JP2012029844A - Moving power source vehicle and power supply method - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a moving power source vehicle in which two or more sorts of different medical equipments can be conveyed at once up to the place of victims of a disaster-stricken area or the like for example, moreover which can supply power to the two or more sorts of medical equipments in the field, and to provide a power supply method.SOLUTION: The moving power source vehicle includes: a truck which can move; two or more medical equipments in which the attachment and detachment are made free to the truck and which have different functions; a power supply source installed in the truck; a power distributor which distributes power from the power supply source corresponding with the two or more medical equipments; and two or more power transmission sections which are installed in the truck and transmit the distributed power toward the corresponding medical equipments.

Description

  The present invention relates to a mobile power supply vehicle and a power supply method. For example, a plurality of different medical devices can be easily transported to a stricken area or the like, and power can be easily supplied to medical devices on the spot. The present invention relates to a mobile power supply vehicle and a power supply method.

  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, and imaging is performed in a field room (imaging field room) other than the X-ray (X-ray) 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 an apparatus for charging the battery of the electronic cassette may be provided.

  In recent years, field emission radiation sources using carbon nanotubes (CNT) have been developed (see Patent Document 3 and Non-Patent Document 1), and the radiographic imaging apparatus including the radiation source has been reduced in size and Lightening is expected.

  Further, Non-Patent Document 2 and Non-Patent Document 3 are known as methods for transmitting power wirelessly. The method described in Non-Patent Document 2 transmits power by electromagnetic induction from a primary coil embedded in a non-contact power transmission sheet. The method described in Non-Patent Document 3 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> 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 a problem, and for example, a plurality of different medical devices can be transported to a victim such as a disaster-stricken area at the same time. It is an object of the present invention to provide a mobile power supply vehicle and a power supply method capable of supplying power to medical devices.

[1] A mobile power supply vehicle according to the first aspect of the present invention includes a movable carriage, a plurality of medical devices that are detachably attached to the carriage, different functions, and a power supply source installed on the carriage. A power distributor that distributes power from the power supply source; and a plurality of power transmission units that are installed in the carriage and transmit the distributed power toward the corresponding medical device. To do.

[2] In the first aspect of the present invention, a power receiving unit is installed corresponding to the plurality of medical devices, receives power transmitted from the corresponding power transmitting unit, and supplies power to the corresponding medical device. It is characterized by that.

[3] In the first aspect of the present invention, the power transmission unit transmits power necessary for charging a battery of the corresponding medical device, and the power reception unit receives power transmitted from the corresponding power transmission unit. And supplying to the battery.

[4] In the first aspect of the present invention, a plurality of the power transmission units are installed in the cart corresponding to the plurality of medical devices, and when the medical devices are accommodated in the cart, Among them, power is transmitted from the power transmission unit wired or wirelessly connected to the power reception unit to the power reception unit.

[5] In the first aspect of the present invention, it further includes a plurality of power control units installed corresponding to the power transmission unit, and among the plurality of power control units, the power reception unit and wired connection or wireless connection The power control unit corresponding to the power transmission unit is configured to convert the power distributed by the power distributor into power necessary to charge the battery of the medical device corresponding to the power reception unit, It supplies to a power transmission part, It is characterized by the above-mentioned.

[6] In the first aspect of the present invention, the power transmission unit transmits power necessary to drive the circuit system of the corresponding medical device, and the power reception unit transmits power transmitted from the corresponding power transmission unit. Is received and supplied to the circuit system.

[7] In the first aspect of the present invention, the power management unit further includes a plurality of power control units installed corresponding to the power transmission unit, and the power reception unit and the wired connection or the wireless connection among the plurality of power control units. The power control unit corresponding to the transmitted power unit converts the power distributed by the power distributor into power necessary for driving the circuit system of the medical device corresponding to the power receiving unit. And supplying to the power transmission unit.

[8] In the first aspect of the present invention, the power transmission unit drives a battery power transmission unit that transmits power necessary for charging the battery of the corresponding medical device and a circuit system of the corresponding medical device. A power transmission unit for driving that transmits necessary power, and the power reception unit receives the power transmitted from the corresponding power transmission unit and supplies the power to the battery, and the corresponding power transmission A driving power receiving unit that receives power transmitted from the unit and supplies the power to the circuit system of the medical device.

[9] In the first aspect of the present invention, the battery further includes a case in which the medical device is accommodated, and the battery power transmission unit corresponds to the plurality of medical devices in the case accommodation unit in which the case is accommodated. A plurality of battery power reception units are installed in the case, a plurality of drive power transmission units are installed in the carriage, and each of the drive power reception units is installed in the medical device. Features.

[10] In the first aspect of the present invention, when the case in which the medical device is accommodated is accommodated in the case accommodating portion, the battery power receiving portion of the case among the plurality of battery power transmitting portions; Electric power is transmitted from the battery power transmission unit that is wired or wirelessly connected to the battery power reception unit.

[11] In the first aspect of the present invention, the battery power control unit further includes a plurality of battery power control units installed corresponding to the battery power transmission unit, and the case of the case among the plurality of battery power control units. The battery power control unit corresponding to the battery power transmission unit wired or wirelessly connected to the power receiving unit is configured to use the power distributed by the power distributor as a battery of the medical device housed in the case. It converts into the electric power required for charging, and supplies it to the said battery power transmission part.

[12] In the first aspect of the present invention, among the medical devices that are taken out from the case and are in use, the medical device that is wired or wirelessly connected to the driving power transmission unit is connected to the driving power transmission unit from the driving power transmission unit. Electric power is transmitted to the drive power receiving unit of the medical device.

[13] In the first aspect of the present invention, it further includes a plurality of driving power control units installed corresponding to the driving power transmission unit, and the driving power receiving unit among the plurality of driving power control units. The drive power control unit corresponding to the drive power transmission unit that is wired or wirelessly connected to a unit is the power distributed by the power distributor, the power of the medical device corresponding to the drive power reception unit It converts into electric power required for driving a circuit system, and supplies it to the said power transmission part for driving.

[14] In the first aspect of the present invention, a plurality of portable information terminals corresponding to the plurality of medical devices are provided.

[15] In the first aspect of the present invention, the power receiving unit is installed corresponding to the medical device and the portable information terminal, receives power transmitted from the corresponding power transmitting unit, and corresponds to the medical device and Power is supplied to the portable information terminal.

[16] In the first aspect of the present invention, the power supply source is any one or more of a generator, a transformer, and a storage battery.

[17] In the power supply method according to the second aspect of the present invention, the power from the power supply source is distributed corresponding to a plurality of medical devices each having a different function housed in a movable carriage, and the distributed power Are transmitted to a corresponding medical device via a plurality of power transmission units, and the power transmitted from the plurality of power transmission units is received by a power receiving unit installed corresponding to each of the medical devices. And supplying to the corresponding medical device.

  As described above, according to the mobile power supply vehicle and the power supply method according to the present invention, it is possible to transport a plurality of different types of medical devices at one time, for example, to the victims such as the stricken area, Power can be supplied to multiple types of medical equipment on site.

  In addition, various medical devices can be brought into a site such as a stricken area where it is not known what is happening, and it is possible to respond quickly to various situations. In addition, even if there is a bias in the use of one or more types of medical devices, it is possible to control the interchange of power, thereby improving the efficiency of power use and various kinds of on-site sites such as disaster areas. The medical device can be used for a long time.

It is a perspective view which shows the mobile power vehicle which concerns on this Embodiment. It is explanatory drawing which shows an example of the radiography apparatus accommodated in the case accommodated in a mobile power supply vehicle. It is a block diagram which shows the circuit structure of a mobile power supply vehicle. It is a perspective view which abbreviate | omits and shows the state which accommodates the case in the case accommodating part of a mobile power vehicle. FIG. 5A to FIG. 5D are explanatory views showing an example of using a generator as a power supply source installed in a mobile power supply vehicle. 6A and 6B are explanatory views showing an example of using a transformer as a power supply source installed in the mobile power supply vehicle, and FIG. 6C is an explanatory view showing an example using a storage battery. FIG. 7A is a block diagram illustrating a battery power transmission unit and a battery power reception unit, and FIG. 7B is a block diagram illustrating a drive power transmission unit and a drive power reception unit. It is a perspective view which shows the radiography apparatus which is an example of a medical device. It is sectional drawing which looked at the cross section along the horizontal surface of the radiography apparatus in FIG. 8 in the direction of IX-IX. It is a top view which shows the state which separated the radiation source main-body part from the cassette main-body part of FIG. It is sectional drawing which shows the inside of the radiation source main-body part of FIG. It is sectional drawing which shows imaging | photography by a radiography apparatus. It is a perspective view which shows the imaging preparation of a radiography apparatus. It is a perspective view which shows imaging | photography by a 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. It is a block diagram which shows the electric power supply system of a mobile power supply vehicle. It is a flowchart which shows an effect | action and operation | movement of a mobile power supply vehicle. It is sectional drawing which shows the modification of a radiation detector. It is sectional drawing which showed schematically the structure of the signal output part of 1 pixel part of the radiation detector shown in FIG.

  Embodiments of a mobile power supply vehicle and a power supply method according to the present invention will be described below with reference to FIGS.

  As shown in FIG. 1, a mobile power supply vehicle (hereinafter referred to as a mobile power supply vehicle 10) according to the present embodiment includes a movable carriage 12 and is detachable from the carriage 12. A plurality of medical devices 14 (contained in the case 20) having different functions and a console 16 for controlling power supply to the medical devices 14 and the like are included.

  Specifically, as shown in FIG. 2, for example, the medical device 14 is accommodated together with the portable information terminal 22 in a case 20 having a handle 18 such as an attache case. That is, the medical device 14 is accommodated in the main body portion 20 a of the case 20, and the portable information terminal 22 is accommodated in the lid portion 20 b of the case 20. As the portable information terminal, for example, a portable information terminal having a size of about B5 and having a touch panel function can be used.

