gate line 134 extending in parallel to the row direction and a signal line 136 extending in parallel to the column direction. Each gate line 134 is connected to the line scan driver 142, and each signal line 136 is connected to the multiplexer 144. Control signals Von and Voff for controlling on / off of the TFTs 140 arranged in the row direction are supplied from the line scan driving unit 142 to the gate line 134. In this case, the line scan driving unit 142 includes a plurality of switches SW1 for switching the gate lines 134, and an address decoder 146 that outputs a selection signal for selecting one of the switches SW1. An address signal is supplied from the cassette control unit 92 to the address decoder 146.

  In addition, the charge held in each pixel 132 flows out to the signal line 136 through the TFTs 140 arranged in the column direction. This charge is amplified by the amplifier 148. A multiplexer 144 is connected to the amplifier 148 via a sample and hold circuit 150. The multiplexer 144 includes a plurality of switches SW2 that switches the signal line 136, and an address decoder 152 that outputs a selection signal for selecting one of the switches SW2. An address signal is supplied from the cassette control unit 92 to the address decoder 152. An A / D converter 154 is connected to the multiplexer 144, and the radiographic image converted into a digital signal by the A / D converter 154 is supplied to the cassette control unit 92.

  Note that the TFT 140 functioning as a switching element may be realized in combination with another imaging element such as a CMOS (Complementary Metal-Oxide Semiconductor) image sensor. Furthermore, it can be replaced with a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting them with a shift pulse corresponding to a gate signal referred to as a TFT.

  FIG. 11 is a block diagram of the first radiographic image capturing apparatus 10A.

  In the description of FIG. 11, the description will focus on components that are not described in FIGS. 1 to 10.

  The cassette control unit 92 includes an address signal generation unit 162, an image memory 164, and an SID determination unit (inter-shooting distance determination unit) 168.

  The address signal generator 162 supplies an address signal to the address decoder 146 of the line scan driver 142 and the address decoder 152 of the multiplexer 144. The image memory 164 stores the radiation image detected by the radiation detector 86.

  The SID determination unit 168 uses the current pull-out amount of the band member 76 based on the pull-out amount of the band member 76 from the measure 72 input from the rotary encoder 78 and the distance 12 stored in advance. Is calculated as a distance between the focal point 122 and the position 124 when the lens is placed above the irradiation surface.

  If the calculated inter-shooting distance matches the SID, the SID determination unit 168 sets the pull-out amount of the belt member 76 as the pull-out amount l1 corresponding to the SID, and confirms that the pull-out amount l1 and the inter-shooting distance match the SID. Information to be displayed is displayed on the display unit 36 via the transceivers 94 and 98. A mechanism may be provided that locks the belt member 76 so that the belt member 76 cannot be pulled out any more when the pull-out amount l1 and the inter-photographing distance match the SID. On the other hand, if the calculated inter-photographing distance does not match the SID, the SID determination unit 168 transmits information indicating that the difference between the current pull-out amount and the pull-out amount l1 and the inter-photographing distance does not match the SID to the transceiver 94, The image is displayed on the display unit 36 via 98.

  The SID determination unit 168, the rotary encoder 78, and the measure 72 constitute an inter-shooting distance setting unit 169.

  The cassette control unit 92 can also transmit the ID information of the cassette body 12 and the radiation image stored in the image memory 164 to the portable terminal 42 via wireless communication via the transceiver 94.

  Here, an operation for preparing for imaging using the cassette body 12 and the radiation source body 18 and an operation for actually performing imaging will be described.

  First, the operator 38 prepares for radiography at the site of the transport destination. That is, by operating the operation unit 40 of the mobile terminal 42, shooting conditions such as subject information (for example, SID) related to the subject 50 that is the shooting target are registered.

  In this case, the operator 38 may operate with the mobile terminal 42 removed from the recess 54 or may operate with the mobile terminal 42 mounted on the cassette body 12. In addition, when the imaging region and the imaging method are determined in advance, these imaging conditions are also registered in advance. If the subject 50 to be imaged is known in advance before going to the destination site, subject information may be registered by operating the portable terminal 42 at a medical institution or the like to which the operator 38 belongs.

  In this way, when the operator 38 operates the operation unit 40 of the portable terminal 42, shooting conditions such as subject information related to the subject 50 to be shot are transmitted from the transceiver 98 to the transceiver 94 by wireless communication. And registered in the cassette control unit 92.

  When the operator 38 presses the lock release button 34, the hook portion 64 is displaced toward the side wall 52 d against the elastic force of the spring member 60, so that the engagement state between the hook portion 64 and the hole 66 is released.

  When the operator 38 removes the radiation source body 18 from the cassette body 12 while the engagement state is being released (while the lock release button 34 is being pressed), the connection between the connection terminal 68a and the connection terminal 70a. The combined state and the engaged state between the connection terminal 68b and the connection terminal 70b are both released, and the integral coupling and fixing state between the cassette body 12 and the radiation source body 18 is released.

  The operator 38 performs the setting operation of the inter-imaging distance and the setting operation for matching the mark 130 displayed on the irradiation surface 20 with the center position 126 of the guide line 22, and then the irradiation surface 20 and the radiation source body 18. The subject 50 is placed between the two and the subject 50 is positioned.

  In this case, the operator 38 first moves the radiation source main body 18 and pulls out the band member 76 until the pull-out amount of the band member 76 from the measure 72 becomes the pull-out amount l1 corresponding to the SID.

  There are the following two methods for pulling out the belt member 76 until the pulling amount l1 is reached.

  The first method is a method in which the SID determination unit 168 automatically determines whether or not the withdrawal amount l1 has been reached, and causes the operator 38 to withdraw the belt member 76 until the withdrawal amount l1 according to the SID is reached. .

  In the first method, the rotary encoder 78 detects the pull-out amount of the band member 76, and the SID determination unit 168 uses the current pull-out amount of the band member 76 based on the detected pull-out amount. The distance between the images is calculated between the focal point 122 and the position 124 when 18 is disposed above the irradiation surface 20.

  If the distance between images matches the SID, the SID determination unit 168 transmits information indicating that the belt member 76 is drawn out (the amount of drawing 11) and the distance between images matches the SID via the transceivers 94 and 98. On the other hand, if the distance between shootings does not match the SID, information indicating that the difference between the current pull-out amount and the pull-out amount l1 and the distance between shootings do not match the SID are transmitted and received by the transceiver 94. , 98 to display on the display unit 36.

  Therefore, according to the first method, the operator 38 only has to pull out the belt member 76 from the measure 72 in accordance with the display content of the display unit 36, so that the setting operation of the distance between photographing can be easily performed.

  The second method is a method in which the operator 38 pulls out the band member 76 from the measure 72 until the pull-out amount l1 is reached while looking at the scale 74 when the pull-out amount l1 is known in advance.

  In this way, after the belt member 76 is pulled out until the pulling amount l1 corresponding to the SID is reached, the operator 38 moves the radiation source main body 18 so as to face the irradiation surface 20.

  At this time, the laser pointer 104 is controlled so that the laser beam 128 is projected onto the irradiation surface 20. Thereby, the center position of the irradiation range of the radiation 46 when the radiation 46 is irradiated onto the irradiation surface 20 is displayed as a cross-shaped mark 130 on the irradiation surface 20. As a result, the operator 38 adjusts the position of the radiation source main body 18 so that the position of the mark 130 and the center position 126 coincide.

  Thus, after adjusting the position of the radiation source main body 18 so that the position of the mark 130 and the center position 126 coincide with each other, the operator 38 determines that the center of the imaging region of the subject 50 is the center position 126 (of the mark 130). The subject 50 is arranged (positioned) on the irradiation surface 20 so as to coincide with the (position).

  The radiation source body 18 is fixed at the adjusted position by a holding member (not shown) after the above-described position adjustment is performed.

  Also, in disaster sites, etc., it may not be possible to shoot with a desired SID, such as shooting in a narrow place. At that time, based on a newly determined SID (new SID) different from the desired, the shooting conditions are recalculated. The image data may be saved together with the new SID, or the new SID and / or the recalculated imaging condition may be transmitted to a data center (medical institution, etc.) via the network and confirmed. Good.

  After positioning the subject 50, the operator 38 operates the exposure switch 48 to start photographing the subject 50.

  Due to the operation of the exposure switch 48, the radiation source control unit 102 requests the cassette control unit 92 to transmit an imaging condition by wireless communication, and the cassette control unit 92 is based on the received request. Then, the imaging condition (control signal) relating to the imaging region of the subject 50 is transmitted to the radiation source main body 18. When the radiation source control unit 102 receives the imaging condition, the radiation source control unit 102 stops the projection of the laser beam 128 by the laser pointer 104, and in accordance with the imaging condition, the radiation source 46 is irradiated with radiation 46 having a predetermined dose. The source 44 is controlled.

  Thereby, in the radiation source 44, the rotation mechanism 106 rotates the rotation shaft 108 and the rotation anode 110 according to the control from the radiation source control unit 102, while the power source unit 118 is based on the power supply from the battery unit 304. In addition, a negative voltage is applied to the field electron emission type electron source 116, and the power source unit 120 applies a voltage between the rotating anode 110 and the cathode 114 based on the power supply from the battery unit 304. The electrons emitted from the electron source 116 are accelerated by the voltage applied between the rotating anode 110 and the cathode 114 and collide with the target layer 112. From the electron collision surface (focal point 122) of the target layer 112, Radiation 46 corresponding to the collided electrons is output to the outside.

  When the subject 50 is irradiated with the radiation 46 for a predetermined irradiation time based on the imaging conditions, the radiation 46 passes through the subject 50 and reaches the radiation detector 86 in the cassette body 12.

  When the radiation detector 86 is an indirect conversion type radiation detector, the scintillator constituting the radiation detector 86 emits visible light having an intensity corresponding to the intensity of the radiation 46 to constitute the photoelectric conversion layer 138. Each pixel 132 converts visible light into an electrical signal and accumulates it as a charge. Next, the charge information, which is the radiation image of the subject 50 held in each pixel 132, is read according to the address signal supplied from the address signal generator 162 constituting the cassette controller 92 to the line scan driver 142 and the multiplexer 144. .

  That is, the address decoder 146 of the line scan driver 142 outputs a selection signal according to the address signal supplied from the address signal generator 162 to select one of the switches SW1, and the TFT 140 connected to the corresponding gate line 134. A control signal Von is supplied to the gates of the first and second gates. On the other hand, the address decoder 152 of the multiplexer 144 outputs a selection signal in accordance with the address signal supplied from the address signal generation unit 162, sequentially switches the switch SW2, and is connected to the gate line 134 selected by the line scan driving unit 142. The radiographic image as the charge information held in each pixel 132 is sequentially read out via the signal line 136.

  The radiation image read out from each pixel 132 connected to the selected gate line 134 is amplified by each amplifier 148, sampled by each sample hold circuit 150, and then A / D converter via the multiplexer 144. 154 to be converted into a digital signal. The radiographic image converted into the digital signal is temporarily stored in the image memory 164 of the cassette control unit 92.

  Similarly, the address decoder 146 of the line scan driver 142 sequentially switches the switch SW1 in accordance with the address signal supplied from the address signal generator 162, and the charge held in each pixel 132 connected to each gate line 134. A radiation image as information is read out via the signal line 136 and stored in the image memory 164 of the cassette control unit 92 via the multiplexer 144 and the A / D converter 154.

  The radiographic image stored in the image memory 164 is transmitted to the mobile terminal 42 by wireless communication via the transceiver 94, and the mobile terminal 42 displays the received radiographic image on the display unit 36 as shown in FIG. Let Thus, the operator 38 can grasp whether or not the imaging of the imaging region of the subject 50 has been appropriately performed by confirming the radiation image displayed on the display unit 36.

  For example, when a radiographic image that does not fit in the imaging region is displayed in the imaging region, the operator 38 determines that the current imaging was not properly performed, and executes the imaging for the subject 50 again. At this time, the operator 38 uses the portable terminal 42 to add and update the number of times of photographing under the photographing condition by the number of times of re-taking.

  Note that the radiographic image displayed on the display unit 36 may be an image that can be used to determine whether or not the current imaging is appropriate, and thus may be a radiographic image stored in the image memory 164 or low data. Or an image processed to a relatively low resolution.

  As shown in FIG. 14, the battery control unit 306 includes a memory 330, a power supply activation unit 336 that activates the power control unit 334 in accordance with the supply timing condition, and each device or wireless power supply connected by wire. A power control unit 334 that supplies power between the batteries 308 (see FIG. 13) in each device that is in a possible area (also referred to as wireless connection), and a power control unit 334 only during the period of shooting. A power supply restriction unit (in-shooting instruction unit) 338 that restricts the power supply operation by, and a pause processing unit 340 that temporarily stops the power control unit 334 when necessary shooting is completed or when power supply is completed. And have. The memory 330 stores ID information for specifying devices (such as the cassette body 12 and the radiation source body 18) in which the battery controller 306 is incorporated, and various conditions. The memory 330 also temporarily stores various table information input via the network, the portable terminal 42, and the like.

  The power supply activation unit 336 is activated when the power is turned on. If the supply timing condition recorded in the memory 330 is not regulated, the power supply switch is operated based on the operation of the power supply switch. The power supply activation unit 336 of the device activates the corresponding power control unit 334. Of course, the power control unit 334 may be activated without waiting for the operation of the power supply switch. In this case, if no interlock processing is performed, the power control units 334 of all the devices that are turned on are activated, and the processing operations may interfere with each other. The activation unit 336 refers to the interlock information registered in the memory 330 (the ID of the radiation source main body 18 or the cassette main body 12 used for imaging, which is set in advance), and is the same as the ID of the interlock information. Only the power supply activation unit 336 of the ID device activates the corresponding power control unit 334. As a result, only the power control unit of the radiation source main body unit 18 used for imaging, for example, operates and does not receive interference from other devices.

  On the other hand, if the supply timing condition is supply before shooting, the power control unit 334 is activated based on the input of shooting conditions (order) from the mobile terminal 42. In this case, only the power supply activation unit 336 of the device having the same ID as that of the radiation source main body 18 or the cassette main body 12 used for imaging registered in the imaging conditions in advance has the corresponding power control unit 334. to start. If the supply timing condition is supply after shooting, the power control unit 334 is activated based on the input of the shooting completion signal from the shooting completion determination unit 386 (see FIG. 15). Also in this case, only the power supply activation unit 336 of the device having the same ID as the ID of the radiation source main body 18 or the cassette main body 12 used for imaging registered in the imaging conditions in advance activates the corresponding power control unit 334. To do.

