X-ray imaging system, X-ray imaging method, X-ray imaging control device and program

Abstract

This prevents DXA imaging in unsuitable conditions, thereby preventing unnecessary radiation exposure to the subject. [Solution] The X-ray imaging system (radiography system 100) is an X-ray imaging system capable of both dual-energy X-ray absorption spectroscopy and general radiography, comprising: an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies; a portable X-ray detector (radiation detector 2) that captures X-ray images based on the X-rays irradiated by the X-ray irradiation device; and an X-ray imaging control device (console 3) that controls the capture of X-ray images by the X-ray detector. The X-ray imaging control device (console 3) comprises a discrimination unit (control unit 31) that determines whether the type of X-ray detector is suitable for X-ray imaging by dual-energy X-ray absorption spectroscopy, and a notification unit (display unit 34) that provides notifications based on the discrimination result of the discrimination unit.

Description

Technical Field

[0001] The present invention relates to an X-ray imaging system, an X-ray imaging method, an X-ray imaging control device, and a program.

Background Art

[0002] Conventionally, a bone density measurement device using the dual-energy X-ray absorption measurement method (DXA; Dual-energy X-ray Absorptiometry, hereinafter also referred to as the DXA method) is a dedicated device, and general imaging and bone density measurement are performed using separate devices. Therefore, the patient has to move between the devices, which causes problems such as the burden on the patient due to the movement and the deterioration of the work efficiency of the technician. In addition, it is necessary to prepare separate imaging rooms for general imaging and bone density measurement, which also causes problems such as space and economic burden.

[0003] Therefore, a bone density measurement device using a cassette-type radiation detector (FPD; Flat Panel Detector, hereinafter referred to as FPD) has been proposed (Patent Document 1). As a result, general imaging and bone density measurement can be performed using the same measurement device by replacing the cassette-type FPD. In this case, since the accuracy of deriving the bone density value may decrease depending on the imaging conditions and the imaging state, the derivation accuracy is evaluated and displayed from the imaging conditions and the image after imaging.

Prior Art Documents

Patent Documents

[0004]

Patent Document 1

Summary of the Invention

Problems to be Solved by the Invention

[0005] However, if general radiography and DXA-based bone density measurement are performed using the same measuring device, the device will no longer be a dedicated device for bone density measurement. Therefore, there is a possibility that the user may make a mistake in the imaging method, such as performing general radiography imaging when the order is for bone density measurement. In addition, since cassette-type FPDs are interchangeable, there is a possibility that an FPD unsuitable for bone density testing may be loaded onto the imaging table. Furthermore, depending on the size of the FPD, it may not be possible to acquire an X-ray image of the range necessary for bone density measurement, or depending on the function or performance of the FPD, it may not be able to handle the pulsed irradiation of X-rays or the precision required for bone density measurement, resulting in the inability to perform high-precision bone density measurement imaging.

[0006] Furthermore, if the accuracy of the bone density calculation evaluated and displayed after imaging is insufficient, re-imaging will be required, resulting in unnecessary exposure.

[0007] Therefore, the objective of the present invention is to prevent DXA imaging in conditions unsuitable for DXA imaging, thereby preventing unnecessary radiation exposure to the subject. [Means for solving the problem]

[0008] To solve the above problems, the X-ray imaging system of the present invention is An X-ray imaging system capable of both dual-energy X-ray absorption spectroscopy and general radiography, An X-ray irradiation device that individually irradiates multiple X-rays with different energies, A portable X-ray detector that captures an X-ray image based on the X-rays irradiated by the aforementioned X-ray irradiation device, The system includes an X-ray imaging control device that controls the acquisition of the X-ray image by the X-ray detector, The aforementioned X-ray imaging control device is A determination unit that determines whether the state of the X-ray irradiation apparatus is suitable for X-ray imaging using the dual-energy X-ray absorption measurement method, A notification unit that provides notification based on the determination result of the aforementioned determination unit, It is characterized by being equipped with [the following features]. Furthermore, the X-ray imaging system of the present invention is An X-ray imaging system capable of both dual-energy X-ray absorption spectroscopy and general radiography, An X-ray irradiation device that individually irradiates multiple X-rays with different energies, A portable X-ray detector that captures an X-ray image based on the X-rays irradiated by the aforementioned X-ray irradiation device, The system includes an X-ray imaging control device that controls the acquisition of the X-ray image by the X-ray detector, The aforementioned X-ray imaging control device is A determination unit that determines whether the irradiation conditions of the X-ray irradiation device are suitable for X-ray imaging by the dual-energy X-ray absorption measurement method, A notification unit that provides notification based on the determination result of the aforementioned determination unit, It is characterized by being equipped with [the following features].

[0009] Furthermore, the X-ray imaging method of the present invention is An X-ray imaging method using an X-ray imaging system that enables both dual-energy X-ray absorption spectroscopy and general radiography, comprising: an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies; a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device; and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, wherein the X-ray imaging system is capable of both dual-energy X-ray absorption spectroscopy and general radiography. A determination step to determine whether the state of the X-ray irradiation apparatus is suitable for X-ray imaging by the dual-energy X-ray absorption measurement method, A notification step which provides notification based on the determination result of the aforementioned determination step, It is characterized by including. Furthermore, the X-ray imaging method of the present invention is An X-ray imaging method using an X-ray imaging system that enables both dual-energy X-ray absorption spectroscopy and general radiography, comprising: an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies; a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device; and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, wherein the X-ray imaging system is capable of both dual-energy X-ray absorption spectroscopy and general radiography. A determination step to determine whether the irradiation conditions of the X-ray irradiation device are suitable for X-ray imaging by the dual-energy X-ray absorption measurement method, A notification step which provides notification based on the determination result of the aforementioned determination step, It is characterized by including.

[0010] Furthermore, the program of the present invention, In an X-ray imaging system that includes an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, the computer of the X-ray imaging control device is configured to perform both dual-energy X-ray absorption spectroscopy and general radiography. A determination unit that determines whether the state of the X-ray irradiation apparatus is suitable for X-ray imaging using the dual-energy X-ray absorption measurement method. A notification unit that provides notification based on the determination result of the determination unit, To make it function as such. Furthermore, the program of the present invention, In an X-ray imaging system that includes an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, the computer of the X-ray imaging control device is configured to perform both dual-energy X-ray absorption spectroscopy and general radiography. A determination unit that determines whether the irradiation conditions of the X-ray irradiation apparatus are suitable for X-ray imaging by the dual-energy X-ray absorption measurement method. A notification unit that provides notification based on the determination result of the determination unit, To make it function as such.

[0011] Furthermore, the X-ray imaging control device of the present invention is An X-ray imaging system including an X-ray irradiator capable of individually irradiating a plurality of X-rays with different energies, a portable X-ray detector for capturing an X-ray image based on the X-rays irradiated by the X-ray irradiator, and an X-ray imaging control device for controlling the capture of the X-ray image by the X-ray detector, and capable of X-ray imaging and general imaging by dual-energy X-ray absorptiometry. The X-ray imaging control device in the system is A discrimination unit that discriminates whether the device state of the X-ray irradiator is suitable for X-ray imaging by dual-energy X-ray absorptiometry; A notification unit that performs notification based on the discrimination result of the discrimination unit; Characterized by comprising. Also, the X-ray imaging control device of the present invention is An X-ray imaging system including an X-ray irradiator capable of individually irradiating a plurality of X-rays with different energies, a portable X-ray detector for capturing an X-ray image based on the X-rays irradiated by the X-ray irradiator, and an X-ray imaging control device for controlling the capture of the X-ray image by the X-ray detector, and capable of X-ray imaging and general imaging by dual-energy X-ray absorptiometry. The X-ray imaging control device in the system is A discrimination unit that discriminates whether the irradiation conditions of the X-ray irradiator are suitable for X-ray imaging by dual-energy X-ray absorptiometry; A notification unit that performs notification based on the discrimination result of the discrimination unit; Characterized by comprising.

Advantages of the Invention

[0012] According to the present invention, it is possible to prevent X-ray imaging by the DXA method in a state not suitable for X-ray imaging by the DXA method, and prevent unnecessary exposure of the subject.