  In addition to the radiation imaging device 24 shown in FIG. 2, the medical device 14 includes an electrocardiograph, an ultrasonic diagnostic device, an AED (Automated External Defibrillator), a sphygmomanometer (not shown). There may be a function to measure the pulse and body temperature), and other medical equipment necessary for taking it to the disaster area. When the radiation imaging apparatus 24 is accommodated in the case 20, the radiation detection apparatus (hereinafter referred to as the cassette body part 26) and the radiation source body part 28 are accommodated in the body 20 a of the case 20, and the lid of the case 20 is accommodated. The portable information terminal 22 is accommodated in the unit 20b. In a medical device 14 such as an electrocardiograph, an ultrasonic diagnostic apparatus, an AED, and a blood pressure monitor (not shown), the medical device 14 is accommodated in the main body portion 20a of the case 20, and the portable information terminal 22 is accommodated in the lid portion 20b of the case 20. To do.

  As shown in FIG. 1, the carriage 12 has a plurality of wheels 30 and can be moved by human power by operating a handle 32. Of course, you may make it move electrically. Further, the carriage 12 has a case accommodating portion 34 that can accommodate a plurality of cases 20, and the plurality of cases 20 are placed on the case accommodating portion 34. The example of FIG. 1 shows an example in which eight cases 20 are accommodated. In addition, you may provide the partition part 36 in the case accommodating part 34 so that the case 20 may be mounted easily.

  In addition, as shown in FIG. 3, the mobile power supply vehicle 10 includes a power supply source 40 installed in the carriage 12 and a power distributor 42 that distributes the power from the power supply source 40 in correspondence with at least the medical device 14. And a plurality of battery power transmission units 44 installed on the cart 12 corresponding to at least the medical device 14 and transmitting the distributed power, and a plurality of driving units installed on the cart 12 and transmitting the distributed power. A plurality of battery power receivers installed corresponding to at least the power transmission unit 46 and the medical device 14 and receiving power transmitted from the corresponding battery power transmission unit 44 and supplying power to the battery of the corresponding medical device 14 A plurality of units 48 and a plurality of units that are installed corresponding to the medical device 14, receive power transmitted from the drive power transmission unit 46, and supply power to the circuit system 50 of the corresponding medical device 14. Having a drive power receiving portion 52, a. As shown in FIG. 4, the battery power transmission unit 44 is installed on the mounting surface of the case housing unit 34 of the carriage 12 so as to correspond to the case 20. In the present embodiment, a battery power transmission unit 44 for the medical device 14 and a battery power transmission unit 44 for the portable information terminal 22 are installed for one case 20. For example, a total of three battery power transmission units 44 for the cassette body 26, the radiation source body 28, and the portable information terminal 22 are installed in the case 20 in which the radiation imaging apparatus 24 is accommodated. For example, for the case 20 in which the electrocardiograph is accommodated, a total of two battery power transmission units 44 for the electrocardiograph and for the portable information terminal are installed. The same applies to other medical devices 14.

  On the other hand, a battery power receiving unit 48 for the medical device 14 and a battery power receiving unit 48 for the portable information terminal 22 are installed on the bottom of the case 20 (the surface opposite to the surface on which the handle 18 is attached). The battery power receiving unit 48 for the medical device 14 is electrically connected to the battery 54 of the medical device 14 via the battery terminal 56, and the battery power receiving unit 48 for the portable information terminal 22 is portable information. The battery is electrically connected to the battery 58 of the terminal 22 via the battery terminal 60. Note that a battery power receiving unit 48 for the cassette body 26, a battery power receiving unit 48 for the radiation source body 28, and a battery for the portable information terminal 22 are provided at the bottom of the case 20 for the radiation imaging apparatus 24. A power receiving unit 48 is installed, a battery power receiving unit 48 for the cassette body 26 is electrically connected to a battery terminal 56 of the cassette body 26, and a battery power receiving unit 48 for the radiation source body 28 is a radiation source body. The battery power receiving unit 48 for the portable information terminal 22 is electrically connected to the battery terminal 60 of the portable information terminal 22.

  The drive power transmission unit 46 may be installed in a total of about two in correspondence with one medical device 14 and one portable information terminal 22 corresponding to the one medical device 14, but there may be a case where two or more medical devices 14 are used at the same time. Since it is assumed, it is preferable to install corresponding to two or more medical devices 14 and two or more portable information terminals 22 corresponding thereto. In the present embodiment, as shown in FIG. 1, an example in which twelve drive power transmission units 46 are installed is shown. Of course, as with the battery power transmission unit 44, the drive power transmission units 46 may be installed in a number equal to the total number of the medical devices 14 accommodated in the carriage 12 and the corresponding portable information terminals 22. On the other hand, the drive power reception unit 52 is installed in each medical device 14 and each portable information terminal 22.

  In addition, as shown in FIG. 3, the mobile power vehicle 10 includes a battery power control unit 62 provided corresponding to at least the medical device 14 and a driving power provided corresponding to the driving power transmission unit 46. And a control unit 64. In the present embodiment, an example in which the battery power control unit 62 is installed corresponding to the medical device 14 and the portable information terminal 22 is shown.

  The battery power control unit 62 converts the power distributed by the power distributor 42 into power necessary for charging the battery 54 of the corresponding medical device 14 or the portable information terminal 22 to convert the power to the battery power transmission unit 44. Output to. The drive power control unit 64 converts the power distributed by the power distributor 42 into power necessary for driving the medical device 14 or the portable information terminal 22 being used and outputs the power to the drive power transmission unit 46.

  As shown in FIGS. 5A to 6C, the power supply source 40 can use any one or more of a generator 66, a transformer 68 (AC-DC converter), and a storage battery 70.

  For example, if the generator 66 is a DC output, the power supply source 40 is configured by the generator 66 (see FIG. 5A), or the power supply source is composed of the generator 66 and the storage battery 70 that stores power from the generator 66. 40 (see FIG. 5B). If the generator 66 is an alternating current output, the power supply source 40 is configured by the generator 66 and the transformer 68 that converts the electric power from the generator 66 into direct current (see FIG. 5C), or the generator 66 and the The power supply source 40 may be configured by a transformer 68 that converts power from the generator 66 into direct current and a storage battery 70 that stores power output from the transformer 68 (see FIG. 5D).

  As the generator 66, the following power generators can be preferably used. One type of power generation device may be used, or a plurality of types of power generation devices may be used in combination.

(1) A solar power generation device using solar energy.
(2) A wind power generator using wind energy.
(3) A dynamo-type power generator using the rotational force of wheels or the like.
(4) The energy of pressure generated when a doctor or radiographer (hereinafter also referred to as an operator) operating the mobile power supply vehicle 10 walks or moves the carriage 12 is converted into electrical energy using a piezoelectric element or the like. So-called power generation floor.
(5) Hydroelectric power generators and wave power generators that generate electricity using water from outdoor rivers and lakes.
(6) Other power generators that can be used outdoors.

  On the other hand, if a commercial power source such as a hospital or a house can be used, as shown in FIG. 6A, a cable 74 connected to the commercial power source 72 and a transformer 68 that converts an AC voltage supplied through the cable 74 into a DC voltage. The power supply source 40 may be configured as shown in FIG. 6B, or the power supply source 40 may be configured by the cable 74, the transformer 68, and the storage battery 70 that stores the power from the transformer 68, as shown in FIG. 6B. . Of course, as shown in FIG. 6C, the power supply source 40 may be configured by only the storage battery 70.

  Examples of the storage battery 70 include secondary batteries (such as nickel metal hydride, nickel-cadmium, and lithium) and capacitors (such as electric field capacitors, electric double layer capacitors, and lithium ion capacitors). Of course, power may be supplied from a storage battery of a vehicle such as an automobile and stored in the storage battery 70 in the mobile power supply vehicle 10.

  When the generator 66 is used as the power supply source 40, the amount of power generation (the amount of power generated) is displayed on the display unit 17 of the console 16, and when the transformer 68 is used, the display unit 17 of the console 16 is displayed. When the amount of power supplied per unit time is displayed and the storage battery 70 is used, the amount of power stored in the display unit 17 of the console 16 is displayed. Further, when the power supply source 40 includes the storage battery 70, the amount of power transmitted to the medical device 14 and the portable information terminal 22 and the remaining amount of the storage battery 70 are displayed. This makes it possible to appropriately adjust the drive time of the generator 66, the connection time of the commercial power supply 72, etc. while viewing the display content of the console 16, and the amount of power entering the mobile power supply vehicle 10 and the mobile power supply vehicle It becomes easy to balance the amount of electric power going out from 10.

  As shown in FIGS. 7A and 7B, the battery power transmission unit 44 and the drive power transmission unit 46 include, for example, an energy output unit 76 that outputs power or the like by contact (wired or the like) or non-contact (wireless or the like); An output energy conversion unit 78 that converts electric power from the battery power control unit 62 and the drive power control unit 64 into energy corresponding to the type of the energy output unit 76 and supplies the energy to the energy output unit 76;

  The battery power reception unit 48 and the drive power reception unit 52 are, for example, an energy input unit 80 that receives power such as contact (wired or the like) or non-contact (wireless or the like) and energy from the energy input unit 80 as power. And an input energy conversion unit 82 for conversion.

  The energy output unit 76, the output energy conversion unit 78, the energy input unit 80, and the input energy conversion unit 82 have different configurations depending on the type of energy (supply energy) to be supplied.