  The power control unit 334 has, for example, two specific examples. In the first specific example, as shown in FIG. 15, power is supplied from the battery 308 of the radiation source main body 18 to the battery 308 of the cassette main body 12 or radiation. This is an example of controlling power supply from the battery 308 of the source body 18 to the battery 308 of the cassette body 12. The device connection detection unit 360, the cassette selection activation unit 362, the cassette selection unit 364, and the integrated supply activation unit 366 , Integrated supply unit 368, power supply path setting unit 370, power supply amount setting unit 372, power supply control unit 374, remaining amount detection unit 376, photographing interruption instruction unit 378, counter 380, and resupply An instruction unit 382, a photographing permission instruction unit 384, a photographing completion determination unit 386, and a power supply completion output unit 388 are included.

  The second specific example is an example in which power supply control is performed between connected devices so that the remaining amount of the battery 308 in each device is interchanged based on preset charging conditions, imaging conditions, and the like. In addition to the various function units described above, the power management unit 390 and associated function units (remaining amount prediction update unit 392, use history update unit 394, remaining amount information transfer unit 396, use history transfer unit 398) are included.

Here, “compatible with the remaining amount” means at least the following aspects.
(1) Power is supplied from one or more devices having a remaining battery level to a device whose remaining battery level (power) is less than that required for shooting.
(2) Supply electric power necessary for photographing from one or more devices not used for photographing to the device used for photographing.
(3) Power is supplied from one or more devices not used for shooting to the device used for shooting, and at least the remaining battery level (power) of the device, that is, the power held by the device is shot. The power required for

  As shown in FIG. 14, the power control unit 334 limits the power supply over the input period of the supply restriction signal from the power supply restriction unit 338. Here, the limitation of power supply refers to stopping power supply, reducing the supply amount per unit time, or controlling power supply in stages. As the stop of power supply, for example, a stop signal is output to the power supply control unit 374, and the power supply control unit 374 sets, for example, the first switching unit 314a to the fifth switching unit 314e to neutral positions (not input or output). (Position) may be relay-controlled. As the reduction of the power supply amount, for example, a supply amount reduction signal is output to the power supply control unit 374 so that the power supply control unit 374 reduces the power supply amount per unit time to a preset value. You may make it control. As step-by-step control of power supply, for example, as will be described later, power supply is stopped during pixel accumulation and AD conversion in the cassette body 12, but weak power supply is performed during data transfer, and data transfer is completed. A strong power supply can be mentioned when idling. Further, the power control unit 334 stops the power supply control based on the input of the temporary stop signal from the temporary stop processing unit 340 and waits for the next startup from the power supply starting unit 336.

  First, in the first specific example, as shown in FIG. 13, for example, the device connection detection unit 360 is connected to at least one of the first energy input / output unit 300 and the second energy input / output unit 302 with the device (radiation source main unit 18 or It detects whether the cassette body 12) is wired or wirelessly connected. The wireless connection is detected by, for example, an apparatus (radiation source main body 18 or cassette main body) in an area where wireless power can be supplied from the first energy input / output unit 300 or the second energy input / output unit 302 by an obstacle sensor (ultrasonic sensor or the like). Part 12) is detected.

  As shown in FIG. 17, the cassette selection activation unit 362 has only a power supply from the cassette body 12 to the radiation source body 18 among the charging conditions recorded in the memory 330. When the apparatus is the radiation source body 18 and the connection of the plurality of cassette bodies 12 is detected, the cassette selection unit 364 is activated.

  The cassette selection unit 364 includes a cassette ID acquisition unit 400, a cassette information acquisition unit 402, and a selection unit 404.

  The cassette ID acquisition unit 400 makes an ID transfer request to the plurality of cassette main body units 12 connected to the radiation source main body unit 18. Each cassette body 12 outputs an ID to the radiation source body 18 based on the transfer request, and therefore acquires the input ID and registers it in the memory 330.

  The cassette information acquisition unit 402 acquires a cassette information table (information such as defective pixels) and a usage history table corresponding to the ID via a network.

  Based on the selection conditions stored in the memory 330 and the acquired cassette information table and usage history table, the selection unit 404 selects a cassette body 12 that meets the selection conditions from the plurality of cassette body 12. . The ID of the selected cassette body 12 is output to the power supply path setting unit 370.

  The selection conditions include the following conditions.

(1-a) Large cassette body 12
This is intended to discharge power from the large cassette body 12 in a special environment where a large size is not used. The size determination is based on the size information recorded in the cassette information table.

(1-b) Small cassette body 12
The purpose of this is to preferentially release power from the cassette body 12 having less versatility.

(1-c) The cassette body 12 having a large number of defective pixels
The purpose of this is to prevent the plurality of cassette main body portions 12 from being used almost simultaneously by preferentially discharging power from the cassette main body portion 12 that is deteriorated and used less frequently. The determination of the number of defective pixels is based on information regarding defective pixels recorded in the cassette information table. Note that information regarding defective pixels in the cassette information table is updated regularly or irregularly, for example, in calibration or the like.

(1-d) The cassette body 12 having a small shootable area
The size of the imageable area is calculated from information related to the defective pixel recorded in the cassette information table, particularly the position information of the defective pixel.

(1-e) The cassette body 12 having a large degree of deterioration of the battery 308
The determination of the degree of deterioration of the battery 308 is based on the number of uses of the cassette body 12 recorded in the use history table.

(1-f) The cassette body 12 with a small degree of deterioration of the battery 308

(1-g) Cassette body 12 having a large number of uses
The determination of the number of uses is based on the number of uses of the cassette body 12 recorded in the use history table or the information on the cumulative exposure dose recorded in the cassette information table.

(1-h) The cassette body 12 with a small amount of internal memory remaining
The determination of the remaining amount of the built-in memory is based on the return result from the cassette control unit 92 by outputting an inquiry about the remaining amount of memory to the cassette control unit 92.

(1-i) The cassette body 12 close to the radiation source body 18 in terms of distance.
The purpose of this is to reduce the burden on the circuit system by selecting the cassette body 12 that can easily supply power in terms of distance.

  The determination of the distance from the radiation source main body 18 to the cassette main body 12 is based on information on each current position by GPS and distance information from a distance measuring sensor (ultrasonic sensor, three-dimensional magnetic sensor, etc.).

  Next, as shown in FIG. 18, the integrated supply activation unit 366 has only a power supply from the plurality of cassette main body parts 12 to the radiation source main body part 18 among the charging conditions recorded in the memory 330. If the apparatus is the radiation source main body 18 and the connection of the plurality of cassette main bodies 12 is detected, the integrated supply unit 368 is activated.

  The accumulation supply unit 368 includes a cassette ID acquisition unit 400, a cassette information acquisition unit 402, and a weight setting unit 406.

  The cassette ID acquisition unit 400 makes an ID transfer request to the plurality of cassette main body units 12 connected to the radiation source main body unit 18. Each cassette body 12 outputs an ID to the radiation source body 18 based on the transfer request, and therefore acquires a plurality of input IDs and registers them in the memory 330.

  The cassette information acquisition unit 402 acquires a cassette information table (information such as defective pixels) and a use history table corresponding to the acquired plurality of IDs via the network.

  The weighting setting unit 406 weights (coefficients) the amount of power supplied from the plurality of cassette main body units 12 to the radiation source main body unit 18 based on the accumulation conditions, the cassette information table, and the usage history table stored in the memory 330. ) Is set. The set coefficient is output to the power supply amount setting unit 372 together with the corresponding ID information.

  The following conditions are mentioned as accumulation conditions.

(2-a) The power supply amount is distributed according to the small number of defective pixels.

  The coefficient is set such that the power supply amount increases as the number of defective pixels increases, and the coefficient decreases as the power supply amount decreases.

(2-b) The power supply amount is distributed according to the small and large imageable area.

  The coefficient is set such that the power supply amount increases as the shootable area decreases, and the coefficient decreases as the power supply amount decreases.

(2-c) The power supply amount is distributed according to whether the degree of deterioration of the battery 308 is large or small.

  The coefficient is set such that the power supply amount increases as the degree of deterioration of the battery 308 increases, and the coefficient is set such that the power supply amount decreases as the battery 308 decreases.

(2-d) The power supply amount is distributed according to the small number of use.

  The coefficient is set so that the power supply amount increases as the number of uses increases, and the coefficient is set such that the power supply amount decreases as the number of uses decreases.

(2-e) The power supply amount is distributed according to the small amount of the internal memory remaining.

  The coefficient is set such that the power supply amount increases as the remaining memory amount decreases, and the coefficient is set such that the power supply amount decreases as the memory remaining amount increases.

(2-f) The power supply amount is distributed according to the distance from the radiation source main body 18 that is close to the distance.

  The coefficient is set such that the power supply amount increases as the distance is shorter, and the coefficient is set such that the power supply amount decreases as the distance increases.

  Next, the power supply path setting unit 370 sets a power supply path based on the conditions related to the path among the charging conditions recorded in the memory 330. For example, it is a path from the radiation source body 18 to the cassette body 12 or a path from the cassette body 12 to the radiation source body 18. When the corresponding ID is supplied from the cassette selection unit 364, the path from the cassette body 12 corresponding to the ID to the radiation source body 18 is set. When a plurality of IDs are supplied from the accumulation supply unit 368, the path from the cassette body 12 to the radiation source body 18 corresponding to these IDs is set. The set route information is displayed on the portable terminal 42. The condition regarding the route is that at least the power supply source is described. If the supply source is the radiation source main body 18, power is supplied from the radiation source main body 18 to the cassette main body 12, and the supply source is the cassette main body. In the case of the unit 12, power is supplied from the cassette body 12 to the radiation source body 18. This condition can be arbitrarily changed by the portable terminal 42. In the case of a resupply instruction from a resupply instruction unit 382 described later (input of a resupply instruction signal from the resupply instruction unit 382), a power supply path is set based on the charging conditions. When the operator 38 performs additional charging of other equipment (radiation source main body 18 or cassette main body 12), the power supply path of the other equipment (radiation source main body 18 or cassette used for imaging from other equipment). The supply path to the main body 12 or the supply path from the radiation source main body 18 or the cassette main body 12 used for imaging to other devices) and the amount of power are input. Based on the set supply path, a supply source instruction signal or a supply destination instruction signal is output from the power supply path setting unit 370 to the power supply control unit 374 of each device.

  The power supply amount setting unit 372 sets the amount of power to be supplied based on the condition relating to the supply amount among the charging conditions. The charging conditions related to the supply amount include items such as at least full charge and supply amount necessary for photographing one image, and the currently selected item is applied. Items to be applied can be arbitrarily selected by the mobile terminal 42. In addition, the amount of power to be supplied can be set as a numerical value on the mobile terminal 42. In addition, when coefficients corresponding to a plurality of IDs are supplied from the integrated supply unit 368, the amount of power supplied to the radiation source main unit 18 from the plurality of cassette main units 12 by multiplying the supplied power by the coefficient, respectively. Set. Furthermore, in the case of a resupply instruction from the resupply instruction unit 382, the amount of power to be supplied is set based on the condition relating to the supply amount among the charging conditions. This amount of power can be arbitrarily changed by the portable terminal 42. If there is an input for additional charging, the amount of power is also set. The set supply amount is supplied to the power supply control unit 374 of the corresponding device.

  As illustrated in FIG. 13, the power supply control unit 374 controls the battery 308 to output power when the supply source instruction signal is input. When the supply destination instruction signal is input, the battery 308 is controlled to input power. Based on the remaining amount from the remaining amount detection unit 376, control is performed so that power is supplied to the battery 308 or supplied from the battery 308 at a constant charge rate (or discharge rate). If the amount of power supplied is small, rapid charging (discharging) is also possible. If the remaining battery level is an amount of power that cannot be used for shooting one image, a non-shooting signal including the amount of power and the ID of the device is output. When the supply of power to the battery 308 or the output of power from the battery 308 is completed, a supply end signal is output.

  As described above, the remaining amount detection unit 376 detects the remaining amount of the battery 308 and notifies the power supply control unit 374 of the detection result.

  The imaging interruption instruction unit 378 shown in FIG. 15 outputs a message indicating interruption of imaging to the portable terminal 42 based on the input of the imaging impossible signal.

  The counter 380 counts the number of operations of the exposure switch 48. The count value is reset (count value = 0) based on the input of the shooting completion signal from the shooting completion determination unit 386.

  The resupply instruction unit 382 receives the resupply instruction signal including the current count value of the counter 380, the amount of power included in the noncapturing signal, and the ID of the device based on the input of the noncapturing signal. The data is output to the setting unit 370, the power supply amount setting unit 372, and a power management unit 390 described later. In the case of supply after imaging, since the power control unit 334 itself is not activated, the resupply instruction unit 382 of the radiation source main body 18 or the cassette main body 12 used for imaging corresponds to the corresponding power for emergency use. The supply path setting unit 370, the power supply amount setting unit 372, and the power management unit 390 are activated by interruption.

  When the supply timing condition recorded in the memory 330 is unregulated or supply before shooting, the shooting permission instructing unit 384 receives supply end signals from the power supply control units 374 of all the devices that supply power. Based on the input, a message indicating permission of photographing is output to the portable terminal 42.

  The shooting completion determination unit 386 compares the number of shootings under the shooting conditions with the count value of the counter 380, and outputs a shooting completion signal when the count value becomes the same as the number of shootings.

  The power supply completion output unit 388 outputs a power supply completion signal based on the input of the supply end signal from the power supply control unit 374 of all the devices that are supplying power.

  The power supply restriction unit 338 in FIG. 14 performs radiographic imaging on the subject 50 if the condition of “power supply is stopped during imaging” is included in the supply timing conditions recorded in the memory 330. Whether or not shooting is in progress (ie, whether or not shooting is in progress) is determined. If shooting is in progress, a supply restriction signal is output over that period. Specifically, the supply limit signal is output when the exposure switch 48 is operated, and the output of the supply limit signal is stopped when a predetermined time has elapsed. The power control unit 334 stops the power supply control over a period during which the supply restriction signal is input, or reduces the amount of power per unit time.

