Radiographic system, radiographic method, and radiographic program

Abstract

To provide a radiographic system, a radiographic method, and a radiographic program capable of presenting a time that next fluoroscopic imaging can be started after the end of fluoroscopic imaging.SOLUTION: On the basis of a data size of a moving image whose storage in a storage device is completed among moving images stored temporarily in a memory by fluoroscopic imaging, a data storage speed to the storage device, and a data size of a moving image acquired by fluoroscopic imaging according to a frame rate and an imaging time of the fluoroscopic imaging, a radiographic system calculates a remaining time until the storage of the moving image acquired by the fluoroscopic imaging to the storage device is completed, and notifies the calculated remaining time when the fluoroscopic imaging is finished.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present disclosure relates to a radiography system, a radiography method, and a radiography program. [Background technology]

[0002] Patent Document 1 discloses a technique for selecting a frame rate for fluoroscopic imaging in an X-ray fluoroscopic imaging apparatus based on information relating to an observation target. [Prior art documents] [Patent documents]

[0003] [Patent Document 1] Japanese Patent Publication No. 2023-000006 Summary of the Invention [Problem to be solved by the invention]

[0004] In radiographic fluoroscopy, the speed at which moving images obtained by the fluoroscopy are saved to a storage device may be slower than the imaging speed corresponding to the frame rate of the fluoroscopy. In this case, the saving of moving images to the storage device is not complete at the end of the fluoroscopy, and the saving of moving images to the storage device continues even after the end of the fluoroscopy. In this case, the amount of moving images that cannot be saved to the storage device increases even if the next fluoroscopy is started, so it is preferable to present the radiographer, such as a technician, with the time until the next fluoroscopy can be started after the end of the fluoroscopy. Note that fluoroscopy means continuously capturing multiple radiographic images at a predetermined frame rate (i.e., capturing moving images).

[0005] The present disclosure has been made in consideration of the above circumstances, and aims to provide a radiography system, a radiography method, and a radiography program that can display the time until the next fluoroscopic imaging can begin after the end of fluoroscopic imaging. [Means for solving the problem]

[0006] A first aspect of the radiography system is a radiography system that has at least one processor and is capable of performing fluoroscopic photography, which successively captures multiple radiographic images at a predetermined frame rate.When the fluoroscopic photography is completed, the processor calculates the remaining time until the moving images obtained by the fluoroscopic photography are completely saved in the storage device based on the data size of the moving images that have been temporarily saved in memory by the fluoroscopic photography and have been saved in the storage device, the data saving speed in the storage device, and the data size of the moving images obtained by the fluoroscopic photography according to the frame rate of the fluoroscopic photography and the photography time, and notifies the user of the calculated remaining time.

[0007] In a second aspect of the radiation imaging system, in the radiation imaging system of the first aspect, the processor issues a notification when the calculated remaining time exceeds a threshold value determined according to the fluoroscopic imaging procedure.

[0008] A third aspect of the radiation imaging system is the radiation imaging system of the second aspect, wherein the threshold value is determined according to a statistical value of the actual value of the remaining time until the next fluoroscopic imaging can be started when the previous fluoroscopic imaging has ended.

[0009] A fourth aspect of the radiation imaging system is the radiation imaging system of the third aspect, wherein the threshold value is determined in accordance with a statistical value of the performance value for each practitioner of fluoroscopic imaging.

[0010] A radiation imaging system of a fifth aspect is the radiation imaging system of any one of the first to fourth aspects, wherein the processor notifies the user of a recommended imaging time according to the fluoroscopic imaging procedure before the start of fluoroscopic imaging.

[0011] A sixth aspect of the radiation imaging system is the radiation imaging system of the fifth aspect, wherein the processor further notifies the user of a recommended frame rate according to the fluoroscopic imaging procedure before the start of fluoroscopic imaging.

[0012] A seventh aspect of the radiation imaging system is the radiation imaging system of the sixth aspect, wherein the processor derives the recommended frame rate based on subject information relating to a subject who is the target of fluoroscopic imaging and a fluoroscopic imaging technique.

[0013] In the eighth aspect of the radiographic imaging method, a processor of a radiographic imaging system has at least one processor and is capable of performing fluoroscopic imaging, which successively captures multiple radiographic images at a predetermined frame rate. When the fluoroscopic imaging is completed, the processor calculates the remaining time until the moving images obtained by the fluoroscopic imaging are completely saved in the storage device based on the data size of the moving images that have been temporarily saved in memory by the fluoroscopic imaging and have been saved in the storage device, the data saving speed in the storage device, and the data size of the moving images obtained by the fluoroscopic imaging according to the frame rate and shooting time of the fluoroscopic imaging, and performs a process to notify the user of the calculated remaining time.

