JP2015146916A - X-ray photographing device, control method thereof, device, communication relay device, and control device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a technology to easily perform setup of an X-ray photographing system with a plurality of components having various interfaces, and reducing restrictions on a photographable environment.SOLUTION: In an X-ray photographing device for acquiring an X-ray image by detecting an X-ray irradiated from an X-ray generation part by a detection part, the X-ray generation part includes: a plurality of components having different communication interfaces respectively; conversion means for converting signals between the communication interfaces of the components and a common communication interface; and communication means for communicating with other devices constituting the X-ray photographing device by the common communication interface.

Description

  The present invention relates to an X-ray imaging apparatus, a control method thereof, and an apparatus, and more particularly to an X-ray imaging system including a plurality of apparatuses connected to each other through a communication path.

  At present, in the X-ray still image photographing system in the medical field, a film system in which a patient as a subject is irradiated with X-rays and the transmitted X-ray image is exposed on a film is mainly used. The film system has a function of displaying and recording information, can be enlarged in area, has high gradation, is lightweight, and is easy to handle, and thus is widely used all over the world. However, in the film system, in addition to the complexity that requires development processing, a place, manpower, and time are required for long-term storage and retrieval.

  In recent years, there has been an increasing demand for digitization of X-ray images, and instead of film, a radiographic apparatus that forms an image by converting radiation into an electrical signal by a plurality of radiation detection elements arranged in a two-dimensional matrix. It has been put into practical use. This type of radiation imaging apparatus uses an X-ray detector (FPD: Flat Panel Detector) in which solid-state imaging elements are arranged in a two-dimensional matrix and converts an X-ray dose into an electrical signal. According to the X-ray imaging apparatus having such an X-ray detector, since the X-ray image can be replaced with digital information, the image information can be confirmed instantaneously. Further, by transmitting digital data by radio, it is possible to connect the terminal for confirming an image and the FPD without a cable. Furthermore, since digital data can be transmitted far away without being degraded, for example, by transmitting X-ray image information, it is possible to receive advanced diagnosis by a large hospital while being far away. Become. Moreover, the storage space of the film in a hospital can be saved by not using a film.

  An X-ray detector (sensor) such as an FPD includes a photoelectric conversion circuit in which a plurality of photoelectric conversion elements that convert radiation into an electric signal are arranged in a matrix, and an electric signal obtained by this conversion. And a readout circuit for reading out from. When the subject is irradiated with X-rays, photoelectric conversion is performed on the transmitted X-rays transmitted through the subject in each photoelectric conversion element of the photoelectric conversion circuit, and signal charges corresponding to the transmitted X-ray dose are accumulated in each photoelectric conversion element. Is done. The readout circuit sequentially reads out the signal charges accumulated in each photoelectric conversion element as an electrical signal by driving each signal line of the photoelectric conversion circuit and appropriately controlling the switch element to which the photoelectric conversion element is connected, Amplify and output.

  In the configuration as described above, an X-ray generation apparatus that generates and emits X-rays can communicate information such as the position and orientation of the apparatus and a synchronization signal with other apparatuses such as an FPD and a control apparatus. Are known.

  For example, when performing X-ray imaging, it is necessary to install the X-ray generator and the FPD so as to face each other, and it is known that the position and orientation are communicated between the devices in order to facilitate such installation. Yes. X-ray imaging should be performed in a patient room (round-trip imaging) or home (at-home imaging) where the subject is photographed using a battery-powered X-ray generator rather than a dedicated imaging room in the hospital. There is. In such a case, the person to be imaged may take an image in a supine position, a sitting position, or a semi-sitting position without taking a standing position, and the X-ray generator and the FPD are connected in accordance with the position of the object to be imaged. It is necessary to install. However, it is generally complicated and the accuracy is low to install the apparatus while visually confirming that the X-ray generation apparatus and the FPD face each other. Thus, it is known to confirm that the X-ray generator and the FPD are opposed to each other by communicating the position and orientation of the apparatus. For example, using a gravitational sensor (three-axis alignment sensor), the operator when the portable X-ray detector is improperly oriented with respect to either the X-ray generator, the Earth, or the patient being imaged There is known a configuration for notifying (Patent Document 1).

  In imaging using the FPD, it is necessary to synchronize the timing of X-ray exposure and charge accumulation in the photoelectric conversion element. Therefore, it is known to communicate a synchronization signal between the FPD and the X-ray generator (Patent Document 2).

JP 2012-452 A JP 2006-25832 A

  However, information such as the position and orientation of the device and the synchronization signal are communicated using different communication interfaces. For example, the information on the gravity sensor described in Patent Document 1 is generally communicated by a communication interface such as SPI (Serial Peripheral Interface) or I2C (Inter-Integrated Circuit). The synchronization signal described in Patent Document 2 is generally communicated by a communication interface such as LVDS (Low Voltage Differential Signaling). Although it is conceivable to communicate battery information of the internal power supply of the X-ray generation unit between apparatuses, the battery information is generally communicated by a communication interface such as a CAN (Controller Area Network).

  When these functions are integrated, as many interfaces as the number of functions are necessary. For this reason, in the conventional configuration, in order to configure the device, it is necessary to connect a dedicated communication cable for each communication information, or to perform wireless communication setting, and the setup of the device is complicated. In addition, since it is necessary to connect many cables, a certain shooting space is required, and the photographed person needs to take a certain posture.

  The present invention has been made in view of the above problems, and makes it possible to simplify the setup of an X-ray imaging system including a plurality of components having various interfaces, and to reduce restrictions on the imaging environment. It aims at providing the technology to do.

According to the present invention, an X-ray imaging apparatus that obtains an X-ray image by detecting X-rays emitted from an X-ray generation unit by a detection unit,
The X-ray generator is
Multiple components, each with a different communication interface;
Conversion means for converting a signal between the communication interface of the component and a common communication interface;
An X-ray imaging apparatus comprising: a communication unit that communicates with another apparatus configuring the X-ray imaging apparatus through the common communication interface.

  According to the present invention, it is possible to provide a technique that makes it easy to set up an X-ray imaging system including a plurality of components having various interfaces and that can reduce restrictions on an imaging environment. it can.

The figure which shows the example of imaging | photography in a hospital room or at home. The timing chart which shows operation | movement of a control part, FPD, and an X-ray generation part. , , , 1 is a block diagram showing a configuration of an X-ray imaging system. The flowchart which shows operation | movement of a X-ray imaging system. The figure which shows the information exchanged between an X-ray generator, an X-ray detector, and an imaging | photography control apparatus. The figure which illustrates embodiment for implement | achieving communication between each apparatus contained in an X-ray imaging system. The figure which shows the modification of a communication relay apparatus. The figure which shows the structural example of the X-ray imaging system using the X-ray generator 801. The figure which shows the hardware structural example of an X-ray imaging system.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings. In the following embodiments, an X-ray imaging system that acquires an X-ray image as a radiation image by performing imaging using X-rays as radiation will be described as an example.

