JP5063391B2 - Radiation imaging apparatus and driving method thereof - Google Patents

Description

  The present invention relates to a radiographic image capturing apparatus that captures a radiographic image and a driving method thereof.

  Conventionally, various photographing such as IVR (Interventional Radiology) and fluoroscopic photographing has been performed using an X-ray image photographing system (X-ray image photographing device) capable of photographing a moving image.

  At this time, for example, an X-ray generator included in an X-ray imaging system, in principle, has a structure that generates a large amount of heat. It was. Therefore, conventionally, for example, when the temperature is increased on the X-ray generator side, a value estimated from the past imaging history is accumulated as the accumulated heat amount. With a certain capacity (tube voltage, tube current), X The generation of X-rays from the X-ray generator is limited. In addition, when X-rays are generated from the X-ray generator for a long time, threshold processing is performed based on the generation time, and a warning is issued by a warning sound (beep sound) or light (blinking lamp). .

  Further, since the main body side of the X-ray imaging apparatus employs a method of displaying an image by transferring a video signal acquired by an imaging means such as an imaging tube to an monitor through an analog line, X-ray imaging is not necessarily performed. There was little need to perform time control with the heat on the main body side of the device.

  That is, conventionally, an X-ray imaging system (X-ray imaging apparatus) has a time during which X-rays cannot be generated due to heat inside the X-ray imaging system (specifically, an X-ray tube).

JP 2001-351091 A JP 2002-593 A

  However, when performing X-ray photography for a long time, if there is a time during which X-rays cannot be generated due to the heat limitation of the X-ray tube described above, doctors and technicians at a desired timing that they really want to take, There was a possibility that an X-ray image could not be acquired.

  In particular, in the X-ray imaging apparatus using a semiconductor as the imaging means, it is possible to capture and store a plurality of X-ray images in a single time as compared with the prior art, so the above-described problem is more remarkable. become. In addition, in the X-ray imaging apparatus using a semiconductor as the imaging means, various new imaging modes are possible including long-time X-ray imaging. Will be subject to restrictions.

  Further, even on the main body side of an X-ray imaging apparatus using a semiconductor as an imaging means, if a moving image is taken and a long-time X-ray is taken, the temperature may rise. In this case, if the white image, which is a sensitivity correction image, has temperature characteristics, the white correction (sensitivity correction) is not effective due to the temperature change described above, and a secondary problem arises that an optimum image quality cannot be obtained (for example, , See Patent Document 1).

  That is, in a conventional X-ray imaging apparatus (radiation imaging apparatus), when imaging takes a long time, there is a possibility that an X-ray image (radiation image) cannot be acquired at a desired timing due to a rise in the temperature inside. In addition, there is a problem that an optimum image quality cannot be obtained.

  The present invention has been made in view of the above-described problems, and is capable of acquiring a radiographic image at a desired timing even when imaging is performed for a long time and obtaining an optimum image quality. Objective.

  The radiographic imaging device of the present invention includes a radiation generating unit that generates radiation on a subject, an imaging unit that captures a radiographic image based on the radiation transmitted through the subject, the radiation generating unit, and the imaging unit. Detection means for detecting internal information related to the temperature inside the device itself, and a frame rate for changing a frame rate of a radiographic image captured by the imaging means based on the internal information related to the temperature detected by the detection means Change means.

  The method for driving a radiographic imaging device of the present invention drives a radiographic imaging device including radiation generating means for generating radiation on a subject and imaging means for capturing a radiographic image based on the radiation transmitted through the subject. A detection step of detecting internal information relating to the internal temperature of the radiographic imaging device, and a radiographic image captured by the imaging means based on the internal information relating to the temperature detected in the detection step A frame rate changing step for changing the frame rate.

  According to the present invention, a radiographic image can be acquired at a desired timing even when imaging is performed for a long time, and an optimal radiographic image quality can be obtained.

  The best mode for carrying out the present invention will be described below in detail with reference to the accompanying drawings.

  In the following description of embodiments of the radiographic imaging apparatus according to the present invention, an example of an X-ray imaging apparatus that applies X-rays as radiation is shown, but the present invention is not limited to this. The radiation of the present invention is not limited to X-rays, and includes, for example, α-rays, β-rays, γ-rays, and the like, and an apparatus for processing a radiographic image captured using these radiations is also included in the present invention. Shall be.

(First embodiment)
FIG. 1 is a block diagram illustrating an example of a schematic configuration of an X-ray imaging apparatus (radiation imaging apparatus) according to an embodiment of the present invention.

  In the X-ray imaging apparatus 100 shown in FIG. 1, an X-ray generation apparatus 101 is a radiation generation unit that generates X-ray 101 a that is radiation, and X-rays of an X-ray beam with respect to a subject (subject) 300. 101a is irradiated. The X-ray generation apparatus 101 is connected to the X-ray generation apparatus control unit 103, and is configured to be controllable based on an output from the X-ray generation apparatus control unit 103.

  The two-dimensional X-ray sensor 102 is an imaging unit that detects an X-ray image signal irradiated from the X-ray generation apparatus 101 and transmitted through the subject 300 as an X-ray image signal and images the subject 300. . In the present embodiment, the two-dimensional X-ray sensor 102 captures a plurality of X-ray images within a unit time. In the two-dimensional X-ray sensor 102, for example, pixels that detect incident X-rays as X-ray image signals are two-dimensionally arranged. Further, for example, the pixels constituting the two-dimensional X-ray sensor 102 are formed of a semiconductor. The two-dimensional X-ray sensor 102 is connected to the A / D conversion unit 104 and the CPU bus 110.

  As shown in FIG. 1, the X-ray generator 101 and the two-dimensional X-ray sensor 102 are provided at both ends of the C arm, and are arranged to face each other with the subject 300 interposed therebetween.

  The A / D conversion unit 104 performs analog / digital conversion processing on the X-ray image signal output from the two-dimensional X-ray sensor 102, and outputs this as X-ray image data. The amplifier amplification unit 105 performs amplification processing on the X-ray image data output from the A / D conversion unit 104. The X-ray image data processed by the amplifier amplification unit 105 is then processed by, for example, the preprocessing unit 116.

  The X-ray imaging apparatus 100 is provided with a detection unit that detects internal information relating to the internal temperature of the own apparatus (X-ray imaging apparatus 100) including the X-ray generation apparatus 101 and the two-dimensional X-ray sensor 102. Yes. Specifically, in the present embodiment, a first internal information detection unit 106 and a second internal information detection unit 107 are provided.

  The first internal information detection unit 106 detects internal information related to the temperature of the X-ray generator 101. The second internal information detection unit 107 detects internal information related to the temperature of the two-dimensional X-ray sensor 102.

  The first cooling unit 108 is for cooling the X-ray generator 101. The second cooling unit 109 is for cooling the two-dimensional X-ray sensor 102.

  These two-dimensional X-ray sensor 102, X-ray generator control unit 103, amplifier amplification unit 105, first internal information detection unit 106, second internal information detection unit 107, first cooling unit 108, and first The second cooling unit 109 is connected to the CPU bus 110. Further, the CPU bus 110 includes a CPU 111, a main memory 112, an operation panel 113, an image display unit 114, a shooting driving condition determination unit 115, a preprocessing unit 116, an image processing unit 117, a storage unit 118, and a frame rate determination. The unit 119 is connected. Further, a frame rate return instruction unit 120, an X-ray dose detection unit 121, and an image processing unit 122 for detecting internal information are connected to the CPU bus 110.