[0014] A ninth aspect of the radiography program causes a processor of a radiography system that has at least one processor and is capable of performing fluoroscopic photography, which successively captures multiple radiographic images at a predetermined frame rate, to execute a process of calculating, when the fluoroscopic photography is completed, the remaining time until the moving images obtained by the fluoroscopic photography are completely saved in the storage device, based on the data size of the moving images that have been temporarily saved in memory by the fluoroscopic photography and that have been completely saved in the storage device, the data saving speed in the storage device, and the data size of the moving images obtained by the fluoroscopic photography corresponding to the frame rate and shooting time of the fluoroscopic photography, and notifying the user of the calculated remaining time. [Effects of the Invention]

[0015] According to the present disclosure, it is possible to present the time until the next fluoroscopic imaging can be started after the end of the fluoroscopic imaging. [Brief explanation of the drawings]

[0016] [Figure 1] FIG. 1 is a diagram illustrating an example of a radiation imaging system. [Figure 2]FIG. 1 is a diagram illustrating an example of a radiation detector. [Figure 3] FIG. 2 is a block diagram showing an example of the hardware configuration of each device constituting the radiation imaging system. [Figure 4] FIG. 10 is a diagram showing the relationship between the fluoroscopic imaging technique, the imaging time, and the number of imaging operations. [Figure 5] FIG. 10 is a diagram for explaining an unsaved radiographic image at the end of fluoroscopic imaging. [Figure 6] FIG. 2 is a block diagram showing an example of a functional configuration of a console. [Figure 7] FIG. 10 is a diagram illustrating an example of a notification screen. [Figure 8] FIG. 10 is a sequence diagram illustrating an example of fluoroscopic imaging processing. [Figure 9] FIG. 10 is a diagram illustrating an example of a warning notification screen. [Figure 10] FIG. 10 is a diagram showing an example of a recommended frame rate notification screen. [Figure 11] FIG. 10 is a diagram for explaining a process for deriving a recommended frame rate. DETAILED DESCRIPTION OF THE INVENTION

[0017] Hereinafter, examples of embodiments for carrying out the technology of the present disclosure will be described in detail with reference to the drawings.

[0018] First, the configuration of a radiography system 2 will be described with reference to FIG. 1. As shown in FIG. 1, the radiography system 2 is a system for irradiating radiation R, such as X-rays or gamma rays, onto a patient P (an example of a subject) to capture a radiographic image of the patient P, and is operated by a radiologist or other person performing radiography (hereinafter referred to as the "radiography performer"). The radiography system 2 can switch between fluoroscopic radiography, which continuously captures multiple radiographic images at a predetermined frame rate, and general radiography, which records a single radiographic image. The radiography system 2 includes a radiation source 10, a radiation detector 11, a voltage generator 12, a control device 13, a console 14, an upright radiography table 15S, a supine radiography table 15L, and a display 17. The radiation source 10, the radiation detector 11, the voltage generator 12, the control device 13, the upright radiography table 15S, the supine radiography table 15L, and the display 17 are installed, for example, in a radiography room in a medical facility. Meanwhile, the console 14 is installed, for example, in a control room adjacent to the radiography room. One radiation source 10 and one radiation detector 11 are provided, and are used for both the upright position radiography table 15S and the supine position radiography table 15L.

[0019] The radiation source 10 includes a radiation tube 20 that emits radiation R and an irradiation field limiter (also called a collimator) 21 that limits the irradiation field of the radiation R. The radiation tube 20 is provided with, for example, a filament, a target, and a grid electrode. A voltage is applied from a voltage generator 12 between the filament, which is a cathode, and the target, which is an anode. The voltage applied between the filament and the target is called the tube voltage. The filament emits thermoelectrons toward the target in accordance with the applied tube voltage. The target emits radiation R due to collisions of the thermoelectrons emitted from the filament. The grid electrode is disposed between the filament and the target. The grid electrode changes the flow rate of thermoelectrons from the filament toward the target in accordance with the voltage applied from the voltage generator 12. The flow rate of thermoelectrons from the filament toward the target is called the tube current.

[0020] The irradiation field limiter 21 has an entrance opening through which the radiation R from the radiation tube 20 enters and an exit opening through which the radiation R exits. Four shielding plates are provided near the exit opening. The shielding plates are made of a material that blocks the radiation R, such as lead. The shielding plates are arranged on each side of a rectangle, in other words, arranged in a checkered pattern, to form a rectangular irradiation opening that transmits the radiation R. The irradiation field limiter 21 changes the size of the irradiation opening by changing the position of each shielding plate, thereby changing the irradiation field of the radiation R.

