JP4609238B2 - Digital radiography equipment - Google Patents

Description

  The present invention relates to a digital radiography apparatus for processing an X-ray detected by an X-ray detection means such as an image intensifier or a flat panel X-ray detector to create an X-ray image.

  In digital radiography equipment, there are inconveniences such as static electricity generated by applying high voltage, transient noise in electrical processing due to external induction, etc., and data loss. As a result, the pixel value becomes an abnormal value and the image deteriorates.

Conventionally, the following has been proposed in order to prevent the image deterioration as described above.
Digital images that are sequentially input are integrated in the time direction, and the difference between the integrated digital image and the digital image that is sequentially input is obtained for each of a plurality of set small areas, and the digital image that is sequentially input The luminance of the image is obtained for each of a plurality of set small regions, the frequency characteristic of the filtering means is determined for each region according to the obtained difference and luminance, and the optimum edge enhancement processing is performed for each region. (For example, refer to Patent Document 1).

Further, a sub-region consisting of a target pixel and a pixel adjacent thereto is set for each of all pixels of image data for one frame of X-ray detected by the X-ray detection means, and the value of each pixel in the sub-region is set. There is a so-called median filter in which an intermediate value that is intermediate between them is extracted, and the extracted intermediate value is used as the pixel value of the target pixel.
JP-A-7-105354

  However, in the case of the conventional example as described above, when the target pixel is affected by noise or data loss, the pixel value becomes an abnormal value, so that the pixel value can be brought close to a normal value. If the target pixel is not affected by noise or data loss, it will be replaced with a value that is far from the actual pixel value. X-ray images have a drawback that they tend to be blurred images.

  The present invention has been made in view of the circumstances as described above, and replaces each pixel with a pixel value that suppresses the influence of noise and data loss as much as possible, thereby minimizing image degradation. The purpose is to be able to.

Digital radiography apparatus according to the invention of 請 Motomeko 1, in order to achieve as described above purpose, the following construction.
That is, (B1) a plurality of windows each having a different number of pixels including a target pixel and a pixel adjacent thereto are set for all the pixels of image data for one frame of X-rays detected by the X-ray detection unit; A window intermediate value extracting unit that obtains a value of each pixel in each window and extracts a window intermediate value serving as an intermediate value thereof; and (B2) calculating a difference between the window intermediate values extracted by the window intermediate value extracting unit. (B3) The difference calculated by the difference calculation means and the set value are compared. When the difference is larger than the set value, a large window signal is displayed, and the difference is smaller than the set value. A window comparing means for outputting a small window signal each time; and (B4) a previous window in response to the large window signal output from the window comparing means. The window intermediate value for the window with a large number of pixels extracted by the window intermediate value extracting means is the pixel value for the window intermediate value for the window with the small number of pixels extracted by the window intermediate value extracting means in response to the small window signal. And (B5) image processing means for creating an X-ray image based on the pixel value output from the pixel value selection means.
As a set value to be compared with the difference calculated by the difference calculating means, an average value of pixel values in the reference image is calculated in advance, and based on the average value, a fixed value such as the same value as the average value or a value two to three times larger. For example, a variation value such as 10 to 50% of the value of the target pixel itself is employed.

(Action / Effect)
According to the configuration of the digital radiography apparatus of the invention according to claim 1 , when the target pixel is affected by noise or data loss, the window intermediate value for a window with a small number of pixels becomes an abnormal value, If the difference between the window intermediate value for a window with a large number of pixels is large and the target pixel is not affected by noise or data loss, the window intermediate value and the number of pixels for a window with a small number of pixels Focusing on the fact that the difference between the window intermediate value for a large number of windows is small and the difference between the window intermediate value for a window with a small number of pixels and the window intermediate value for a window with a large number of pixels is larger than the set value As pixels are affected by noise and data loss, If the difference between the window intermediate value for a window with a small number of pixels and the window intermediate value for a window with a large number of pixels is smaller than the set value Assuming that the pixels are not affected by noise or data loss, a window intermediate value for a window having a small number of pixels is used as a pixel value, and an X-ray image is created using these pixel values.
Therefore, only when the target pixel is affected by noise or data loss, the window intermediate value for a window with a large number of pixels that suppresses the influence is used as the pixel value, and the target pixel is noise or data loss. When not affected by the window, the window intermediate value for a window with a small number of pixels, that is, the value of the pixel close to the target pixel is used as the pixel value, so that the influence of noise and data loss is minimized for each pixel. Pixel values can be replaced, and image degradation can be minimized.