  As a period during which the supply restriction signal is output, the radiation 46 transmitted through the subject 50 is irradiated to the radiation detector 86 and converted into visible light by a scintillator (not shown), and the visible light is converted into an electrical signal by each pixel 132. Thereafter, a period (accumulation period) in which the electric charge (signal charge) is accumulated, a period in which the accumulated electric charge is read (reading period), and the read electric charge (analog signal) is converted into a digital signal by the A / D converter 154 Among the periods (conversion period to digital signal) to be converted into the period, any period, a period combining each period, or a period including all periods is preferable. This is because the influence of noise superposition on the image signal (radiation image information) is particularly remarkable in these three periods. That is, in the accumulation period and the reading period, the influence of noise is large because the charge is very small, and in the conversion period to the digital signal, the analog signal is less resistant to noise than the digital signal before A / D conversion. This is because noise that is a signal and superimposed on the analog signal is easily converted into a digital signal and appears in image data.

  In this case, a part of the accumulation period includes a time for exposing the radiation 46 from the radiation source 44. In other words, the operation after the reading should be performed immediately after the accumulation is started, the exposure is started at the earliest possible timing, the exposure is stopped, and the time lag in each of these operations is made as much as possible. If it is reduced, it is suitable for suppressing so-called dark current, and the quality of the obtained radiographic image can be further improved. In addition, the reading period is a period in which the TFT 140 is turned on and a signal flows to the A / D converter 154 via each amplifier 148 and the like. The reading period and the conversion period to the digital signal are time axes. In practice, the reading period (starting) actually occurs slightly earlier.

  Therefore, the output period of the supply restriction signal is from the time when the supply restriction signal is output until at least the irradiation of the radiation 46 by the radiation source main body 18 is completed, and more preferably during the period during which the above imaging is determined. If it is implemented, the detection of the radiation 46 by the cassette body 12 can be performed with high quality. Further, a predicted time required for radiographic image capturing or display may be set in advance, and this predicted time may be used as the output period of the supply restriction signal. In addition, the degree of reduction in the amount of power per unit time is determined in advance by experiments or the like to such an extent that noise is not superimposed on the radiographic image, or noise can be suppressed to such an extent that noise does not affect the image quality of the radiographic image. It is preferable to set based on the experimental result.

  If the supply timing condition recorded in the memory 330 is no timing restriction or supply before shooting, the temporary stop processing unit 340 in FIG. 14 performs power control based on the input of the shooting completion signal from the shooting completion determination unit 386. A pause signal is output to the unit 334. If the supply timing condition is post-imaging supply, a temporary stop signal is output to the power control unit 334 based on the input of the power supply completion signal from the power supply completion output unit 388.

  On the other hand, in the second specific example, the power management unit 390 of FIG. 16 interchanges the remaining amount of the battery 308 in each device based on the preset charging conditions, photographing conditions, and the like between the connected devices. Thus, information for controlling the power supply is provided to the power supply control unit 374. The power management unit 390 is incorporated in the radiation source main body 18 and / or the cassette main body 12. As illustrated in FIG. 19, the power management unit 390 includes an ID acquisition unit 410, various information acquisition units 412, a power consumption amount prediction unit 414, and an information update unit 416.

  The ID acquisition unit 410 makes a request for ID transfer to a device in which the power management unit 390 is incorporated and other devices connected to the device. Each device outputs an ID to the power management unit 390 based on the transfer request, so that the input ID is acquired and registered in the memory 330. In addition to the radiation source main body 18 and the cassette main body 12 used for imaging, if the other radiation source main body 18 or the cassette main body 12 is connected (or in a wireless power supply area), the other The ID of the radiation source body 18 or the cassette body 12 is also acquired.

  The various information acquisition unit 412 uses the current or previous shooting conditions (input via the mobile terminal 42 or the network), the remaining amount information table corresponding to the ID, the previous shooting conditions corresponding to the ID, and the use corresponding to the ID. A history table is acquired and stored in the memory 330.

  The power consumption prediction unit 414 consumes the radiation source main body 18 and the cassette main body 12 used for imaging based on the charging conditions (previously stored in the memory 330) and the current or previous imaging conditions (number of imaging, mAs value, etc.). The amount of electric power is calculated, and the usage history (coefficient corresponding to the number of times of use) is multiplied and corrected, and the amount of electric power consumed by the current imaging unit 18 and the cassette body unit 12 or the previous imaging. Each power amount of the radiation source main body 18 and the cassette main body 12 that would have been consumed is predicted. When a resupply instruction signal is input from the resupply instruction unit 382, the amount of shooting that has already been completed out of the charging conditions (previously stored in the memory 330) and the current shooting conditions (number of shots, mAs value, etc.) From the imaging conditions (imaging conditions for imaging to be performed in the future) excluding the imaging value indicated by the count value), the power consumption amount of the device (radiation source main body 18 or cassette main body 12 to be resupplied) is determined. Then, the power consumption of the device with the ID to be consumed in the future shooting is predicted by multiplying and correcting the usage history (coefficient corresponding to the number of times of use).

  In the remaining amount information table, the information update unit 416 subtracts the remaining amount of the device that is the power supply source by the supplied power amount, and adds the remaining amount of the device that is the power supply destination by the supplied power amount. In the case of a resupply instruction from the resupply instruction unit 382, only the remaining amount of the device with the ID is changed. A value obtained by adding the current supply amount to the power amount included in the resupply instruction signal is recorded. Since this value reflects the amount of power from the power supply control unit 374, the remaining amount error due to the predicted value alone is corrected at this stage.

  In the second specific example, since the power management unit 390 exists, the operations of the power supply path setting unit 370 and the power supply amount setting unit 372 are different from those in the first specific example.

  That is, the power supply path setting unit 370 in the second specific example sets the power supply path based on the predicted power amount and the remaining battery levels (remaining capacity information table) of the radiation source main body 18 and the cassette main body 12. To do. As a typical example, a route for supplying electric power to a device that has almost no remaining battery charge is set. This information is displayed on the mobile terminal 42. In the case of a resupply instruction from the resupply instruction unit 382, a path through which power is supplied to the device with the ID is set. When the operator 38 performs additional supply using other equipment (the radiation source main body 18 or the cassette main body 12 that is not used for imaging), the power supply path of other equipment (supply from the other equipment to the equipment with the ID) Route) and electric energy. When the operator 38 performs additional charging using other equipment (radiation source body 18 or cassette body 12), the power supply path of the other equipment (radiation source body 18 used for imaging from other equipment). Alternatively, the supply path to the cassette body 12 or the radiation source body 18 used for imaging or the supply path from the cassette body 12 to other devices), the amount of power, and the order of supply are input. Based on the set supply path, a supply source instruction signal or a supply destination instruction signal is output from the power supply path setting unit 370 to the power supply control unit 374 of each device.

  The power supply amount setting unit 372 in the second specific example sets the power amount to be supplied based on the predicted power amount and the remaining battery power (residual amount information table) of the radiation source main body 18 and the cassette main body 12. . As a result, the maximum predicted amount of power is supplied to a device that has almost no remaining battery charge in the current shooting. It may be 1/2 or 1/3 of the predicted power amount. This information is displayed on the mobile terminal 42. This amount of power can be arbitrarily changed by the portable terminal 42. If there is an input for additional charging, the amount of power is also set. It should be noted that the power supply predicted based on the previous shooting condition complements the power consumed in the previous shooting. In the case of a resupply instruction from the resupply instruction unit 382, the predicted electric energy is set. The set power amount can be arbitrarily changed by the portable terminal 42. If there is an input for additional charging, the amount of power is also set. The set supply amount is supplied to the power supply control unit 374 of the corresponding device.

  Among the functional units attached to the power management unit 390, the remaining amount prediction update unit 392 in FIG. 16 functions when the supply timing condition recorded in the memory 330 is supply before photographing, and operates the exposure switch 48. Each time, the remaining battery level (the remaining battery levels of the radiation source main unit 18 and the cassette main unit 12 performing imaging) is updated by subtraction. For the radiation source main body 18 and the cassette main body 12 performing imaging, the power consumption for each imaging is calculated based on the imaging conditions and the usage history table, and recorded in the remaining amount information table. Subtract from the remaining battery power of the radiation source body 18 and the cassette body 12.

  The use history update unit 394 adds the number of operations of the exposure switch 48 to the number of uses recorded in the use history table (the number of uses of the radiation source main body 18 and the cassette main body 12 performing imaging).

  When the supply timing condition recorded in the memory 330 is supply before shooting, the remaining amount information transfer unit 396 in FIG. 16 is based on the input of the shooting completion signal from the shooting completion determination unit 386 and the remaining amount information table. Is transferred to the database of the medical institution via the network and updated. In the case of supply after imaging, based on the input of the power supply completion signal from the power supply completion output unit 388, the remaining amount information table is transferred to the database of the medical institution via the network and updated.

  When the supply timing condition recorded in the memory 330 is supply before shooting, the use history transfer unit 398 updates the use history table via the network based on the input of the shooting completion signal from the shooting completion determination unit 386. Transfer and update to the medical institution database. In the case of supply after imaging, based on the input of the power supply completion signal from the power supply completion output unit 388, the usage history table is transferred to the database of the medical institution via the network and updated.

  10 A of 1st radiographic imaging apparatuses are fundamentally comprised as mentioned above, Next, the operation | movement is demonstrated, also referring the flowchart of FIGS. 20-26.

  First, an operation in the case where the supply timing condition is no timing restriction will be described with reference to the flowcharts of FIGS.

  First, in step S1, the power supply activation unit 336 activates the power control unit 334 based on the operation input of the power supply switch. Of course, the power control unit 334 may be activated without waiting for the operation of the power supply switch. In this case, referring to the interlock information registered in the memory 330 (the ID of the radiation source main body 18 or the cassette main body 12 used for imaging, which is set in advance), the ID of the same ID as the interlock information ID Only the power supply activation unit 336 of the device activates the corresponding power control unit 334.

  In step S <b> 2, the device connection detection unit 360 detects whether or not a device (the radiation source body 18 or the cassette body 12) is connected to the first energy input / output unit 300 or the second energy input / output unit 302.

  At the detected stage, the process proceeds to the next step S3, and the cassette selection activation unit 362 determines whether or not the condition is for activating the cassette selection unit 364. That is, among the charging conditions recorded in the memory 330, the condition regarding the path is only power supply from one cassette body 12 to the radiation source body 18, and the device is the radiation source body 18. When the connection of the plurality of cassette main body sections 12 is detected, the cassette selecting section 364 is activated.

  In step S4, the cassette selection unit 364, the plurality of IDs acquired by the cassette ID acquisition unit 400, the selection conditions stored in the memory 330, the cassette information table acquired by the cassette information acquisition unit 402, and the use history Based on the table, the cassette body 12 that meets the selection condition is selected from the plurality of cassette bodies 12. The ID of the selected cassette body 12 is output to the power supply path setting unit 370.

  When the processing in step S4 is completed, or when it is determined in step S3 that the cassette selection unit 364 is not activated, the process proceeds to step S5, where the accumulation supply activation unit 366 activates the accumulation supply unit 368. It is determined whether or not. That is, among the charging conditions recorded in the memory 330, the condition relating to the path is only power supply from the plurality of cassette body parts 12 to the radiation source body part 18, and the device is the radiation source body part 18. When the connection of the plurality of cassette body parts 12 is detected, the integrated supply part 368 is activated.

  In step S6, the accumulation supply unit 368 determines the plurality of IDs acquired by the cassette ID acquisition unit 400, the accumulation conditions stored in the memory 330, the cassette information table acquired by the cassette information acquisition unit 402, and the use history. Based on the table, the weight (coefficient) of the amount of power supplied from the plurality of cassette main body portions 12 to the radiation source main body portion 18 is set. The set coefficient is output to the power supply amount setting unit 372 together with the corresponding ID information.

  When the process in step S6 is completed, or when it is determined in step S5 that the condition is not the condition for starting the integrated supply unit 368, the process proceeds to step S7, and the power supply path setting unit 370 stores the charge recorded in the memory 330. Among the conditions, a power supply route is set based on a route-related condition. For example, a supply path from the radiation source body 18 to the cassette body 12 or a supply path from the cassette body 12 to the radiation source body 18 is set. In addition, when the corresponding ID is supplied from the cassette selection unit 364, the power supply path setting unit 370 sets the path from the cassette body 12 to the radiation source body 18 corresponding to the ID, and the integrated supply unit When a plurality of IDs are supplied from 368, a route from the cassette body 12 to the radiation source body 18 corresponding to these IDs is set. Thereafter, the power supply path setting unit 370 outputs the set supply path information (path information) to the power supply control unit 374. Specifically, a supply source instruction signal and a supply destination instruction signal are output to the power supply control unit 374 of each device based on the set supply path. For example, assuming that the first energy input / output unit 300 of the radiation source main body 18 is connected to the first energy input / output unit 300 of the cassette main body 12, the radiation source main body 18 to the cassette main body 12 is connected. If it is a supply path, a supply source instruction signal is output to the power supply control unit 374 of the radiation source main body 18, and a supply destination instruction signal is output to the power supply control unit 374 of the cassette main body 12. If the supply path is from the cassette body 12 to the radiation source body 18, a supply destination instruction signal is output to the power supply controller 374 of the radiation source body 18 and supplied to the power supply controller 374 of the cassette body 12. The original instruction signal is output.

  In step S <b> 8, the power supply amount setting unit 372 sets the amount of power to be supplied (supply power amount) based on the condition related to the supply amount among the charging conditions. For example, the amount of power supply required for full charge or one image is set. In addition, when the power supply amount setting unit 372 is supplied with coefficients corresponding to a plurality of IDs from the integrated supply unit 368, the power supply amount setting unit 372 multiplies the supply power by a coefficient, and the plurality of cassette main body units 12 outputs the radiation source. The amount of power supplied to the main body 18 is set. The power supply amount setting unit 372 outputs information on the set power supply amount to the power supply control unit 374 of the corresponding device.

  In step S9, the power supply control unit 374 controls to output power to the battery 308 when the supply source instruction signal is input, and to the battery 308 when the supply destination instruction signal is input. In contrast, control is performed so that power is input. Then, when the supply of power to the battery 308 or the output of power from the battery 308 is completed, a supply end signal is output.

  In step S10, the power supply completion output unit 388 outputs a power supply completion signal based on the input of the supply end signal from the power supply control unit 374 of all the devices that are supplying power.

  In step S <b> 11, the photographing permission instruction unit 384 outputs a message indicating photographing permission to the portable terminal 42 based on the input of the power supply completion signal from the power supply completion output unit 388.

