JP2006122723A - Radiographic imaging system and control device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiographic imaging system and a control device capable of providing easy-to-work environment with high working efficiency for a user among a mixture of different types of radiographic imaging systems with different detecting means, reducing the installation area of devices, introduced at a low cost, having expandability and reliability, easy to use and providing images with a certain finish even if using different detecting means. <P>SOLUTION: This radiographic imaging system is provided with; a plurality of types of radiograph output devices 1 including a radiograph output device 1 having a solid-state flat detector as a detecting means which detects an X-ray 15 irradiated from an X-ray tube 4 by a detecting means and outputs it as digitized image data, and a radiograph output device 1 having a photostimulable phosphor as a detecting means; and a control device 2 controlling the plurality of types of radiograph output devices. The control device 2 is provided with a communication means acquiring image data outputted from the plurality of types of radiograph output devices 1, respectively, and a means associating image data attached information with the respective image data acquired by the communication means. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to an X-ray imaging system and a control device.

  In recent years, there has been an increasing tendency to increase the efficiency and speed of diagnosis by digitizing X-ray image information of patients generated in hospitals and storing and transmitting the information. For this reason, in the field of direct imaging, an X-ray imaging apparatus that outputs digital data is often used instead of the conventional screen / film system.

  X-ray imaging apparatuses that output digital data are classified into X-ray imaging apparatuses using solid-state flat detectors and X-ray imaging apparatuses using stimulable phosphors, depending on the type of X-ray detection means. can do.

  A typical X-ray imaging apparatus using a solid flat detector is a solid flat detector in which a solid-state imaging device called a so-called flat panel detector (FPD) is two-dimensionally arranged. In the FPD, a photoconductive material that generates charges of electrons and holes by X-ray energy such as a-Se is used as a detection means, so that the X-ray energy is directly converted into charges, and the charges are finely converted. There is a direct type FPD that reads out as an electric signal by a reading element (reading unit) such as a TFT arranged two-dimensionally in area units.

  In addition, the X-ray energy is converted into light by a scintillator or the like, and the converted light is converted into electric charge by a photoelectric conversion element such as a-Si arranged two-dimensionally in a fine area unit. An indirect type FPD that reads out an electric signal by a reading element (reading means) such as a TFT arranged two-dimensionally in the same fine area unit as the photoelectric conversion element is also well known.

  Further, in the present invention, the X-ray energy is converted into light by a scintillator or the like, and a lot of the converted light is arranged in a grid on the same plane via a condenser such as a lens or an optical fiber. An image division type FPD that receives light by a sensor and reads out as an electrical signal via photoelectric conversion and electronic / voltage conversion inside a CCD or CMOS sensor is also defined as one of solid state flat detectors.

  On the other hand, an X-ray imaging apparatus using a stimulable phosphor is commonly called a computed radiography (CR). In this apparatus, a part of the X-ray energy transmitted through the subject is detected by a sheet-like detection means called a stimulable phosphor, and at the same time, the detected energy is temporarily stored in the stimulable phosphor. To do. The energy accumulated in the photostimulable phosphor can be extracted as photostimulated light by being excited with a laser beam having a predetermined wavelength. This stimulated light can be extracted as an electrical signal using a photoelectric conversion element such as a photomultiplier.

  In general, as shown in FIGS. 1, 2, and 3, the digital X-ray imaging apparatus mainly includes an X-ray image output device 1, a control device 2, an X-ray generation control device 3, and an X-ray tube 4. An X-ray imaging system as a component is formed.

  Such X-ray imaging systems are roughly classified into a dedicated type X-ray imaging system and a cassette-compatible type X-ray imaging system.

  In the dedicated type X-ray imaging system, since the detection means (detector unit) for detecting X-rays is fixed or built in the imaging apparatus, the user cannot easily carry the detection means. Either a solid flat detector or a photostimulable phosphor can be used as the detection means.

  On the other hand, in a cassette-compatible X-ray imaging system, the X-ray detection means is housed in a portable thin box-like casing called a cassette, and the user can easily connect the X-ray detection means together with the cassette. Can be carried around. Either a solid flat detector or a photostimulable phosphor can be used as the detection means.

  The dedicated type X-ray imaging system is further classified into a standing X-ray imaging system as shown in FIG. 1 and a supine X-ray imaging system as shown in FIG.

  As shown in FIG. 1, the standing X-ray image capturing system is characterized by an elevator 60 and an X-ray image output device 1, and is a system that captures an image of a subject 50 in an upright state. Since the X-ray image output apparatus 1 is configured to be able to move up and down along the lifting platform 60, the position of the X-ray image output apparatus 1 can be adjusted in the vertical direction according to the height of the subject 50. Yes. In the present invention, the type of the X-ray image output apparatus 1 used in such a standing X-ray imaging system is defined as a standing X-ray image output apparatus.

  On the other hand, as shown in FIG. 2, the supine type X-ray imaging system is characterized by a plate member 70, a bed 80, and the X-ray image output device 1, and the subject 50 lies on the plate member 70. It is a system that takes pictures in a state where In the present invention, the type of the X-ray image output apparatus 1 used in such a supine X-ray imaging system is defined as a supine X-ray image output apparatus.

  FIG. 3 is a view showing a cassette-compatible type X-ray imaging system using a stimulable phosphor as an X-ray detection means. A cassette-compatible X-ray imaging system using a stimulable phosphor includes a detection means 100 for detecting X-rays 5, that is, a portable cassette 6 incorporating a stimulable phosphor plate, and a stimulable phosphor. Is characterized by an X-ray image output apparatus 1 that reads X-ray image information stored in the X-ray image information. In the present invention, the type of the X-ray image output apparatus 1 used in such a cassette-compatible X-ray imaging system is defined as a cassette-compatible (cassette-compatible type) X-ray image output apparatus.

  As described above, a great many types of X-ray imaging systems are mixed. However, since different types of imaging systems using the respective detection means are used in a situation where they operate individually, the work efficiency is poor for the user and the work is difficult.

  In addition, since each device forms an individual system, there is a problem that the installation area of the device and the cost of introducing the device increase.

  In addition, the operability of each system still has many problems, and it is difficult to say that a user-friendly and reliable system can be provided to users. In addition, there is a problem in that the finished image taken is different between systems using different detection means.

  The present invention has been made in view of such a situation, and in the presence of mixed X-ray imaging systems of different types and different detection means, it is possible for the user to obtain a work environment with good work efficiency. An object of the present invention is to provide an X-ray imaging system and a control apparatus.

  It is another object of the present invention to provide an expandable X-ray imaging system and a control apparatus that reduce the installation area of the apparatus and are inexpensive to introduce.

  It is another object of the present invention to provide an X-ray imaging system and a control device that are easy to use and reliable.

  It is another object of the present invention to provide an X-ray imaging system capable of obtaining a constant finished image even when different detection means are used.

  In order to solve the above-described problems and achieve the object, the present invention is configured as follows.

According to the first aspect of the present invention, “X-ray image output using a solid flat detector that detects X-rays emitted from an X-ray tube and outputs them as digitized image data after detection by the detection means. X-ray imaging having an apparatus and a plurality of types of X-ray image output apparatuses including an X-ray image output apparatus using a stimulable phosphor as detection means, and a control device for controlling the plurality of types of X-ray image output apparatuses A system,
The control device includes communication means for acquiring image data output from each of the plurality of types of X-ray image output devices;
An X-ray imaging system comprising: means for associating image data attached information with each image data acquired by the communication means. ].

  According to a second aspect of the present invention, “the control device includes: an image processing unit that performs different correction processing according to the type of the detection unit on each image data acquired by the communication unit”. The X-ray imaging system according to claim 1. ].

  According to a third aspect of the present invention, “the control device outputs a plurality of display screens using the image data output, acquired and corrected from each of the plurality of types of X-ray image output devices as one display screen. The X-ray imaging system according to claim 2, further comprising display control means for displaying on the display means. ].

The invention according to claim 4 is: "When the detection means is a solid flat detector, the image processing means performs at least one correction process of gain correction and offset correction;
When the detection means is a photostimulable phosphor, correction of the tilting of the polygon used by the laser scanning means, correction of unevenness generated by the light collecting means for condensing the stimulating light, sensitivity inherent to the stimulable phosphor 4. The X-ray imaging system according to claim 2, wherein at least one correction process is performed among the correction of unevenness and the correction of sub-scanning unevenness caused by the conveying means. ].

The invention according to claim 5 is: "When the detection means is a solid flat detector, the image processing means performs logarithmic conversion on the image data and then performs predetermined image processing;
4. The X-ray imaging according to claim 2, wherein when the detection means is a stimulable phosphor, predetermined image processing is performed without logarithmic conversion on the image data. system. ].

