JP2013027654A - Radiation detecting device, radiographic device, mobile radiographic imaging device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiation detecting device that can accommodate electric power from the radiation detecting device having a power-supply source to the other apparatuses while easily performing a radiography for a long time in a disaster site or the like, and to provide a radiographic device and a mobile radiographic imaging device.SOLUTION: The radiation detecting device includes: a case body; a radiation detector provided in the case body for converting the radiation transmitting through a photographic subject into radiographic image information; a power-supply source 58; and a power transmission section 60 for transmitting at least one part of electric power from the power-supply source 58 to external apparatuses.

Description

  The present invention relates to a radiation detection apparatus, a radiation imaging apparatus, and a mobile radiographic imaging apparatus. For example, the power generated outdoors can be interchanged with other devices so that medical actions can be easily performed at a disaster site or the like. The present invention relates to a radiation detection apparatus, a radiation imaging apparatus, and a mobile radiographic imaging apparatus.

  In recent years, there has been an increasing demand for imaging of critically ill patients who are difficult to move from a hospital room and emergency imaging in an operating room. There is an increasing need for doctors to quickly and accurately check the images that have been taken.

  In order to meet such needs, mobile radiographic imaging devices have been proposed. As a prior art of the mobile radiographic imaging apparatus, for example, a mobile round-table wheel described in Patent Document 1 can be cited.

  The traveling round-trip car described in Patent Document 1 includes a carriage that can be moved electrically or manually, and a radiation imaging apparatus main body installed on the carriage. The radiographic apparatus main body includes at least an X-ray source, a cassette containing a stimulable phosphor panel in which radiographic image information of a subject is recorded, an image reading device that reads radiation image information from the stimulable phosphor panel of the cassette, A battery for supplying power to various devices. In particular, Patent Document 1 also describes an example in which an electronic cassette containing a radiation solid detector is used instead of a cassette containing a stimulable phosphor panel.

  Conventionally, there has been proposed an example in which a hot spot is not generated by adjusting the temperature of the electronic cassette during storage of the flat panel detector (electronic cassette) (Patent Document 2). Although there is no specific description regarding the power supply source in this Patent Document 2, there is a description that the device for charging the battery of the electronic cassette may be provided.

In recent years, field electron emission type radiation sources using carbon nanotubes (CNT) have been developed (see Patent Document 3 and Non-Patent Document 1), and miniaturization of a radiographic imaging apparatus including the radiation source has been developed. In addition, weight reduction is expected. In addition, a small high-energy X-ray source using LiTaO ₃ crystal, which is a typical pyroelectric crystal, has been developed (see Non-Patent Document 2).

  Further, Non-Patent Document 3 and Non-Patent Document 4 are known as methods for transmitting power wirelessly. 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.

JP 2009-201561 A JP 2006-102492 A 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, [2009 7 Month 8 Search], Internet <URL: http: // www. aist. go. jp / aist_j / press_release / pr2009 / pr200990319 / pr200990319. html> Advances in X-Ray Chemical Analysis, Japan, 41 (2010) p. 195-p. 200 “Applying Pyroelectric Crystal to Small High Energy X-Ray Source” 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”

  However, the round-trip wheel as shown in the above-mentioned Patent Document 1 is intended only to capture a radiographic image of a patient in a hospital room in a hospital, and is not configured to be used outdoors in a disaster area or the like. . In addition, since the battery that has been charged in advance is mounted and used, the travel distance of the round-trip car and the number of imaging are limited by the power consumption (remaining amount) of the battery.

  Most of the transportation of medical equipment to the stricken area uses vehicles such as trucks and ambulances, and the transportation destination is a tent where medical teams gather. Carrying a medical instrument to the victim is difficult with a vehicle or the like, and is currently carried by a doctor, nurse, radiographer, etc. by hand. There is a similar problem even if a conventional mobile power supply vehicle is used.

  Using a small radiation detector makes it easier to carry by hand, but it requires a separate battery and is cumbersome.

  Also, depending on the victim's damage situation, it may be necessary to perform an electrocardiogram or ultrasonic diagnosis in addition to radiography, but such a case cannot be dealt with quickly. The victims themselves had to be transported or taken to a tent where medical teams gathered for electrocardiograms and ultrasound diagnosis. In Patent Document 2, there is a description that a device for charging a battery may be provided, but since its specific configuration is not described, it is unclear how to configure it. Moreover, since only the example in which a plurality of electronic cassettes are integrated is described in Patent Document 2, it is completely unknown how to supply power to a plurality of different medical devices.

  The present invention has been made in consideration of such problems. Power can be interchanged from a radiation detection apparatus having a power supply source to other devices, and radiation imaging at a disaster site or the like can be easily performed over a long period of time. It is an object of the present invention to provide a radiation detection apparatus that can be performed in a simple manner.

  Another object of the present invention is to supply power from a power supply source at least to equipment necessary for radiography (radiation source, radiation detector, etc.) at a disaster site, etc. An object of the present invention is to provide a radiographic apparatus capable of easily performing medical practice in Japan.

  Another object of the present invention is to carry medical devices including at least devices necessary for radiography (radiation sources, radiation detectors, etc.) to disaster victims such as disaster sites at the same time. It is an object of the present invention to provide a mobile radiographic imaging apparatus that can supply power to medical equipment at a site and can easily perform a medical practice at a disaster site or the like.

[1] A radiation detection apparatus according to a first aspect of the present invention includes a housing, a radiation detector that is installed in the housing and converts radiation transmitted through a subject into radiation image information, a power supply source, and the power. A power transmission unit configured to transmit at least part of the power from the supply source to an external device, and the power supply source is a solar cell panel installed on a surface of the casing. And

[2] In the first aspect of the present invention, a power distributor that distributes power from the power supply source to at least the power transmission unit and the radiation detector may be provided.

[3] In the first aspect of the present invention, a power storage unit that is installed in the housing and supplies power to at least the radiation detector; power from the power supply source; and at least the power transmission unit and the power You may make it have a power divider | distributor distributed to an accumulation | storage part.

[4] In the first aspect of the present invention, a power receiving unit that receives power from a power transmitting unit in another device and supplies the power to at least the radiation detector may be provided.

[5] In the first aspect of the present invention, the power storage unit that is installed in the casing and supplies power to at least the radiation detector, and receives power from a power transmission unit in another device, the power You may make it have a power receiving part supplied to an accumulation | storage part.

[6] In this case, the solar cell panel may be installed on the surface of the casing opposite to the irradiation surface irradiated with the radiation transmitted through the subject.

[7] In the first aspect of the present invention, the solar battery panel may further include a case that houses the housing, and the power supply source may be a solar cell panel installed on a surface of the case.

[8] In the first aspect of the present invention, the power transmission unit may transmit power to the external device in a non-contact manner, and the radiation detection device itself may function as a power source of a non-contact power feeding method.

[9] A radiation imaging apparatus according to a second aspect of the present invention includes one or more devices used for radiation imaging, a case in which the devices are detachably accommodated, a power supply source, and a power supply source. A power transmission unit configured to transmit at least part of the electric power to a device outside the case, wherein the power supply source is a solar cell panel installed on a surface of the case.

[10] In the second aspect of the present invention, a power distributor that distributes power from the power supply source to at least the power transmission unit and the device in the case may be provided.

[11] In the second aspect of the present invention, the device to be taken in and out of the case has a housing and a power storage unit installed in the housing, and the power from the power supply source is You may make it have an electric power divider | distributor distributed to at least the said power transmission part and the said electric power storage part.

[12] In the second aspect of the present invention, a power receiving unit that receives power from a power transmitting unit in another device and supplies the power to the device in the case may be provided.

[13] In this case, two or more devices can be inserted into and removed from the case, and a second power distributor that distributes the power from the power receiving unit to the two or more devices may be provided.

[14] Alternatively, two or more devices can be freely inserted into and removed from the case, and the two or more devices each include a housing and a power storage unit installed in the housing, and the power receiving unit. A second power distributor that distributes the power from the power to each of the power storage units in the two or more devices.

[15] In the second aspect of the present invention, the power transmission unit may transmit power to a device outside the case in a non-contact manner so that the radiation imaging apparatus itself functions as a power source of a non-contact power feeding method.

[16] A mobile radiographic imaging device according to a third aspect of the present invention is a movable carriage and a radiation that is detachable from the carriage and detects radiation transmitted through a subject and converts it into radiation image information. One or more detector main bodies that house the detector, one or more power supply sources, a power distributor that is installed in the cart and distributes power from the power supply source, and is installed and distributed in the cart And a plurality of cart side power transmission units that transmit the generated electric power toward the corresponding detector main body unit.

[17] In the third aspect of the present invention, the detector main body may further include a power receiving unit that receives power from the cart-side power transmission unit and supplies the power to at least the radiation detector.

[18] In the third aspect of the present invention, the detector body further receives at least power from a power storage unit that supplies power to the radiation detector and the cart side power transmission unit, and stores the power. A power receiving unit that supplies power to the unit.

[19] In the third aspect of the present invention, the apparatus further includes one or more radiation source main bodies that are detachable from the carriage and contain a radiation source that outputs radiation toward the detector main body. The plurality of carriage-side power transmission units may transmit the distributed power toward at least one of the radiation source main body and the detector main body.

[20] In this case, the radiation source main body may further include a power receiving unit that receives power from the carriage-side power transmission unit and supplies at least the radiation source.

[21] Alternatively, the radiation source main body further includes at least a power storage unit that supplies power to the radiation source, and a power reception unit that receives power from the carriage-side power transmission unit and supplies the power to the power storage unit. You may make it have.

[22] In the third aspect of the present invention, the power supply source is installed in at least one detector main body, and the detector main body in which the power supply source is installed is supplied with power from the power supply source. You may make it have an apparatus side power transmission part which transmits at least one part of to the said electric power divider | distributor.

[23] In the third aspect of the present invention, the power generator has two or more power supply sources, and a current collector that collects power from each of the power supply sources is installed in the cart, and the power distributor is You may make it distribute the electric power from a current collection part.

[24] In this case, the two or more power supply sources are each installed in the detector main body, and the detector main body in which the power supply source is installed has at least one of the power from the power supply source. You may make it have an apparatus side power transmission part which transmits a part to the said current collection part.

[25] In [22] or [24], the power supply source may be a solar cell panel installed on a surface of the detector main body.

[26] In this case, the cart has a shelf in which at least the detector main body is accommodated, and in the power generation in the solar cell panel, a part or all of the radiation detector is drawn from the shelf, You may make it carry out in the state which faced the said solar cell panel upwards.

[27] Further, the carriage may include two or more shelves in which at least two or more detector main bodies are accommodated, and the two or more shelves may be provided on at least two side surfaces of the carriage. Good.

[28] A mobile radiographic imaging device according to a fourth aspect of the present invention is a movable cart, and a radiographic device having one or more devices that are detachable from the cart and used for radiography. One or more power supply sources, a power distributor installed in the cart and distributing power from the power supply source, and the power installed and distributed in the cart directed to the corresponding radiation imaging apparatus And a plurality of cart-side power transmission units that transmit power.

[29] In the fourth aspect of the present invention, the power supply source is installed in at least one of the radiation imaging apparatuses, and the radiation imaging apparatus in which the power supply source is installed receives at least power from the power supply source. You may make it have a part apparatus side power transmission part which transmits a part to the said electric power divider | distributor.

[30] In the fourth aspect of the present invention, the power generator has two or more power supply sources, and a current collector that collects power from each of the power supply sources is installed on the carriage, and the power distributor is You may make it distribute the electric power from a current collection part.

[31] In this case, the two or more power supply sources are each installed in the radiation imaging apparatus, and the radiation imaging apparatus in which the power supply source is installed receives at least a part of the power from the power supply source. A device-side power transmission unit that transmits power to the current collector may be provided.

[32] In [29] or [31], the radiographic imaging device has a case in which one or more of the devices used for radiography are accommodated in a removable manner, and the power supply source is the case It may be a solar cell panel installed on the surface.

[33] In this case, the carriage has at least an accommodating portion in which the case is accommodated, and power generation in the solar cell panel is accommodated in a state where the case faces the solar cell panel upward. You may be made to perform in.

  As described above, according to the radiation detection apparatus of the present invention, power can be interchanged from a radiation detection apparatus having a power supply source to other devices, and radiation imaging at a disaster site or the like can be easily performed over a long period of time. Can be done.

  Further, according to the radiation imaging apparatus of the present invention, in a disaster site or the like, the power from the power supply source can be supplied at least to equipment (radiation source, radiation detector, etc.) necessary for radiation imaging. And can easily carry out medical treatments at disaster sites.

  Moreover, according to the mobile radiographic imaging apparatus according to the present invention, medical equipment including at least equipment (radiation source, radiation detector, etc.) necessary for radiography is transported to a victim at a disaster site at a time. In addition, power can be supplied to the medical device at the disaster site and the like, and medical practice at the disaster site can be easily performed.

