JP2014055960A - Image acquisition system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To easily supply power to a radiation detecting device and to acquire a radiation image of high quality.SOLUTION: An electronic cassette 24 mounted to a radiation image capturing system 10 comprises: a radiation detecting device 40 for detecting radiation X emitted from an image capturing apparatus 22 and transmitted through a patient 14; a contactless power reception part 49 for receiving electric power supplied by non-contact from a power feeder 25 and supplying the electric power to a battery 44; an A/D converter 70 for performing A/D conversion to convert radiation image information generated due to the radiation X applied to the radiation detecting device 40; an end-of-A/D conversion determining part 107 for determining whether the A/D conversion is finished; and a charging controller 108 for stopping the power feeder 25 from supplying electric power by non-contact after the image capturing apparatus 22 has started capturing images until the end-of-A/D conversion determining part 107 determines that the A/D conversion is finished.

Description

  The present invention relates to a radiation detection apparatus including a radiation detector that detects radiation transmitted through a subject and a non-contact power receiving unit, and a radiographic imaging system including a non-contact power supply apparatus that performs non-contact power supply to the radiation detection apparatus. And a radiographic imaging method.

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

  On the other hand, in an operating room or the like, it is necessary to immediately read out and display a radiation image from a radiation conversion panel after imaging in order to perform a quick and accurate treatment on a patient. Similarly, rapid imaging is also required for imaging of infants, children, elderly people, and patients who cannot stand for a long time due to illness or injury. Radiation detection using a solid-state detector that converts radiation directly into electrical signals, or converts radiation into visible light with a scintillator and then converts it into electrical signals to read out as a radiation conversion panel that can meet such demands A vessel has been developed.

  For example, Patent Document 1 describes a radiation detection apparatus (electronic cassette) having a function of transmitting radiation image information obtained by a radiation detector to an image processing unit or the like by a wireless transmission system. The electronic cassette has a built-in battery. When charging the battery, the electronic cassette is mounted on a separately provided cradle, and is contactless (wireless) by a non-contact charging device built in the cradle. Charging can be performed.

JP 2008-170315 A

  By the way, in the above-described conventional technology, for example, when the remaining battery level is insufficient due to intermittently performing multiple imaging during one operation, the electronic cassette installed in the patient is moved to the cradle and charged. Need to do. For this reason, it takes a lot of time for charging, and there is a possibility of causing a longer operation time and an increased burden on the patient.

  On the other hand, when non-contact power feeding is performed, for example, during A / D conversion of radiation image information obtained by a radiation detector built in the electronic cassette during surgery, the magnetic flux used for the non-contact power feeding The noise resulting from the above may have a great influence on the captured image, particularly the analog signal before conversion, and it may be difficult to acquire a high-quality radiation image.

  The present invention has been made in consideration of the above-described conventional problems, and can easily supply power to the radiation detection apparatus and can acquire a high-quality radiation image. An object is to provide an image capturing system and a radiographic image capturing method.

  A radiation detection device according to the present invention receives a radiation detector that detects radiation irradiated from an external imaging device and transmitted through a subject, and power supplied in a non-contact manner from an external non-contact power supply device, and a power supply unit A non-contact power receiving unit that supplies power to the radiation detector, an A / D converter that performs A / D conversion on radiation image information of the radiation applied to the radiation detector, and whether or not the A / D conversion is complete A non-contact power feeding from the non-contact power feeding device between an A / D conversion end judging unit for judging and an end of the A / D conversion by the A / D conversion end judging unit from a photographing start by the photographing device And a charge control unit that stops the operation.

  In addition, the radiographic imaging system according to the present invention includes an imaging device that irradiates a subject with radiation, a radiation detector that detects radiation transmitted through the subject, and radiographic image information based on the radiation applied to the radiation detector. An A / D converter that performs A / D conversion, a radiation detection device that includes a power supply unit that supplies power to the radiation detector, and non-contact power reception that is provided in the radiation detection device and supplies power to the power supply unit A radiographic imaging system comprising: a non-contact power supply device that supplies power to a unit in a non-contact manner; and the imaging device, the radiation detection device, and a control device that controls driving of the non-contact power supply device. An A / D conversion end determination unit that determines whether or not the A / D conversion has ended, and the A / D conversion by the A / D conversion end determination unit from the start of shooting by the shooting apparatus Until determination of conversion of termination, characterized in that the charging control unit is provided to stop the non-contact power supply from the non-contact power feeding device.

  According to such a configuration, a radiation detection apparatus having a radiation detector for detecting radiation, for example, an electronic cassette is placed at a predetermined imaging position, and power is supplied to the radiation detection apparatus by the non-contact power supply apparatus. Therefore, the power feeding operation can be further facilitated. In addition, an A / D conversion end determination unit and a charge control unit are provided, and the non-contact power supply from the non-contact power supply device to the non-contact power reception unit is stopped from the start of imaging until the end of A / D conversion. Therefore, since non-contact power feeding is prohibited at least from the start of imaging until the conversion of radiation image information detected by the radiation detector into a digital signal is completed, radiation with analog signals that are particularly susceptible to noise It is possible to prevent the noise caused by the non-contact power transmission from the non-contact power feeding apparatus from affecting the image information, and to acquire a high-quality radiation image. Furthermore, since power supply can be started quickly after the A / D conversion, which is relatively less susceptible to the influence of the noise, for example, when the remaining power of a battery or the like used for shooting is greatly reduced. Even if it exists, it can charge rapidly after completion | finish of imaging | photography and can prepare for the next imaging | photography.

  In addition, in order to reliably stop the non-contact power feeding from the non-contact power feeding device to the non-contact power receiving unit between the start of photographing and the end of A / D conversion, the charging control unit starts photographing by the photographing device. Before, when a power supply prohibition signal for prohibiting contactless power supply from the contactless power supply device is generated, or when it is determined by the A / D conversion end determination unit that A / D conversion has ended, contactless power supply You may generate the electric power feeding permission signal which permits non-contact electric power feeding from an apparatus.

  In this case, the image processing apparatus further includes an image memory in which the radiation image information converted into a digital signal by the A / D converter is stored, and the A / D conversion end determination unit includes the radiation converted into the digital signal. If it is determined that the A / D conversion is completed when image information is stored in the image memory, it is possible to effectively avoid being affected by the noise during data transfer to the image memory. It is possible to prevent garbled data or the like and obtain a higher quality radiographic image.

  Further, when the power supply prohibition signal is generated from the charge control unit, the non-contact power supply prohibition control during photographing is more reliably provided with a photographing control unit that generates a photographing permission signal for permitting photographing by the photographing device. Can be executed.

  The radiographic imaging system is connected to an information management system that stores a desired number of imaging times of the subject, and the A / D conversion end determination unit is equivalent to the number of imaging times stored in the information management system. If the A / D conversion end determination is performed after the imaging is completed, all the imaging is completed and it is surely waited for the A / D conversion of the obtained radiation image information to be completed. After that, it is possible to start non-contact power feeding.

  Further, the charging control unit is configured to generate the power supply permission signal when it is determined that the irradiation of the radiation from the imaging apparatus is stopped and the A / D conversion is completed. For example, even when information on the desired number of times of imaging cannot be obtained from the network or the like, it is possible to estimate the end of the desired number of times of imaging by stopping radiation irradiation, for example, by turning off the imaging switch. It is possible to start non-contact power supply after reliably waiting for the completion of imaging and A / D conversion of the obtained radiographic image information.

  Furthermore, when the charging control unit is configured to generate the power supply permission signal after a predetermined time has elapsed after it is determined that the A / D conversion has ended, the A / D conversion is reliably performed. It is possible to guarantee the time for completion of data transfer and further transfer of the radio signal information of the digital signal after conversion to the image memory, and effectively avoid the influence of the noise on the transferred data and the like. be able to.

  Still further, when the charging control unit is configured to generate the power supply permission signal after a predetermined time has elapsed after the irradiation of radiation from the imaging apparatus is started, the charging control unit performs A / A from the start of irradiation of radiation. It is possible to generate a power supply permission signal while ensuring time for completion of D conversion and further data transfer to the image memory. In this case, the A / D conversion end determination unit may determine that A / D conversion has ended in consideration of a predetermined time from the start of radiation irradiation, that is, the function of the A / D conversion end determination unit. Can be configured to be integrated into the charge control unit.

  The radiographic imaging method according to the present invention is a radiographic imaging method of irradiating a subject with radiation, detecting the radiation with a radiation detector mounted on a radiation detection device, converting the radiation into radiation image information, and obtaining a desired radiation image. The power supply to the power supply unit of the radiation detection apparatus is supplied in a non-contact manner, and after the start of radiographic imaging, at least until the A / D conversion of the radiation image information detected by the radiation detector is completed. During the period, the non-contact power supply is stopped.

  According to such a method, at least the end of A / D conversion of the acquired radiation image information is waited for, and noise generated due to the power supplied in a non-contact manner from the non-contact power feeding device is started by starting the power supply in a non-contact manner. Can prevent a photographed image from being affected, and a high-quality radiation image can be obtained.

  According to the present invention, since the radiation detection apparatus having the radiation detector can be supplied to the radiation detection apparatus by the non-contact power supply apparatus in a state where the radiation detection apparatus is disposed at the predetermined imaging position, the power supply operation is further facilitated. Can be. Furthermore, an A / D conversion end determination unit and a charge control unit are provided, and non-contact power supply from the non-contact power supply device to the non-contact power reception unit is stopped from the start of imaging until the end of A / D conversion. Therefore, since non-contact power feeding is prohibited at least from the start of imaging until the conversion of radiation image information detected by the radiation detector into a digital signal is completed, radiation with analog signals that are particularly susceptible to noise It is possible to prevent the noise caused by the non-contact power transmission from the non-contact power feeding apparatus from affecting the image information, and to acquire a high-quality radiation image.

It is explanatory drawing of the operating room where the radiographic imaging system which concerns on the 1st Embodiment of this invention was installed. It is a partially cutaway perspective explanatory view of the electronic cassette shown in FIG. It is a circuit block diagram of the radiation detector of FIG. It is block explanatory drawing of the radiographic imaging system shown in FIG. FIG. 5 is a block explanatory diagram of an imaging system that more specifically shows the configuration of the electronic cassette shown in FIG. 4. It is a flowchart which shows an example of the imaging | photography procedure of the radiographic imaging system shown in FIG. It is a block explanatory view of the radiographic imaging system concerning a 2nd embodiment of the present invention. It is a flowchart which shows the 1st imaging | photography procedure of the radiographic imaging system shown in FIG. It is a flowchart which shows the 2nd imaging | photography procedure of the radiographic imaging system shown in FIG. It is a flowchart which shows the 3rd imaging | photography procedure of the radiographic imaging system shown in FIG. It is block explanatory drawing of the radiographic imaging system which concerns on the 1st modification of the radiographic imaging system shown in FIG. It is another block diagram of an electronic cassette. It is a block diagram of the cradle which charges an electronic cassette. It is explanatory drawing of the radiographic imaging system which concerns on the 2nd modification of the radiographic imaging system shown in FIG. It is explanatory drawing of the radiographic imaging system which concerns on the 3rd modification of the radiographic imaging system shown in FIG. It is explanatory drawing of the radiographic imaging system which concerns on the 4th modification of the radiographic imaging system shown in FIG. It is explanatory drawing of the radiographic imaging system which concerns on the 5th modification of the radiographic imaging system shown in FIG.

  DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, a radiographic imaging system and a radiographic imaging method according to the present invention will be described in detail with reference to the accompanying drawings by giving preferred embodiments in relation to a radiation detection apparatus used in the system.

  As shown in FIG. 1, the operating room 12 in which the radiographic image capturing system 10 (hereinafter also referred to as “imaging system 10”) according to the first embodiment of the present invention is installed is a bed on which a patient 14 lies. A certain operating table 16 and an instrument table 20 on which various instruments used by the doctor 18 for surgery are placed. Around the operating table 16, various devices necessary for the operation such as an anesthesia machine, an aspirator, an electrocardiograph, and a blood pressure monitor (not shown) are arranged.

  The imaging system 10 includes an imaging device (radiation irradiation device) 22 that irradiates a patient 14 as a subject with a dose of radiation X according to imaging conditions, and a radiation detector 40 that detects the radiation X transmitted through the patient 14 (FIG. 2). The electronic cassette 24, which is a radiation detection device with a built-in reference), and a power supply device that supplies power wirelessly (non-contact) to the battery 44 (see FIG. 2) built in the electronic cassette 24 (non-contact power supply device, wireless) A power supply device) 25, a display device 26 that displays a radiation image based on the radiation X detected by the radiation detector 40, and a console (control device) 28 that comprehensively controls the imaging system 10. In the imaging system 10, signals can be transmitted and received between the imaging device 22, the electronic cassette 24, the power feeding device 25, the display device 26, and the console 28 by wireless communication using, for example, UWB (Ultra Wide Band).

  Further, since the power supply device 25 and the electronic cassette 24 are in a non-contact state, as described above, the power supply method from the power supply device 25 to the electronic cassette 24 (the battery 44) is non-contact (wireless). ) Adopts a non-contact power feeding method to supply power.

  Specifically, the non-contact power feeding method includes (1) a microwave power feeding method in which power is supplied from the power feeding device 25 to the electronic cassette 24 using electromagnetic waves in a microwave band, and (2) a power feeding device 25. An electromagnetic induction method in which power is supplied by electromagnetic induction in a state in which the provided coil and the coil provided in the electronic cassette 24 are close to each other; (3) electromagnetic field resonance between the power feeding device 25 and the electronic cassette 24; There is a resonance method in which power is supplied using a phenomenon.

  In the resonance method (3) as well, the resonance frequency of the coil of the power supply device 25 and the coil of the electronic cassette 24 is made substantially the same, and the coil of the power supply device 25 on the transmission side has a high frequency power in a predetermined space in the operating room 12. On the other hand, there is a magnetic resonance method that enables reception of the high-frequency power by arranging the coil of the receiving electronic cassette 24 in the electromagnetic field.

  As the non-contact power supply (microwave power supply method, electromagnetic induction method, resonance method, magnetic resonance method) from the power supply device 25 to the electronic cassette 24, a known non-contact power supply method can be adopted.

  In the following description, unless otherwise specified, power supply from the power supply device 25 to the battery 44 of the electronic cassette 24 will be described as being performed by a magnetic resonance method which is one of non-contact power supply methods.

  The imaging device 22 is connected to a free arm 30 extending from the ceiling, can be moved to a desired position according to the imaging region of the patient 14, and can be retracted to a position that does not obstruct the operation by the doctor 18. Similarly, the power feeding device 25 is connected to the universal arm 31 and can be moved to a desired position according to the arrangement of the electronic cassette 24. The display device 26 is connected to the free arm 32 and can be moved to a position where the doctor 18 can easily confirm the displayed radiation image. The free arms 30 to 32 may be provided on a wall, a floor, a movable wagon, or the like, and the power feeding device 25 or the display device 26 may be fixed to a ceiling, a wall, a floor, or the like without using a free arm. Good. Note that the power supply device 25 is configured so that the magnetic field M (electromagnetic field generated by high-frequency power) applied to the radiation detection device (such as the electronic cassette 24) avoids the patient 14, for example, in the lateral direction of the radiation detection device (FIG. 1 and FIG. It is preferable that it is disposed below the bottom surface (see FIG. 15) or the like.

  FIG. 2 is a partially cut perspective explanatory view of the electronic cassette 24 of FIG. The electronic cassette 24 includes a box-shaped casing 34 made of a material that transmits the radiation X. In the casing 34, a grid 38 for removing scattered radiation of the radiation X by the patient 14 and a radiation detector (radiation for detecting the radiation X transmitted through the patient 14) in order from the irradiation surface 36 side where the radiation X is irradiated. Conversion panel) 40 and a lead plate 42 that absorbs backscattered radiation X are arranged in layers. The irradiation surface 36 of the casing 34 can also be configured as a grid 38.

  The electronic cassette 24 includes a battery 44 that functions as a power supply unit, a cassette control unit 46 that performs drive control of the radiation detector 40 using power from the battery 44, and information on the radiation X detected by the radiation detector 40. A transceiver 48 that wirelessly transmits and receives a signal including (radiation image information) to and from the console 28 is provided. The battery 44, the cassette control unit 46, and the transmitter / receiver 48 are preferably provided with a lead plate or the like on the irradiation surface 36 side in order to avoid damage caused by irradiation with the radiation X. Further, the electronic cassette 24 receives a magnetic field (magnetic field, magnetic flux) M that is converted from electrical energy (high frequency power) by the power feeding device 25 and applied by non-contact power feeding (wireless), and the magnetic field M is converted into electrical energy. A wireless power receiving unit (non-contact power receiving unit) 49 for re-conversion is provided.

  FIG. 3 is a circuit configuration block diagram of the radiation detector 40. The radiation detector 40 has a photoelectric conversion layer 51 made of a material such as amorphous selenium (a-Se) that senses the radiation X and generates charges on an array of thin film transistor (TFT) 52. After the generated charge is stored in the storage capacitor (storage unit) 53, the TFT 52 is sequentially turned on for each row, and the charge is read as an image signal. In FIG. 3, only the connection relationship between one pixel 50 including the photoelectric conversion layer 51 and the storage capacitor 53 and one TFT 52 is shown, and the configuration of the other pixels 50 is omitted. Amorphous selenium must be used within a predetermined temperature range because its structure changes and its function decreases at high temperatures. Therefore, it is preferable to provide means for cooling the radiation detector 40 in the electronic cassette 24.

  A gate line 54 extending parallel to the row direction and a signal line 56 extending parallel to the column direction are connected to the TFT 52 connected to each pixel 50. Each gate line 54 is connected to a line scanning drive unit 58, and each signal line 56 is connected to a multiplexer 66 constituting a reading circuit.

  Control signals Von and Voff for controlling on / off of the TFTs 52 arranged in the row direction are supplied from the line scanning drive unit 58 to the gate line 54. In this case, the line scan driving unit 58 includes a plurality of switches SW1 for switching the gate lines 54 and an address decoder 60 for outputting a selection signal for selecting one of the switches SW1. An address signal is supplied from the cassette control unit 46 to the address decoder 60.

  In addition, the charge held in the storage capacitor 53 of each pixel 50 flows out to the signal line 56 through the TFTs 52 arranged in the column direction. This charge is amplified by the amplifier 62. A multiplexer 66 is connected to the amplifier 62 via a sample and hold circuit 64. The multiplexer 66 includes a plurality of switches SW2 for switching the signal line 56, and an address decoder 68 for outputting a selection signal for selecting one of the switches SW2. An address signal is supplied from the cassette control unit 46 to the address decoder 68. An A / D converter 70 is connected to the multiplexer 66, and radiation image information converted into a digital signal by the A / D converter 70 is supplied to the cassette control unit 46.

  The TFT 52 functioning as a switching element may be realized in combination with another imaging element such as a CMOS (Complementary Metal-Oxide Semiconductor) image sensor. Furthermore, it can be replaced with a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting them with a shift pulse corresponding to a gate signal referred to as a TFT.

  FIG. 4 is a block explanatory diagram of the photographing system 10 including the photographing device 22, the electronic cassette 24, the power feeding device 25, the display device 26, and the console 28.

  The console 28 stores radiographic image information and other information handled by the radiology department in the hospital, for example, order information (ordering information) such as the number of imaging (number of imaging, number of exposure) for each patient 14, A radiology information system (RIS, information management system) 29 for comprehensively managing these pieces of information is connected. Further, a medical information system (HIS) 33 that manages medical information in the hospital in an integrated manner is connected to the RIS 29. It can also be configured as a comprehensive system in which the functions of the RIS 29 are added to the HIS 33 in an integrated manner.

  The imaging device 22 includes an imaging switch 72, a radiation source 74, a transceiver 76, and a radiation source controller 78. The transceiver 76 receives imaging conditions from the console 28 by wireless communication, and transmits an imaging completion signal and the like to the console 28. The radiation source control unit 78 drives and controls the radiation source 74 based on the imaging start signal supplied from the imaging switch 72 and the imaging conditions supplied from the console 28. The radiation source 74 outputs the radiation X based on the control from the radiation source control unit 78.

  The power supply apparatus 25 receives a power supply start signal and the like from the console 28 by wireless communication with a power supply 80 connected to an external power supply or the like (not shown), while the console 28 receives ID information (identification data) of the power supply apparatus 25 and the like. Is supplied from the console 28, the LC resonator (power transmission unit) 84 that converts the electric energy from the power source 80 into the magnetic field M and transmits the electric energy to the electronic cassette 24 in a contactless (wireless) manner, and the console 28. And a power supply control unit 86 for driving and controlling the LC resonator 84 based on the power supply start signal.

  FIG. 5 is a block explanatory diagram of the imaging system 10 more specifically showing the configuration of the electronic cassette 24 as the radiation detection apparatus according to the present embodiment.

  As shown in FIGS. 4 and 5, the electronic cassette 24 includes a radiation detector 40, a battery 44, a wireless power receiving unit 49, a cassette control unit 46, and a transceiver 48.