  According to a sixth aspect of the present invention, “the control device includes a storage unit that stores the contents of the correction processing performed in the image processing in association with the image data corrected as image data attached information. The X-ray imaging system according to any one of claims 2 to 5, wherein: ].

  According to a seventh aspect of the present invention, the X-ray according to the sixth aspect of the present invention is characterized in that the control device includes a second communication unit that outputs image data associated with the image data attached information. Image shooting system. ].

The invention according to claim 8 is: “X-ray image output using a solid flat detector that detects X-rays emitted from an X-ray tube and outputs them as digitized image data. A control device for controlling a plurality of types of X-ray image output devices including the device and an X-ray image output device using a stimulable phosphor as detection means,
Communication means for acquiring image data output from each of the plurality of types of X-ray image output devices;
An image processing unit that performs different correction processing on the image data acquired by the communication unit depending on the type of the detection unit. ].

  With the above configuration, the present invention has the following effects.

  According to the first aspect of the present invention, a plurality of types of X-ray image output devices including an X-ray image output device using a solid flat detector as detection means and an X-ray image output device using stimulable phosphors as detection means; A control device that controls a plurality of types of X-ray image output devices, acquires image data output from each of the plurality of types of X-ray image output devices, and attaches image data to each of the acquired image data By associating information, if there are multiple types of X-ray image output devices with different characteristics in a mixed system and display can be confirmed on one screen, the same patient can be imaged with different X-ray image output devices, or the same patient Even when the image data is read out by different X-ray image output devices, it is only necessary to input patient information once, and it is possible to save the trouble of inputting the same patient information for each X-ray image output device used for imaging. In addition, since a plurality of types of X-ray image output devices can be controlled by a single control device, the system can be easily constructed or expanded at low cost. In addition, since only one control device is required for a plurality of types of X-ray image output devices, the installation area of the control device can be minimized. In addition, it is possible to obtain an image with a constant finish even when different detection means are used.

  In the invention according to claim 2, in a system in which a plurality of types of X-ray image output devices having different characteristics are applied to each acquired image data, and different correction processing is performed according to the type of detection means, Display can be confirmed on a single screen by performing image processing.

  In the invention described in claim 3, the image data output from each of the plurality of types of X-ray image output devices, acquired, and corrected is displayed as a single display screen, and a plurality of display screens are displayed on the display means. In a system in which a plurality of types of X-ray image output apparatuses having characteristics are mixed, display can be confirmed on one screen by performing image processing.

  In the invention according to claim 4, when the detecting means is a solid flat detector, at least one correction processing is performed among gain correction and offset correction, and when the detecting means is a stimulable phosphor, laser scanning means is provided. At least of correction of surface tilt of the polygon used in the correction, correction of unevenness generated by the condensing means for condensing the stimulating light, correction of sensitivity unevenness inherent to the stimulable phosphor, and correction of sub-scanning unevenness generated by the conveying means Since the image processing can be performed after one correction processing is performed and the correction processing according to the type of the detection means is performed, the finish of the image processing is improved, and image data with favorable image quality can be provided to the user. In addition, since the correction processing is configured so as to be compatible with both solid state flat detectors and stimulable phosphor detection means, a flexible system can be constructed regardless of the detection means.

  In the invention of claim 5, when the detection means is a solid flat detector, predetermined image processing is performed after logarithmic conversion is performed on the image data, and when the detection means is a stimulable phosphor Since the image data is subjected to predetermined image processing without logarithmic conversion and can be processed by the same image processing means regardless of which of the X-ray image output apparatuses is connected, it does not depend on the data format of the image data. A versatile system can be constructed.

  According to the sixth aspect of the present invention, the contents of the correction processing performed by the image processing are stored in association with the image data corrected as image data additional information, and image data with stable image quality is always provided. Therefore, it is possible to construct a versatile system that is not affected by the difference in detection means or the operation of the X-ray image output apparatus.

  According to the seventh aspect of the present invention, there is provided a second communication means for outputting the image data associated with the image data auxiliary information, and there is no risk of being confused with other patient images. Reliability and safety can be improved.

  In the invention described in claim 8, a plurality of types of X-ray image output devices including an X-ray image output device using a solid flat detector as detection means and an X-ray image output device using stimulable phosphors as detection means are provided. A control device that controls, acquires image data output from each of a plurality of types of X-ray image output devices, and performs different correction processing on the acquired image data depending on the type of detection means, and has different characteristics In a system in which a plurality of types of X-ray image output apparatuses are mixed, display can be confirmed on one screen by performing image processing.

  Embodiments of the X-ray imaging system and the control device of the present invention will be described below. First, the operation of an individual system that forms the minimum unit of the X-ray imaging system according to the present invention will be described with reference to FIGS. 1, 2, and 3. FIG.

  First, a dedicated type X-ray imaging system will be described with reference to FIGS. The standing X-ray imaging system shown in FIG. 1 and the supine X-ray imaging system shown in FIG. 2 operate in the same manner, and will be described at once.

  When the X-ray generation control device 3 is operated to irradiate the subject 50 with the X-ray 5 from the X-ray tube 4, the X-ray transmitted through the subject 50 is detected by the detection unit 100. Since a part of the irradiated X-ray 5 is absorbed by the subject 50, the X-ray detected by the detection unit 100 can be regarded as X-ray image information reflecting the X absorption distribution of the subject 50.

  The X-ray image information detected by the detection unit 100 is read as an electrical signal by the reading unit 110 in response to an instruction from the control device 2 and digitized by the AD conversion unit 120. Hereinafter, the digitized X-ray image information is referred to as image data. The image data generated by the AD conversion unit 120 is transferred to the control device 2 via the communication unit 130 and the communication cable 10.

  A series of main operations of the X-ray image output apparatus 1 are controlled by the control apparatus 2 via the communication cable 10. The control device 2 is connected to an X-ray generation control device 3 that controls generation of the X-rays 5 via a communication cable 30.

  The generation timing of the X-ray 5 is notified from the X-ray generation control device 3 to the control device 2 via the communication cable 30. The control device 2 instructs the X-ray image output device 1 to read out image data in synchronization with the notified X-ray generation timing.

  Next, a cassette-compatible X-ray imaging system will be described with reference to FIG. In this example, the detection means 100 is a stimulable phosphor plate.

  The cassette 6 is applied to a portion of interest of the subject 50 (a portion where X-ray imaging is desired), and the X-ray generation control device 3 is operated to irradiate the X-ray 5 from the X-ray tube 4. The X-ray energy that has passed through the subject 50 is detected by the detection means 100 built in the cassette 6, and then accumulated and held in the inside of the photostimulable phosphor plate that is the detection means 100.

When the cassette 6 is inserted into the X-ray image output apparatus 1 having the reading means 110 after the X-ray imaging is completed, the X-ray image output apparatus 1 pulls out the detection means 100 from the cassette 6, and the transport means 90 detects the detection means 100, that is, the brightness. The X-ray image information accumulated and held in the detection means 100 is read out by the reading means 110 while carrying the sub-scanning transport of the stimulable phosphor plate in the direction A.
The reading unit 110 includes a laser scanning unit 111, a condensing unit 112, and a photoelectric conversion unit 113. While the detecting unit 100 is being sub-scanned and conveyed by the conveying unit 90, the laser scanning unit 111 scans the laser beam 114 in a direction (main scanning direction) perpendicular to the sub-scanning direction.

  When laser light acts on the photostimulable phosphor plate that is the detection means 100, the energy accumulated in the phosphor is generated as photostimulated light 115. The energy emitted as the stimulating light has an energy amount proportional to the X-ray energy amount detected by the detecting means 100. The stimulated light 115 is condensed by the condensing means 112, and the condensed stimulated light 115 is extracted as an electric signal by the light beam converting means 113 such as a photomultiplier.

  The stimulated light 115 read out as an electrical signal by the reading unit 110 is digitized by the AD conversion unit 120 to generate image data. The image data generated by the AD conversion unit 120 is transferred to the control device 2 via the communication cable 10 by the communication unit 130.

  A series of main operations of the X-ray image output apparatus 1 are controlled by the control apparatus 2 via the communication cable 10.

  In the cassette type X-ray imaging system, the irradiation time of the X-ray 5 from the X-ray tube 4 toward the subject 50 and the detection time of the X-ray image information by the detection means 100 are the X-ray image by the reading means 110. It is not necessary to synchronize with the information read time.

  FIG. 4 is a diagram for explaining the control device 2 which is a part of the present invention in more detail. The control device 2 includes a patient information input unit 210, a display unit 220, a condition input unit 221, and a control unit 230.