It is explanatory drawing which shows an example of the radiography apparatus (1st radiography apparatus) which concerns on 1st Embodiment. It is a perspective view which shows the cassette main-body part and radiation source main-body part of a 1st radiography apparatus. It is sectional drawing which looked at the cross section along the horizontal surface of the 1st radiography apparatus in FIG. 2 in the direction of III-III. It is a top view which shows the state which separated the radiation source main-body part from the cassette main-body part of the 1st radiography apparatus. It is sectional drawing which shows the inside of the radiation source main-body part of a 1st radiography apparatus. It is sectional drawing which shows imaging | photography by a 1st radiography apparatus. It is a perspective view which shows the imaging preparations of a 1st radiography apparatus. It is a perspective view which shows imaging | photography by the 1st radiography apparatus. It is a perspective view which shows the back side of the cassette main-body part of a 1st radiography apparatus. It is a block diagram which shows the electric power supply system of the cassette main-body part of a 1st radiography 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 a radiography apparatus (1st radiography apparatus-5th radiography apparatus). It is sectional drawing which abbreviate | omits and shows an example of the printer installed in a cassette main-body part. It is a block diagram which shows the electric power supply system of the cassette main-body part of the radiography apparatus (2nd radiography apparatus) which concerns on 2nd Embodiment. FIG. 16A is a perspective view showing a radiation imaging apparatus (third radiation imaging apparatus) according to the third embodiment together with other portable information terminals and a console, and FIG. 16B is a perspective view showing a bottom side of the third radiation imaging apparatus. FIG. It is a block diagram which shows the electric power supply system of a 3rd radiography apparatus. It is a block diagram which shows the electric power supply system of the radiography apparatus (4th radiography apparatus) which concerns on 4th Embodiment. It is a perspective view which shows the cassette main-body part and radiation source main-body part of the radiography apparatus (5th radiography apparatus) which concerns on 5th Embodiment. It is explanatory drawing which shows a mode that the operator is carrying the 5th radiography apparatus. It is sectional drawing which looked at the cross section along the horizontal surface of the 5th radiography apparatus in FIG. 19 in the direction of XXI-XXI. It is a top view which shows the state which separated the radiation source main-body part from the cassette main-body part of the 5th radiography apparatus. It is a perspective view which shows the back side of a 5th radiography apparatus. It is a perspective view which shows the movement type radiographic imaging apparatus (1st movement apparatus) which concerns on 1st Embodiment. It is a block diagram which shows the electric power supply system of a 1st moving apparatus. It is a block diagram which shows the electric power supply system of the movement type radiographic imaging apparatus (2nd movement apparatus) which concerns on 2nd Embodiment. It is a perspective view which shows the movement type radiographic imaging apparatus (3rd movement apparatus) which concerns on 3rd Embodiment. 28A to 28C are explanatory views showing a configuration example of an attaching / detaching mechanism with respect to the arm portion of the radiation source main body portion. It is a block diagram which shows the electric power supply system of a 3rd moving apparatus. It is a perspective view which shows the movement type radiographic imaging apparatus (4th moving apparatus) which concerns on 4th Embodiment. It is sectional drawing which abbreviate | omits and shows an example of the printer installed in the trolley | bogie of a 4th moving apparatus. FIG. 32A is a perspective view showing a mobile radiographic image capturing apparatus (fifth mobile apparatus) according to the fifth embodiment, and FIG. 32B is a plan view showing the fifth mobile apparatus as viewed from above. It is a block diagram which shows the electric power supply system of a 5th moving apparatus. It is a figure which shows roughly the structure for 3 pixels of the radiation detector which concerns on a modification. FIG. 35 is a schematic configuration diagram of a TFT and a charge storage unit shown in FIG. 34.

  Hereinafter, embodiments of a radiation detection apparatus, a radiation imaging apparatus, and a medical moving apparatus according to the present embodiment will be described with reference to FIGS.

  First, a radiographic apparatus according to the first embodiment (hereinafter, referred to as a first radiographic apparatus 10A) includes, for example, a case 14 having a handle 12 such as an attache case as shown in FIG. A cassette body 16 (radiation detection device) having a substantially rectangular outer shape housed therein, a columnar radiation source body 18, and a portable information terminal 20 are included. As the portable information terminal 20, for example, a portable information terminal having a size of about B5 and having a touch panel function can be used. When the cassette body 16 and the like are accommodated in the case 14, the cassette body 16 and the radiation source body 18 are accommodated in the body 14a of the case 14, and the portable information terminal 20 is accommodated in the lid 14b of the case 14. To accommodate.

  As shown in FIG. 2, the cassette body 16 includes a housing 22 made of a material having a substantially rectangular outer shape and capable of transmitting radiation 50 (see FIG. 6). On one surface (irradiation surface 24) of the housing 22, a guide line 26 serving as a reference for an imaging region and an imaging position is formed. A handle 30 is provided on one long first side surface 28 a of the housing 22. Further, of the two short side surfaces (the second side surface 28b and the third side surface 28c) of the housing 22, the second side surface 28b has a USB (Universal) as an interface means capable of transmitting / receiving information to / from an external device. A serial bus) terminal 32 and a card slot 36 into which a memory card 34 is loaded.

  Further, as shown in FIG. 3, a measure 38 is also arranged in the cassette body 16. The measure 38 is, for example, a measure that winds the band member 42 with the scale 40 swung into a roll shape by the action of a spring member (not shown), and the side of the measure 38 has a band member 42 from the measure 38 on the side. A rotary encoder 44 for detecting the drawing amount is attached. The distal end portion of the band member 42 drawn out from the measure 38 is fixed to the radiation source main body portion 18 through a hole 46 formed at a location facing the measure 38 in the other long fourth side surface 28d of the cassette main body portion 16. Has been.

  Therefore, as shown in FIG. 3, in a state where the radiation source body 18 is brought close to the cassette body 16, most of the band member 42 is rolled in the measure 38 by the action of the spring member inside the measure 38. Rolled up. On the other hand, as shown in FIGS. 4 to 8, when the cassette body 16 and the radiation source body 18 are separated, the radiation source body 18 is separated from the cassette body 16 against the action of the spring member. Thus, the band member 42 can be pulled out from the measure 38 through the hole 46.

  In the above description, the measure 38 can wind the band member 42 with the scale 40 swung, but instead of the band member 42, the measure 38 is a string member (string) with the scale 40 swung. Of course, the same function as that of the belt member 42 can be achieved.

  Furthermore, as shown in FIG. 6, the cassette main body 16 includes a radiation 50 from the radiation source main body 18 to the subject 48 (a victim, a victim, a medical examinee, a home-stayed person or the like who is a subject of radiographic imaging). A grid 52 for removing scattered radiation of the radiation 50 from the subject 48, a radiation detector 54 for detecting the radiation 50 transmitted through the subject 48, and a lead plate 56 for absorbing the back scattered radiation of the radiation 50. These are arranged in order with respect to the irradiation surface 24 on the object 48 side. Note that the irradiation surface 24 may be configured as a grid 52.

  As the radiation detector 54, for example, the radiation 50 transmitted through the subject 48 is temporarily converted into visible light by a scintillator, and the converted visible light is a solid-state detection element (hereinafter referred to as “a-Si”). An indirect conversion type radiation detector (including a front side reading method and a back side reading method) that converts to an electric signal can also 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 arranged in order along the irradiation direction of the radiation 50. 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 50. Further, as the radiation detector 54, in addition to the above-described indirect conversion type radiation detector, direct conversion in which the dose of the radiation 50 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 be employed.

  Further, as shown in FIG. 2 and the like, the cassette body 16 makes contact with, for example, a power supply source 58 (see FIGS. 6 and 9) and at least a part of the power from the power supply source 58 (wired or the like). And a power transmission unit 60 that transmits power to other devices by non-contact (wireless etc.) and a power receiving unit 62 that receives power (power reception) by contact (wired etc.) or non-contact (wireless etc.), for example. ing.

  6 and 9, a solar cell panel 64 is used as the power supply source 58, and the solar cell panel 64 is the irradiation surface 24 irradiated with the radiation 50 transmitted through the subject 48 on the surface of the housing 22. An example is shown in which the power transmission unit 60 and the power reception unit 62 are provided on the second side surface 28b of the surface of the housing 22 as shown in FIG.

  As the solar cell panel 64, a commercially available small solar cell panel or a flexible solar cell panel can be used. As the power supply source 58, a bio battery, a fuel cell, and the like can be preferably used in addition to the solar cell panel 64 described above.

  Inside the cassette body 16, as shown in FIG. 3 and the like, a battery 68 (power storage unit) as a power source of the cassette body 16, and at least the power transmission unit 60 and the battery 68 receive power from the power supply source 58. A power distribution unit 70 that distributes the battery 68, a cassette control unit 72 that drives and controls the radiation detector 54 (see FIG. 6) with power supplied from the battery 68, and a remaining amount detection unit 74 that detects the remaining amount of the battery 68. A transmitter / receiver 76 that receives and transmits a signal including information on the radiation 50 detected by the radiation detector 54 is accommodated. The power received by the power receiving unit 62 is supplied to the battery 68.

  When the battery 68 is not built in, the power from the power supply source 58 may be distributed to the power transmission unit 60, the radiation detector 54, the cassette control unit 72, and the like in the power distributor 70. Similarly, the power received by the power receiving unit 62 may be supplied to the radiation detector 54, the cassette control unit 72, and the like. Further, the battery 68, the power distributor 70, the cassette controller 72, the transmitter / receiver 76, and the like are prevented from being damaged by the radiation 50, so that the battery 68, the power distributor 70, the cassette controller 72, and the transmitter / receiver are transmitted. It is preferable to arrange a lead plate or the like on the irradiation surface 24 side of the machine 76 or the like.

  As shown in FIG. 10, the power transmission unit 60 includes, for example, an energy output unit 78 that outputs power and the like by contact (wired or the like) or non-contact (wireless or the like), and power from the power distributor 70 as an energy output unit. And an output energy conversion unit 80 that converts the energy into the energy output unit 78 according to the type of the energy.

  The power receiving unit 62 includes, for example, an energy input unit 82 that receives input of electric power or the like by contact (wired or the like) or non-contact (wireless or the like), and an input energy conversion unit 84 that converts energy from the energy input unit 82 into electric power. Have

  The energy output unit 78, the output energy conversion unit 80, the energy input unit 82, and the input energy conversion unit 84 have different configurations depending on the type of energy (supply energy) to be supplied.

  For example, if power is supplied by a wired connection such as a cable or a connection terminal, the energy output unit 78 and the energy input unit 82 are connectors connected to the cable and the connection terminal, for example. The output energy conversion unit 80 is, for example, a voltage converter that converts the voltage supplied from the power distributor 70 into an optimum voltage for power transmission. The input energy conversion unit 84 is, for example, a voltage converter that converts a voltage input via the energy input unit 82 into an optimum voltage for supplying to a battery or the like.

  In the case of electromagnetic induction by a coil (primary coil or secondary coil) embedded in a non-contact power transmission sheet as in Non-Patent Document 3, the energy output unit 78 is a primary coil, and the energy input unit 82 is a secondary coil. is there. The output energy conversion unit 80 is a voltage-current converter or the like that converts the voltage supplied from the power distributor 70 into a current that flows to the energy output unit 78 (in this case, functions as a primary coil). Reference numeral 84 denotes, for example, a voltage converter that converts the voltage generated by the energy input unit 82 (in this case, functioning as a secondary coil) into an optimum voltage for supplying to a battery or the like.

  In the case of wireless power transmission technology using magnetic field resonance as in Non-Patent Document 4, the energy output unit 78 is a first LC resonator for power transmission, and the energy input unit 82 corresponds to the first LC resonator. It is the 2nd LC resonator installed. The output energy conversion unit 80 is a coil for outputting the voltage supplied from the power distributor 70 as electromagnetic energy from the energy output unit 78 (which functions as the first LC resonator in this case) (the coil of the first LC resonator). The input energy conversion unit 84 converts the electromagnetic energy generated by the energy input unit 82 (in this case, functioning as a second LC resonator) into electric energy by electromagnetic induction. A coil to be converted (secondary coil when the coil of the second LC resonator is a primary coil) or the like.

  Of course, the supply energy may be light energy or heat energy. In the case of light energy, the energy input unit 82 is a light energy receiving unit, and the input energy conversion unit 84 corresponds to a photoelectric conversion unit that converts the received energy into electric power. In the case of thermal energy, the energy input unit 82 is a heat receiving unit that receives thermal energy, and the input energy conversion unit 84 is a thermoelectric conversion element that converts received heat into electric power (for example, a thermoelectric conversion element using the Seebeck effect). Etc.

  As the battery 68, 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 68 may be constituted by a small built-in capacitor capable of storing an amount of power necessary for photographing at least one sheet.

  Since the transmitter / receiver 76 can transmit / receive signals to / from the outside, the transmitter / receiver 76 transmits / receives signals to / from the portable information terminal 20 or the transmitter / receiver 90 (of the radiation source main body 18 separated from the cassette main body 16). Signal transmission / reception to / from the console (not shown) and signal transmission / reception to / from a console (an apparatus that controls the cassette body 16 and the radiation source body 18 to perform radiation imaging) are performed. Is possible.

  On the other hand, the radiation source body 18 has a cylindrical casing 86 as shown in FIG. As shown in FIG. 5, the housing 86 includes a radiation source 88, a battery 68, a remaining amount detection unit 74, a transceiver 90, a radiation source control unit 92 that controls the radiation source 88, A laser pointer 94 is arranged. A power receiving unit 62 similar to the cassette body 16 is provided on the side surface of the housing 86, and the power received by the power receiving unit 62 is supplied to the battery 68. When the battery 68 is not built in, the power received by the power receiving unit 62 may be supplied to the radiation source 88, the radiation source control unit 92, and the like. Further, as shown in FIG. 2, an exposure switch 96 for starting output of radiation 50 (see FIG. 6) from the radiation source 88 is provided on the side surface of the housing 86.

  The radiation source 88 is a radiation source using a field electron emission electron source similar to the field electron emission electron source described in Patent Document 3 described above.

  That is, as shown in FIG. 5, the radiation source 88 has a disk-shaped rotating anode 102 attached to a rotating shaft 100 rotated by a rotating mechanism 98, and a metal element such as Mo is mainly formed on the surface of the rotating anode 102. An annular target layer 104 as a component is formed. On the other hand, a cathode 106 is disposed so as to face the rotating anode 102, and a field electron emission electron source 108 is disposed on the cathode 106 so as to face the target layer 104. Furthermore, it has the 1st power supply part 110 which applies a voltage (negative voltage) to the field electron emission electron source 108, and the 2nd power supply part 112 which applies a voltage between the rotating anode 102 and the cathode 106. FIG.