Brief Description of the Drawings

[0013] [Figure 1] It is a block diagram showing a radiation imaging system according to an embodiment of the present invention. [Figure 2] It is a schematic diagram showing a configuration example of a radiation generator and a radiation detector. [Figure 3]This is a block diagram representing the console of a radiography system. [Figure 4] This flowchart illustrates the DXA method used by the console to determine whether or not imaging is possible. [Figure 5] This is a diagram showing a management table for shooting methods. [Figure 6] This figure shows the FPD individual information management table. [Figure 7] This is a schematic diagram (horizontal view) of a supine radiography table used for general radiography. [Figure 8] This is a schematic diagram (horizontal view) of a supine imaging table compatible with DXA. [Figure 9] This is a schematic diagram (horizontal view) of a supine imaging table compatible with DXA. [Figure 10] This is a schematic diagram (horizontal view) of a supine imaging table compatible with DXA. [Figure 11] This is a schematic diagram (perpendicular view) of a supine imaging table compatible with DXA. [Figure 12] This is a schematic diagram (perpendicular view) of a supine imaging table compatible with DXA. [Figure 13] This is a schematic diagram (perpendicular view) of a supine imaging table compatible with DXA. [Figure 14] This is a schematic diagram (perpendicular view) of a supine imaging table compatible with DXA. [Figure 15] This is a schematic diagram (perpendicular view) of a supine imaging table compatible with DXA. [Figure 16] This is a schematic diagram (perpendicular view) of a supine imaging table compatible with DXA. [Figure 17] This is a schematic diagram (perpendicular view) of a supine imaging table compatible with DXA. [Figure 18] This is a schematic diagram (perpendicular view) of a supine imaging table compatible with DXA. [Modes for carrying out the invention]

[0014] The following describes a radiography system according to one embodiment of the present invention with reference to the drawings. However, the scope of the present invention is not limited to the embodiments and drawings described below. The radiography system of this embodiment is capable of not only X-ray imaging using dual-energy X-ray absorptiometry (DXA) but also general radiography. DXA is a method that uses two types of radiation (high kV and low kV) to distinguish between bone and other soft tissues, allowing only the bone components to be measured. Furthermore, general radiography refers to still image capture using a single type of radiation.

[0015] First, the schematic configuration of the radiography system 100 according to this embodiment will be described. Figure 1 is a block diagram representing the radiography system 100.

[0016] As shown in Figure 1, the radiography system 100 of this embodiment includes a radiation generator 1, a radiation detector 2, a console 3, and a server 4. These can communicate with each other via the communication network N.

[0017] Furthermore, the radiography system 100 (X-ray imaging system 100) may be connected to a hospital information system (HIS), a radiology information system (RIS), a picture archiving and communication system (PACS), an image analysis device, etc. (not shown).

[0018] As shown in Figure 2, the radiation generator 1 (X-ray irradiation device) includes a generator that applies a voltage according to preset irradiation conditions (tube voltage, tube current, irradiation time, tube current-time product (mAs value), etc.), a radiation source 11 that generates radiation (e.g., X-rays) in a dose corresponding to the tube current when a voltage is applied from the generator, a K-edge filter 12, a slit 13, etc. These are arranged facing the subject H, in the order of slit 13, K-edge filter 12, and radiation source 11 from the subject H side. The device status of radiation generator 1 refers to the SID (Source Image receptor Distance), slit width (aperture width of slit 13), filter type (type of K-edge filter 12), etc., as described later.

[0019] The radiation source 11 (tube) is configured to generate radiation (e.g., X-rays) in a manner corresponding to the radiation image to be captured.

[0020] The K-edge filter 12 is a filter that absorbs X-rays in the mid-range of the X-ray spectrum, thereby separating high-energy X-rays from low-energy X-rays. In other words, the K-edge filter 12 functions as an energy separation method. For example, materials such as Gd (gadolinium) and Cu (copper) are used in the K-edge filter 12.

[0021] Slit 13 is a mechanism for narrowing the X-ray irradiation area in order to minimize the scattered radiation component that affects the accuracy of bone density measurements. Since bone density changes over time, very high accuracy is required, and therefore it is necessary to minimize the scattered radiation component. For example, one method is to use a collimator provided on the radiation source 11 (tube), or to attach an external slit mechanism to the radiation source 11.

[0022] The radiation generator 1 may be installed inside the imaging room, or it may be incorporated into a mobile unit called a mobile medical unit along with the console 3, etc. Furthermore, the K-edge filter 12 and the slit 13 may be attached externally to the radiation source 11. For example, the radiation source 11 may be provided with a loading section for the K-edge filter 12 and the slit 13.

[0023] The radiation detector 2 (FPD; Flat Panel Detector), although not shown in the diagram, comprises a substrate in which pixels equipped with radiation detection elements that generate an electric charge corresponding to the dose when exposed to radiation, and switch elements that store and release electric charge, are arranged in a two-dimensional (matrix) manner; a scanning circuit that switches each switch element on and off; a readout circuit that reads out the amount of electric charge emitted from each pixel as a signal value; a control unit that generates a radiation image from the multiple signal values ​​read out by the readout circuit; and an output unit that outputs the generated radiation image data to the outside. The radiation detector 2 generates a radiation image corresponding to the irradiated radiation, synchronized with the timing of radiation irradiation from the radiation generator 1. The irradiation image generation synchronization timing, which synchronizes the timing of radiation irradiation from the radiation generator 1 with the timing of radiation image generation, is generated by the radiation generator 1 and sent to the radiation detector 2 via the communication network N described later. The radiation detector 2 generates the radiation image based on the irradiation image generation synchronization timing. Alternatively, the radiation detector 2 may generate the irradiation image generation synchronization timing and send it to the radiation generator 1 via the communication network N, and the radiation generator 1 may irradiate radiation based on the irradiation image generation synchronization timing. In addition, the irradiation image generation synchronization timing may be transmitted using a cable for irradiation image generation synchronization timing separately from the communication network N. Furthermore, the communication network N and the cable for irradiation image generation synchronization timing may be combined into a single cable (common cable for communication network and irradiation image generation synchronization timing).

[0024] Furthermore, the radiation detector 2 may be a so-called indirect type that incorporates a scintillator or the like and converts the irradiated radiation into light of other wavelengths such as visible light using the scintillator, and generates an electric charge corresponding to the converted light, or it may be a so-called direct type that generates an electric charge directly from the radiation without going through a scintillator or the like. Furthermore, the radiation detector 2 is portable (cassette type) and is loaded onto the imaging table S, as shown in Figure 2. Additionally, typical sizes of radiation detectors 2 (cassette-type FPDs) include 14 x 17 inches, 17 x 17 inches, and 10 x 12 inches. Furthermore, in this embodiment, the radiation detector 2 must be compatible with DXA imaging (hereinafter referred to as DXA imaging). For example, when imaging is performed by moving the X-ray tube while focusing the X-rays with a slit, as described later (called slot imaging, etc.), the X-rays are pulsed, so the FPD must be capable of control that corresponds to pulsed irradiation (for example, control that generates a radiation image in synchronization with the irradiation timing of pulsed irradiation). Furthermore, the radiation detector 2 is managed using the FPD individual information management table T2, which will be described later.

[0025] Furthermore, the distance between the radiation source 11 and the radiation detector 2, as shown in Figure 2, is called the SID (Source Image Receptor Distance). More precisely, the Source is the focal point of the radiation source 11, which is a light tube, and the Image Receptor is the image-receiving surface of the radiation detector 2 (FPD), so it is the distance between the focal point and the FPD.

[0026] Console 3 consists of an image processing unit and electronic equipment, comprising a PC and dedicated devices. Furthermore, Console 3 can set various shooting conditions (tube voltage, tube current, irradiation time, tube current-time product (mAs value), frame rate, subject H's physique, presence or absence of grid, etc.) on the imaging device based on shooting order information obtained from other systems (such as HIS and RIS) and user operations.

[0027] As shown in Figure 3, the console 3 according to this embodiment includes a control unit 31, a communication unit 32, a storage unit 33, a display unit 34, and an operation unit 35. Each of the parts 31-35 is electrically connected by a bus.

[0028] The control unit 31 is composed of a CPU (Central Processing Unit), RAM (Random Access Memory), and the like. The CPU of the control unit 31 reads various programs stored in the memory unit 33, expands them into RAM, executes various processes according to the expanded programs, and centrally controls the operation of each part of the console 3. The control unit 31 functions as a discrimination unit that determines whether the type of radiation detector 2, the device status of the radiation generator 1, and the irradiation conditions of the radiation generator 1 are suitable for X-ray imaging using the dual-energy X-ray absorption spectroscopy method. Furthermore, the control unit 31 functions as a first prohibition unit that prohibits imaging if the size, function, or performance of the radiation detector 2 is not suitable for X-ray imaging by dual-energy X-ray absorptiometry. Furthermore, the control unit 31 functions as a second prohibition unit that prohibits imaging if the slit and / or K-edge filter that narrows the X-ray irradiation range are not suitable for DXA imaging. Furthermore, the control unit 31 functions as a third prohibition unit that prohibits imaging when the distance between the radiation generator 1 and the subject (subject H) is outside a predetermined range.