  In step S <b> 12, the operator 38 prepares for radiation imaging at the destination site. Since the preparation for photographing has been described in detail, the description thereof is omitted here.

  When the subject 50 is positioned in preparation for photographing, the process proceeds to step S13 in FIG. 21, and the operator 38 operates the exposure switch 48 to start photographing the subject 50. At this time, the counter 380 updates the count value by +1.

  Further, when the exposure switch 48 is operated in step S13 described above, in step S14, the power supply restriction unit 338 outputs a supply restriction signal to the power control unit 334 over the predetermined period described above. The power control unit 334 temporarily interrupts the power supply operation over a period during which the supply restriction signal is input.

  Next, in step S15, it is determined whether or not resupply of power is necessary. This determination is made based on whether or not an imaging impossible signal is output from the power supply control unit 374 of any device. That is, if the battery remaining amount of the radiation source main body 18 or the cassette main body 12 is an amount of power that cannot be imaged for one sheet, the imaging impossible signal is sent to the resupply instruction unit 382 including the amount of power and the ID of the device. Is required to supply power again.

  If re-supply is necessary, the process proceeds to step S <b> 16, and the shooting interruption instruction unit 378 outputs a message indicating the interruption of shooting to the mobile terminal 42. A message indicating interruption of shooting is displayed on the display screen of the portable terminal 42, and preferably an alarm is output as a sound to prompt the operator 38 to stop shooting.

  Thereafter, in step S <b> 17, the resupply instruction unit 382 outputs a resupply instruction signal to the power supply path setting unit 370 and the power supply amount setting unit 372.

  In step S18, the power supply path setting unit 370 sets a path for resupplying power (resupply path) based on the charging condition, and sets the power supply control unit 374 of each device based on the set resupply path. A supply source instruction signal or a supply destination instruction signal is output.

  In step S19, the power supply amount setting unit 372 sets the amount of power to be resupplied (resupply power amount) based on the condition relating to the supply amount among the charging conditions, and information on the set resupply power amount Are supplied to the power supply control unit 374 of each corresponding device.

  In step S20, the power supply control unit 374 controls to output power to the battery 308 when the supply source instruction signal is input, and to the battery 308 when the supply destination instruction signal is input. In contrast, control is performed so that power is input. Then, when the supply of power to the battery 308 or the output of power from the battery 308 is completed, a supply end signal is output.

  In step S21, the power supply completion output unit 388 outputs a power supply completion signal based on the input of the supply end signal from the power supply control unit 374 of all the devices that are resupplying power.

  In step S <b> 22, the photographing permission instruction unit 384 outputs a message indicating photographing permission to the mobile terminal 42 based on the input of the power supply completion signal. Then, it returns to the process after step S13.

  If it is determined in step S15 that re-supply is not necessary, the process proceeds to step S23, and the shooting completion determination unit 386 determines whether shooting is completed. This determination is made by comparing the number of times of photographing under the photographing conditions with the count value of the counter 380. If the count value is less than the number of times of photographing, the process returns to step S13, and the processing after step S13 is performed until the photographing is completed. repeat. If the photographing is completed, the process proceeds to step S24, and the power control unit 334 is temporarily stopped. Specifically, the shooting completion determination unit 386 outputs a shooting completion signal. The pause processing unit 340 outputs a pause signal to the power control unit 334 based on the input of the shooting completion signal from the shooting completion determination unit 386. The power control unit 334 stops the power supply control based on the input of the suspension signal from the suspension processing unit 340 and waits for the next activation from the power supply activation unit 336. At this stage, the processing operation of the first radiographic image capturing apparatus 10A is temporarily terminated. Again, when the power supply switch is operated or the power supply is turned on, the processes in and after step S1 are repeated.

  Next, the operation when the supply timing condition is supply before photographing will be described with reference to the flowcharts of FIGS. In the following description, the operation by the power management unit 390 is mainly shown, but the cassette selection unit 364 and the integrated supply unit 368 described above may be included.

  First, in step S <b> 101, a message prompting input of shooting conditions is output to the mobile terminal 42.

  In step S <b> 102, the power supply activation unit 336 activates the power control unit 334 based on the input of the current photographing condition (order) from the portable terminal 42. In this case, only the power supply activation unit 336 of the device having the same ID as the ID of the radiation source main body 18 or the cassette main body 12 used for imaging registered in the imaging conditions in advance activates the corresponding power control unit 334. To do. The current imaging condition may be input from a medical institution via a network and the mobile terminal 42. The current photographing condition is stored in the memory 330.

  In step S <b> 103, the device connection detection unit 360 detects whether or not a device (the radiation source body 18 or the cassette body 12) is connected to the first energy input / output unit 300 or the second energy input / output unit 302.

  At the detected stage, the process proceeds to the next step S104, and the ID acquisition unit 410 of the power management unit 390 shown in FIG. 19 acquires the ID of the connected device. Specifically, the ID acquisition unit 410 requests the connected device to transfer the ID. Since each device outputs an ID to the power management unit 390 based on the transfer request, the ID acquisition unit 410 acquires the input ID and registers it in the memory 330.

  In step S105, the various information acquisition unit 412 corresponds to the remaining shooting information table corresponding to ID, the previous shooting condition corresponding to ID, and ID in addition to the current shooting condition (already stored in the memory 330). The usage history table is acquired from the medical institution through the network and stored in the memory 330.

  In step S <b> 106, the power consumption amount predicting unit 414 performs shooting based on the condition related to the supply amount among the charging conditions (previously stored in the memory 330) and the current or previous shooting conditions (such as the number of shots and mAs value). The radiation source main body 18 and the cassette main body 12 are calculated by calculating the power consumption of the radiation source main body 18 and the cassette main body 12 to be used, and further multiplying and correcting the usage history (coefficient corresponding to the number of times of use). Each of the 12 electric energy amounts or the respective electric energy amounts of the radiation source main body portion 18 and the cassette main body portion 12 that would have been consumed are predicted. Among the charging conditions, the conditions relating to the supply amount include the amount of power required for the current number of shots, the amount of power required for one shot, the amount of power used in the previous shot, and the like. Therefore, when the condition regarding the supply amount indicates “the amount of power necessary for the current number of images”, the power consumption amount of the radiation source main body 18 and the cassette main body 12 used for the current imaging is calculated, The history (the coefficient corresponding to the number of times of use) is multiplied and corrected, and the radiation source main body 18 and the cassette main body 12 consumed in the current imaging or the radiation source main body that would have been consumed in the previous imaging. Each electric energy of the unit 18 and the cassette body 12 is predicted. When the condition relating to the supply amount indicates “the amount of power used in the previous imaging”, the amount of power consumed in the previous imaging of the radiation source body 18 and the cassette body 12 is calculated, and the usage history is further calculated. (Coefficient corresponding to the number of times of use) is multiplied and corrected to predict each power amount of the radiation source main body 18 and the cassette main body 12 that would have been consumed in the previous imaging.

  In step S <b> 107, the power supply path setting unit 370 sets a power supply path based on the predicted power amount and the remaining battery power (information in the remaining amount information table) of the radiation source main body 18 and the cassette main body 12. . As a typical example, a route for supplying electric power to a device that has almost no remaining battery charge is set. This information is displayed on the mobile terminal 42. When the operator 38 performs additional supply using other equipment (the radiation source main body 18 or the cassette main body 12 that is not used for imaging), the power supply path of other equipment (supply from the other equipment to the equipment with the ID) Route) and electric energy. When the operator 38 performs additional charging using other equipment (radiation source body 18 or cassette body 12), the power supply path of the other equipment (radiation source body 18 used for imaging from other equipment). Alternatively, the supply path to the cassette body 12 or the radiation source body 18 used for imaging or the supply path from the cassette body 12 to other devices), the amount of power, and the order of supply are input. Based on the set supply path, a supply source instruction signal or a supply destination instruction signal is output from the power supply path setting unit 370 to the power supply control unit 374 of each device.

  Thereafter, in step S108, the power supply amount setting unit 372 supplies the power amount to be supplied based on the predicted power amount and the remaining battery levels (information in the remaining amount information table) of the radiation source main body 18 and the cassette main body 12. Set (Supply power amount). As a result, the maximum predicted amount of power is supplied to a device that has almost no remaining battery charge in the current shooting. It may be 1/2 or 1/3 of the predicted power amount. This information is displayed on the mobile terminal 42. This amount of supplied power can be arbitrarily changed by the portable terminal 42. If there is an input for additional charging, the amount of power is also set. It should be noted that the power supply predicted based on the previous shooting condition complements the power consumed in the previous shooting. If there is an input for additional charging, the power supply amount is also set. The set power supply amount is output to the power supply control unit 374 of the corresponding device.

  In step S109, the power supply control unit 374 controls to output power to the battery 308 when the supply source instruction signal is input, and to the battery 308 when the supply destination instruction signal is input. In contrast, control is performed so that power is input. Then, when the supply of power to the battery 308 or the output of power from the battery 308 is completed, a supply end signal is output.

  In step S110, the information update unit 416 of the power management unit 390 updates the remaining power information table by subtracting the remaining power of the device that is the power supply source by the supplied power amount, and becomes the power supply destination device. The remaining power is updated by adding the amount of power supplied.

  In step S111, the power supply completion output unit 388 outputs a power supply completion signal based on the input of the supply end signal from the power supply control unit 374 of all the devices that are supplying power.

  In step S <b> 112, the photographing permission instruction unit 384 outputs a message indicating photographing permission to the mobile terminal 42 based on the input of the power supply completion signal from the power supply completion output unit 388.

  In step S113 of FIG. 23, the operator 38 prepares for radiography at the site of the transport destination. Since the preparation for photographing has been described in detail, the description thereof is omitted here.

  In step S <b> 114, the operator 38 operates the exposure switch 48 to start photographing the subject 50. At this time, the counter 380 updates the count value by +1.

  When the exposure switch 48 is operated in step S114 described above, in step S115, the power supply restriction unit 338 outputs a supply restriction signal to the power control unit 334 over a predetermined period. The power control unit 334 stops the power supply operation or reduces the supply amount per unit time over the period when the supply restriction signal is input.

  In step S116, the remaining amount prediction update unit 392 subtracts and updates the remaining battery amounts (remaining battery amounts of the radiation source main body 18 and the cassette main body 12 performing imaging) recorded in the remaining amount information table. Specifically, for the radiation source main body 18 and the cassette main body 12 that are performing imaging, each power consumption for each exposure is calculated based on the imaging conditions and the usage history table, and the remaining amount information table. Is subtracted from the remaining battery power of the radiation source main body 18 and the cassette main body 12 recorded in the table.

  In step S117, it is determined whether or not resupply of power is necessary. This determination is made based on whether or not an imaging impossible signal is output from the power supply control unit 374 of any device.

  If resupply is necessary, the process advances to step S118, and the shooting interruption instruction unit 378 outputs a message indicating the interruption of shooting to the mobile terminal 42. A message indicating interruption of shooting is displayed on the display screen of the portable terminal 42, and preferably an alarm is output as a sound to prompt the operator 38 to stop shooting.

  Thereafter, in step S119, the resupply instruction unit 382 outputs the resupply instruction signal to the power supply path setting unit 370, the power supply amount setting unit 372, and the power management unit 390.

  In step S120, the power supply path setting unit 370 sets a path for supplying power to the device corresponding to the ID included in the input resupply instruction signal as a resupply path, and sets the set resupply path as the resupply path. Based on this, a supply source instruction signal or a supply destination instruction signal is output to the power supply control unit 374 of each device.

  In step S121, the power consumption amount predicting unit 414 of the power management unit 390 has already completed the shooting among the charging conditions (previously stored in the memory 330) and the current shooting conditions (number of shots, mAs value, etc.) The power consumption of the device (radiation source main body 18 or cassette main body 12 to be resupplied) is calculated from the imaging conditions (the imaging conditions for imaging to be performed in the future) excluding the imaging values indicated by the numerical values. Furthermore, the usage history (coefficient corresponding to the number of times of use) is multiplied and corrected, and the amount of power of the device with the ID to be consumed in the shooting to be performed is predicted.

  In step S122, the power supply amount setting unit 372 sets the power amount predicted by the power consumption amount prediction unit 414 as the resupply power amount, and sets the information on the set resupply power amount for each corresponding device. This is supplied to the power supply control unit 374.

  In step S123, the power supply control unit 374 controls to output power to the battery 308 when the supply source instruction signal is input, and to the battery 308 when the supply destination instruction signal is input. In contrast, control is performed so that power is input. Then, when the supply of power to the battery 308 or the output of power from the battery 308 is completed, a supply end signal is output.

  In step S124, the power supply completion output unit 388 outputs a power supply completion signal based on the input of the supply end signal from the power supply control unit 374 of all the devices that are resupplying power.

  In step S125, the photographing permission instruction unit 384 outputs a message indicating photographing permission to the mobile terminal 42 based on the input of the power supply completion signal. Thereafter, the processing returns to step S114 and subsequent steps.

  When it is determined in step S117 described above that re-supply is not necessary, the process proceeds to step S126 in FIG. 24, and the shooting completion determination unit 386 determines whether shooting is completed. This determination is performed by comparing the number of times of photographing under the photographing condition with the count value of the counter. If the count value is less than the number of times of photographing, the process returns to step S114 in FIG. Repeat the process. When the imaging is completed, the process proceeds to step S127 in FIG. 24, and the usage history update unit 394 uses the usage count recorded in the usage history table (the usage count of the radiation source main body 18 and the cassette main body 12 performing imaging). ) Is added to the number of operations of the exposure switch 48.

  In step S128, the remaining amount information transfer unit 396 transfers the remaining amount information table to the database of the medical institution via the network and updates it.

  In step S129, the use history transfer unit 398 transfers the use history table to the database of the medical institution via the network and updates it.

  In step S130, the power control unit 334 is temporarily stopped. Specifically, the shooting completion determination unit 386 outputs a shooting completion signal. The pause processing unit 340 outputs a pause signal to the power control unit 334 based on the input of the shooting completion signal from the shooting completion determination unit 386. The power control unit 334 stops the power supply control based on the input of the suspension signal from the suspension processing unit 340 and waits for the next activation from the power supply activation unit 336. At this stage, the processing operation of the first radiographic image capturing apparatus 10A is temporarily terminated. Again, when the shooting conditions are input, the processes in and after step S102 are repeated.