  For example, if power is supplied through a wired connection such as a cable or a connection terminal, the energy output unit 76 and the energy input unit 80 are, for example, connectors connected to the cable and the connection terminal. The output energy conversion unit 78 is, for example, a voltage converter that converts the voltage supplied from the battery power control unit 62 and the drive power control unit 64 into an optimum voltage for power transmission. The input energy conversion unit 82 is, for example, a voltage converter that converts a voltage input via the energy input unit 80 into an optimum voltage to be supplied to the circuit system 50.

  As in Non-Patent Document 2, if electromagnetic induction is performed by a coil (primary coil or secondary coil) embedded in a non-contact power transmission sheet, the energy output unit 76 is a primary coil, and the energy input unit 80 is a secondary coil. is there. The output energy conversion unit 78 converts a voltage supplied from the battery power control unit 62 and the drive power control unit 64 into a current that flows to the energy output unit 76 (in this case, functions as a primary coil). The input energy conversion unit 82 converts the voltage generated by the energy input unit 80 (in this case, functioning as a secondary coil) into an optimum voltage for supplying to the circuit system 50, for example, a voltage converter Etc.

  As in Non-Patent Document 3, if the wireless power transmission technology uses magnetic field resonance, the energy output unit 76 is a first LC resonator for power transmission, and the energy input unit 80 corresponds to the first LC resonator. It is the 2nd LC resonator installed. The output energy conversion unit 78 outputs the voltage supplied from the battery power control unit 62 and the drive power control unit 64 as electromagnetic energy from the energy output unit 76 (in this case, functions as the first LC resonator). (The primary coil when the coil of the first LC resonator is a secondary coil) and the like, and the input energy conversion unit 82 is generated by the energy input unit 80 (in this case, functions as the second LC resonator) A coil for converting electromagnetic energy into electric power energy by electromagnetic induction (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 80 is a light energy receiving unit, and the input energy conversion unit 82 corresponds to a photoelectric conversion unit that converts received energy into electric power. In the case of thermal energy, the energy input unit 80 is a heat receiving unit that receives thermal energy, and the input energy conversion unit 82 is a thermoelectric conversion element that converts received heat into electric power (for example, a thermoelectric conversion element using the Seebeck effect). Etc.

  In the following description, the energy output unit 76 of the battery power transmission unit 44 (and the drive power transmission unit 46) and the energy input unit 80 of the battery power reception unit 48 (and the drive power reception unit 52) are connected by cables, connection terminals, or the like. The state in which energy can be input / output is described as “wired connection”, and energy input / output can be performed in a non-contact state, for example, the energy output unit 76 and the energy input unit 80 enter an area where wireless power feeding is possible. The state is described as “wireless connection”.

  Here, as a specific example of the medical device 14, for example, a radiation imaging apparatus 24 is used. As shown in FIG. 8, a housing having a substantially rectangular outer shape and capable of transmitting radiation 84 (see FIG. 11). A cassette body 26 and a columnar radiation source body 28.

  In this case, a guide line 88 serving as a reference for the imaging region and the imaging position is formed on one surface (irradiation surface 86) of the cassette body 26. A handle 92 is provided on one long side surface 90a. Further, of the two short side surfaces 90b and 90c of the cassette body 26, one side surface 90b has a USB (Universal Serial Bus) terminal 94 as an interface means capable of transmitting and receiving information to and from an external device, A card slot 98 for loading the memory card 96, the above-described battery terminal 56, and the drive power receiving unit 52 are provided. On the other hand, the radiation source main body 28 includes an exposure switch 102 for starting output of radiation 84 (see FIG. 11) from the radiation source 100 described later, the battery terminal 56 described above, and a drive power receiving unit 52. Is provided.

  Further, as shown in FIG. 9, a measure 104 is also arranged in the cassette body 26. The measure 104 is, for example, a measure that winds the band member 108 with the scale 106 swung into a roll shape by the action of a spring member (not shown), and the side of the measure 104 has a band member 108 from the measure 104 on the side. A rotary encoder 110 that detects the amount of drawer is attached. The distal end portion of the band member 108 drawn out from the measure 104 is fixed to the radiation source main body portion 28 through a hole 112 formed at a location facing the measure 104 on the other long side surface 90d of the cassette main body portion 26. Yes.

  Therefore, as shown in FIG. 9, in a state where the radiation source main body 28 is brought close to the cassette main body 26, most of the band member 108 is rolled in the measure 104 by the action of the spring member inside the measure 104. Rolled up. On the other hand, as shown in FIGS. 10 to 14, when the cassette body 26 and the radiation source body 28 are separated, the radiation source body 28 is separated from the cassette body 26 against the action of the spring member. Thus, the band member 108 can be pulled out from the measure 104 through the hole 112.

  In the above description, the measure 104 can take up the band member 108 with the scale 106 swung, but instead of the band member 108, the measure 104 is a string member (string) with the scale 106 swung. Of course, the same function as the belt member 108 can be achieved.

  Furthermore, as shown in FIG. 12, the cassette body 26 is irradiated with radiation 84 from a radiation source 100 to a subject 114 (a victim, a victim, a medical examinee, a home-stayed person, etc., which is a radiographic image capturing target). The grid 116 for removing the scattered radiation of the radiation 84 from the subject 114, the radiation detector 118 for detecting the radiation 84 transmitted through the subject 114, and the lead plate 120 for absorbing the back scattered radiation of the radiation 84 are included in the subject. They are arranged in order with respect to the irradiation surface 86 on the 114 side. Note that the irradiation surface 86 may be configured as the grid 116.

  In this case, as the radiation detector 118, for example, the radiation 84 transmitted through the subject 114 is temporarily converted into visible light by a scintillator, and the converted visible light is made of a substance such as amorphous silicon (a-Si). (Hereinafter also referred to as “pixels”) An indirect conversion type radiation detector that converts an electrical signal into an electrical signal, or a dose of radiation 84 is directly converted into an electrical signal by a solid-state detection element made of a substance such as amorphous selenium (a-Se). A direct conversion type radiation detector can be employed.

  Furthermore, inside the cassette body 26, as shown in FIG. 9, a battery 54 as a power source for the cassette body 26, and a switching unit 122 for switching between the power from the battery 54 and the power from the power receiving unit 52 for driving. A cassette control unit 124 that drives and controls the radiation detector 118 (see FIG. 12) with the electric power supplied from the battery 54 or the driving power receiving unit 52, and a signal including information on the radiation 84 detected by the radiation detector 118. A transceiver 126 that transmits and receives to / from the outside is accommodated. The cassette control unit 124 and the transceiver 126 are provided with a lead plate or the like on the irradiation surface 86 side of the cassette control unit 124 and the transceiver 126 in order to avoid damage due to the radiation 84 being irradiated. It is preferable.

  Here, the battery 54 or the drive power receiving unit 52 supplies power to the rotary encoder 110, the radiation detector 118, the cassette control unit 124, and the transceiver 126 in the cassette body 26 via the switching unit 122.

  As the battery 54, 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 54 may be constituted by a small built-in capacitor capable of storing an amount of power necessary for photographing at least one sheet.

  The transmitter / receiver 126 can transmit / receive a signal to / from the outside. Therefore, the transmitter / receiver 126 transmits / receives a signal to / from the portable information terminal 22 corresponding to the radiation imaging apparatus 24, and the radiation source body separated from the cassette body 26. It is possible to transmit / receive signals to / from the transceiver 128 (see FIG. 11) of the unit 28 and to / from the console 16 installed on the carriage 12.

  As shown in FIG. 11, the radiation source main body 28 includes a radiation source 100, a battery 54, a switching unit 122, a transceiver 128, a radiation source control unit 130 that controls the radiation source 100, and a laser. A pointer 132 is disposed, and a battery terminal 56 and a drive power receiving unit 52 similar to those of the cassette body 26 are provided on a side surface of the housing.

  The radiation source 100 is a field emission type radiation source similar to that of Patent Document 3.

  That is, in the radiation source 100, a disk-shaped rotating anode 138 is attached to a rotating shaft 136 that is rotated by a rotating mechanism 134, and an annular target whose main component is a metal element such as Mo is formed on the surface of the rotating anode 138. Layer 140 is formed. On the other hand, a cathode 142 is disposed facing the rotating anode 138, and a field emission electron source 144 is disposed on the cathode 142 so as to face the target layer 140.

  The radiation source control unit 130 controls the radiation source 100 to output the radiation 84 due to the operation of the exposure switch 102 by the operator. In other words, in the radiation source 100, the rotating mechanism 134 rotates the rotating shaft 136 according to the control from the radiation source control unit 130, so that the rotating anode 138 rotates, and the power source unit 146 is based on the power supply from the switching unit 122. When a voltage (negative voltage) is applied to the field emission electron source 144 and the power supply unit 148 applies a voltage between the rotating anode 138 and the cathode 142 based on the power supply from the switching unit 122 (the rotating anode 138). When a positive voltage is applied to the cathode 142 and a negative voltage is applied to the cathode 142), electrons are emitted from the field emission electron source 144, and the emitted electrons are caused by the voltage applied between the rotating anode 138 and the cathode 142. It is accelerated and collides with the target layer 140. From the electron collision surface (focal point 150) in the target layer 140, radiation 84 corresponding to the collided electrons is output to the outside.

  Here, when a radiographic image is taken by irradiating the subject 114 with the radiation 84, between the focal point 150 of the radiation source 100 and the position 152 of the radiation detector 118 just below the focal point 150 (see FIG. 12). Is set in advance as the distance between the source image and the image (SID), and the center position of the irradiation range of the radiation 84 on the irradiation surface 86 and the center position 154 of the guide line 88 (crossed in a cross shape). It is necessary to perform a shooting preparation work including a work to match the intersection of the two guide lines 88.