The radiation source control unit 92 controls the radiation source 88 to output the radiation 50 due to the operation of the exposure switch 96 by the operator. In other words, in the radiation source 88, the rotating mechanism 98 rotates the rotating shaft 100 according to the control from the radiation source control unit 92, whereby the rotating anode 102 rotates, and the first power supply unit 110 is based on the power supply from the battery 68. When a voltage (negative voltage) is applied to the field electron emission electron source 108 and the second power supply unit 112 applies a voltage between the rotating anode 102 and the cathode 106 based on power supply from the battery 68 ( When a positive voltage is applied to the rotating anode 102 and a negative voltage is applied to the cathode 106), electrons are emitted from the field electron emission type electron source 108, and the emitted electrons are applied between the rotating anode 102 and the cathode 106. Accelerated by the generated voltage and collides with the target layer 104. From the electron collision surface (focal point 116) in the target layer 104, radiation 50 corresponding to the collided electrons is output to the outside. As the radiation source 88, 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, a voltage of about 100 kV can be generated by using LiNbO ₃ with an axial length of 1 cm.

  By the way, when a radiation image is taken by irradiating the subject 48 with the radiation 50, it is between the focal point 116 of the radiation source 88 and the position 118 (see FIG. 6) of the radiation detector 54 just below the focal point 116. The distance (inter-imaging distance) is set in advance as the distance between the source image and the received image (SID), and the central position of the irradiation range of the radiation 50 on the irradiation surface 24 and the central position 120 (see FIG. 2) of the guide line 26 (see FIG. 2). It is necessary to perform a shooting preparation work including a work of matching the intersection of two guide lines 26 intersecting in a cross shape.

  In this case, as shown in FIGS. 6 and 7, the operator pulls out the band member 42 from the measure 38 in accordance with the SID while the radiation source body 18 is separated from the cassette body 16. The belt member 42 is pulled out until Further, the laser pointer 94 projects the laser beam 122 onto the irradiation surface 24 according to the control from the radiation source control unit 92 (see FIG. 5), so that the radiation 50 is irradiated when the irradiation surface 24 is irradiated with the radiation 50. The center position of the irradiation range is displayed on the irradiation surface 24 as a cross-shaped mark 124.

In addition, SID≈ is generally between the distance l2 between the position 118 and the center position 120 and the side surface 28d provided with the hole 46 from which the band member 42 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 42 is pulled out from the measure 38 by the pull-out amount l1, the position of the radiation source body 18 is adjusted so that the position of the mark 124 displayed on the irradiation surface 24 and the center position 120 coincide with each other. Thereafter, as shown in FIG. 8, the radiation image of the subject 48 is irradiated by irradiating the subject 50 disposed on the irradiation surface 24 from the radiation source 88 due to the operator turning on the exposure switch 96. It is possible to appropriately perform the shooting. In FIG. 8, a case where the hand of the subject 48 is photographed is illustrated.

  As schematically shown in FIG. 11, the radiation detector 54 has a large number of pixels 126 arranged on a substrate (not shown), a large number of gate lines 128 that supply control signals to the pixels 126, and a large number of gates 128. A large number of signal lines 130 for reading out electrical signals output from the pixels 126 are arranged.

  Next, as an example, the circuit configuration of the cassette body 16 when the indirect conversion type radiation detector 54 is employed will be described in detail with reference to FIG.

  The radiation detector 54 has a photoelectric conversion layer 132 in which each pixel 126 made of a substance such as a-Si that converts visible light into an electrical signal is formed on an array of TFT-shaped TFTs (Thin Film Transistors) 134. It has an arranged structure. In this case, in each pixel 126, 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 134 for each row. .

  A gate line 128 extending in parallel with the row direction and a signal line 130 extending in parallel with the column direction are connected to the TFT 134 connected to each pixel 126. Each gate line 128 is connected to a line scan driver 136, and each signal line 130 is connected to a multiplexer 138. Control signals Von and Voff for controlling on / off of the TFTs 134 arranged in the row direction are supplied from the line scan driving unit 136 to the gate line 128. In this case, the line scan driving unit 136 includes a plurality of switches SW1 for switching the gate lines 128 and an address decoder 140 for outputting a selection signal for selecting one of the switches SW1. An address signal is supplied to the address decoder 140 from the cassette control unit 72.

  In addition, the charge held in each pixel 126 flows out to the signal line 130 through the TFTs 134 arranged in the column direction. The signal due to this charge is amplified by the amplifier 142. A multiplexer 138 is connected to the amplifier 142 via a sample and hold circuit 144. The multiplexer 138 includes a plurality of switches SW2 for switching the signal line 130, and an address decoder 146 that outputs a selection signal for selecting one of the switches SW2. An address signal is supplied from the cassette control unit 72 to the address decoder 146. An A / D converter 148 is connected to the multiplexer 138, and a radiographic image converted into a digital signal by the A / D converter 148 is supplied to the cassette control unit 72.

  Note that the TFT 134 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 the charges by a shift pulse corresponding to the gate signal referred to in the TFT 134.

  FIG. 13 is a block diagram of the first radiation imaging apparatus 10A. In the description of FIG. 13, the description will focus on components that are not described in FIGS. 2 to 12.

  The portable information terminal 20 includes an operation unit 150 operated by an operator, a battery 68, a remaining amount detection unit 74, a display unit 152 on which radiation image information and the like are displayed, a radiation source body unit 18, a cassette body unit 16, and the like. A transmitter / receiver 154 that communicates with each other, and a terminal control unit 156 that controls them.

  The cassette control unit 72 of the cassette body 16 includes an address signal generation unit 158, an image memory 160, an SID determination unit (inter-shooting distance determination unit) 162, and a power distribution setting unit 164.

  The address signal generator 158 supplies an address signal to the address decoder 140 of the line scan driver 136 and the address decoder 146 of the multiplexer 138 shown in FIG. The image memory 160 stores the radiation image detected by the radiation detector 54.

  As shown in FIG. 6, the SID determination unit 162 also determines the current band member 42 based on the pull-out amount of the band member 42 from the measure 38 input from the rotary encoder 44 and the distance 12 stored in advance. The distance between the imaging between the focal point 116 and the position 118 when the radiation source main body 18 is temporarily arranged above the irradiation surface 24 is calculated by the amount of extraction.

  If the calculated inter-shooting distance matches the SID, the SID determination unit 162 sets the pull-out amount of the band member 42 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. The displayed information is displayed on the display unit 152 of the portable information terminal 20 via the transceiver 76 and the transceiver 154 of the portable information terminal 20. A mechanism may be provided that locks the belt member 42 so that the belt member 42 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 162 transmits information indicating that the difference between the current extraction amount and the extraction amount l1 and the inter-imaging distance does not match the SID to the transceiver 76, It is displayed on the display unit 152 via 154.

  The SID determination unit 162, the rotary encoder 44, and the measure 38 constitute an inter-photographing distance setting unit 166.

  The cassette control unit 72 can also transmit the ID information of the cassette body 16 and the radiation image stored in the image memory 160 to the portable information terminal 20 via the transceiver 76 via wireless communication.

  In addition, a printer 167 (driven by power supply from the battery 68) for printing data from the radiation source control unit 92 may be installed in the radiation source main body unit 18, or the cassette control unit 72 is installed in the cassette main body unit 16. A printer 168 (driven by power supply from the battery 68) for printing data from the printer may be installed. In general, printers for medical use include, for example, a printer for a heat-sensitive transmission document (first type printer), an ink jet printer for reflection originals (second type printer), and the like. If the second type printer is used, the radiation source main body 18 and the cassette main body 16 can be downsized. Note that both the first-type printer and the second-type printer consume a large amount of power. In particular, the first-type printer is a thermal head type printer (see, for example, Japanese Patent Laid-Open No. 10-51635) for miniaturization. ) Etc. may be used, but the increase in power consumption becomes significant. Thus, as will be described later, by controlling the power supply so that the power from the power supply source 58 can be interchanged, it is possible to use printers with high power consumption as the printers 167 and 168.

  Here, as an example, a printer 168 installed in the cassette body 16 will be described with reference to FIG.

  The printer 168 installed in the cassette body 16 is installed in the housing space 170 near the first side surface 28 a to which the handle 30 is attached, for example, in the housing 22 of the cassette body 16. Further, the housing 22 is provided with an opening 174 for pulling out the leading end portion of the recording material 172 to the outside of the housing 22 at a position near the first side surface 28 a in the irradiation surface 24, for example. Note that the recording material 172 is attached to the accommodation space 170 in a replaceable manner. The cassette body 16 may have a structure in which, for example, the handle 30 (the gripping part 176) can be removed. In this case, the printer 168 may be structured so as to be removable together with the grip portion 176. For example, the printer 168 may be configured to be detachably attached to the cassette body 16 with a hook 178 or the like. FIG. 14 shows an example in which a hook 178 provided on the printer 168 is engaged with the cassette body 16. When the printer 168 is removed, for example, a portion of the printer 168 close to the hook 178 may be pressed as indicated by a dashed arrow 180 to disengage the hook 178 from the cassette body 16.

  The printer 168 opens the supply roller pair 182 that pulls out the leading end of the recording material 172, the printing head 184 that prints a desired image (for example, radiographic image information) on the recording material 172, and the recording material 172 on which the image or the like is printed. A conveyance roller pair 186 that conveys the recording material 172 and a cutter 188 that cuts the recording material 172 into predetermined length units. As the printing head 184, for example, an inkjet printer head or a thermal printer head can be used. Since the printer 168 is a printer of the second type described above, the image quality is inferior to that of the printer of the first type, but can be used for urgent diagnosis purposes, confirmation of shooting conditions, and the like. In addition, character information such as imaging conditions, patient information, and GPS position information may be printed. The structure of the printer 168 for the cassette body 16 described above may be used as the printer 167 for the radiation source body 18.

  Next, the power distribution setting unit 164 incorporated in the cassette control unit 72 will be described.

  The power distribution setting unit 164 operates in the following case. That is, first, the battery remaining amount based on the information from the remaining amount detecting unit 74 of the portable information terminal 20 is displayed on the display unit 152 of the portable information terminal 20, and further, the remaining amount detecting unit of the radiation source main body unit 18. 74 and information from the remaining amount detection unit 74 of the cassette body 16 are transmitted to the portable information terminal 20, whereby the remaining battery levels of the radiation source body 18 and the cassette body 16 are also displayed. The operator inputs the power distribution ratio through the operation unit 150 while checking the remaining amount of each battery. For example, if the battery 68 of the cassette body 16 is in a fully charged state, the power distribution ratio to the power transmission unit 60 is 100%, or if the remaining amount of the battery 68 in the cassette body 16 is almost zero, If the power distribution ratio to the battery 68 is set to 100%, or if it is desired to preferentially supply power to other devices, the power distribution ratio to the power transmission unit 60 is set to a range of 80 to 100%, the battery If it is desired to supply power to 68 preferentially, the power distribution ratio to the battery 68 may be in the range of 80 to 100%. The input power distribution ratio information is transmitted to the cassette body 16.

  Then, the power distribution setting unit 164 controls the power distributor 70 based on the information on the power distribution ratio from the portable information terminal 20 and distributes power according to the power distribution ratio input at the portable information terminal 20. Set to ratio.

  And as shown in FIG. 10, the electric power from the power transmission part 60 installed in the cassette main-body part 16 is transmitted toward the power receiving part 62 of another apparatus (The radiation source main-body part 18 and the other cassette main-body part 16) ( Power). That is, the energy output unit 78 of the power transmission unit 60 of the cassette body 16 and the energy input unit 82 of the power reception unit 62 of another device can input and output energy by a cable, a connection terminal, or the like, or the energy output unit 78 and the energy input unit 82 enter an area where wireless power feeding (wireless power feeding) can be performed, and energy can be input and output in a non-contact state, so that the power from the power transmission unit 60 installed in the cassette body 16 can be obtained. Electric power is transmitted toward the power receiving unit 62 of another device. In the following description, a state in which the energy output unit 78 of the power transmission unit 60 and the energy input unit 82 of the power reception unit 62 can input and output energy through a cable, a connection terminal, or the like is referred to as “wired connection”. A state in which energy can be input and output in a non-contact state, such as 78 and the energy input unit 82 entering an area where wireless power feeding is possible, is referred to as “wireless connection”.

  The radiation imaging apparatus 10 is transported (moved) to a hospital site, a home of a home patient, a disaster site such as a disaster area, and the like. Since dust, mud, sewage, or the like may be attached at a disaster site or the like, a sealed structure may be employed for at least a portion surrounding the electrical system of the cassette body 16 and the radiation source body 18 of the radiation imaging apparatus 10. Accordingly, as a power feeding method, non-contact power feeding by wireless connection or the like is preferable to contact power feeding by wired connection or the like.

  Here, an operation for preparing for imaging using the cassette body 16 and the radiation source body 18 and an operation for actually imaging will be described.

  First, the operator selects one or more cases 14 (see FIG. 1) in which the cassette body 16, the radiation source body 18, and the portable information terminal 20 are housed, for example, a disaster site victim (a victim who needs radiation imaging). Transport to the place. When the operator arrives at the disaster site, the operator takes out the cassette body 16, the radiation source body 18, and the portable information terminal 20 from the case 14, and for example, backside of the cassette body 16 (sun Electricity is generated by the solar panel 64 with the surface on which the battery panel 64 is installed facing upward or obliquely upward. At this time, using the display unit 152 of the portable information terminal 20, the remaining battery levels of the portable information terminal 20, the cassette body unit 16, and the radiation source body unit 18 are confirmed, and the power distribution ratio according to these remaining battery levels is determined. Input is performed using the operation unit 150.

  For example, when the radiation source main body 18 or the portable information terminal 20 has a low remaining battery level and is to be charged with priority, the power transmission unit 60 of the cassette main body 16 and the power reception unit 62 of the radiation source main body 18 or the power reception of the portable information terminal 20 The unit 62 is wired or wirelessly connected, and the power distribution ratio to the power transmission unit 60 is set in the range of 80 to 100%. Of course, when the cassette main body 16 has a small remaining battery capacity and is to be preferentially charged, the power distribution ratio to the battery 68 is set in the range of 80 to 100%. When two or more cassette body parts 16 are being transported, the back surface of the cassette body part 16 that is not used for the time being (the surface on which the solar cell panel 64 is installed) is directed upward or obliquely upward. Power generation at In this case, the battery remaining amount of the cassette body 16 to be used immediately is confirmed, and if charging is necessary, the power transmission unit 60 of the cassette body 16 that is not used for the time being and the power receiving unit of the cassette body 16 to be used immediately. 62 is wired or wirelessly connected, and the power distribution ratio to the power transmission unit 60 is set in a range of, for example, 80 to 100% according to the remaining battery level.