The invention according to claim 2, in digital radiography according to claim 1, constituting a window intermediate value extracting means median filter.

(Action / Effect)
According to the configuration of the digital radiography apparatus of the second aspect of the invention, the value of each pixel in the window is obtained, and an intermediate value between them is extracted.
Therefore, for example, a process for extracting an intermediate value as compared with a case where the value of each pixel in the window is obtained, an average value thereof is calculated to obtain an intermediate value, and the intermediate value is used as the intermediate value. Can be done easily and quickly.

According to the configuration of the digital radiography apparatus of the invention according to claim 1, when the target pixel is affected by noise or data loss, the window intermediate value for a window with a small number of pixels becomes an abnormal value, If the difference between the window intermediate value for a window with a large number of pixels is large and the target pixel is not affected by noise or data loss, the window intermediate value and the number of pixels for a window with a small number of pixels Focusing on the fact that the difference between the window intermediate value for a large number of windows is small and the difference between the window intermediate value for a window with a small number of pixels and the window intermediate value for a window with a large number of pixels is larger than the set value As pixels are affected by noise and data loss, And the pixel value windows intermediate values for example were a large number of pixels window, whereas, when the difference between the window intermediate values for large window of windows intermediate value and the number of pixels to a small window number of pixels is smaller than the set value, the target Assuming that the pixels are not affected by noise or data loss, a window intermediate value for a window having a small number of pixels is used as a pixel value, and an X-ray image is created using these pixel values.
Therefore, only when the target pixel is affected by noise or data loss, the window intermediate value for a window with a large number of pixels that suppresses the influence is used as the pixel value, and the target pixel is noise or data. When not affected by defects, the window intermediate value for a window with a small number of pixels, that is, the value of the pixel close to the target pixel is used as the pixel value, so the influence of noise and data loss is minimized for each pixel. The pixel values can be replaced, and image degradation can be minimized.

  Next, embodiments of the present invention will be described in detail with reference to the drawings.

FIG. 1 is a block diagram showing an overall schematic configuration of a digital radiography apparatus according to a first embodiment of the present invention. An X-ray tube 1 for irradiating a subject H with X-rays across the subject H A flat panel X-ray detector 2 is provided as X-ray detection means for detecting X-rays transmitted through the subject H.
An X-ray generator 3 that generates X-rays with respect to the X-ray tube 1 is connected to the X-ray tube 1.

  An image processing unit 4 is connected to the flat panel X-ray detector 2, and a display monitor 5 is connected to the image processing unit 4, and an X-ray image detected by the flat panel X-ray detector 2. An X-ray image is created by processing data, and the created X-ray image can be displayed.

The image processing unit 4 includes an intermediate value extraction unit 6, a difference calculation unit 7, a pixel value comparison unit 8, a pixel value selection unit 9, and an image processing unit 10.
The intermediate value extraction means 6 sets a sub-region consisting of the target pixel and adjacent pixels for all the pixels of the image data for one frame of X-rays detected by the flat panel X-ray detector 2. Then, the value of each pixel in the sub-region is obtained, and an intermediate value that is intermediate between them is extracted.

The difference calculation means 7 calculates the difference between the intermediate value extracted by the intermediate value extraction means 6 and the value of the target pixel (original value).
The pixel value comparison unit 8 compares the difference calculated by the difference calculation unit 7 with the set value. When the difference is larger than the set value, the intermediate value signal is obtained. When the difference is smaller than the set value, the original value signal is obtained. Each is designed to output. As the set value, an average value of pixel values in the reference image is calculated in advance, and based on the average value, it is a fixed value such as a value that is the same as the average value or 2 to 3 times, or 10 to 10 of the value of the target pixel itself. A variation value such as a value of 50% is adopted. Any value is sufficiently smaller than an abnormal value when an abnormality occurs due to the influence of noise or data loss.