  The battery 44 is configured by a rechargeable secondary battery such as a lithium ion battery, and is a power source that supplies power to each part of the electronic cassette 24 such as the radiation detector 40, the cassette control unit 46, and the transceiver 48. In addition to the secondary battery, for example, a storage element such as an electric double layer capacitor can be used as the battery 44. In short, the battery 44 can be charged and functions appropriately as a power source for the electronic cassette 24. That's fine.

  The wireless power receiving unit 49 has a function of receiving power supplied from the power supply device 25 in a contactless (wireless) manner and supplying (charging) the battery 44. The wireless power receiving unit 49 receives the magnetic field M applied from the LC resonator 84 of the power feeding device 25 and reconverts it into electric energy (high frequency power), and the electricity reconverted by the LC resonator 88. And a charging circuit 90 that converts energy into desired power and supplies it to the battery 44. The LC resonator 88 includes an LC resonance circuit having a coil and a capacitor. The charging circuit 90 rectifies the current generated by the LC resonator 88 and charges the battery 44 with a predetermined constant current, for example.

  Further, the wireless power receiving unit 49 is arranged in parallel with the LC resonator 88 and detects the detection LC resonator 94 smaller than the LC resonator 88 and the electric energy reconverted by the detection LC resonator 94. An energy detection unit 96 is provided. The detection LC resonator 94 is also composed of an LC resonance circuit having a coil and a capacitor, like the LC resonator 88. In addition, the energy detection unit 96 detects that the electronic cassette 24 is within the power supplyable area of the power supply device 25 by detecting the electrical energy, and transmits a power supply area detection signal to the cassette control unit 46. .

  As described above, for the electronic cassette 24 from the power supply device 25, the resonance (magnetic resonance) of the magnetic field M from the LC resonator 84 configured by an LC resonance circuit having a coil and a capacitor to the LC resonator 88 is used. Therefore, it is possible to perform non-contact (wireless) power supply (charging) using a known power transmission technique.

  As shown in FIG. 5, the cassette control unit 46 includes an address signal generation unit 98, an image memory 100, an operation management unit 102, a cassette ID memory 104, and a data management unit 106. The address signal generator 98 supplies an address signal to the address decoder 60 of the line scan driver 58 and the address decoder 68 of the multiplexer 66 that constitute the radiation detector 40. The image memory 100 stores radiation image information detected by the radiation detector 40. That is, the image memory 100 stores radiation image information that is irradiated to the radiation detector 40 and accumulated as signal charges, and then read and converted into digital signals.

  The operation management unit 102 controls driving of the wireless power receiving unit 49 and the battery 44, and also controls driving of the entire electronic cassette 24. Further, the operation management unit 102 is provided with an A / D conversion end determination unit 107, a charging control unit 108, and a photographing control unit 109.

  The A / D conversion end determination unit 107 determines whether or not A / D conversion of the radiation image information by the A / D converter 70 has ended. The charge control unit 108 generates a signal (power supply prohibition signal, charge prohibition signal) for prohibiting power supply (charging) from the power supply device 25 to the electronic cassette 24 before the photographing by the photographing device 22 is started, and A / D conversion. When the end determination unit 107 determines that the A / D conversion has ended, a signal (power supply permission signal, charge permission signal) for permitting power supply (charging) from the power supply device 25 to the electronic cassette 24 is generated. Such a charging control unit 108 can also be configured as a plurality of control units (signal generation units) corresponding to the respective signals. The shooting control unit 109 generates control signals (shooting permission signal, shooting prohibition signal) and the like that allow and prohibit shooting by the shooting device 22.

  The power supply prohibition signal and the power supply permission signal issued by the charge control unit 108 and the image capture permission signal and the image capture prohibition signal issued by the imaging control unit 109 are transmitted to the console 28 via the transceiver 48. Upon reception of these signals, the console 28 prohibits (stops) or starts (restarts) control of non-contact power feeding (wireless power feeding) from the power feeding device 25, and permits (starts) control of photographing from the photographing device 22. And prohibit (stop) control. Note that a power supply prohibition (permission) signal or a photographing permission (prohibition) signal is directly transmitted from the electronic cassette 24 to the power supply device 25 without going through the console 28, for example, by the power supply control unit 86 or the radiation source control unit 78. You may comprise so that electric power feeding prohibition (start) control and imaging | photography start (prohibition) control may be performed.

  The cassette ID memory 104 stores cassette ID information for specifying the electronic cassette 24. The data management unit 106 manages ID information (identification data) for specifying the power supply device 25 corresponding to the power supply of the electronic cassette 24, a power supply area detection signal from the energy detection unit 96, and the like.

  The transceiver 48 receives the transmission request signal and the ID information of the power supply device 25 from the console 28 by wireless communication, while receiving radiographic image information, cassette ID information, a wireless power supply enable signal, a power supply prohibition signal, power supply to the console 28. A permission signal, a photographing permission signal, a photographing prohibition signal, and the like are transmitted.

  As shown in FIG. 4, the display device 26 includes a receiver 110 that receives radiation image information from the console 28, a display control unit 112 that processes the received radiation image information, and a radiation processed by the display control unit 112. And a display unit 114 that displays image information.

  The console 28 includes a transceiver 116, an imaging condition management unit 118, an image processing unit 120, an image memory 122, a patient information management unit 124, a cassette information management unit 126, and a power supply information management unit 128. Note that the console 28 may be installed outside the operating room 12 as long as signals can be reliably transmitted to and received from the imaging device 22, the electronic cassette 24, the power supply device 25, and the display device 26.

  The transmitter / receiver 116 needs to include radiation image information, a power supply prohibition (permission) signal, and an imaging permission (prohibition) signal between the console 28 and the imaging device 22, the electronic cassette 24, the power supply device 25, and the display device 26. Such information is transmitted and received by wireless communication. The shooting condition management unit 118 manages shooting conditions necessary for shooting by the shooting device 22, and further, shooting start control and shooting prohibition control of the shooting device 22 based on a shooting permission signal and a shooting prohibition signal from the shooting control unit 109. I do. The image processing unit 120 performs predetermined image processing on the radiation image information received from the electronic cassette 24. The image memory 122 stores the radiation image information processed by the image processing unit 120. The patient information management unit 124 manages patient information of the patient 14 to be imaged. The cassette information management unit 126 manages the cassette information including the wireless power feed enable signal and the cassette ID information received from the electronic cassette 24. The power supply information management unit 128 performs operation control of the power supply device 25, management of ID information transmitted from the power supply device 25, and the like, and also a power supply device based on a power supply prohibition signal and a power supply permission signal from the charge control unit 108. 25, power supply prohibition control and power supply start control (power supply resumption control) are performed.

  The imaging conditions are conditions for determining a tube voltage, a tube current, an irradiation time, and the like for irradiating radiation X having an appropriate dose to an imaging region of the patient 14. Conditions such as a photographing method can be given. Furthermore, as imaging conditions, conditions, such as the frequency | count of imaging | photography, are mentioned as order information from RIS29, for example. The patient information is information for identifying the patient 14 such as the name, sex, and patient ID number of the patient 14. The imaging order information including these imaging conditions and patient information can be set directly on the console 28 or supplied to the console 28 from the outside via the RIS 29. Further, the cassette information includes a wireless power feedable signal from the data management unit 106 in addition to the cassette ID information for specifying the electronic cassette 24.

  The photographing system 10 according to the present embodiment is basically configured as described above, and the operation thereof will be described next with reference to the flowchart of FIG.

  The imaging system 10 is installed in the operating room 12, and is used when, for example, it is necessary to capture a radiographic image during surgery. Therefore, the patient information, the number of shots, and the like of the patient 14 to be imaged are registered in advance in the patient information management unit 124 of the console 28 prior to imaging. If the imaging region and the imaging method are determined in advance, these imaging conditions are registered in the imaging condition management unit 118 in advance. These registrations can be performed by obtaining information from the RIS 29. The operation on the patient 14 is performed in the state where the above preparation work is completed.

  First, in step S1 of FIG. 6, when taking a radiographic image during an operation, the doctor 18 or a radiographer in charge takes the patient 14 and the operating table 16 with the irradiation surface 36 facing the imaging device 22 side. The electronic cassette 24 is installed at a desired position between the two.

  Here, in conjunction with the start of operation of the console 28 or by operation of an operation start switch (not shown), the power feeding device 25 is driven under a predetermined operation condition (low output operation). Therefore, the electronic cassette 24 can detect that the electronic cassette 24 is disposed in the power supplyable area of the power supply device 25 by the detection LC resonator 94 and the energy detection unit 96 of the wireless power receiving unit 49. That is, the energy detection unit 96 functions as a power reception availability detection unit that detects whether or not the electronic cassette 24 is in an area where power can be received from the power supply device 25. At this time, the power supply control unit 86 of the power supply device 25 applies a weak magnetic field M that allows the detection LC resonator 94 and the energy detection unit 96 of the electronic cassette 24 to detect the presence or absence of the magnetic field M from the LC resonator 84. Low power operation is performed to effectively reduce power consumption.

  On the other hand, in the electronic cassette 24, a power feeding area detection signal is supplied from the energy detection unit 96 to the data management unit 106. Upon receiving the power supply area detection signal, the data management unit 106 receives the ID information of the power supply device 25 stored in the power supply information management unit 128 from the console 28, while transmitting the wireless power supply enable signal to the cassette information management unit 126 of the console 28. And send.

  The power supply area detection signal is further transmitted from the energy detection unit 96 to the operation management unit 102. Upon receiving the power feeding area detection signal, the operation management unit 102 turns on the electronic cassette 24 so that the electronic cassette 24 can be used, thereby completing the preparation for photographing. Of course, a power switch (not shown) operated by the doctor 18 or the like can be provided on the side surface of the electronic cassette 24 or the like.

  In the photographing system 10, after the preparation for photographing as described above is completed, in step S <b> 2, it is determined that the battery 44 needs to be charged under the remaining amount management of the battery 44 by the cassette control unit 46 or the cassette information management unit 126. If this is the case (NO in step S2), a power supply start signal is transmitted from the cassette information management unit 126 of the console 28 to the power supply control unit 86 of the power supply device 25. Thereby, in the imaging system 10, it is possible to perform power supply (charging) to the electronic cassette 24 at a desired power amount and timing by the power supply device 25 (step S3). In addition, when the remaining amount of the battery 44 is insufficient during the operation, the electronic cassette 24 can be appropriately charged while being placed in a predetermined photographing position. Of course, if the remaining amount of the battery 44 is insufficient even during preparation for photographing (during installation of the electronic cassette 24) or before the photographing is started, it is immediately non-contact before or after the operation is started. Charging (wireless charging) can be performed and preparation for shooting can be completed quickly.