  Thereafter, preparations for radiography are made at the stage when there is an instruction for radiography. That is, first, by operating the operation unit 150 of the portable information terminal 20, shooting conditions such as subject information (for example, SID) related to the subject 48 to be shot are registered. If the imaging region and imaging method are determined in advance, these imaging conditions are also registered in advance. If the subject 48 to be imaged is known in advance before going to the destination site, the subject information may be registered by operating the portable information terminal 20 at a medical institution to which the operator belongs.

  In this way, when the operator operates the operation unit 150 of the portable information terminal 20, shooting conditions such as subject information related to the subject 48 that is a shooting target are transmitted and received by the cassette main body unit 16 by wireless communication from the transceiver 154. Is transmitted to the machine 76 and registered in the cassette control unit 72.

  The operator performs the setting operation of the distance between photographing and the setting operation of matching the mark 124 (see FIG. 7) displayed on the irradiation surface 24 with the center position 120 of the guide line 26, and then the irradiation surface 24 and the radiation. A subject 48 is placed between the source main body 18 and the subject 48 is positioned.

  In this case, the operator first moves the radiation source main body 18 and pulls out the band member 42 until the pull-out amount of the band member 42 from the measure 38 becomes the pull-out amount 11 corresponding to the SID.

  There are the following two methods for pulling out the belt member 42 until the pulling amount l1 is reached.

  The first method is a method in which the SID determination unit 162 automatically determines whether or not the withdrawal amount l1 has been reached, and allows the operator to pull out the belt member 42 until the withdrawal amount l1 corresponding to the SID is reached.

  In the first method, the rotary encoder 44 detects the pull-out amount of the band member 42, and the SID determination unit 162 uses the current pull-out amount of the band member 42 based on the detected pull-out amount. A distance between photographing between the focal point 116 and the position 118 (see FIG. 6) when the 18 is temporarily disposed above the irradiation surface 24 is calculated.

  If the distance between images matches the SID, the SID determination unit 162 transmits information indicating that the belt member 42 is pulled out (drawing amount 11) and the distance between images matches the SID via the transceivers 76 and 154. On the other hand, if the distance between images does not match the SID, information indicating that the difference between the current withdrawal amount and the amount l1 and the distance between images does not match the SID are displayed on the transceiver 76. , 154 to display on the display unit 152.

  Therefore, according to the first method, the operator only needs to pull out the band member 42 from the measure 38 in accordance with the display content of the display unit 152, so that the setting operation of the inter-photographing distance can be easily performed.

  The second method is a method in which the operator pulls out the band member 42 from the measure 38 until the pulling amount l1 is reached while looking at the scale 40 when the pulling amount l1 is known in advance.

  In this way, after the belt member 42 is pulled out until the pulling amount 11 corresponding to the SID is reached, the operator moves the radiation source main body 18 so as to face the irradiation surface 24.

  At this time, as shown in FIG. 7, the laser pointer 94 is controlled so that the laser beam 122 is projected onto the irradiation surface 24. Accordingly, the center position of the irradiation range of the radiation 50 when the irradiation surface 24 is irradiated with the radiation 50 is displayed as a cross-shaped mark 124 on the irradiation surface 24. As a result, the operator adjusts the position of the radiation source body 18 so that the position of the mark 124 and the center position 120 coincide.

  Thus, after adjusting the position of the radiation source main body 18 so that the position of the mark 124 and the center position 120 coincide with each other, the operator sets the center of the imaging region of the subject 48 to the center position 120 (the position of the mark 124). The object 48 is arranged (positioned) on the irradiation surface 24 so as to coincide with ().

  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 48, the operator operates the exposure switch 96 to start photographing the subject 48.

  Due to the operation of the exposure switch 96, the radiation source control unit 92 requests the cassette control unit 72 to transmit the imaging conditions by wireless communication, and the cassette control unit 72 is based on the received request. The imaging condition (control signal) relating to the imaging region of the subject 48 is transmitted to the radiation source body 18. When the radiation source control unit 92 receives the imaging condition, the radiation source control unit 92 stops the projection of the laser beam 122 by the laser pointer 94 and, according to the imaging condition, emits radiation 50 having a predetermined dose to the subject 48. Source 88 is controlled.

  Thereby, in the radiation source 88, the rotation mechanism 98 rotates the rotating shaft 100 and the rotating anode 102 according to the control from the radiation source control unit 92, while the first power source unit 110 supplies power from the battery 68. Based on this, a negative voltage is applied to the field electron emission electron source 108, and the second power supply unit 112 applies a voltage between the rotating anode 102 and the cathode 106 based on power supply from the battery 68. The electrons emitted from the emission electron source 108 are accelerated by the voltage applied between the rotating anode 102 and the cathode 106 and collide with the target layer 104, and from the electron collision surface (focal point 116) of the target layer 104. The radiation 50 corresponding to the collided electrons is output to the outside.

  When the subject 50 is irradiated with the radiation 50 for a predetermined irradiation time based on the imaging conditions, the radiation 50 passes through the subject 48 and reaches the radiation detector 54 in the cassette body 16.

  When the radiation detector 54 is an indirect conversion type radiation detector, the scintillator constituting the radiation detector 54 emits visible light having an intensity corresponding to the intensity of the radiation 50 to constitute the photoelectric conversion layer 132. Each pixel 126 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 48 held in each pixel 126, is read according to the address signal supplied from the address signal generator 158 of the cassette controller 72 to the line scan driver 136 and the multiplexer 138.

  That is, the address decoder 140 of the line scan driver 136 outputs a selection signal according to the address signal supplied from the address signal generator 158 to select one of the switches SW1, and the TFT 134 connected to the corresponding gate line 128. A control signal Von is supplied to the gates of the two. On the other hand, the address decoder 146 of the multiplexer 138 outputs a selection signal in accordance with the address signal supplied from the address signal generator 158 and sequentially switches the switch SW2, and is connected to the gate line 128 selected by the line scan driver 136. Radiation images, which are charge information held in each pixel 126, are sequentially read out via the signal line 130.

  The radiographic image read from each pixel 126 connected to the selected gate line 128 is amplified by each amplifier 142, sampled by each sample hold circuit 144, and then A / D converter via the multiplexer 138. 148 to be converted into a digital signal. The radiographic image converted into the digital signal is temporarily stored in the image memory 160 of the cassette control unit 72.

  Similarly, the address decoder 140 of the line scan driver 136 sequentially switches the switch SW1 according to the address signal supplied from the address signal generator 158, and the charge held in each pixel 126 connected to each gate line 128. A radiation image as information is read out via the signal line 130 and stored in the image memory 160 of the cassette control unit 72 via the multiplexer 138 and the A / D converter 148.

  The radiographic image stored in the image memory 160 is transmitted to the portable information terminal 20 by wireless communication via the transceiver 76, and the portable information terminal 20 causes the display unit 152 to display the received radiographic image. Accordingly, the operator can grasp whether or not the imaging of the imaging region of the subject 48 has been appropriately performed by confirming the radiation image displayed on the display unit 152.

  For example, when a radiographic image that does not fit in the imaging region is displayed in the imaging region, the operator determines that the current imaging was not properly performed, and executes reimaging on the subject 48.

  Note that the radiographic image displayed on the display unit 152 may be an image that can be used to determine whether or not the current imaging is appropriate. Therefore, the radiographic image stored in the image memory 160 may be used. Or an image processed to a relatively low resolution.

  Then, the battery remaining amount of the cassette body 16 after the radiation imaging is confirmed, and the back surface (the surface on which the solar cell panel 64 is installed) of the cassette body 16 is directed upward until the next radiation imaging instruction is given. Alternatively, the solar cell panel 64 generates power in an obliquely upward direction, and at the same time, the battery is charged to the radiation source main body 18 and the portable information terminal 20. When power is generated by the solar battery panel 64 of the cassette main body 16 that is not used for the time being, the cassette main body 16 is used in the next radiography, and the cassette main body used in the previous radiography during that time. The 16 solar cell panels 64 generate electric power, and at the same time, the radiation source main body 18 and the portable information terminal 20 used in the previous radiation imaging can be charged.

  Of course, while power is being generated by the solar panel 64, the power transmission unit 60 of the cassette body 16 and other medical devices such as an electrocardiograph, an ultrasonic diagnostic device, an AED (automated external defibrillator). : Automated External Deflator, blood pressure monitor (may have a function to measure pulse and body temperature), and other medical devices necessary for taking to disaster areas etc. by wired connection or wireless connection, these Power supply to other medical devices and battery charging can be performed.

  The cassette body 16 also functions as a power source that performs non-contact power feeding. For example, while power is being generated by the solar battery panel 64, power can be transmitted from the power transmission unit 60 of the cassette body 16 to various medical devices by wireless connection (non-contact power supply). In a disaster site where it is not easy to use, the radiation imaging device can be used without worrying about the number of power supplies, the distance that the power line reaches, etc., and without restricting the work behavior to the power line, Diagnosis by radiography at disaster sites can be continued. Moreover, since it also functions as a non-contact power supply type power source for various medical devices, it is possible to continue other medical activities other than radiography and to proceed smoothly.

  Thus, in the cassette body 16 (radiation detection device) of the first radiation imaging apparatus 10A, the power supply source 58 and at least a part of the power from the power supply source 58 are transmitted to an external device. In addition to using part of the power generated by the power supply source 58 in the cassette body 16, the remaining power can be accommodated in other devices. This makes it possible to perform radiography at disaster sites where it is difficult to secure power over a long period of time, and also to supply power to other medical devices flexibly. Various medical actions including photographing can be easily performed.

  Here, “accommodating power” 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

  Next, a radiation imaging apparatus (hereinafter referred to as a second radiation imaging apparatus 10B) according to a second embodiment will be described with reference to FIG.

  The second radiation imaging apparatus 10B has substantially the same configuration as the first radiation imaging apparatus 10A described above, but includes a power distributor 70 (see FIG. 10) and a power distribution setting unit 164 as shown in FIG. However, it is different in that the power from the power supply source 58 is directly supplied to the power transmission unit 60. That is, the power distribution ratio from the power supply source 58 to the power transmission unit 60 is always 100%. Accordingly, the power supply source 58 in the second radiation imaging apparatus 10B is used exclusively as a power supply source for supplying power to other devices.

  Usually, depending on the frequency of use of the radiation imaging apparatus, the number of defective pixels of the radiation detector 54 may increase, or the degree of deterioration of the battery 68 may increase, and such a radiation imaging apparatus cannot be used in the middle. There is. Even in this case, in the second radiographic apparatus 10B, the cassette body 16 functions as a power supply source for other devices, that is, as a power source for contact power supply or non-contact power supply, and thus cannot be used as a radiographic apparatus. But its utility value is high.

  Next, a radiation imaging apparatus according to the third embodiment (hereinafter referred to as a third radiation imaging apparatus 10C) will be described with reference to FIGS. 16A to 17.

  This third radiation imaging apparatus 10C is different in that a power supply source 58 is installed in the case 14 as shown in FIG. 16A. In the example of FIG. 16A, an example in which a solar cell panel 64 is installed on the surface of the lid portion 14b of the case 14 is shown.

  Further, as shown in FIG. 16B, for example, at the bottom surface 220 of the case 14, at least a part of the power from the power supply source 58 is transmitted to other devices by, for example, contact (wired or the like) or non-contact (wireless or the like). And a power receiving unit 62 that receives power (receives power) by contact (wired or the like) or non-contact (wireless or the like), for example.

  Inside the case 14, as shown in FIG. 17, a battery 68, a remaining amount detection unit 74, a first power distributor 70a, a first power distribution setting unit 164a, a second power distributor 70b, It has the 2nd power distribution setting part 164b, the transmitter / receiver 190, and the control part 192 which controls these.

  The first power distributor 70 a distributes the power from the power supply source 58 to the power transmission unit 60, the battery 68 of the cassette body 16, the battery 68 of the radiation source body 18, and the battery 68 of the portable information terminal 20. To do. The first power distribution setting unit 164a sets the power distribution ratio in the first power distributor 70a in accordance with an instruction from an operator or the like. The second power distributor 70 b distributes the power received by the power receiving unit 62 to the battery 68 of the cassette body 16, the battery 68 of the radiation source body 18, and the battery 68 of the portable information terminal 20. The second power distribution setting unit 164b sets the power distribution ratio in the second power distributor 70b in accordance with an instruction from an operator or the like. The transceiver 190 transmits / receives a signal including information such as a power distribution ratio to / from the outside. The power from the power distributor 70 is supplied to the corresponding battery 68 through the cassette body 16, the radiation source body 18, and the power receiving units 62 of the portable information terminal 20.

  An instruction to supply power to the power transmission unit 60 and each battery 68 is, for example, the portable information terminal 20 of the third radiation imaging apparatus 10C, another portable information terminal 20a (see FIG. 16A), or the console 194 (cassette body unit 16). And an apparatus that controls the radiation source main body 18 and performs radiation imaging (see FIG. 16A).

  For example, assuming the case of using another portable information terminal 20a, the display unit 152 of the other portable information terminal 20a includes information from the remaining amount detection unit 74 of the case 14 in the third radiation imaging apparatus 10C. The remaining battery level is displayed, and further from the remaining amount detection unit 74 of the portable information terminal 20 (see FIG. 13), the remaining amount detection unit 74 of the radiation source body unit 18 and the remaining amount detection unit 74 of the cassette body unit 16. By transmitting information to the other portable information terminal 20a, the remaining battery levels of the portable information terminal 20, the radiation source main body 18 and the cassette main body 16 are also displayed. The operator inputs the power distribution ratio through the operation unit 150 of the other portable information terminal 20a while checking the remaining amount of each battery. For example, the power distribution ratio to the power transmission unit 60 of the case 14, the battery 68 of the case 14, the cassette body 16 (battery 68), the radiation source body 18 (battery 68) and the portable information terminal 20 (battery 68) is 30%. If you want 10%, 20%, 20% and 20%, or if you want to preferentially supply power to other devices, set the power distribution ratio to the power transmission unit 60 higher, for example, the cassette body If it is desired to preferentially supply power to the unit 16 and the radiation source body 18, the power distribution ratio to these devices is set higher. The input power distribution ratio information is supplied to the first power distribution setting unit 164a via the transceiver 190 and the control unit 192 of the case 14.