(overall structure)
FIG. 1 is a diagram schematically illustrating a state in which a subject in a semi-sitting position is imaged by an X-ray imaging system (X-ray imaging apparatus) 10. In the configuration of FIG. 1, it is necessary to install an FPD (detection unit) 2 behind the subject and to install an X-ray generation unit (X-ray generation device) 1 so as to face the FPD 2. The X-ray generation unit 1 exposes (irradiates) the X-rays 11 in accordance with, for example, an input from the operation input unit 6 including the exposure switch 61. In the present embodiment, the operation input unit 6 is provided in the X-ray generation unit 1. However, the operation input unit 6 may be provided in another device such as a control unit (control device) 3 that controls the operation of the entire device, or as an independent device. You may make it install. At present, it is common to confirm mainly that the FPD 2 and the X-ray generator 1 are opposed to each other mainly by visual observation of the photographer. For this reason, there is a possibility that the X-ray 11 is exposed in a state where the X-ray is not opposed firmly, that is, in a state where the X-ray exposure direction is largely deviated from the direction perpendicular to the surface of the FPD 2. X-ray imaging in a state where the FPD 2 and the X-ray generator 1 do not face each other with high accuracy results in oblique X-ray insertion and re-imaging. Therefore, in the present embodiment, the X-ray imaging system is easily set up by detecting the postures of the X-ray generator 1 and the FPD 2 and communicating between the apparatuses.

  In FIG. 1, 4 indicates a communication path between the FPD 2 and the control unit 3, and 5 indicates a communication path between the X-ray generation unit 1 and the control unit 3. In some cases, the FPD 2 and the X-ray generator 1 are communicating with each other. Such synchronization signal communication will be described with reference to FIG. FIG. 2 is a timing chart showing operations of the control unit 3, the FPD 2, and the X-ray generation unit 1.

  When an imaging request is issued from the control unit 3 (TC201), the FPD 2 prepares for imaging (TC202). In some cases, preparation for photographing is not performed (not shown). When the preparation for imaging is completed, the FPD 2 is ready for X-ray imaging (TC203). For safety reasons, when the exposure switch 61 of the operation input unit 6 is pressed when the FPD 2 is not in an X-ray imaging enabled state (TC204), X-ray exposure is not permitted (TC205). The FPD 2 in the X-ray imaging ready state converts the X-rays (TC207) exposed from the X-ray generation unit 1 by pressing the exposure switch (TC206) into charges as described above and stores (TC208). Thereafter, charge due to dark current for correcting the image is accumulated (TC209). In some cases, charge accumulation due to dark current is not performed. When the depression of the exposure switch is finished, the FPD 2 finishes the X-ray radiographable state (TC203). The X-ray imaging data and dark current data acquired by the TC 208 and the TC 209 are transferred to the control unit 3 and displayed as an image (TC210). At the time of image display, there are a case where the calculation is performed after the calculation based on the X-ray imaging data and dark current data acquired by the TC 208 and TC 209 in the FPD 2, and the calculation is performed inside the control unit 3.

  Note that the X-ray generation unit 1 needs a function that allows the photographer to make various settings (tube voltage, tube current, product of tube current and exposure time) according to the imaging conditions. In addition, in order to perform a plurality of imaging under the same imaging conditions, when X-ray imaging is completed and the X-ray image is stored, information on the actually exposed radiation and the captured image are stored in association with each other. It is desirable to do. Accordingly, in the present embodiment, information regarding X-ray irradiation conditions such as imaging conditions set in the X-ray generation unit 1 and actually used imaging conditions is communicated between the X-ray generation unit 1 and the control unit 3. To do.

  In addition, when the X-ray generator is driven by a battery, it is known that if a discharge requiring a large amount of power such as X-ray exposure is performed in a state where the remaining amount of the battery is low, the life of the battery is remarkably reduced. It has been. In the case of a system that discharges a large amount of power, it is important to properly monitor the remaining battery level and use the information to operate the system. Therefore, in the present embodiment, information regarding the battery such as the remaining battery level is communicated between the X-ray generation unit 1 and the control unit 3. As a result, the system can be operated according to the remaining battery level.

  As described above, in the present embodiment, various communications are performed between the constituent elements of the apparatuses constituting the X-ray imaging system 10. In such a system, conventionally, each component of the apparatus is generally connected by a separate wired communication cable. However, the system connected by the cable has caused restrictions on the installation of the X-ray generator 1 and the imaging environment. In addition, since the communication interface is different for each component, installation and setup of a communication path is expensive. Therefore, in the present embodiment, the communication interfaces of a plurality of components are aggregated, signals are converted into a common communication interface, and communication is performed with other devices that configure the X-ray imaging system 10 using the common communication interface. This greatly reduces the time and labor required for setting up the system, and reduces restrictions on the installation of the X-ray generator 1 and the imaging environment.

(System configuration)
3A to 3D are block diagrams illustrating functional configuration examples of the devices of the X-ray generation unit 1, the FPD 2, and the control unit 3 included in the X-ray imaging system 10. The X-ray generation unit 1 includes a first communication unit 108, the FPD 2 includes a second communication unit 205, and the control unit 3 includes a third communication unit 301. 3A, the X-ray generation unit 1 and the control unit 3 are connected via the first communication unit 108 and the third communication unit 301 through the wireless path 5, and the FPD 2 and the control unit 3 are respectively connected to the second communication unit 205. And the third communication unit 301 through the wireless path 4. In the configuration of FIG. 3B, the X-ray generation unit 1 and the FPD 2 are connected by the wireless path 7 through the first communication unit 108 and the second communication unit 205, respectively, and the FPD 2 and the control unit 3 are connected with the second communication unit 205, respectively. A wireless path 4 is connected through the third communication unit 301. In the configuration of FIG. 3C, the X-ray generation unit 1 and the FPD 2 are connected by the wireless path 7 through the first communication unit 108 and the second communication unit 205, respectively, and the X-ray generation unit 1 and the control unit 3 are respectively connected to the first communication unit 108 and the second communication unit 205. The communication unit 108 and the third communication unit 301 are connected via the wireless path 5. In the configuration of FIG. 3D, the X-ray generation unit 1, the FPD 2, and the control unit 3 are connected to each other by wireless paths 7, 4, and 5 through communication units 108, 205, and 301, respectively. The system configuration shown in FIGS. 3A to 3D can be appropriately selected according to the use and purpose of the photographer.

  As illustrated in FIGS. 3A to 3D, the X-ray generation unit 1 includes an interface conversion unit 109 that aggregates communication interfaces 103 to 107 and converts the communication interfaces into a common communication interface. The X-ray generation unit 1 communicates with other devices such as the FPD 2 and the control unit 3 through the common communication interface converted by the interface conversion unit 109. In this way, the X-ray generation unit 1 converts the signal format of communication by the constituent elements of the X-ray generation unit 1 to obtain a predetermined signal format with other devices constituting the X-ray imaging system 10. Communicate with. In the present embodiment, the wireless paths 4, 5, and 7 are realized by a wireless LAN, but other wireless communication methods such as Bluetooth (registered trademark) may be used. Communication between the X-ray generator 1, the FPD 2, and the controller 3 is not limited to the wireless communication method, and may be performed by wired communication means such as Ethernet (registered trademark) or an optical fiber cable. In addition, a common interface is applied to the communication path between the X-ray generator 1 and the FPD 2, the communication path between the FPD 2 and the controller 3, and the communication path between the controller 3 and the X-ray generator 1. Alternatively, a separate interface may be used.

  The X-ray generator 1 is often driven by an internal power source (battery) 102 in a portable X-ray imaging system such as home imaging as described above. The internal power supply 102 is an internal power supply monitoring unit that monitors the remaining amount of the battery remaining in the internal power supply 102 or the potential difference between the cells when the internal power supply 102 is an internal power supply having a plurality of cells (not shown). 103. The interface of the internal power supply monitoring unit 103 is, for example, a CAN (Controller Area Network), and is selected according to the purpose.