  The control unit 230 includes a communication unit 231 that is a unit for acquiring image data from the X-ray image output apparatus 1 or transmitting a control signal to the X-ray image output apparatus 1 via the communication cable 10, and a patient information input unit. 210, a patient information input control unit 232 for controlling 210, a display control unit 233 for controlling the display unit 220, a condition input control unit 234 for controlling the condition input unit 221, and image data and information associated with the image data are transmitted via a communication cable. 20, a communication unit 235 that outputs to the outside via the control unit 20, a control unit 236 that controls each unit in the control device 2 and the X-ray image output device 1, and an image that processes image data received from the X-ray image output device 1 A processing unit 237, a storage unit 238 for storing image data, information accompanying the image data, patient information, and the like. Is constituted by the communication unit 239 is means for communicating via the Le 30.

  The patient information input unit 210 is a unit for inputting patient information of a patient to be imaged. For example, when the patient information input unit 210 is connected to a hospital information system (HIS) or a radiation information system (RIS), Patient information can be received online from HIS or RIS. In this case, information related to imaging such as an imaging region and an imaging direction can be taken into the control device 2 via the patient information input unit 210.

  The patient information input means 210 may be a barcode reader. In this case, the patient information is expressed by a barcode, and the patient information that is barcoded is read by the barcode reader that is the patient information input means 210.

  The patient information input means 210 may be a magnetic card reader or an IC card reader. In this case, patient information is stored in a magnetic card or IC card, and patient information stored in the magnetic card or IC card is read by a magnetic card reader or IC card reader serving as the patient information input means 210.

  The patient information input unit 210 may be a keyboard. In this case, a user inputs patient information using a keyboard.

  The patient information input unit 210 may be a device for inputting voice. In this case, the user inputs patient information by voice. Patient information includes, for example, the patient's name, date of birth, gender, address, ID number, and date of imaging. Patient information input from the patient information input unit 210 is temporarily stored in the storage unit 238.

  The display unit 220 is a unit capable of displaying character information and image information such as a CRT display or a liquid crystal display, for example, and includes patient information, imaging sensitivity information, type of imaging apparatus, imaging site, imaging direction, and X-ray generation control device. X-ray imaging conditions acquired from 3, information specifying the X-ray image output device from which the image data was acquired, resolution or sampling pitch of the image data, the number of pixels of the image data, the number of bits per pixel of the image data, image processing Type information, image processing parameters, information of correction processing, and the like (hereinafter, these information will be collectively referred to as image data attached information), and video of captured image data. The display content is controlled by the display control means 233. The user can confirm the patient name, the imaging region, and the like before imaging by the information displayed on the display unit 220. In addition, it is possible to confirm whether the shooting is good or bad by viewing the video of the image data displayed on the display unit 220 after shooting.

  The condition input means 221 is assumed to be a touch panel in the case of FIG. 4, but may be other means such as a keyboard, a mouse, a trackball, a voice input device, or the like. When the condition / information required by the user is selected from the image data attached information displayed on the display unit 220 via the condition input unit 221, the selected condition / information is input via the input control unit 234. It is taken into the control unit 230 and registered. In addition, it is possible to change or delete already input conditions / information by operating the condition input means 221.

  For example, a list of imaging regions is displayed as a plurality of icons on the display unit 220, and when the user touches (selects) one of the icons with a finger, the icon corresponds to the touched (selected) icon. The imaging part is stored (registered) in the storage unit 237 as image data attached information.

  The communication unit 231 is a unit that manages communication with the X-ray image output apparatus 1 via the communication cable 10. The communication contents include control information of the X-ray image output apparatus 1, information for specifying the X-ray image output apparatus, image data output from the X-ray image output apparatus 1, correction data used for correcting the image data, and the like. is there. Image data and correction data received by the communication unit 231 are stored in the storage unit 238. The communication means 231 can be added depending on the number of connected X-ray image output apparatuses 1 and the connection method.

  The image processing unit 237 is a unit that performs predetermined image processing on the image data received by the communication unit 231. Types of image processing include gradation conversion processing for converting the gradation of image data, frequency processing for converting frequency characteristics of image data, and dynamic range compression processing for compressing the dynamic range of image data.

  In particular, in the gradation conversion processing, the gradation characteristic of image data linear to the logarithm of the X-ray intensity is nonlinear with the logarithm of the X-ray intensity for the purpose of obtaining gradation characteristics as when shooting with a screen / film system. The process of converting to gradation characteristics is most often used. Since image processing such as gradation conversion processing, frequency processing, and dynamic range compression processing is desirably performed on image data that is linear in the logarithm of the X-ray intensity, in the present invention, it is output from the X-ray image output apparatus 1. If the image data is data that is substantially linear with respect to the X-ray intensity, a process of performing logarithmic conversion is automatically performed before the image processing.

  For example, in the case where the X-ray image output apparatus 1 is an apparatus using a fixed plane detector, generally image data that is substantially linear with respect to the X-ray intensity is often output. Control is performed so that logarithmic conversion processing is automatically performed on the image data.

  On the other hand, in the case where the X-ray image output apparatus 1 is an apparatus using a stimulable phosphor, generally linear image data is output with respect to the logarithm of the X-ray intensity. Control is performed so that logarithmic conversion processing is not performed on the image data.

  As described above, in the present invention, the image data that is substantially linear with respect to the X-ray intensity is automatically subjected to the logarithmic conversion process. Therefore, the X-ray that outputs image data that is approximately linear with respect to the X-ray intensity. Regardless of which of the image output device and the X-ray image output device that outputs image data substantially linear in the logarithm of the X-ray intensity, the same image processing means 237 can perform image processing.

  If the type and content (the degree of processing, etc.) of the image processing processed by the image processing means 237 are the same in the case of the apparatus using the fixed flat detector and the case of the apparatus using the stimulable phosphor, The processing program is simplified and the development cost can be reduced. In addition, the storage capacity required to store the processing program and processing parameters can be reduced.

  Further, the type and content of the image processing (the degree of processing, etc.) processed by the image processing means 237 are different between the case of the apparatus using the fixed flat detector and the case of the apparatus using the stimulable phosphor. Anyway. This is because the detection means are different between the fixed flat detector and the photostimulable phosphor, and the frequency and gradation characteristics of the image data are slightly different. Therefore, by changing the type of image processing depending on the detection means, or by changing the content and degree of processing even in the same image processing, it is possible to finish the image data so that the difference between the different detection means is not noticeable.

  In order for the result of the image processing performed by the image processing unit 237 to be preferable, it is preferable that correction processing for correcting unevenness peculiar to the detection unit 100 and the reading unit 110 is performed before the image processing is performed. The correction process may be performed by the image processing unit 237 or may be performed inside the X-ray image output apparatus 1.

  As correction processing when the detection means 100 is a solid flat detector, there are gain correction and offset correction. The offset correction process is a process for correcting variations in the implied output voltage of the solid-state flat panel detector, variations in readout amplifier noise, and the like. On the other hand, the gain correction is a process for correcting the sensitivity unevenness of the solid flat panel detector and the gain unevenness of the readout amplifier.

x is the pixel position of the data, image data before correction is f (x), image data after correction is F (x), data for gain correction is p (x), and data for offset correction is q (x). If expressed, the image data after gain correction and offset correction is
F (x) = {f (x) −q (x)} * p (x) (1)
It is represented by

If you only need to perform offset correction,
F (x) = f (x) −q (x) (2)
It is represented by

If you only need to perform gain correction,
F (x) = f (x) * p (x) (3)
It is represented by

  Here, the uncorrected image data f (x), the corrected image data F (x), the gain correction data p (x), and the offset correction data q (x) are all data linear in the X-ray intensity. It is.

  On the other hand, the correction process when the detection unit 100 is a stimulable phosphor includes a polygon surface tilt correction process used by the laser scanning unit 111 and a correction of unevenness generated by the condensing unit 112 that collects the stimulated light. Processing, correction processing of sensitivity unevenness unique to the stimulable phosphor, correction processing of sub-scanning unevenness generated in the transport unit 90, and the like.

When x is a pixel position of data, image data before correction is represented by g (x), image data G (x) after correction, and correction data is represented by h (x), the image data after correction is
G (x) = g (x) ± h (x) (4)
It is represented by

  Here, the image data g (x) before correction, the image data G (x) after correction, and the correction data h (x) are all data linear to the logarithm of the X-ray intensity.

  In the present invention, since the image processing is performed after performing the correction processing according to the type of the detection means 100 as described above, the finish of the image processing is improved, and image data with good image quality can be obtained.