  Then, the first power distribution setting unit 164a controls the first power distributor 70a based on the information on the power distribution ratio from the other portable information terminal 20a, and is input at the other portable information terminal 20a. Set the power distribution ratio according to the power distribution ratio.

  And as shown in FIG. 17, the electric power from the power transmission part 60 installed in the case 14 is the power receiving part 62 of another apparatus (radiation source main-body part 18 or other cassette main-body part 16), or another 3rd radiography. Power is transmitted (powered) toward the power receiving unit 62 of the case 14 in the device 10C. That is, the energy output unit 78 of the power transmission unit 60 of the case 14 and the energy input unit 82 of the power reception unit 62 of another device are connected by wire, or the energy output unit 78 and the energy input unit 82 are wirelessly connected. As a result, power from the power transmission unit 60 installed in the case 14 is transmitted toward the power reception unit 62 of another device or the power reception unit 62 of the other case 14. At the same time, in the case 14 of the third radiation imaging apparatus 10C, the power distributed by the first power distributor 70a according to the set power distribution ratio is the case 14, the cassette body 16, the radiation source body 18 and It is supplied to each battery 68 of the portable information terminal 20. Of course, depending on the set power distribution ratio, some batteries may not be supplied with power.

  When power is transmitted from the power transmission unit 60 of the third radiography apparatus 10C to the power reception unit 62 of another third radiography apparatus 10C, the operator can perform another third radiography from the other portable information terminal 20a. Request the device 10C to transmit the remaining battery power. By this request, the remaining amount detection unit 74 of the case 14 of the other third radiation imaging apparatus 10 </ b> C, the remaining amount detection unit 74 of the portable information terminal 20, the remaining amount detection unit 74 of the radiation source body unit 18, and the cassette body unit 16. Information from the remaining amount detection unit 74 is transmitted to the other portable information terminal 20 a via the control unit 192 and the transceiver 190 and displayed on the display unit 152. The operator inputs the power distribution ratio through the operation unit 150 of the other portable information terminal 20a while checking the remaining amount of each battery. For example, the power distribution ratio to the battery 68, the cassette body 16 (battery 68), the radiation source body 18 (battery 68), and the portable information terminal 20 (battery 68) of the case 14 of the other third radiation imaging apparatus 10C is 10 %, 40%, 30% and 20%. The input power distribution ratio information is supplied to the second power distribution setting unit 164b via the transceiver 190 and the control unit 192 of the case 14.

  Then, the second power distribution setting unit 164b controls the second power distributor 70b based on the information on the power distribution ratio from the other portable information terminal 20a, and is input at the other portable information terminal 20a. Set the power distribution ratio according to the power distribution ratio.

  When power is transmitted (powered) from the power transmission unit 60 of the third radiography apparatus 10C to the power reception unit 62 of the other third radiography apparatus 10C, the case 14 of the other third radiography apparatus 10C. The power distributed by the second power distributor 70b in accordance with the set power distribution ratio is supplied to the case 14, the cassette body 16, the radiation source body 18, and the batteries 68 of the portable information terminal 20. Of course, depending on the set power distribution ratio, some batteries may not be supplied with power.

  Here, an operation for preparing for imaging using the third radiation imaging apparatus 10C and an operation for actually performing imaging will be described.

  First, the operator selects one or more cases 14 (see FIGS. 1 and 16A) in which the cassette main body 16, the radiation source main body 18 and the portable information terminal 20 are accommodated, for example, victims of disaster sites (radiation imaging is necessary). Transport it to the victim. When the operator arrives at the disaster site, the operator directs the surface of the case 14 (the surface on which the solar cell panel 64 is installed) upward or obliquely upward until, for example, an instruction for radiography is given. Power generation at

  At this time, for example, using the display unit 152 of the other portable information terminal 20a, the remaining battery levels of the case 14, the portable information terminal 20, the cassette body unit 16, and the radiation source body unit 18 are confirmed. The power distribution ratio according to the above is input using the operation unit 150. For example, when the other cassette main body 16 or the radiation source main body 18 that has been brought together has little remaining battery power and is to be preferentially charged, the power transmission section 60 of the case 14 and the power receiving section 62 of the other cassette main body section 16 are used. Alternatively, the power receiving unit 62 of the radiation source main body unit 18 is connected by wire or wirelessly, and the power distribution ratio to the power transmission unit 60 is set in the range of 80 to 100%. Of course, when the battery main body 16 in the case 14 has a small remaining battery capacity and is to be preferentially charged, the power distribution ratio to the cassette main body 16 in the case 14 is set in the range of 80 to 100%. When carrying 2 or more 3rd radiography apparatuses 10C, the surface of the case 14 (surface in which the solar cell panel 64 is installed) of the 3rd radiography apparatus 10C which is not used for the time being upward or diagonally upward direction The solar cell panel 64 generates power toward In this case, the remaining amount of the battery such as the cassette body 16 in the third radiation imaging apparatus 10C to be used immediately is confirmed, and if charging is necessary, the power transmission section of the case 14 in the third radiation imaging apparatus 10C that is not used for the time being. 60 and the power receiving unit 62 of the case 14 of the third radiation imaging apparatus 10C to be used immediately are wired or wirelessly connected, and the power distribution ratio to the power transmitting unit 60 is, for example, 80 to 100% depending on the remaining battery level. Set to range. Further, the power distribution ratio to be supplied to each battery is set from the remaining amount of each battery 68 accommodated in the third radiation imaging apparatus 10C that receives power supply. In this way, the power according to the set power distribution ratio is supplied from the power transmission unit 60 of the third radiographic apparatus 10C that is generating power to the cassette main body 16 or the radiation source main body 18, or the third radiographic apparatus. Power is transmitted to the 10C power receiving unit 62. In particular, the power supplied to the third radiation imaging apparatus 10C is supplied to each battery 68 according to a separately set power distribution ratio.

  After that, at the stage when there is an instruction for radiography, preparation for radiography is performed, and then radiography of the subject 48 is performed.

  Then, the battery remaining amount of the cassette body 16 and the like after the radiography is confirmed, and the surface of the case 14 (the surface on which the solar panel 64 is installed) is directed upward or until the next radiography instruction is given. Electricity is generated by the solar cell panel 64 in an obliquely upward direction, and at the same time, battery charging is performed on the cassette body 16, the radiation source body 18, the portable information terminal 20, and the like. When power is generated by the solar cell panel 64 of the third radiation imaging apparatus 10C that is not used for the time being, the third radiation imaging apparatus 10C is used in the next radiation imaging and used in the previous radiation imaging during that time. The power is generated by the solar cell panel 64 of the third radiation imaging apparatus 10C, and the battery main unit 16, the radiation source body 18, the portable information terminal 20, and the like used in the previous radiation imaging are also charged. It can be carried out.

  Of course, in this case as well, while power is being generated by the solar panel 64, the power transmission unit 60 of the cassette body 16 and other medical devices such as an electrocardiograph, an ultrasonic diagnostic device, an AED, a sphygmomanometer, In addition, it is possible to perform power supply and battery charging to these other medical devices by wired connection or wireless connection with medical devices necessary for taking them to the stricken area.

  As described above, in the third radiation imaging apparatus 10 </ b> C, one or more devices used for radiation imaging, a case in which the devices are removably accommodated, the power supply source 58, and the power supply source 58 Since at least a part of the power is provided with the power transmission unit 60 that transmits power to the device outside the case 14, a part of the power generated in the power supply source 58 is one or more of the third radiation imaging apparatus 10C. In addition to being used in other devices, the remaining power can be accommodated in other devices. This makes it possible to perform radiography at disaster sites where it is difficult to secure power over a long period of time, and also to supply power to other medical devices flexibly. Various medical actions including photographing can be easily performed.

  Moreover, since it functions also as a power supply of a non-contact electric power feeding system, it becomes possible to continue diagnosis smoothly by radiography at a disaster site or the like and other medical activities and to proceed smoothly.

  Next, a radiation imaging apparatus (hereinafter, referred to as a fourth radiation imaging apparatus 10D) according to a fourth embodiment will be described with reference to FIG.

  The fourth radiation imaging apparatus 10D has substantially the same configuration as the third radiation imaging apparatus 10C described above, but as shown in FIG. 18, the first power distributor 70a (see FIG. 17) and the first power distribution setting are configured. The difference is that the unit 164 a does not exist and the power from the power supply source 58 is directly supplied to the power transmission unit 60. That is, the power distribution ratio from the power supply source 58 to the power transmission unit 60 is always 100%. Accordingly, the power supply source 58 in the fourth radiation imaging apparatus 10D is used exclusively as a power supply source for supplying power to other devices.

  In the fourth radiation imaging apparatus 10D, similarly to the second radiation imaging apparatus 10B described above, the number of defective pixels in the radiation detector 54 increases or the battery 68 deteriorates depending on the frequency of use of the fourth radiation imaging apparatus 10D. Even if it becomes unusable, it functions as a power source for performing contact power supply or non-contact power supply to other devices or other radiographic imaging devices (first radiography device 10A to fourth radiography device 10D). Its utility value is high.

  Next, a radiation imaging apparatus (hereinafter, referred to as a fifth radiation imaging apparatus 10E) according to a fifth embodiment will be described with reference to FIGS.

  The fifth radiation imaging apparatus 10 </ b> E is different in that the cassette body 16 has a mechanism for detachably mounting the radiation source body 18 on the fourth side surface 28 d of the housing 22.

  That is, as shown in FIG. 19, the cassette body 16 protrudes outward from both ends of the fourth side surface 28d of the cassette body 16 (the side surface opposite to the first side surface 28a provided with the handle 30). And holding members 196a and 196b that detachably hold the radiation source body 18.

  The second side surface 28b of the cassette body 16 is provided with the USB terminal 32 described above, a card slot 36 for loading the memory card 34, and a lock release button 198 described later. In addition, a small portable information terminal 20 that is removable from the cassette body 16 is mounted on the second side surface 28b.

  FIG. 20 shows a state where the operator 199 is transporting the fifth radiation imaging apparatus 10E. In this case, the cassette main body 16 and the radiation source main body 18 are integrally connected and fixed. Accordingly, the operator 199 holds the handle 30 and transports the fifth radiation imaging apparatus 10E to, for example, an accident site, a disaster site, a health check-up or a home nursing site, so that the fifth radiation image is received at the destination site. For example, radiographic images of victims at accident sites and disaster victims, imaging of radiographic images of those who undergo medical examinations (consultants), and home-care workers who need home nursing It is possible to take a radiographic image of

  Here, the integrally connected and fixed state of the cassette main body 16 and the radiation source main body 18 means that the cassette main body can be transported by the fifth radiation imaging apparatus 10E by a connection mechanism 200 (see FIG. 21) described later. The state where the part 16 and the radiation source main body part 18 are integrally connected. Of course, the radiation source main body 18 can be detached from the cassette main body 16. For example, if a mechanism for locking the drawer of the measure 38 in the middle is incorporated, the lock is released and the radiation source main body 18 is removed. It is also possible. In addition, it is possible to perform imaging using another radiation source main body 18 in a state where the radiation source main body 18 is mounted on the cassette main body 16, and in this case, the devices constituting the fifth radiation imaging apparatus 10E are as follows. The cassette body 16 to which the radiation source body 18 is attached and the other radiation source body 18 are obtained.

  As shown in FIG. 21, the USB terminal 32, the card slot 36, and the lock release button 198 described above are arranged on the second side surface 28 b of the cassette body 16. Further, the portion between the card slot 36 and the lock release button 198 on the second side surface 28 b is a concave portion 202 recessed inward, and the portable information terminal 20 can be attached to the concave portion 202.

  The lock release button 198 can be displaced along the fourth side surface 28d toward the third side surface 28c due to the pressing operation by the operator 199. In this case, a slide portion 204 is formed along the fourth side surface 28d on the third side surface 28c side of the lock release button 198, and the slide portion 204 and a projection 206 projecting inward from the fourth side surface 28d are formed. A spring member 208 is interposed between the projection 206 and the second side surface 28b. In addition, a hole 210 that communicates the inside and the outside of the cassette body 16 is formed in a part of the fourth side face 28d that the slide part 204 contacts, and the side of the slide part 204 passes through the hole 210. A hook portion 212 is formed.

  On the other hand, as shown in FIG. 21, when the radiation source body 18 is held by the cassette body 16 by the holding members 196a and 196b, A hole 214 having substantially the same size as the hole 210 is formed. Accordingly, the hook portion 212 is displaced toward the second side face 28b by the elastic force of the spring member 208, so that the hook portion 212 and the hole 214 are engaged. As a result, the radiation source main body portion with respect to the cassette main body portion 16 is engaged. 18 can be integrally connected and fixed.

  In addition, a conductive connection terminal (first radiation source side connection terminal 216a) is attached to one end portion on the holding member 196a side of the radiation source main body portion 18, and the other end portion on the holding member 196b side is attached to the other end portion on the holding member 196b side. The conductive connection terminal (second source side connection terminal 216b) is mounted. In this case, the first radiation source side connection terminal 216a is convex toward the holding member 196a, while the second radiation source side connection terminal 216b is concave toward the holding member 196b. The first radiation source side connection terminal 216 a and the second radiation source side connection terminal 216 b may be configured as a power reception unit 62 dedicated to the radiation source main body 18.