  The main memory 112 stores programs and various data necessary for processing executed by the CPU 111 and functions as a working memory for the CPU 111. The CPU 111 performs operation control and the like related to the entire X-ray imaging apparatus 100 in accordance with a user operation from the operation panel 113 using programs and various data stored in the main memory 112.

  When a shooting instruction is input from the user via the operation panel 113, the shooting instruction information is stored in the storage unit 118 and displayed on the operation panel 113. At this time, the photographing instruction is transmitted from the CPU 111 to the photographing driving condition determining unit 115 via the CPU bus 110. Then, the imaging driving condition determination unit 115 determines the driving conditions of the X-ray generator 101, the two-dimensional X-ray sensor 102, and the like at the time of imaging in response to an imaging instruction from the CPU 111. When the imaging driving condition determining unit 115 determines the imaging driving condition, the CPU 111 controls the X-ray generating apparatus 101 via the X-ray generating apparatus control unit 103 based on the driving condition. The dimensional X-ray sensor 102 is controlled to perform X-ray imaging.

  In the X-ray imaging, first, the X-ray 101a is irradiated from the X-ray generator 101 to the subject 300. The emitted X-ray 101 a passes through the subject 300 while being attenuated, and reaches the two-dimensional X-ray sensor 102. The two-dimensional X-ray sensor 102 serving as radiation detection means detects the incident X-ray 101a as an X-ray image signal. In the present embodiment, a human body is applied as an example of the subject 300. For this reason, the X-ray image output from the two-dimensional X-ray sensor 102 is a human body image.

  The A / D conversion unit 104 converts the X-ray image signal output from the two-dimensional X-ray sensor 102 into a predetermined digital signal, which is converted into X-ray image data via the amplifier amplification unit 105 as a preprocessing unit 116. To supply. The preprocessing unit 116 performs preprocessing such as dark current correction processing and gain correction processing on the X-ray image data from the amplifier amplification unit 105. The preprocessed X-ray image data is transferred as original image data to the main memory 112 and the image processing unit 117 via the CPU bus 110 under the control of the CPU 111.

  When X-ray imaging for a certain period of time using the X-ray generator 101 and the two-dimensional X-ray sensor 102 is performed, the internal states of the X-ray generator 101 and the two-dimensional X-ray sensor 102 change. In the X-ray generator 101 and the two-dimensional X-ray sensor 102, examples of the internal state that changes include heat. What cools the heat of the X-ray generator 101 and the two-dimensional X-ray sensor 102 is a first cooling unit 108 and a second cooling unit 109, respectively.

  As described above, the first internal information detection unit 106 and the second internal information detection unit 107 detect internal information related to the temperatures of the X-ray generator 101 and the two-dimensional X-ray sensor 102, respectively. The internal information related to this temperature is acquired as needed. The internal information relating to the temperature is preferably information on temperature that is an index of heat generation (that is, information on the temperature itself). However, in the present embodiment, the internal information relating to the temperature is not limited to the information of the temperature itself. For example, the internal information related to the temperature may be information related to the temperature, specifically, information indicating the cause of the temperature change, information indicating the phenomenon due to the temperature change, or the same factor as the factor causing the temperature change. It is also possible to apply information indicating the phenomenon that is caused. For example, the information indicating the cause of the temperature change includes these electric power values and an electrical index necessary for obtaining the electric power value. Further, for example, information indicating a phenomenon due to a temperature change includes the temperature of the surface of the casing, the temperature detected by each corresponding cooling unit, and the like.

  When the internal information relating to the temperature detected by the first internal information detection unit 106 and the second internal information detection unit 107 exceeds a specific threshold value, the frame rate determination unit 119 performs threshold processing. Then, based on the output value of the threshold processing by the frame rate determination unit 119, the imaging drive condition determination unit 115 drives the X-ray generator 101, the two-dimensional X-ray sensor 102, and the like so that imaging cannot be performed at a specific frame rate or higher. Determine the conditions.

  Note that the frame rate in the present embodiment is regarded as one of indices indicating how many X-ray images (radiation images) can be captured per second in moving image X-ray imaging. Here, the unit of frame rate is fps (frame per second). For example, when the frame rate is 30 fps, 30 X-ray images (radiation images) are captured per second. In principle, X-ray imaging at a frame rate higher than the scanning frequency (refresh rate) of the two-dimensional X-ray sensor 102 cannot be performed.

  The imaging drive condition determination unit 115 performs control to change the frame rate (imaging frame rate) in the two-dimensional X-ray sensor 102 to the frame rate determined and determined by the frame rate determination unit 119 under the control of the CPU. That is, the photographing drive condition determining unit 115 that performs this control constitutes a frame rate changing unit. In addition, the imaging drive condition determination unit 115 sends a synchronization signal related to the frame rate determined and determined by the frame rate determination unit 119 to the X-ray generation device control unit 103 under the control of the CPU. When the X-ray generator control unit 103 receives the synchronization signal from the imaging drive condition determination unit 115, the X-ray generator 101 controls the pulse of the X-ray 101a based on the synchronization signal, that is, at a frame rate corresponding to the two-dimensional X-ray sensor 102. The X-ray generator 101 is controlled so as to occur.

  In addition, as will be described in detail in a second embodiment described later, the user requests shooting that gives priority to the shooting conditions instructed by the user with respect to the system restrictions in consideration of the durability of the apparatus, as necessary. It is assumed that the best mode is to use the frame rate return instruction unit 120 when performing the above. At this time, when the user really wants to take a picture, the user is able to cancel the validity of the restriction that the picture cannot be taken at a specific frame rate or higher via the operation panel 113. However, in this method of use, since the photographing is continued at a high temperature or the like, the durability of the apparatus may be reduced. For example, in the X-ray generation apparatus 101, a metal part called a target with which electrons collide is in a vacuum, but when a high temperature is reached, the metal part of the target melts and adheres to the package surface of the vacuum part. For this reason, since the said metal part becomes easy to generate | occur | produce in a vacuum etc., there exists a possibility that durability of an apparatus may fall. Such a reactive fact is desirably displayed on the operation panel 113 when the priority order is changed, for example.

  The image processing unit 122 and the X-ray dose detection unit 121 for detecting internal information shown in FIG. 1 will be described in detail in a third embodiment and a fourth embodiment described later. Information (information correlated with temperature) obtained by the X-ray dose detection unit 121 and the image processing unit 122 for detecting internal information becomes information for the frame rate determination unit 119 to determine the frame rate. That is, the information obtained by each of these units serves as alternative information or an interpolation index in the internal information relating to the temperature detected by the first internal information detection unit 106 and the second internal information detection unit 107.

  The two-dimensional X-ray sensor 102 that is an X-ray image detector has a temperature-dependent element. Therefore, it can be considered that the sensitivity of the two-dimensional X-ray sensor 102 changes depending on the temperature. In the X-ray imaging apparatus 100 including the two-dimensional X-ray sensor 102 formed of a semiconductor in this embodiment, the preprocessing unit 116 performs gain correction related to the sensitivity of the two-dimensional X-ray sensor 102. Therefore, in the gain correction in the preprocessing unit 116, not only the sensitivity depending on the temperature of the two-dimensional X-ray sensor 102 but also the correction related to the sensitivity depending on the temperature of the A / D conversion unit 104 and the amplifier amplification unit 105 is performed. It will be.