  At the time of non-contact power supply (wireless power supply) to the electronic cassette 24, a predetermined operation condition (the magnetic field M applied from the LC resonator 84 to the electronic cassette 24 is changed to a magnetic field sufficiently stronger than the low output operation ( The power supply device 25 may be driven and controlled by high output operation and power supply operation). Further, in the electronic cassette 24, the power received by the LC resonator 94 for detection together with the LC resonator 88 can be used for charging the battery 44 from the charging circuit 90, so that the battery 44 can be charged more rapidly. .

  In the imaging system 10, the ID information of the corresponding power supply device 25 can be confirmed between the electronic cassette 24 and the power supply device 25 via the console 28 as described above. For this reason, for example, even when a plurality of power supply apparatuses are installed, it is possible to appropriately and selectively perform a power supply operation from the corresponding desired power supply apparatus to the electronic cassette 24, and wasteful power consumption, malfunction, etc. It can be avoided.

  If it is determined in step S2 that the battery 44 has a sufficient remaining amount (YES in step S2), then a power supply prohibition signal is issued from the charge control unit 108 (step S4), and photographing control is performed. A photographing permission signal is issued from the unit 109 (step S5). Therefore, under the control of the console 28 (the imaging condition management unit 118 and the power supply information management unit 128), the power supply device 25 is set in a power supply prohibition state, while the imaging device 22 is set in a shooting start standby state in which imaging can be performed. As a result, non-contact power supply (wireless power supply) is performed during radiographic image capturing. For example, the voltage supplied from the battery 44 to the radiation detector 40 becomes unstable and fluctuates greatly. It can be effectively avoided that noise caused by the magnetic field M applied from the side affects the radiation detector 40 side and noise is mixed into the radiographic image taken and the quality of the radiographic image is deteriorated. .

  In step S <b> 6, the doctor 18 or the radiographer moves the imaging device 22 to a position facing the electronic cassette 24, and then operates the imaging switch 72 to capture a radiographic image. In this case, the imaging switch 72 is configured in, for example, two stages, and by operating the first-stage switch, the radiation source 74 is activated to a predetermined tube current or the like to prepare for irradiation, and the second-stage switch is turned on. The radiation X is irradiated by the operation.

  That is, based on the operation of the imaging switch 72 by the doctor 18 or the like, the radiation source control unit 78 of the imaging apparatus 22 transmits a signal requesting transmission of imaging conditions to the console 28. Based on the received request, the console 28 transmits to the imaging device 22 the imaging conditions and the number of images taken for the imaging region of the patient 14 registered in the imaging condition management unit 118. Upon receiving the imaging conditions, the radiation source control unit 78 controls the radiation source 74 based on the imaging conditions, and irradiates (exposes) the patient 14 with radiation X having a predetermined dose. Of course, the imaging conditions may be transmitted in advance from the console 28 to a memory (not shown) of the radiation source controller 78.

  The radiation X transmitted through the patient 14 is irradiated with the radiation detector 40 after the scattered radiation is removed by the grid 38 of the electronic cassette 24, and an electric signal is transmitted by the photoelectric conversion layer 51 of each pixel 50 constituting the radiation detector 40. Then, the charge is held as a charge in the storage capacitor 53 (see FIG. 3). Next, the charge information (signal charge) that is the radiographic image information of the patient 14 held in each storage capacitor 53 is supplied from the address signal generation unit 98 that constitutes the cassette control unit 46 to the line scanning drive unit 58 and the multiplexer 66. Read according to the address signal.

  That is, the address decoder 60 of the line scan driver 58 outputs a selection signal according to the address signal supplied from the address signal generator 98, selects one of the switches SW1, and the TFT 52 connected to the corresponding gate line 54. A control signal Von is supplied to the gates of the first and second gates. On the other hand, the address decoder 68 of the multiplexer 66 outputs a selection signal in accordance with the address signal supplied from the address signal generation unit 98, sequentially switches the switch SW2, and is connected to the gate line 54 selected by the line scan driving unit 58. Radiation image information, which is charge information held in the storage capacitor 53 of each pixel 50, is sequentially read out via the signal line 56.

  The radiation image information read from the storage capacitor 53 of each pixel 50 connected to the selected gate line 54 of the radiation detector 40 is amplified by each amplifier 62 and then sampled by each sample and hold circuit 64. The signal is supplied to the A / D converter 70 via the multiplexer 66 and A / D converted into a digital signal (step S7). The radiographic image information converted into the digital signal is temporarily stored in the image memory 100 of the cassette control unit 46.

  Similarly, the address decoder 60 of the line scan driving unit 58 sequentially switches the switch SW1 in accordance with the address signal supplied from the address signal generating unit 98, and the storage capacitor 53 of each pixel 50 connected to each gate line 54. The stored radiation image information, which is charge information, is read out via the signal line 56 and A / D converted via the multiplexer 66 and the A / D converter 70 (step S7), and stored in the image memory 100 of the cassette control unit 46. Remember.

  The radiation image information stored in the image memory 100 is transmitted to the console 28 by wireless communication. The radiation image information transmitted to the console 28 is subjected to predetermined image processing in the image processing unit 120 and then associated with the patient information of the patient 14 registered in the patient information management unit 124. Is remembered.

  The radiographic image information subjected to the image processing is transmitted from the console 28 to the display device 26. The display device 26 that has received the radiation image information performs image display processing while displaying the radiation image while controlling the display unit 114 by the display control unit 112. For this reason, the doctor 18 can perform the operation while confirming the radiation image displayed on the display unit 114.

  In such an imaging system 10, for example, radiographic imaging is performed a plurality of times during surgery, and even if the remaining amount of the battery 44 of the electronic cassette 24 is insufficient, the power feeding device 25 supplies the electronic cassette 24 to the electronic cassette 24. Since non-contact power feeding (wireless power feeding) can be performed, charging can be appropriately performed while the electronic cassette 24 is installed at a predetermined photographing position. However, during radiographic image capturing, especially until A / D conversion is completed, the obtained radiographic image information is an analog signal, so the influence of noise due to the above-described non-contact power supply (wireless power supply) is large. Therefore, the noise may be mixed in the captured radiographic image, which may make it difficult to acquire a high-quality radiographic image.

  Therefore, in the imaging system 10 according to the present embodiment, an A / D conversion end determination unit 107, a charging control unit 108, and an imaging control unit 109 are provided, and at least radiographic image information detected by the radiation detector 40 is converted into a digital signal. Control is performed so as to prohibit contactless power feeding (wireless power feeding) until the conversion is completed.

  That is, in the radiographing system 10, when radiographing is performed, the radiographing switch 72 is operated by the doctor 18 or the like, or when the radiographic source controller 78 of the radiographing device 22 requests transmission of radiographing conditions to the console 28. When the substantial preparation for photographing is started, the console 28 transmits the photographing start signal to the electronic cassette 24 simultaneously with the control of the photographing device 22 or prior to the control of the photographing device 22 to control the cassette. The unit 46 is driven and controlled, and the electronic cassette 24 is brought into a photographing preparation completion state (steps S1 and S2). At the same time, the electronic cassette 24 generates a power supply prohibition signal from the charging control unit 108 and also generates a photographing permission signal from the imaging control unit 109 to place the power supply device 25 in a power supply prohibited state, while placing the imaging device 22 in a shooting standby state. (Steps S4 and S5).

  Subsequently, when imaging is started (step S6), the radiation image information detected by the radiation detector 40 is A / D converted by the A / D converter 70 (step S7). The irradiation of the radiation X and the A / D conversion of the detected radiation image information are performed until a predetermined number of photographings (predetermined number of exposures) are completed (step S8).

  If the predetermined number of images has been taken (YES in step S8), the A / D conversion end determination unit 107 determines whether or not the A / D conversion immediately after the predetermined number of images has been taken in step S9. Determined. When the A / D conversion end determination unit 107 determines that the A / D conversion has been completed, that is, the digitalization of the radiographic image information obtained by the current imaging has been completed (YES in step S9). Next, in step S <b> 10, a power supply permission signal is issued from the charging control unit 108.

  The power supply permission signal is transmitted from the electronic cassette 24 to the console 28. For example, under the management of the power supply information management unit 128, control for starting power supply by the power supply device 25, or power supply device 25 so that power supply can be started immediately. Is controlled to enter a power supply start standby state (power supply restart standby state) (step S12). Thereby, after A / D conversion of all acquired radiographic image information is completed after a predetermined number of radiographs, non-contact power feeding (wireless power feeding) to the battery 44 can be performed quickly (step S13). When the power supply start standby control is performed, for example, in the state where the console 28 has received the power supply permission signal, the battery 44 by the cassette control unit 46 or the cassette information management unit 126 as shown in step S11. In consideration of the remaining amount of power, it is preferable to perform power supply start control. Further, the power supply permission signal is directly transmitted from the electronic cassette 24 to the power supply device 25 without the console 28, and power supply start control is performed by the power supply control unit 86 of the power supply device 25 or the cassette control unit 46 of the electronic cassette 24. Alternatively, power supply start standby control may be executed.

  In this case, the end determination of the A / D conversion in step S9 is performed, for example, by irradiating the radiation detector 40 with the radiation X transmitted through the patient 14 and converting it into an electrical signal by the photoelectric conversion layer 51 of each pixel 50. Thereafter, a period during which signal charges are accumulated in the storage capacitor 53 (accumulation period), a period during which charges accumulated in the storage capacitor 53 are read (read period), and the read charge (analog signal) is A / D converted. It is preferable that the determination condition is the end of the period (A / D conversion period) in which the digital signal is converted by the device 70. This is because the influence of noise superposition on the image signal (radiation image information) is particularly remarkable in these three periods. That is, in the accumulation period and the reading period, the influence of noise is large because the charge is very small, and in the conversion period to the digital signal, the analog signal is less resistant to noise than the digital signal before A / D conversion. This is because noise that is a signal and superimposed on the analog signal is easily converted into a digital signal and appears in image data.

  The part of the accumulation period includes a time for exposing the radiation X from the radiation source 74. In other words, the operation after the reading should be performed immediately after the accumulation is started, the exposure is started at the earliest possible timing, the exposure is stopped, and the time lag in each of these operations is made as much as possible. If it is reduced, it is suitable for suppressing so-called dark current, and the quality of the obtained radiographic image can be further improved. The reading period is a period in which the TFT 52 is turned on and a signal flows to the A / D converter 70 via each amplifier 62 and the like. The reading period and the conversion period to the digital signal are time axes. In practice, the reading period (starting) actually occurs slightly earlier.