  In the case of home imaging or the like, it is necessary to make the X-ray generator 1 face the patient firmly and accurately. To that end, it is necessary to detect how much the X-ray generator 1 is inclined. . The first posture detection unit 104 is, for example, a three-axis gyro sensor, and detects how much the X-ray generation unit 1 is tilted. The output interface from the first attitude detection unit is, for example, SPI or I2C, but is selected according to the purpose.

  When performing X-ray imaging, the imaging conditions are usually set according to the body part to be imaged. Such imaging conditions include tube voltage (kV), tube current (mA), exposure time (s), or product of tube current and exposure time (mAs). For example, a tube voltage of 100 kV, a tube current of 20 mA, and an exposure time of 0.2 s are set for chest imaging, and a tube voltage of 80 kV, a tube current of 100 mA, an exposure time of 0.2 s, and the like are set for abdominal imaging. Therefore, the X-ray generator 1 has a function that can set imaging conditions. In the case of FIG. 3A, the condition setting unit 105 is input to the condition input unit 302 of the control unit 3 and received via the third communication unit 301, the communication path 5, the first communication unit 108, and the interface conversion unit 109. The imaging conditions are set in the X-ray generator 1. 3B to 3D, information that reaches the condition setting unit 105 through each communication path is reflected in the X-ray generation unit 1. In this embodiment, the condition input unit 302 is provided in the control unit 3, but may be provided in the FPD 2 or the X-ray generation unit 1. When the condition input unit 302 is provided in the FPD 2, the condition setting unit 105 is connected to the second communication unit 205, and when the condition input unit 302 is provided in the X-ray generation unit 1, The condition input unit 302 is directly connected (not shown). In that case, communication between the condition setting unit 105 and the condition input unit 302 is performed by, for example, Ethernet.

  In addition, the photographer can set the exposure conditions using the condition input unit 302. However, when leaving an imaging record, both the set information and the information of the actually exposed X-ray are recorded. It is hoped that it can be done. Therefore, in this embodiment, when the information acquisition unit 106 acquires information on the X-rays actually exposed, the information is transmitted to the control unit 3 and stored in the storage unit 303. In the example of FIG. 3A, the acquired information is stored in the storage unit 303 in association with an X-ray image to be described later via the interface conversion unit 109, the first communication unit 108, the third communication unit 301, and the related storage unit 304. Is done. Such X-ray information includes X-ray tube voltage (kV), tube current (mA), exposure time (s), or product of tube current and exposure time (mAs). Here, the information input to the condition input unit 302 may also be associated and stored at the same time. An interface of information from the information acquisition unit 106 is, for example, Ethernet.

  In imaging using the FPD 2, it is necessary to synchronize the timing of X-ray exposure and charge accumulation in the photoelectric conversion element as described above (synchronization). Therefore, the X-ray generation unit 1 includes an exposure permission unit 107 that determines whether or not exposure is possible depending on the state of the FPD 2. In the case of FIG. 3A, the exposure permission signal generation unit 202 of the FPD 2 outputs an exposure permission signal in response to the FPD 2 being ready for charge accumulation, and the X-ray generation unit 1 of the X-ray generation unit 1 via the control unit 3. The exposure permission unit 107 is notified. That is, the exposure permission unit 107 sends the exposure permission signal from the exposure permission signal generation unit 202 to the second communication unit 205, the communication path 4, the third communication unit 301, the communication path 5, and the first communication unit. 108, received through the interface conversion unit 109. The exposure permission unit 107 exposes the exposure from the exposure permission signal generation unit 202 in order to exclude the risk that the FPD 2 is exposed in a state where the charge accumulation is not ready and an invalid image cannot be acquired. As long as the permission signal is not received, the X-ray generator 1 is configured so as not to be exposed to X-rays. The signal interface to the exposure permission signal generation unit 202 and the exposure permission unit 107 is, for example, LVDS. Provide a function (timeout) for canceling the exposure permission signal to the exposure permission unit 107 when X-rays are not irradiated even after a predetermined time has elapsed since the input of the exposure permission signal to the exposure permission unit 107 Also good. Further, as shown in FIGS. 3B to 3D, the exposure permission signal is not transmitted via the control unit 3 when the first communication unit 108 and the second communication unit 205 can directly communicate with each other. Can be directly transmitted from the communication unit 205 to the first communication unit 108.

  As described above, the information interfaces to the internal power supply monitoring unit 103, the first attitude detection unit 104, the condition setting unit 105, the information acquisition unit 106, and the exposure permission unit 107 are often different. When these are made wireless one by one, a function of converting to wireless is required for each interface. The interface conversion unit 109 has a function of consolidating the interfaces and converting the interfaces into a single interface suitable for wireless communication. The signal sent to the interface conversion unit 109 includes a signal destination and an interface. The interface conversion unit 109 decodes the signal, converts it to an optimum interface, and delivers information to a desired destination. As a result, a plurality of interfaces can be easily handled without having a complicated communication path.

  In the case of the above-described shooting at the half sitting position at home shooting, the detection surface of the FPD 2 is not horizontal with respect to the ground. For this reason, when the FPD 2 and the X-ray generator 1 are opposed to each other in this state, it is useful to detect the postures of both. Therefore, the FPD 2 is also provided with a second posture detection unit 204 that detects the posture of the FPD 2. The 2nd attitude | position detection part 204 is a 3-axis gyro sensor, for example. The second posture detection unit 204 is preferably the same element as the first posture detection unit 104, but may be different. The output interface from the second posture detection unit 204 is, for example, SPI or I2C, but is selected according to the purpose. The posture information of the X-ray generation unit 1 detected by the first posture detection unit 104 and the posture information of the FPD 2 detected by the second posture detection unit 204 are transmitted to the control unit 3, and the X-ray generation unit Information indicating the relationship between the posture 1 and the posture of the FPD 2 is displayed on the display unit 305. As for the postures of the X-ray generation unit 1 and the FPD 2, for example, display control of the other posture relative to one posture can be performed to simplify the alignment of the apparatus. Thereby, it becomes easy to make the FPD 2 and the X-ray generator 1 face each other firmly and accurately even in imaging such as a half-sitting position. Note that, in order to prevent re-imaging due to entry, control may be performed so that the exposure permission signal is not generated from the exposure permission signal generation unit 202 when the FPD 2 and the X-ray generation unit 1 are not opposed to each other. When the FPD 2 and the X-ray generation unit 1 face each other with a desired accuracy, the control unit 3 generates an alignment completion flag. The fact that the FPD 2 and the X-ray generation unit 1 face each other is because, for example, the difference in posture angle transmitted from the first posture detection unit 104 and the second posture detection unit 204 is equal to or less than a predetermined range. Can be determined. By displaying the fact on the display unit 305 in response to the occurrence of the alignment completion flag, it is possible to further facilitate the alignment (alignment) of the operator's device.

  The shooting setting unit 203 has a function of determining a shooting method of the FPD 2 in accordance with information from the condition input unit 302. For example, in the case of imaging with a long exposure time, settings are made such that the charge accumulation of the FPD 2 does not end before the X-ray exposure ends.