  FIG. 2 is a schematic diagram illustrating an example of an X-ray image capturing system (radiation image capturing system) to which the X-ray image capturing apparatus (radiation image capturing apparatus) illustrated in FIG. 1 is applied. 2, the same reference numerals are given to the same configurations as those in FIG. 1.

  FIG. 2 shows a system using a C-arm that can shoot moving images. Specifically, an X-ray imaging system having a C arm 202 rotatably supported on a stand 201 is shown. An X-ray generator 101 and a two-dimensional X-ray sensor 102 which is an X-ray image detector are attached to the end of the C arm 202. The PC 203 includes, for example, the components 103, 110 to 112, and 115 to 122 shown in FIG. In FIG. 2, the first cooling unit 108 and the second cooling unit 109 shown in FIG. 1 are not shown.

  In FIG. 2, a floor mount or a ceiling mount can be used instead of the stand 201. Further, it may be possible to attach the two-dimensional X-ray sensor 102 on the stand 201 similarly to the still image X-ray imaging apparatus with a structure without the C-arm 202.

  A subject 300 to be irradiated with X-rays by the X-ray generator 101 is disposed on the patient bed 204. The patient bed 204 is generally formed having a table plate 204a and a mattress 204b.

  The X-ray generator 101 includes an X-ray tube 205 that generates X-rays, and a diaphragm 206 having a collimator and a pre-filter. For example, the X-ray generation apparatus 101 generates X-rays after receiving an X-ray exposure permission signal from the CPU 111 (or the X-ray generation apparatus control unit 103) in the PC 203, for example. The X-ray generation apparatus 101 is provided with a first internal information detection unit 106 that is applied as a temperature detection sensor, for example.

  In front of the two-dimensional X-ray sensor 102, a scattered X-ray removal grid 207 is disposed. The scattered X-ray removal grid 207 reduces the incidence of X-rays scattered by the inspection object, in this case, the subject 300, to the two-dimensional X-ray sensor 102. X-rays attenuated according to the X-ray transmittance of the subject 300 enter the two-dimensional X-ray sensor 102.

  The two-dimensional X-ray sensor 102 uses, for example, a pixel using a photoelectric conversion element and a phosphor made of amorphous silicon, a pixel using a photoelectric conversion element and a phosphor of a CMOS sensor, and a conversion element made of amorphous selenium. What was there. Here, in the thing using the photoelectric conversion element and the phosphor, the incident X-ray is converted into light by the phosphor, the light converted by the phosphor is converted into an electric signal (charge) by the photoelectric conversion element, An X-ray image signal is obtained. Moreover, in the case of using a conversion element made of amorphous selenium, an incident X-ray is directly converted into an electric signal (charge) to obtain an X-ray image signal. In the two-dimensional X-ray sensor 102, although there is an upper limit of the frame rate, it is variable.

  The X-ray generator 101 is provided with a second internal information detection unit 107 that is applied as a temperature detection sensor, for example. Further, in the example shown in FIG. 2, a temperature detection sensor 208 is installed in the A / D conversion unit 104 and the amplifier amplification unit 105. The temperature detection sensor 208 desirably measures the temperature at the previous stage of the amplifier amplification unit 105, for example. This is because, from the viewpoint of image quality, since the signal is amplified after the amplifier amplification unit 105, the amount of influence of temperature is small. In this case, for example, the preprocessing unit 116 performs gain correction of the X-ray image data based on the temperature detected by the second internal information detection unit 107 and the temperature detected by the temperature detection sensor 208. Also good. In this case, for example, the frame rate determination unit 119 sets the temperature detected by the temperature detection sensor 208 in addition to the temperature detected by the first internal information detection unit 106 and the second internal information detection unit 107. Based on this, the frame rate may be determined.

  In addition, the object whose temperature is detected by the second internal information detection unit 107 is not necessarily limited to the photoelectric conversion element of the two-dimensional X-ray sensor 102. For example, any object capable of detecting the temperature in the vicinity thereof can be used. good. When detecting the temperature near the photoelectric conversion element, for example, the temperature may be detected using a temperature detector provided on the substrate of the two-dimensional X-ray sensor 102.

  An output signal of the two-dimensional X-ray sensor 102 which is an X-ray image detector is subjected to dark current image correction, gain correction, and the like in the preprocessing unit 116 in the PC 203 via the A / D conversion unit 104 and the amplifier amplification unit 105. Is pre-processed. At this time, it is desirable to acquire an image for dark current correction and an image for gain correction before photographing each X-ray image. In the case where an amplifier can be mounted in a pixel as in a CMOS sensor, it goes without saying that the implementation of the present invention is not affected even if the order of signal processing is different.

  Thereafter, the pre-processed X-ray image data is supplied to the preview image display unit 209, and an X-ray image based on the X-ray image data is displayed through predetermined image processing. Further, the X-ray image data is sent to the monitor device 210 via the PC 203. The monitor device 210 includes an image display unit 114 that displays an X-ray image based on X-ray image data that has been subjected to image processing by the image processing unit 117, an operation panel 113, and an observation monitor. Yes.

  The light output device 211 is a signal for informing, for example, when X-rays are emitted from the X-ray generator 101. In the present embodiment, the frame rate may be adjusted to a setting different from the instruction value during long-time X-ray photography. In such a case, the light output of the light output device 211 is turned on, for example. It is desirable to notify.

  FIG. 3 is a flowchart illustrating an example of a processing procedure of the X-ray imaging apparatus (radiation imaging apparatus) according to the first embodiment of the present invention. Here, the flowchart shown in FIG. 3 is performed, for example, when the CPU 111 executes a program stored in the main memory 112 and controls each device of the X-ray imaging apparatus 100 shown in FIG.

  First, when a user (user) inputs shooting conditions via the operation panel 113, in step S301, the CPU 111 performs processing for setting shooting conditions. At this time, under the control of the CPU 111, the imaging driving condition determination unit 115 determines the driving conditions of the X-ray generator 101, the two-dimensional X-ray sensor 102, and the like at the time of imaging, and the driving conditions are also set. In this example, in the setting of the shooting conditions in step S301, shooting end conditions (for example, shooting time or number of shots) are also set.

  Subsequently, in step S302, the CPU 111 starts X-ray imaging based on the imaging conditions set in step S301 when, for example, the imaging start button is operated by the user (user). Here, in this embodiment, a high-throughput X-ray image capturing apparatus that captures a plurality of X-ray images per unit time or a moving image X-ray image capturing apparatus that can be used for fluoroscopy and IVR is used. It is assumed that it will be used for X-ray imaging.

  Subsequently, in step S303, the CPU 111 continues the X-ray imaging in step S302.

  Subsequently, in step S304, for example, the frame rate determination unit 119 determines that the internal information relating to the temperature detected by the first internal information detection unit 106 and the second internal information detection unit 107 is OK under the control of the CPU 111. Determine whether or not. At this time, in step S304, among the internal information related to the temperatures detected by the first internal information detection unit 106 and the second internal information detection unit 107, the internal information related to both temperatures is OK. It is determined to be OK.