  Next, the operation when the supply timing condition is supply after photographing will be described with reference to the flowcharts of FIGS. In the following description, the operation by the power management unit 390 is mainly shown, but the cassette selection unit 364 and the integrated supply unit 368 described above may be included.

  First, in step S <b> 201, a message that prompts input of shooting conditions is output to the mobile terminal 42.

  In step S <b> 202, the operator 38 prepares for radiography at the destination site. Thereafter, in step S203, the operator 38 operates the exposure switch 48 to start photographing the subject 50.

  In step S204, it is determined whether or not resupply of power is necessary. This determination is made based on whether or not an imaging impossible signal is output from the power supply control unit 374 of any device.

  If re-supply is necessary, the process proceeds to step S205, and the photographing interruption instruction unit 378 outputs a message indicating the photographing interruption to the portable terminal 42. Thereafter, in step S206, the resupply instruction unit 382 outputs a resupply instruction signal to the power supply path setting unit 370, the power supply amount setting unit 372, and the power management unit 390, and the power supply path setting unit 370, the power supply The amount setting unit 372 and the power management unit 390 are activated by interruption.

  In step S207, the power supply path setting unit 370 sets a path for supplying power to the device corresponding to the ID included in the input resupply instruction signal as a resupply path, and sets the set resupply path. Based on this, a supply source instruction signal or a supply destination instruction signal is output to the power supply control unit 374 of each device.

  In step S208, the power consumption amount predicting unit 414 of the power management unit 390 has already completed the shooting among the charging conditions (previously stored in the memory 330) and the current shooting conditions (number of shots, mAs value, etc.). The power consumption of the device (radiation source main body 18 or cassette main body 12 to be resupplied) is calculated from the imaging conditions (the imaging conditions for imaging to be performed in the future) excluding the imaging values indicated by the numerical values. Furthermore, the usage history (coefficient corresponding to the number of times of use) is multiplied and corrected, and the amount of power of the device with the ID to be consumed in the shooting to be performed is predicted.

  In step S209, the power supply amount setting unit 372 sets the power amount predicted by the power consumption amount prediction unit 414 as the resupply power amount, and sets the information on the set resupply power amount for each corresponding device. This is supplied to the power supply control unit 374.

  In step S210, the power supply control unit 374 controls to output power to the battery 308 when the supply source instruction signal is input, and to the battery 308 when the supply destination instruction signal is input. In contrast, control is performed so that power is input. Then, when the supply of power to the battery 308 or the output of power from the battery 308 is completed, a supply end signal is output.

  In step S211, the power supply completion output unit 388 outputs a power supply completion signal based on the input of the supply end signal from the power supply control unit 374 of all the devices that are supplying power again.

  In step S212, the photographing permission instruction unit 384 outputs a message indicating photographing permission to the mobile terminal 42 based on the input of the power supply completion signal. Thereafter, the processing returns to step S203 and subsequent steps.

  If it is determined in step S204 that re-supply is not necessary, the process proceeds to step S213, and the shooting completion determination unit 386 determines whether shooting has been completed. If shooting has not been completed, the process returns to step S203, and the processing from step S203 onward is repeated until shooting is completed. If the photographing is completed, the process proceeds to step S214, and the power supply activation unit 336 activates the power control unit 334 based on the input of the photographing completion signal. In this case, only the power supply activation unit 336 of the device having the same ID as the ID of the radiation source main body 18 or the cassette main body 12 used for imaging registered in the imaging conditions in advance activates the corresponding power control unit 334. To do.

  In step S <b> 215, the device connection detection unit 360 detects whether a device is connected to the first energy input / output unit 300 or the second energy input / output unit 302.

  At the detected stage, the process proceeds to the next step S216, and the ID acquisition unit 410 of the power management unit 390 acquires the ID of the connected device. Thereafter, in step S217, in addition to the current shooting condition (already stored in the memory), the various information acquisition unit 412 sets the remaining amount information table corresponding to the ID, the previous shooting condition corresponding to the ID, and the ID. The corresponding usage history table is acquired from the medical institution through the network.

  In step S218, the power consumption amount prediction unit 414 determines the radiation source main body 18 and the cassette main body to be used for imaging from the conditions regarding the supply amount among the charging conditions, the current or previous imaging conditions (number of imaging, mAs value, etc.). The power consumption of the unit 12 is predicted.

  In step S219, the power supply path setting unit 370 sets a power supply path based on the predicted power amount and the remaining battery levels (information in the remaining amount information table) of the radiation source main body 18 and the cassette main body 12. .

  Thereafter, in step S220, the power supply amount setting unit 372 supplies power based on the predicted power amount and the remaining battery power (information in the remaining amount information table) of the radiation source main body 18 and the cassette main body 12. Set (Supply power amount).

  In step S221, the power supply control unit 374 controls to output power to the battery 308 when the supply source instruction signal is input, and to the battery 308 when the supply destination instruction signal is input. In contrast, control is performed so that power is input. Then, when the supply of power to the battery 308 or the output of power from the battery 308 is completed, a supply end signal is output.

  In step S <b> 222, the information update unit 416 updates the remaining amount of the device that is the power supply source by subtracting the remaining amount of the device that is the power supply source by the supply power amount, and supplies the remaining amount of the device that is the power supply destination. Update by adding only the amount of power.

  In step S223, the power supply completion output unit 388 outputs a power supply completion signal based on the input of the supply end signal from the power supply control unit 374 of all the devices that are supplying power.

  In step S224, the use history update unit 394 adds the number of operations of the exposure switch 48 to the number of uses recorded in the use history table (the number of uses of the radiation source and cassette in which imaging is performed).

  In step S225, the remaining amount information transfer unit 396 transfers the remaining amount information table to the database of the medical institution via the network and updates it. In step S226, the usage history transfer unit 398 transfers the usage history table to the database of the medical institution via the network and updates it. Thereafter, in step S227, the suspension processing unit 340 temporarily stops the power control unit 334. At this stage, the processing operation of the first radiographic image capturing apparatus 10A is temporarily terminated. Again, when the shooting conditions are input, the processes in and after step S202 are repeated.

  As described above, in the first radiographic image capturing apparatus 10A, power supply is limited (stopped or reduced per unit time) in a period in which noise may be mixed into the radiographic image information being captured. Therefore, wasteful power consumption can be suppressed and low power consumption can be achieved while avoiding deterioration of the image quality of the radiation image information. Further, it is only necessary to prepare the battery 308 for the radiation source main body 18 and the battery 308 for the cassette main body 12. Therefore, the carrying size is small, the weight is small, and the usability (including portability) is improved. When the power control unit 334 performs control so that power is supplied only along the path from the radiation source main body 18 to the cassette main body 12, a cassette is used by using an internal capacitor as the battery of the cassette main body 12. There is no need to prepare the battery 308 for the main body 12, and it is more convenient to carry. Similarly, when the power control unit 334 controls to supply power only along the path from the cassette body 12 to the radiation source body 18, an internal capacitor is used as the battery 308 of the radiation source body 18. By using it, it is not necessary to prepare the battery 308 for the radiation source body 18 and it is convenient to carry.

  And, in the event of accidents, disaster sites, ambulances (including when stopped), railways, ships, airplanes, etc., when there is a situation that requires radiography, do not force the victims or victims to move. In this case (such as taking the patient to a medical examination car), it is possible to start photographing quickly. Also, if it is a transportation facility, it is possible to start shooting quickly without waiting for arrival at a station, port or airport. If the image is taken in an ambulance, the radiographic image information can be transmitted to a medical institution before arriving at the hospital. As a result, the condition of the victim can be known in advance, and appropriate and quick preparation and treatment can be expected.

  In addition, it is possible to bring several first radiographic imaging devices 10A with an examination car for regular medical examinations and temporary examinations where there are a large number of subjects such as schools and large companies. Normally, only one examination car is provided, so in places where there are a large number of subjects, such as schools, the subjects may have to wait for a long time. By using the photographing apparatus 10A in parallel, the photographing waiting time can be greatly reduced.

  As for the power supply route, a route by wired connection or a route by wireless power feeding can be set. For example, a route from the radiation source body 18 used for imaging to the cassette body 12, other not used for imaging. A path from the radiation source body 18 to the cassette body 12 used for imaging and a path from another cassette body 12 not used for imaging to the cassette body 12 can be set. Further, the path from the cassette body 12 to the radiation source body 18, the path from the other cassette body 12 to the radiation source body 18, and the other radiation source body 18 to the radiation source body 18. Can be set. The wireless power supply can be started when the device enters an area where wireless power supply is possible.

  For example, when fixing to the supply path from the radiation source body 18 to the cassette body 12 or fixing to the supply path from the cassette body 12 to the radiation source body 18, the power of the supply source is confirmed. The preparatory work is simplified such that it is only necessary to do so, and the photographing can be performed quickly.

  Further, for example, by using the first energy input / output unit 300 for wired connection and the second energy input / output unit 302 for wireless connection, a complex connection for power supply becomes possible. As a result, the path from the radiation source body 18 to the cassette body 12 and the path to the other radiation source body 18, the path from the radiation source body 18 to the cassette body 12, and the other cassette body. The path from the cassette body 12 to the radiation source body 18, the path from the cassette body 12 to the other cassette body 12, the path from the cassette body 12 to the radiation source body 18, and the other A route to the radiation source main body 18 can be set.

  Further, when power is supplied from the cassette body 12 to the radiation source body 18, the power of the cassette body 12 having a high degree of deterioration and the cassette body 12 having a small amount of built-in memory are preferentially used. Therefore, the power of the cassette main body 12 having a low degree of deterioration and the cassette main body 12 having a large remaining amount of built-in memory can be preserved, and a quick response can be made in an emergency.

  Similarly, when power is supplied from the cassette body 12 to the radiation source body 18, the power of the cassette body 12 close to the radiation source body 18 is preferentially supplied to the radiation source body 18. The time required for power supply can be shortened, and it is possible to respond quickly in an emergency.

  Similarly, when power is supplied from the cassette body 12 to the radiation source body 18, the power of the cassette body 12 having a small size is preferentially supplied to the radiation source body 18. The electric power of the cassette body 12 having a large size can be preserved, and a quick response can be made even in an emergency.

  In addition, since the power management unit 390 is provided, it is possible to manage the power necessary for the number of shots and supply, for example, the shortage from the surplus side, so that the radiation source main body 18 and the cassette main body 12 can be supplied. On the other hand, it is possible to efficiently supply electric power, and it is possible to respond quickly even in an emergency. In addition, since it is possible to supply power necessary for photographing with interchange from other devices not used for photographing, it is possible to respond quickly in an emergency. Since power required for the number of shots is predicted and supplied, power management can be saved.

  The power supply timing can be arbitrarily determined. For example, if the supply timing is set so that power is supplied before photographing, power necessary for photographing can be secured, and wasteful power consumption does not occur. In addition, power supply can be performed efficiently because the power required for the number of shots is predicted and supplied. If the supply timing is set so that power is supplied after shooting, the power required for at least one shooting can be secured, so that the next shooting can be performed quickly.

  In the above-described example, the battery control unit 306 is provided in each device. However, the following configuration may be employed. That is, among the various components of the battery control unit 306, the power supply control unit 374 and the remaining amount detection unit 376 are provided in each device, and other components are used, for example, the radiation source main unit 18 or the cassette main unit used for imaging. 12 (in the third radiographic image capturing apparatus 10C described later), it may be provided only in one of the radiation source main body 18, the cassette main body 12, and the PC 280 used for imaging. Of the power control unit 334, only the power management unit 390 is used for imaging. One of the radiation source main body 18 and the cassette main body 12 (in the third radiographic image capturing apparatus 10C described later, used for imaging). Any one of the radiation source main body 18, the cassette main body 12, and the PC 280) may be provided.

  Further, in the first radiographic image capturing apparatus 10A, when moving, the radiation source main body 18 and the cassette main body 12 are moved in a state where they are integrally connected and fixed by the connecting mechanism 82. After the source body 18 and the cassette body 12 are separated, the radiation 46 is output from the radiation source 44 accommodated in the radiation source body 18 to irradiate the subject 50 with the radiation 46, so that the size and weight are reduced. Even with the portable first radiographic image capturing apparatus 10 </ b> A in which the above is achieved, preparation for imaging can be performed easily and in a short time.

  The radiation detector 86 can also be applied to the case where a radiation image is acquired using a light readout type radiation detector. In this light readout type radiation detector, when radiation enters each solid detection element, an electrostatic latent image corresponding to the dose is accumulated and recorded in the solid detection element. When reading the electrostatic latent image, the radiation detector is irradiated with reading light, and the value of the generated current is acquired as a radiation image. Note that the radiation detector can erase and reuse the radiation image, which is the remaining electrostatic latent image, by irradiating the radiation detector with erasing light (see Japanese Patent Application Laid-Open No. 2000-105297).

  Furthermore, in the first radiographic image capturing apparatus 10A, in order to prevent the risk of blood and other germs adhering, for example, the entire apparatus has a waterproof and airtight structure, and is sterilized and washed as necessary. Thus, one first radiographic image capturing apparatus 10A can be used repeatedly and continuously.

  Further, the wireless communication between the first radiographic image capturing apparatus 10A and the external device may be performed by optical wireless communication using infrared rays or the like instead of normal communication using radio waves.

  In the first embodiment, as shown in FIG. 27, the measure 72 may be omitted. Even in this case, the effects of the components other than the major 72 can be easily obtained.

  Further, in the above description, the case where the main components of the coupling mechanism 82 are arranged in the cassette main body 12 has been described. However, even if the coupling mechanism 82 is arranged in the radiation source main body 18, the above-described effects. Is easily obtained.

  Moreover, the following modifications are also conceivable as the first radiographic image capturing apparatus 10A.

  That is, FIG. 28 shows a modification in which the lock release button 34, the hook portion 64, and the like are provided in the radiation source main body portion 18.

  In this case, the holding members 16a and 16b are not formed on the side surface 14a of the cassette main body 12, while the side surface 14a side of the radiation source main body 18 has a flat shape corresponding to the side surface 14a. ing. And the lock release button 34 is provided in the both ends of the radiation source main-body part 18, the hole 62 and the hook part 64 are provided in the vicinity of both ends in a flat part, and the connection terminal 68a on the one end part side in the said flat part. , 68b are arranged.

  In contrast, the side surface 14a of the cassette body 12 is provided with a hole 66 facing the hole 62 and with connection terminals 70a and 70b facing the connection terminals 68a and 68b.