In the pixel value selection means 9, the intermediate value extracted by the intermediate value extraction means 6 in response to the intermediate value signal output from the pixel value comparison means 8, and the value of the target pixel in response to the original value signal, respectively. A value is selected and output.
The image processing unit 10 creates an X-ray image based on the pixel value output from the pixel value selection unit 9.

Next, an image processing operation when a sub-region composed of three 1 × 3 pixels P0, P1, and P2 is set will be described.
In FIG. 2A, it is assumed that the value of the target pixel P0 becomes an abnormal value (remarkably larger than the values of the normal pixels P1 and P2) due to noise, and The values of the other pixels P1 and P2 are normal values, and for convenience, the pixel values are P1 <P2.

  As a result, the intermediate value extraction unit 6 extracts the pixel value of the pixel P2 that is a normal value as the intermediate value, and the difference calculation unit 7 calculates the difference (the value of the pixel P0−the value of the pixel P2). The set value is compared by the pixel value comparison means 8. Since the value of the pixel P0 is an abnormal value, the difference becomes a large value and becomes larger than the set value, so that an intermediate value signal is output, and the pixel value selection means 9 responds to the intermediate value signal and outputs the target pixel. The value of the pixel P2, which is the intermediate value extracted as the pixel value, is replaced.

  On the other hand, as shown in FIG. 2B, the value of the target pixel P0 (assuming that it is smaller than the adjacent pixel P1) is a normal value, and the value of the adjacent pixel P2 is abnormal due to noise. If the value is a value, the normal value of the pixel P1 is extracted as an intermediate value, and the difference calculation means 7 calculates a difference (the value of the pixel P0−the value of the pixel P1, which is an absolute value). The pixel value comparison means 8 compares the value. For convenience, the pixel value is P0 <P1. Since the values of the pixels P0 and P1 are both normal values, an original value signal is output because the difference is small and smaller than the set value, and the pixel value selection means 9 responds to the original value signal. Thus, the value of the target pixel P0 itself is replaced as the pixel value of the target pixel. These processes are performed on pixels for one frame, and an X-ray image is created in the image processing means 10 based on the obtained pixel values.

  With the above configuration, when the value of the target pixel is a normal value, the value of the target pixel itself is left as it is, and only when the value of the target pixel is an abnormal value, it is replaced with the intermediate value in the sub-region. A sharp X-ray image can be created with the pixel value of.

Next, the operation of image processing when a sub-region consisting of nine 3 × 3 pixels P0, P1, P2, P3, P4, P5, P6, P7, and P8 is set will be described.
In FIG. 3A, it is assumed that the values of two pixels P2 and P7 adjacent to the target pixel P0 are abnormal values (remarkably larger values than P1 and P2) due to noise. The values of the other pixels P1, P3, P4, P5, P6, and P8 are normal values. For convenience, the pixel values are P1 <P3 <P4 <P5 <P6 <P8.

  As a result, the intermediate value extraction unit 6 extracts the pixel value of the pixel P6 that is a normal value as the intermediate value, and the difference calculation unit 7 calculates the difference (the value of the pixel P0−the value of the pixel P6). The set value is compared by the pixel value comparison means 8. Since the value of the pixel P0 is an abnormal value, the difference becomes a large value and becomes larger than the set value, so that an intermediate value signal is output, and the pixel value selection means 9 responds to the intermediate value signal and outputs the target pixel. The value of the pixel P6 that is the intermediate value extracted as the pixel value is replaced.

On the other hand, as shown in FIG. 3B, the values of the target pixel P0 and the adjacent pixels P1, P2, P4, P6, and P7 are normal values, and the values of the adjacent pixels P3, P5, and P8 are noise. If it is an abnormal value, the value of the pixel P6 that is a normal value is extracted as an intermediate value. For convenience, the pixel values are P0 <P1 <P2 <P4 <P6 <P7.
A difference (P0-P6, which is an absolute value) is calculated by the difference calculation means 7, and the difference and the set value are compared by the pixel value comparison means 8. Since the values of the pixels P0 and P6 are both normal values, an original value signal is output because the difference is small and smaller than the set value, and the pixel value selection means 9 responds to the original value signal. Then, the value of the target pixel P0 itself is replaced as the pixel value of the target pixel, and is output to the image processing means 10 as the pixel value of the target pixel. These processes are performed on the pixels for one frame, and the obtained pixel value An X-ray image is created based on the above.