  It is known that the resolution, density resolution, the number of bits per pixel, and the like, which are attributes of image data, differ depending on the detection means 100 used and the operation of the X-ray image output apparatus 1. Generally, in an apparatus that processes an X-ray image, image processing is designed on the assumption of a specific detection means, and therefore normal image processing cannot be performed when there is a variation in image data attributes.

  For example, when trying to perform a certain frequency process on image data, if the resolution of the image data is different, the frequency components and frequency bands to be emphasized or attenuated will be different, so the image finish will be different. Arise.

  In the present invention, in order to solve such problems, the following two methods are provided.

  First, the first method determines the reference value of the attribute of the image data. If the acquired attribute of the image data is different from the reference value, the image data itself is modified (correction processing is performed on the image data itself). This is a method of matching the attribute of the image data with the reference value. For example, when the reference value of the number of bits per pixel is 12 bits, if the number of bits per pixel of the acquired image data is 14 bits, the lower 2 bits of the acquired image data are discarded and forced Thus, the process of converting to 12-bit data is performed.

  In this manner, the acquired image data itself is deformed, and the image processing unit 237 performs image processing after forcibly matching the attribute of the image to the reference value. Since the attribute of the image data is adjusted to the reference value, image processing can be performed without causing a problem. In the second method, the image data is not adjusted to the reference value, and the image processing program absorbs the variation in the attribute of the image data caused by the difference in the detection means 100 and the operation in the X-ray image output apparatus 1. It is a method to do. In other words, an image processing program that allows variation in image data attributes is designed, and before image processing is performed, the attributes of the image data are passed as parameters to the image processing program.

  For example, if the number of bits per pixel of image data is 14 bits, a parameter indicating that the number of bits per pixel is 14 bits is transferred to the image processing program. For example, the image processing program executes a predetermined image processing program on the image data after recognizing that the maximum value of the input image data is 16383 in decimal.

  If image processing is performed in this way, variations in the attributes of image data can be absorbed within the image processing program, so that image processing can be performed without causing problems.

  In the present invention, the contents of the various correction processes described so far, the type of image processing, the image processing parameters, and the like are stored in the storage unit 238 as image data auxiliary information in association with the image data. The contents of the correction processing and image processing applied to can be confirmed later.

  The storage means 238 is a means for temporarily or long-term storing image data, correction data, image data attached information, and the like. The image data preferably stores both image data before image processing and image data after image processing.

  The communication means 239 is means for communicating with the X-ray generation control device 1 via the communication cable 30. The communication contents are information related to the timing of X-ray irradiation and X-ray imaging conditions. The X-ray imaging conditions include information such as the X-ray irradiation time, the current value flowing through the X-ray tube, the tube voltage of the X-ray tube, and when there are a plurality of X-ray tubes, which X-ray tube is selected. This is information indicating whether or not.

  Information related to the timing of X-ray irradiation is important in the case of a dedicated type X-ray imaging system or in the case of a cassette-compatible type X-ray imaging system using a flat panel detector.

  In such an X-ray imaging system in which X-ray irradiation timing is important, the reading unit 110 in the X-ray image output apparatus 1 receives the timing for reading image data from the detection unit 100 from the X-ray generation control apparatus 1. It is created in the control means 236 based on the timing of X-ray irradiation.

  The communication means 235 is connected to a network inside the hospital via the communication cable 20 and is used for various devices such as a viewing station for displaying image data on a CRT or the like for diagnosis, and image data for storing image data for a long time. Image data and other information are output to an archiver, a dry imager that outputs image data to a film, or an ink jet printer.

  Next, an embodiment of an X-ray imaging system according to the present invention, that is, an embodiment of a dedicated type X-ray imaging system will be described with reference to FIG. In this example, three X-ray image output apparatuses 1a, 1b, and 1c are sequentially connected on the communication cable 10.

  In the X-ray imaging room, the installation locations of the X-ray image output devices 1a, 1b, and 1c and the installation location of the control device 2 are separated as much as possible so that the user is not exposed to X-rays. That is, the communication cable length between the control device 2 and the X-ray image output device 1a is the communication cable length between the X-ray image output device 1a and the X-ray image output device 1b, or the X-ray image output device 1b and the X-ray image output. In many cases, the length is longer than the communication cable length between the devices 1c.

  For this reason, by configuring the X-ray image output apparatuses 1a, 1b, and 1c to be sequentially connected on the communication cable 10, the total cable length of the communication cable can be shortened, and the apparatus cost can be reduced. . Moreover, the interface board which comprises the communication means 231 by the side of the control apparatus 2 can be comprised by one sheet, and apparatus cost can be reduced further. Further, since it is sufficient to control one system interface, the communication control program of the control means 236 can be simplified, and the development cost and development load can be reduced. The X-ray image output apparatuses 1a, 1b, and 1c are controlled by one control apparatus 2 via the communication cable 10. The control device 2 manages the three X-ray image output devices 1a, 1b, and 1c using, for example, ID numbers.

  In this example, one control apparatus 2 controls three X-ray image output apparatuses 1a, 1b, and 1c. However, the present invention limits the number of X-ray image output apparatuses controlled by the control apparatus 2. It is not a thing. Each of the three X-ray image output devices 1a, 1b, 1c is a dedicated type X-ray image output device in this example, and may be either a standing type or a standing type.

  The detection means 100 of each of the three X-ray image output apparatuses 1a, 1b, and 1c may be a fixed plane detector, a photostimulable phosphor, or other X-ray detection means. There may be.

  Three X-ray tubes 4a, 4b, and 4c are connected to the X-ray generation control device 3 that is connected to the control device 2 by the communication cable 30 via the cable 40, and the X-ray tubes 4a, 4b, and 4c are connected. Are associated with the X-ray image output apparatuses 1a, 1b, and 1c, respectively. That is, when imaging is performed by the X-ray image output apparatus 1a, the X-ray tube 4a is used. When imaging is performed by the X-ray image output apparatus 1b, the X-ray tube 4b is converted by the X-ray image output apparatus 1c. When imaging is performed at X, the X-ray tube 4c is controlled to be used.

  In this example, the X-ray tube and the X-ray image output device are associated one-to-one. For example, the X-ray tube 4c does not exist and the X-ray tube 4b is replaced with the X-ray image output device 1b. 1c may be associated. That is, one X-ray tube may be configured to be associated with two or more X-ray image output apparatuses.

  In this case, when imaging with the X-ray image output device 1a is instructed, the X-ray tube 4a is controlled to be used, and imaging with the X-ray image output device 1b or the X-ray image output device 1c is instructed. Then, the X-ray tube 4b is controlled to be used.

  When one of the three X-ray tubes 4 a, 4 b, 4 c is selected by the X-ray generation control device 3, information specifying the selected X-ray tube is reported to the control device 2 via the communication cable 30. Is done. The control device 2 automatically selects an X-ray image output device corresponding to the reported X-ray tube in accordance with a predetermined association. Since the user only needs to select an X-ray tube (there is no need to select an X-ray image output device), the work efficiency can be improved, and at the same time, the correspondence between the X-ray tube and the X-ray image output device is incorrect. There is no risk of selection.

  At this time, if information that can be specified by the automatically selected X-ray image output device is displayed on the display means 220 of the control device 2, the user confirms which X-ray image output device should be used. Can be done instantly before shooting.

  When the control device 2 selects one of the three X-ray image output devices 1a, 1b, and 1c, information for designating an X-ray tube corresponding to the selected X-ray image output device is transmitted to the communication cable 30. May be configured to be reported to the X-ray generation control device 3 via In this case, the X-ray generation control device 3 automatically selects the X-ray tube designated by the control device 2.

  In this case, since the user only needs to select the X-ray image output device (there is no need to select the X-ray tube), work efficiency can be improved, and at the same time, the correspondence between the X-ray tube and the X-ray image output device can be achieved. There is no risk of selecting an attachment by mistake.

  At this time, if information that can automatically identify the selected X-ray tube is displayed on the display means 220 of the control device 2, the user confirms which X-ray tube should be used before imaging. Can be done instantly.

  FIG. 5 shows an example in which X-ray imaging is performed using the X-ray tube 4b. This example is an example of a method in which a user selects an X-ray tube (the X-ray image output device is automatically selected), but a method in which the user selects an X-ray image output device (X-ray tube). It goes without saying that may be automatically selected).

  First, the user sets the subject 50, that is, a patient to be imaged, at a position where imaging can be performed with respect to the X-ray image output apparatus 1b.