  The internal information relating to the temperature detected by the first internal information detection unit 106 and the second internal information detection unit 107 is an index that changes particularly when long-time X-ray imaging is performed. Here, as the internal information relating to this temperature, for example, information on the temperature itself is applied. When long-time X-ray imaging is performed continuously, the first cooling unit 108 and the second cooling unit 109 are provided, but in principle, the X-ray generator 101 (X-ray tube 205) and the second cooling unit 109 are provided. The temperature of the X-ray imaging apparatus 100 such as the dimensional X-ray sensor 102 will rise. In the best mode in the present embodiment, the actually measured temperature is used instead of the predicted value as the internal information relating to this temperature.

  Regarding the temperature detection method, the first internal information detection unit 106 and the second internal information detection unit 107 are respectively connected to the X-ray generator 101 (X-ray tube 205) and the two-dimensional X-ray sensor 102 (for example, an amplifier). Install in a place near heat generation (near the IC) and acquire it every hour. Detailed contents of the determination process in the internal information relating to each temperature in step S304 will be described later with reference to FIG.

  If it is determined as NG as a result of the determination in step S304 (S304 / NO), the process proceeds to step S305. In step S305, the shooting-time drive condition determination unit 115 performs control to change the shooting frame rate based on the determination result in the frame rate determination unit 119 under the control of the CPU. Here, when the frame rate determination unit 119 determines that at least the temperature detected by the first internal information detection unit 106 or the second internal information detection unit 107 exceeds a specific threshold, the shooting frame rate is set. Perform the lowering process.

  Subsequently, in step S306, the CPU 111 performs a process of displaying the actual shooting frame rate changed in step S305, for example, on the operation panel 113 (or the image display unit 114). Thereby, the frame rate set in step S301 can be changed by the internal processing of the X-ray imaging apparatus 100 to inform the user (user) of the actual frame rate. Thereafter, the process returns to step S303.

  On the other hand, if it is determined that the result of step S304 is OK (S304 / YES), the process proceeds to step S307. In step S307, the CPU 111 determines whether to end shooting based on the shooting end condition set in step S301.

  As a result of the determination in step S307, if shooting is not completed (S307 / NO), that is, if shooting is continued, the process returns to step S303.

  On the other hand, if the result of determination in step S307 is that shooting is to end (S307 / YES), processing proceeds to step S308. In step S308, the CPU 111 performs shooting end processing. Thereafter, the flowchart shown in FIG. 3 ends.

  In the example illustrated in FIG. 3, the shooting frame rate is determined by the shooting driving condition determination unit 115 so as to gradually decrease the shooting frame rate by periodically repeating the loop of steps S303 to S306. With the processing of the flowchart shown in FIG. 3, it is possible to avoid a problem that X-ray imaging cannot be performed due to a limitation due to heat generation of the X-ray generator 101 (X-ray tube 205), and imaging can be performed for a longer time.

Next, an example of the operation screen on the operation panel 113 in the first embodiment will be described.
FIG. 4 is a schematic diagram illustrating an example of an operation screen of the operation panel 113 of the X-ray imaging apparatus according to the first embodiment of the present invention. Here, FIG. 4 shows an example of an operation screen on the operation panel 113 before the shooting frame rate change control is performed.

  In the X-ray moving image imaging system of the present embodiment, actual X-ray imaging is started under the same conditions as the imaging conditions set by the user (user) as shown in step S302 shown in FIG.

  At the top of FIG. 4, an actual shooting condition 401 indicating a shooting condition that is actually shot is displayed. In the next line, a user instruction condition 402 indicating a photographing condition input by the user is displayed. At the time when imaging is started in step S302, since a lot of time has not passed, there is no change in the temperatures of the X-ray generator 101, the two-dimensional X-ray sensor 102, and the like. Accordingly, X-ray imaging is performed under the same imaging conditions as the imaging conditions input by the user. However, since there is a time when the imaging condition of the X-ray imaging apparatus 100 does not necessarily match the imaging condition input by the user due to some limitation, a function for displaying both is provided.

  FIG. 5 is a schematic diagram illustrating an example of an operation screen of the operation panel 113 of the X-ray imaging apparatus according to the first embodiment of the present invention. Here, FIG. 5 shows an example of an operation screen on the operation panel 113 after the shooting frame rate is changed. Specifically, an example of the operation screen of the operation panel 113 when the internal information related to the temperature is determined to be NG in step S304 and the shooting frame rate is changed in step S305 is shown.

  In FIG. 5, the shooting condition input by the user is displayed in the user instruction condition 503. As the imaging time becomes longer, internal information relating to the temperatures of the X-ray generator 101 and the two-dimensional X-ray sensor 102 (in this example, information on the temperature itself) becomes higher. In FIG. 5, after the frame rate determination unit 119 determines that the detected value of the temperature exceeds the threshold value and decreases the frame rate, the shooting drive condition determination unit 115 decreases the shooting frame rate. It is an example of an operation screen. Specifically, the shooting frame rate after the shooting frame rate is lowered is shown in the actual shooting condition 502.

  In the present embodiment, not only the frame rate or the like is reduced, but also the reason 501 for reducing the frame rate is displayed on the operation panel 113. The operation panel 113 also displays items and amounts that have changed due to limitations of the X-ray imaging apparatus 100 such as a frame rate.

  FIG. 6 is a timing chart showing the relationship between the X-rays radiated (exposed) from the X-ray generator 101 shown in FIG. 1 and the frame rate. FIG. 6A shows a timing chart when the frame rate is 30 fps, and FIG. 6B shows a timing chart when the frame rate is 15 fps.

  In the two-dimensional X-ray sensor 102, as shown in FIG. 6 (b), since the frame time decreases, the read time interval becomes longer, so that the minimum required power consumption can be reduced. , Heat generation can be reduced.

  In the two-dimensional X-ray sensor 102 using a semiconductor, the amount of dark current changes as the accumulation time (WAIT time) increases. In the preprocessing unit 116, dark current correction and gain correction are mainly performed. Correcting the dark current due to the difference in the accumulation time is dark current correction. In the present embodiment, since it is assumed that the frame rate is changed one by one, for example, it is desirable to hold a dark current image along each change table in advance and use it for dark current correction. The gain correction is the same as the dark current correction.

  FIG. 7 is a schematic diagram for explaining determination criteria in the frame rate determination process performed by the frame rate determination unit 119 shown in FIG. In FIG. 7, time [s] is taken on the horizontal axis and temperature is taken on the vertical axis in order to explain the frame rate determination criteria.

  In FIG. 7, if the cooling capacity of the cooling unit and the heat generation amount of the X-ray generator 101 (or two-dimensional X-ray sensor 102) are balanced, the X-ray generator 101 (or two-dimensional X-ray sensor 102) The temperature is constant. If the cooling capacity of the cooling unit is higher than the heat generation amount of the X-ray generator 101 (or the two-dimensional X-ray sensor 102), the temperature decreases. On the other hand, if the heat generation amount of the X-ray generator 101 (or the two-dimensional X-ray sensor 102) is higher than the cooling capacity of the cooling unit, the temperature increases.

7, the initial temperature of the X-ray generator 101 (or two-dimensional X-ray sensor 102) is the initial temperature C _0. This initial temperature C ₀ is substantially equal to the temperature of the environment where the apparatus is placed. In an X-ray imaging system using a two-dimensional X-ray sensor 102 using a semiconductor, it is assumed that the system is used in an air-conditioned facility in a hospital. Therefore, the environment where the apparatus is placed is a temperature of 5 ° C. to 35 ° C. (humidity 30% RH to 75% RH).