  In this way, setting a sub-region with a large number of pixels is useful when an abnormal value is predicted to span a plurality of pixels, such as data loss.

FIG. 4 is a block diagram showing the overall schematic configuration of a digital radiography apparatus according to Embodiment 2 of the present invention. The differences from Embodiment 1 are as follows.
That is, the image processing unit 4 includes a window intermediate value extracting unit 21, a difference calculating unit 22, a window comparing unit 23, a pixel value selecting unit 24, a final value determining unit 25, and an image processing unit 26.

  In the window intermediate value extracting means 21, the number of pixels composed of the target pixel and the adjacent pixels is different for each of all pixels of the image data for one frame of the X-ray detected by the flat panel X-ray detector 2. A plurality of windows are set, the value of each pixel in each window is obtained, and a window intermediate value that is intermediate between them is extracted, and the number of the set windows is output to the final value determining means 25. .

The difference calculation means 22 calculates the difference between the window intermediate values extracted by the window intermediate value extraction means 21.
The window comparison means 23 compares the difference calculated by the difference calculation means 22 with the set value. When the difference is larger than the set value, the large window signal is obtained. When the difference is smaller than the set value, the small window signal is obtained. It is designed to output. As the set value, an average value of pixel values in the reference image is calculated in advance, and based on the average value, it is a fixed value such as a value that is the same as the average value or 2 to 3 times, or 10 to 10 of the value of the target pixel itself. A variation value such as a value of 50% is adopted. Any value is sufficiently smaller than an abnormal value when an abnormality occurs due to the influence of noise or data loss. When three or more windows are set, comparison is performed in order from the smallest number of pixels.

  In the pixel value selection unit 24, in response to the large window signal output from the window comparison unit 23, the window intermediate value for the window having a large number of pixels extracted by the window intermediate value extraction unit 21 is output in response to the small window signal. A window intermediate value for a window with a small number of pixels extracted by the window intermediate value extracting means 21 is selected and output as a pixel value.

Based on the number of windows selected from the window intermediate value extraction unit 21, the final value determination unit 25 outputs pixel values from the pixel value selection unit 24 a number of times smaller than the selected number (final number). If the final number of times has not been reached, the pixel value is output to the difference calculation means 22, and the difference from the intermediate value of the window having a larger number of pixels from the intermediate value extraction means 21 is calculated. If the final number has been reached, the pixel value output from the pixel value selection means 24 is output to the image processing means 26.
The image processing unit 26 creates an X-ray image based on the pixel value output from the pixel value selection unit 24.

  Next, a 3 × 3 9 pixels P0, P1, P2, P3, P4, P5, P6, P7, P8 and a 5 × 5 25 pixels P0, P1, P2,. An image processing operation when a middle window composed of P22, P23, and P24 and a large window composed of 49 pixels of 7 × 7 P0, P1, P2,..., P46, P47, and P48 will be described.

As shown in FIG. 5, the values of the five pixels P2, P3, P5, P7, and P8 adjacent to the target pixel P0 are significantly larger than the abnormal values (P1, P4, and P6) due to data loss. Value), and the values of the other pixels P1, P4 and P6 are normal. For the sake of convenience, the values of the pixels are P0 <P2 <P3 <P5 <P7 <P8. , and P1 <P4 <P6 <P 9 <... <P24 <P25 <... <P48 as the value of the pixel.

  As a result, in the window intermediate value extraction means 21, the pixel value of the pixel P2 that is an abnormal value as an intermediate value in the small window [see FIG. 5A], and the pixel that is a normal value as the intermediate value in the intermediate window The pixel value of P17 [see (b) of FIG. 5] is extracted in the large window, and the pixel value of the pixel P30, which is a normal value, is extracted as an intermediate value [see (c) of FIG. 5]. Further, the set number of windows 3 is output to the final value determining means 25.