  The image acquisition unit 201 has a function of accumulating X-rays emitted from the X-ray generation unit 1 as electric charges and acquiring an image by reading the amount for each pixel. Thereby, FPD2 operate | moves as a detector provided with the several detection element which acquires an electrical signal, when an X-ray is irradiated. In the case of FIG. 3A, the image acquired by the image acquisition unit 201 is transmitted to the related storage unit 304, the storage unit 303, and the display unit 305 through the second communication unit 205, the communication path 4, and the third communication unit 301. The The association storage unit 304 stores the information from the condition setting unit 105 and the condition input unit 302 and the image from the image acquisition unit 201 in association with each other as described above. When shooting at home, it is often taken periodically. Therefore, in order to increase the reproducibility at the next shooting by recording shooting conditions (such as the angle of the FPD 2), information from the first posture detection unit and the second posture detection unit is also stored in association with each other. May be. In addition to displaying the image from the image acquisition unit 201, the display unit 305 can be used for confirmation or the like by displaying the conditions of the current photographing. In order to enhance convenience, the display unit 305 may include a touch pad and include a condition input unit 302.

(System operation)
FIG. 4 is a flowchart showing a procedure of processing executed in the X-ray imaging system according to the present embodiment. Hereinafter, the operation of the X-ray imaging system 10 will be described with reference to FIGS. 3A to 3D and FIG. 4.

  When starting the operation, the X-ray imaging system 10 first acquires the remaining amount of the internal power supply 102 of the X-ray generation unit 1 using the internal power supply monitoring unit 103 and notifies the control unit 3 (S401). The operator inputs the X-ray exposure condition of the part to be imaged from the condition input unit 302 to the control unit 3 (S402). Specifically, the tube voltage (kV), tube current (mA), exposure time (s), product of tube current and exposure time (mAs), or the like is input.

  The control unit 3 determines whether exposure can actually be performed under the input exposure conditions and the remaining amount of the internal power supply 102 (S403). This determination is made, for example, by comparing the X-ray irradiation conditions such as the tube voltage (kV), tube current (mA), and exposure time (s) of the X-ray tube, and the remaining battery level necessary for image capturing under the conditions. This can be done by preparing a table showing the correspondence and referring to the table. If it is determined that exposure is not possible (NO in S403), the imaging is terminated. If it is determined that exposure is possible (YES in S403), the FPD 2 starts preparation for X-ray imaging (S404).

  Further, the operator starts alignment of the apparatus so that the FPD 2 and the X-ray generation unit 1 face each other. At this time, information of the first posture detection unit 104 and the second posture detection unit 204 is sequentially sent to the control unit 3 (S405), and the postures of the FPD 2 and the X-ray generation unit 1 are relatively displayed on the display unit 305. Is displayed. The operator performs alignment between the FPD 2 and the X-ray generator 1 while referring to the relatively displayed postures of the FPD 2 and the X-ray generator 1.

  Next, it is determined whether or not there is an X-ray imaging request by the operator (S406). If there is no X-ray imaging request, the X-ray imaging system 10 stands by until it is present (NO in S406). If there is an X-ray imaging request (YES in S406), it is confirmed whether the FPD 2 is ready for imaging (S407). If it is not ready, it waits until it is ready (NO in S407). When the FPD 2 is ready for photographing (YES in S407), the control unit determines whether there is an alignment completion flag (S408).

  In X-ray imaging, it has been described that the facing of the FPD 2 and the X-ray generation unit 1 is important. However, exposure may be performed in a state where they are not facing each other depending on the imaging technique. In order to make this possible, it is determined whether or not the X-ray generator 1 and the FPD 2 are opposed to each other, and the time during which imaging is permitted is controlled after the preparation for imaging is completed according to the determination result. Specifically, in the X-ray imaging system 10 according to the present embodiment, the control is divided between the case where there is an alignment completion flag (YES in S408) and the case where there is no alignment completion flag (NO in S408). As described above, the alignment completion flag is generated in response to the FPD 2 and the X-ray generation unit 1 facing each other with a predetermined accuracy.

  If there is an alignment completion flag (YES in S408), the timeout timer 1 is first started (S409). It is confirmed whether or not the preset timeout time 1 has elapsed (S410), and if the timeout time 1 has elapsed without an exposure request, shooting is terminated (NO in S411, YES in S410). If there is an exposure request from the operator within the timeout time 1 (NO in S410) (YES in S411), X-ray imaging is performed by exposing X-rays (S418). Then, the FPD 2 transmits the X-ray image to the control unit 3 (S418).

  If there is no alignment completion flag (NO in S408), processing is performed assuming that the FPD 2 and the X-ray generation unit 1 are not opposed to each other. First, the timeout timer 2 is started (S413), and the transmission of posture information from the FPD 2 and the X-ray generator 1 is stopped (S414). Next, it is confirmed whether or not the preset timeout time 2 has passed (S415). If the timeout time 2 has passed without an exposure request, the shooting is terminated (NO in S416, YES in S415). ). If there is an exposure request from the operator within the time-out time 2 (NO in S415) (YES in S416), X-ray imaging is performed by exposing X-rays (S417). Then, the FPD 2 transmits the X-ray image to the control unit 3 (S418). The time-out time 2 is a time until the exposure is performed in a state where the X-ray generation unit 1 and the FPD 2 are not opposed to each other. For this reason, it is desirable to set the time shorter than the time-out time 1 for the purpose of preventing the exposure of extra radiation due to re-imaging by the entry, but it may be set to the same value as the time-out time 1 according to the operator's request or the like.

  When the control unit 3 receives the X-ray image from the FPD 2 in S <b> 418, the information acquisition unit 106 transmits information on the actually exposed X-rays to the control unit 3. Further, the first posture detection unit 104 transmits the current posture information of the X-ray generation unit 1 and the second posture detection unit 204 transmits the current posture information of the FPD 2 to the control unit 3 (S419). The control unit 3 uses the association storage unit 304 to store the image received in S418, the information of the exposed X-ray received in S419, the posture information of the X-ray generation unit 1, and the posture information of the FPD 2. The data are stored in the storage unit 303 in association with each other.

  Next, it is determined based on an operator's instruction or the like whether or not to end shooting (S421). If not completed (NO in S421), the process returns to S401, and the above-described processing is repeated for the next shooting. When the process is to be ended (YES in S421), the internal power supply monitoring unit 103 of the X-ray generation unit 1 notifies the control unit 3 of the remaining internal power supply of the internal power supply 102 (S422), and the process ends.

  Note that when the components 103 to 107 of the X-ray generation unit 1 communicate with the FPD 2 and the control unit 3 in the above processing, information is transmitted and received through interface conversion in the interface conversion unit 109.

  Specifically, for example, when the internal power supply monitoring unit 103 that is a component of the X-ray generation unit 1 transmits information on the remaining battery level to the control unit 3 in S401, the internal power supply monitoring unit 103 includes a destination of information. The signal is transmitted to the interface conversion unit 109. This destination includes identification information of an apparatus (in this case, the control unit 3) constituting the X-ray imaging system 10, and further, information for identifying a component (for example, the related storage unit 304) of the apparatus. Etc. may be included. When the interface conversion unit 109 receives a signal from the internal power supply monitoring unit 103, the interface conversion unit 109 analyzes the signal and acquires an information destination and transmission information. Then, the signal to be transmitted is converted in accordance with a communication protocol for communicating with an external device. In this embodiment, since a wireless LAN is used for communication between the X-ray generation unit 1, the FPD 2, and the control unit 3, the IP address assigned to the control unit 3 is set as the destination address, and the remaining battery information Is generated in the payload portion. Then, the first communication unit 108 sends out the IP packet.