  Next, the X-ray generation control device 3 selects the X-ray tube 4b. When the X-ray tube 4 b is selected by the X-ray generation control device 3, information for identifying the selected X-ray tube, for example, the ID number of the X-ray tube 4 b is reported to the control device 2 via the communication cable 30. Is done.

  The user confirms the patient information input through the patient information input unit 210 and other image data attached information through the display unit 220. In addition, conditions such as an imaging region and an imaging direction are newly input or changed from the condition input unit 221 as necessary. The input of patient information or the like may be performed either when inputting before imaging or when inputting after imaging.

  When various conditions are determined, the user operates the X-ray generation control device 3 and instructs the X-ray tube 4b to generate X-rays. When the user instructs the generation of X-rays, the X-ray generation control device 3 generates X-rays from the already selected X-ray tube 4b via the cable 40. That is, X-rays 5 are emitted toward the subject 50 from the X-ray tube 4b. At this time, the timing at which X-rays are generated is also notified to the control device 2 via the communication cable 30.

  The control device 2 sends the X-ray image output device 1b to the X-ray image output device 1b almost in synchronization with the X-ray generation timing so that the X-ray image information detected by the detection means 100 in the X-ray image output device 1b can be read immediately. Issue an X-ray image read command.

  The X-ray image output device 1b that has received an X-ray image read command from the control device 2 converts the X-ray image information detected by the detecting means 100 into image data according to the procedure described with reference to FIGS.

  The generated image data is transferred to the control device 2 via the communication unit 130, the communication cable 10, and the communication unit 231, and is temporarily stored in the storage unit 238 in association with the image data attached information. At the same time, the image is displayed on the display unit 220 as an image. The user confirms whether or not normal photographing has been performed by viewing the image of the image data displayed on the display unit 220.

  The image data temporarily stored in the storage unit 238 is read out by the image processing unit 237, subjected to predetermined correction processing and image processing, and again corresponds to the image data attached information in the storage unit 238. Attached and memorized.

  The image data after the image processing is displayed again on the display means 220 so that the user can confirm whether normal image processing has been performed. If the X-ray image output device used for imaging or information that can specify the type of the X-ray image output device is stored in association with the image data as image data attached information, even after a considerable amount of time has elapsed since imaging This is very convenient because the taken X-ray image output device can be identified immediately. In particular, when a person other than the user refers to the image data and finds some trouble in the image data, there is an advantage that it is possible to quickly identify which X-ray image output apparatus has taken the image data.

  Further, at an appropriate time before and after X-ray generation, information such as X-ray imaging conditions set by the X-ray generation control device 3, that is, X-ray irradiation time, current value flowing through the X-ray tube, tube voltage of the X-ray tube, etc. Is transmitted from the X-ray generation control device 3 to the control device 2 and stored in the storage means 238 in the control device 2 as image data auxiliary information in association with the image data, the acquired image becomes It is very convenient because it is possible to determine under what conditions the image was taken.

  Further, it is more preferable to display the X-ray imaging conditions on the display unit 220 because the user can reconfirm the X-ray imaging conditions. The image data and the image data attached information stored in the storage unit 238 in the control device 2 are output to the communication cable 20 by the communication unit 235 as necessary.

  The X-ray image capturing system in FIG. 6 is an example in which the connection method between the control device 2 and the X-ray image output devices 1a, 1b, and 1c in the X-ray image capturing system in FIG. 5 is changed.

  In FIG. 5, the X-ray image output apparatuses 1a, 1b, and 1c are sequentially connected on the communication cable 10, but in FIG. 6, the X-ray image output is performed by the three communication cables 10a, 10b, and 10c. The devices 1a, 1b and 1c are connected to the control device 2 separately.

  In this connection method, since one communication cable is assigned to one X-ray image output device, the communication speed between the control device 2 and the X-ray image output devices 1a, 1b, and 1c is increased. In addition, the specifications of the communication means 130 built in the X-ray image output apparatuses 1a, 1b, and 1c, the specifications of the communication cable connected to the communication means 130, the types of communication protocols, etc. Since it is not necessary to share the output device, it can be optimally designed for each X-ray image output device. As described above, in the present invention, a plurality of X-ray image output apparatuses having different communication specifications by one control apparatus can be controlled without any problem. Other operations are the same as those in the X-ray imaging system of FIG.

  In the X-ray imaging system of the present invention shown in FIGS. 5 and 6, only one control device 2 is required regardless of the number of X-ray image output devices 1 to be connected. An inexpensive system can be supplied when the number is two or more. In addition, since only one control device 2 is required for two or more X-ray image output devices 1, when two or more X-ray image output devices 1 are used, the installation area of the control device 2 is equivalent to one. You can do it.

  In the present invention, since a plurality of X-ray image output apparatuses 1 are controlled by a single control apparatus 2, patient information input from the patient information input means 210, image processing conditions input from the condition input means 221, and imaging If the image data attached information such as the type of device, imaging region, imaging direction, etc. is input to the control device 2 only once, the image data read by any X-ray image output device 1 can be Since these pieces of information can be associated, there is no need to input these pieces of information for each X-ray image output apparatus.

  In the present invention, since the X-ray tube 4 to be used and the X-ray image output device 1 controlled by the control device 2 can be controlled in association with each other, the user can control the X-ray image output device 1 and the X-ray tube. The risk of mistaken correspondence of 4 was eliminated. Further, the trouble of selecting both the X-ray image output apparatus 1 and the X-ray tube 4 is eliminated, and imaging can be performed only by selecting either one.

  Next, another embodiment of the X-ray imaging system according to the present invention, that is, an embodiment of a cassette-compatible type X-ray imaging system will be described with reference to FIG. In this example, three X-ray image output devices 1d, 1e, and 1f are sequentially connected on the communication cable 10. Since the effect of the sequential connection is the same as that described with reference to FIG. 5, the description thereof is omitted here.

  The X-ray image output devices 1d, 1e, and 1f are controlled by one control device 2 via the communication cable 10. The control device 2 manages the three X-ray image output devices 1d, 1e, and 1f using, for example, ID numbers.

  In this example, one control apparatus 2 controls three X-ray image output apparatuses 1d, 1e, and 1f. However, the present invention limits the number of X-ray image output apparatuses controlled by the control apparatus 2. It is not a thing.

  In this example, a cassette-compatible X-ray imaging system using a photostimulable phosphor is described. However, a cassette-compatible X-ray imaging system using a solid flat detector is also used for X-ray image output. It goes without saying that the connection between the device and the control device can be constructed in a similar manner.

  First, the user sets the subject 50 and the cassette 6 at an optimal position within the X-ray irradiation range of the X-ray tube 4.

  The user confirms the patient information input through the patient information input unit 210 and other image data attached information through the display unit 220. In addition, conditions such as an imaging region and an imaging direction are newly input or changed from the condition input unit 221 as necessary. The input of patient information or the like may be performed either when inputting before imaging or when inputting after imaging.

  When various conditions are determined, the user operates the X-ray generation control device 3 to instruct the X-ray tube 4 to generate X-rays. When generation of X-rays is instructed by the user, the X-ray generation control device 3 generates X-rays from the X-ray tube 4 via the cable 40. That is, X-rays 5 are emitted from the X-ray tube 4 toward the subject 50.

  When the X-ray irradiation is completed, the user inserts the cassette 6 into any of the X-ray image output devices 1d, 1e, and 1f. In the present invention, the number of cassette insertion openings of the X-ray image output apparatus is not limited.

  The user can continuously perform photographing a plurality of times using a plurality of cassettes with respect to the subject 50. In this case, a plurality of cassettes for which imaging has been completed may be inserted into the X-ray image output apparatuses 1d, 1e, and 1f (or a part thereof) at the same time.

  When the cassette is inserted into any of the X-ray image output apparatuses 1d, 1e, and 1f, the stimulable phosphor plate serving as the detection means 100 is pulled out with the insertion of the cassette as a trigger, which has been described with reference to FIG. Image data is generated according to the procedure. Which of the X-ray image output devices 1d, 1e, and 1f is to be controlled by the control device 2 is determined by referring to information on whether or not a cassette has been inserted into the X-ray image output device.

  The generated image data is transferred to the control device 2 via the communication unit 130, the communication cable 10, and the communication unit 231, and is temporarily stored in the storage unit 238 in association with the image data attached information. At the same time, the image is displayed on the display unit 220 as an image. The user confirms whether or not normal photographing has been performed by viewing the image of the image data displayed on the display unit 220.

 The image data temporarily stored in the storage unit 238 is read out by the image processing unit 237, subjected to predetermined correction processing and image processing, and again corresponds to the image data attached information in the storage unit 238. Attached and memorized. The image data after the image processing is displayed again on the display means 220 so that the user can confirm whether normal image processing has been performed.