  In the first radiographic imaging apparatus 10A of FIG. 28, the hook portion 64 is engaged with the hole 66 and connected with the flat portion of the radiation source main body portion 18 and the side surface 14a of the cassette main body portion 12 facing each other. The radiation source main body 18 and the cassette main body 12 are integrally connected and fixed by engaging the terminals 68a and 68b with the connection terminals 70a and 70b, respectively.

  Also in this modified example, each effect mentioned above can be acquired easily.

  In the example of FIG. 28, the lock release buttons 34 are provided at both ends of the radiation source main body 18, so that the operator 38 moves the radiation source main body 18 from the cassette main body 12 while pressing the lock release button 34. Only by removing, the integral connection fixed state of the radiation source main body 18 and the cassette main body 12 can be easily released.

  Furthermore, in the first embodiment, it is preferable to place a cradle 180 for charging the battery 308 of the first radiographic imaging apparatus 10A as shown in FIG. 29 at a necessary location in the hospital. In this case, the cradle 180 may transmit / receive necessary information to / from an external device in the hospital using not only the charging of the battery 308 but also the wireless communication function or the wired communication function of the cradle 180. . The information to be transmitted / received can include a radiographic image recorded on the first radiographic imaging device 10 </ b> A loaded in the cradle 180.

  In addition, a display unit 182 is provided in the cradle 180, and the charged state of the loaded first radiographic image capturing device 10A and the radiographic image acquired from the first radiographic image capturing device 10A are displayed on the display unit 182. Necessary information to be included may be displayed.

  Further, a plurality of cradle 180 is connected to the network, and the charging state of the first radiographic imaging apparatus 10A loaded in each cradle 180 is collected via the network, and the first radiographic imaging in a usable charging state is collected. It can also comprise so that the location of apparatus 10A can be confirmed.

  Next, a portable radiographic image capturing apparatus (hereinafter referred to as a second radiographic image capturing apparatus 10B) according to a second embodiment will be described with reference to FIGS.

  The second radiographic image capturing apparatus 10B has the same configuration as the first radiographic image capturing apparatus 10A described above, but a cassette body portion is provided on the side surface 14b opposite to the side surface 14a on which the holding members 16a and 16b are formed. 12 differs in that a part of the detection screen 250 is slightly pulled out from 12 and a weight bar 252 is connected to the tip of the detection screen 250. Of the remaining two side surfaces 14c and 14d of the cassette body 12, the first energy input / output unit 300 or the second energy input / output unit 302 that inputs and outputs power, for example, by wire or wireless, is provided on one side surface 14c. (See FIG. 13), a USB terminal 28 as an interface means capable of transmitting / receiving information to / from an external device, a card slot 32 for loading a memory card 30, and an unlock button 34 to be described later. It has been. Furthermore, on the upper surface 254, a portable terminal 42 that is removable from the cassette body 12 and on which the display unit 36 and the operation unit 40 operated by the operator 38 are arranged is mounted. On the other hand, the radiation source body 18 is provided with an exposure switch 48 (see FIG. 11) for starting output of radiation 46 from a radiation source 44 described later.

  30 and 31 show a state when the operator 38 transports the second radiographic image capturing apparatus 10B. In this case, the cassette main body 12 and the radiation source main body 18 are integrally connected and fixed.

  Next, the state of the second radiographic image capturing apparatus 10B when the second radiographic image capturing apparatus 10B is brought into a disaster site or home nursing site outside a medical institution will be described with reference to FIGS. To do.

  As shown in FIG. 36, a concave portion 54 that is recessed inward is formed on the upper surface 254, and the portable terminal 42 can be attached to the concave portion 54. As shown in FIGS. 32 and 33, the cassette body 12 has a roll screen structure in which a detection screen 250 made of a material that transmits the radiation 46 and having flexibility is wound and accommodated in a roll shape. A storage box 256 is disposed. A rotary encoder 258 that detects the amount by which the detection screen 250 is pulled out from the storage box 256 is attached to the side of the storage box 256. Further, a slot 260 for drawing out the detection screen 250 from the storage box 256 is formed in the side wall 52.

  Accordingly, when the operator 38 pulls the weight bar 252 in a direction away from the cassette body 12, the detection screen 250 can be pulled out (extended) from the storage box 256 through the slot 260. In other words, the detection screen 250 is housed in a state of being wound in a roll shape in the housing box 256 at the time of transport, but is pulled out to the outside by the operation of the weight bar 252 by the operator 38 at the time of photographing. In this case, the radiation source body 18 is arranged (elongated and developed) in a substantially planar shape (see FIGS. 34, 36, and 37). A scale 262 is swung on both sides of the detection screen 250 along the direction in which the detection screen 250 is pulled out.

  As shown in FIG. 35, when the subject 50 is irradiated with the radiation 46 from the radiation source 44, the detection screen 250 passes through the subject 50 and the grid 84 for removing scattered rays of the radiation 46 from the subject 50. A radiation detector 86 that detects the radiation 46 and a lead sheet 89 that absorbs backscattered rays of the radiation 46 are provided on the irradiation surface 20 on the subject 50 side of the detection screen 250 (the detection screen 250 shown in FIGS. 34 to 37). The upper surface is disposed in order. Note that the irradiation surface 20 may be configured as a grid 84. Further, the grid 84, the radiation detector 86, and the lead sheet 89 are also flexible.

  When a radiation image is taken by irradiating the subject 50 with radiation 46, the distance between the focal point 122 of the radiation source 44 and the position 124 (see FIG. 35) of the radiation detector 86 just below the focal point 122 (see FIG. 35). (Distance between photographing) is set in advance as the distance between the source image and the received image (SID), and the center position 126 on a part of the irradiation surface 20 of the detection screen 250 drawn out from the storage box 256 by the amount of drawing 13 is Therefore, it is necessary to perform an imaging preparation operation including an operation for matching the center position of the irradiation range of the radiation 46 on the irradiation surface 20.

  In this case, as shown in FIG. 34 to FIG. 36, the operator 38 sets the drawing amount of the band member 76 from the measure 72 in accordance with the SID in a state where the radiation source main body portion 18 is separated from the cassette main body portion 12. The band member 76 is pulled out until it becomes l1. In addition, the laser pointer 104 projects the laser beam 128 onto the irradiation surface 20 according to the control from the radiation source control unit 102, thereby irradiating the irradiation surface 20 with the radiation 46. Is displayed on the irradiation surface 20 as a cross-shaped mark 130.

Since only the scale 262 is displayed on the irradiation surface 20, the operator 38 specifies the center position 126 of the irradiation surface 20 while looking at the scale 262, for example. In addition, SID≈ is generally between the distance l2 between the position 124 and the center position 126 and the side surface 14a provided with the hole 80 through which the band member 76 is drawn, the amount of withdrawal l1 according to the SID, and the SID. The relationship (l1 ² -l2 ² ) ^1/2 is established.

  Therefore, after the band member 76 is pulled out from the measure 72 by the pull-out amount l1, the position of the radiation source body 18 is adjusted so that the position of the mark 130 displayed on the irradiation surface 20 and the center position 126 coincide with each other. Thereafter, as shown in FIG. 37, radiation 46 is emitted from the radiation source 44 to the subject 50 disposed on the irradiation surface 20 due to the operator 38 turning on the exposure switch 48, thereby causing radiation to the subject 50. It is possible to appropriately capture an image. Note that FIG. 37 illustrates a case where the hand of the subject 50 is photographed.

  The second radiographic image capturing apparatus 10B also performs the operations shown in FIGS. 21 to 26 described above. The operation from the preparation for imaging to the acquisition of radiographic image information is performed as follows.

  That is, shooting conditions such as subject information (for example, SID) relating to the subject 50 to be photographed are registered by operating the operation unit 40 of the portable terminal 42 at the site of the transport destination.

  First, the operator 38 pulls the weight bar 252 and pulls out (extends) the detection screen 250 having a length (drawing amount l3) necessary for imaging the imaging region of the subject 50 from the storage box 256. The rotary encoder 258 detects the drawing amount l3 of the detection screen 250 and notifies the SID determination unit 168 of it.

  Next, when the operator 38 presses the lock release button 34, the hook portion 64 is displaced toward the side wall 52d against the elastic force of the spring member 60, so that the engagement state between the hook portion 64 and the hole 66 is released. Is done.

  When the operator 38 removes the radiation source body 18 from the cassette body 12 while the engagement state is being released (while the lock release button 34 is being pressed), the connection between the connection terminal 68a and the connection terminal 70a. The combined state and the engaged state between the connection terminal 68b and the connection terminal 70b are both released, and the integral coupling and fixing state between the cassette body 12 and the radiation source body 18 is released. The operator 38 performs the setting operation of the inter-imaging distance and the setting operation for matching the mark 130 displayed on the irradiation surface 20 with the center position 126, and then between the irradiation surface 20 and the radiation source main body 18. The subject 50 is arranged and the subject 50 is positioned. In this case, the operator 38 first moves the radiation source main body 18 and pulls out the band member 76 until the pull-out amount of the band member 76 from the measure 72 becomes the pull-out amount l1 corresponding to the SID.

  Thus, after adjusting the position of the radiation source main body 18 so that the position of the mark 130 and the center position 126 coincide with each other, the operator 38 determines that the center of the imaging region of the subject 50 is the center position 126 (of the mark 130). The subject 50 is arranged (positioned) on the irradiation surface 20 so as to coincide with the (position).

  The radiation source body 18 is fixed at the adjusted position by a holding member (not shown) after the above-described position adjustment is performed.

  After positioning the subject 50, the operator 38 turns on the exposure switch 48 to start photographing the subject 50.

  This second radiographic image capturing apparatus 10B also has the same effect as the first radiographic image capturing apparatus 10A described above.

  According to the second radiographic image capturing apparatus 10B, when moving, the radiation source main body 18 and the cassette main body 12 are moved in a state where they are integrally connected and fixed by the connecting mechanism 82, while at the time of imaging, radiation is used. The source body 18 and the cassette body 12 are separated from each other, and after the detection screen 250 is pulled out (extended) from the cassette body 12, the radiation 46 is output from the radiation source 44 accommodated in the radiation source body 18. Since the subject 50 is irradiated with the radiation 46, even the portable second radiographic image capturing apparatus 10B that is reduced in size and weight can be easily prepared for imaging in a short time. It becomes.

  In addition, the storage box 256 disposed in the cassette body 12 winds and stores the flexible detection sheet 250 in a roll shape. Accordingly, the detection screen 250 is wound in a roll shape around the storage box 256 when transported to a disaster site or home care site, while being taken out from the storage box 256 and flattened during photographing. Be expanded. Thereby, size reduction of the whole 2nd radiographic imaging apparatus 10B is easily realizable.

  Next, a portable radiographic imaging device (hereinafter referred to as a third radiographic imaging device 10C) according to a third embodiment will be described with reference to FIGS.

  The radiation source body 18, the cassette body 12, and the radiation source body 18 are electrically connected via a wired or wireless input / output unit, and the cassette body is connected via a wired or wireless input / output unit. 12, a personal computer (control device: hereinafter referred to as PC 280) that has a built-in digital camera 270 that captures a predetermined imaging region and that can be operated by an operator 38 (see FIG. 41). And have. In this case, the PC 280 can transmit and receive signals to and from the medical institution to which the operator 38 belongs by wireless communication via a network using a public line or the like.

  The cassette body 12 includes a battery unit 304, a battery control unit 306, a radiation detector 86, a cassette control unit 92, and a transceiver 94, as in FIG. 11 described above. As shown in FIG. 39, a first energy input / output unit 300 and a second energy input / output unit 302 are provided on the side surface of the casing of the cassette body 12. Similarly to FIG. 11 described above, the radiation source main body 18 also includes the radiation source 44, the battery unit 304, the battery control unit 306, the transceiver 100, and the radiation source control unit 102 that controls the radiation source 44. A laser pointer 104 is arranged. As shown in FIG. 3, a first energy input / output unit 300 or a second energy input / output unit 302 similar to the cassette body 12 is provided on the side surface and the peripheral surface of the housing.

  As shown in FIG. 38, the PC 280 has an appearance of a so-called notebook personal computer, and includes an operation unit 282 such as a keyboard and a display unit 284 such as a display. Of course, a mobile phone or PDA (personal information terminal) may be used instead of the PC 280.

  The PC 280 is provided with a power switch, a speaker, a microphone, and the like, as in a normal notebook computer. Further, the PC 280 incorporates a transceiver 288 (see FIG. 42) capable of transmitting / receiving information to / from external devices (network, radiation source main body 18, cassette main body 12, etc.). A first energy input / output unit 300 and a second energy input / output unit 302 are provided. In the example of FIG. 38, the first energy input / output unit 300 of the PC 280 and the first energy input / output unit 300 of the radiation source body 18 are connected by wire, and the second energy input / output unit 302 of the PC 280 and the cassette body 12 are connected. Although an example in which the first energy input / output unit 300 is connected by wire is shown, wireless connection may be used.

  Furthermore, inside the PC 280, as shown in FIG. 42, a battery unit 304 and a battery control unit 306 similar to those in the cassette body 12 and the radiation source body 18 are incorporated.

  FIG. 41 shows a state when the operator 38 transports the third radiographic imaging apparatus 10C.

  In this case, the radiation source main body 18, the cassette main body 12, and the folded PC 280 are housed inside the attache case 286 in a state where the electrical connection is released. Accordingly, the operator 38 transports the attach case 286 from the medical institution to a desired location, for example, a disaster site or home nursing site while holding the handle 24, and the radiation source body 18 from the attach case 286 at the transport destination site. Taking out the cassette body 12 and the folded PC 280 and assembling it to the state shown in FIG. 38 to FIG. 40, preparation for photographing performed before photographing radiation images for disaster victims, or Therefore, it is possible to perform imaging preparations that are performed before radiographic images are acquired for home residents who need home nursing.

  The third radiographic imaging device 10C also performs the operations shown in FIGS. 21 to 26 described above, but the operation for preparing for imaging is performed as follows.

  That is, the operator 38 takes out the radiation source body 18 and the cassette body 12 from the attach case 286, and electrically connects the radiation source body 18 and the cassette body 12 to the PC 280 (wired connection or wireless connection). To do. The operator 38 arranges the PC 280, the radiation source main body 18 and the cassette main body 12 so as to have the positional relationship shown in FIGS.

  The operator 38 is ready for radiography by activating the PC 280. Thereafter, radiography is performed by operating the exposure switch 48.