  Also, when information is transmitted from an external device to the components of the X-ray generation unit 1, the interface conversion unit 109 performs interface conversion processing. For example, consider a case where imaging condition information is transmitted from the condition input unit 302 of the control unit 3 to the condition setting unit 105 of the X-ray generation unit 1. In this case, the third communication unit uses the IP address of the X-ray generation unit 1 as the destination address, and provides information on imaging conditions, identification information of the constituent elements of the X-ray generation unit 1 (in this case, the condition setting unit 105), and the like. The IP packet included in the payload part is transmitted. When the first communication unit 108 receives this IP packet, the interface conversion unit 109 analyzes the payload portion and obtains an information destination and received information. And a signal is produced | generated according to the communication interface of the component of the X-ray generation part 1. FIG. When the condition setting unit 105 and the interface conversion unit 109 are connected via Ethernet, an IP packet is generated that uses the IP address assigned to the condition setting unit 105 as a destination address and includes information on imaging conditions in the payload portion. Then, the IP packet is transmitted to the information acquisition unit 106 via Ethernet.

As described above, in the configuration of the present embodiment, the X-ray generation unit 1 includes the constituent elements 103 to 107 of the X-ray generation unit 1 and other devices (FPD2, control unit 3) that configure the X-ray imaging apparatus. Etc.) using a common communication interface. That is, the X-ray generation unit 1 converts signals between different communication interfaces of a plurality of components and a common communication interface, and other devices configuring the X-ray imaging apparatus by the common communication interface. connect. For this reason, it is possible to greatly reduce the labor of connection of communication paths and communication settings between the components of the apparatus constituting the X-ray imaging apparatus. Furthermore, even if the communication path is realized by a wired cable, the number of cables can be reduced, so that it is possible to greatly reduce the restrictions on the environment in which photographing can be performed.
Therefore, according to the present embodiment, it is possible to provide a radiation imaging apparatus that can be operated safely and conveniently with simple communication.

(Other embodiments)
In the above embodiment, when transmitting information from the component of the X-ray generation unit 1 to another device, the component transmits the identification information of the destination. However, the component transmits the information of the destination. The destination may be determined in the interface conversion unit 109 without transmitting. For example, when the destination is known in advance, the interface conversion unit 109 can transmit information toward the predetermined destination without the component specifying the destination. Further, for example, the interface conversion unit 109 can distribute information transmission destinations according to the progress of processing. In this way, by configuring the interface conversion unit 109 to centrally manage information destinations, it is not necessary to set communication destinations for each component, and communication settings can be set more easily. Is possible.

  In the above-described embodiment, the configuration in which only the X-ray generation unit 1 includes the interface conversion unit has been described. However, the interface conversion unit may be provided in other devices such as the FPD 2 and the control unit 3.

  FIG. 5 is a diagram illustrating information exchanged between the X-ray generation apparatus, the X-ray detector, and the imaging control apparatus. The X-ray imaging system according to the embodiment includes, for example, an X-ray generation device 501, an X-ray detector 502, and an imaging control device 503. The imaging control device 503 includes a display unit 504 and a control unit 505. The control unit 505 has at least one CPU, for example, and controls the operation of the imaging control device 503 in an integrated manner.

  The imaging control apparatus 503 is connected to the hospital network by a communication circuit, for example, and receives an X-ray imaging order from an external radiation information system (RIS). The imaging order includes information on the subject, imaging site, imaging position, and imaging direction. It is also possible to include information on resolution and irradiation conditions. When the RIS is not used, the subject information is obtained by reading the identification information certification card worn by the subject using an attached barcode reader or the like. Alternatively, the shooting control device 503 generates various information corresponding to the shooting order.

  With the subject, the X-ray generator 501 and the X-ray detector 502 positioned under conditions corresponding to the imaging order, the X-ray generator 501 generates X-rays under irradiation conditions corresponding to the imaging order. The X-ray detector 502 obtains X-ray image data corresponding to the imaging order by detecting X-rays with an X-ray sensor. The imaging control apparatus 503 receives X-ray image data through a communication circuit. Further, the imaging control apparatus 503 performs diagnostic image processing such as sensor characteristic correction processing such as offset correction and gain correction, gradation processing and noise reduction processing on the received X-ray image data by the CPU or GPU. Then, the imaging control device 503 displays the image processed image on the display unit 504. In response to an operation input from the operation unit, the imaging control device 503 performs image processing correction and region extraction for diagnosis.

  The X-ray generation device 501 transmits the irradiation conditions for X-ray irradiation to the imaging control device 503. Thereafter, the imaging control device 503 transfers the image data subjected to the necessary process correction by the communication circuit together with the irradiation condition to an image management system (PACS) that is a system for storing and transmitting / receiving images. The image stored in the PACS is used for diagnosis by an interpreting doctor. Implementation information including the implementation details of imaging such as dose information is transmitted by the imaging control device 503 to the RIS or the hospital information system (HIS). Thereby, the accounting process regarding the subject is performed.

  The X-ray generation apparatus 501 transmits to the imaging control apparatus 503 the posture information of the X-ray tube and the execution information that is the X-ray irradiation condition used for imaging. Conversely, the imaging control device 503 transmits imaging conditions such as an irradiation condition and a frame rate to the X-ray generation device 501. The X-ray generator 501 and the X-ray detector 502 communicate operation timing synchronization signals. This communication is a synchronous communication for allowing the X-ray irradiation period to be included in the period in which the X-ray detector 502 is in a charge accumulation state. If the X-ray detector 502 supports asynchronous imaging and is in an imaging mode in which asynchronous imaging is performed, the synchronous communication is not necessary.

  The imaging control apparatus 503 instructs the X-ray detector 502 to specify a drive mode and control the operation. The drive mode instruction includes, for example, the length of the period during which the charge is accumulated and the selection of the above-described synchronous mode and asynchronous mode. In the case of moving image shooting, information on the image signal readout range corresponding to the frame rate and irradiation field may be included. As for the operation control, for example, there is power control, and there is control of energization / non-energization to the X-ray sensor and control of power states to other parts. The X-ray detector 502 performs imaging and generation of X-ray image data according to the instructed driving mode and operation control, and transmits this to the imaging control apparatus 503. In addition, state information of the X-ray detector 502 is transmitted. Such state information is displayed on the display unit 504 by the imaging control device 503.

  FIG. 6 is a diagram illustrating an embodiment for realizing communication between devices included in the X-ray imaging system. A communication relay device 601 is connected to the X-ray generator 501, and the communication relay device 601 and the imaging control device 503 are connected to each other by LAN cables 607 and 608 via the router 602. The X-ray detector 502 has a communication circuit 604 including an antenna. The X-ray detector 502 is wirelessly connected to other devices via the communication circuit 604 and a wireless AP 603 connected to the router via a LAN cable 609.