  Although not shown in FIG. 7, similarly to FIGS. 5 and 6, a communication cable 30 is arranged between the control device 2 and the X-ray generation control device 3 to control the control device 2 and the X-ray generation control. The apparatus 3 may be allowed to communicate. In this way, the control device 2 can acquire X-ray imaging conditions such as the X-ray irradiation time, the current value flowing through the X-ray tube, and the tube voltage of the X-ray tube from the line generation control device 3. The acquired X-ray imaging conditions can be stored in the storage unit 238 in the storage unit 238 in association with the image data as a part of the image data attached information.

  The image data and the image data attached information stored in the storage unit 238 in the control device 2 are output to the communication cable 20 by the communication unit 235 as necessary.

  In the present invention, the control device 2 may be a device having a separate housing from the X-ray image output device 1, or is incorporated in any one of the X-ray image output devices 1d, 1e, and 1f. May be.

  The X-ray image capturing system of FIG. 8 is an example in which the connection method between the control device 2 and the X-ray image output devices 1d, 1e, and 1f of the X-ray image capturing system of FIG. 7 is changed.

  In FIG. 7, the X-ray image output devices 1d, 1e, and 1f are sequentially connected on the communication cable 10, but in FIG. 8, X-ray image output is performed by the three communication cables 10d, 10e, and 10f. The devices 1d, 1e, and 1f are separately connected to the control device 2.

  Such an X-ray imaging system of the connection method has the same effect as the X-ray imaging system described with reference to FIG.

  Other operations are the same as those in the X-ray imaging system of FIG.

  The X-ray image output apparatus 1 of the X-ray image capturing system described with reference to FIGS. 7 and 8 determines the number of X-ray image output apparatuses 1 connected to the control apparatus 2 according to the scale of the facility and the X-ray imaging frequency. Can be changed.

  For example, it is sufficient to connect one X-ray output device 1 to one control device 2 in a facility where imaging frequency is low or a facility that does not perform many imaging operations for one patient at a time.

  In a facility where the frequency of X-ray imaging is high or in a hospital that performs a lot of imaging for one patient at a time, if a plurality of X-ray output devices 1 are connected to one control device 2, X-rays can be obtained. It is possible to improve the processing capability of the image capturing system.

  As described above, in the X-ray image capturing system of the present invention, only one control device 2 is required regardless of the number of X-ray image output devices 1 to be connected. Therefore, the number of X-ray image output devices 1 to be connected is two. In the above case, a low-cost system can be supplied.

  Further, when the control device 2 is configured with a separate housing from the X-ray image output device 1, only one control device 2 is required for two or more X-ray image output devices 1. When more than one X-ray image output apparatus 1 is used, the installation area of the control apparatus 2 can be reduced by one.

  In addition, if m X-ray image output apparatuses 1 having cassette insertion slots of n slots are connected, a maximum of nxm cassettes can be inserted continuously, so if you want to process many cassettes at once, The imaging cycle time can be shortened without being bothered by inserting and removing the cassette.

  When m X-ray image output devices 1 are connected to the control device 2, the m X-ray output devices 1 can read image data at the same time. The reading time when reading at the same time is reduced to 1 / m. This can be regarded as an apparatus having a throughput of m times that of a single X-ray image output apparatus 1 having a single nxm slot cassette insertion slot. In addition, in order to control a plurality of X-ray image output devices 1 with a single control device 2, patient information input from the patient information input means 210, image processing conditions input from the condition input means 221, type of imaging device, If image data attached information such as an imaging region and an imaging direction is input only once to the control device 2, it can be associated with image data read by any X-ray image output device. There is no need to input such information for each image output apparatus.

  The X-ray imaging system of FIG. 9 is a modification of the X-ray imaging system of FIGS. 7 and 8, the plurality of X-ray image output devices 1d, 1e, and 1f are controlled by the single control device 2, but in FIG. 9, the plurality of X-ray image output devices 1d, 1e, and 1f are controlled. On the other hand, the control devices 2d, 2e, and 2f are connected one-to-one by communication cables 10d, 10e, and 10f. The control devices 2d, 2e, and 2f are configured to be able to communicate with each other via the communication cable 11, and the patient information, image processing conditions, imaging region, imaging direction and other image data attached information, image data, etc. The control devices 2d, 2e, and 2f can be shared.

  Each of the control devices 2d, 2e, and 2f may include a patient information input unit 210. In this case, there is an advantage that the user can input patient information from any control device.

  Moreover, you may comprise so that any one of control apparatus 2d, 2e, 2f may have the patient information input means 210. FIG. In this case, the user can input patient information only from the control device to which the patient information input unit 210 is connected, but there is an advantage that the cost of the X-ray imaging system can be reduced.

  In addition, each of the control devices 2d, 2e, and 2f may include a display unit 220. In this case, the user can confirm the image data and the image data attached information from any control device, and there is an advantage that the work can be made efficient. In particular, when a plurality of cassettes are read almost simultaneously with a plurality of X-ray image output apparatuses, an image can be displayed by a plurality of display means, so that there is an advantage that an operation for confirming image data can be speeded up. Further, any one of the control devices 2d, 2e, and 2f may be configured to include the display unit 220. In this case, the user can confirm the image data attached information and the image data only from the control device to which the display unit 220 is connected, but there is an advantage that the cost of the X-ray imaging system can be reduced. is there.

  Similarly, the condition input means 221 may be provided in each of the control devices 2d, 2e, and 2f, or may be provided in any one of the control devices 2d, 2e, and 2f.

  In the X-ray imaging system of FIG. 9, when a plurality of cassettes are processed at the same time, the reading operation and the image processing operation are performed in parallel by the plurality of X-ray image output devices and the control device. There is an advantage that the processing speed of the photographing system is remarkably improved. In addition, since image data and information attached to image data such as patient information is shared between the control devices, it can be handled as a single device, and it does not cause a decrease in operability even when operated in parallel. There are benefits.

  The embodiment and effect of the X-ray imaging system in which a plurality of X-ray image output devices 1 are connected to a plurality of control devices 2 on a one-to-one basis have been described with reference to FIG. It is clear that a similar system can be constructed for a type of system. At that time, the same effect as described in FIG. 9 can be obtained.

  The X-ray imaging system of FIG. 10 includes the dedicated type X-ray imaging system shown in FIGS. 5, 6, and 9, and the cassette-compatible type X-ray imaging shown in FIGS. 7, 8, and 9. It is one Example of the composite system of a system.

  In this example, the dedicated type X-ray imaging system of FIG. 6 and the control device 2 of the cassette-compatible type X-ray imaging system of FIG. 7 are configured to be controlled in a single unit. The present invention is not limited to the combination of the examples. For example, a combination of the dedicated type X-ray imaging system shown in FIG. 5 and the cassette-compatible type X-ray imaging system shown in FIG. 8 may be used, or other combinations may be used.

  This example has an effect that combines the effects described in each X-ray imaging system, and the most efficient system can be constructed.

  Since the operation of this example conforms to the operations of the dedicated type X-ray imaging system of FIG. 6 and the cassette-compatible type X-ray imaging system of FIG.

  Next, another embodiment of the X-ray imaging system according to the present invention will be described with reference to FIGS. FIG. 11 is an example of the control screen 1 displayed on the display unit 220 of the control device 2. Since the display means 220 is equipped with a touch panel as the condition input means 221, it is possible to input, specify and select conditions and the like by touching the displayed screen. .

  In this example, an example in which a touch panel is used as the condition input unit 221 will be described. However, the present invention does not limit the condition input unit 221 to a touch panel. Other means such as a keyboard, a mouse, a trackball, a voice input device, etc. may be used.

  The screen A is a screen for selecting the X-ray image output device 1 connected to the control device 2 and displaying the selected X-ray image output device 1. The icons (a1) to (a4) display names or sketches of the plurality of X-ray image output devices 1 connected to the control device 2, and can be used by touching any one of the icons. The X-ray image output apparatus 1 to be selected can be selected.

  When the X-ray image output device 1 is designated by the X-ray generation control device 3, that is, the X-ray tube 4 used by the user is designated by the X-ray generation control device 3, and the designated X-ray tube 4 is designated. When the control device 2 automatically selects one of the plurality of X-ray image output devices 1 based on the above, the icon corresponding to the automatically selected X-ray image output device 1 blinks or the density is The user is notified of which X-ray image output apparatus 1 is automatically selected by inverting or changing the color.

  In screens (b1) to (b7), reservation information for imaging, for example, patient ID information, name, imaging region, imaging direction, etc. are displayed, so that the user can confirm the order of the patients to be imaged. In addition, it is possible to know in advance what kind of shooting should be performed in the future.