  The determination of the end of A / D conversion in step S9 is a point in time after the obtained radiographic image information has been A / D converted (after the end of the A / D conversion period) and saved in the image memory 100 has ended. It is more preferable to set to. Then, although not as much as A / D conversion, it is possible to effectively avoid the influence of noise caused by non-contact power feeding (wireless power feeding) when transferring data to the image memory 100 that is considered to be somewhat affected by noise. It is possible to prevent data corruption and the like. Of course, the completion of data transmission from the image memory 100 by the transceivers 48 and 116 is determined as the end point of the A / D conversion, and control is performed so as to more reliably avoid the influence of noise due to non-contact power feeding (wireless power feeding). You can also.

  The generation of the power supply permission signal in step S10 is after the end of the A / D conversion in step S9, for example, after the transmission of the digital signal from the electronic cassette 24 to the console 28 is completed. Needless to say, it can be implemented at a predetermined timing.

  As described above, in the photographing system 10, even when the power supply prohibition control is performed during photographing (step S <b> 4), the power is quickly supplied to the battery 44 after the A / D conversion with relatively little influence of noise. Can be started (resumed) (steps S10 to S13). For this reason, for example, it is particularly effective when the remaining amount of the battery 44 used in shooting is greatly reduced and it is desired to charge the battery quickly before the next shooting. In addition, after imaging | photography and electric power supply by above-mentioned step S1-S13 are complete | finished, when it is due to image | photograph again, etc., it should just return to each procedure, such as step S1, after completion | finish of step S13 (step S11). .

  In such an imaging system 10, it goes without saying that charging of the battery 44 may be appropriately performed under the control of the console 28 other than during imaging.

  As described above, in the imaging system 10 according to the present embodiment, even when the electronic cassette 24 is installed at a desired imaging position with respect to the patient 14, the power supply device 25 can easily supply power to the electronic cassette 24. It can be carried out. For this reason, even when it is necessary to charge the battery 44 of the electronic cassette 24 during the operation, the electronic cassette 24 can be charged without moving the electronic cassette 24, and the electronic cassette 24 and the imaging system. The handleability of the entire 10 can be improved. Further, it is possible to effectively avoid interruption and extension of imaging and surgery due to a shortage of the battery 44 of the electronic cassette 24.

  In addition, the imaging system 10 (electronic cassette 24) includes an A / D conversion end determination unit 107, a charging control unit 108, and an imaging control unit 109. A power feeding prohibition signal is issued before imaging starts, and A / D conversion is performed. When finished, a power supply permission signal is issued. Therefore, at least until the conversion of the radiation image information detected by the radiation detector 40 into a digital signal is completed, non-contact power feeding (wireless power feeding) is prohibited, so that an analog signal that is particularly susceptible to noise is used. It is possible to prevent the noise caused by the non-contact power transmission (wireless power transmission) from the power supply device 25 from affecting the radiation image information, and to acquire a high-quality radiation image. In addition, when a power supply prohibition signal is generated from the charging control unit 108, a shooting permission signal is generated from the shooting control unit 109, so that power supply during shooting can be more reliably prohibited.

  Further, after the end of A / D conversion, which is relatively less susceptible to the influence of noise, power supply can be started (restarted) quickly by the generation of a power supply permission signal from the charge control unit 108. Even if the remaining amount of 44 is greatly reduced, the battery can be charged quickly after the shooting is completed to prepare for the next shooting.

  In the imaging system 10, when the electronic cassette 24 is arranged in the power supplyable area of the corresponding power supply device 25, information is automatically transmitted and received between the electronic cassette 24 and the power supply device 25 via the console 28. The electronic cassette 24 is driven and controlled so that it can be photographed. Therefore, it is possible to omit providing a manual power switch or the like in the electronic cassette 24, and it is possible to prevent a shooting mistake caused by forgetting to operate the operation switch. For this reason, the handleability of the electronic cassette 24 and the imaging system 10 can be further improved. In this case, when the desired magnetic field M is not detected by the energy detection unit 96 of the electronic cassette 24, for example, a wireless power supply impossible signal is transmitted from the data management unit 106 to the cassette information management unit 126, and further, the wireless power supply is performed. By transmitting the disabled signal to the display device 26, the display unit 114 can notify the doctor or the like to that effect.

  FIG. 7 is an explanatory block diagram of the radiographic image capturing system 10a according to the second embodiment of the present invention.

  The imaging system 10a according to the present embodiment is basically the same as the imaging system 10 according to the first embodiment (see FIGS. 4 and 5) except that the RIS 29 and the HIS 33 are not connected to the console 28. The control method related to the photographing procedure, particularly the non-contact power feeding (wireless power feeding) is different. That is, in the imaging system 10a, the operations according to the first to third imaging procedures shown in the flowcharts of FIGS. 8 to 10 are performed. The imaging system 10a is preferably used for a system to which the RIS 29 and the HIS 33 are not connected, for example, a hospital that does not own the RIS 29, an imaging system for round trips, and the like.

  First, the first shooting procedure of the shooting system 10a will be described with reference to FIG. In FIG. 8, the detailed description of the control steps to which the same step numbers (S1 and the like) as those in FIG. 6 are given is omitted because the same or the same operation is performed, and the same applies hereinafter.

  The first imaging procedure is basically the same as the imaging procedure of the imaging system 10 shown in FIG. 6 except that step S8a is executed instead of step S8 shown in FIG.

  In the imaging system 10a, since the RIS 29 is not connected, it is not possible to acquire order information related to the number of images (number of times of imaging, number of exposures). Therefore, in step S8a, it is determined whether or not the irradiation of the radiation X by the imaging device 22 has been completed, for example, whether or not the imaging switch 72 has been turned off.

  That is, when it is determined that the irradiation with the radiation X has ended (YES in step S8a), for example, information on the imaging switch 72 being turned off is supplied to the charging control unit 108 under the control of the console 28. Further, in step S9, the A / D conversion end determination unit 107 determines whether or not the digitalization of the radiation image information obtained by the current imaging has been completed.

  As described above, in the first imaging procedure of the imaging system 10a, when it is determined that the irradiation with the radiation X is completed (YES in step S8a) and the A / D conversion is completed (YES in step S9). In step S10, the charging control unit 108 issues a power supply permission signal. Thereby, even when information on the desired number of shots cannot be obtained via the RIS 29, it is possible to determine the end of the desired number of shots by stopping the irradiation of the radiation X, for example, by turning off the shooting switch 72. It is possible to prevent noise caused by non-contact power transmission (wireless power transmission) from the power supply device 25 from affecting radiographic image information of the analog signal, and further, a power supply permission signal from the charge control unit 108 after the A / D conversion is completed. The power supply can be started (restarted) quickly due to the occurrence of.

  Next, a second imaging procedure of the imaging system 10a will be described with reference to FIG. The second imaging procedure is a control method for executing steps S8b and S9b instead of steps S8a and S9 in FIG.

  In step S8b of FIG. 9, the A / D conversion end determination unit 107 performs the A / D conversion end determination of the radiation image information in substantially the same manner as in step S9 of FIGS. Next, when it is determined in step S8b that the A / D conversion is completed (YES in step S8b), step S9b is executed.

  In step S9b, for example, whether or not a predetermined time (fixed time) has elapsed after the end of A / D conversion in step S8b by the charge control unit 108 that has received the end determination of the A / D conversion end determination unit 107. judge. If it is determined that a predetermined time has elapsed after the end of the A / D conversion (YES in step S9b), a power supply permission signal is issued from the charging control unit 108 in step S10. That is, in step S9b, by determining whether a predetermined time has elapsed after the end of A / D conversion, the data transfer time (storage time) of the radiation image information of the digital signal subjected to A / D conversion to the image memory 100 is ensured. In other words, since the power supply start signal is generated after waiting for the time related to the data transfer, it is possible to effectively avoid the influence of noise on the transferred data.

  Next, the third imaging procedure of the imaging system 10a will be described with reference to FIG. The third imaging procedure is a control method that executes step S7c instead of steps S7, S8a, and S9 in FIG.

  In step S7c of FIG. 10, it is determined whether or not a predetermined time (fixed time) has elapsed after the start of imaging in step S6, that is, irradiation of radiation X is started. In this case, the time when the predetermined time is counted in step S7c, that is, the time when the irradiation of the radiation X is started is, for example, after the operation of the imaging switch 72 (the second-stage switch described above) or with the radiation detector 40. Examples include the time when the radiation X is detected.

  If it is determined in step S7c that the predetermined time has elapsed after the start of shooting (YES in step S7c), then, in step S10, the charging control unit 108 issues a power supply permission signal. That is, in step S7c, by determining the elapse of a predetermined time after the start of imaging, the above-described accumulation period, reading period, A / D conversion period, and further, the image of the radiographic image information of the A / D converted digital signal In the data transfer time (storage time) to the memory 100, it is possible to prevent non-contact power feeding (wireless power feeding) from being executed, and to influence the noise caused by the non-contact power feeding (wireless power feeding) on the obtained radiation image information. It can be effectively avoided. In this case, the A / D conversion end determination unit 107 may determine that the A / D conversion has ended in consideration of a predetermined time from the start of radiation X irradiation, that is, the A / D conversion end determination unit 107. These functions can be integrated into the charging control unit 108.

  In the photographing system 10a as well, as in the case of the photographing system 10 described above, the power generation permission signal generation timing (step S10) is set after being transmitted from the image memory 100 to the console 28 via the transceivers 48 and 116. It is also possible to do.

  In the photographing system 10a, for example, when a predetermined number of shots can be set in advance by the console 28 or the like, control similar to the control flow shown in FIG. 6 can be performed according to the number of shots.

  FIG. 11 is a block diagram of a radiographic image capturing system 10b according to a first modification of the radiographic image capturing system 10 shown in FIG.

  In the imaging systems 10 and 10 a described above, the electronic cassette 24 includes the A / D conversion end determination unit 107, the charging control unit 108, and the imaging control unit 109 related to the power supply prohibition control of the power supply device 25 and the imaging start control of the imaging device 22. It was. On the other hand, in the imaging system 10b, the A / D conversion end determination unit 107a, the charging control unit 108a, and the imaging control unit 109a are provided in the console 28.

  In the imaging system 10b, the A / D conversion end determination unit 107a determines that the A / D conversion has ended, for example, when the radiation image information after A / D conversion is transmitted from the image memory 100 to the console 28. Then, by notifying the charging control unit 108a and the imaging control unit 109a, an operation based on the imaging procedure shown in FIG. 6 and the like is performed. The A / D conversion end determination unit 107, the charging control unit 108, and the imaging control unit 109 provided in the electronic cassette 24 may be set not to use the functions under the control of the console 28. . Of course, in the imaging system 10b, a simplified electronic cassette in which the A / D conversion end determination unit 107, the charging control unit 108, and the imaging control unit 109 are omitted can be used.