[0029] The communication unit 32 consists of communication modules and the like. The communication unit 32 is configured to send and receive various signals and data with other devices connected via a communication network N (such as a LAN (Local Area Network), WAN (Wide Area Network), or the Internet).

[0030] The memory unit 33 is composed of non-volatile semiconductor memory, a hard disk, or the like. Furthermore, the memory unit 33 stores various programs executed by the control unit 31, as well as parameters necessary for program execution. The memory unit 33 may also be capable of storing radiation images. Furthermore, the memory unit 33 may be capable of storing information related to the imaging method (imaging method management table T1, described later) and individual FPD information (FPD individual information management table T2, described later).

[0031] The display unit 34 consists of an image display device such as an LCD (Liquid Crystal Display) or CRT (Cathode Ray Tube), a light-emitting lamp (LED, etc.), a speaker that outputs sound, a vibrating transducer, and the like. The display unit 34 functions as a notification unit that provides notifications based on the determination results of the control unit 31.

[0032] The control unit 35 consists of a keyboard equipped with cursor keys, number input keys, various function keys, a pointing device such as a mouse, and a touch panel laminated on the surface of the display device. The operation unit 35 then outputs control signals to the control unit 31 in accordance with the operations performed by the user.

[0033] The control unit 31 of the console 3 configured in this way has the function of executing a DXA method feasibility determination process (DXA imaging feasibility determination process) as shown in Figure 4, triggered, for example, by the loading of the radiation detector 2 onto the imaging table S.

[0034] Server 4 consists of PCs, dedicated devices, virtual servers on the cloud, etc. Furthermore, server 4 has a database 41. Database 41 stores information about the imaging method (imaging method management table T1) and individual FPD information (FPD individual information management table T2). Here, we will explain the imaging method management table T1 shown in Figure 5. The imaging method management table T1 is a table that manages imaging-related information for each imaging method. Imaging information includes patient information and examination information. For example, it includes SID, tube voltage, slit width, filter, required panel size, etc., corresponding to the imaging method. Next, we will explain the FPD individual information management table T2 shown in Figure 6. The FPD individual information management table T2 is a table that manages individual information for each FPD. Individual information includes, for example, functions such as whether pulse irradiation is possible and whether bone density measurement is possible, performance such as pixel size and supported frame rate, and panel size. The type of radiation detector 2 (X-ray detector), which will be described later, is a combination of column names in the FPD individual information management table T2. The type of radiation detector 2 (X-ray detector) classifies whether DXA imaging is possible. In this embodiment, the database 41 is provided on a server 4 that is independent of the console 3, etc., but the database 41 may be provided within the console 3, or within other devices of the radiography system 100. Furthermore, if other systems such as PACS are connected to the radiography system 100, the radiography system may be located within the other system.

[0035] In this embodiment, the radiation imaging system 100 is configured such that the radiation source of the radiation generator 1 and the radiation detector 2 are placed opposite each other with a space in between, and by irradiating the subject H, which is placed between them, with radiation from the radiation source, it is possible to capture a radiation image of the subject H.

[0036] When the radiographic image is a still image (still image capture; general radiography), radiation irradiation and image generation are performed only once per shooting operation. When the radiographic image is a moving image (motion capture; serial capture), pulsed radiation irradiation and frame image generation are repeated multiple times in a short period of time (for example, 15 times per second) per shooting operation.

[0037] In DXA imaging, as shown by the arrows in Figure 2, the radiation source 11 is moved in a straight line, thereby moving the irradiation area narrowed by the slit 13 relative to the subject H, and scanning is performed. In the DXA method, bone density is measured by irradiating with X-rays of two different energies, high energy and low energy, and measuring the difference in absorption rates between bone and soft tissue. For example, in the forward path, the tube voltage of the radiation source 11 is set to 70kV and the K-edge filter 12 is set to Gd, and a scan is performed. In the return path, the tube voltage of the radiation source 11 is set to 110kV and the K-edge filter 12 is set to Cu, and a round-trip scan is performed. Alternatively, a method of performing a one-directional scan while switching the tube voltage of the radiation source 11 and the K-edge filter 12 for each irradiation area is also possible. Furthermore, the radiation source 11 performs pulsed irradiation for each irradiation area. This is because exposing the entire imaging area in one pass would result in a large amount of scattered radiation, affecting the accuracy of bone density measurements. Therefore, by using a slit to narrow the irradiation area and performing pulsed irradiation for each area, the effects of scattered radiation can be reduced. Furthermore, the irradiation range on the radiation detector 2 is determined by the width of the slit 13 and the SID.

[0038] Next, the DXA imaging feasibility determination process will be explained using the flowchart in Figure 4. The DXA imaging feasibility determination process is the process by which the control unit 31 determines whether or not the radiography system 100 is in a state where DXA imaging is possible. It is assumed that the user, the person performing the imaging (radiologist), has already operated the control unit 35 and entered the patient information and examination information of the subject H. Furthermore, the settings for the radiation generator 1 may be automatically configured based on the imaging method management table T1. For example, in the case of SID, the SID is set by automatically moving the device that fixes the radiation source 11 (e.g., an arm). Also, in the case of tube voltage, for example, the tube voltage to be applied to the radiation source 11 is automatically set. Because this device can perform both general radiography and DXA with a single device, there is a possibility of mistakenly applying imaging conditions such as SID and tube voltage intended for general radiography to DXA imaging, but this method can reduce human error.

[0039] First, when the user starts the inspection, the control unit 31 determines whether the imaging to be performed is DXA imaging or not based on the imaging order information obtained from the RIS, etc. (step S1). If it is DXA imaging (step S1; YES), the process proceeds to step S2; if it is not DXA imaging (step S1; NO), the DXA imaging feasibility determination process ends.

[0040] Next, the control unit 31 determines whether the FPD loaded into the imaging table S by the imaging operator is capable of DXA imaging, based on the individual FPD information stored in the database 41 (step S2). If DXA imaging is possible (step S2; YES), the process proceeds to step S3; otherwise, the process proceeds to step S8. Specifically, the control unit 31 determines that an FPD is for DXA imaging if both the pulse irradiation capability and bone density measurement capability are available in the FPD individual information management table T2 shown in Figure 6. Alternatively, instead of using the FPD individual information management table T2 for determination, information on whether or not DXA imaging is possible (information indicating that both general and DXA imaging are possible, or information indicating that DXA imaging is not possible, or information indicating that only general imaging is possible) may be stored in each FPD, and based on that information, it may be determined whether or not the loaded FPD is capable of DXA imaging.

[0041] Next, the control unit 31 determines whether the size of the FPD loaded into the imaging table S by the person performing the imaging is appropriate, based on the individual FPD information stored in the database 41 (step S3). If the size is appropriate (step S3; YES), the process proceeds to step S4; if the size is not appropriate (step S3; NO), the process proceeds to step S8. Specifically, the control unit 31 makes a determination using the required panel size of the imaging method management table T1 shown in Figure 5 and the size of the FPD individual information management table T2 shown in Figure 6. For example, as shown in the required panel size of the imaging method management table T1 shown in Figure 5, the parts to be imaged in DXA imaging are often the lumbar spine and femur, and a size of 10×12 may be insufficient. In such cases, the FPD individual information management table T2 may determine whether imaging is permitted if an FPD with a size of 10×12 is loaded.

[0042] Next, the control unit 31 calculates the SID based on the position information of a device (e.g., an arm) that fixes the radiation source 11 (not shown), and determines whether the SID is the desired SID set for DXA imaging or based on the imaging method management table T1 (step S4). If the SID is appropriate (step S4; YES), the process proceeds to step S5; if the SID is not appropriate (step S4; NO), the process proceeds to step S8. Specifically, the control unit 31 determines whether the calculated SID is within a predetermined distance range from the SID for DXA imaging (120 cm in Figure 5) in the imaging method management table T1 shown in Figure 5. Note that if the SID is set automatically based on the imaging method management table T1, step S4 may not be executed. Even if the SID is set automatically, step S4 may be executed if it is detected that the SID has been manually changed after the automatic setting. This ensures reliable determination even in cases where automatic and manual operations are mixed.