  In this case, as shown in FIGS. 12 and 13, the operator pulls out the band member 108 from the measure 104 in accordance with the SID while the radiation source body 28 is separated from the cassette body 26. The band member 108 is pulled out until Further, the laser pointer 132 projects the laser beam 156 onto the irradiation surface 86 according to the control from the radiation source control unit 130, so that the center position of the irradiation range of the radiation 84 when the radiation 84 is irradiated onto the irradiation surface 86. Is displayed on the irradiation surface 86 as a cross-shaped mark 158.

In addition, SID≈ is generally between the distance l2 between the position 152 and the center position 154 and the side surface 90d provided with the hole 112 from which the band member 108 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 108 is pulled out from the measure 104 by the pulling amount l1, the position of the radiation source main body 28 is adjusted so that the position of the mark 158 displayed on the irradiation surface 86 and the center position 154 coincide with each other. Thereafter, as shown in FIG. 14, the radiation image of the subject 114 is irradiated by irradiating the subject 114 arranged on the irradiation surface 86 from the radiation source 100 due to the operator turning on the exposure switch 102. It is possible to appropriately perform the shooting. Note that FIG. 14 illustrates the case where the hand of the subject 114 is photographed.

  As schematically shown in FIG. 15, the radiation detector 118 includes a plurality of pixels 160 arranged on a substrate (not shown), a plurality of gate lines 162 that supply control signals to the pixels 160, and a plurality of gate lines 162. A large number of signal lines 164 for reading out electrical signals output from the pixels 160 are arranged.

  Next, as an example, the circuit configuration of the cassette body 26 when the indirect conversion type radiation detector 118 is employed will be described in detail with reference to FIG.

  The radiation detector 118 has a structure in which a photoelectric conversion layer 166 in which each pixel 160 made of a substance such as a-Si that converts visible light into an electric signal is formed is arranged on an array of matrix-shaped TFTs 168. In this case, in each pixel 160, 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 168 for each row. .

  To the TFT 168 connected to each pixel 160, a gate line 162 extending in parallel with the row direction and a signal line 164 extending in parallel with the column direction are connected. Each gate line 162 is connected to the line scan driver 170, and each signal line 164 is connected to the multiplexer 172. Control signals Von and Voff for controlling on / off of the TFTs 168 arranged in the row direction are supplied from the line scan driving unit 170 to the gate line 162. In this case, the line scan driver 170 includes a plurality of switches SW1 for switching the gate lines 162, and an address decoder 174 that outputs a selection signal for selecting one of the switches SW1. An address signal is supplied from the cassette control unit 124 to the address decoder 174.

  In addition, the charge held in each pixel 160 flows out to the signal line 164 through the TFTs 168 arranged in the column direction. This charge is amplified by amplifier 176. A multiplexer 172 is connected to the amplifier 176 via a sample and hold circuit 178. The multiplexer 172 includes a plurality of switches SW2 that switches the signal line 164, and an address decoder 180 that outputs a selection signal for selecting one of the switches SW2. An address signal is supplied to the address decoder 180 from the cassette control unit 124. An A / D converter 182 is connected to the multiplexer 172, and a radiographic image converted into a digital signal by the A / D converter 182 is supplied to the cassette control unit 124.

  Note that the TFT 168 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 charge-coupled device (CCD) image sensor that transfers charges while shifting them with a shift pulse corresponding to the gate signal referred to in the TFT 168.

  FIG. 17 is a block diagram of the radiation imaging apparatus 24. In the description of FIG. 17, the description will focus on components that have not been described in FIGS. 8 to 16.

  The cassette control unit 124 includes an address signal generation unit 184, an image memory 186, and an SID determination unit (inter-photographing distance determination unit) 188.

  The address signal generator 184 supplies an address signal to the address decoder 174 of the line scan driver 170 and the address decoder 180 of the multiplexer 172. The image memory 186 stores the radiation image detected by the radiation detector 118.

  The SID determination unit 188 uses the current pull-out amount of the band member 108 based on the pull-out amount of the band member 108 from the measure 104 input from the rotary encoder 110 and the distance 12 stored in advance. Is calculated as a distance between the focal point 150 and the position 152 when the lens is placed above the irradiation surface.

  If the calculated inter-shooting distance matches the SID, the SID determination unit 188 sets the pull-out amount of the band member 108 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 192 of the portable information terminal 22 via the transceiver 126 and the transceiver 190 of the portable information terminal 22. A mechanism may be provided that locks the belt member 108 so that the belt member 108 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 determining unit 188 sends information indicating that the difference between the current withdrawal amount and the withdrawal amount l1 and the inter-photographing distance does not match the SID to the transceiver 126, The image is displayed on the display unit 192 via 190.

  The SID determination unit 188, the rotary encoder 110, and the measure 104 constitute an inter-shooting distance setting unit 194.

  The cassette control unit 124 can also transmit the ID information of the cassette body unit 26 and the radiation image stored in the image memory 186 to the portable information terminal 22 via wireless communication via the transceiver 126.

  Here, an operation for preparing for imaging using the cassette body 26 and the radiation source body 28 and an operation for actually imaging will be described.

  First, the operator prepares for radiation imaging at the destination site. That is, by operating the operation unit 196 of the portable information terminal 22, shooting conditions such as subject information (for example, SID) related to the subject 114 to be photographed are registered. If the imaging region and imaging method are determined in advance, these imaging conditions are also registered in advance. If the subject 114 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 22 at a medical institution to which the operator belongs.

  In this way, when the operator operates the operation unit 196 of the portable information terminal 22, the shooting conditions such as subject information related to the subject 114 to be imaged are transmitted and received by the cassette main body 26 from the transceiver 190 by wireless communication. Is transmitted to the machine 126 and registered in the cassette control unit 124.

  The operator performs the setting operation of the inter-imaging distance and the setting operation for matching the mark 158 displayed on the irradiation surface 86 with the center position 154 of the guide line 88, and then the irradiation surface 86 and the radiation source main body 28. The subject 114 is placed between the two and the subject 114 is positioned.

  In this case, the operator first moves the radiation source main body 28 and pulls out the band member 108 until the pull-out amount of the band member 108 from the measure 104 becomes the pull-out amount l1 corresponding to the SID.

  There are the following two methods for pulling out the belt member 108 until the pulling amount l1 is reached.

  The first method is a method in which the SID determination unit 188 automatically determines whether or not the withdrawal amount l1 has been reached, and causes the operator to pull out the belt member 108 until the withdrawal amount l1 corresponding to the SID is reached.

  In the first method, the rotary encoder 110 detects the pull-out amount of the band member 108, and the SID determination unit 188 uses the current pull-out amount of the band member 108 based on the detected pull-out amount. The distance between photographing between the focal point 150 and the position 152 when the 28 is disposed above the irradiation surface 86 is calculated.

  If the distance between images matches the SID, the SID determination unit 188 sends information indicating that the amount of withdrawal of the belt member 108 (the amount of extraction 11) and the distance between images matches the SID via the transceivers 126 and 190. On the other hand, if the distance between images does not match the SID, information indicating that the difference between the current amount of withdrawal and the amount of withdrawal 11 and the distance between images does not match the SID are displayed on the transceiver 126. , 190 are displayed on the display unit 192.

  Therefore, according to the first method, the operator only has to pull out the band member 108 from the measure 104 in accordance with the display content of the display unit 192, so that it is possible to easily perform the setting operation of the inter-photographing distance.

  The second method is a method in which, when the pullout amount l1 is known in advance, the operator pulls out the band member 108 from the measure 104 until the pullout amount l1 is reached while looking at the scale 106.

  In this way, after the band member 108 is pulled out until the pulling amount 11 corresponding to the SID is reached, the operator moves the radiation source main body 28 so as to face the irradiation surface 86.

  At this time, the laser pointer 132 is controlled so that the laser beam 156 is projected onto the irradiation surface 86. Accordingly, the center position of the irradiation range of the radiation 84 when the radiation 84 is irradiated on the irradiation surface 86 is displayed as a cross-shaped mark 158. As a result, the operator adjusts the position of the radiation source main body 28 so that the position of the mark 158 and the center position 154 coincide.

  Thus, after adjusting the position of the radiation source main body 28 so that the position of the mark 158 and the center position 154 coincide with each other, the operator determines that the center of the imaging region of the subject 114 is the center position 154 (the position of the mark 158). The subject 114 is placed (positioned) on the irradiation surface 86 so as to coincide with ().

  The radiation source main body 28 is fixed at the adjusted position by a holding member (not shown) after the above-described position adjustment is performed, for example.

  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 114, the operator operates the exposure switch 102 to start photographing the subject 114.

  Due to the operation of the exposure switch 102, the radiation source control unit 130 requests the cassette control unit 124 to transmit an imaging condition by wireless communication, and the cassette control unit 124 determines based on the received request. The imaging condition (control signal) relating to the imaging region of the subject 114 is transmitted to the radiation source main body 28. When the radiation source control unit 130 receives the imaging condition, the radiation source control unit 130 stops the projection of the laser beam 156 by the laser pointer 132 and, according to the imaging condition, emits radiation 84 having a predetermined dose to the subject 114. Control the source 100.

  Thereby, in the radiation source 100, the rotation mechanism 134 rotates the rotation shaft 136 and the rotation anode 138 according to the control from the radiation source control unit 130, while the power source unit 146 is based on the power supply from the switching unit 122. Thus, a negative voltage is applied to the field emission electron source 144, and the power source unit 148 applies a voltage between the rotating anode 138 and the cathode 142 based on the power supply from the switching unit 122. The electrons emitted from the 144 are accelerated by the voltage applied between the rotating anode 138 and the cathode 142 and collide with the target layer 140, and the collision surface (focal point 150) of the target layer 140 causes the collision. Radiation 84 corresponding to the emitted electrons is output to the outside.

  When the subject 84 is irradiated with the radiation 84 for a predetermined irradiation time based on the imaging conditions, the radiation 84 passes through the subject 114 and reaches the radiation detector 118 in the cassette body 26.