  Specifically, as shown in FIG. 7, since the heat generation amount increases as the frame rate is changed from 7.5 fps to 10 fps and further increased to 15 fps, the threshold value C to the threshold value related to the temperature depends on each frame rate. A is set. Here, the reason why the heat generation amount increases as the frame rate increases is that the readout time per unit time increases, and in this case, the heat generation amount uniquely increases.

  In step S304, first, as shown in FIG. 7, each of the first internal information detection unit 106 and the second internal information detection unit 107 is based on the frame rate of the currently performed X-ray imaging. Set the threshold. Then, the temperatures detected by the first internal information detection unit 106 and the second internal information detection unit 107 are respectively compared with the corresponding threshold values. If the threshold values are exceeded, it is determined as NG. The

  As a cooling method of the cooling units (108 and 109) in this embodiment, for example, water cooling or air cooling can be considered. When the cooling capacity is changed depending on the frame rate, the temperature threshold at each frame rate shown on the vertical axis changes depending on the relative relationship with the heat generation amount.

  In FIG. 7, the temperature distribution when the frame rate reduction control process according to the present embodiment is performed and when the frame rate decrease control process according to the present embodiment is not performed are indicated by a broken line and a solid line, respectively. ing. When the frame rate decrease control process is not performed in the X-ray imaging apparatus 100 of the present embodiment, the temperature increases with the passage of time as shown by the temperature distribution shown by the solid line in FIG. On the other hand, in the X-ray imaging apparatus 100 according to the present embodiment, when the temperature rises, a change process that lowers the frame rate is performed, so the amount of temperature rise is similar to the temperature distribution indicated by the broken line in FIG. Reduced. As a result, it is possible to perform X-ray imaging for a longer time within the temperature tolerance of the X-ray generator 101 or the like.

  In the present embodiment, an example is shown in which the frame rate is controlled not to exceed a certain value when the temperature exceeds a certain value. However, the present invention is not limited to this example. . For example, even when the amount of temperature increase per unit time, for example, when the slope in the temperature distribution in FIG. 7 exceeds a certain value, the frame rate is controlled so as not to exceed a certain value. it can.

  Next, advantages of the two-dimensional X-ray sensor 102 and the X-ray generator 101 due to the decrease in the frame rate will be described.

First, advantages of the two-dimensional X-ray sensor 102 due to the decrease in the frame rate will be described from the viewpoint of heat.
As the frame rate decreases, the readout time on the signal line in the two-dimensional X-ray sensor 102 per unit time is shortened. The main cause of heat generation in the two-dimensional X-ray sensor 102 is the amplifier IC. As the frame rate decreases, the time period during which the voltage (or current) of the power supply of the amplifier IC is weakened increases. Note that the effect of reducing heat due to the temporal voltage (or current) strength of the power supply of the amplifier IC is disclosed in, for example, Patent Document 2 described above.

Next, advantages of the X-ray generation apparatus 101 due to the decrease in the frame rate will be described from the viewpoint of heat.
In the X-ray generator 101, electrons emitted from the cathode of the X-ray tube 205 lose energy when they hit a target such as tungsten, and X-rays and heat are generated as by-products. From the viewpoint of energy distribution, the energy used for generating heat is larger than the energy used for generating X-rays, and heat is generated very much. By reducing the frame rate, the time for which electrons hit the target can be shortened, so heat generation can be reduced.

As described above, the X-ray imaging apparatus 100 of the present embodiment detects internal information related to the temperature inside the X-ray imaging apparatus 100 and performs imaging based on the internal information related to the temperature. The frame rate of the line image is changed. Specifically, when the internal information related to temperature exceeds a predetermined threshold, a change is made to reduce the frame rate.
According to such a configuration, it is possible to suppress an increase in temperature inside the X-ray imaging apparatus 100 even when imaging is performed for a long time. Accordingly, it is possible to avoid the stop of the imaging due to the temperature rise, so that the X-ray image can be acquired at a desired timing. Further, since the temperature rise inside the X-ray imaging apparatus 100 can be suppressed, even if the white image for sensitivity correction has a temperature characteristic, the influence can be reduced, and the optimum Therefore, it is possible to obtain a good X-ray image quality. Furthermore, since the temperature rise inside the X-ray imaging apparatus 100 (particularly, the X-ray generation apparatus 101) can be suppressed, it is possible to prevent deterioration of durability due to heat of the X-ray imaging apparatus 100. Become.

(Second Embodiment)
Next, a second embodiment of the present invention will be described.
FIG. 8 is a flowchart showing an example of a processing procedure of the X-ray imaging apparatus (radiation imaging apparatus) according to the second embodiment of the present invention. Here, the flowchart shown in FIG. 8 is performed, for example, when the CPU 111 executes a program stored in the main memory 112 and controls each device of the X-ray imaging apparatus 100 shown in FIG.

  First, when a user (user) inputs shooting conditions via the operation panel 113, the CPU 111 performs processing for setting shooting conditions in step S801. At this time, under the control of the CPU 111, the imaging driving condition determination unit 115 determines the driving conditions of the X-ray generator 101, the two-dimensional X-ray sensor 102, and the like at the time of imaging, and the driving conditions are also set. In this example, in the setting of the shooting conditions in step S801, shooting end conditions (for example, shooting time or number of shots) are also set.

  Subsequently, in step S802, the CPU 111 performs X-ray imaging based on the imaging conditions set in step S801, for example, when a user (user) operates an imaging start button (or X-ray exposure button). Start.

  Subsequently, in step S803, the CPU 111 continues the X-ray imaging (moving image imaging or the like) in step S802.

  Subsequently, in step S804, for example, the frame rate determination unit 119 determines that the internal information relating to the temperature detected by the first internal information detection unit 106 and the second internal information detection unit 107 is OK under the control of the CPU 111. Determine whether or not. The details of the determination in step S804 are the same as the determination in step S304 described in the first embodiment, and thus description thereof is omitted.

  If it is determined as NG as a result of the determination in step S804 (S804 / NO), the process proceeds to step S805. In step S805, the shooting-time drive condition determination unit 115 performs control to change the shooting frame rate based on the determination result in the frame rate determination unit 119 under the control of the CPU. Here, when the frame rate determination unit 119 determines that at least the temperature detected by the first internal information detection unit 106 or the second internal information detection unit 107 exceeds a specific threshold, the shooting frame rate is set. Perform the lowering process.

  Subsequently, in step S806, the CPU 111 performs a process of displaying the actual shooting frame rate changed in step S805, for example, on the operation panel 113 (or the image display unit 114). As a result, the user (user) can be notified of the actual frame rate by changing the frame rate set in step S801 by the internal processing of the X-ray imaging apparatus 100. Thereafter, the process returns to step S803.

  In the example shown in FIG. 8, by repeating the loop of steps S803 to S806 regularly, the heat generation of the X-ray generator 101 and the two-dimensional X-ray sensor 102 is suppressed while reducing the frame rate even during long-time imaging. X-ray imaging can be continued.

  On the other hand, if it is determined as OK as a result of the determination in step S804 (S804 / YES), the process proceeds to step S807. In step S807, the CPU 111 continues the X-ray imaging (moving image imaging or the like) in step S802.

Subsequently, the process proceeds to step S808.
Before describing the processing in step S808, the “priority” used in the second embodiment will be described.