  The wireless AP 603 is a wireless communication circuit for the X-ray generator 501 to communicate with the X-ray detector 502. In the example illustrated in FIG. 6, the imaging control device 503 communicates with the communication relay device 601 via the router 602, but may perform communication via the wireless AP 603. When the X-ray generator 501 and the X-ray detector 502 do not perform synchronous communication, there is a possibility that communication between the X-ray generator 501 and the X-ray detector 502 is not performed. In addition, when it is not necessary to exchange implementation information and imaging conditions, there is a possibility that communication between the X-ray generation apparatus 501 and the imaging control apparatus 503 is not performed. Here, the wireless AP 603 can connect a wired cable instead of wireless communication and perform wired communication with the X-ray detector 502. However, the wireless communication is advantageous in that it is not bothered by the cable.

  The communication relay device 601 has a first connector 6013 for connecting the RS232C cable 605 with the X-ray generator 501 and a second connector for connecting the dedicated cable 606 with the X-ray generator 501. And a connector 6014. Thereby, the communication relay apparatus 601 and the X-ray generator 501 are connected. The RS232C cable 605 is a communication cable for mainly mediating communication of signals related to X-ray irradiation conditions such as implementation information and transmitting the signals to the imaging control apparatus 503. In addition, it may be used for communication of a signal indicating the state of the X-ray generator. In another embodiment, a LAN cable may be used depending on the type of the X-ray generator 501, so the communication relay device 601 according to one embodiment has a LAN cable connector. Here, the dedicated line cable 606 is used as an interface with the film changer, and has, for example, a plurality of signal lines including input and output signal lines as viewed from the X-ray generator 501. The dedicated line cable 606 mediates communication of signals related to the generation timing of X-rays with the X-ray generator 501.

  The signal line from the irradiation switch and the input cable from the dedicated cable 606 are connected to the input terminal of the AND circuit. The output terminal of the AND circuit is connected to a control circuit for instructing the trigger for starting X-ray irradiation, whereby the X-ray irradiation timing can be controlled by a signal from the communication relay device 601 side. In addition, the signal line from the irradiation switch is connected to the signal line on the output side of the dedicated line cable before being input to the AND circuit. Thereby, the communication relay apparatus 601 can transmit the signal from an irradiation switch to another apparatus, and can use it for control.

  The communication relay apparatus 601 includes a first converter 6011 connected to the connector 6013 of the RS232C cable 605, a second converter 6012 connected to the connector 6014 of the dedicated cable 606, and a timing control unit 6015. . The timing control unit 6015 or the communication relay device 601 has a connector for connecting to the LAN cable 607, thereby connecting to the router 602. The first converter 6011 converts the signal in the RS232C format into another format and supplies the converted signal to the timing control unit 6015. The second converter 6012 converts the dedicated line format signal into another format and supplies it to the timing control unit 6015. The first converter 6011, the second converter 6012, and the timing control unit 6015 may be integrally formed.

  The timing control unit 6015 has a function of relaying information exchange between the X-ray generator 501 and other devices. The timing control unit 6015 receives a first signal indicating that the X-ray irradiation switch has been pressed, starts a timer, and uses the first signal as it is or a signal corresponding to the first signal. Transmit to the X-ray detector 502. The X-ray detector 502 performs a reset operation of the X-ray sensor in response to the reception of the signal, and makes the X-ray sensor transition to a charge accumulation enabled state. In response to the transition to the state, the X-ray detector 502 transmits a second signal to the communication relay device 601. The communication relay device 601 that has received the second signal determines whether or not the timer count is within a predetermined timeout period. If it is within the time-out period, the second signal is transmitted as it is or a signal corresponding to the second signal is transmitted to the X-ray generator 501. Thereby, generation of X-rays is started. If the timeout time is exceeded, no signal is transmitted to the X-ray generator 501. In this case, generation of X-rays is not started. The timeout time is a time for determining whether or not the X-ray irradiation period falls within the accumulation period, and takes into account a communication delay in wireless communication or a delay in X-ray generation in the X-ray generation unit. Determined. In this way, the timing control unit 6015 can synchronize the operation timing by synchronous communication, and can realize X-ray imaging that does not cause unnecessary exposure.

  In this way, by connecting the cables 605 and 606 of the X-ray generation apparatus 501 to the connectors 6013 and 6014 of the communication relay apparatus 601, communication in the X-ray imaging system is facilitated, and the efficiency of information generated by each apparatus Sharing and interoperability between devices in the system can be improved. In particular, when a plurality of cables need to be connected to the X-ray generator 501, it is only necessary to connect to a single device called the communication relay device 601. Therefore, a digital X-ray imaging system having an X-ray sensor is provided. The time and labor required for installation can be reduced.

  The timing control unit 6015 monitors input and output from the RS232C cable 605 and the dedicated cable 606, and restricts relaying as necessary. In one embodiment, the timing control unit 6015 causes the signal received via the second connector 6014 to be transmitted to the communication circuit in preference to the signal received via the first connector 6013. For example, the timing control unit 6015 receives the irradiation switch signal from the dedicated line cable 606 when receiving the irradiation switch signal from the dedicated line cable 606 during or immediately after receiving the implementation information from the RS232C cable 605. First, the data is transmitted via the LAN cable 607. If the transmission of the execution information has been started, the transmission is interrupted and the transmission of the irradiation switch signal is started. In this way, it is possible to give priority to transmission of a signal having a higher priority, that is, a signal indicating that X-ray imaging is started. In addition, the delay in transmission can reduce the delay in shooting timing, and hence the possibility of re-shooting due to this.

  In another example, the timing control unit 6015 receives the irradiation switch signal from the leased line cable 606 during or immediately after the reception of the imaging condition information via the LAN cable 607. The control of transferring the imaging condition information to the X-ray generation apparatus 501 via the RS232C cable 605 is performed without relaying the signal. Under such circumstances, it is highly probable that the shooting conditions have been corrected before and after the irradiation switch is pressed, so the relay switch signal should not be relayed to reduce the possibility of shooting under incorrect conditions. It is a thing. Thereby, the possibility of causing the subject to be exposed unnecessarily can be reduced.

  Alternatively, the timing control unit 6015 always has the latest imaging conditions in preparation for a change in irradiation conditions on the X-ray generation apparatus 501 side, or a change in imaging conditions on the X-ray detector 502 or imaging control apparatus 503 side. A memory for storing is provided. In response to receiving information on imaging conditions different from the imaging conditions from any of the X-ray generator 501, the imaging controller 503, and the X-ray detector 502, the irradiation switch signal is not relayed. Control. Thereby, it is possible to prevent the shooting from being stopped when there is no change in the shooting condition and only information on the same shooting condition as the set shooting condition is communicated.

  Note that it is useful that communication of shooting conditions is performed in combination with the ID of the next shooting to be shot, so that it is not confused with a notification of another shooting condition. For example, assuming that the ID of the next image capturing is 005, and the change of the image capturing condition for ID 005 is triggered, the timing control unit 6015 does not relay the irradiation switch signal. On the other hand, when a change in shooting conditions other than ID005 is triggered, the timing control unit 6015 does not prohibit the relay of the irradiation switch, and transmits the signal of the irradiation switch with priority over the change of the shooting condition. Thus, X-ray imaging can be made more efficient while reducing erroneous exposure.

  FIG. 7 is a diagram showing a modification of the communication relay device. In FIG. 7A, in the communication relay device 701, the timing control unit 7013 relays only the signal from the dedicated line cable 606 and is not connected to the RS232C cable 605. A timing control unit 7013 is integrated with the second converter 6012. Further, each of the first converter 6011 and the timing control unit 7013 is connected to the router 602 via LAN cables 7071 and 7072. In this way, the control can be simplified.