  As shown in FIG. 11, in the imaging system 10b, in addition to or instead of the A / D conversion end determination unit 107a, the charging control unit 108a, and the imaging control unit 109a, the A / D conversion end determination is performed in the imaging device 22. 107b, charging control unit 108b, and imaging control unit 109b may be provided, and the A / D conversion end determination unit 107c, charging control unit 108c, and imaging control unit 109c may be provided in the power feeding device 25. That is, if the A / D conversion end determination unit, the charging control unit, and the imaging control unit are provided together in at least one of the console 28, the imaging device 22, the power feeding device 25, and the electronic cassette 24, Operations similar to those of the imaging systems 10 and 10a can be performed, and a dedicated console or the like may be installed as a matter of course. When an A / D conversion end determination unit, a charge control unit, and an imaging control unit are provided in a plurality of devices, for example, an A / D conversion end determination unit mounted on any device under the control of the console 28 The charging control unit and the imaging control unit may be set to be selectively used, and the functions of the A / D conversion end determination unit, the charging control unit, and the imaging control unit of other devices may be configured not to be used.

  Since the electronic cassette 24 includes the A / D conversion end determination unit 107, the charging control unit 108, and the imaging control unit 109 as described above, for example, the console can be used for an existing radiographic imaging system. There is an advantage that the control function related to the power supply permission after the end of the A / D conversion can be easily added by slightly changing the control program of 28.

  In the radiographic imaging systems 10, 10 a, and 10 b described above, the radiographic image used during the operation is displayed on the display device 26. It goes without saying that it is possible. Similarly, the electronic cassette 24 is not limited to being used in the operating room 12 and can be applied to, for example, a medical examination or a round in a hospital.

  Further, as described at the beginning of the description of the first embodiment, the power supply device 25 only needs to be able to supply power to the electronic cassette 24 by non-contact (wireless). For example, instead of the LC resonators 84 and 88 and the detection LC resonator 94 (magnetic resonance method), each may be made of a dielectric and may use an electric field instead of the magnetic field M (electric field resonance method). Other than the so-called resonance type wireless power feeding apparatus as described above may be used. That is, as the supply energy obtained by converting the electric energy supplied from the power supply device 25 to the electronic cassette 24, for example, light energy, heat energy, or the like can be applied.

  Furthermore, in the radiographic imaging systems 10, 10 a, and 10 b, for example, the radiation detector 40 accommodated in the electronic cassette 24 converts the incident radiation X dose directly into an electrical signal by the photoelectric conversion layer 51. Instead of this, the incident radiation X is once converted into visible light by a scintillator, and then the visible light is converted into an electrical signal using a solid-state detection element such as amorphous silicon (a-Si). A detector may be used (see Japanese Patent No. 3494683).

  Furthermore, radiation image information can be acquired using a light conversion type radiation detector. In this light conversion type radiation detector, when radiation is incident on each solid detection element arranged in a matrix, an electrostatic latent image corresponding to the dose is accumulated and recorded in the solid detection element. When reading the electrostatic latent image, the radiation detector is irradiated with reading light, and the value of the generated current is acquired as radiation image information. The radiation detector can erase and reuse the radiation image information that is the remaining electrostatic latent image by irradiating the radiation detector with erasing light (see Japanese Patent Laid-Open No. 2000-105297). .

  Further, for example, transmission / reception of signals among the photographing device 22, the power feeding device 25, the display device 26, the console 28, and the like can be performed by wired communication. The wireless communication between the electronic cassette 24 and the external device may be performed by optical wireless communication using infrared rays or the like instead of normal communication using radio waves.

  FIG. 12 is a configuration diagram of an electronic cassette 500 according to a modification of the electronic cassette 24. In the electronic cassette 500, a guide line 504 serving as a reference for an imaging region and an imaging position is formed on the radiation irradiation surface side of the casing 502. By using the guide line 504 to position the subject (patient 14) with respect to the electronic cassette 500 and setting the radiation X irradiation range, the radiographic image information can be recorded in an appropriate imaging region.

  A display unit 506 that displays various types of information related to the electronic cassette 500 is disposed outside the imaging area of the electronic cassette 500. In the display unit 506, the ID information of the patient 14 recorded in the electronic cassette 500, the number of uses of the electronic cassette 500, the cumulative exposure dose, the state of charge (remaining capacity) of the battery 44 built in the electronic cassette 500, The imaging conditions of the radiation image information, the positioning image of the patient 14 with respect to the electronic cassette 500, and the like are displayed. In this case, for example, the radiologist confirms the patient 14 according to the ID information displayed on the display unit 506, confirms in advance that the electronic cassette 500 is in a usable state, and displays the displayed positioning image. Based on this, it is possible to position the desired imaging region of the patient 14 on the electronic cassette 500 and to perform imaging of optimal radiation image information.

  Further, by forming the handle portion 508 in the electronic cassette 500, the electronic cassette 500 can be easily handled and carried.

  On the side of the electronic cassette 500, an AC adapter input terminal 510, a USB (Universal Serial Bus) terminal 512, and a card slot 516 for loading a memory card 514 are preferably provided.

  The input terminal 510 is connected to the AC adapter from the outside when the charging function of the battery 44 built in the electronic cassette 500 is deteriorated or when sufficient time for charging the battery 44 cannot be secured. By supplying power, the electronic cassette 500 can be immediately used.

  The USB terminal 512 or the card slot 516 can be used when the electronic cassette 500 cannot transmit and receive information by wireless communication with an external device such as the console 28. In other words, by connecting a cable to the USB terminal 512, information can be transmitted / received to / from an external device by wired communication. In addition, information can be transmitted and received by loading a memory card 514 into the card slot 516, recording necessary information on the memory card 514, and then removing the memory card 514 and loading it into an external device.

  As shown in FIG. 13, it is preferable to place a cradle 518 that is loaded with an electronic cassette 24 and charges a built-in battery 44 at a required location in the operating room 12 or hospital. In this case, the cradle 518 uses the wireless communication function or the wired communication function of the cradle 518 as well as charging the battery 44 by a non-contact power supply device (not shown) similar to the power supply device 25 described above, and uses the RIS 29, the HIS 33, the console. Necessary information may be exchanged with an external device such as 28. The information to be transmitted / received can include radiation image information recorded in the electronic cassette 24 loaded in the cradle 518.

  In addition, a display unit 520 is provided in the cradle 518, and the display unit 520 displays necessary information including the charged state of the electronic cassette 24 loaded and the radiation image information acquired from the electronic cassette 24. You may do it.

  Further, a plurality of cradle 518 is connected to the network, and the charging state of the electronic cassette 24 loaded in each cradle 518 is collected via the network so that the location of the electronic cassette 24 in the usable charging state can be confirmed. It can also be configured.

  FIG. 14 is an explanatory diagram of a radiographic image capturing system 10c according to a second modification of the radiographic image capturing system 10 shown in FIG.

  In the imaging system 10 and the like described above, the configuration in which the electronic cassette 24 is used as a radiation detection apparatus that detects the irradiated radiation X and acquires radiation image information has been described. On the other hand, in the imaging system 10c, a configuration in which the supine imaging is performed using the radiation detection device 152 built in the imaging table 150, which is a bed on which the patient 14 lies, instead of the electronic cassette 24 will be described.

  In the imaging system 10c, the radiation detection device 152 has substantially the same configuration and structure as the electronic cassette 24 described above, and includes a radiation detector 40, a battery 44, a wireless power receiving unit 49, a control unit 46a, a transceiver 48, and the like. Each device is housed in a box-shaped casing 154 made of a material that transmits radiation X. The control unit 46a functions in substantially the same manner as the cassette control unit 46 constituting the electronic cassette 24, and includes an A / D conversion end determination unit 107, a charge control unit 108, a photographing control unit 109, and the like.

  A rail 156 is provided on the lower surface of the imaging table 150 along the longitudinal direction thereof. The radiation detection device 152 is moved along the rail 156 by a slider mechanism (not shown) provided in the casing 154. It can be moved to a desired position in the arrow X direction (horizontal direction). Therefore, the radiation detection device 152 can be easily moved to a desired imaging region of the patient 14 lying on the imaging table 150.

  As described above, in the imaging system 10c, while the radiation detection device 152 can be moved, the radiation detection device 152 incorporates the battery 44 and the wireless power receiving unit 49 in substantially the same manner as the electronic cassette 24 described above. A power cable or the like to the detection device 152 is not necessary. Therefore, the radiation detection device 152 can be smoothly moved without being affected by the cables, and the handleability can be improved. Similarly to the imaging system 10 and the like, non-contact power feeding (wireless power feeding) from the power supply device 25 to the battery 44 and imaging by the imaging device 22 can be appropriately controlled, and high-quality radiographic images can be acquired. Is possible.

  As shown in FIG. 14, the imaging system 10 c may have a configuration in which wheels 158 are provided on the legs of the imaging platform 150. In this case, the imaging table 150 itself can be easily moved to a desired position in the room, and the rail 156 can be eliminated if necessary, and the radiation detection device 152 can be fixed to the imaging table 150.

  FIG. 15 is an explanatory diagram of a radiographic image capturing system 10d according to a third modification of the radiographic image capturing system 10 shown in FIG.

  The imaging system 10d does not use the electronic cassette 24 in the same manner as the imaging system 10c described above, but stands by using a radiation detection device 164 that is detachable from a column 162 that is fixed to a floor surface and a wall surface 160 (not shown). This is a system for shooting.

  The radiation detection device 164 has substantially the same configuration and structure as the electronic cassette 24 and the radiation detection device 152 described above, and includes a radiation detector 40, a battery 44, a wireless power reception unit 49, a control unit 46a, a transceiver 48, and the like. Each of these devices is housed in a box-shaped casing 154 made of a material that transmits the radiation X.

  In this case, a pair of hook members 166 and 168 spaced apart in the vertical direction are provided on the back surface of the radiation detection apparatus 164 functioning as a standing imaging stand. On the other hand, a mounting recess 170 is formed on the side surface of the support column 162 facing the radiation detection device 164. The mounting recess 170 extends in the horizontal direction (the shoulder width direction of the patient 14) and corresponds to the hook members 166 and 168. A pair of shafts 172 and 174 spaced apart in the vertical direction are fixed. Further, the lower hook member 168 can swing upward with a support shaft 176 as a fulcrum by a spring mechanism (not shown) (see a two-dot chain line in FIG. 15).

  Therefore, the hook members 166 and 168 can be easily and reliably attached to and detached from the shafts 172 and 174 by using the swinging motion of the hook member 168, that is, the radiation detection device 164 can be easily attached to the column 162. And can be securely attached and detached. Further, the radiation detection device 164 is movable in the arrow Y direction (vertical direction) by a slide mechanism (not shown) while being attached to the support column 162.