  The “priority” used in the second embodiment indicates a priority between “user (user) instruction content” and “system restriction content”. Here, “the instruction content of the user (user)” includes, for example, the photographing conditions input by the user in step S801. The “system restriction content” includes, for example, the frame rate restriction (frame rate reduction) performed inside the X-ray imaging apparatus 100 in step S805. In the present embodiment, it is assumed that the priority of “system restriction contents” is set higher in the initial setting (default).

  In step S808, the CPU 111 determines whether or not the priority of the “user (user) instruction content” is higher than the “system restriction content” priority according to an input instruction from the user (user). Judging. That is, in step S808, it is determined whether or not the priority has been changed between “user (user) instruction content” and “system restriction content” with respect to the initial setting (default).

  As a result of the determination in step S808, when the priority of “user (user) instruction content” is higher than the priority of “system restriction content” (S808 / YES), the process proceeds to step S809. In step S809, the CPU 111 instructs the shooting-time drive condition determination unit 115 to perform shooting based on the shooting conditions from the user rather than the durability of the system. In this case, the CPU 111 cancels the effectiveness of changing the frame rate by the shooting-time drive condition determining unit 115 which is a frame rate changing unit. Thereby, the imaging driving condition determination unit 115 sets the driving conditions of the X-ray generation apparatus 101, the two-dimensional X-ray sensor 102, and the like based on the imaging conditions instructed by the user in step S801, for example.

  Subsequently, in step S810, the CPU 111 performs processing for displaying the shooting conditions changed in step S809 on, for example, the operation panel 113 (or the image display unit 114). Thereafter, the process returns to step S807, imaging is performed based on the imaging conditions changed in step S809, and X-ray imaging is continued.

  On the other hand, as a result of the determination in step S808, if the priority of the “user (user) instruction content” is not higher than the priority of the “system restriction content” (S808 / YES), the process proceeds to step S811. move on. In step S811, the CPU 111 performs imaging under imaging conditions in which “system restriction content” is given priority over “user (user) instruction content”, and X-ray imaging is continued.

  Subsequently, in step S812, the CPU 111 determines whether or not to end shooting based on the shooting end condition set in step S801.

  As a result of the determination in step S812, if shooting is not completed (S812 / NO), that is, if shooting is continued, the process returns to step S803.

  On the other hand, if the result of determination in step S812 is that shooting is to end (S812 / YES), processing proceeds to step S813. In step S813, the CPU 111 performs a shooting end process. Thereafter, the flowchart shown in FIG. 8 ends.

Next, an example of an operation screen on the operation panel 113 in the second embodiment will be described.
FIG. 9 is a schematic diagram illustrating an example of an operation screen of the operation panel 113 of the X-ray imaging apparatus according to the second embodiment of the present invention. Here, FIG. 9 shows an example of an operation screen of the operation panel 113 on the assumption that shooting is performed under the shooting conditions according to “contents of user instruction” while changing the priority.

  As in the case of FIG. 5, FIG. 9 shows a reason 901 for reducing the frame rate, an actual shooting condition 902 indicating actual shooting conditions, and a user instruction condition 903 indicating shooting conditions input by the user. Has been. As a result, the user (user) knows the “reason” for lowering the frame rate and the “index” for the current shooting conditions, and which shooting conditions have changed compared to the shooting conditions that he / she has input. You can know about that. At the same time, when the user (user) really wants to take an image, a return button 904 corresponding to the frame rate return instruction unit 120 is provided so that the image cannot be taken due to the limitation of the X-ray image capturing apparatus 100. When the return button 904 is operated, the imaging driving condition determination unit 115 sets driving conditions for the X-ray generator 101, the two-dimensional X-ray sensor 102, and the like based on the imaging conditions instructed by the user. Will do.

  FIG. 10 is a schematic diagram illustrating an example of an operation screen of the operation panel 113 of the X-ray imaging apparatus according to the second embodiment of the present invention. Here, FIG. 10 shows an example of an operation screen on the operation panel 113 after an instruction is given to perform photographing under photographing conditions according to “contents of user instruction”.

  The reason why the photographing can be performed under the photographing conditions according to the “user instruction contents” is because the effectiveness of the frame rate limitation by the X-ray imaging apparatus 100 has been lifted. In this case, as shown in FIG. 10, a prompt 1001 indicating warning contents such as information that the durability of the system is deteriorated and information that the temperature exceeds the specification is displayed on the operation panel 113, and the warning display is displayed. Made.

  In the second embodiment, in addition to the processing of the first embodiment, the “system restriction content” is canceled, and the imaging processing based on the imaging conditions in which the “user instruction content” is prioritized can be performed. It has become. Thus, although there is a disadvantage that the durability of the apparatus is lowered, there is an advantage in that it is possible to surely perform photographing under the designated photographing conditions in medical practice when it is absolutely necessary to photograph.

(Third embodiment)
Next, a third embodiment of the present invention will be described.
In the first embodiment and the second embodiment described above, the internal information related to the temperature in the X-ray generator 101 and the two-dimensional X-ray sensor 102 is used as the internal information related to the internal temperature of the X-ray imaging apparatus 100. It was a form to detect (detect). In the third embodiment, information obtained by performing image processing on captured X-ray image data is detected as information correlated with the temperature inside the X-ray image capturing apparatus 100. That is, in the third embodiment, the temperature inside the X-ray imaging apparatus 100 is indirectly detected (detected).

FIG. 11A is a schematic diagram illustrating an example of an X-ray image (radiation image) used in the third embodiment of the present invention.
The X-ray image shown in FIG. 11A shows a subject area 1101 and a blank area 1102 in the subject (subject) 300.

  FIG. 11-2 is a flowchart illustrating an example of a processing procedure of the X-ray imaging apparatus (radiation imaging apparatus) according to the third embodiment of the present invention. Here, in the flowchart shown in FIG. 3, for example, the CPU 111 executes a program stored in the main memory 112, and the image processing unit 122 and the frame rate determination unit 119 for detecting internal information shown in FIG. This is done by controlling.

  First, in step S1101, the image processing unit 122 for detecting internal information reads each X-ray image (each X-ray image data) processed by the preprocessing unit 116.

  Subsequently, in step S1102, the image processing unit 122 for detecting internal information performs image processing of each X-ray image, and the region of each X-ray image that is most hit by the X-ray (the most X-ray is detected). The pixel value of the irradiated region) is extracted as a feature amount. In general, the region that is most exposed to X-rays is a missing region 1102 shown in FIG. 11A. Therefore, in this embodiment, the pixel value of the missing region 1102 is extracted. Specifically, in step S1102, an average value of pixel values is extracted as a feature amount.

  Subsequently, in step S1103, the image processing unit 122 for detecting internal information accumulates the average value (feature value) of the pixel values extracted in step S1102 for each X-ray image. At this time, for example, when the power supply is restarted every day, the accumulated feature amount is reset every time the power supply is turned on / off. In addition, it is most desirable to perform weighting with a larger coefficient as the time is closer to the feature amount that is the accumulated dose accumulated up to the last several hours, for example, 3 hours ago.

  Subsequently, in step S1104, the image processing unit 122 for detecting internal information, based on the average value of the pixel values accumulated in step S1103, internal information relating to the internal temperature of the X-ray imaging apparatus 100 (this example). Then, temperature is estimated. Specifically, in step S1104, the weighted accumulated value of the average value of the pixel values accumulated in step S1103 is converted into an estimated index corresponding to the temperature.