[0021] The radiation source 10 is suspended from the ceiling of the radiography room by a support 22. The support 22 is attached via wheels to rails that run around the ceiling. The support 22, and therefore the radiation source 10, can move horizontally within the radiography room by means of the rails and wheels. The support 22 can also extend and retract in the height direction, allowing the radiation source 10 to move in the height direction. Furthermore, the radiation source 10 can rotate relative to the support 22 around an axis that is perpendicular to the plane of the drawing.

[0022] The radiation detector 11 is portable, detects radiation R that has passed through the patient P, and outputs a radiation image of the patient P. The radiation detector 11 transmits the radiation image to the console 14. The radiation detector 11 is housed in the upright position radiography table 15S or the supine position radiography table 15L when used. Alternatively, the radiation detector 11 may be removed from the upright position radiography table 15S or the supine position radiography table 15L in a radiography room and held by the patient P, or placed under the patient P lying supine on a bed in a hospital room. Note that FIG. 1 illustrates an example of radiography of the chest of the patient P positioned in front of the upright position radiography table 15S.

[0023] The voltage generator 12 generates a tube voltage to be applied to the radiation tube 20. The voltage generator 12 and the radiation tube 20 are connected by a voltage cable. The tube voltage generated in the voltage generator 12 is supplied to the radiation tube 20 via this voltage cable.

[0024] The control device 13 controls the operation of the radiation source 10 via the voltage generator 12 in accordance with the irradiation conditions of the radiation R. The irradiation conditions include the tube voltage applied to the radiation tube 20, the tube current, and the irradiation time of the radiation R. Note that the irradiation condition may be the product of the tube current and the irradiation time, a so-called mAs value, instead of the tube current and the irradiation time. In fluoroscopy, the control device 13 determines the irradiation conditions for the next frame based on the dose of the radiation R that has reached the radiation detector 11, which is derived from the radiographic image of the previous frame. In this way, in fluoroscopy, the control device 13 controls the dose of the radiation R for each frame during irradiation of the radiation R.

[0025] An instruction to start and an instruction to end radiation imaging are input to the control device 13 by the person performing the imaging via an irradiation switch (not shown). The irradiation switch is installed in at least one of the control room and the imaging room. The irradiation switch may be a switch operated by hand or a switch operated by foot. When a start instruction is input, the control device 13 operates the voltage generator 12 according to the irradiation conditions, and causes the radiation tube 20 to emit radiation R.

[0026] The console 14 has a function for the radiographer to check and input irradiation conditions for radiation R, and a function for performing image processing on the radiation image obtained by the radiation detector 11. Examples of the console 14 include a computer such as a personal computer or a server computer.

[0027] The upright position imaging platform 15S includes a stand 25, a connection part 26, and an upright position holder 27S. The stand 25 is composed of a base 28 placed on the floor of the imaging room and a support column 29 extending in the height direction from the base 28. The connection part 26 connects the upright position holder 27S to the stand 25. The connection part 26, and therefore the upright position holder 27S, is movable in the height direction relative to the support column 29, allowing the height to be adjusted according to the height of the patient P or the region to be imaged.

[0028] The standing holder 27S is box-shaped and houses the radiation detector 11 inside. Most of the standing holder 27S is made of a conductive material with electromagnetic wave shielding properties, such as aluminum or stainless steel. The front surface of the standing holder 27S, which faces the radiation source 10, is made of a material that transmits radiation R, such as carbon.

[0029] The supine position imaging table 15L includes a base 30, a connection part 31, a top plate 32, and a supine position holder 27L, which are installed on the floor of the imaging room. The connection part 31 connects the top plate 32 to the base 30. The base 30 is elevating type, which allows the height of the top plate 32 and the supine position holder 27L to be adjusted. The top plate 32 is a rectangular plate having a length and width that allows the patient P to lie supine, and is made of a material that transmits radiation R, such as carbon.

[0030] The supine position holder 27L is disposed in the space formed by the connection portion 31 between the base 30 and the top plate 32. The supine position holder 27L is box-shaped with the top covered by the top plate 32, and houses the radiation detector 11 inside. The supine position holder 27L is made of a conductive material with electromagnetic wave shielding properties, such as aluminum or stainless steel. The supine position holder 27L can be slid along the long side of the top plate 32 by a slide mechanism.