  Note that reference numeral 178 in FIG. 15 is a frame fixed in both width directions of the casing 154, and when the patient 14 takes a desired imaging posture with respect to the radiation detection device 164, which is an imaging table, the imaging posture. It is a bar member grasped in order to maintain.

  As described above, in the imaging system 10d, the radiation detection device 164 is detachable and movable with respect to the support column 162, while the radiation detection device 164 includes the battery 44 in substantially the same manner as the electronic cassette 24 and the radiation detection device 152 described above. In addition, since the wireless power receiving unit 49 is built in, a power cable or the like is unnecessary. Therefore, the radiation detection apparatus 164 can be easily moved and detached without being affected by the cables. Similarly to the imaging system 10 and the like, non-contact power feeding (wireless power feeding) from the power supply device 25 to the battery 44 and imaging by the imaging device 22 can be appropriately controlled, and high-quality radiographic images can be acquired. Is possible.

  FIG. 16 is an explanatory diagram of a radiographic image capturing system 10e according to a fourth modification of the radiographic image capturing systems 10 and 10b illustrated in FIGS. 4 and 11.

  In this imaging system 10e, an A / D conversion end determination unit 107 and an imaging control unit 109 are arranged in the operation management unit 102, while charging control units 108a, 108b, 108c differs from the above-described imaging systems 10 and 10b (see FIGS. 4 and 11) in that 108c is arranged.

  In FIG. 16, other than the operation management unit 102, the A / D conversion end determination unit 107, the imaging control unit 109, and the charging control units 108 a, 108 b, and 108 c in the imaging device 22, the electronic cassette 24, the power feeding device 25, and the console 28. These components are not shown.

  In addition, although the charging control units 108a, 108b, and 108c are arranged in the photographing device 22, the power feeding device 25, and the console 28, it is sufficient that the charging control unit is arranged in any one of the devices. That is, in the fourth modified example, the A / D conversion end determination unit, the imaging control unit, and the charging control unit include at least two devices (two of the imaging device 22, the electronic cassette 24, the power feeding device 25, and the console 28). If it is arranged in a state of being distributed, it is possible to exhibit the same function as the operation management unit 102 of FIG. Accordingly, the fourth modified example is not limited to the example of FIG. 16. For example, only the A / D conversion end determination unit is arranged in one device, and the imaging control unit and the charging control unit are arranged in the other device. It is also applicable when the is arranged.

  In the imaging system 10e of FIG. 16, the A / D conversion end determination unit 107 and the imaging control unit 109 in the operation management unit 102 recognize the state (operation mode) of the electronic cassette 24 and charge control units 108a and 108b. , 108c as various signals, and the charge control units 108a, 108b, 108c identify the optimum power supply state based on the notified operation mode (signal), and the signal corresponding to the identified optimum power supply state Is generated.

  In the imaging system 10e according to the fourth modification, it is possible to obtain the same effects as those of the imaging system 10 according to the first embodiment and the imaging system 10b according to the first modification.

  FIG. 17 is an explanatory diagram of a radiographic image capturing system 10f according to a fifth modification of the radiographic image capturing system 10 shown in FIG.

  This imaging system 10f is the imaging system 10 according to the first embodiment in that the power supply control unit 86 of the power supply apparatus 25 includes the mutual inductance detection unit 200 and the wireless power reception unit 49 includes the relay 202 (FIGS. 4 and 5). 5)). In FIG. 17, the components other than the LC resonator 84 and the power supply control unit 86 of the power supply device 25 and the battery 44 and the wireless power reception unit 49 of the electronic cassette 24 are not shown.

  As an example, the LC resonator 84 of the power supply apparatus 25 is configured by an LC parallel resonance circuit in which a coil 204 and a capacitor 206 are connected in parallel, while the LC resonator 88 of the electronic cassette 24 or the detection LC resonator 94. Is composed of an LC parallel resonant circuit in which a coil 208 and a capacitor 210 are connected in parallel. The relay 202 includes an operation coil 212 to which a signal (current) is supplied from the charging control unit 108, and a contact switch 214 that is turned on or off due to excitation of the operation coil 212 based on the current. Shall be. Note that one end of the switch 214 is connected to the coil 208 and the capacitor 210, and the other end is connected to the charging circuit 90.

  Here, when the charging control unit 108 determines charging of the battery 44 and causes a current to flow through the operation coil 212, the operation coil 212 generates a magnetic flux based on the current and magnetizes an electromagnet (not shown). Thereby, the iron piece which comprises switch 214 is attracted | sucked to the said electromagnet side, and it switches from OFF to ON. As a result, non-contact power feeding from the power feeding device 25 to the battery 44 is possible.

  On the other hand, when non-contact power feeding is performed, the coil 204 of the LC resonator 84 and the coil 208 of the LC resonator 88 or the detection LC resonator 94 are magnetically coupled with each other with a mutual inductance mi.

  In this state, when the charging control unit 108 determines to stop (prohibit) charging the battery 44 and stops energization of the operation coil 212, generation of magnetic flux by the operation coil 212 is stopped. Thereby, the iron piece is separated from the electromagnet, and the switch 214 is switched from on to off. As a result, the electrical connection between the coil 208 and the charging circuit 90 and the battery 44 is interrupted, and the mutual inductance mi between the coil 204 and the coil 208 changes suddenly.

  The mutual inductance detection unit 200 detects the current flowing through the coil 204. When the magnitude of the current suddenly changes with time, the mutual inductance mi suddenly changes due to switching of the switch 214 from on to off. Judge that.

  When the mutual inductance detection unit 200 detects a sudden change in the mutual inductance mi, the power supply control unit 86 determines that the charging control unit 108 has decided to stop (prohibit) charging the battery 44, and to the LC resonator 84. Stop supplying electrical energy (high frequency power).

  In the imaging system 10f according to the fifth modified example, the power supply device 25 is based on detection of a temporal change in the mutual inductance mi by the mutual inductance detection unit 200 even when the power supply prohibition signal is not supplied for some reason. Thus, non-contact power feeding can be stopped, so that power feeding control for the battery 44 can be performed accurately and reliably. That is, the power supply device 25 can make a self-determination as to whether or not power supply to the battery 44 should be prohibited without the supply of the power supply prohibition signal from the charge control unit 108.

  In the above description, when it is determined that the battery 44 has a sufficient remaining amount, a photographing permission signal and a power feeding prohibition signal are issued, and charging prohibition control resulting from the start of photographing is performed. When the battery 44 has a sufficient remaining amount, in place of such charge prohibition control, a power switch (not shown) provided on the side surface of the electronic cassette 24 and operated by the doctor 18 or a technician is turned on. The charging prohibition control may be performed by considering the start of imaging and issuing an imaging permission signal and a power supply prohibition signal.

  As described above, in the imaging systems 10, 10 a to 10 f according to the present embodiment, the electronic cassette 24 and the radiation detection devices 152 and 164 that are radiation detection devices can be moved, but these are set at desired imaging positions. Even in this case, the power supply device 25 can easily supply power to the electronic cassette 24. In addition, since the A / D conversion end determination unit, the charging control unit, and the imaging control unit are provided, at least until the A / D conversion of the detected radiation image information is completed, non-contact (wireless) power feeding is performed. It will not be done. For this reason, it is possible to capture and acquire a high-quality image while avoiding the influence of noise caused by the non-contact power transmission (wireless power transmission), while performing quick charging during non-photographing (end of photographing). it can.

  The present invention is not limited to the above-described embodiments, and various configurations can be adopted without departing from the gist of the present invention.

10, 10a to 10f ... Radiation imaging system 22 ... Imaging device 24, 500 ... Electronic cassette 25 ... Power feeding device 26 ... Display device 28 ... Console 40 ... Radiation detector 44 ... Battery 46 ... Cassette control unit 46a ... Control unit 49 ... Wireless power receiving unit 70 ... A / D converter 72 ... Imaging switches 107, 107a to 107c ... A / D conversion end determination units 108, 108a to 108c ... Charging control units 109, 109a to 109c ... Imaging control units 152, 164 ... radiation Detection device

The present invention is, energy into a subject (e.g., radiation energy) is irradiated with, relates to an image acquisition system for converting energy from the subject to the image information.

By the way, in the above-described conventional technology, for example, when the remaining battery level is insufficient by intermittently performing a plurality of imagings during a single operation, an electronic cassette (image acquisition device) laid on the patient is cradled. It is necessary to move it to charge. For this reason, it takes a lot of time for charging, and there is a possibility of causing a longer operation time and an increased burden on the patient.

On the other hand, when non-contact power feeding is performed, for example, during A / D conversion of radiation image information obtained by a radiation detector (image acquisition unit) incorporated in the electronic cassette during surgery or the like, the non-contact power feeding is performed. Noise caused by the magnetic flux used in the process may have a large effect on a captured image, particularly an analog signal before conversion, and it may be difficult to acquire a high-quality radiation image (image information) .

The present invention has been made in consideration of the conventional problems described above, the power supply to the image acquisition device can be easily performed, the image acquisition system that allows the acquisition of high-quality image information The purpose is to provide.

The present invention includes an energy irradiation device that irradiates energy to a subject , an image acquisition device that converts energy from the subject into image information, and a non-contact power supply device that supplies power to the image acquisition device in a non-contact manner. The present invention relates to an image acquisition system comprising: the energy irradiation device; the image acquisition device; and a control device that controls driving of the non-contact power supply device. In the present invention, the image acquisition device includes an image acquisition unit that acquires the image information, an A / D converter that performs A / D conversion on the image information, a power supply unit that supplies power to the image acquisition unit, and has a non-contact power receiving unit supplied to the power supply unit to receive power supplied contactlessly from the non-contact power feeding device. In addition, at least two of the energy irradiation device, the image acquisition device, the non-contact power feeding device, and the control device determine whether the A / D conversion has been completed. a determination unit, between the start of the irradiation of the energy until the determination of the end of the a / D conversion by the a / D conversion completion determination unit, and a charging control unit to stop the non-contact power supply from the non-contact power feeding device Provided. Further, the control device controls an A / D conversion end determination unit and a charge control unit of any one of the energy irradiation device, the image acquisition device, the non-contact power feeding device, and the control device .