[0043] Next, the control unit 31 determines, based on the imaging method management table T1, whether the tube voltage applied to the radiation source 11 is the desired tube voltage set for DXA imaging (step S5). If the tube voltage is appropriate (step S5; YES), the process proceeds to step S6; if the tube voltage is inappropriate (step S5; NO), the process proceeds to step S8. Specifically, the control unit 31 determines whether the set tube voltage is equal to the tube voltage in the imaging method management table T1 shown in Figure 5. Note that if the tube voltage is set automatically based on the imaging method management table T1, step S5 may be omitted. Even if the tube voltage is set automatically, step S5 may be executed if it is detected that the tube voltage has been manually changed after the automatic setting. This ensures reliable detection even in cases where automatic and manual operations are mixed. Furthermore, the system may be configured to determine whether the tube voltage is within a predetermined range suitable for DXA imaging.

[0044] Next, the control unit 31 determines whether the width of the slit 13 loaded by the person performing the imaging is the desired slit width set for DXA imaging (step S6). If the slit width is appropriate (step S6; YES), proceed to step S7; if the slit width is not appropriate (step S6; NO), proceed to step S8. Specifically, the control unit 31 determines whether the width of the loaded slit 13 is equal to the slit width of the imaging method management table T1 shown in Figure 5. Furthermore, it may be possible to determine whether the slit width is within a predetermined range suitable for DXA imaging.

[0045] Next, the control unit 31 determines whether the K-edge filter 12 loaded by the photographer is the desired filter set for DXA imaging (step S7). If the filter is appropriate (step S7; YES), the process ends; if the filter is not appropriate (step S7; NO), the process proceeds to step S8. Specifically, the control unit 31 determines whether the loaded K-edge filter 12 is the same as the filter in the imaging method management table T1 shown in Figure 5. The process may proceed to step S8 if the slit 13 and K-edge filter 12 are not externally attached to the radiation source 11.

[0046] Next, the control unit 31 prohibits (denies) the taking of photographs (step S8). Next, the control unit 31 displays a warning on the display unit 34 (step S9). The warning is displayed (notified) by a message (such as "DXA shooting is not permitted," "A cassette FPD unsuitable for DXA shooting has been loaded," "SID is inappropriate," etc.) appropriate to the content of steps S1 to S7 above, as well as by sound, vibration, etc. An icon indicating NG may be displayed before the message, and pressing the icon may display a message indicating the reason for the NG. Conversely, if all the conditions necessary for DXA are met, a message such as "DXA shooting is possible" may be displayed, or an icon indicating this may be displayed, so that the user is clearly informed of this. Furthermore, it is not limited to prohibiting photography and displaying a warning; the system may also be configured to only prohibit photography (step S8) or only display a warning (step S9).

[0047] (Other variations) (Filming permission / warning) In addition, the control unit 31 will issue a warning and / or prohibit shooting in step S8 if the SID is other than the predetermined SID during DXA shooting as described above in step S4, but may permit shooting during general shooting. Furthermore, the SID setting for auto-tracking (the radiography system 100 automatically sets the SID) may be user-configurable in the case of general radiography, but not user-configurable in the case of DXA radiography. For example, during DXA radiography, the radiography system 100 may fix the SID set by auto-tracking and prevent it from being changed. In this case, step S4 may be omitted. Since the SID is a fixed length in DXA radiography, this prevents the user from mistakenly setting the SID to a distance other than the predetermined distance.

[0048] Furthermore, the control unit 31 may allow the user to switch any additional filter during general radiography, but may not allow filter switching during DXA radiography. This is because a specific filter (K-edge filter 12) used for energy separation is predetermined during DXA radiography, while the user can select which additional filter to use during general radiography. If a filter unsuitable for DXA radiography is used out of habit from general radiography, the bone density measurement accuracy will be compromised. For example, if a filter is switched during DXA radiography, a warning and / or prohibition of radiography may be issued in steps S8 and S9, or the special filter for DXA radiography may be made unselectable during general radiography, or a warning and / or prohibition of radiography may be issued. As mentioned above, a specific filter is predetermined during DXA radiography, leaving no room for user selection. Therefore, the filter switching icon may not be displayed on the UI during DXA radiography, or it may be grayed out to make it unselectable. Also, since the specific filter used during DXA radiography is not used during general radiography, the specific filter used during DXA radiography may be excluded from the display during selection to prevent accidental selection. This prevents the user from mistakenly changing to a filter other than the predetermined one.

[0049] Furthermore, the control unit 31 may add a step in the DXA shooting feasibility determination process to determine whether the angle is appropriate based on the tube angle information (+ panel angle) before starting DXA shooting, and issue a warning and / or prohibit exposure in steps S8 and S9. Depending on the conditions of the previous shooting, the tube may be tilted, but by doing so, it is possible to prevent shooting from starting at an angle other than the predetermined angle, resulting in wasted shooting. Furthermore, the control unit 31 may add a step in the DXA shooting feasibility determination process to issue a warning and / or prohibit shooting if the table T (top plate T) of the shooting stand S is different from a predetermined one. Since it is up to the user which shooting stand the panel is loaded onto, there is a possibility that it may be mistakenly loaded onto a shooting stand that is not DXA compatible, but this method makes it possible to notice panel loading errors before shooting. One possible method is to write a unique ID to the I / F cable that connects the panel to the shooting stand to determine if it is DXA compatible, and further associate the unique ID with the type of shooting stand, so that when the panel is connected to the I / F cable the unique ID is read and it is determined which shooting stand it is loaded onto.

[0050] Furthermore, the control unit 31 may turn off AEC (Auto Exposure Control) during DXA imaging. This measure is taken because AEC uses power near the panel and can be a source of noise, and this noise component may affect the bone density results. By doing so, the disturbances caused by AEC can be avoided. Furthermore, the control unit 31 may allow the user to switch AEC ON / OFF during general imaging, but may not allow AEC ON / OFF switching during DXA imaging. As mentioned above, AEC can be a source of noise, and there may be times when one would want to turn it OFF during DXA imaging. However, by doing this, it is possible to avoid situations where the user accidentally turns AEC ON during DXA imaging and does not obtain the desired bone density results.

[0051] Now, let's explain AEC. In general radiography, AEC helps reduce the burden on the radiographer by automatically determining the illumination conditions according to the subject. However, in DXA radiography, X-rays that have passed through the subject are incident on the AEC, generating scattered radiation. Therefore, it is desirable that the AEC is not located between the subject and the FPD. Generally, AEC is most commonly used for chest radiography, and since most chest radiography is performed using a standing radiography table, in an X-ray system that supports both DXA and general radiography, it is advisable to omit the AEC from the supine radiography table used for DXA radiography, and to install the AEC on radiography tables that do not support DXA radiography (for example, standing radiography tables). Furthermore, if there are three or more imaging tables in total, including both standing and supine imaging tables, it is advisable to designate one of them as compatible with DXA imaging, and to provide AEC (Automatic Exposure Control) on the other tables, while keeping AEC on that table. For example, if there are two supine imaging tables and one standing imaging table, one of the supine imaging tables should be designated for DXA imaging and should not have an AEC, while the other supine imaging table and the standing imaging table should have AECs. This approach allows for a balance between the convenience of DXA imaging and general radiography. However, in this case, if DXA imaging is performed on a supine imaging table equipped with AEC, scattered radiation from the AEC will be generated. Therefore, the control unit 31 may add a step in the DXA imaging feasibility determination process, and if the imaging table selected by the photographer for DXA imaging is equipped with AEC, it may issue a warning and / or prohibit exposure in steps S8 and S9. Alternatively, the selection of an imaging table without AEC may be used as one of the conditions for permitting DXA imaging.