[0031] The display 17 is a liquid crystal display or an EL (Electro Luminescence) display. The display 17 is mounted on a display cart with casters so that it can be moved within the radiography room. The display 17 may also be a liquid crystal display disposed in the radiation source 10. The display 17 may also be a liquid crystal display disposed in the irradiation field limiter 21. The display 17 is connected to the console 14.

[0032] As shown in Fig. 2, the radiation detector 11 has a housing 40 and a detection panel 41. The housing 40 has a flat, approximately rectangular parallelepiped shape with a rectangular planar shape, and houses the detection panel 41 inside. Most of the front surface of the housing 40 is formed from a material that transmits radiation R, such as carbon. The radiation detector 11 is set in the standing position holder 27S or the lying position holder 27L with the front surface of the housing 40 facing the radiation source 10.

[0033] The detection panel 41 is configured with an array of pixels that generate signal charges in response to radiation R or visible light converted from radiation R by a scintillator. In addition to the detection panel 41, the housing 40 also houses a control device 18, which will be described later. The housing 40 also houses a communication unit and a battery that supplies power to each unit. The radiation detector 11 may be a so-called CR (Computed Radiography) cassette that houses an imaging plate instead of the detection panel 41.

[0034] Next, the hardware configuration of the control device 13, the console 14, and the control device 18 will be described with reference to Fig. 3. As shown in Fig. 3, the control device 13 includes a CPU (Central Processing Unit) 50, a memory 51 as a temporary storage area, and a non-volatile storage unit 52. The CPU 50 is an example of a processor.

[0035] The storage unit 52 is realized by a hard disk drive (HDD), a solid state drive (SSD), a flash memory, or the like. The storage unit 52 serving as a storage medium stores a control program 53. The CPU 50 reads the control program 53 from the storage unit 52, loads it into the memory 51, and executes the loaded control program 53.

[0036] The console 14 includes a CPU 60, a memory 61 used by the CPU 60 as a temporary storage area, a non-volatile storage unit 62, an input device 64 such as a keyboard and a mouse, and a display 65 such as a liquid crystal display or an EL display. The console 14 also includes an FPGA (Field Programmable Gate Array) 66 and a memory 67 used by the FPGA 66 as a temporary storage area. The CPU 60 and FPGA 66 are examples of processors. The FPGA 66 includes a logic circuit in which the logic of image processing to be performed on radiation images is pre-programmed.

[0037] The storage unit 62 is realized by an HDD, an SSD, a flash memory, or the like. The storage unit 62 serving as a storage medium stores an information processing program 63. The CPU 60 reads the information processing program 63 from the storage unit 62, loads it into the memory 61, and executes the loaded information processing program 63. The information processing program 63 is an example of a radiographic program according to the disclosed technology.

[0038] The storage unit 62 also stores a pre-registered imaging order 68. The imaging order 68 includes radiation R irradiation conditions as an example of imaging conditions for a radiographic image in fluoroscopic imaging. The imaging order 68 also includes patient information such as the age of the patient P, information on the physique of the patient P, and the region to be imaged. The storage unit 62 is an example of a storage device according to the disclosed technology.

[0039] The control device 18 includes a CPU 70, a memory 71 serving as a temporary storage area, a non-volatile storage unit 72, and an image memory 74. The CPU 70 is an example of a processor. The storage unit 72 is realized by a HDD, an SSD, a flash memory, or the like. A control program 73 is stored in the storage unit 72 serving as a storage medium. The CPU 70 reads the control program 73 from the storage unit 72, loads it into the memory 71, and executes the loaded control program 73. The image memory 74 has a storage capacity capable of storing a predetermined number of radiation images.

[0040] As shown in Fig. 4, in fluoroscopy, the imaging time for one session and the number of sessions of fluoroscopy in one examination vary depending on the fluoroscopy technique. Furthermore, in fluoroscopy, the time from the completion of one session until the start of the next session of fluoroscopy also varies depending on the fluoroscopy technique. For example, in the case of a procedure that does not require a change in the positioning of the patient P or a change in the irradiation conditions of the radiation R, the time from the completion of one session of fluoroscopy until the start of the next session of fluoroscopy is relatively short. Here, one session of fluoroscopy refers to the period from when the person performing the radiography issues an instruction to start radiography via the irradiation switch until when he or she issues an instruction to end radiography. In other words, there are also procedures in which multiple sessions of fluoroscopy are performed in one examination.

[0041] Furthermore, in fluoroscopic imaging, the FPGA 66 performs various image processing such as offset correction processing, sensitivity correction processing, and defective pixel correction processing on the radiation image of each frame, and the radiation image after image processing is temporarily stored in the memory 67. Furthermore, the radiation images stored in the memory 67 are permanently stored by being stored in the storage unit 62. The radiation images stored in the memory 67 are displayed on the display 17, allowing the person performing imaging to check the radiation image of each frame.