  In FIG. 7B, the communication relay device 702 is configured as a single device including a router 602 and a wireless AP 603. In this case, the imaging control device 503 may be wired to the router 602 or may be wirelessly connected to the wireless AP 603. Note that the router 602 and the wireless AP 603 may be integrally formed. By doing in this way, the merit at the time of installation of an X-ray imaging system further improves. In addition, since the number of units constituting the system can be greatly reduced, there is a great merit when managing and changing the configuration. In addition, by connecting the communication relay device 601 to the X-ray generator, an X-ray generator capable of wireless communication can be obtained. In addition, the router 602 is connected to the X-ray generator 501 via the LAN cable 703. This is because when the (first) posture detection unit 104 is provided on the X-ray generation device 501 side as in the above-described embodiment, a signal from the posture detection unit 104 is transmitted to another device. It is a configuration.

  The communication relay device 704 in FIG. 7C is integrated with a LAN cable 705 that eliminates the RS232C cable 605 and transmits a signal from the attitude detection unit 104.

  FIG. 8 is a diagram illustrating a configuration example of an X-ray imaging system using the X-ray generator 801. The X-ray generator 801 is a type of X-ray generator that does not have an interface for the dedicated cable 606. In this case, communication with the timing control unit 7013 via the dedicated line is not performed, but posture information from the posture detection unit 104 is performed via the LAN cable 703, and communication of shooting conditions and execution information is performed via the RS232C cable 605. Is done through.

  The imaging control device 503 can be configured to have a virtual wireless AP 506 by the control unit 505 and the communication circuit. The control unit 505 depends on whether the system is formed with either the X-ray generator 501 capable of synchronous communication as shown in FIG. 6 or the X-ray generator 801 not capable of synchronous communication as shown in FIG. It is determined whether the communication should be relayed between the wireless AP 603 of the communication relay apparatus 702 or the wireless AP 506 of the imaging control apparatus 503.

  A case where the communication relay device 702 of FIG. 8 is used will be described as an example. When performing X-ray imaging a plurality of times under the control of a certain imaging control device 503 while switching between a plurality of X-ray generation devices, it is convenient to perform communication via the wireless AP 506 of the imaging control device 503. On the other hand, when imaging by one or a plurality of imaging control devices for one X-ray generation device, it is convenient to use the wireless AP 603 on the X-ray generation device side. Therefore, the imaging control device 503 performs control to select a wireless AP and change the network configuration so that an appropriate wireless AP is used according to the situation. For this purpose, the control unit 505 first detects at least one of switching of the X-ray generation apparatus used for imaging and switching of the imaging control apparatus used for imaging. In accordance with the detection result, one of the wireless repeaters of the wireless AP 603 coupled to the X-ray generator 501 and the wireless AP 506 coupled to the imaging control device 503 is replaced with the X-ray detector 502 and the imaging control device 503. As a wireless repeater used to relay communications with Here, the combination refers to both that the wireless AP 603 of another apparatus is connected to the X-ray generation apparatus 501 and that the imaging control apparatus 503 and the wireless AP 506 are integrated.

  Detailed operation will be described. The control unit 505 of the imaging control apparatus 503 determines whether imaging using a plurality of different X-ray generation apparatuses is performed based on the imaging order information. For example, the imaging control apparatus as table information in which the imaging order and the X-ray generation apparatus to be used are associated with each other based on the imaging region, the imaging posture, or each irradiation condition related to the output size of the X-ray generation apparatus. The data is stored in the memory 503. Using such table information, it is determined whether or not it is necessary to switch between a plurality of X-ray generators. Of course, the X-ray generator to be used may be switched in accordance with a user operation input to the operation unit of the imaging control apparatus 503. When it is determined that a plurality of X-ray generation apparatuses are switched to perform imaging in accordance with the above-described determination process or operation input, the control unit 505 of the imaging control apparatus 503 starts network setting. The control unit 505 outputs an instruction for changing the communication settings of the wireless AP 603 and the wireless AP 506 so that the wireless AP 506 relays the communication when the wireless AP 603 relays the communication. The communication circuit of the X-ray detector 502 communicates with the X-ray generation apparatus and the imaging control apparatus 503 through the wireless AP 506 by changing the communication setting.

  Note that the change of the communication setting is desirably performed between a plurality of photographings. For example, it is desirable that the communication setting is not changed at a timing when the user wants to perform X-ray photographing. Therefore, the control unit 505 outputs the above communication setting change instruction when the next X-ray imaging is not triggered even after a predetermined period has elapsed since the previous X-ray irradiation.

  Alternatively, when it is found that a plurality of X-ray generation apparatuses are switched to perform imaging as described above, the control unit 505 displays a message prompting the display unit 504 to switch communication settings such as “Do you want to switch network settings?” Display. At the same time, the control unit 505 displays an “OK button” and a “cancel button” for accepting an instruction to switch. In response to the OK button being pressed by an operation input to the operation unit, the control unit 505 outputs an instruction for changing the communication setting. By doing so, communication settings can be changed at a user-desired timing, so that deterioration in shooting efficiency can be suppressed.

  Furthermore, here, when an imaging control device different from the imaging control device used for imaging so far requests establishment of communication with the X-ray generation device 501, the network configuration is switched to the radio AP of the imaging control device. Therefore, the control unit 505 outputs a communication setting change instruction. In addition to this, the output timing of such instructions is such as turning off the power of the photographing control apparatus used for photographing until now, completion of all received photographing orders, completion of execution of software for photographing control, etc. It may be performed accordingly. By doing in this way, it can be set as the communication setting which respond | corresponds flexibly to the change of a system configuration. In another embodiment, instead of the control unit 505, the timing control unit 7013 of the communication relay device 702 or the X-ray detector 502 may perform this.

  FIG. 9 is a diagram illustrating a hardware configuration example of the X-ray imaging system according to the embodiment. A description of the same components as those described above will be omitted. The X-ray generation apparatus 501 includes an X-ray source 901, an X-ray generation control unit 902, an irradiation switch 903, and a diaphragm 904. The X-ray source 901 has, for example, a rotary type or transmission type anode, and generates X-rays by collision of high-speed electrons. The X-ray generation control unit 902 controls the X-ray intensity, radiation quality, and generation timing by controlling the voltage and current for generating high-speed electrons in the X-ray source 901. An irradiation switch 903 is a switch for controlling the start and period of X-ray irradiation. An FPGA 6016 that operates as a timing control unit is connected to the second converter 6012.

  The X-ray detector 502 includes a pixel array 916, a phosphor 917, a drive circuit 918, a readout circuit 919, a power source 913, a connector 914 for wired connection, a wireless communication circuit including an antenna 915, and these And an imaging control unit 912 that controls the above in an integrated manner. Each of these units is stored in a housing 911. The phosphor 917 is made of a substance such as CsI and converts X-rays into visible light. The drive circuit 918 drives the pixel array 916 to convert each pixel of the pixel array into an accumulation state or a readout state, thereby performing conversion into an X-ray electric signal and output of the obtained electric signal. The readout circuit 919 includes an amplifier and an AD converter, and amplifies the electrical signal output from the pixel array and converts it into a digital value. The obtained digital data is input to the imaging control unit 912. The imaging control unit 912 outputs this as image data via the connector 914 or the antenna 915. The power source 913 has a battery and a DCDC converter, for example, and is a power source for supplying power to each part of the X-ray detector 502. In addition, the imaging control unit 912 includes at least one MPU and controls the operation of each unit of the X-ray detector 502 in an integrated manner.