  (C) of the screen C is a screen for displaying the video of the image data read by the X-ray image output apparatus 1. When the image data output by the X-ray image output apparatus 1 is received by the control apparatus 2, a video of the received image data is displayed on the screen (c).

  Further, when the image processing unit 237 performs image processing on the received image data, the image displayed on the screen (c) is changed from the image data image before image processing to the image after image processing. It changes to video of data.

  It is also possible to call up image data captured in the past and display it on the screen (c).

  Part (c) of the screen C displays a part of the image data attached information of the image data displayed on the screen (c). For example, the patient name, patient ID number, imaging region, imaging direction, etc. are displayed. For this reason, the user can reconfirm the attached information of the image data displayed on the screen (c).

  On the screen D (d1) to (d4), the reduced images of the image data captured so far are displayed. Further, on the screens (dd1) to (dd4), part of the image data attached information corresponding to each of the reduced images (d1) to (d4), for example, the patient name and the patient ID number are displayed.

  The video of the reduced image and the image data supplementary information displayed on the screens (d1) to (d4) and the screens (dd1) to (dd4) are displayed in order from the screen (d1) to the screen (d4). Placed towards the. The “time” here refers to the time when the X-ray imaging system accepts imaging reservation registration or a time corresponding thereto, the time when the X-ray is irradiated to the subject 50 or the time equivalent thereto, and the X-ray image output apparatus 1. Any one of the time when the image data is generated or the time corresponding thereto, the time when the control device 2 receives the image data or the time corresponding thereto, or the like may be used.

  Since the user can refer to and confirm past photographing according to a time-series order such as photographing time, the reference and confirmation work can be made very efficient.

  When the control device 2 receives new image data and the image of the received new image data is displayed on the screen (c), the image of the image data that has been displayed on the screen (c) is reduced. And is newly displayed at the position (d1). At this time, the reduced images that have been displayed in (d1) to (d3) are moved one by one in the direction of (d4) and displayed in (d2) to (d4), and until then (d4). The displayed reduced image is no longer displayed on the screen.

  The timing at which the image of the new image data received on the screen (c) is reduced and newly displayed at the position (d1) may be the timing at which the photographing of the screen (c) is approved. That is, an “OK” button for approving the image data image displayed on the screen (c) and a “re-shoot” button for requesting re-shooting (re-shooting) are displayed in the control screen 1. When the “OK” button is selected, the video of the new image data received on the screen (c) is reduced and newly displayed at the position (d1). When the “re-photograph” button is selected, the image data of the image data displayed on the screen (c) is erased and prepared for the next re-photographing.

  The video of the image data displayed on the screens (d1) to (d4) may be limited to those of the same patient (subject) as the video of the image data displayed on the screen (c). That is, when a plurality of X-ray images are taken by the same patient, the image data received last by the control device 2 is displayed on the screen (c), and the image data received by the control device 2 before that is Are displayed on the screens (d1) to (d4). Next, when a different patient is imaged, the video of the image data that has been displayed on the screens (d1) to (d4) is erased from the screen. With this operation, it goes without saying that the screen (cc) and the screens (dd1) to (dd4) operate in the same relationship.

  When the icon of the arrow pointing right or left shown on the screen E is touched, the video of the reduced image displayed on (d1) to (d4) of the screen D and the image displayed on the screen (dd1) to (dd4) The data ancillary information is displayed again by scrolling in the direction of the arrow. That is, by operating the screen E, the captured video of the reduced image and the image data attached information are sequentially scroll-displayed on the screens (d1) to (d4) and (dd1) to (dd4) according to the time-series order. Since it is configured as described above, it is possible to refer to and confirm the image by going back to an arbitrary time in the past.

  Further, when any one of the reduced image images is touched, the touched reduced image image is enlarged and displayed on the screen (c). At this time, the image data attached information corresponding to the image data image newly displayed on the screen (c) is displayed on the screen (cc).

  Further, when any of the reduced image images is touched, the touched image of the reduced image may be enlarged and displayed on a screen other than the newly generated screen (c).

FIG. 12 is an example of the control screen 2 displayed on the display unit 220 of the control device 2.
In the icons (f1) to (f9) on the screen F, a large classification of the imaging region is displayed. Major classification is a rough classification based on the main components of the human body such as “head”, “chest”, “abdomen”, “upper limb”, “lower limb”, “spine”, “pelvis”. is there. The user notifies the controller 2 of the major classification of the part to be photographed by selecting and touching the part to be photographed from the icons (f1) to (f9).

  In the present invention, according to the X-ray imaging apparatus registered on the screen A, the major classification part names displayed on the screen F are controlled.

  For example, in the case where three X-ray imaging apparatuses of the standing type, the lying type, and the cassette type are registered on the screen A, that is, the standing type, the standing type, and the cassette type are registered in the control device 2. When three X-ray imaging apparatuses are connected, for example, five items of “chest”, “abdomen”, “lumbar spine”, “upper limb”, and “lower limb” are registered in the large classification of the screen F corresponding to the standing type. Has been. In addition, the major classification of the screen F corresponding to the supine type includes, for example, “head”, “chest”, “abdomen”, “spine”, “pelvis”, “upper limb”, “lower limb”, “soft part, etc.” 8 items are registered. In addition, for example, “head”, “chest”, “abdomen”, “spine”, “pelvis”, “upper limb”, “lower limb”, “soft part, etc.” Nine items of “newborn” are registered.

  When the user selects the standing icon on the screen A, the screen F includes the above five items “chest”, “abdomen”, “lumbar spine”, “upper limb”, and “lower limb”. Is selected on the screen F, eight items of “head”, “chest”, “abdomen”, “spine”, “pelvis”, “upper limb”, “lower limb”, “soft part etc.” are displayed on the screen A. When the cassette-compatible icon is selected, the screen F displays “Head”, “Chest”, “Abdomen”, “Spine”, “Pelvis”, “Upper limb”, “Lower limb”, “Soft limb”, “Newborn” 9 items are displayed as selections in any of (f1) to (fg) of the screen F.

  In this way, in the present invention, the pre-registered major classification is displayed for the selected X-ray imaging apparatus, and an extra major classification (major classification not used in the selected X-ray imaging apparatus). Therefore, when the user selects the large classification, the target large classification can be selected in a short time without confusion.

  When the X-ray imaging apparatus and the major classification are determined, the determined X-ray imaging apparatus and the small classification of the imaging region corresponding to the major classification are displayed as selections in (g1) to (g4) of the screen G. The The sub-category of the imaged part is the part classified in the major classification into more detailed parts. For example, when the major classification is “upper limb”, “shoulder joint”, “scapula”, “shoulder chain” “Indirect”, “Humeral bone”, “Elbow joint”, “Forearm bone”, “Hand joint”, “Carpal bone”, “Finger bone”, etc. fall into the small classification. On the screen H (h11) to (h14), the shooting direction corresponding to the small classification (g1) is shown, and in (h21) to (h24), the shooting direction corresponding to the small classification (g2) is (h31). In (h34), the shooting direction corresponding to the small classification (g3) is displayed as a selection branch, and in (h41) to (h44), the shooting direction corresponding to the small classification (g4) is displayed as a selection branch.

  Representative examples of the shooting direction are “backward forward shooting (PA)”, “front-rear direction shooting (AP)”, “LAT (Lateral radiography)”, “slanting” “Oblique Radiography” ”and the like.

  In the present invention, the small classification and the imaging direction are registered for each combination of the X-ray imaging apparatus and the large classification. For a combination of the selected X-ray image capturing apparatus and the large classification, a pre-registered small classification and an imaging direction are displayed as selection branches, and an extra small classification and an imaging direction (selected X-ray image capturing apparatus are selected. In this case, the user does not get confused when selecting a small category or a shooting direction in a short time. The target small classification and shooting direction can be selected.

  On the screen I (i1) to (i4), set shooting menus corresponding to the small classifications (g1) to (g4) are displayed as selection branches. Set shooting is a set of several commonly used shooting directions, such as a two-way shooting set and a three-way shooting set. For example, when a set shooting menu in which three-way shooting, that is, front-rear direction shooting, front-rear direction shooting, and direction-measurement shooting is registered, is selected. The shooting direction is selected at once. For this reason, the user can save the trouble of individually selecting the three photographing directions.

  The above-described major classification, minor classification, imaging direction, set imaging menu contents, presence / absence of display, display order, and the like are preferably customized according to the hospital or user's preference. For example, when there are large classifications, small classifications, shooting directions, set shooting menus, and the like that are not used in a certain shooting room, it is more convenient to be able to deal with the display unit 220 not to display them.