[0042] Generally, the speed at which data is saved in the memory 67 is higher than the speed at which data is saved in the storage unit 62. That is, in fluoroscopic imaging, the speed at which radiographic images are saved in the storage unit 62 is slower than the speed at which they are captured. The radiographic image capturing speed referred to here means the speed at which the radiation detector 11 acquires a radiographic image, the FPGA 66 performs various image processing on the radiographic image, and the radiographic image is saved in the memory 67, i.e., the speed at which the radiographic image is displayed on the display 17 so that the radiographic image can be confirmed by the radiographer. Furthermore, the speed at which radiographic images are saved in the storage unit 62 referred to here means the speed at which the radiographic images saved in the memory 67 are saved in the storage unit 62. In this embodiment, the imaging speed and saving speed are expressed in units of fps (frames per second).

[0043] Therefore, as shown in Fig. 5, at the end of one fluoroscopic imaging session, among the radiation images of each frame constituting the moving image stored in the memory 67 by that fluoroscopic imaging session, there are radiation images that have not yet been stored in the storage unit 62. In the example of Fig. 5, the shaded area represents the storage area for radiation images that have been completely stored in the storage unit 62 at the end of the fluoroscopic imaging session. In this case, it is preferable to perform the next fluoroscopic imaging session after all of the radiation images of the frames constituting the moving image have been completely stored in the storage unit 62. Therefore, the console 14 according to this embodiment has a function of notifying the user of the remaining time until the moving image is completely stored when the fluoroscopic imaging session is ended. The moving image referred to here refers to moving image data.

[0044] Next, the functional configuration of the console 14 will be described with reference to Fig. 6. As shown in Fig. 6, the console 14 includes an acquisition unit 100, a transmission unit 102, a reception unit 104, a reception unit 106, an image processing unit 108, a storage control unit 110, a display control unit 112, a calculation unit 114, and an alarm unit 116. The CPU 60 executes an information processing program 63, thereby functioning as the acquisition unit 100, the transmission unit 102, the reception unit 104, the reception unit 106, the storage control unit 110, the display control unit 112, the calculation unit 114, and the alarm unit 116. The FPGA 66 executes pre-programmed logic, thereby functioning as the image processing unit 108.

[0045] The acquisition unit 100 acquires the imaging order 68 from the storage unit 62. The transmission unit 102 transmits, to the control device 13, irradiation conditions for fluoroscopic imaging according to the imaging order 68 acquired by the acquisition unit 100.

[0046] The reception unit 104 receives a start instruction for fluoroscopic imaging input by the radiographer via the exposure switch, and also receives an end instruction for fluoroscopic imaging input by the radiographer via the exposure switch.

[0047] The receiving unit 106 receives moving images obtained by fluoroscopic imaging and transmitted from the radiation detector 11. In this embodiment, radiation images constituting the moving image are transmitted frame by frame from the radiation detector 11 to the console 14. The receiving unit 106 receives the radiation images constituting the moving image frame by frame.

[0048] The image processing unit 108 performs various image processing such as offset correction processing, sensitivity correction processing, and defective pixel correction processing on the moving image received by the receiving unit 106. The image processing unit 108 performs image processing on the radiographic images that make up the moving image for each frame, and stores the radiographic images that have undergone image processing in the memory 67.

[0049] The storage control unit 110 stores the moving image in the storage unit 62 by sequentially storing the radiation images of each frame that make up the moving image stored in the memory 67 in the storage unit 62 .

[0050] The display control unit 112 controls the display 17 to sequentially display each frame of radiographic images constituting the moving image stored in the memory 67. The display control unit 112 may also control the display 65 to display the radiation R irradiation conditions and patient information related to fluoroscopic imaging based on the imaging order 68. In addition, when the display 17 has multiple panels, the display control unit 112 may control the first panel to display the moving image obtained by fluoroscopic imaging, and the second panel to display the same screen as the display 65.

[0051] When the receiving unit 104 receives an instruction to end fluoroscopic imaging, that is, when fluoroscopic imaging is finished, the calculation unit 114 calculates the remaining time (hereinafter simply referred to as "remaining time") until the moving images obtained by fluoroscopic imaging are completely saved in the storage unit 62. In this case, the calculation unit 114 calculates the remaining time based on the data size of the moving images that have been saved in the storage unit 62 out of the moving images that have been temporarily saved in the memory 67 by fluoroscopic imaging, the data saving speed in the storage unit 62, and the data size of the moving images obtained by fluoroscopic imaging according to the frame rate and imaging time of fluoroscopic imaging.