  When the radiation detector 118 is an indirect conversion type radiation detector, the scintillator constituting the radiation detector 118 emits visible light having an intensity corresponding to the intensity of the radiation 84 to constitute the photoelectric conversion layer 166. Each pixel 160 converts visible light into an electrical signal and accumulates it as a charge. Next, the charge information that is the radiation image of the subject 114 held in each pixel 160 is read according to the address signal supplied from the address signal generation unit 184 constituting the cassette control unit 124 to the line scan driving unit 170 and the multiplexer 172. .

  That is, the address decoder 174 of the line scan driver 170 outputs a selection signal according to the address signal supplied from the address signal generator 184, selects one of the switches SW1, and the TFT 168 connected to the corresponding gate line 162. A control signal Von is supplied to the gates of the first and second gates. On the other hand, the address decoder 180 of the multiplexer 172 outputs a selection signal in accordance with the address signal supplied from the address signal generation unit 184, sequentially switches the switch SW2, and is connected to the gate line 162 selected by the line scan driving unit 170. Radiation images as charge information held in each pixel 160 are sequentially read out via the signal line 164.

  The radiographic image read out from each pixel 160 connected to the selected gate line 162 is amplified by each amplifier 176, then sampled by each sample hold circuit 178, and then A / D converter via the multiplexer 172. 182, and is converted into a digital signal. The radiographic image converted into the digital signal is temporarily stored in the image memory 186 of the cassette control unit 124.

  Similarly, the address decoder 174 of the line scan driver 170 sequentially switches the switch SW1 in accordance with the address signal supplied from the address signal generator 184, and the charge held in each pixel 160 connected to each gate line 162. A radiation image as information is read out via the signal line 164 and stored in the image memory 186 of the cassette control unit 124 via the multiplexer 172 and the A / D converter 182.

  The radiographic image stored in the image memory 186 is transmitted to the portable information terminal 22 by wireless communication via the transceiver 126, and the portable information terminal 22 causes the display unit 192 to display the received radiographic image. Accordingly, the operator can grasp whether or not the imaging of the imaging region of the subject 114 has been appropriately performed by confirming the radiation image displayed on the display unit 192.

  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 performs reimaging on the subject 114.

  Note that the radiographic image displayed on the display unit 192 may be an image that can be used to determine whether or not the current imaging is appropriate, and thus may be a radiographic image stored in the image memory 186 or low data. Or an image processed to a relatively low resolution.

  The mobile power supply vehicle 10 has at least two functions as power supply to the medical device 14 and the portable information terminal 22.

  The first power supply function will be described with the medical device 14 as a main component. For example, as shown in FIG. 4, while the case 20 is placed in the case housing portion 34 of the carriage, the first power supply function is used for the battery of the medical device 14. When the power receiving unit 48 (installed at the bottom of the case 20) and the battery power transmission unit 44 on the cart 12 side are connected by wire or wirelessly, the state is detected and the medical device 14 is Electric power necessary for charging the battery 54 of the medical device 14 is transmitted via the battery power transmission unit 44 and the battery power reception unit 48. The same applies to the portable information terminal 22.

  When the medical device 14 is used (when it is taken out from the case 20 and actually used), the second power supply function is a power receiving unit 52 for driving the medical device 14 and a power transmitting unit for driving on the cart 12 side. 46 is connected to the medical device 14 by a wired connection or a wireless connection, and the power (for example, rated power) necessary for driving the medical device 14 is detected by the driving power transmission unit 46 and the drive. Power is transmitted via the power receiving unit 52. The same applies to the portable information terminal 22.

  In order to realize these functions, as shown in FIG. 18, the battery power reception unit 48 for the medical device and the portable information terminal includes an RFID (Radio Frequency IDentification), a remaining amount detection unit 200, and a first transmission. The battery power transmission unit 44 includes an RFID reader 204 and a second transmission unit 206, and the drive power reception unit 52 similarly includes a third transmission unit 208.

  The remaining amount detection unit 200 detects the remaining amount of the battery 54 (58), and outputs a signal indicating full charge to the first transmission unit 202 when the battery 54 (58) is fully charged. The first transmission unit 202 transmits a charge completion signal Sa toward the console 16 based on an input of a signal indicating full charge from the remaining amount detection unit 200. The charging completion signal Sa includes ID information of the medical device 14 or the portable information terminal 22 that is the transmission source.

  The RFID reader 204 of the battery power transmission unit 44 is configured such that the case 20 in which the medical device 14 and the portable information terminal 22 are accommodated is placed and fixed on the case accommodation unit 34 of the carriage 12, and the battery power reception unit 48 is located on the carriage 12 side. When the battery power transmission unit 44 is wired or wirelessly connected, the ID information of the RFID installed in the battery power reception unit 48 is read and output to the second transmission unit 206.

  The second transmission unit 206 of the battery power transmission unit 44 transmits the first connection detection signal Sb including the input ID information and the port number of the battery power transmission unit 44 toward the console 16 and the corresponding medical device. 14 or the switching unit 122 of the portable information terminal 22. Further, the second transmission unit 206 is configured such that when the case 20 is taken out from the case housing unit 34 of the carriage 12 and the wired connection or the wireless connection between the battery power transmission unit 44 and the battery power reception unit 48 is disconnected, 1 cut detection signal Sc is output. The first disconnection detection signal Sc includes the port number of the battery power transmission unit 44 in which the wired connection or the wireless connection is disconnected.

  The third transmission unit 208 of the drive power reception unit 52 outputs the second connection detection signal Sd when the drive power reception unit 52 is wired or wirelessly connected to the drive power transmission unit 46 on the cart 12 side, and wired. When the connection is disconnected or the wireless connection is disconnected, the second disconnection detection signal Se is transmitted to the console 16. The second connection detection signal Sd and the second disconnection detection signal Se include ID information of the medical device 14 or the portable information terminal 22 that is the transmission source. In particular, the second connection detection signal Sd is also transmitted to the switching unit 122.

  The switching unit 122 switches the power from the battery 54 to be sent to the circuit system 50 when the first connection detection signal Sb is input, and the power from the power receiving unit 52 for driving based on the input of the second connection detection signal Sd. To be sent to the circuit system 50.

  The console 16 of the mobile power supply vehicle 10 includes a transceiver 210, a first determination unit 212, a second determination unit 214, a first power information acquisition unit 216, a second power information acquisition unit 218, and a first power transmission. It has a stop unit 220, a second power transmission stop unit 222, a memory 224, and an empty port extraction unit 226.

  The first determination unit 212 determines whether or not the signal received via the transceiver 210 is the charge completion signal Sa, the first connection detection signal Sb, or the first disconnection detection signal Sc.

  The first power information acquisition unit 216 is activated when the first determination unit 212 determines that it is the first connection detection signal Sb, and transmits based on the ID information included in the first connection detection signal Sb. Information on the power necessary for charging the battery 54 (58) of the original medical device 14 or the portable information terminal 22 (battery power information Da) is acquired from the memory 224 of the console 16 or the network, and the first connection detection signal Sb Are supplied to the battery power control unit 62 connected to the battery power transmission unit 44 of the port number included in the.

  The first power information acquisition unit 216 also includes a combination of the ID information of the medical device (or portable information terminal) connected in a wired or wireless manner and the port number of the battery power transmission unit 44 in the first power transmission information table having a list structure. Is registered as list data.

  The battery power control unit 62 converts the power distributed from the power distributor 42 into the power indicated by the battery power information Da from the first power information acquisition unit 216 and outputs the power to the corresponding battery power transmission unit 44. To do.

  The first power transmission stop unit 220 is activated when the first determination unit 212 determines that the charge completion signal Sa or the first disconnection detection signal Sc is detected, and the first power transmission stop unit 220 generates a charge completion signal Sa or the first disconnection detection signal Sc. Based on the included ID information, for example, the port number corresponding to the ID is searched from the first power transmission information table, and the battery power control unit 62 connected to the battery power transmission unit 44 corresponding to the searched port number is driven. To stop. In particular, when the first power transmission stop unit 220 is activated based on the first disconnection detection signal Sc, list data in which the ID information included in the first disconnection detection signal Sc is registered in the first power transmission information table. Is deleted.

  The second determination unit 214 determines whether the signal received via the transceiver 210 is the second connection detection signal Sd or the second disconnection detection signal Se.

  The empty port extraction unit 226 displays the port number of the drive power transmission unit 46 that is not in use on the display unit of the console 16. The second power transmission information table stored in the memory 224 is used to search for the drive power transmission unit 46 that is not in use. In the second power transmission information table, each record is registered in association with the port number of the power transmission unit 46 for wired or wireless connection and the ID information of the corresponding medical device 14 or portable information terminal 22. It has become so. In the initial stage, ID information is not registered, and an initial value is registered. That is, the port number of the drive power transmission unit 46 that is not connected by wire or wirelessly is registered in association with the initial value instead of the ID information.

  Therefore, the free port extraction unit 226 extracts one of the port numbers registered corresponding to the initial values from the port numbers registered in the second power transmission information table and displays them on the display unit 17 of the console 16. To do. At this time, an LED (light emitting element) is provided corresponding to each of the plurality of drive power transmission units 46 installed in the carriage 12, and the LED corresponding to the drive power transmission unit 46 corresponding to one extracted port number is emitted. You may make it do. The operator can recognize at a glance which drive power transmission unit 46 is free by the port number displayed on the display unit of the console 16 or the light emission of the LED. In particular, by emitting light, it is convenient to confirm at a glance which drive power transmission unit 46 should be connected during a wired connection or wireless connection with the drive power reception unit 52. . The operator makes a wired connection or a wireless connection between the instructed drive power transmission unit 46 and the medical device 14 or the portable information terminal 22 that can no longer be used. At this time, the second connection detection signal Sd is transmitted from the third transmission unit 208 of the drive power reception unit 52.