[0052] The above-described X-ray imaging system 100 avoids the effects of scattered radiation due to the AEC during DXA imaging by having an imaging table S without an AEC. However, the effects of scattered radiation can also be avoided by devising the arrangement of the AEC and radiation detector 2 on the imaging table S. Typically, as shown in Figure 7, the supine radiography table ST1 used for general radiography has a grid space SP (grid slot) for inserting a grid under the top plate T on which the patient rests, an AEC (Automated Electron Computing) is located below that, and below that is a first FPD space SP1 (FPD tray) for inserting a radiation detector 2. The radiation detector 2 can be inserted into and removed from the first FPD space SP1 (the FPD tray is pulled out from the radiography table, the radiation detector 2 is set and secured in the tray, and the tray is pushed back into the radiography table. To remove it, the reverse procedure is followed). In contrast, as shown in Figure 8, a second FPD space SP2 into which a radiation detector 2 can be inserted may be provided beneath the top plate T on which the patient is placed, and a DXA-compatible supine imaging table ST2 may be used in which the radiation detector 2 is inserted into the second FPD space SP2 for DXA imaging. In this DXA-compatible supine imaging table ST2, there is no AEC between the patient (subject H) and the radiation detector 2, so the effects of scattered radiation caused by the AEC can be avoided. The second FPD space SP2 may be located between the grid space SP and the AEC. Alternatively, as shown in Figure 9, the grid space SP may be shared with the second FPD space SP2 (shared space SP3), allowing the grid or radiation detector 2 to be inserted. Alternatively, as shown in Figure 10, a second FPD space SP2 may be provided on the upper part of the tabletop T on which the patient rests. If a second FPD space SP2 is provided on the upper part of the tabletop T, a rectangular recess can be provided in the center of the tabletop T, as shown in Figure 11, into which the radiation detector 2 can be fitted, and the radiation detector 2 used for DXA can be stored there as shown in Figure 12. As shown in Figure 11, the second FPD space SP2 is provided with interfaces for the radiation detector 2's communication network N, an interface for the irradiation image generation synchronization timing, and a power supply interface, allowing the radiation detector 2 to be housed in this space and connected to these interfaces. These interfaces may be separate, or multiple interfaces may be integrated into a single cable / connector CN, as shown in the communication network / irradiation image generation synchronization timing common cable N1 in Figure 11. Furthermore, as shown in Figure 13, after the radiation detector 2 is housed, a cover CV can be attached to this space, thereby reducing the physical burden on the patient (such as back pain) caused by the step in the top plate T. This cover CV can also be attached when the radiation detector 2 is not housed. When performing AEC imaging in general radiography, the radiation detector 2 is housed in the first FPD space SP1, and the second FPD space SP2 is not housed in the radiation detector 2, but the cover is attached to the second FPD space SP2 for imaging. This prevents the radiation detector 2 in the second FPD space SP2 from being captured in the image. Furthermore, as shown in Figures 14, 15, and 16, one side of the rectangular recess of the second FPD space SP2 may be left open from the edge of the top plate T. This makes it easier to insert and remove the radiation detector 2 than if it were a rectangular recess. For example, as shown in Figure 16, with the cover CV of the second FPD space SP2 attached, the radiation detector 2 can be inserted into the second FPD space SP2 through the opening O at the edge of the top plate T, meaning that the radiation detector 2 can be inserted and removed while the patient is on the top plate T, thus increasing convenience. Also, if the communication network / irradiation image generation synchronization timing common cable N1 is routed through the opening O, the cable N1 can be removed from the second FPD space SP2 when it is not in use. This eliminates concerns about the cable appearing in images when performing AEC imaging in general radiography. Alternatively, the top plate T may not have a recess, and the radiation detector 2 may be placed on top plate T. In this case, during general radiography, the patient will stand directly on top plate T, but for DXA radiography, the radiation detector 2 will be placed on top plate T, and the patient will stand on top of it. If the radiation detector 2 is displaced when the patient stands on it or when the patient moves during radiography, it may become an unsuitable position for DXA radiography, potentially leading to a failed scan. Therefore, as shown in Figure 17, it is advisable to provide the top plate T with convex protrusions (FPD placement guides G1) that catch on the edges and / or corners of the radiation detector 2 to prevent the radiation detector 2 from being displaced. The FPD placement guide G1 is positioned so that it catches on at least two (preferably four or more) sides and / or corners. When the radiographer places the radiation detector 2 on the top plate T, they can position the radiation detector 2 in a suitable position for DXA imaging simply by aligning the FPD placement guide G1 with the sides and / or corners of the radiation detector 2, thus improving work efficiency. When the radiation detector 2 is placed on the top plate T in this way and the patient is placed on top of it, the height difference of the radiation detector 2 becomes a physical burden on the patient. Therefore, as shown in Figure 17, a space SP4 for positioning a riser material B to eliminate the height difference is provided around the second FPD space SP2. When positioning the patient on the radiation detector 2 and riser material B, if the position of the riser material B is misaligned, it becomes necessary to remove the patient, reposition the riser material B, and reposition the patient, which is time-consuming. Therefore, the space SP4 for placing the raising material is provided with a convex protrusion for the raising material (raising material placement guide G2) that catches on a part of the raising material B, thereby preventing the raising material B from shifting (Figures 17 and 18). Furthermore, if there are many height-adjustment material placement guides G2 near the center of the tabletop T, when a patient directly sits on the tabletop T during general radiography, the patient may feel a protrusion, causing physical discomfort. To avoid this, it is best to place the height-adjustment material placement guides around the edges of the tabletop T (for example, in the area from the edge of the tabletop T to 10 cm inward) rather than near the center of the tabletop T. Furthermore, since providing both an FPD placement guide G1 and a riser material placement guide G2 makes it difficult to determine which guide the radiation detector 2 and the riser material B should follow, it is advisable to make them easier to distinguish by changing the shape and / or color of the FPD placement guide G1 and the riser material placement guide G2. Alternatively, each space could be marked to indicate whether it is a space for an FPD or a space for a riser material. Up to this point, we have explained how to equip the X-ray imaging system 100 with the DXA-compatible supine imaging table ST2. However, the X-ray imaging system 100 may have multiple imaging tables S, some of which may be the DXA-compatible imaging tables described above, and others which may be non-DXA-compatible imaging tables. In this case, if DXA imaging is performed on a non-DXA-compatible imaging table, scattered radiation due to AEC will be generated. Therefore, the control unit 31 may add a step in the DXA imaging feasibility determination process, and if the imaging table selected by the radiographer for DXA imaging is a non-DXA-compatible imaging table, it may issue a warning and / or prohibit exposure in steps S8 and S9. Alternatively, the selection of a DXA-compatible imaging table may be used as one of the conditions for permitting DXA imaging. As described above, the DXA-compatible imaging table is susceptible to scattered radiation if the radiation detector 2 used for DXA imaging is located in the first FPD space SP1. Therefore, the radiation detector 2 used for DXA imaging must be located in the second FPD space SP2. In contrast, the X-ray imaging system 100 has a mechanism to detect when the radiation detector 2 is located in the second FPD space SP2. The control unit 31 adds a step in the DXA imaging feasibility determination process, and if the radiation detector 2 is not located in the second FPD space SP2 in the case of DXA imaging, it may issue a warning and / or prohibit exposure in steps S8 and S9. Alternatively, the presence of the radiation detector 2 in the second FPD space SP2 may be used as one of the conditions for permitting DXA imaging. Furthermore, the system has a mechanism to identify the individual or type of radiation detector 2 located in the second FPD space SP2. Even if a radiation detector 2 is located in the second FPD space, if the individual or type of radiation detector 2 is not suitable for DXA imaging, or if it is a different individual or type from the radiation detector 2 selected by the photographer, a warning and / or exposure may be denied in steps S8 and S9. Alternatively, the presence of a radiation detector 2 in the second FPD space SP2, and the fact that the individual or type of radiation detector 2 is suitable for DXA imaging, or matches the radiation detector 2 selected by the photographer, may be used as one of the conditions for permitting DXA imaging.

[0053] Furthermore, the control unit 31 may add a step in the DXA imaging feasibility determination process to issue a warning and / or prohibit imaging if the grid loading state differs from a predetermined one. In general radiography, the user can choose whether or not to load a grid, but in DXA imaging, predetermined conditions are set in advance, such as not loading a grid or fixing the specifications of the grid to be loaded, in order to calculate bone density. In this way, it is possible to avoid situations where imaging is performed under unintended conditions and the desired bone density results are not obtained. Furthermore, while the flowchart in Figure 4 shows the determination of whether DXA shooting is possible in steps S1 to S7, the order does not necessarily have to be S1 to S7; the order can be changed, or the decisions can be made simultaneously.