  The pixel array 916 and the phosphor 917 together constitute an X-ray sensor. The pixel array 916 includes a plurality of photoelectric conversion elements 920, row selection lines 921, column signal lines 922, switching elements 923, and bias lines 924. The plurality of photoelectric conversion elements 920a to 920d are arranged in a matrix, and selection lines 921a and 921b common to the photoelectric conversion elements in each row are connected to the base side of the switching elements 923a to d. In addition, common column signal lines 922a and 922b in the photoelectric conversion elements of the respective columns are connected to the photoelectric conversion elements 920a to 920d through the switching elements 923a to 923d. The photoelectric conversion element 920 and the switching element may be referred to as a pixel.

  The switching elements 923 are collectively turned on and off in units of rows in accordance with the ON voltage and the OFF voltage applied to the row selection line 921 by the drive circuit 918. The photoelectric conversion element 920 accumulates charges in response to the switching element 923 being turned off, and an electric signal corresponding to the accumulated charges is output in response to being turned on. The timing when all the pixels are in the accumulation state may be referred to as “the accumulation state” by the X-ray sensor or X-ray detector 502.

  The imaging control apparatus 503 includes an electronic computer having a CPU 932, a RAM 933, an HDD 934, and a NIC 935, and each unit of the electronic computer is connected to each other via a BUS 936. An operation unit 931 and a display unit 504 are connected to the electronic computer. The HDD 934 of the electronic computer stores a program for operating the electronic computer as the above-described photographing control device 503. When the CPU 932 develops this in the RAM and sequentially executes it, it can function as the photographing control device 503 described above.

  The present invention can also be realized by executing the following processing. That is, software (program) that realizes the functions of the above-described embodiments is supplied to a system or apparatus via a network or various storage media, and a computer (or CPU, MPU, or the like) of the system or apparatus reads the program. It is a process to be executed.

Claims (16)

An X-ray imaging apparatus for obtaining an X-ray image by detecting X-rays emitted from an X-ray generation unit by a detection unit,
The X-ray generator is
Multiple components, each with a different communication interface;
Conversion means for converting a signal between the communication interface of the component and a common communication interface;
An X-ray imaging apparatus comprising: a communication unit that communicates with another apparatus constituting the X-ray imaging apparatus through the common communication interface. The signal input from the component to the conversion means includes identification information that identifies a device that is the destination of the signal,
The X-ray imaging apparatus according to claim 1, wherein the communication unit sends the converted signal to an apparatus identified by the identification information. The signal input from the other device to the communication unit includes identification information for identifying a component of the X-ray generation unit that is the destination of the signal,
The X-ray imaging apparatus according to claim 1, wherein the communication unit sends the input signal to a component identified by the identification information via the conversion unit. The X-ray generation unit includes a detection unit that detects the posture of the X-ray generation unit as the component,
The conversion means converts a signal indicating the attitude of the X-ray generation unit input via the communication interface of the detection unit into the common communication interface format,
The communication means sends out the signal indicating the converted attitude of the X-ray generation unit to the control unit that controls the operations of the X-ray generation unit and the detection unit through the common communication interface. The X-ray imaging apparatus according to claim 1 or 2. The detector is
Means for detecting the posture of the detection unit;
Means for sending a signal indicating the attitude of the detection unit to the control unit;
The X-ray imaging apparatus according to claim 4, wherein the control unit includes a display control unit that displays information indicating a relationship between an attitude of the X-ray generation unit and an attitude of the detection unit on a display unit. . The controller is
Determination means for determining whether or not the X-ray generation unit and the detection unit are opposed to each other based on the posture of the X-ray generation unit and the posture of the detection unit;
The X-ray imaging apparatus according to claim 5, further comprising: a control unit that controls a time during which imaging is permitted after completion of imaging preparation in accordance with a result of determination by the determination unit. The X-ray generator includes, as the component, a monitoring unit that monitors the remaining battery level of an internal power source that drives the X-ray generator,
The converting means converts the signal indicating the remaining battery level input via the communication interface of the monitoring unit into the common communication interface format,
The said communication means sends out the signal which shows the said battery remaining amount to the control part which controls operation | movement of the said X-ray generation part and the said detection part by the said common communication interface. The X-ray imaging apparatus according to 1 or 2.   The X-ray imaging apparatus according to claim 7, wherein the control unit includes a unit that determines whether imaging is possible based on the remaining battery level.   4. The X-ray imaging apparatus according to claim 1, wherein the communication unit communicates a synchronization signal for synchronizing operation with the detection unit through the common communication interface. 5.   In the plurality of components, a setting unit that sets an irradiation condition of X-rays emitted from the X-ray generation unit, and acquisition of information on irradiation conditions of X-rays actually emitted from the X-ray generation unit 4. The X-ray imaging apparatus according to claim 1, wherein at least one of the first and second units is included. 5. An apparatus that constitutes an X-ray imaging apparatus that obtains an X-ray image by a plurality of detection elements that obtain an electrical signal when X-rays are irradiated from an X-ray generation unit,
Multiple components, each with a different communication interface;
Conversion means for converting a signal between the communication interface of the component and a common communication interface;
An apparatus comprising: a communication unit configured to communicate with another apparatus included in the X-ray imaging apparatus through the common communication interface. A first connector for connecting a first cable that mediates communication of signals relating to X-ray irradiation conditions with the X-ray generator;
A second connector for connecting a second cable that mediates communication of signals related to the generation timing of X-rays with the X-ray generation device;
A communication circuit for communicating with at least one of an X-ray detector and an imaging control device;
Control means for transmitting the signal received via the second connector to the communication circuit in preference to the signal received via the first connector;
A communication relay device comprising: A first connector for connecting a first cable that mediates communication of signals relating to X-ray irradiation conditions with the X-ray generator;
A second connector for connecting a second cable that mediates communication of signals related to the generation timing of X-rays with the X-ray generation device;
A wireless communication circuit for wirelessly communicating with either the X-ray detector or the imaging control device;
A communication relay device comprising: A control device for an X-ray imaging system,
Detection means for detecting at least one of switching of an X-ray generator used for imaging or switching of an imaging control device used for imaging;
Depending on the detection result of the detection means, either one of the first wireless relay means coupled to the X-ray generator and the second wireless relay means coupled to the imaging control device is set to X Selecting means for selecting as a wireless repeater used for relaying communication between the line detector and the imaging control device;
A control device comprising: An X-ray imaging apparatus that obtains an X-ray image by a plurality of detection elements that obtain an electrical signal when X-rays are irradiated from an X-ray generation unit,
The X-ray generation unit converts a communication signal format by components of the X-ray generation unit, and communicates with a predetermined signal format with other devices constituting the X-ray imaging apparatus. An X-ray imaging apparatus comprising: A control method of an X-ray imaging apparatus for obtaining an X-ray image by detecting X-rays emitted from an X-ray generation unit by a detection unit,
In the X-ray generator,
A conversion step in which the conversion means converts a signal between the communication interface of the component of the X-ray generation unit and the common communication interface;
A communication step in which a communication means communicates with another apparatus constituting the X-ray imaging apparatus by the common communication interface;
A control method for an X-ray imaging apparatus, comprising:

Images