  Subsequently, in step S1105, the frame rate determination unit 119 performs threshold processing using the internal information (specifically, the estimated temperature index) related to the temperature detected in step S1104, as in FIG. Do.

  Thereafter, as in the first and second embodiments, when the frame rate determination unit 119 determines that the internal information relating to the temperature has exceeded the threshold value, the shooting-time drive condition determination unit 115 performs shooting. The form which performs the process which reduces the frame rate to perform is taken.

  In the flowchart illustrated in FIG. 11B, the irradiation line is estimated by performing image processing on the X-ray image, and it is determined whether or not the imaging frame rate is reduced. However, in practice, depending on only the accumulated dose and the detected temperature as a criterion for determining the frame rate, the determination may be one-sided.

  In view of the necessity of the frame rate, a high frame rate is generally required when the subject moves a lot. Conversely, when the movement of the subject is small, generally a low frame rate is required.

Therefore, in addition to the above-described embodiment, it is also possible to perform the following processing.
For example, the image processing unit 122 (or the image processing unit 117) for detecting internal information performs image processing of an X-ray image and detects the movement of the subject (subject) 300. When the subject (subject) 300 is not moving, the frame rate determining unit 119 determines that a high frame rate is not necessary, and lowers the frame rate threshold at each temperature. As described above, when the movement of the subject is detected from the X-ray image and a high frame rate is not required, the frame rate is reduced even below a specific threshold to suppress the temperature rise inside the X-ray image capturing apparatus 100. This is the best mode of this embodiment.

Further, the X-ray image in the present embodiment assumes a human body as a subject.
Therefore, for example, image processing (pattern recognition processing) of a captured X-ray image is performed to detect information related to the part of the subject recognized from the X-ray image, and the above-described high frame is determined depending on the part of the subject. It is also possible to determine when the rate is not necessary. In this case, when the recognized subject portion does not need to be imaged at a high frame rate, the frame rate is reduced even below a specific threshold value in the same manner as described above, so that the inside of the X-ray image capturing apparatus 100 can be reduced. It is the best mode of the present embodiment to suppress the temperature rise.

  Specifically, the heart is one of the parts of the human body that requires imaging at the highest frame rate. For example, when this heart is not shown in the X-ray image, the frame rate is reduced to, for example, 5 fps or less even if it is below a specific threshold value, thereby suppressing an increase in temperature inside the X-ray imaging apparatus 100. You can also.

  Also in the third embodiment, the same effect as in the first embodiment described above can be obtained.

(Fourth embodiment)
Next, a fourth embodiment of the present invention will be described.
In the first embodiment and the second embodiment described above, the internal information related to the temperature in the X-ray generator 101 and the two-dimensional X-ray sensor 102 is used as the internal information related to the internal temperature of the X-ray imaging apparatus 100. It was a form to detect (detect). In the fourth embodiment, information related to the X-ray dose (radiation dose) emitted from the X-ray generation apparatus 101 is detected as information correlated with the temperature inside the X-ray imaging apparatus 100. That is, in the fourth embodiment, the temperature inside the X-ray imaging apparatus 100 is indirectly detected (detected).

  FIG. 12A is a schematic diagram illustrating an example of a schematic configuration of an X-ray imaging apparatus (radiation imaging apparatus) according to the fourth embodiment of the present invention. FIG. 12A shows only the portions related to the X-ray generator 101, the two-dimensional X-ray sensor 102, and the X-ray dose detector 121 in the configuration shown in FIG. Of course, the X-ray imaging apparatus has the other configuration shown in FIG.

  12A, the X-ray dose detection unit 121 is provided between the X-ray generation apparatus 101 and the two-dimensional X-ray sensor 102 (or the subject (subject) 300). Specifically, the X-ray dose detection unit 121 is formed by an area dosimeter, for example. The X-ray dose detection unit 121 detects the X-ray dose of the X-ray 101a irradiated from the X-ray generation apparatus 101 via the collimator 1201, and accumulates the detected X-ray dose. Then, the X-ray dose detection unit 121 estimates the internal temperature of the X-ray imaging apparatus 100 using the accumulated total X-ray dose value.

  FIG. 12-2 is a flowchart illustrating an example of a processing procedure of the X-ray imaging apparatus (radiation imaging apparatus) according to the fourth embodiment of the present invention. Here, in the flowchart shown in FIG. 3, for example, the CPU 111 executes a program stored in the main memory 112 to control the X-ray generator control unit 103, the X-ray dose detection unit 121, and the like shown in FIG. Is done.

  First, in step S1201, the X-ray generation device control unit 103 causes the X-ray generation device 101 to irradiate the subject (subject) 300 with X-rays 101a under the control of the CPU 111.

  Subsequently, in step S1202, the X-ray dose detection unit 121 detects the X-ray dose (radiation dose) emitted from the X-ray generation apparatus 101.

  Subsequently, in step S1203, the X-ray dose detection unit 121 accumulates the value of the X-ray dose detected in step S1202 for each radiographing of each X-ray image.

  Subsequently, in step S1204, the X-ray dose detection unit 121 detects internal information (in this example, temperature in the X-ray imaging apparatus 100) based on the value of the X-ray dose accumulated in step S1203. ) Guess. Specifically, in step S1204, for example, as described in step S1103, the weighting of the X-ray dose in the closer time is increased, and the internal information related to the temperature inside the X-ray imaging apparatus 100 is estimated.

  Thereafter, the frame rate determination unit 119 performs threshold processing similarly to FIG. 7 using the internal information related to the temperature detected in step S1204. Then, when the frame rate determination unit 119 determines that the internal information related to the temperature exceeds the threshold, the shooting drive condition determination unit 115 performs a process of reducing the shooting frame rate.

  According to the fourth embodiment, the temperature state inside the X-ray image capturing apparatus that performs moving image capturing is controlled by the irradiated X-ray dose, and the temperature of the user (user) until the user really wants to take the image. The rise can be mitigated. That is, also in the fourth embodiment, the same effect as that of the first embodiment described above is obtained.

  In the embodiment of the present invention, when an X-ray imaging apparatus having a large thermal tolerance of the X-ray tube 205 (X-ray generation apparatus 101) is used, the threshold used by the frame rate determination unit 119 changes. . Similarly, when the cooling units (108, 109) having a high cooling capacity are used for the X-ray generation apparatus 101, the two-dimensional X-ray sensor 102, and the like, the threshold used by the frame rate determination unit 119 changes. Even in this case, as long as the physical principle of heat generation exists fundamentally, it is considered that the effect of the embodiment of the present invention can be obtained only by the threshold value used in the frame rate determination unit 119 being different.

  2 shows an example in which the X-ray imaging apparatus 100 shown in FIG. 1 is applied to an X-ray imaging system using the C-arm 202, but it may be applied to other X-ray imaging systems. Is possible. An example of application to another X-ray imaging system is shown in FIG.

FIG. 13 is a schematic diagram illustrating another example of an X-ray image capturing system (radiation image capturing system) to which the X-ray image capturing apparatus (radiation image capturing apparatus) illustrated in FIG. 1 is applied.
The X-ray imaging apparatus according to the embodiment of the present invention can be applied as, for example, a head imaging apparatus shown in FIG. 13A or a U alarm type Bucky imaging apparatus shown in FIG. . In addition, the X-ray imaging apparatus according to the embodiment of the present invention can be applied to, for example, a bucky standing imaging stand shown in FIG. 13B or a bucky table shown in FIG. is there.