[0054] (Filming support) Furthermore, when the collimator of the radiation generator 1 is used in the slit 13, the control unit 31 may display the relationship between the target aperture and the current aperture to assist in setting the aperture width in step S8. Since the irradiation area irradiated onto the panel is determined by the aperture width, it is necessary to adjust the aperture width to a predetermined width in millimeter increments, but this is difficult to do visually, so the control unit 31 assists in this process. The display may show the relationship between the target aperture and the current aperture as a digital value, or it may only show the current aperture width digitally. In this way, the aperture width can also be adjusted manually in millimeter increments. Furthermore, the control unit 31 calculates the position information of the imaging system and the amount of vertical and horizontal position correction that should be centered in the image from the general radiographic image (pre-imaging performed before DXA imaging), and displays it on the console 3 or a separate monitor placed near the patient. The amount of positional movement of the imaging system is also visualized at the same time to support positioning. If the radiography system 100 is capable of auto-positioning, it may be automatically adjusted based on the position information. This is because if the area required for DXA imaging is not included in the ROI (Region of Interest) of the still image acquired in the pre-imaging, accurate bone density measurement cannot be performed, so the purpose is to support the positioning required for DXA imaging using the image acquired in the pre-imaging. Furthermore, the control unit 31 may display the previously captured image. It is preferable to take the image under the same conditions as the previous time (i.e., the same positioning) for monitoring the progress of bone density. By displaying the previously captured image, the user can recognize the difference in positioning between the previous and current images and make minor adjustments to the positioning. Furthermore, the control unit 31 may prompt the user to pay attention to positioning if there is curvature of the lumbar spine or other conditions. For example, it may calculate the amount of vertical and horizontal position correction and display it on the console. Depending on the patient's condition, such as curvature of the lumbar spine, positioning that takes that condition into account is necessary, so prompting the user can reduce the risk of imaging failure due to positioning. In addition, by calculating and displaying the amount of position correction to reproduce the positioning from the previous imaging session, the user can intuitively make minor adjustments to their positioning. Furthermore, the control unit 31 may display the shooting status and instructions in an easy-to-understand manner for the photographer. For example, it may graphically display whether it is in the forward or return phase, change the sound during shooting, change the color of the LED, or display the remaining time until shooting is complete. Since shooting involving the movement of the tube in the forward and return phases is not necessarily a common method, it is conceivable that the user might forget that there is a return phase and release the exposure switch, interrupting the illumination, or that the user might lose track of whether it is the forward or return phase during shooting. By doing so, the current shooting status can be intuitively recognized by the user, and the risk of shooting failure due to user misunderstanding can be reduced.

[0055] (Equipment configuration) Furthermore, since the control unit 31 may need to control the tube voltage kV, tube current, and tube current-time product mAs value with higher precision than the specifications of the radiation generator 1, it may input dose information to the console 3 by means of either equipping the radiation source 11 with a dosimeter or transmitting dose information from the radiation generator 1, thereby correcting for variations in signal values ​​on the image due to variations in dose. Although the radiation generator 1 is often unable to irradiate with the precision required by DXA imaging, this method allows for obtaining an effect equivalent to that of irradiating with the same dose. Alternatively, the dose information output by the radiation generator 1 may be used as a substitute for a dosimeter. Furthermore, the control unit 31 may derive the SSD (Source Skin Distance; the distance from the focal point of the tube to the surface of the subject H) using a visible light camera and / or a distance measuring sensor (distance measuring camera) attached to the tube (radiation source 11). For example, the control unit 31 may subtract the SSD from the SID obtained from the mechanical arrangement information of the radiation generator 1 to obtain the body thickness and use it for scattered radiation correction (if the body thickness is large, the dose needs to be increased, and as a result the scattered radiation also increases, so correction is more necessary). The SSD may also be used for the automatic deriving of imaging conditions.

[0056] (console) Furthermore, since the control unit 31 controls both general radiography and DXA radiography, it may enable both general radiography and DXA radiography within the same inspection and manage each captured image in a linked manner. Since still images (general radiography) are taken in most cases before DXA radiography, grouping and managing these as the same inspection will make subsequent image and inspection management on the user's side smoother. Furthermore, the control unit 31 may display on the console 3's display unit 34 that it is in DXA shooting mode in order to accurately inform the user of which shooting mode is currently in operation. When performing general shooting and DXA shooting consecutively, delays in the workflow can be expected due to reasons such as the shooting mode not switching and the inability to start shooting when preparations are made. However, by doing this, the user can intuitively recognize the current shooting mode and perform efficient shooting without having to redo operations. Furthermore, the control unit 31 may switch wireless access between general shooting and DXA shooting. Since DXA shooting consumes more power than general shooting, it is preferable to shoot while supplying power to the panel via a wired connection. In this case, it is preferable to use wired communication and image transfer, which have a high transfer speed. For this reason, there is no need to configure wireless settings for DXA shooting, so for example, a control may be implemented that does not allow switching to wireless during DXA shooting, while allowing switching to wireless during general shooting. In this way, the system performance can always be optimized for shooting depending on the shooting mode. Furthermore, the control unit 31 may change the scattered radiation correction processing parameters based on the type information of the imaging table S being used. For example, different parameters may be used depending on the type of table T of the imaging table S, the distance from table T to FPD, etc.

[0057] (Pre-shoot) Furthermore, from the perspective of preventing unnecessary DXA imaging, the control unit 31 may take still images (pre-imaging) after positioning for DXA and determine whether imaging is possible. For example, if the control unit 31 determines from the pre-imaging images that DXA imaging is not possible for reasons such as the area required for DXA imaging not being within the ROI, it will notify the user from the console that DXA imaging is not possible. In this way, the user can be informed of inappropriate conditions (e.g., patient positioning) before starting DXA imaging, thus preventing unnecessary DXA imaging. Furthermore, since the reproducibility of positioning is important from the perspective of monitoring progress, the control unit 31 may compare the pre-imaging image from the previous DXA scan with the pre-imaging image from the current scan to evaluate the reproducibility of positioning. Furthermore, the control unit 31 may estimate the body thickness of the relevant area (lumbar spine or femur) using a pre-imaging still image and adjust the dose during DXA imaging. For example, three ranges of body thickness—large, medium, and small—can be defined and associated with corresponding imaging conditions (tube voltage kV and tube current-time product mAs), and the dose can be automatically adjusted based on the body thickness obtained through body thickness estimation. In this way, DXA imaging can be performed with appropriate imaging conditions tailored to the patient's body type, without relying on user judgment. Furthermore, the control unit 31 may derive the area requiring irradiation from the pre-imaging image and determine the range of movement of the light tube from there. For example, in DXA imaging, the areas that should be included in the imaging range for each measurement site, such as the lumbar spine and femur, are indicated in guidelines. It is conceivable to determine the area requiring irradiation by including these necessary parts at a minimum and adding a certain margin. In this way, imaging can always be performed with the optimal irradiation range, regardless of the patient's positioning, and the user's operation to determine the irradiation range itself can be omitted. If pre-imaging has not been performed, the entire panel may be used as the range of movement. The area requiring irradiation may be determined from the structure of the subject, from the irradiation field of the pre-imaging, or from the user's indication on the screen. Alternatively, the control unit 31 may derive the DXA imaging range from the collimator aperture width and SID information, and determine the range of movement of the tube based on that. Alternatively, the control unit 31 may determine the irradiation field from the tube camera (a camera installed on the radiation source 11) and determine the range of movement of the tube.

[0058] (Filming in progress) Furthermore, the control unit 31 may update the dark image for offset correction when the forward / return path is reversed. Furthermore, the control unit 31 may switch the afterimage correction between the forward and return paths at the same time as updating the offset image.

[0059] (Effects, etc.) Based on the above, the X-ray imaging system (radiography system 100) is an X-ray imaging system capable of both dual-energy X-ray absorption spectroscopy and general radiography, comprising an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that captures X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the capture of X-ray images by the X-ray detector. The X-ray imaging control device (console 3) comprises a discrimination unit (control unit 31) that determines whether the type of X-ray detector is suitable for X-ray imaging using dual-energy X-ray absorption spectroscopy, and a notification unit (display unit 34) that provides notification based on the discrimination result of the discrimination unit, thereby preventing DXA imaging in conditions unsuitable for DXA imaging and preventing unnecessary radiation exposure to the patient.

[0060] Furthermore, the X-ray imaging system (radiography system 100) is an X-ray imaging system capable of both dual-energy X-ray absorption spectroscopy and general radiography, comprising an X-ray irradiation device (radiation generator 1) that individually irradiates multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that captures X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the capture of X-ray images by the X-ray detector. The X-ray imaging control device (console 3) includes a discrimination unit (control unit 31) that determines whether the device status of the X-ray irradiation device is suitable for X-ray imaging using dual-energy X-ray absorption spectroscopy, and a notification unit (display unit 34) that provides notification based on the discrimination result of the discrimination unit, thereby preventing DXA imaging when the device is not suitable for DXA imaging and preventing unnecessary radiation exposure to the patient.