  On the other hand, a conductive connection terminal (first cassette side connection terminal) 218a is mounted on the radiation source main body 18 side of the holding member 196a of the cassette main body 16, and the radiation source main body 18 of the holding member 196b. A conductive connection terminal (second cassette side connection terminal) 218b is mounted on the side. In this case, the first cassette side connection terminal 218a has a concave shape corresponding to the first radiation source side connection terminal 216a, while the second cassette side connection terminal 218b corresponds to the second radiation source side connection terminal 216b. It is convex. You may comprise these 1st cassette side connection terminals 218a and 2nd cassette side connection terminals 218b as the power transmission part 60 only for the radiation source main-body part 18. As shown in FIG.

  Accordingly, as shown in FIG. 21, in the state where the hook portion 212 and the hole 214 are engaged by the elastic force of the spring member 208 and the cassette body portion 16 and the radiation source body portion 18 are integrally connected and fixed. The convex first source side connection terminal 216a and the concave first cassette side connection terminal 218a are engaged, and the concave second source side connection terminal 216b and the convex second cassette side connection terminal 218b are engaged. And the cassette body 16 and the radiation source body 18 can be reliably maintained in an integrally connected and fixed state. That is, these connection terminals 216a, 216b, 218a, 218b are also members for assisting in maintaining an integrally connected and fixed state of the cassette body 16 and the radiation source body 18 by the hook portion 212 and the hole 214. Function.

  On the other hand, as shown in FIG. 22, when the operator 199 presses the lock release button 198 and moves the lock release button 198 to the third side surface 28c against the elastic force of the spring member 208, the hook portion 212 and the slide The portion 204 is displaced toward the third side face 28c, and the engagement state between the hook portion 212 and the hole 214 is released. Therefore, the operator 199 removes the radiation source body 18 from the cassette body 16 (separation) in a state where the engagement state between the hook portion 212 and the hole 214 is released (the operator 199 is pressing the lock release button 198). By doing so, the integrally connected and fixed state of the cassette body 16 and the radiation source body 18 is released.

  The leading end of the band member 42 drawn out from the measure 38 is inserted through a hole 46 formed at a location facing the measure 38 in the fourth side surface 28d to be connected to the second radiation source side connection terminal of the radiation source main body 18. It is fixed in the vicinity of 216b.

  Therefore, as shown in FIG. 21, in the state where the radiation source main body 18 is integrally connected and fixed to the cassette main body 16, most of the band member 42 is caused by the action of the spring member inside the major 38. In 38, it is wound up into a roll. On the other hand, as shown in FIG. 22, if the integral connecting and fixing state of the cassette body 16 and the radiation source body 18 is released, the radiation source from the cassette body 16 resists the action of the spring member. By separating the main body 18, the band member 42 can be pulled out from the measure 38 through the hole 46.

  The cassette main body 16 and the radiation source main body are transported by the lock release button 198, the slide portion 204, the spring member 208, the hook portion 212, the connection terminals 216a, 216b, 218a, 218b and the measure 38 when the fifth radiation imaging apparatus 10E is transported. On the other hand, a connecting mechanism 200 that separates the cassette body 16 and the radiation source body 18 during imaging is configured.

  Also in this fifth radiation imaging apparatus 10E, as shown in FIG. 23, a solar cell panel 64 is used as the power supply source 58, and the solar cell panel 64 is placed on the surface of the casing 22 of the cassette body 16. In addition, it is installed on the back surface 66 opposite to the irradiation surface 24 irradiated with the radiation 50 transmitted through the subject 48, and further, as shown in FIG. 19 and the like, the power transmission unit 60 and the power reception unit 62 are connected to the surface of the housing 22. Of these, it is provided on the second side face 28b. As the solar cell panel 64, a commercially available small solar cell panel or a flexible solar cell panel can also be used in this example.

  In the fifth radiation imaging apparatus 10E, as in the first radiation imaging apparatus 10A described above, a part of the power generated by the power supply source 58 is used in the cassette body 16 and the remaining power is used in other ways. Can be accommodated in other equipment. This makes it possible to perform radiography at disaster sites where it is difficult to secure power over a long period of time, and also to supply power to other medical devices flexibly. Various medical actions including photographing can be easily performed.

  In particular, in the fifth radiation imaging apparatus 10E, as shown in FIG. 20, the cassette body 16, the radiation source body 18 and the portable information terminal 20 can be carried without being accommodated in a case or the like. Since the main body 16 can be carried with the solar cell panel 64 exposed, the solar cell panel 64 can also generate power when the fifth radiation imaging apparatus 10E is carried.

  Also in the fifth radiography apparatus 10E, a configuration in which the power from the power supply source 58 is directly supplied to the power transmission unit 60 may be adopted as in the second radiography apparatus 10B (see FIG. 15) described above. .

  Next, a mobile radiographic image capturing apparatus (hereinafter referred to as first mobile apparatus 500A) according to the first embodiment will be described with reference to FIGS. 24 and 25. FIG.

  As shown in FIG. 24, the first moving device 500A is movable and can be attached to and detached from the cart 502. The plurality of third radiation imaging devices 10C described above (see FIGS. 16A and 16B). ) And a console 504 for controlling power transmission / reception, radiation imaging and the like for the third radiation imaging apparatus 10C. Of course, the fourth radiation imaging apparatus 10D may be used instead of the third radiation imaging apparatus 10C.

  The console 504 has the appearance of a so-called laptop computer in appearance, and has an operation unit 506 such as a keyboard and a display unit 508 such as a display, to which an operator belongs by wireless communication via a network using a public line or the like. It is possible to send and receive signals to and from a data center (such as a medical institution). Of course, a mobile phone or a PDA (personal information terminal) may be used instead of the console 504.

  As shown in FIG. 24, the carriage 502 has a plurality of wheels 510 and can be moved by human power by operating the handle 512. Of course, you may make it move electrically. In addition, the carriage 502 includes two case accommodating portions 514 and 514 that can accommodate a plurality of cases 14. A partition wall 516 is provided between the two case housing portions 514. Each case accommodating portion 514 is configured such that a plurality of cases 14 can be placed in a two-layer stack in the horizontal direction. The example of FIG. 24 shows an example in which four cases 14 are accommodated in each case accommodating portion 514, and a total of eight cases 14 are accommodated. In addition, you may provide the partition part 518 in each case accommodating part 514 so that the case 14 may be easily mounted.

  In order to accommodate the case 14, first, the case 14 is placed on the upper stage of the case accommodating portion 514 so that the solar cell panel 64 faces upward. The case 14 may be accommodated in the lower stage of the case accommodating portion 514 so that the solar cell panel 64 faces upward or downward.

  A power receiving unit 62 (see FIG. 25) connected to a power transmission unit 60 (see FIG. 16B) installed in the case 14 and a power receiving unit 62 (see FIG. 25) installed in the case 14 are provided on a surface of the partition wall 516 facing the bottom surface of the case 14. A power transmission unit 60 connected to the power reception unit 62 is also provided. For example, a part of the partition wall 516 corresponding to the case 14 accommodated in the upper stage is provided with a power receiving unit 62 connected to the power transmission unit 60 of the case 14, and the part corresponding to the case 14 accommodated in the lower stage is provided. The power transmission unit 60 connected to the power reception unit 62 of the case 14 is provided.

  Therefore, in the upper stage of the case housing part 514, the power transmitted from the power transmission part 60 of the case 14 is received by the power reception part 62 of the partition wall 516.

  Then, in the carriage 502, as shown in FIG. 25, a current collector 520 that collects the power received by the plurality of power receivers 62, and a plurality of power transmissions in the lower stage from the power collector 520 A third power distributor 70c that distributes to the unit 60, and a third power distribution setting unit 164c that sets a power distribution ratio in the third power distributor 70c in accordance with an instruction from an operator or the like.

  The power distribution rate of each first power distributor 70a (see FIG. 17) in the plurality of third radiation imaging apparatuses 10C mounted on the upper stage of the case housing section 514, and the plurality of modules mounted on the lower stage of the case housing section 514. The power distribution ratio of each second power distributor 70b (see FIG. 17) in the third radiation imaging apparatus 10C and the power distribution ratio of the third power distributor 70c in the carriage 502 are determined by, for example, the display unit of the console 504 by the operator. The remaining battery level of each battery 68 is displayed in 508, and can be arbitrarily set using the operation unit 506 of the console 504 based on the remaining battery level.

  In other words, since the plurality of third radiation imaging apparatuses 10C are placed on the upper stage of the case housing portion 514 with the solar cell panels 64 facing upward, respectively, the large-sized solar cell including the plurality of solar cell panels 64 in total. Since the battery panel is mounted and the power transmitted from each power transmission unit 60 is collected out of the power from each solar panel 64, the power that can be distributed can be increased. It becomes. Therefore, it is possible to supply power to the plurality of third radiation imaging apparatuses 10C on average, or to supply power intensively to the third radiation imaging apparatus 10C where power consumption is severe. Flexibility can be increased.

  Of course, the power supply to each cassette body 16 in the plurality of third radiation imaging apparatuses 10C, the power supply to the radiation source body 18, the power supply to the portable information terminal 20, etc. Since it can set finely through the 1st power distribution setting part 164a and the 2nd power distribution setting part 164b, useless power supply can be suppressed.

  Next, a mobile radiographic image capturing apparatus (hereinafter referred to as a second mobile apparatus 500B) according to a second embodiment will be described with reference to FIG.

  The second mobile device 500B has substantially the same configuration as the first mobile device 500A described above, but, as shown in FIG. 26, a battery 68 that stores the power from the current collector 520 in the carriage 502, A remaining power detection unit 74 that detects the remaining amount of the battery 68, a fourth power distributor 70d that distributes the power from the battery 68 to the plurality of power transmission units 60 in the upper stage and the lower stage, and a fourth power according to an instruction from an operator or the like And a fourth power distribution setting unit 164d that sets a power distribution ratio in the distributor 70d.

  In the second moving apparatus 500B, electric power can be supplied to the plurality of third radiography apparatuses 10C placed on the upper stage of the case housing portion 514, and all the third radiography apparatuses 10C can be uniformly supplied. Therefore, it is possible to avoid an increase in the frequency of use of only some of the third radiation imaging apparatuses 10C. In addition, since the power received by the plurality of power receiving units 62 of the carriage 502 is collected and temporarily stored in the battery 68 of the carriage 502, in addition to the power generation of the solar panel 64, an arbitrary time zone Since the electric power can be supplied to the third radiation imaging apparatus 10C, for example, it is possible to quickly cope with, for example, emergency radiography.

  Next, a mobile radiation imaging apparatus (hereinafter referred to as a third mobile device 500C) according to a third embodiment will be described with reference to FIGS.

  As shown in FIG. 27, the third moving device 500C includes a carriage 502 and one or more fifth radiography apparatuses 10E housed in the carriage 502 (see FIG. 19), similarly to the first moving apparatus 500A described above. ), A console 504 for controlling at least the fifth radiation imaging apparatus 10E, and an arm part 522 to which the radiation source body 18 of the fifth radiation imaging apparatus 10E is attached and detached.

  As the attachment / detachment mechanism 524 with respect to the arm part 522 of the radiation source main body part 18, for example, as shown in FIG. 28A, a mechanism using an internal thread 526 and an external thread 528 may be used. For example, a female screw 526 is formed at the distal end portion 522 a of the arm portion 522, and a male screw 528 is formed on the side surface of the cylindrical portion 530 formed so as to protrude from the central portion of the radiation source main body portion 18. The radiation source body 18 can be attached to the arm 522 by screwing the male screw 528 of the radiation source body 18 into the female screw 526 of the arm 522, and the radiation source body 18 can be turned by turning in the opposite direction. It can be removed from the arm portion 522.

  Further, as shown in FIG. 28B, the attachment / detachment mechanism 524 may be a mechanism using a locking piece 532. For example, a plurality of openings 534 are provided on a side surface of a cylindrical portion 530 formed to protrude from the central portion of the radiation source main body portion 18, and a locking piece 532 having a triangular cross section, for example, is always outwardly attached to each opening 534 with a spring or the like. As a result, the protruding amount gradually increases downward, forming a protruding portion whose side surface is a triangular slope and whose lower surface is a triangular bottom surface. On the other hand, a hole 536 into which the cylindrical portion 530 of the radiation source main body portion 18 is inserted is formed on the lower surface (tip surface) of the distal end portion 522a of the arm portion 522, and is further locked to the side surface of the distal end portion 522a of the arm portion 522. An opening 538 into which the piece 532 (projection) enters is formed. Then, by inserting the cylindrical portion 530 of the radiation source main body portion 18 into the hole 536 on the distal end surface of the arm portion 522, the locking piece 532 (projection portion) enters the opening 538 of the arm portion 522, and the radiation source main body. The part 18 is attached to the arm part 522. On the contrary, by pushing the locking piece 532 inward against the bias of the spring or the like, the engagement of the locking piece 532 with the inner wall of the opening 538 of the arm portion 522 is released, and the radiation source main body portion 18 is moved to the arm portion. 522 can be removed.

  Further, as shown in FIG. 28C, the attachment / detachment mechanism 524 may use a mechanism using a magnet on the assumption that the generation of the radiation 50 is not affected. For example, a metal piece 540 is attached to the upper surface of a cylindrical portion 530 formed to protrude from the central portion of the radiation source main body portion 18, and a magnet sheet 542 is attached to the distal end surface 522 b of the arm portion 522. Then, the metal piece 540 on the upper surface of the cylindrical portion 530 in the radiation source main body portion 18 is magnetically attracted by bringing it into contact with the magnet sheet 542 on the tip end surface 522b of the arm portion 522, and the radiation source main body portion 18 is attached to the arm portion 522. Will be. On the contrary, the radiation source body 18 can be easily detached from the arm 522 by separating the radiation source body 18 against the magnetic adsorption.

  As shown in FIG. 27, the carriage 502 includes a plurality of shelves 544, and the fifth radiation imaging apparatus 10E is accommodated in each of the shelves 544, respectively. The size of each fifth radiation imaging apparatus 10E may be the same or different.