  When the upward and downward arrow icons shown on the screen J are touched, the screen G, the screen h, and the screen I are synchronously scrolled in the direction of the arrow. If there are many small categories that cannot be displayed on the display screen, this icon can be used to scroll the screen and search for small categories that were not displayed on the screen.

  The selected small category and shooting direction are sequentially displayed on screens (k1) to (k8). For example, 1) major classification = “chest”, minor classification = “upper rib”, imaging direction = “posterior anterior imaging (PA)”, 2) major classification = “vertebra”, minor classification = “thoracic vertebra” , Shooting direction = “front-rear direction shooting (AP)”, 3) large classification = “upper limb”, small classification = “humerus”, shooting direction = “measurement direction shooting (LAT: Lateral rediographyh)” Is performed, “knee upper PA” is displayed on the (k1) screen, “thoracic vertebra AP” is displayed on the (k2) screen, and “humerus LAT” is displayed on the (k3) screen. If the minor classification is displayed, the major classification can be understood without being dared to display. Therefore, in the present invention, only the minor classification and the shooting direction are displayed. However, even if other information is displayed, there is no problem.

  As described above, in the present invention, the information on the selected imaging region and imaging direction is sequentially displayed on the screen K. Therefore, the user can proceed while constantly confirming what is selected, and Operation mistakes can be prevented. In the above example, only the information on the imaging region and the imaging direction is displayed on the screen K. However, other information, for example, the type of the X-ray image output apparatus may be displayed together.

  The icon (11) on the screen L is an icon for instructing confirmation of information displayed on the screen K. When this icon is touched, information such as the small classification and the imaging direction displayed on the screen K is registered as confirmed information in association with the patient information in the storage unit 237 in the control device 2.

  The icon (12) on the screen L is an icon for instructing cancellation of the information displayed on the screen K. When this icon is touched, information such as the small classification and the shooting direction displayed on the screen K is erased from the screen.

  The icon (13) on the screen L is an icon for instructing partial deletion of information displayed on the screen K. When the icon (13) is touched after the icons (k1) to (k8) to be deleted are specified (touched), information such as the small classification and the shooting direction corresponding to the specified icon is deleted from the screen.

  Further, the icon (13) on the screen L may be an icon for instructing partial correction of information displayed on the screen K. If the icons (k1) to (k8) to be corrected are designated (touched) and then the icon (13) is touched, information such as the large classification, the small classification, and the shooting direction corresponding to the designated icon can be corrected. Here, when information such as a large classification, a small classification, and an imaging direction is newly selected, the newly selected information is newly displayed on the designated icon portion.

  As described above, according to the present invention, the user can select, categorize, cancel, partially delete, or partially modify the selected imaging region, such as major classification, minor classification, and imaging direction. Even if a mistake is made, it is possible to correct the error in the shortest time by a minimum operation.

  In the present invention, the image processing means 237 performs optimal image processing on the image data in accordance with the imaging region and the imaging direction determined in this way. It is possible to maintain the finished image. In particular, since it is preferable to optimize the processing parameters, the type of processing, the degree of processing, and the like in the gradation conversion processing according to the imaging region and the imaging direction, the difference in the imaging region and the imaging direction as in the present invention. Accordingly, by determining processing parameters, processing types, processing levels, etc., it is possible to always maintain an optimal image finish. In this example, only major classifications, minor classifications, and shooting directions that can be used as control screens are displayed. For example, all major classifications, minor classifications, and shooting directions are displayed in advance, and major classifications that cannot be used are displayed. The user can be informed of selectable items by changing the display color of the small classification and shooting direction. At this time, even if an unusable item is selected, it is preferable that error information is displayed so that the major classification to be selected is not accepted.

  As described above, it is possible to construct an X-ray imaging system that allows different detection means and different types of devices and performs integrated control over a plurality of X-ray image output devices and a plurality of X-ray tubes. It is possible to provide an environment with high work efficiency in which the labor of operation is minimized.

  In addition, it is possible to construct an X-ray imaging system that can be controlled by a single control device for a plurality of X-ray image output devices without being limited to the type of detection means or apparatus, thereby minimizing the installation area. The system can be easily constructed or expanded at a low cost according to the scale of the hospital and the imaging frequency.

  In addition, it eliminates complicated operations related to selection of imaging region, imaging direction, etc., and references to past images, and it is possible to construct an X-ray imaging system that can prevent and recover a user's operation error. Can provide a reliable system.

  In addition, since the X-ray imaging system is equipped with image processing means that can automatically respond to differences in detection means and correction content, even when different detection means or different types of devices are connected, always with a constant finish, An image with good image quality can be provided.

  INDUSTRIAL APPLICABILITY The present invention can be applied to an X-ray imaging system and a control apparatus, and the X-ray imaging system of different types and different detection means is mixed. In addition, the installation area of the apparatus can be reduced, the introduction cost is low, it is scalable, and it is easy to use and reliable. In addition, it is possible to obtain an image with a constant finish even when different detection means are used.

1 is a diagram illustrating a configuration example of a standing type X-ray imaging system. It is a figure which shows the structural example of a supine type X-ray imaging system. It is a figure which shows the structural example of the X-ray imaging system of a cassette corresponding | compatible type. It is a figure which shows the structural example of a control apparatus. It is a figure which shows the structural example of the X-ray imaging system which has several X-ray image output apparatuses of a dedicated type. It is a figure which shows another example of a structure of the X-ray imaging system which has several X-ray image output apparatuses of a dedicated type. It is a figure which shows the structural example of the X-ray image imaging system which has a some cassette corresponding | compatible X-ray image output device. It is a figure which shows another structural example of the X-ray imaging system which has a some cassette corresponding | compatible X-ray image output device. It is a figure which shows another example of a structure of the X-ray imaging system which has a some cassette corresponding | compatible X-ray image output apparatus. It is a figure which shows the example of 1 structure of the X-ray imaging system which has a some X-ray image output device of a special type, and a cassette corresponding | compatible X-ray image output device. It is a figure which shows an example of a control screen. It is a figure which shows an example of another control screen.

Explanation of symbols

1 X-ray image output device 2 Control device 3 X-ray generation control device 4 X-ray tube 5 X-ray 6 Cassette

Claims (8)

An X-ray image output device using a solid flat detector as detection means and detecting means for detecting a stimulable phosphor, which outputs X-rays emitted from an X-ray tube with detection means and then outputs them as digitized image data An X-ray imaging system having a plurality of types of X-ray image output devices including the X-ray image output device and a control device for controlling the plurality of types of X-ray image output devices,
The control device includes communication means for acquiring image data output from each of the plurality of types of X-ray image output devices;
An X-ray imaging system comprising: means for associating image data attached information with each image data acquired by the communication means.   2. The X-ray image according to claim 1, wherein the control device includes an image processing unit that performs correction processing that is different depending on a type of the detection unit, on each image data acquired by the communication unit. Shooting system.   The control device includes display control means for displaying a plurality of display screens on a display means using the image data output, acquired and corrected from each of the plurality of types of X-ray image output devices as one display screen. The X-ray imaging system according to claim 2. The image processing means performs at least one correction process of gain correction and offset correction when the detection means is a solid flat detector,
When the detection means is a photostimulable phosphor, correction of the tilting of the polygon used by the laser scanning means, correction of unevenness generated by the light collecting means for condensing the stimulating light, sensitivity inherent to the stimulable phosphor 4. The X-ray imaging system according to claim 2, wherein at least one correction process is performed among the correction of unevenness and the correction of sub-scanning unevenness caused by the conveying means. When the detection means is a solid flat detector, the image processing means performs predetermined image processing after performing logarithmic conversion on the image data,
4. The X-ray imaging according to claim 2, wherein when the detection means is a stimulable phosphor, predetermined image processing is performed without logarithmic conversion on the image data. system.   The control device has storage means for storing the contents of the correction processing performed in the image processing in association with the image data corrected as image data additional information. The X-ray imaging system according to any one of 5.   The X-ray imaging system according to claim 6, wherein the control device includes a second communication unit that outputs image data associated with the image data auxiliary information. An X-ray image output device using a solid flat detector as detection means and detecting means for detecting a stimulable phosphor, which outputs X-rays emitted from an X-ray tube with detection means and then outputs them as digitized image data A control device for controlling a plurality of types of X-ray image output devices including the X-ray image output device,
Communication means for acquiring image data output from each of the plurality of types of X-ray image output devices;
An image processing unit that performs different correction processing on the image data acquired by the communication unit depending on the type of the detection unit.