[0061] Furthermore, the X-ray imaging system (radiography system 100) is an X-ray imaging system capable of both dual-energy X-ray absorption spectroscopy and general radiography, comprising an X-ray irradiation device (radiation generator 1) that individually irradiates multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that captures X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the capture of X-ray images by the X-ray detector. The X-ray imaging control device (console 3) includes a discrimination unit (control unit 31) that determines whether the irradiation conditions of the X-ray irradiation device are suitable for X-ray imaging using dual-energy X-ray absorption spectroscopy, and a notification unit (display unit 34) that provides notification based on the discrimination result of the discrimination unit, thereby preventing DXA imaging in conditions unsuitable for DXA imaging and preventing unnecessary radiation exposure to the patient.

[0062] Furthermore, the X-ray irradiation device (radiation generator 1) performs X-ray imaging using dual-energy X-ray absorption spectroscopy by irradiating multiple times. If the imaging area is exposed in a single pass, the effect of scattered radiation becomes large, affecting the accuracy of bone density measurements. However, by narrowing the irradiation area using a slit and irradiating multiple times, the effect of scattered radiation can be reduced.

[0063] Furthermore, by exposing the tissue to multiple pulses at at least different tube voltages—that is, by irradiating it with two different energy levels of X-rays, high and low—bone and soft tissue can be distinguished.

[0064] Furthermore, the type of X-ray detector (radiation detector 2) is determined by the size, function, or performance of the X-ray detector. The notification unit (display unit 34) notifies the user if the size, function, or performance of the X-ray detector is not suitable for X-ray imaging using the dual-energy X-ray absorption spectroscopy method. This prevents DXA imaging in unsuitable conditions and avoids unnecessary radiation exposure for the subject.

[0065] Furthermore, the X-ray imaging control device (console 3) is equipped with a first prohibition unit (control unit 31) that prohibits imaging if the size, function, or performance of the X-ray detector is not suitable for X-ray imaging by dual-energy X-ray absorption spectroscopy. This prevents DXA imaging in conditions unsuitable for DXA imaging, thereby preventing unnecessary radiation exposure to the patient.

[0066] Furthermore, the discrimination unit determines that the slit and / or K-edge filter used to narrow the X-ray irradiation range are unsuitable for DXA imaging, thereby preventing DXA imaging in unsuitable conditions and preventing unnecessary radiation exposure to the subject.

[0067] Furthermore, the X-ray imaging control device includes a second prohibition unit (control unit 31) that prohibits imaging when the slit and / or K-edge filter used to narrow the X-ray irradiation range are not suitable for DXA imaging. This prevents DXA imaging in conditions unsuitable for DXA imaging, thereby preventing unnecessary radiation exposure to the patient.

[0068] Furthermore, because the slit and filter are attached externally to the X-ray irradiation device, they can be installed even in cases where these mechanisms cannot be installed inside the X-ray tube when adding DXA imaging as an option to a general radiography system later on.

[0069] Furthermore, by including either the distance to the subject or the tube voltage as irradiation conditions, it is possible to appropriately measure bone density over time. In other words, since bone density testing measures subtle changes in the subject over time, it is desirable to fix the imaging conditions such as SID and tube voltage. By not allowing imaging if the SID or tube voltage falls outside the conditions specified for DXA imaging, unnecessary radiation exposure to the subject can be prevented.

[0070] Furthermore, the irradiation condition is the distance between the X-ray irradiation device and the subject, and the discrimination unit determines that if the distance is outside a predetermined range, it is not suitable for X-ray imaging by dual-energy X-ray absorptiometry. This prevents DXA imaging in conditions unsuitable for DXA imaging, thereby preventing unnecessary radiation exposure to the subject.

[0071] Furthermore, the X-ray imaging control device includes a third prohibition unit (control unit 31) that prohibits imaging when the distance is outside a predetermined range, thereby preventing DXA imaging in conditions unsuitable for DXA imaging and preventing unnecessary radiation exposure to the patient.

[0072] Furthermore, the X-ray imaging method is an X-ray imaging method using an X-ray imaging system (radiation imaging system 100) that is capable of performing both dual-energy X-ray absorption spectroscopy and general radiography. This system includes an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that takes X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the acquisition of X-ray images by the X-ray detector. This X-ray imaging method includes a discrimination step that determines whether the type of X-ray detector is suitable for X-ray imaging using dual-energy X-ray absorption spectroscopy, and a notification step that provides notification based on the discrimination result of the discrimination unit. This prevents DXA imaging when the conditions are unsuitable for DXA imaging, thereby preventing unnecessary radiation exposure to the subject.

[0073] Furthermore, the X-ray imaging method is an X-ray imaging method that uses an X-ray imaging system (radiation imaging system 100) capable of performing both dual-energy X-ray absorption spectroscopy and general radiography, comprising an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that takes X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the acquisition of X-ray images by the X-ray detector. This X-ray imaging method includes a determination step to determine whether the device state of the X-ray irradiation device is suitable for X-ray imaging by dual-energy X-ray absorption spectroscopy, and a notification step to provide notification based on the determination result of the determination unit, thereby preventing DXA imaging when the device state is unsuitable for DXA imaging and preventing unnecessary radiation exposure to the subject.

[0074] Furthermore, the X-ray imaging method is an X-ray imaging method using an X-ray imaging system (radiation imaging system 100) that is capable of both dual-energy X-ray absorption spectroscopy and general radiography, comprising an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that takes an X-ray image based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the acquisition of X-ray images by the X-ray detector. This X-ray imaging method includes a determination step to determine whether the irradiation conditions of the X-ray irradiation device are suitable for X-ray imaging by dual-energy X-ray absorption spectroscopy, and a notification step to provide notification based on the determination result of the determination unit, thereby preventing DXA imaging in conditions unsuitable for DXA imaging and preventing unnecessary radiation exposure to the subject.

[0075] Furthermore, the program is used in an X-ray imaging system (radiation imaging system 100) that is capable of both dual-energy X-ray absorption spectroscopy and general radiography, comprising an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that takes X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the acquisition of X-ray images by the X-ray detector. The program is used in the X-ray imaging control device. By making the computer of the X-ray imaging control device function as a discrimination unit that determines whether the type of X-ray detector is suitable for X-ray imaging by dual-energy X-ray absorption spectroscopy, and a notification unit that provides notifications based on the discrimination result of the discrimination unit, it is possible to prevent DXA imaging in conditions unsuitable for DXA imaging and prevent unnecessary radiation exposure to the patient.

[0076] Furthermore, the program is used in an X-ray imaging system (radiation imaging system 100) that is capable of both dual-energy X-ray absorption spectroscopy and general radiography, comprising an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that takes X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the acquisition of X-ray images by the X-ray detector. The program is used in the X-ray imaging control device. By making the computer of the X-ray imaging control device function as a discrimination unit that determines whether the device status of the X-ray irradiation device is suitable for X-ray imaging by dual-energy X-ray absorption spectroscopy, and a notification unit that provides notifications based on the discrimination result of the discrimination unit, it is possible to prevent DXA imaging when the device is not suitable for DXA imaging, thereby preventing unnecessary radiation exposure to the patient.

[0077] Furthermore, the program is used in an X-ray imaging system (radiation imaging system 100) that is capable of both dual-energy X-ray absorption spectroscopy and general radiography, comprising an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that takes X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the acquisition of X-ray images by the X-ray detector. The program is used in the X-ray imaging control device. By making the computer of the X-ray imaging control device function as a discrimination unit that determines whether the irradiation conditions of the X-ray irradiation device are suitable for X-ray imaging by dual-energy X-ray absorption spectroscopy, and a notification unit that provides notifications based on the discrimination result of the discrimination unit, it is possible to prevent DXA imaging in conditions unsuitable for DXA imaging and prevent unnecessary radiation exposure to the patient.

[0078] Furthermore, the X-ray imaging control device (console 3) is an X-ray imaging control device (radiation imaging system 100) capable of performing both dual-energy X-ray absorption spectroscopy and general radiography, comprising an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that takes X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the acquisition of X-ray images by the X-ray detector. The X-ray imaging control device (console 3) includes a discrimination unit (control unit 31) that determines whether the type of X-ray detector is suitable for X-ray imaging by dual-energy X-ray absorption spectroscopy, and a notification unit (display unit 34) that provides notification based on the discrimination result of the discrimination unit, thereby preventing DXA imaging in conditions unsuitable for DXA imaging and preventing unnecessary radiation exposure to the patient.

[0079] Furthermore, the X-ray imaging control device (console 3) is an X-ray imaging control device (radiography system 100) capable of performing both dual-energy X-ray absorption spectroscopy and general radiography. This system comprises an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that captures X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the capture of X-ray images by the X-ray detector. The X-ray imaging control device (console 3) includes a discrimination unit (control unit 31) that determines whether the device state of the X-ray irradiation device is suitable for X-ray imaging using dual-energy X-ray absorption spectroscopy, and a notification unit (display unit 34) that provides notification based on the discrimination result of the discrimination unit. This prevents DXA imaging when the device state is unsuitable for DXA imaging, thereby preventing unnecessary radiation exposure to the patient.