  In particular, when the fifth radiation imaging apparatus 10E is accommodated in, for example, the uppermost shelf 544 among the plurality of shelves 544, a part of the shelf 544 is pulled out and the solar cell panel 64 is exposed upward. To. As a result, it is possible to generate power with the solar cell panel 64 of the fifth radiation imaging apparatus 10E partially accommodated in the uppermost shelf 544.

  In each shelf 544, as shown in FIG. 29, a power receiving unit 62 corresponding to the power transmitting unit 60 of the cassette body 16 and a power transmitting unit 60 corresponding to the power receiving unit 62 of the cassette body 16 are installed. For example, in the uppermost shelf 544, the power transmission unit 60 of the fifth radiation imaging apparatus 10E and the power reception unit 62 in the shelf 544 are wired or wirelessly connected, and in the other shelves 544, the power reception unit of the fifth radiation imaging apparatus 10E. 62 and the power transmission unit 60 in the shelf 544 are connected in a wired or wireless connection.

  Further, in the carriage 502, the battery 68, the remaining amount detection unit 74, and the power received by the uppermost power reception unit 62 are distributed to the battery 68 and the power transmission units 60 of the other shelves 544. It has a power distributor 70e and a fifth power distribution setting unit 164e that sets a power distribution ratio in the fifth power distributor 70e in accordance with an instruction from an operator or the like.

  Accordingly, at least part of the power from the solar cell panel 64 of the fifth radiation imaging apparatus 10E partially accommodated in the uppermost shelf 544 is transferred from the power transmission unit 60 of the fifth radiation imaging apparatus 10E to the uppermost shelf 544. The electric power supplied to the fifth power distributor 70e via the power receiving unit 62 and further distributed by the fifth power distributor 70e passes through the corresponding power transmitting units 60 in addition to the battery 68 in the carriage 502. Is supplied to the fifth radiation imaging apparatus 10E.

  The power distribution ratio of each power distributor 70 (see FIG. 10) in the plurality of fifth radiography apparatuses 10E accommodated in the plurality of shelves 544 and the power distribution ratio of the fifth power distributor 70e in the carriage 502 are, for example, The operator displays the remaining battery level of each battery 68 on the display unit 508 of the console 504, and can be arbitrarily set using the operation unit 506 of the console 504 based on the remaining battery level.

  When using the third mobile device 500C, as shown in FIG. 27, the operator moves the cart 502 to the subject 48 (for example, an accident site victim, a disaster site victim, a person who undergoes a health checkup). Then, the fifth radiation imaging apparatus 10E is taken out from the carriage 502, and the radiation source body 18 is separated from the cassette body 16. Thereafter, the radiation source main body 18 is attached to the distal end 522a of the arm 522, and the cassette main body 16 is placed between the subject 48 and a bed 546 or a bedcloth (blanket or the like) for example, in the case of lying position photography. For example, at this stage, when the operator operates the exposure switch 96 (see FIG. 19), a radiographic image can be captured on the subject 48 using the fifth radiographic apparatus 10E.

  Thus, in the third moving apparatus 500C, for example, the solar cell panel 64 of the fifth radiation imaging apparatus 10E partially accommodated in the uppermost shelf 544 is replaced with the fifth radiation imaging apparatus 10E and other fifth radiations. It can be used as a power supply source for the batteries 68 of the photographing apparatus 10E and the carriage 502. That is, a part of the electric power generated in the solar cell panel 64 of the fifth radiography apparatus 10E partially accommodated in the uppermost shelf 544 is used in the fifth radiography apparatus 10E, and the remaining electric power is used. The battery 502 of the carriage 502 and other fifth radiation imaging apparatus 10E can be accommodated. This makes it possible to perform radiography at disaster sites where it is difficult to secure power over a long period of time, and also to supply power to other medical devices flexibly. Various medical actions including photographing can be easily performed.

  Next, a mobile radiographic imaging apparatus (hereinafter referred to as a fourth mobile apparatus 500D) according to a fourth embodiment will be described with reference to FIGS. 30 and 31. FIG.

  The fourth moving device 500D has substantially the same configuration as the third moving device 500C described above, but the printer 168 described above is installed in the cassette body 16 of the fifth radiographic apparatus 10E as shown in FIG. The difference is that a printer 548 is installed on the carriage 502.

  As the printers 168 and 548, the above-described first-type printer and second-type printer can be used. Also in the fourth moving device 500D, as in the third moving device 500C described above, a part of the electric power generated in the solar cell panel 64 of the fifth radiation imaging apparatus 10E partially accommodated in the uppermost shelf 544. Can be used in the fifth radiation imaging apparatus 10E, and the remaining power can be accommodated in the battery 68 of the carriage 502 and other fifth radiation imaging apparatuses 10E. A large printer can be used.

  The printer 168 installed in the cassette body 16 can preferably employ the same configuration as the printer 168 (see FIG. 14) installed in the cassette body 16 of the first radiation imaging apparatus 10A.

  On the other hand, the printer 548 installed on the carriage 502 uses a recording material that does not require a wet development process, exposes the recording material by scanning exposure with a light beam made of laser light, forms a latent image, and then performs thermal development. To obtain a visible image, and then a printer using a device that cools to room temperature can be used.

  As shown in FIG. 30, the printer 548 includes a recording material loading unit 552 on a side surface of the carriage 502 in which a cartridge 550 containing a recording material 172 (see FIG. 31) is loaded. The cartridge 550 contains a roll-shaped recording material 172 wound in a roll.

  As shown in FIG. 31, the printer 548 basically includes a recording material supply unit 554, an image exposure unit 556 as a recording unit, a heat development unit 558, and a cooling unit in the order of conveyance of the recording material 172. 560, a conveyance means for conveying the recording material 172 provided at a key point between each unit, and a printer control unit 562 that drives and controls each unit.

  The recording material supply unit 554 includes the above-described recording material loading unit 552 (see FIG. 30), a supply roller pair 564, and a cutter 566. A cartridge 550 is detachably loaded in the recording material loading unit 552 shown in FIG. A plurality of types of cartridges 550 are prepared according to the size (for example, B4, half-cut, six-cut, etc.) of the recording material 172 to be accommodated. In FIG. 30, a symbol indicating the size of the recording material 172 (“B4” indicating B4 size, “H” indicating half-cut size, "M" indicating a six-cut size) is attached. The information by size is attached to the outer surface of the cartridge 550 by manual input by an operator (such as input using the operation unit 506 of the console 504) when the cartridge 550 is loaded in the recording material loading unit 552. The barcode 563 is detected by a recognition sensor (not shown) in the recording material loading unit 552 and is input to the printer control unit 562.

  The cartridge 550 is formed with a casing having a sealing property, and the inside serves as a storage space for the recording material 172, and this storage space opens to the outlet 550a. That is, the recording material 172 has its leading end drawn out from the outlet 550a.

  The leading end portion pulled out from the outlet 550a of the cartridge 550 is pinched by the supply roller pair 564, and is fed out from the cartridge 550 by the rotation of the supply roller pair 564. A cutter 566 is disposed on the downstream side in the conveying direction of the supply roller pair 564, and the cutter 566 cuts the recording material 172 fed out by the supply roller pair 564 by a predetermined length. The recording material 172 is cut by detecting the feeding length of the recording material 172 from the rotation amount of the supply roller pair 564 or by a sensor (not shown), and the printer controller 562 controls the operation of the cutter 566 based on the detected value. Is called.

  The image exposure unit 556 scans and exposes the light beam L to the recording material 172 conveyed from the recording material supply unit 554 in the main scanning direction (a direction substantially perpendicular to the conveyance direction of the recording material 172), and performs recording. By conveying the material 172 in the sub-scanning direction (conveying direction of the recording material 172), a desired image (for example, radiation image information) is recorded on the recording material 172 to form a latent image.

  The thermal development unit 558 heats a heat-treated recording material to which heat treatment is applied, and is configured by arranging one or more plate heaters 568 in the conveyance direction of the recording material 172. The plate heater 568 is a heating body that has a temperature necessary for processing the recording material 172.

  The thermal developing unit 558 including the plate heater 568 slides the recording material 172 while making contact with the upper surface of the plate heater 568 and relatively moves the recording material 172. At this time, as a conveying means for the recording material 172, a supply roller 570 and a plurality of pressing rollers 572 that also serve as heat transfer from each plate heater 568 to the recording material 172 are provided. As the pressing roller 572, a metal roller, a resin roller, a rubber roller, or the like can be used. A discharge roller (not shown) that conveys the recording material 172 is disposed at the end of the conveyance path of the recording material 172 in the thermal developing unit 558.

  Then, the recording material 172 carried out from the heat developing unit 558 is cooled while being conveyed by the cooling roller pair 574 by the cooling unit 560. The recording material 172 discharged from the cooling unit 560 is guided into a guide plate 576 provided in the middle of the conveyance path, and further discharged from a discharge roller pair 578 to a discharge tray 580. The operator can confirm the photographing state by viewing an image (for example, radiation image information) recorded on the recording material 172 having a predetermined length discharged from the discharge tray 580. In addition, since the printer 548 is the first-type printer described above, the image quality is good and interpretation is possible.

  Next, a mobile radiographic imaging apparatus (hereinafter referred to as a fifth mobile apparatus 500E) according to a fifth embodiment will be described with reference to FIGS. 32A to 33.

  As shown in FIGS. 32A and 32B, the fifth moving apparatus 500E includes a movable carriage 502, a plurality of fifth radiation imaging apparatuses 10E accommodated in the carriage 502, and a console (not shown).

  The carriage 502 is provided with one shelf 544 on each of four side surfaces (first side surface 502a to fourth side surface 502d), and each shelf 544 has a different height. For example, the shelf 544 of the first side surface 502a is provided in the uppermost level, the shelf 544 of the second side surface 502b is provided in the second level from the top, the shelf 544 of the third side surface 502c is provided in the third level from the top, A shelf 544 with four side surfaces 502d is provided at the fourth level (the lowest level) from the top.

  When the fifth radiation imaging apparatus 10E is accommodated in each shelf 544, a part is pulled out and the solar cell panel 64 is exposed upward. Further, the fifth radiation imaging apparatus 10E is also placed on the upper surface 502u of the carriage 502 with the solar cell panel 64 facing upward. This makes it possible to generate power in each of the five solar cell panels 64.

  In each shelf 544, as shown in FIG. 33, a power receiving unit 62 corresponding to the power transmission unit 60 of the fifth radiation imaging apparatus 10E (for example, the cassette body 16) and a fifth radiation imaging apparatus 10E (for example, the cassette body). 16), the power transmission unit 60 corresponding to the power reception unit 62 is installed, and the power reception unit 62 and the power transmission unit 60 are also installed on the upper surface 502u of the carriage 502. In each shelf 544, the power transmission unit 60 of the fifth radiation imaging apparatus 10E and the power reception unit 62 in the shelf 544 are wired or wirelessly connected, and the power reception unit 62 of the fifth radiation imaging apparatus 10E and the power transmission unit 60 in the shelf 544 are connected. Are in a wired or wireless connection state. Also in the fifth radiation imaging apparatus 10E placed on the upper surface 502u of the carriage 502, the power transmission unit 60 of the fifth radiation imaging apparatus 10E and the power reception unit 62 of the carriage 502 are connected by wire or wirelessly, and the fifth radiation. The power receiving unit 62 of the photographing apparatus 10E and the power transmission unit 60 of the carriage 502 are connected in a wired or wireless manner.

  Further, in the carriage 502, as shown in FIG. 33, a battery 68, a remaining amount detecting unit 74, a current collecting unit 520 that collects power received by the five power receiving units 62, and the current collecting unit A sixth power distributor 70f that distributes the power collected by the unit 520 to the battery 68 of the carriage 502 and the five power transmission units 60, and a power distribution by the sixth power distributor 70f according to instructions from an operator or the like And a sixth power distribution setting unit 164f for setting the rate.

  Accordingly, at least part or all of the electric power from each solar cell panel 64 of the five fifth radiography apparatuses 10E is guided into the carriage 502 via the corresponding power transmission unit 60 and power reception unit 62, respectively, and the current collecting unit After being collected at 520, it is supplied to the sixth power distributor 70f and distributed. The power distributed by the sixth power distributor 70f is supplied to the fifth radiation imaging apparatus 10E via the corresponding power transmission unit 60 in addition to the battery 68 in the carriage 502.

  The power distribution ratio of each of the sixth power distributors 70f in the five fifth radiography apparatuses 10E and the power distribution ratio of the sixth power distributor 70f in the carriage 502 are determined by the operator on the display unit 508 of the console 504, for example. The remaining battery level of the battery 68 is displayed and can be arbitrarily set using the operation unit 506 of the console 504 based on the remaining battery level.

  As described above, in the fifth moving apparatus 500E, the solar cell panels 64 of all the fifth radiation imaging apparatuses 10E accommodated in the plurality of shelves 544 of the carriage 502 and the fifth panels placed on the upper surface 502u of the carriage 502 are arranged. The solar battery panel 64 of the radiation imaging apparatus 10E can be used as a power supply source for the fifth radiation imaging apparatus 10E and the battery 68 of the carriage 502. That is, in addition to using a part of the power generated in the solar cell panel 64 of the fifth radiation imaging apparatus 10E in the corresponding fifth radiation imaging apparatus 10E, the remaining power is used for the battery 68 of the carriage 502, Other 5th radiography apparatus 10E can be accommodated. This makes it possible to perform radiography at disaster sites where it is difficult to secure power over a long period of time, and also to supply power to other medical devices flexibly. Various medical actions including photographing can be easily performed.

  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 54 may be the radiation detector 600 according to the modification shown in FIGS. 34 and 35. FIG. 34 is a schematic cross-sectional view schematically showing the configuration of three pixel portions of the radiation detector 600 according to the modification.

  As shown in FIG. 34, the radiation detector 600 includes a signal output unit 604, a sensor unit 606 (photoelectric conversion unit), and a scintillator 608 sequentially stacked on an insulating substrate 602. A pixel unit is configured by the sensor unit 606. A plurality of pixel portions are arranged in a matrix on the substrate 602, and the signal output portion 604 and the sensor portion 606 in each pixel portion are configured to overlap each other.