  The second power information acquisition unit 218 is activated when the second determination unit 214 determines that it is the second connection detection signal Sd, and based on, for example, ID information included in the second connection detection signal Sd, Information (drive power information Db) of power (for example, rated power) necessary for driving the medical device 14 and the portable information terminal 22 is acquired from the memory 224 of the console 16 or the network. The second power information acquisition unit 218 is a port number from the empty port extraction unit 226 (one drive power transmission unit 46 extracted from the drive power transmission unit 46 that is not in use. The port number of the drive power transmission unit 46 that is wired or wirelessly connected) is acquired.

  Then, the second power information acquisition unit 218 supplies the drive power information Db acquired this time to the drive power control unit 64 connected to the drive power transmission unit 46 corresponding to the acquired port number. The drive power control unit 64 converts the power distributed from the power distributor 42 into the power indicated by the drive power information Db from the second power information acquisition unit 218 and outputs it to the corresponding drive power transmission unit 46. To do.

  Further, the second power information acquisition unit 218 is included in the second connection detection signal Sd instead of the initial value in the record in which the acquired port number is registered among the records of the second power transmission information table. Register ID information. Accordingly, the correspondence relationship between the drive power transmission unit 46 and the drive power reception unit 52 that are wired or wirelessly connected is registered in the second power transmission information table.

  The second power transmission stop unit 222 is activated when the second determination unit 214 determines that it is the second disconnection detection signal Se, and based on, for example, ID information included in the second disconnection detection signal Se. The port number is searched from the second power transmission information table, and driving of the driving power control unit 64 connected to the driving power transmission unit 46 corresponding to the searched port number is stopped. Thereafter, the second power transmission stopping unit 222 sets the ID of the record in which the ID information included in the second disconnection detection signal Se is registered in the second power transmission information table as an initial value.

  Next, the operation and operation of the mobile power supply vehicle 10 will be described with reference to the flowchart of FIG.

  First, in step S <b> 1 of FIG. 19, the case 20 in which the medical device 14 and the portable information terminal 22 are accommodated is placed and fixed in the case accommodating portion 34 of the mobile power supply vehicle 10.

  In step S <b> 2, charging of the battery 54 of the medical device 14 and the battery 58 of the portable information terminal 22 housed in each case 20 is started. When the case 20 is placed and fixed on the case housing portion 34, the battery power transmission unit 44 and the battery power reception unit 48 are connected by wire or wirelessly, and further, the RFID is installed on the battery power reception unit 48 from the RFID. The information is read, and the first connection detection signal Sb is output from the second transmission unit 206 of the battery power transmission unit 44 toward the console 16. Thereby, the electric power necessary for charging each battery 54 (58) of the medical device 14 and the portable information terminal 22 accommodated in the corresponding case 20 is transmitted from the battery power transmission unit 44 on which the case 20 is placed. The The electric power (energy) output from the battery power transmission unit 44 is received by the corresponding battery power reception unit 48 and supplied to each battery 54 (58) of the medical device 14 and the portable information terminal 22 to be charged. .

  In step S <b> 3, the operator pushes the mobile power supply vehicle 10 by hand and moves (transports) to the victim in the disaster area, for example. If the generator 66 is included in the power supply source 40, power generation is performed when the mobile power supply vehicle 10 is moving or stopped, for example, and the power is supplied to the power distributor 42, the battery power control unit 62, and the battery power transmission. Are supplied to each medical device 14 and the battery 54 (58) of each portable information terminal 22 via the unit 44 and the battery power receiving unit 48, and charging is performed in each battery 54 (58).

  In this battery charging, the power from the power distributor 42 is converted into the power indicated by the battery power information Da from the first power information acquisition unit 216 in the battery power control unit 62, and the corresponding battery power transmission is performed. Output to the unit 44 and supplied to the corresponding battery 54 (58) via the battery power receiving unit 48 from the battery power transmitting unit 44. For the medical device 14 and the portable information terminal 22 that have been charged, the first power transmission stop unit 220 corresponds to the corresponding battery power control unit based on the output of the charging completion signal Sa from the corresponding battery power receiving unit 48. By stopping driving 62, power supply to the battery 54 (58) is stopped.

  After that, in step S4, when the mobile power supply vehicle 10 arrives at the site of the disaster area, the doctor selects the medical device 14 to be used from the damage situation of the victim, and the case 20 corresponding to the selection is a cart. Will be taken down from 12. For the medical device 14 and the portable information terminal 22 housed in the case 20 that is lowered from the cart 12, the first power transmission stop unit is based on the output of the first disconnection detection signal Sc from the corresponding battery power transmission unit 44. When 220 stops driving the corresponding battery power control unit 62, power supply to the battery 54 (58) is stopped.

  In step S <b> 5, the operator takes out the medical device 14 and the portable information terminal 22 from the case 20 and starts an inspection using the medical device 14. For example, radiographing device 24 may be used to photograph victims or broken patients under the building, or an electrocardiograph may be used to cause an electric shock to victims with cardiopulmonary arrest. When it is analyzed that the electric shock is necessary, the AED is used to give the victim an electric shock. Moreover, ultrasonic diagnosis, blood pressure measurement (including pulse, body temperature measurement, etc.) and the like are performed as necessary. In some cases, the above-described inspection or the like is performed on a plurality of victims. In using the medical device 14 and the portable information terminal 22, power from the battery 54 (58) is supplied to the circuit system 50 through the switching unit 122.

  When using various medical devices 14, the corresponding portable information terminal 22 is used as a controller, and the necessary information is obtained using the touch panel while watching the menu screen displayed on the display screen of the portable information terminal 22. It is done while inputting.

  In step S6, the data of the test result of the victim obtained by using the medical device 14 is transmitted to the console 16 of the mobile power supply car 10 via the corresponding portable information terminal 22, and if necessary, It is also sent to medical institutions via the network.

  In step S7, when the remaining battery level of the medical device 14 and / or the portable information terminal 22 in use is low, the operator cannot use the medical device 14 and / or the portable information terminal 22 in step S8. Select whether to continue using or to stop using and charge the battery.

  If it is battery charging, it will progress to step S13 and will accommodate the medical device 14 and / or the portable information terminal 22 which became unusable in the case 20, and will accommodate in the case accommodating part 34 of the trolley | bogie 12. FIG.

  If it is a continuation use, it will progress to step S9 and an operator will confirm the drive power transmission part 46 which should be used. That is, the port number displayed on the display unit 17 of the console 16 (the port number extracted by the empty port extraction unit 226 among the port numbers of the driving power transmission unit 46 not in use) or the driving power transmission unit 46. Confirm the light emission of the LED installed corresponding to.

  In step S <b> 10, the drive power transmission unit 46 corresponding to the designated port number and the medical device 14 and / or the drive power reception unit 52 of the portable information terminal 22 that are no longer usable are connected by wire or wirelessly.

  In step S11, power supply to the circuit system 50 of the medical device 14 and / or the portable information terminal 22 is started. That is, the second connection detection signal Sd is output from the third transmission unit 208 of the drive power reception unit 52 to the console 16. Electric power necessary for driving is transmitted from the driving power transmission unit 46 corresponding to the instructed port number to the medical device 14 and / or the circuit system 50 of the portable information terminal 22 that has been continuously used this time. At this time, since the switching unit 122 switches the power from the battery 54 (58) to the power from the driving power receiving unit 52, the power from the driving power transmission unit 46 is changed to the driving power receiving unit 52 and the switching unit. It is supplied to the circuit system 50 via 122.

  In step S <b> 12, power necessary for driving the medical device 14 and / or the circuit system 50 of the portable information terminal 22 is supplied and the circuit system 50 is driven again, so that the medical device 14 and / or the portable information terminal 22 Use (continuous use) becomes possible. At this time, while looking at the power generation amount and the power transmission amount displayed on the display unit 17 of the console 16, if necessary, the generator 66 is driven or the commercial power source 72 is used to connect the mobile power supply vehicle 10. Electric power is supplied and accumulated so that the amount of power entering the mobile power source vehicle 10 and the amount of power leaving the mobile power source vehicle 10 are balanced.

  In step S13, when the use of the medical device 14 and the portable information terminal 22 is finished, the medical device 14 and the portable information terminal 22 are accommodated in the case 20, and further, the case 20 is accommodated in the case accommodating portion 34 of the carriage 12. .

  In step S14, if the work by the mobile power source vehicle 10 has not been completed, the process returns to the processes in and after step S2, and the process of the mobile power source vehicle 10 is completed at the stage where the work has been completed.

  As described above, the mobile power supply vehicle 10 according to the present embodiment can carry a plurality of types of medical devices 14 to a victim such as a disaster-stricken area at the same time. In addition to radiography, an electrocardiogram or an ultrasonic wave When it is necessary to perform diagnosis or the like, it is possible to respond quickly.

  The battery 54 (58) of the plurality of types of medical devices 14 and the portable information terminal 22 can be charged while moving or stopped, and the medical device 14 can be quickly reached when it arrives at the victim or the like. Can be used for inspection and diagnosis. Further, for example, when a plurality of cases 20 containing the radiation imaging apparatus 24 are accommodated, first, the first radiation imaging apparatus 24 is used, and the remaining amount of the battery of the radiation imaging apparatus 24 is reduced to one time. It is also possible to take out the second radiation imaging apparatus 24 and resume the imaging at the stage where the imaging of the above cannot be performed.

  During the examination and diagnosis using the medical device 14, even after the remaining battery level is low and cannot be used, the power supply to the circuit system 50 of the medical device 14 and the portable information terminal 22 or the battery 54 (58) Can be charged and can be used continuously. In addition, it is possible to cope with re-imaging of radiography and additional imaging.