  By the way, the power supply using this PC 280 can adopt a method different from that of the first radiographic imaging apparatus 10A and the second radiographic imaging apparatus 10B described above. For example, the battery unit 304 of the PC 280 collects all or part of the power stored in the battery 308 of the radiation source body 18 and all or part of the power stored in the battery 308 of the cassette body 12. It is processing to do.

  Here, the current collecting unit 420 for realizing the current collecting process will be described with reference to FIGS. 43 and 44.

  The current collector 420 is incorporated in the battery controller 306 and is activated based on an operation for instructing current collection (such as a left click on an icon indicating current collection). As shown in FIG. 43, the current collector 420 includes the above-described device connection detector 360, a current collection ID acquisition unit 422, a current collection information acquisition unit 424, and a current collection supply path setting unit. 426, a current collection amount setting unit 428, the above-described power supply control unit 374, the above-described remaining amount detection unit 376, a remaining power collection update unit 430, and a remaining power collection information transfer unit 432. .

  Here, the breakdown and operation of the configuration of the current collector 420 will be described with reference to the flowchart of FIG.

  First, the device connection detection unit 360 detects whether or not a device (the radiation source body 18 or the cassette body 12) is connected to the first energy input / output unit 300 or the second energy input / output unit 302 (FIG. 44). Step S301).

  The collecting ID acquisition unit 422 makes an ID transfer request to the connected device. Since each device outputs an ID to the current collector 420 based on the transfer request, the device acquires the input ID and registers it in the memory 330 (see FIG. 14) (step S302).

  The power collection information acquisition unit 424 acquires the remaining amount information table corresponding to each ID and stores it in the memory 330 (step S303).

  The power collection supply path setting unit 426 sets a path from the device connected to the first energy input / output unit 300 to the PC 280, and sets a path from the device connected to the second energy input / output unit 302 to the PC 280. To do. Based on the set supply path, a supply source instruction signal is output from the power collection supply path setting unit 426 to the power supply control unit 374 of each device (step S304).

  The current collection amount setting unit 428 sets the current collection amount using the operation unit 282 (keyboard or mouse) of the PC 280. The amount of power collected is the first power amount supplied from the device connected to the first energy input / output unit 300 of the PC 280 to the battery 308 of the PC 280, and the battery of the PC 280 from the device connected to the second energy input / output unit 302 of the PC 280. This indicates the total amount of the second power supplied to 308. The set first power amount and second power amount are respectively supplied to the power supply control unit 374 of the corresponding device (step S305).

  The power supply control unit 374 of each device controls the battery 308 to output power because the supply source instruction signal is input. Since the supply destination instruction signal is input, the power supply control unit 374 of the PC 280 performs control to input power to the battery 308 (step S306). Based on the remaining amount from the remaining amount detection unit 376, control is performed so that power is supplied to the battery 308 or supplied from the battery 308 at a constant charge rate (or discharge rate). If the amount of power supplied is small, rapid charging (discharging) is also possible.

  The power collection remaining amount update unit 430 updates the second power amount by subtracting the first power amount from the remaining battery amount corresponding to the ID of the device connected to the first energy input / output unit 300 in the remaining amount information table. The second power amount is subtracted and updated from the remaining battery level corresponding to the ID of the device connected to the energy input / output unit 302 (step S307).

  The remaining power collection information transfer unit 432 transfers the remaining amount information table to the database of the medical institution via the network and updates it when the update process in the remaining power collection update unit 430 has been completed (step). S308).

  The current collector 420 may be activated by, for example, an operation input to the operation unit 282 regardless of the place or time. For example, when being brought into a medical institution, the current collector 420 is activated to collect power in the battery 308 of the PC 280, and when brought into the field, the radiation source main body 18 and the cassette used for imaging are collected. The main body 12 may be supplied with power from the PC 280. At this time, the power management unit 390 supplies the optimum amount of power for imaging to the radiation source body 18 and the cassette body 12. Of course, the current collector 420 is also activated in the field to collect power from the radiation source main body 18 and the cassette main body 12 that cannot be used for radiography, for example, due to severe deterioration, and collects power to the PC 280 and used for radiography. Alternatively, power may be supplied to the cassette body 12.

  In the third radiographic imaging apparatus 10C, since power can be supplied from the PC 280 to various devices, the path from the PC 280 to the radiation source main body 18 used for imaging, and the cassette main body used from the PC 280 for imaging. A route to 12 can be set. Further, with the PC 280 as a supply source, a path from the PC 280 to the radiation source body 18 and a path from the PC 280 to the cassette body 12 can be set. In addition, the path from the radiation source body 18 to the PC 280, the path from the PC 280 to the cassette body 12, the path from the cassette body 12 to the PC 280, and the path from the PC 280 to the radiation source body 18 are set using the PC 280 as an intermediary. Can do.

  As described above, since power can be supplied from the PC 280 to the radiation source main body 18 and the cassette main body 12, or between the radiation source main body 18 and the cassette main body 12 via the PC 280, the PC 280 can be supplied. Therefore, power management can be performed in a concentrated manner, and power can be efficiently supplied between the radiation source main body 18 and the cassette main body 12. Moreover, since it is possible to collect power from the one or more radiation source main body sections 18 and one or more cassette main body sections 12 to the PC 280, the PC 280 performs a kind of storage battery function, thereby realizing efficient power management. Inconveniences such as interruption of power supply when necessary can be avoided.

  Note that the present invention is not limited to the above-described embodiment, and it is needless to say that various configurations can be adopted without departing from the gist of the present invention.

  For example, the radiation detector 86 may be the radiation detector 600 according to the modification shown in FIGS. 45 and 46. FIG. 45 is a schematic cross-sectional view schematically showing the configuration of three pixel portions of the radiation detector 600 according to the modification.

  In the radiation detector 600, a signal output unit 604, a sensor unit 606, and a scintillator 608 are sequentially stacked on an insulating substrate 602. A pixel unit is configured by the signal output unit 604 and the sensor unit 606. ing. The pixel units are arranged in a matrix on the substrate 602, and the signal output unit 604 and the sensor unit 606 in each pixel unit are configured to overlap each other.

  The scintillator 608 is formed on the sensor unit 606 with a transparent insulating film 610 interposed therebetween. The scintillator 608 converts the radiation 46 incident from above (the side opposite to the side where the substrate 602 is located) into light and emits light. The body is formed into a film. The wavelength range of light emitted by the scintillator 608 is preferably the visible light range (wavelength 360 nm to 830 nm), and in order to enable monochrome imaging by the radiation detector 600, the wavelength range of green is included. Is more preferable.

  Specifically, the phosphor used for the scintillator 608 preferably contains cesium iodide (CsI) when imaging using X-rays as the radiation 46, and the emission spectrum during X-ray irradiation is 420 nm to 600 nm. It is particularly preferred to use some CsI (Tl) (cesium iodide with thallium added). Note that the emission peak wavelength of CsI (Tl) in the visible light region is 565 nm.

  The scintillator 608 may be formed, for example, by vapor-depositing CsI (Tl) having a columnar crystal structure on a vapor deposition base. When the scintillator 608 is formed by vapor deposition as described above, Al is often used as the vapor deposition substrate from the viewpoint of X-ray transmittance and cost, but is not limited thereto. Note that in the case where GOS is used as the scintillator 608, the scintillator 608 may be formed by applying GOS to the surface of the TFT active matrix substrate without using a vapor deposition substrate. Alternatively, after the GOS is applied to the resin base to form the scintillator 608, the scintillator 608 may be bonded to the TFT active matrix substrate. As a result, the TFT active matrix substrate can be preserved even if GOS application fails.

  The sensor unit 606 includes an upper electrode 612, a lower electrode 614, and a photoelectric conversion film 616 disposed between the upper electrode 612 and the lower electrode 614.

Since the upper electrode 612 needs to make the light generated by the scintillator 608 incident on the photoelectric conversion film 616, it is preferable that the upper electrode 612 is made of a conductive material that is transparent at least with respect to the emission wavelength of the scintillator 608. It is preferable to use a transparent conductive oxide (TCO) having a high transmittance for visible light and a small resistance value. Note that although a metal thin film such as Au can be used as the upper electrode 612, a resistance value tends to increase when the transmittance of 90% or more is obtained, so that the TCO is preferable. For example, ITO, IZO, AZO, FTO, SnO ₂ , TiO ₂ , ZnO _{2 and the} like can be preferably used, and ITO is most preferable from the viewpoint of process simplicity, low resistance, and transparency. Note that the upper electrode 612 may have a single configuration common to all the pixel portions, or may be divided for each pixel portion.

  The photoelectric conversion film 616 includes an organic photoconductor (OPC), absorbs light emitted from the scintillator 608, and generates a charge corresponding to the absorbed light. If the photoelectric conversion film 616 includes an organic photoconductor (organic photoelectric conversion material), the photoelectric conversion film 616 has a sharp absorption spectrum in the visible light region, and electromagnetic waves other than light emitted by the scintillator 608 are almost absorbed by the photoelectric conversion film 616. In addition, noise generated when the radiation 46 is absorbed by the photoelectric conversion film 616 can be effectively suppressed. Note that the photoelectric conversion film 616 may be configured to include amorphous silicon instead of the organic photoconductor. In this case, it has a wide absorption spectrum and can efficiently absorb light emitted by the scintillator 608.

  The organic photoconductor constituting the photoelectric conversion film 616 preferably has a peak wavelength closer to the emission peak wavelength of the scintillator 608 in order to absorb light emitted by the scintillator 608 most efficiently. Ideally, the absorption peak wavelength of the organic photoconductor coincides with the emission peak wavelength of the scintillator 608. However, if the difference between the two is small, the light emitted from the scintillator 608 can be sufficiently absorbed. . Specifically, the difference between the absorption peak wavelength of the organic photoconductor and the emission peak wavelength with respect to the radiation of the scintillator 608 is preferably within 10 nm, and more preferably within 5 nm.

  Examples of organic photoconductors that can satisfy such conditions include quinacridone organic compounds and phthalocyanine organic compounds. For example, since the absorption peak wavelength in the visible region of quinacridone is 560 nm, if quinacridone is used as the organic photoconductor and CsI (Tl) is used as the material of the scintillator 608, the difference in peak wavelength can be made within 5 nm. Thus, the amount of charge generated in the photoelectric conversion film 616 can be substantially maximized.

  The sensor unit 606 is configured to stack or mix a site that absorbs electromagnetic waves, a photoelectric conversion site, an electron transport site, a hole transport site, an electron blocking site, a hole blocking site, a crystallization prevention site, an electrode, and an interlayer contact improvement site. It is comprised including the organic layer formed by. The organic layer preferably contains an organic p-type compound (organic p-type semiconductor) or an organic n-type compound (organic n-type semiconductor).

  An organic p-type semiconductor is a donor organic semiconductor (compound) typified by a hole-transporting organic compound and refers to an organic compound having a property of easily donating electrons. More specifically, an organic compound having a smaller ionization potential when two organic materials are used in contact with each other. Therefore, any organic compound can be used as the donor organic compound as long as it is an electron-donating organic compound.

  An organic n-type semiconductor is an acceptor organic semiconductor (compound) typified by an electron-transporting organic compound and refers to an organic compound having a property of easily accepting electrons. More specifically, the organic compound having the higher electron affinity when two organic compounds are used in contact with each other. Therefore, as the acceptor organic compound, any organic compound can be used as long as it is an electron-accepting organic compound.

  The materials applicable as the organic p-type semiconductor and the organic n-type semiconductor and the configuration of the photoelectric conversion film 616 are described in detail in Japanese Patent Application Laid-Open No. 2009-32854, and thus the description thereof is omitted. Note that the photoelectric conversion film 616 may be formed by further containing fullerenes or carbon nanotubes.

  The thickness of the photoelectric conversion film 616 is preferably as large as possible in terms of absorbing light from the scintillator 608. However, when the thickness is larger than a certain level, the photoelectric conversion film 616 is generated in the photoelectric conversion film 616 by a bias voltage applied from both ends of the photoelectric conversion film 616. Since electric field strength is reduced and charges cannot be collected, the thickness is preferably 30 nm to 300 nm, more preferably 50 nm to 250 nm, and particularly preferably 80 nm to 200 nm.

  The photoelectric conversion film 616 has a single-layer configuration common to all the pixel portions, but may be divided for each pixel portion. The lower electrode 614 is a thin film divided for each pixel portion. However, the lower electrode 614 may have a single configuration common to all the pixel portions. The lower electrode 614 can be made of a transparent or opaque conductive material, and aluminum, silver, or the like can be preferably used. The thickness of the lower electrode 614 can be, for example, 30 nm or more and 300 nm or less.

  In the sensor unit 606, by applying a predetermined bias voltage between the upper electrode 612 and the lower electrode 614, one of charges (holes, electrons) generated in the photoelectric conversion film 616 is moved to the upper electrode 612. The other can be moved to the lower electrode 614. In the radiation detector 600 according to this modification, a wiring is connected to the upper electrode 612, and a bias voltage is applied to the upper electrode 612 via the wiring. In addition, the polarity of the bias voltage is determined so that electrons generated in the photoelectric conversion film 616 move to the upper electrode 612 and holes move to the lower electrode 614, but this polarity is opposite. May be.

  The sensor unit 606 constituting each pixel unit only needs to include at least the lower electrode 614, the photoelectric conversion film 616, and the upper electrode 612. In order to suppress an increase in dark current, the electron blocking film 618 and the hole blocking are included. It is preferable to provide at least one of the films 620, and it is more preferable to provide both.

  The electron blocking film 618 can be provided between the lower electrode 614 and the photoelectric conversion film 616. When a bias voltage is applied between the lower electrode 614 and the upper electrode 612, electrons are transferred from the lower electrode 614 to the photoelectric conversion film 616. It is possible to suppress the dark current from increasing due to the injection of.

  An electron-donating organic material can be used for the electron blocking film 618. The material actually used for the electron blocking film 618 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 616, and the like, and 1.3 eV or more from the work function (Wf) of the material of the adjacent electrode. A material having a large electron affinity (Ea) and an Ip equivalent to or smaller than the ionization potential (Ip) of the material of the adjacent photoelectric conversion film 616 is preferable. Since the material applicable as the electron donating organic material is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, description thereof is omitted.

  The thickness of the electron blocking film 618 is preferably 10 nm or more and 200 nm or less, more preferably 30 nm or more and 150 nm or less, and particularly preferably, in order to surely exhibit the dark current suppressing effect and prevent a decrease in photoelectric conversion efficiency of the sensor unit 606. It is good to set it to 50 nm or more and 100 nm or less.