[0052] Specifically, the calculation unit 114 calculates the remaining time according to the following equation (1). Remaining time=(data size of moving images obtained by fluoroscopic imaging−data size of moving images that have been saved in the storage unit 62) / data saving rate in the storage unit 62 (1) The data size calculated by the subtraction in the parentheses on the right side of equation (1) is the data size of the radiation image that has not yet been saved in the storage unit 62 at the time when the fluoroscopic imaging shown in FIG. 5 is completed.

[0053] For example, if the imaging speed of the fluoroscopic imaging is 15 [fps], the imaging time of the fluoroscopic imaging is 60 [sec], and the data saving speed in the memory unit 62 is 10 fps, the data size of the radiographic images that have not yet been saved in the memory unit 62 at the end of the fluoroscopic imaging can be calculated using the following equation (2). Data size of 1 frame of radiographic image × 15 [fps] × 60 [sec] - Data size of 1 frame of radiographic image × 10 [fps] × 60 = Data size of 1 frame of image × 5 [fps] × 60 (2) Furthermore, the remaining time in this case is calculated by the following equation (3). (Data size of one frame of radiographic image × 5 [fps] × 60) ÷ (Data size of one frame of radiographic image × 10 [fps]) = 30 [sec] (3)

[0054] The data storage rate in the storage unit 62 may be set in advance based on the performance evaluation results of the shipping inspection of the console 14. Alternatively, the data storage rate in the storage unit 62 may be set by a self-check by the CPU 60 when the console 14 is started up. Alternatively, the calculation unit 114 may calculate the data storage rate in the storage unit 62 by dividing the data size of the moving images that have been saved in the storage unit 62 during fluoroscopic imaging by the time required for saving the moving images in the storage unit 62. Alternatively, the calculation unit 114 may calculate the data storage rate in the storage unit 62 by dividing the data size of the moving images obtained by the most recently performed fluoroscopic imaging by the time required for saving the moving images in the storage unit 62.

[0055] The notification unit 116 notifies the remaining time calculated by the calculation unit 114. In the present embodiment, as shown in Fig. 7 as an example, the notification unit 116 notifies the person performing the imaging of the remaining time by controlling the display 17 to display the remaining time. Note that the notification unit 116 may control the display 17 to display the remaining time by counting down the remaining time as time passes.

[0056] Furthermore, the notification unit 116 may notify the remaining time by sound via an audio output device such as a speaker. In this case, the notification unit 116 may notify the remaining time by a predetermined sound such as a beep. For example, the notification unit 116 may notify the remaining time by shortening the interval between beeps as the remaining time gets shorter. The notification unit 116 may also notify the remaining time by increasing the volume of the beep as the remaining time gets shorter.

[0057] Next, the operation of the radiation imaging system 2 will be described with reference to Fig. 8. Fig. 8 is a sequence diagram showing an example of fluoroscopic imaging processing executed by the radiation imaging system 2.

[0058] When the imaging order 68 is registered, in step S10, the acquisition unit 100 acquires the imaging order 68 from the storage unit 62. Then, the transmission unit 102 transmits, to the control device 13, irradiation conditions for fluoroscopic imaging according to the imaging order 68 acquired by the acquisition unit 100.

[0059] In accordance with the radiography order 68, the radiography implementer either has the patient P stand in front of the upright radiography platform 15S or has the patient P lie supine on the top board 32 of the supine radiography platform 15L. Then, the radiography implementer inputs a command to start fluoroscopic radiography via the irradiation switch. When the command to start fluoroscopic radiography is input, in step S12, the CPU 50 of the control device 13 operates the voltage generator 12 in accordance with the irradiation conditions for fluoroscopic radiography transmitted from the console 14 in step S10, and causes the radiation tube 20 to emit radiation R. This starts the irradiation of radiation R.

[0060] In step S14, the CPU 70 of the control device 18 starts transmitting moving images obtained at a predetermined frame rate. As a result, the CPU 70 sequentially transmits the radiographic images of each frame constituting the moving images obtained by fluoroscopic imaging to the console 14. The receiving unit 106 sequentially receives the radiographic images transmitted from the radiation detector 11 in step S14.

[0061] In step S16, the image processing unit 108 performs various image processing on the radiographic image received by the receiving unit 106, as described above, and stores the processed radiographic image in the memory 67. In step S18, the display control unit 112 controls the display 17 to display the radiographic image stored in the memory 67 in step S16. The processing of steps S16 and S18 is repeatedly executed at a predetermined frame rate from the start to the end of the fluoroscopic imaging, and thereby a moving image obtained by the fluoroscopic imaging is displayed on the display 17.