  By installing the portable information terminal 22 for each medical device 14, the measurement information by the medical device 14 can be displayed on the display screen of the portable information terminal 22, and diagnosis can be performed on the spot. In addition, each measurement information such as radiation image information, electrocardiogram information, blood pressure information, etc. can be transferred to a medical institution along with the victim's name, location information, damage status, etc. The detailed diagnosis can be performed at a medical institution (service center), and advice to doctors at the site can be quickly provided.

  By using the transformer 68 as the power supply source 40, it is possible to use the commercial power source of the hospital and the home power source of the home patient, and supply power to each battery 54 (58) at each round of visit. Can do.

  By using the generator 66 and the storage battery 70 as the power supply source 40, it is possible to realize medical activities outdoors such as without a commercial power source. In particular, using the generator 66 enables long-term medical treatment outdoors. Activities can be realized.

  In the above-described example, the case 20 in which the medical device 14 and the portable information terminal 22 are accommodated is placed in the case accommodating portion 34 of the carriage 12, and the battery power transmitting portion 44 and the battery power receiving portion 48 are connected by wire or wirelessly. Although charging to the battery 54 (58) of the medical device 14 and the portable information terminal 22 is automatically started at the connected stage, the following modes can also be preferably adopted.

(1) The case 20 is placed in the case housing portion 34 of the carriage 12 and the battery 54 (58) is immediately charged even if the battery power transmission unit 44 and the battery power reception unit 48 are connected by wire or wirelessly. The charging of only the battery 54 (58) of the medical device 14 (and the portable information terminal 22) accommodated in the case 20 selected by the operator may be started without starting. As this selection operation, for example, a diagram schematically showing the case housing portion 34 on which the case 20 is placed is displayed on the display unit 17 of the console 16. For example, the schematic diagram of the case 20 in which the device 14 (and the portable information terminal 22) is accommodated is indicated on the touch panel, or the mouse pointer is positioned and left-clicked, for example. For example, the selected case 20 may be displayed in red so that it can be distinguished from other cases 20 (for example, green display) at a glance.

(2) The case 20 is placed in the case housing part 34 of the carriage 12 and the battery 54 (58) is immediately charged even if the battery power transmission part 44 and the battery power reception part 48 are connected by wire or wirelessly. The mobile power supply vehicle 10 arrives at the disaster-stricken area or the like without confirming the damage status, and after confirming the damage status of the victim, the medical device 14 to be used by the operator is selected, and the selected medical device 14 is displayed on the console 16. The charging of the selected medical device 14 (and the portable information terminal 22) to the battery 54 (58) may be started at the stage when the information regarding is input. In this case, in the memory 224 of the console 16, an information table in which information on the medical device 14 accommodated in the case 20 placed in the case accommodation unit 34 is associated with position information on the case 20 on the case accommodation unit 34. Is stored, the battery power transmission unit 44 is specified based on this information table, and charging is started. Also in this case, as in (1), a diagram schematically showing the case housing portion 34 on which the case 20 is placed is displayed on the display portion 17 of the console 16, and the medical device 14 (and the mobile phone) in which charging has started. A schematic diagram of the case 20 in which the information terminal 22) is accommodated may be displayed in red, for example, so that it can be distinguished from other cases 20 at a glance.

  In the above-described aspects (1) and (2), the following charging method can also be preferably used.

(A) The battery 54 of the medical device 14 is usually hardly charged, and what is used for the purpose of use (for example, how many radiographic images are taken in radiography) If it is an electrocardiograph, input how many ECGs to measure, etc.), and charge at least that much power.

(B) Each medical device 14 is charged with a predetermined amount of power (for example, if the radiography device 24 is used, the power required for one person's imaging, if the electrocardiograph is one person The power required to measure the ECG of the minute), what purpose to use when using it (for example, how many radiographic images are taken for radiography, and if it is an electrocardiograph) If there is not enough charging power for the power used according to the purpose (usage power), at least the difference power is charged.

  By adopting any of the above-described aspects (1), (2), (a) and (b), various medical devices 14 are brought into the field such as a disaster area where it is unknown what is present. Even if there is a bias in the use of one or more types of medical devices 14, the power from the power supply source 40 can be interchanged, thereby improving the efficiency of power use and in the field such as the disaster area. The various medical devices 14 can be used for a long time.

  Note that the mobile power supply vehicle and the power supply method according to the present invention are not limited to the above-described embodiments, and various configurations can be adopted without departing from the gist of the present invention.

  That is, in the mobile power supply vehicle 10 described above, the installation of the drive power transmission unit 46 and the drive power control unit 64 to the carriage 12 is omitted, and the drive power reception unit 52 and the switching unit to the medical device 14 and the portable information terminal 22 are omitted. The installation of 122 may be omitted.

  Also in this case, for example, when a plurality of cases 20 containing the radiation imaging apparatus 24 are accommodated, first, the first radiation imaging apparatus 24 is used, and the remaining battery level of the radiation imaging apparatus 24 decreases. At this stage, it is possible to take out the second radiation imaging apparatus 24 and resume the imaging at the stage when the imaging for one time cannot be performed.

  Moreover, since the circuit configuration is simplified, the mobile power supply vehicle 10 can be downsized.

  Alternatively, in the mobile power supply vehicle 10 described above, the installation of the battery power transmission unit 44 and the battery power control unit 62 in the carriage 12 is omitted, and the battery power reception unit 48 and the switching unit in the medical device 14 and the portable information terminal 22 are omitted. The installation of 122 may be omitted.

  In this case, since the installation of the battery 54 (58) to the medical device 14 and the portable information terminal 22 can be omitted, it is possible to reduce the weight of the case 20 and thus the mobile power supply vehicle 10. Moreover, since the circuit configuration is simplified, the mobile power supply vehicle 10 can be downsized.

  For example, in the above-described example, the photoelectric conversion layer 138 that is one of the constituent elements of the radiation detector 118 is shown as being formed of a substance such as a-Si, but in addition, photoelectric conversion including an organic photoelectric conversion material is included. Layers may be used.

  Here, an example of a radiation detector using a photoelectric conversion layer containing an organic photoelectric conversion material will be described with reference to FIGS.

  As shown in FIG. 20, the radiation detector 600 includes a signal output unit 604, a sensor unit 606, and a scintillator 608 sequentially stacked on an insulating substrate 602, and the signal output unit 604 and the sensor unit 606 form a pixel. The part is composed. A plurality of pixel portions are arranged 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 is formed by forming a phosphor that emits light by converting radiation incident from above (opposite the substrate 602) into light. It is. By providing such a scintillator 608, the radiation transmitted through the subject 114 is absorbed and light is emitted.

  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 radiation, and has an emission spectrum of 420 nm to 600 nm at the time of X-ray irradiation. It is particularly preferable to use CsI (Ti) (cesium iodide added with titanium). Note that the emission peak wavelength of CsI (Ti) in the visible light region is 565 nm.

  The sensor unit 606 includes an upper electrode 612, a lower electrode 614, and a photoelectric conversion film 616 disposed between the upper and lower electrodes. The photoelectric conversion film 616 absorbs light emitted from the scintillator 608 and generates charges. It is composed of an organic photoelectric conversion material.

Since the upper electrode 612 needs to cause the light generated by the scintillator 608 to be incident on the photoelectric conversion film 616, it is preferable that the upper electrode 612 be formed 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 photoelectric conversion material, absorbs light emitted from the scintillator 608, and generates charges according to the absorbed light. In this way, the photoelectric conversion film 616 including an organic photoelectric conversion material has a sharp absorption spectrum in the visible range, and electromagnetic waves other than light emitted by the scintillator 608 are hardly absorbed by the photoelectric conversion film 616, and X-rays are obtained. The noise generated by the radiation such as being absorbed by the photoelectric conversion film 616 can be effectively suppressed.

  The organic photoelectric conversion material constituting the photoelectric conversion film 616 preferably has an absorption peak wavelength that is 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 photoelectric conversion material matches the emission peak wavelength of the scintillator 608, but 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 photoelectric conversion material and the emission peak wavelength with respect to the radiation of the scintillator 608 is preferably within 10 nm, and more preferably within 5 nm.

  Examples of organic photoelectric conversion materials that can satisfy such conditions include quinacridone-based organic compounds and phthalocyanine-based 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 photoelectric conversion material and CsI (Ti) is used as the material of the scintillator 608, the difference between the peak wavelengths can be within 5 nm. Thus, the amount of charge generated in the photoelectric conversion film 616 can be substantially maximized.

  Next, the photoelectric conversion film 616 applicable to the above-described radiation detector 600 will be specifically described.

  The electromagnetic wave absorption / photoelectric conversion site in the radiation detector 600 can be configured by an organic layer including a pair of electrodes 612 and 614 and a photoelectric conversion film 616 sandwiched between the electrodes 612 and 614. More specifically, this organic layer is 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 preventing part, an electrode, and an interlayer contact improvement. It can be formed by stacking or mixing parts.

  The organic layer preferably contains an organic p-type compound or an organic n-type compound.

  The organic p-type semiconductor (compound) is a donor organic semiconductor (compound) mainly represented 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 (compound) is an acceptor organic semiconductor (compound) mainly represented 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.

  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. Those 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 are 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 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 surely exhibit the dark current suppressing effect and prevent a decrease in photoelectric conversion efficiency of the sensor unit 606. Is from 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 that the Ea is equal to or larger than the electron affinity (Ea) of the material of the adjacent photoelectric conversion film 4. 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.

  A signal output unit 604 is formed on the surface of the substrate 602 below the lower electrode 614 of each pixel unit. FIG. 21 schematically shows the configuration of the signal output unit 604.