  The hole blocking film 620 can be provided between the photoelectric conversion film 616 and the upper electrode 612. When a bias voltage is applied between the lower electrode 614 and the upper electrode 612, the hole blocking film 620 is applied from the upper electrode 612 to the photoelectric conversion film 616. It is possible to suppress the increase in dark current due to the injection of holes.

  An electron-accepting organic material can be used for the hole blocking film 620. The thickness of the hole blocking film 620 is preferably 10 nm or more and 200 nm or less, more preferably 30 nm or more and 150 nm or less, and particularly preferably, in order to reliably exhibit the dark current suppressing effect and prevent a decrease in photoelectric conversion efficiency of the sensor unit 606. Is preferably 50 nm to 100 nm.

  The material actually used for the hole blocking film 620 may be selected according to the material of the adjacent electrode, the material of the adjacent photoelectric conversion film 616, and the like, and 1.3 eV from the work function (Wf) of the material of the adjacent electrode. As described above, it is preferable that the ionization potential (Ip) is large and the Ea is equal to or larger than the electron affinity (Ea) of the material of the adjacent photoelectric conversion film 616. Since the material applicable as the electron-accepting organic material is described in detail in Japanese Patent Application Laid-Open No. 2009-32854, description thereof is omitted.

  Note that, among the charges generated in the photoelectric conversion film 616, when a bias voltage is set so that holes move to the upper electrode 612 and electrons move to the lower electrode 614, the electron blocking film 618 and the hole blocking are set. The position of the film 620 may be reversed. Further, it is not necessary to provide both the electron blocking film 618 and the hole blocking film 620. If either one is provided, a certain dark current suppressing effect can be obtained.

  As shown in FIG. 46, the signal output unit 604 is provided on the surface of the substrate 602 corresponding to the lower electrode 614 of each pixel unit, and the storage capacitor 622 that accumulates the electric charge moved to the lower electrode 614; The TFT 624 converts the electric charge accumulated in the accumulation capacitor 622 into an electric signal and outputs the electric signal. The region where the storage capacitor 622 and the TFT 624 are formed has a portion that overlaps with the lower electrode 614 in plan view. With such a structure, the signal output unit 604 and the sensor unit 606 in each pixel unit are connected to each other. There will be overlap in the thickness direction. If the signal output unit 604 is formed so as to completely cover the storage capacitor 622 and the TFT 624 with the lower electrode 614, the plane area of the radiation detector 600 (pixel unit) can be minimized.

  The storage capacitor 622 is electrically connected to the corresponding lower electrode 614 through a wiring made of a conductive material formed through an insulating film 626 provided between the substrate 602 and the lower electrode 614. Thereby, the charge collected by the lower electrode 614 can be moved to the storage capacitor 622.

  The TFT 624 includes a gate electrode 628, a gate insulating film 630, and an active layer (channel layer) 632, and a source electrode 634 and a drain electrode 636 are formed on the active layer 632 with a predetermined interval. The active layer 632 can be formed of, for example, amorphous silicon, amorphous oxide, organic semiconductor material, carbon nanotube, or the like. Note that the material forming the active layer 632 is not limited thereto.

The amorphous oxide that can form the active layer 632 is preferably an oxide containing at least one of In, Ga, and Zn (for example, In—O-based), and at least two of In, Ga, and Zn. Oxides containing one (for example, In—Zn—O, In—Ga—O, and Ga—Zn—O) are more preferable, and oxides including In, Ga, and Zn are particularly preferable. As the In—Ga—Zn—O-based amorphous oxide, an amorphous oxide whose composition in a crystalline state is represented by InGaO ₃ (ZnO) _m (m is a natural number of less than 6) is preferable, and InGaZnO is particularly preferable. ₄ is more preferable. Note that the amorphous oxide that can form the active layer 632 is not limited thereto.

  Examples of the organic semiconductor material that can form the active layer 632 include, but are not limited to, phthalocyanine compounds, pentacene, vanadyl phthalocyanine, and the like. In addition, about the structure of a phthalocyanine compound, since it describes in detail in Unexamined-Japanese-Patent No. 2009-212389, description is abbreviate | omitted.

  If the active layer 632 of the TFT 624 is formed of an amorphous oxide, an organic semiconductor material, or a carbon nanotube, the radiation 46 such as X-rays is not absorbed, or even if it is absorbed, a very small amount remains. Generation of noise in the unit 604 can be effectively suppressed.

  In addition, when the active layer 632 is formed of carbon nanotubes, the switching speed of the TFT 624 can be increased, and a TFT 624 having a low light absorption in the visible light region can be formed. Note that when the active layer 632 is formed of carbon nanotubes, the performance of the TFT 624 is remarkably deteriorated only by mixing a very small amount of metallic impurities into the active layer 632, so that extremely high purity carbon nanotubes are separated by centrifugation or the like.・ It needs to be extracted and formed.

  Here, any of the above-described amorphous oxide, organic semiconductor material, carbon nanotube, and organic photoconductor can be formed at a low temperature. Therefore, the substrate 602 is not limited to a substrate having high heat resistance such as a semiconductor substrate, a quartz substrate, and a glass substrate, and a flexible substrate such as plastic, aramid, or bionanofiber can also be used. Specifically, flexible substrates such as polyesters such as polyethylene terephthalate, polybutylene phthalate, polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, polychlorotrifluoroethylene, etc. Can be used. If such a plastic flexible substrate is used, it is possible to reduce the weight, which is advantageous for carrying around, for example.

  In addition, the photoelectric conversion film 616 is formed from an organic photoconductor, and the TFT 624 is formed from an organic semiconductor material, whereby the photoelectric conversion film 616 and the TFT 624 are formed at a low temperature on a plastic flexible substrate (substrate 602). It is possible to reduce the thickness and weight of the radiation detector 600 as a whole. Thereby, the cassette body 12 that accommodates the radiation detector 600 can be made thinner and lighter, and convenience in use outside the hospital is improved. In addition, since the base material of the photoelectric conversion portion is made of a flexible material unlike general glass, damage resistance during carrying and use of the device can be improved.

  In addition, the substrate 602 is provided with an insulating layer for ensuring insulation, a gas barrier layer for preventing permeation of moisture and oxygen, an undercoat layer for improving flatness or adhesion to electrodes, and the like. May be.

  Since aramid can be applied at a high temperature process of 200 ° C. or more, the transparent electrode material can be cured at a high temperature to reduce the resistance, and can also be used for automatic mounting of a driver IC including a solder reflow process. Moreover, since aramid has a thermal expansion coefficient close to that of ITO (indium tin oxide) or a glass substrate, warping after production is small and it is difficult to crack. In addition, aramid can form a substrate thinner than a glass substrate or the like. Note that the substrate 602 may be formed by stacking an ultrathin glass substrate and an aramid.

  Bionanofiber is a composite of cellulose microfibril bundles (bacterial cellulose) produced by bacteria (Acetobacter Xylinum) and a transparent resin. The cellulose microfibril bundle has a width of 50 nm and a size of 1/10 of the visible light wavelength, and has high strength, high elasticity, and low thermal expansion. By impregnating and curing a transparent resin such as an acrylic resin or an epoxy resin in bacterial cellulose, a bio-nanofiber having a light transmittance of about 90% at a wavelength of 500 nm can be obtained while containing 60-70% of the fiber. Bionanofiber has a low coefficient of thermal expansion (3-7ppm) comparable to silicon crystals, and is as strong as steel (460MPa), highly elastic (30GPa), and flexible. The substrate 602 can be formed thin.

  In this modification, a signal output unit 604, a sensor unit 606, and a transparent insulating film 610 are sequentially formed on a substrate 602, and a scintillator 608 is attached to the substrate 602 using an adhesive resin having low light absorption. Thus, the radiation detector 600 is formed.

  In the radiation detector 600 according to the above-described modification, the photoelectric conversion film 616 is made of an organic photoconductor, and the active layer 632 of the TFT 624 is made of an organic semiconductor material. At 604, the radiation 46 is hardly absorbed. Thereby, the fall of the sensitivity with respect to the radiation 46 can be suppressed.

  Both the organic semiconductor material constituting the active layer 632 of the TFT 624 and the organic photoconductor constituting the photoelectric conversion film 616 can be formed at a low temperature. Therefore, the substrate 602 can be formed of plastic resin, aramid, or bionanofiber that absorbs less radiation 46. Thereby, the fall of the sensitivity with respect to the radiation 46 can be suppressed further.

  For example, when the radiation detector 600 is attached to the irradiation surface 20 portion in the housing and the substrate 602 is formed of a highly rigid plastic resin, aramid, or bionanofiber, the rigidity of the radiation detector 600 itself may be increased. Therefore, the irradiation surface 20 portion of the housing can be formed thin. Further, when the substrate 602 is formed of a highly rigid plastic resin, aramid, or bionanofiber, the radiation detector 600 itself has flexibility, so that even when an impact is applied to the irradiation surface 20, the radiation detector 600 is damaged. It ’s hard.

  In the radiation detector 600 according to the above-described modification, the light emitted from the scintillator 608 is converted into charges by the sensor unit 606 (photoelectric conversion film 616) located on the side opposite to the side where the radiation source 44 is located. Although it is configured as a so-called back side scanning method (PSS (Penetration Side Sampling) method) for reading an image, it is not limited to this configuration.

  For example, the radiation detector may be configured as a so-called surface reading system (ISS (Irradiation Side Sampling) system). In this case, the substrate 602, the signal output unit 604, the sensor unit 606, and the scintillator 608 are stacked in this order along the irradiation direction of the radiation 46, and the light emitted from the scintillator 608 is sensor unit on the side where the radiation source 44 is located. At 606, the radiation image is read after being converted into electric charges. In general, the scintillator 608 emits light more strongly on the irradiation surface side of the radiation 46 than on the rear side. Therefore, in the radiation detector configured by the front surface reading method, compared to the radiation detector 600 configured by the back surface reading method, The distance until the light emitted from the scintillator 608 reaches the photoelectric conversion film 616 can be shortened. Thereby, since the diffusion / attenuation of the light can be suppressed, the resolution of the radiation image can be increased.

10A to 10C: First radiographic imaging device to third radiographic imaging device 12: Cassette main body 18 ... Radiation source main body 44 ... Radiation source 46 ... Radiation 50 ... Subject 86 ... Radiation detector 92 ... Cassette control unit 280 ... PC
DESCRIPTION OF SYMBOLS 300 ... 1st energy input / output part 302 ... 2nd energy input / output part 304 ... Battery part 306 ... Battery control part 308 ... Battery 334 ... Power control part 336 ... Power supply starting part 370 ... Power supply path setting part 372 ... Power supply Quantity setting unit 374 ... Power supply control unit 376 ... Remaining amount detection unit 390 ... Power management unit 420 ... Current collection unit

Claims (13)

A radiation source body that houses a radiation source that outputs radiation;
A portable radiographic imaging device having a detector main body that houses a radiation detector that detects radiation transmitted through the subject and converts it into a radiographic image when the radiation source irradiates the subject with the radiation; There,
At least one of the radiation source main body part and the detector main body part has a power supply regulation unit that regulates and controls power supply,
The power supply regulation unit
A power controller that controls bidirectional power supply between the battery in the radiation source body and the battery in the detector body;
A radiographic imaging, comprising: a power supply limiting unit that limits power supply between the radiation source main body and the detector main body by the power control unit during a period during which radiography is performed. apparatus. The radiographic imaging apparatus according to claim 1,
The radiographic imaging apparatus, wherein the power supply restriction unit stops power supply between the radiation source main body and the detector main body by the power control unit. The radiographic imaging apparatus according to claim 1,
The power supply restriction unit reduces a supply amount per unit time of power supply between the radiation source main body and the detector main body by the power control unit. The radiographic imaging apparatus according to claim 1,
The radiographic imaging apparatus, wherein the power supply restriction unit controls power supply between the radiation source main body and the detector main body in a stepwise manner by the power control unit. The radiographic imaging apparatus according to claim 1,
The radiographic imaging apparatus, wherein the power control unit controls to supply power only along a path from the radiation source main body to the detector main body based on a power supply request. The radiographic imaging apparatus according to claim 1,
The radiographic imaging apparatus, wherein the power control unit controls the power storage unit of the radiation source body unit to supply power to the power storage unit of the detector body unit. The radiographic imaging device according to claim 6,
The power storage unit of the radiation source main body is a battery that supplies power to the radiation source,
The radiation image capturing apparatus according to claim 1, wherein the power storage unit of the detector body is a built-in capacitor that supplies power to the radiation detector. The radiographic imaging apparatus according to claim 1,
The power control unit controls to supply power only along a path from the detector main body to the radiation source main body based on a power supply request. The radiographic imaging apparatus according to claim 1,
The radiographic imaging apparatus, wherein the power control unit controls the power storage unit of the detector main body to supply power to the power storage unit of the radiation source main body. The radiographic imaging apparatus according to claim 9, wherein
The power storage unit of the radiation source main body is a built-in capacitor that supplies power to the radiation source,
The radiation image capturing apparatus according to claim 1, wherein the power storage unit of the detector body is a battery that supplies power to the radiation detector. The radiographic imaging apparatus according to claim 1,
The power control unit includes a power management unit that manages power necessary for the number of shots,
The power management unit has a power shortage with respect to the necessary power from a side where power is surplus with respect to the necessary power among at least the radiation source main body and the detector main body. And a radiation image capturing apparatus, wherein: The radiographic imaging apparatus according to claim 1,
The radiation detector includes a photoelectric conversion unit that absorbs light converted by the scintillator and generates a charge corresponding to the light;
A signal output unit that outputs the electric charge generated in the photoelectric conversion unit as an electrical signal corresponding to radiation image information,
The photoelectric conversion unit is configured to include an organic photoconductor,
The radiographic imaging apparatus characterized in that the signal output unit includes a channel layer made of an organic semiconductor material. A radiation source main body that houses a radiation source that outputs radiation, and a radiation detector that detects radiation transmitted through the subject and converts it into a radiation image when the radiation source irradiates the subject with the radiation. A power supply method for a portable radiographic imaging device having a detector main body,
Controlling bi-directional power supply between the battery in the source body and the battery in the detector body; and
And a step of restricting power supply between the radiation source main body and the detector main body during a period during which radiographing is performed.

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