Specifically, in the image acquisition system according to the present invention, the energy irradiation apparatus is an imaging apparatus that irradiates the subject with radiation . Further, the image acquiring apparatus, the radiation detector as the image acquisition unit for converting the radiation transmitted through the object to detect and radiation image information, the A / D converter of the radiation image information to A / D conversion , the power supply unit, and a radiation detecting device having the non-contact power receiving unit. In this case, the charging control unit stops the non-contact power feeding from the non-contact power feeding device from the start of photographing by the photographing device to the end of the A / D conversion by the A / D conversion end judging unit. To do . Further, the control device, the imaging device, the radiation detection device, wherein one of the non-contact power feeding device and the control device, select one of the A / D conversion completion determination unit and charge control unit provided in the apparatus By using the contactless power supply, the timing of contactless power feeding from the contactless power feeding device to the contactless power receiving unit is controlled .

In this case, the radiation detection apparatus further includes an image memory in which the radiation image information converted into a digital signal by the A / D converter is stored, and the A / D conversion end determination unit includes the digital signal. If the radiation image information converted into the image data is stored in the image memory, the A / D conversion is determined to be completed, so that it is affected by the noise during data transfer to the image memory. Can be effectively avoided, causing garbled data and the like, and acquisition of a higher-quality radiation image becomes possible.

Further, when the power supply prohibition signal is generated from the charge control unit, the non-contact power supply prohibition control during photographing is more reliably provided with a photographing control unit that generates a photographing permission signal for permitting photographing by the photographing device. Can be executed. Further, in the image acquisition system, at least two of the imaging device, the radiation detection device, the non-contact power feeding device, and the control device include the A / D conversion end determination unit, the charge control unit, and the control device. An imaging control unit may be provided. In this case, the control device includes an A / D conversion end determination unit, a charge control unit, and a control device provided in any one of the imaging device, the radiation detection device, the non-contact power feeding device, and the control device. The photographing control unit may be selectively used.

The image acquisition system is connected to an information management system that stores a desired number of times of photographing of the subject, and the A / D conversion end determination unit is configured to capture the number of times of photographing stored in the information management system. When the A / D conversion end determination is performed after the image processing is completed, all imaging is completed, and it is surely waited for the A / D conversion of the obtained radiation image information to be completed. Thus, it is possible to start non-contact power feeding.

Incidentally, Oite the present invention, the non-contact power feeding apparatus, the supply power in a non-contact manner with respect noncontact power receiving unit by magnetic coupling without contact power receiving unit and the mutual inductance, the charge control unit is the When the mutual inductance changes due to stopping the supply of power from the non-contact power receiving unit to the power source unit, the non-contact power supply to the non-contact power receiving unit may be stopped.

In the present invention, the control device further includes a power supply information management unit that manages identification data for specifying each of the non-contact power supply devices when a plurality of the non-contact power supply devices are installed. Also good. In this case, the radiation detection device, the identification data of the non-contact power feeding device which supplies power contactlessly to the non-contact power receiving unit may be received from the feeding information manager. In the present invention, the non-contact power receiving unit may receive a magnetic field from the non-contact power feeding device and convert the electric energy into electric energy, and supply power corresponding to the converted electric energy to the power source unit. In this case, the non-contact power feeding device outputs a first magnetic field in a predetermined power feeding area by being driven under a first operating condition, and the radiation detecting device is arranged in the power feeding area so as to be in the non-contact state. When the power receiving unit detects the first magnetic field, the second magnetic field stronger than the first magnetic field may be output in the power feeding area by driving under the second operating condition.

Hereinafter, preferred embodiments of an image acquiring system according to the present invention will be described in detail with reference to the accompanying drawings.

As shown in FIG. 1, a patient 14 is placed in an operating room 12 where a radiographic imaging system (image acquisition system) 10 (hereinafter also referred to as “imaging system 10” ) according to the first embodiment of the present invention is installed. An operating table 16 which is a bed on which the patient lies is placed, and an instrument table 20 on which various instruments used by the doctor 18 for surgery are placed. Around the operating table 16, various devices necessary for the operation such as an anesthesia machine, an aspirator, an electrocardiograph, and a blood pressure monitor (not shown) are arranged.

The imaging system 10 detects an imaging device ( energy irradiation device, radiation irradiation device) 22 that irradiates a patient 14 as a subject with a dose of radiation (energy) X in accordance with imaging conditions, and the radiation X transmitted through the patient 14. Electric power is supplied to an electronic cassette 24 that is a radiation detection device (image acquisition device) including a radiation detector (image acquisition unit) 40 (see FIG. 2) and a battery 44 (see FIG. 2) built into the electronic cassette 24. A power supply device (non-contact power supply device, wireless power supply device) 25 that supplies wirelessly (contactlessly), a display device 26 that displays a radiation image based on the radiation X detected by the radiation detector 40, and the imaging system 10 And a console (control device) 28 for comprehensive control. In the imaging system 10, signals can be transmitted and received between the imaging device 22, the electronic cassette 24, the power feeding device 25, the display device 26, and the console 28 by wireless communication using, for example, UWB (Ultra Wide Band).

Here, in conjunction with the start of operation of the console 28 or by operation of an operation start switch (not shown), the power feeding device 25 is driven under predetermined operation conditions ( first operation condition, low output operation). Therefore, the electronic cassette 24 can detect that the electronic cassette 24 is disposed in the power supplyable area of the power supply device 25 by the detection LC resonator 94 and the energy detection unit 96 of the wireless power receiving unit 49. That is, the energy detection unit 96 functions as a power reception availability detection unit that detects whether or not the electronic cassette 24 is in an area where power can be received from the power supply device 25. At this time, the power supply control unit 86 of the power supply device 25 has a weak magnetic field that allows the detection LC resonator 94 and the energy detection unit 96 of the electronic cassette 24 to detect the presence or absence of the magnetic field M from the LC resonator 84 (the first magnetic field ). (Magnetic field) Low power operation is applied to apply M, and power consumption is effectively suppressed.

In the non-contact power supply (wireless power supply) to the electronic cassette 24, the magnetic field M applied from the LC resonator 84 to the electronic cassette 24 is changed to a magnetic field (second magnetic field) M that is sufficiently stronger than the low output operation. The power feeding device 25 may be driven and controlled under the changed predetermined operating conditions ( second operating conditions, high output operation, power feeding operation). Further, in the electronic cassette 24, the power received by the LC resonator 94 for detection together with the LC resonator 88 can be used for charging the battery 44 from the charging circuit 90, so that the battery 44 can be charged more rapidly. .

Claims (13)

A radiation detector that detects radiation irradiated from an external imaging device and transmitted through the subject;
A non-contact power receiving unit that receives non-contact power supplied from an external non-contact power feeding device and supplies power to the power source unit;
An A / D converter that performs A / D conversion on radiation image information of the radiation applied to the radiation detector;
An image memory in which the radiation image information converted into a digital signal by the A / D converter is stored;
An A / D conversion end determination unit that determines that the A / D conversion is completed when the radiation image information converted into the digital signal is stored in the image memory;
A charging control unit for stopping non-contact power feeding from the non-contact power feeding device from the start of photographing by the photographing device to the end of the A / D conversion by the A / D conversion end judging unit;
A radiation detection apparatus comprising: The radiation detection apparatus according to claim 1,
The radiation control apparatus, wherein the charging control unit generates a power supply prohibition signal for prohibiting non-contact power supply from the non-contact power supply apparatus before the start of imaging by the imaging apparatus. The radiation detection apparatus according to claim 1 or 2,
When the A / D conversion end determination unit determines that the A / D conversion has ended, the charge control unit generates a power supply permission signal that permits non-contact power supply from the non-contact power supply device. A radiation detection apparatus characterized by the above. The radiation detection apparatus according to claim 2.
The radiation detection apparatus further includes an imaging control unit that generates an imaging permission signal that permits imaging by the imaging apparatus when the power supply prohibition signal is generated from the charging control unit. An imaging device for irradiating a subject with radiation;
A radiation detector that detects radiation that has passed through the subject, an A / D converter that performs A / D conversion on radiation image information emitted from the radiation applied to the radiation detector, and a digital signal that is converted by the A / D converter An image memory in which the radiation image information is stored, and a radiation detection apparatus having a power supply for supplying power to the radiation detector;
A non-contact power feeding device that is provided in the radiation detection device and supplies power in a non-contact manner to a non-contact power receiving unit that supplies power to the power source unit;
A control device for controlling driving of the imaging device, the radiation detection device, and the non-contact power feeding device;
A radiographic imaging system comprising:
An A / D conversion end determination unit that determines that the A / D conversion is completed when the radiation image information converted into the digital signal is stored in the image memory;
A charging control unit for stopping non-contact power feeding from the non-contact power feeding device from the start of photographing by the photographing device to the end of the A / D conversion by the A / D conversion end judging unit;
A radiographic imaging system characterized in that is provided. In the radiographic imaging system of Claim 5,
The radiographic imaging system according to claim 1, wherein the charging control unit generates a power supply prohibiting signal for prohibiting non-contact power feeding from the non-contact power feeding device before starting photographing by the photographing device. In the radiographic imaging system according to claim 5 or 6,
When the A / D conversion end determination unit determines that the A / D conversion has ended, the charge control unit generates a power supply permission signal that permits non-contact power supply from the non-contact power supply device. A radiographic imaging system characterized by In the radiographic imaging system of Claim 6,
The radiographic imaging system further comprising: an imaging control unit that generates an imaging permission signal that permits imaging by the imaging apparatus when the power supply prohibition signal is generated from the charging control unit. In the radiographic imaging system of any one of Claims 5-8,
The radiation image capturing system is connected to an information management system that stores a desired number of times of capturing the subject,
The radiographic imaging system, wherein the A / D conversion end determination unit performs the A / D conversion end determination after imaging for the number of imaging times stored in the information management system is completed. In the radiographic imaging system of Claim 7,
The charging controller generates the power supply permission signal when it is determined that the irradiation of the radiation from the imaging apparatus is stopped and the A / D conversion is completed, and the radiographic imaging is characterized in that system. In the radiographic imaging system of Claim 7,
The radiographic imaging system characterized in that the charging control unit generates the power supply permission signal after a predetermined time has elapsed after it is determined that the A / D conversion has been completed. In the radiographic imaging system of Claim 7,
The radiographic imaging system, wherein the charging control unit generates the power supply permission signal after a predetermined time has elapsed after the start of radiation irradiation from the imaging apparatus. A radiation image capturing method for irradiating a subject with radiation, detecting the radiation with a radiation detector mounted on a radiation detection device, converting the radiation into radiation image information, and obtaining a desired radiation image,
While performing non-contact power feeding to the power supply unit of the radiation detection device,
After the start of radiographic imaging, at least the radiation image information detected by the radiation detector is A / D converted, and the radiation image information converted into a digital signal is stored in an image memory so that the A / D is stored. The radiographic imaging method, wherein the non-contact power supply is stopped until the conversion is completed.

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