  The signal output unit 604 corresponds to the lower electrode 614, a capacitor 622 that accumulates charges transferred to the lower electrode 614, and a field effect thin film transistor (Thin Film) that converts the charges accumulated in the capacitor 622 into an electric signal and outputs the electric signal. Transistor, hereinafter referred to simply as a thin film transistor) 624 is formed. The region where the capacitor 622 and the thin film transistor 624 are formed has a portion that overlaps with the lower electrode 614 in a 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. In order to minimize the plane area of the radiation detector 600 (pixel portion), it is desirable that the region where the capacitor 622 and the thin film transistor 624 are formed is completely covered with the lower electrode 614.

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

In the thin film transistor 624, as shown in FIG. 21, a gate electrode 628, a gate insulating film 630, and an active layer (channel layer) 632 are stacked. It is formed by opening. In the radiation detector 600, the active layer 632 is formed of an amorphous oxide. As the amorphous oxide constituting the active layer 632, an oxide containing at least one of In, Ga, and Zn (for example, In—O-based) is preferable, and at least two of In, Ga, and Zn are used. An oxide containing In (for example, In—Zn—O, In—Ga, or Ga—Zn—O) is more preferable, and an oxide containing In, Ga, and Zn is 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 less than 6) is preferable, and InGaZnO is particularly preferable. ₄ is more preferable.

  If the active layer 632 of the thin film transistor 624 is formed of an amorphous oxide, it does not absorb radiation such as X-rays, or even if it is absorbed, it remains extremely small. It can be effectively suppressed.

  Here, any of the amorphous oxide constituting the active layer 632 of the thin film transistor 624 and the organic photoelectric conversion material constituting the photoelectric conversion film 616 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 materials such as polyesters such as polyethylene terephthalate, polybutylene phthalate, and polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, and poly (chlorotrifluoroethylene). A conductive substrate 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 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 break. In addition, aramid can form a substrate thinner than a glass substrate or the like. Note that the substrate 602 may be formed by stacking an ultrathin glass substrate and an aramid.

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

  In the radiation detector 600, the photoelectric conversion film 616 is made of an organic photoelectric conversion material, and radiation is hardly absorbed by the photoelectric conversion film 616. For this reason, the radiation detector 600 described above can suppress a decrease in sensitivity to the radiation X because the amount of radiation absorbed by the photoelectric conversion film 616 is small even when the radiation passes through the TFT substrate 638 by backside illumination. In backside illumination, radiation passes through the TFT substrate 638 and reaches the scintillator 608. Thus, when the photoelectric conversion film 616 of the TFT substrate 638 is made of an organic photoelectric conversion material, the radiation of the photoelectric conversion film 616 is reduced. Since there is almost no absorption and radiation attenuation can be suppressed to a low level, it is suitable for backside illumination.

  In addition, the amorphous oxide that forms the active layer 632 of the thin film transistor 624 and the organic photoelectric conversion material that forms the photoelectric conversion film 616 can be formed at a low temperature. Therefore, the substrate 602 can be formed using a plastic resin, aramid, or bionanofiber that absorbs little radiation. Since the substrate 602 formed in this manner has a small amount of radiation absorption, a decrease in sensitivity to the radiation X can be suppressed even when the radiation is transmitted through the TFT substrate 638 by backside illumination.

DESCRIPTION OF SYMBOLS 10 ... Mobile power supply car 12 ... Carriage 14 ... Medical equipment 16 ... Console 20 ... Case 22 ... Portable information terminal 24 ... Radiography apparatus 26 ... Cassette body 28 ... Radiation source body 30 ... Wheel 32 ... Handle 34 ... Case housing part DESCRIPTION OF SYMBOLS 40 ... Power supply source 42 ... Power divider 44 ... Battery power transmission part 46 ... Drive power transmission part 48 ... Battery power reception part 50 ... Circuit system 52 ... Drive power reception part 54, 58 ... Battery 56, 60 ... Battery terminal 62 ... Battery power control unit 64 ... Driving power control unit 66 ... Generator 68 ... Transformer 70 ... Storage battery 72 ... Commercial power supply 74 ... Cable 118 ... Radiation detector 124 ... Cassette control unit 200 ... Remaining amount detection unit 202 ... No. DESCRIPTION OF SYMBOLS 1 Transmission part 204 ... RFID reader 206 ... 2nd transmission part 208 ... 3rd transmission part 210 ... Transceiver 212 ... 1st discrimination | determination part 214 ... 2nd discrimination | determination part 216 ... 1st electric power information acquisition part 218 ... 2nd electric power information acquisition part 220 ... 1st electric power transmission stop part 222 ... 2nd electric power transmission stop part 224 ... Memory 226 ... Empty port extraction part

Claims (17)

A movable carriage,
A plurality of medical devices that are detachable from the carriage and have different functions;
A power supply source installed on the carriage;
A power distributor for distributing power from the power supply;
A mobile power supply vehicle, comprising: a plurality of power transmission units installed on the carriage and transmitting the distributed power toward the corresponding medical device. The mobile power supply vehicle according to claim 1,
A mobile power supply vehicle, comprising: a power receiving unit that is installed corresponding to the plurality of medical devices, receives power transmitted from the corresponding power transmitting unit, and supplies power to the corresponding medical device. The mobile power supply vehicle according to claim 2,
The power transmission unit transmits power necessary for charging the battery of the corresponding medical device,
The power receiving unit receives the power transmitted from the corresponding power transmitting unit and supplies the power to the battery. The mobile power supply vehicle according to claim 3,
A plurality of the power transmission units are installed in the cart corresponding to the plurality of medical devices,
When the medical device is accommodated in the cart, power is transmitted from the power transmission unit to the power reception unit that is wired or wirelessly connected to the power reception unit among the plurality of power transmission units. And moving power car. The mobile power supply vehicle according to claim 4,
And a plurality of power control units installed corresponding to the power transmission units,
Among the plurality of power control units, the power control unit corresponding to the power transmission unit wired or wirelessly connected to the power reception unit corresponds to the power reception unit with the power distributed by the power distributor. A mobile power supply vehicle, characterized in that it is converted into electric power necessary for charging a battery of the medical device and supplied to the power transmission unit. The mobile power supply vehicle according to claim 2,
The power transmission unit transmits power necessary to drive the circuit system of the corresponding medical device,
The power receiving unit receives the power transmitted from the corresponding power transmitting unit and supplies the power to the circuit system. The mobile power supply vehicle according to claim 6,
And a plurality of power control units installed corresponding to the power transmission units,
Among the plurality of power control units, the power control unit corresponding to the power transmission unit wired or wirelessly connected to the power reception unit corresponds to the power reception unit with the power distributed by the power distributor. A mobile power supply vehicle, characterized in that it is converted into electric power necessary for driving the circuit system of the medical device and supplied to the power transmission unit. The mobile power supply vehicle according to claim 2,
The power transmission unit
A battery power transmission unit that transmits power necessary for charging the battery of the corresponding medical device, and a drive power transmission unit that transmits power necessary to drive the circuit system of the corresponding medical device,
The power receiving unit
Receiving the power transmitted from the corresponding power transmission unit and supplying the battery to the battery; and receiving the power transmitted from the corresponding power transmission unit and supplying the power to the circuit system of the medical device And a power receiving vehicle for driving. The mobile power supply vehicle according to claim 8,
Furthermore, it has a case in which the medical device is accommodated,
A plurality of the battery power transmission units are installed in the case housing unit in which the case is accommodated corresponding to the plurality of medical devices,
The battery power receiving unit is installed in the case,
A plurality of the drive power transmission units are installed on the carriage,
The driving power receiving unit is installed in the medical device, respectively. The mobile power supply vehicle according to claim 9, wherein
When the case in which the medical device is accommodated is accommodated in the case accommodating portion, among the plurality of battery power transmitting portions, the battery for the battery that is wired or wirelessly connected to the battery power receiving portion of the case A mobile power supply vehicle in which power is transmitted from a power transmission unit to the battery power reception unit. The mobile power supply vehicle according to claim 10, wherein
Furthermore, it has a plurality of battery power control units installed corresponding to the battery power transmission unit,
Of the plurality of battery power control units, the battery power control unit corresponding to the battery power transmission unit wired or wirelessly connected to the power receiving unit of the case is distributed by the power distributor. A mobile power supply vehicle, wherein electric power is converted into electric power necessary for charging a battery of the medical device housed in the case and supplied to the battery power transmission unit. The mobile power supply vehicle according to claim 9, wherein
Among the medical devices that are taken out from the case and are in use, the medical device that is wired or wirelessly connected to the drive power transmission unit is connected from the drive power transmission unit to the drive power reception unit of the medical device. A mobile power supply vehicle that transmits electric power. The mobile power vehicle according to claim 12,
Furthermore, it has a plurality of drive power control units installed corresponding to the drive power transmission unit,
Of the plurality of driving power control units, the driving power control unit corresponding to the driving power transmission unit wired or wirelessly connected to the driving power receiving unit is the power distributed by the power distributor Is converted into electric power necessary for driving the circuit system of the medical device corresponding to the driving power receiving unit, and is supplied to the driving power transmission unit. The mobile power supply vehicle according to claim 2,
A mobile power supply vehicle having a plurality of portable information terminals corresponding to the plurality of medical devices. The mobile power vehicle according to claim 14,
The power receiving unit is installed corresponding to the medical device and the portable information terminal, receives power transmitted from the corresponding power transmission unit, and supplies power to the corresponding medical device and portable information terminal. Features a mobile power supply car. The mobile power supply vehicle according to claim 1,
The power supply vehicle according to claim 1, wherein the power supply source is at least one of a generator, a transformer, and a storage battery. Distributes the electric power from the power supply source corresponding to a plurality of medical devices each having a different function housed in a movable carriage,
Transmit the distributed power to the corresponding medical devices via multiple power transmission units,
A power supply method characterized by receiving the power transmitted from the plurality of power transmission units at a power reception unit installed corresponding to each of the medical devices and supplying the power to the corresponding medical devices.

Images