[0062] In step S20, the radiographic images of each frame constituting the moving image stored in memory 67 in step S18 are sequentially stored in storage unit 62, thereby storing the moving image in storage unit 62. The processing of step S20 is executed from the start of fluoroscopic imaging until the storage of all the radiographic images of the frames constituting the moving image obtained by fluoroscopic imaging in storage unit 62 is completed.

[0063] When one fluoroscopic imaging session is completed, the imaging practitioner inputs an instruction to end the fluoroscopic imaging session via the irradiation switch. When the instruction to end the fluoroscopic imaging session is input, the CPU 50 of the control device 13 ends the irradiation of the radiation R in step S22.

[0064] Furthermore, when the receiving unit 104 receives an instruction to end fluoroscopic imaging, in step S24 the calculation unit 114 calculates the remaining time according to equation (1), as described above. In step S26, the notification unit 116 notifies the remaining time calculated in step S24, as described above. The person performing imaging recognizes the notified remaining time and makes preparations for the next fluoroscopic imaging. In the next fluoroscopic imaging, the same sequence of fluoroscopic imaging processing is executed.

[0065] As described above, according to this embodiment, it is possible to present the time until the next fluoroscopic imaging can be started after the end of the fluoroscopic imaging.

[0066] In the above embodiment, the notification unit 116 may issue a warning when the remaining time calculated by the calculation unit 114 exceeds a threshold value determined according to the fluoroscopic imaging procedure. As an example, as shown in Fig. 9, the notification unit 116 may issue a warning by controlling the display 17 to display, in addition to the remaining time, a message indicating that the remaining time has exceeded the threshold. The notification unit 116 may also issue the warning by voice via an audio output device.

[0067] Furthermore, the notification unit 116 may determine the threshold value in this embodiment according to a statistical value of the actual value of the remaining time until the next fluoroscopic imaging can be started when the previous fluoroscopic imaging has ended. Examples of the statistical value in this case include an average value or a median value. The actual value of the remaining time here is, for example, the remaining time calculated by the calculation unit 114 in the previous fluoroscopic imaging.

[0068] The notification unit 116 may also determine the threshold value in this embodiment according to a statistical value of the performance values ​​for each imaging implementer. Examples of the statistical value in this case include an average value or a median value.

[0069] Furthermore, in the above embodiment, the notification unit 116 may notify a recommended imaging time according to the fluoroscopic imaging procedure before the start of fluoroscopic imaging. Furthermore, the notification unit 116 may further notify a recommended frame rate according to the fluoroscopic imaging procedure before the start of fluoroscopic imaging. As an example, as shown in FIG. 10 , the notification unit 116 may notify the recommended imaging time and the recommended frame rate by controlling the display 17 to display the recommended imaging time and the recommended frame rate according to the fluoroscopic imaging procedure. Examples of the timing before the start of fluoroscopic imaging include the timing when an imaging order 68 is registered or the timing when the imaging implementer enters the radiography room. Furthermore, the notification unit 116 may notify the recommended imaging time and the recommended frame rate by voice via an audio output device.

[0070] Furthermore, the CPU 60 may derive the recommended frame rate based on subject information about the subject to be fluoroscopically photographed and the fluoroscopic technique. In this case, the CPU 60 may use a trained model M obtained by machine learning, which receives subject information and the technique as input and outputs a recommended frame rate. Specifically, as shown in Fig. 11, the CPU 60 may derive the recommended frame rate by inputting patient information and the fluoroscopic technique included in the imaging order 68 into the trained model M.

[0071] Furthermore, at least one of the functional units included in the console 14 in the above embodiment may be provided in the control device 13 or the control device 18.

[0072] Furthermore, in the above embodiment, the following various processors can be used as the hardware structure of a processing unit that executes various processes, such as each functional unit of the console 14. As described above, the various processors include a CPU, which is a general-purpose processor that executes software (programs) and functions as various processing units, as well as dedicated electrical circuits, such as a programmable logic device (PLD), a processor whose circuit configuration can be changed after manufacture, such as an FPGA, and an application specific integrated circuit (ASIC), which is a processor with a circuit configuration designed specifically for executing specific processes.

[0073] A single processing unit may be configured with one of these various processors, or may be configured with a combination of two or more processors of the same or different types (for example, a combination of multiple FPGAs, or a combination of a CPU and an FPGA). Also, multiple processing units may be configured with a single processor.