[0080] Furthermore, the X-ray imaging control device (console 3) is an X-ray imaging control device (radiation imaging system 100) capable of performing both dual-energy X-ray absorption spectroscopy and general radiography. This system comprises an X-ray irradiation device (radiation generator 1) capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector (radiation detector 2) that captures X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device (console 3) that controls the capture of X-ray images by the X-ray detector. The X-ray imaging control device (console 3) includes a discrimination unit (control unit 31) that determines whether the irradiation conditions of the X-ray irradiation device are suitable for X-ray imaging using dual-energy X-ray absorption spectroscopy, and a notification unit (display unit 34) that provides notification based on the discrimination result of the discrimination unit. This prevents DXA imaging in conditions unsuitable for DXA imaging, thereby preventing unnecessary radiation exposure to the patient.

[0081] Although the present invention has been described in detail based on embodiments above, the present invention is not limited to the above embodiments and can be modified without departing from the spirit of the invention.

[0082] For example, in the above embodiment, the console 3 has the function to perform the above-mentioned processing during imaging, but the function to perform this processing during imaging, or a part thereof, may be provided in other devices of the radiography system 100 or in other systems connected to the radiography system 100.

[0083] Furthermore, while the above-mentioned X-ray imaging system is capable of both dual-energy X-ray absorption spectroscopy and general radiography, it may also be equipped with other imaging functions (e.g., fluoroscopy, dynamic imaging, tomosynthesis, DES, long-length imaging, etc.). Alternatively, for example, a DXA imaging system implemented using a fluoroscopy device may also be used.

[0084] Furthermore, while the above description has disclosed examples in which semiconductor memory and hard disks are used as computer-readable media for the program according to the present invention, the invention is not limited to these examples. Other computer-readable media that can be used include non-volatile memory such as flash memory and portable recording media such as CD-ROMs. Furthermore, a carrier wave can also be used as a medium for providing program data according to the present invention via a communication line. [Explanation of Symbols]

[0085] 100. Radiography system (X-ray imaging system) 1. Radiation generating device (X-ray irradiation device) 2. Radiation detector (X-ray detector) 3. Console (X-ray imaging control device) 31 Control Unit (Discrimination Unit, First Prohibition Unit, Second Prohibition Unit, Third Prohibition Unit) 32 Communications Department 33 Storage section 34 Display section (notification section) 35 Control section 4 servers 41 Databases N Communication Network

Claims

1. An X-ray imaging system capable of both dual-energy X-ray absorption spectroscopy and general radiography, An X-ray irradiation device that individually irradiates multiple X-rays with different energies, A portable X-ray detector that captures an X-ray image based on the X-rays irradiated by the aforementioned X-ray irradiation device, The system includes an X-ray imaging control device that controls the acquisition of the X-ray image by the X-ray detector, The aforementioned X-ray imaging control device is A determination unit that determines whether the state of the X-ray irradiation apparatus is suitable for X-ray imaging using the dual-energy X-ray absorption measurement method, A notification unit that provides notification based on the determination result of the aforementioned determination unit, An X-ray imaging system characterized by having the following features.

2. An X-ray imaging system capable of both dual-energy X-ray absorption spectroscopy and general radiography, An X-ray irradiation device that individually irradiates multiple X-rays with different energies, A portable X-ray detector that captures an X-ray image based on the X-rays irradiated by the aforementioned X-ray irradiation device, The system includes an X-ray imaging control device that controls the acquisition of the X-ray image by the X-ray detector, The aforementioned X-ray imaging control device is A determination unit that determines whether the irradiation conditions of the X-ray irradiation apparatus are suitable for X-ray imaging by the dual-energy X-ray absorption measurement method, A notification unit that provides notification based on the determination result of the aforementioned determination unit, An X-ray imaging system characterized by having the following features.

3. The X-ray irradiation device is characterized by performing X-ray imaging by dual-energy X-ray absorption measurement using multiple irradiations, as described in claim 1 or 2.

4. The X-ray imaging system according to claim 3, characterized in that the multiple irradiations are performed at at least different tube voltages.

5. The X-ray imaging system according to claim 1, characterized in that the discrimination unit determines that the slit and / or filter for narrowing the X-ray irradiation range is not suitable for X-ray imaging by the dual-energy X-ray absorption measurement method.

6. The X-ray imaging control device is further characterized by comprising a second prohibition unit that prohibits imaging when the slit and / or filter for narrowing the X-ray irradiation range is not suitable for X-ray imaging by the dual-energy X-ray absorption measurement method, as described in claim 5.

7. The X-ray imaging system according to claim 6, characterized in that the slit and filter for narrowing the X-ray irradiation range are attached externally to the X-ray irradiation device.

8. The X-ray imaging system according to claim 2, characterized in that the irradiation conditions include one of the distance from the subject and the tube voltage.

9. The irradiation conditions are the distance between the X-ray irradiation device and the subject, The X-ray imaging system according to claim 2, characterized in that the discrimination unit determines that the X-ray imaging is not suitable for the dual-energy X-ray absorption measurement method when the distance is outside a predetermined range.

10. The X-ray imaging control device is further characterized by comprising a third prohibition unit that prohibits imaging when the distance is outside a predetermined range, as described in claim 9.

11. An X-ray imaging method using an X-ray imaging system that enables both dual-energy X-ray absorption spectroscopy and general radiography, comprising: an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies; a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device; and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, wherein the X-ray imaging system is capable of both dual-energy X-ray absorption spectroscopy and general radiography. A determination step to determine whether the state of the X-ray irradiation apparatus is suitable for X-ray imaging by the dual-energy X-ray absorption measurement method, A notification step which provides notification based on the determination result of the aforementioned determination step, An X-ray imaging method characterized by including [a certain element].

12. An X-ray imaging method using an X-ray imaging system that enables both dual-energy X-ray absorption spectroscopy and general radiography, comprising: an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies; a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device; and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, wherein the X-ray imaging system is capable of both dual-energy X-ray absorption spectroscopy and general radiography. A determination step to determine whether the irradiation conditions of the X-ray irradiation apparatus are suitable for X-ray imaging by the dual-energy X-ray absorption measurement method, A notification step which provides notification based on the determination result of the aforementioned determination step, An X-ray imaging method characterized by including [a certain element].

13. In an X-ray imaging system that enables both dual-energy X-ray absorption spectroscopy and general radiography, the computer of the X-ray imaging control device comprises an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, the computer of the X-ray imaging control device is, A determination unit that determines whether the state of the X-ray irradiation apparatus is suitable for X-ray imaging using the dual-energy X-ray absorption measurement method. A notification unit that provides notification based on the determination result of the determination unit, A program that makes it function as such.

14. In an X-ray imaging system that enables both dual-energy X-ray absorption spectroscopy and general radiography, the computer of the X-ray imaging control device comprises an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies, a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device, and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, the computer of the X-ray imaging control device is, A determination unit that determines whether the irradiation conditions of the X-ray irradiation apparatus are suitable for X-ray imaging by the dual-energy X-ray absorption measurement method. A notification unit that provides notification based on the determination result of the determination unit, A program that makes it function as such.

15. An X-ray imaging system comprising: an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies; a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device; and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, wherein the X-ray imaging control device is capable of performing both dual-energy X-ray absorption spectroscopy and general radiography, wherein the X-ray imaging control device is... A determination unit that determines whether the state of the X-ray irradiation apparatus is suitable for X-ray imaging using the dual-energy X-ray absorption measurement method, A notification unit that provides notification based on the determination result of the aforementioned determination unit, An X-ray imaging control device characterized by comprising:

16. An X-ray imaging system comprising: an X-ray irradiation device capable of individually irradiating multiple X-rays of different energies; a portable X-ray detector for capturing X-ray images based on the X-rays irradiated by the X-ray irradiation device; and an X-ray imaging control device for controlling the capture of the X-ray images by the X-ray detector, wherein the X-ray imaging control device is capable of performing both dual-energy X-ray absorption spectroscopy and general radiography, wherein the X-ray imaging control device is... A determination unit that determines whether the irradiation conditions of the X-ray irradiation apparatus are suitable for X-ray imaging by the dual-energy X-ray absorption measurement method, A notification unit that provides notification based on the determination result of the aforementioned determination unit, An X-ray imaging control device characterized by comprising:

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