The difference calculating means 22 first calculates the difference (the value of the pixel P2−the value of the pixel P17) between the intermediate value of the small window (value of the pixel P2) and the intermediate value of the middle window (value of the pixel P17). The window comparator 23 compares the difference with the set value. Since the intermediate value of the small window (the value of the pixel P2) is an abnormal value, the large window signal is output to the difference is greater than the set value becomes a large value, the pixel value selection section 24, the large window In response to the signal, the intermediate value P17 of the middle window having a large number of pixels is selected as the pixel value of the target pixel and output to the final value determining means 25.

  The final value discriminating means 25 discriminates whether or not the pixel value is output from the pixel value selecting means 24 by the number of times (final number of times) smaller by 1 than the number of selected windows. The intermediate value (value of pixel P17) of the middle window selected by the pixel value selection means 24 is output to the difference calculation means 22, and the intermediate value (value of pixel P17) and the intermediate value of the large window (value of pixel P30). ) (The value of the pixel P17−the value of the pixel P30), and the difference is compared with the set value by the window comparison unit 23. Since the intermediate value of the middle window (the value of the pixel P17) is a normal value, the difference becomes a small value and becomes smaller than the set value, so that a small window signal is output. In response to the signal, the intermediate value (the value of the pixel P17) of the middle window with a small number of pixels is selected as the pixel value of the target pixel and output to the final value determining means 25.

  The final value determination unit 25 determines that the final value is the second value because it is the second time, and the intermediate value (the value of the pixel P17) selected by the pixel value selection unit 24 is used as the pixel value of the target pixel for image processing. The data is output to the means 26, and those processes are performed on the pixels for one frame, and an X-ray image is created based on the obtained pixel values.

  According to the second embodiment, in the case where an abnormality occurs in a relatively large number of pixels due to data loss or the like, the image deterioration is avoided by avoiding replacing the abnormal value as the value of the target pixel by median filter processing as much as possible. Can be suppressed.

  In the above embodiment, in order to extract the intermediate value in the sub-region or window, the intermediate value is replaced as the value of the target pixel by the median filter processing. The average value of all the pixel values may be calculated, and the average value may be extracted as an intermediate value. In short, an intermediate value that is intermediate in a sub-region or window is extracted. I just need it.

  The present invention is not limited to the flat panel X-ray detector 2 and can be applied to processing of X-rays detected by an image intensifier.

1 is a block diagram showing an overall schematic configuration of Embodiment 1 of a digital radiography apparatus according to the present invention. FIG. 6 is a diagram for explaining an image processing operation according to the first exemplary embodiment. FIG. 6 is a diagram for explaining another image processing operation according to the first exemplary embodiment. It is a block diagram which shows the whole schematic structure of Example 2 of the digital radiography apparatus based on this invention. FIG. 10 is a diagram for explaining an image processing operation according to the second embodiment.

Explanation of symbols

2. Flat panel X-ray detector (X-ray detection means)
6 ... Intermediate value extracting means 7 ... Difference calculating means 8 ... Pixel value comparing means 9 ... Pixel value selecting means 10 ... Image processing means 21 ... Window intermediate value extracting means 22 ... Difference calculating means 23 ... Window comparing means 24 ... Pixel value selecting Means 25 ... Image processing means

Claims (2)

(B1) A plurality of windows each having a different number of pixels including a target pixel and pixels adjacent thereto are set for each of all pixels of image data for one frame of X-rays detected by the X-ray detection means, seeking the value of each pixel in the calculated and the window intermediate value extracting means for extracting a window intermediate value serving as their intermediate values, the difference between the window intermediate values each other extracted in (B2) the window intermediate value extracting means The difference calculation means and (B3) comparing the difference calculated by the difference calculation means with the set value. When the difference is larger than the set value, a large window signal is obtained. When the difference is smaller than the set value, the difference is small. Window comparison means for outputting each of the window signals; and (B4) the window in response to the large window signal output from the window comparison means. The window intermediate value for the window with a large number of pixels extracted by the intermediate value extraction means is used as the pixel value for the window intermediate value for the window with a small number of pixels extracted by the window intermediate value extraction means in response to the small window signal. Digital radiography comprising: pixel value selection means for selecting and outputting; and (B5) image processing means for creating an X-ray image based on the pixel value output from the pixel value selection means. apparatus. 2. The digital radiography apparatus according to claim 1 , wherein the window intermediate value extracting means is a median filter.

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