  The scintillator 608 is formed on the sensor unit 606 via a transparent insulating film 610, and converts the radiation 50 incident from above (the side opposite to the side where the substrate 602 is located) into light to emit fluorescence. 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 in the scintillator 608 preferably contains cesium iodide (CsI) when imaging using X-rays as the radiation 50, and the emission spectrum during X-ray irradiation is 420 nm to 700 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 low 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 50 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 of the scintillator 608 with respect to the radiation 50 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 a stack of a part that absorbs electromagnetic waves, a photoelectric conversion part, an electron transport part, a hole transport part, an electron blocking part, a hole blocking part, a crystallization prevention part, an electrode, an interlayer contact improvement part, or the like. An organic layer formed by mixing is included. 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, any organic compound can be used as the acceptor organic compound 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 of them is provided, a certain dark current suppressing effect can be obtained.

  As shown in FIG. 35, 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 for storing 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 50 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. In addition, 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 16 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 material having flexibility different from that of general glass, it is possible to improve damage resistance when the device is carried or used.

  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 manufacturing 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.

  The bionanofiber is a composite of a cellulose microfibril bundle (bacterial cellulose) produced by bacteria (acetobacterium 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. Compared to glass substrates, etc. Thus, a thin substrate 602 can be formed.

  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. Therefore, the photoelectric conversion film 616 and the signal output unit 604 are used. The radiation 50 is hardly absorbed. Thereby, the fall of the sensitivity with respect to the radiation 50 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 50. Thereby, the fall of the sensitivity with respect to the radiation 50 can be suppressed further.

  Further, for example, when the radiation detector 600 is attached to the irradiation surface 24 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 24 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 24, the radiation detector 600 is damaged. It ’s hard.

  The radiation detector 600 described above may be configured as follows.

  (1) The photoelectric conversion film 616 may be formed of an organic photoelectric conversion material, and the TFT layer 638 using a CMOS sensor may be formed. In this case, since only the photoelectric conversion film 616 is made of an organic material, the TFT layer 638 including the CMOS sensor may not have flexibility.

(2) The photoelectric conversion film 616 may be formed of an organic photoelectric conversion material, and the flexible TFT layer 638 may be realized by a CMOS circuit including a TFT 624 made of an organic material. In this case, pentacene may be adopted as the material of the p-type organic semiconductor used in the CMOS circuit, and copper fluoride phthalocyanine (F ₁₆ CuPc) may be adopted as the material of the n-type organic semiconductor. Thus, a flexible TFT layer 638 that can have a smaller bending radius can be realized. In addition, by configuring the TFT layer 638 in this way, the gate insulating film can be significantly reduced, and the driving voltage can be lowered. Furthermore, the gate insulating film, the semiconductor, and each electrode can be manufactured at room temperature or 100 ° C. or lower. Furthermore, a CMOS circuit can be directly formed over the flexible substrate 602. Moreover, the TFT 624 made of an organic material can be miniaturized by a manufacturing process in accordance with a scaling law. Note that when the polyimide precursor is applied to a thin polyimide substrate by a spin coat method and heated, the polyimide precursor changes to polyimide, so that a flat substrate without unevenness can be realized.

  (3) Applying a self-alignment placement technique (Fluidic Self-Assembly method) that places a plurality of micron-order device blocks at specified positions on a substrate 602, a photoelectric conversion film 616 and a TFT 624 made of crystalline Si are formed on a resin substrate You may arrange | position on the board | substrate 602 which consists of. In this case, the photoelectric conversion film 616 and TFT 624 as micro device blocks of micron order are fabricated in advance on another substrate and then separated from the substrate, and the photoelectric conversion film 616 and TFT 624 in the liquid are placed on the substrate 602 as the target substrate. Sprinkle on and place statistically. The substrate 602 is processed in advance to be adapted to the device block, and the device block can be selectively placed on the substrate 602. Therefore, an optimal device block (photoelectric conversion film 616 and TFT 624) made of an optimal material can be integrated on an optimal substrate (semiconductor substrate, quartz substrate, glass substrate, etc.), and is not a crystal. It is also possible to integrate device blocks (photoelectric conversion film 616 and TFT 624) optimum for a substrate (flexible substrate such as plastic).

  In the radiation detector 600 according to the above-described modification, the light emitted from the scintillator 608 is converted into electric charges by the sensor unit 606 (photoelectric conversion film 616) located on the side opposite to the side where the radiation source 88 is located. Although it is configured as a so-called back side scanning method (PSS (Penetration Side Sampling) method) for reading an image, the present invention is not limited to this configuration.

  For example, the radiation detector 600 may be configured as a so-called surface reading method (ISS (Irradiation Side Sampling) method). 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 50, and the light emitted from the scintillator 608 is sensor unit on the side where the radiation source 88 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 50 than on the rear surface side. Therefore, in the radiation detector configured by the front surface reading method, the scintillator is compared with the radiation detector configured by the rear surface reading method. The distance until the light emitted in 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.

DESCRIPTION OF SYMBOLS 10A-10E ... 1st radiography apparatus-5th radiography apparatus 14 ... Case 16 ... Cassette main-body part 18 ... Radiation source main-body part 20 ... Portable information terminal 22 ... Case 24 ... Irradiation surface 48 ... Subject 50 ... Radiation 54 ... Radiation detector 58 ... Power supply source 60 ... Power transmission unit 62 ... Power reception unit 64 ... Solar cell panel 66 ... Back surface 68 ... Battery 70 ... Power distributors 70a to 70f ... First power distributor to sixth power distributor 72 ... Cassette Control unit 74: Remaining amount detection unit 78 ... Energy output unit 80 ... Output energy conversion unit 82 ... Energy input unit 84 ... Input energy conversion unit 86 ... Housing 88 ... Radiation source 92 ... Radiation source control unit 164 ... Power distribution setting unit 164a to 164f... 1st power distribution setting unit to 6th power distribution setting unit 500A to 500E... 1st mobile device to 5th mobile device 502. 1 side surface-4th side surface 504 ... console 514 ... case accommodating part 520 ... current collecting part 544 ... shelf

Claims (33)

A housing,
A radiation detector installed in the housing for converting radiation transmitted through the subject into radiation image information;
A power supply,
A power transmission unit that transmits at least part of the power from the power supply source toward an external device, and
The radiation detection apparatus according to claim 1, wherein the power supply source is a solar battery panel installed on a surface of the casing. The radiation detection apparatus according to claim 1,
A radiation detection apparatus comprising: a power distributor that distributes power from the power supply source to at least the power transmission unit and the radiation detector. The radiation detection apparatus according to claim 1,
Furthermore, a power storage unit that is installed in the housing and supplies power to at least the radiation detector;
A radiation detection apparatus comprising: a power distributor that distributes power from the power supply source to at least the power transmission unit and the power storage unit. The radiation detection apparatus according to claim 1,
The radiation detection apparatus further includes a power reception unit that receives power from a power transmission unit in another device and supplies the power to at least the radiation detector. The radiation detection apparatus according to claim 1,
Furthermore, a power storage unit that is installed in the housing and supplies power to at least the radiation detector;
A radiation detection apparatus comprising: a power reception unit that receives power from a power transmission unit in another device and supplies the power to the power storage unit. The radiation detection apparatus according to claim 1,
The said solar cell panel is installed in the surface on the opposite side to the irradiation surface irradiated with the radiation which permeate | transmitted the said object among the surfaces of the said housing | casing, The radiation detection apparatus characterized by the above-mentioned. The radiation detection apparatus according to claim 1,
Furthermore, it has a case for housing the housing,
The radiation detection apparatus according to claim 1, wherein the power supply source is a solar cell panel installed on a surface of the case. The radiation detection apparatus according to claim 1,
The power transmission unit transmits power in a non-contact manner to the external device,
A radiation detection apparatus that functions as a power supply of a non-contact power supply method. One or more devices used for radiography;
A case in which the device is removably accommodated;
A power supply,
A power transmission unit that transmits at least part of the power from the power supply source toward the device outside the case, and
The radiation imaging apparatus according to claim 1, wherein the power supply source is a solar cell panel installed on a surface of the case. The radiographic apparatus according to claim 9, wherein
A radiation imaging apparatus, comprising: a power distributor that distributes power from the power supply source to at least the power transmission unit and the device in the case. The radiographic apparatus according to claim 9, wherein
The device to be taken in and out of the case has a casing, and a power storage unit installed in the casing.
A radiation imaging apparatus comprising: a power distributor that distributes power from the power supply source to at least the power transmission unit and the power storage unit. The radiographic apparatus according to claim 9, wherein
The radiation imaging apparatus further includes a power reception unit that receives power from a power transmission unit in another device and supplies the power to the device in the case. The radiation imaging apparatus according to claim 12,
Two or more devices can be taken in and out of the case,
A radiation imaging apparatus comprising: a second power distributor that distributes power from the power receiving unit to two or more devices. The radiation imaging apparatus according to claim 12,
Two or more devices can be taken in and out of the case,
The two or more devices each have a housing and a power storage unit installed in the housing,
A radiation imaging apparatus comprising: a second power distributor that distributes power from the power reception unit to each of the power storage units in two or more devices. The radiation detection apparatus according to claim 9.
The power transmission unit transmits power in a non-contact manner to equipment outside the case,
A radiation imaging apparatus characterized by functioning as a non-contact power supply type power source. A movable carriage,
One or more detector main bodies that contain a radiation detector that is detachable from the carriage and that detects radiation transmitted through the subject and converts the radiation into radiation image information;
One or more power supplies;
A power distributor installed in the carriage and distributing power from the power supply source;
A mobile radiographic imaging apparatus, comprising: a plurality of carriage-side power transmission units installed on the carriage and transmitting the distributed power toward the corresponding detector main body. The mobile radiographic imaging device according to claim 16, wherein
The mobile radiographic imaging device, wherein the detector main body further includes a power receiving unit that receives power from the cart side power transmission unit and supplies the power to at least the radiation detector. The mobile radiographic imaging device according to claim 16, wherein
The detector main body further includes:
A power storage unit for supplying power to at least the radiation detector;
A mobile radiographic imaging apparatus comprising: a power receiving unit that receives power from the cart side power transmission unit and supplies the power to the power storage unit. The mobile radiographic imaging device according to claim 16, wherein
Furthermore, it has one or more radiation source main body portions that are detachable from the carriage and accommodate a radiation source that outputs radiation toward the detector main body portion,
The plurality of carriage-side power transmission units transmit the distributed power toward at least one of the radiation source main body and the detector main body. The mobile radiographic imaging apparatus according to claim 19,
The mobile radiation image capturing apparatus, wherein the radiation source main body further includes a power receiving unit that receives power from the carriage-side power transmission unit and supplies the power to at least the radiation source. The mobile radiographic imaging apparatus according to claim 19,
The radiation source main body further includes:
A power storage unit for supplying power to at least the radiation source;
A mobile radiographic imaging apparatus comprising: a power receiving unit that receives power from the cart side power transmission unit and supplies the power to the power storage unit. The mobile radiographic imaging device according to claim 16, wherein
The power supply source is installed in at least one of the detector body parts,
The detector main body portion on which the power supply source is installed has a device-side power transmission unit that transmits at least part of the power from the power supply source to the power distributor. Shooting device. The mobile radiographic imaging device according to claim 16, wherein
Have two or more power supplies,
A current collector that collects power from each of the power supply sources is installed on the carriage,
The mobile radiation image capturing apparatus, wherein the power distributor distributes power from the current collector. The mobile radiographic imaging device according to claim 23,
The two or more power supply sources are respectively installed in the detector main body,
The detector main body portion in which the power supply source is installed has a device-side power transmission unit that transmits at least part of the power from the power supply source to the current collector. Shooting device. The mobile radiographic imaging apparatus according to claim 22 or 24,
The mobile radiation image capturing apparatus, wherein the power supply source is a solar cell panel installed on a surface of the detector main body. The mobile radiation imaging apparatus according to claim 25,
The carriage has a shelf that accommodates at least the detector body.
Power generation by the solar cell panel is performed in a state in which a part or all of the radiation detector is pulled out from the shelf and the solar cell panel faces upward. The mobile radiographic imaging apparatus according to claim 26, wherein
The cart has two or more shelves in which at least two or more detector main bodies are accommodated,
Two or more shelves are provided on at least two side surfaces of the carriage. A movable carriage,
A radiographic apparatus that is detachable from the carriage and includes one or more devices used for radiography;
One or more power supplies;
A power distributor installed in the carriage and distributing power from the power supply source;
A mobile radiographic image capturing apparatus, comprising: a plurality of cart-side power transmission units configured to transmit the distributed power installed in the cart toward the corresponding radiographic apparatus. The mobile radiographic imaging apparatus according to claim 28,
The power supply source is installed in at least one of the radiation imaging apparatuses;
The radiographic apparatus equipped with the power supply source includes a mobile radiographic image capturing apparatus including a device-side power transmission unit that transmits at least part of the power from the power supply source to the power distributor. apparatus. The mobile radiographic imaging apparatus according to claim 28,
Have two or more power supplies,
A current collector that collects power from each of the power supply sources is installed on the carriage,
The mobile radiation image capturing apparatus, wherein the power distributor distributes power from the current collector. The mobile radiation imaging apparatus according to claim 30, wherein
Two or more power supply sources are installed in the radiation imaging apparatus,
The radiographic apparatus provided with the power supply source includes a mobile radiographic image capturing apparatus including a device-side power transmission unit that transmits at least part of the power from the power supply source to the current collector. apparatus. The mobile radiographic imaging apparatus according to claim 29 or 31,
The radiographic image capturing apparatus includes:
Having a case in which one or more of the devices used for radiography are detachably accommodated;
The mobile radiation imaging apparatus according to claim 1, wherein the power supply source is a solar cell panel installed on a surface of the case. The mobile radiation imaging apparatus according to claim 32,
The carriage has a storage portion in which at least the case is stored,
The mobile radiation image capturing apparatus according to claim 1, wherein power generation by the solar cell panel is performed by housing the case with the solar cell panel facing upward.

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