[0074] Examples of configuring multiple processing units with a single processor include, first, a form in which one processor is configured with a combination of one or more CPUs and software, and this processor functions as multiple processing units, as typified by computers such as client and server. Second, a form in which a processor is used to realize the functions of the entire system including multiple processing units with a single IC (Integrated Circuit) chip, as typified by systems on chips (SoCs). In this way, various processing units are configured using one or more of the above-mentioned various processors as a hardware structure.

[0075] Furthermore, more specifically, the hardware structure of these various processors can be an electric circuit that combines circuit elements such as semiconductor elements.

[0076] In the above embodiment, the various programs are pre-stored (installed) in the storage unit, but the present invention is not limited to this. The various programs may be provided in a form recorded on a recording medium such as a CD-ROM (Compact Disc Read Only Memory), a DVD-ROM (Digital Versatile Disc Read Only Memory), or a USB (Universal Serial Bus) memory. The various programs may also be downloaded from an external device via a network. [Explanation of symbols]

[0077] 2 Radiography system 10 Radiation source 11 Radiation detector 12 Voltage generator 13, 18 Control device 14 Console 15L lying position photography stand 15S Standing Photography Stand 17,65 display 20 Radiation tube 21 Irradiation field limiter 22, 29 pillars 25 Stand 26, 31 Connection 27L Supine holder 27S Standing Holder 28, 30 pedestal 32 Top plate 40 cabinets 41 Detection Panel 50, 60, 70 CPUs 51, 61, 67, 71 memory 52, 62, 72 storage section 53, 73 Control Program 63 Information Processing Program 64 Input Devices 66 FPGA 68 Photoshoot Order 74 Image Memory 100 Acquisition Department 102 Transmitter 104 Reception 106 Receiving unit 108 Image Processing Unit 110 Memory control unit 112 Display control unit 114 Calculation Unit 116 Information Department M trained models P patient R Radiation

Claims

1. A radiography system including at least one processor and capable of performing fluoroscopic photography for continuously capturing a plurality of radiographic images at a predetermined frame rate, The processor: When the fluoroscopic imaging is completed, the remaining time until the moving images obtained by the fluoroscopic imaging are completely saved in the storage device is calculated based on the data size of the moving images that have been temporarily saved in the memory by the fluoroscopic imaging and have been completely saved in the storage device, the data saving speed in the storage device, and the data size of the moving images obtained by the fluoroscopic imaging according to the frame rate and imaging time of the fluoroscopic imaging; Notify the calculated remaining time Radiography system.

2. The processor: If the calculated remaining time exceeds a threshold determined according to the fluoroscopic procedure, a notification is issued. The radiography system according to claim 1 .

3. The threshold value is determined according to a statistical value of the actual remaining time until the next fluoroscopic imaging can be started when the previous fluoroscopic imaging has ended. The radiography system according to claim 2 .

4. The threshold value is determined according to a statistical value of the performance value for each fluoroscopic imaging practitioner. The radiography system according to claim 3 .

5. The processor: Before the start of fluoroscopy, the recommended imaging time according to the fluoroscopy technique is notified. The radiation imaging system according to any one of claims 1 to 4.

6. The processor: Before the start of fluoroscopy, the recommended frame rate according to the fluoroscopy procedure is further notified. The radiography system according to claim 5 .

7. The processor: The recommended frame rate is derived based on subject information relating to the subject to be fluoroscopically photographed and the fluoroscopic technique. The radiography system according to claim 6 .

8. A radiography system including at least one processor, the processor being capable of performing fluoroscopic photography for continuously capturing a plurality of radiographic images at a predetermined frame rate, When the fluoroscopic imaging is completed, the remaining time until the moving images obtained by the fluoroscopic imaging are completely saved in the storage device is calculated based on the data size of the moving images that have been temporarily saved in the memory by the fluoroscopic imaging and have been completely saved in the storage device, the data saving speed in the storage device, and the data size of the moving images obtained by the fluoroscopic imaging according to the frame rate and imaging time of the fluoroscopic imaging; Notify the calculated remaining time The radiographic method by which the process is carried out.

9. A radiography system including at least one processor, the processor being capable of performing fluoroscopic photography for continuously capturing a plurality of radiographic images at a predetermined frame rate, When the fluoroscopic imaging is completed, the remaining time until the moving images obtained by the fluoroscopic imaging are completely saved in the storage device is calculated based on the data size of the moving images that have been temporarily saved in the memory by the fluoroscopic imaging and have been completely saved in the storage device, the data saving speed in the storage device, and the data size of the moving images obtained by the fluoroscopic imaging according to the frame rate and imaging time of the fluoroscopic imaging; Notify the calculated remaining time A radiography program to carry out the process.

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