  Each step of FIGS. 3, 8, 11-2, and 12-2 showing the driving method of the X-ray imaging apparatus 100 according to the embodiment of the present invention described above is stored in a computer RAM, ROM, or the like. This can be realized by running the program. This program and a computer-readable storage medium storing the program are included in the present invention.

  Specifically, the program is recorded in a storage medium such as a CD-ROM, or provided to a computer via various transmission media. As a storage medium for recording the program, a flexible disk, a hard disk, a magnetic tape, a magneto-optical disk, a nonvolatile memory card, and the like can be used in addition to the CD-ROM. On the other hand, as the transmission medium of the program, a communication medium in a computer network (LAN, WAN such as the Internet, wireless communication network, etc.) system for propagating and supplying program information as a carrier wave can be used. In addition, examples of the communication medium at this time include a wired line such as an optical fiber, a wireless line, and the like.

  Further, the present invention is not limited to a mode in which the function of the X-ray imaging apparatus 100 according to the embodiment of the present invention is realized by executing a program supplied by a computer. Even when the function of the X-ray imaging apparatus 100 according to the embodiment of the present invention is realized in cooperation with an OS (operating system) running on a computer or other application software, the program is not limited to this program. Included in the invention. Also, when all or part of the processing of the supplied program is performed by a function expansion board or function expansion unit of the computer, the function of the X-ray imaging apparatus 100 according to the embodiment of the present invention is realized. Such a program is included in the present invention.

  In addition, the above-described embodiments of the present invention are merely examples of implementation in carrying out the present invention, and the technical scope of the present invention should not be construed in a limited manner. It is. That is, the present invention can be implemented in various forms without departing from the technical idea or the main features thereof.

It is a block diagram which shows an example of schematic structure of the X-ray imaging device (radiation imaging device) which concerns on embodiment of this invention. FIG. 2 is a schematic diagram illustrating an example of an X-ray image capturing system (radiation image capturing system) to which the X-ray image capturing apparatus (radiation image capturing apparatus) illustrated in FIG. 1 is applied. It is a flowchart which shows an example of the process sequence of the X-ray imaging device (radiation imaging device) which concerns on the 1st Embodiment of this invention. It is a schematic diagram which shows an example of the operation screen of the operation panel of the X-ray imaging device (radiation imaging device) which concerns on the 1st Embodiment of this invention. It is a schematic diagram which shows an example of the operation screen of the operation panel of the X-ray imaging device (radiation imaging device) which concerns on the 1st Embodiment of this invention. It is a timing chart which shows the relationship between the X-ray irradiated from the X-ray generator shown in FIG. 1, and a frame rate. It is a schematic diagram for demonstrating the judgment standard in the judgment process of the frame rate performed by the frame rate judgment part shown in FIG. It is a flowchart which shows an example of the process sequence of the X-ray imaging device (radiation imaging device) which concerns on the 2nd Embodiment of this invention. It is a schematic diagram which shows an example of the operation screen of the operation panel of the X-ray imaging device (radiation imaging device) which concerns on the 2nd Embodiment of this invention. It is a schematic diagram which shows an example of the operation screen of the operation panel of the X-ray imaging device (radiation imaging device) which concerns on the 2nd Embodiment of this invention. It is a schematic diagram which shows an example of the X-ray image (radiation image) used in the 3rd Embodiment of this invention. It is a flowchart which shows an example of the process sequence of the X-ray imaging device (radiation imaging device) which concerns on the 3rd Embodiment of this invention. It is a schematic diagram which shows an example of schematic structure of the X-ray imaging device (radiation imaging device) which concerns on the 4th Embodiment of this invention. It is a flowchart which shows an example of the process sequence of the X-ray imaging device (radiation imaging device) which concerns on the 4th Embodiment of this invention. It is a schematic diagram which shows another example of the X-ray image imaging system (radiation image imaging system) to which the X-ray image imaging device (radiation image imaging device) shown in FIG. 1 is applied.

Explanation of symbols

DESCRIPTION OF SYMBOLS 100 X-ray imaging device 101 X-ray generator 101a X-ray 102 Two-dimensional X-ray sensor 103 X-ray generator control part 104 A / D conversion part 105 Amplifier amplification part 106 1st internal information detection part 107 2nd inside Information detection unit 108 First cooling unit 109 Second cooling unit 110 CPU bus 111 CPU
112 Main memory 113 Operation panel 114 Image display unit 115 Imaging drive condition determination unit 116 Preprocessing unit 117 Image processing unit 118 Storage unit 119 Frame rate determination unit 120 Frame rate return instruction unit 121 X-ray dose detection unit 122 Internal information detection Image processing unit 300 for subject (subject)

Claims (14)

Radiation generating means for generating radiation on the subject;
Imaging means for capturing a radiographic image based on radiation transmitted through the subject;
Detecting means for detecting internal information related to the temperature inside the apparatus including the radiation generating means and the imaging means;
A radiographic imaging apparatus comprising: a frame rate changing unit that changes a frame rate of a radiographic image captured by the imaging unit based on internal information related to the temperature detected by the detection unit.   The radiographic image capturing apparatus according to claim 1, wherein the internal information related to the temperature includes temperature information and information correlated with the temperature.   The radiographic imaging apparatus according to claim 1, wherein the detection unit detects at least internal information relating to the temperature in the radiation generation unit.   The radiographic image capturing apparatus according to claim 1, wherein the detection unit detects at least internal information relating to the temperature in the imaging unit.   The radiographic image capturing apparatus according to claim 2, wherein the detection unit detects information related to a radiation dose irradiated from the radiation generation unit as information correlated with the temperature.   The radiographic image capturing apparatus according to claim 2, wherein the detection unit detects information obtained by performing image processing on the radiographic image as information correlated with the temperature.   The radiographic image capturing apparatus according to claim 6, wherein the image processing includes a process of extracting a feature amount from the radiographic image.   The radiographic image capturing apparatus according to claim 7, wherein the feature amount is an average value of pixel values of a region of each radiographic image that is irradiated with the most X-rays.   The radiographic image capturing apparatus according to claim 7, wherein in the image processing, a process of detecting a part of the subject from the radiographic image is further performed.   The radiographic image capturing apparatus according to claim 9, wherein the process of detecting the part of the subject is performed by a pattern recognition process of the radiographic image.   The radiographic image capturing apparatus according to claim 1, wherein the frame rate changing unit changes the frame rate to be reduced. Canceling means for canceling the validity of the frame rate changing means;
Return means for returning the frame rate of the radiographic image captured by the imaging means to the frame rate before being changed by the frame rate changing means when the validity of the frame rate changing means is released by the releasing means The radiographic image capturing apparatus according to claim 1, further comprising:   The radiographic image capturing apparatus according to any one of claims 1 to 11, wherein the imaging unit is a radiation detection unit made of a semiconductor that captures a plurality of radiographic images within a unit time. A radiation image capturing apparatus driving method, comprising: radiation generating means for generating radiation on a subject; and imaging means for capturing a radiation image based on radiation transmitted through the subject,
A detection step of detecting internal information relating to the internal temperature of the radiographic imaging device;
And a frame rate changing step of changing a frame rate of a radiographic image captured by the imaging unit based on internal information relating to the temperature detected in the detecting step. .

Images