Method and apparatus for classifying picture elements in radiation images

Abstract: Calculations are made to find the differences, Δij=fij-f0, between the value of an image signal component f0 representing a picture element P0 in a radiation image and the values of image signal components fij representing the picture elements Pij, which are located on each of a plurality of lines Li, where i=1, 2, ..., n, extending from the picture element P0 to the peripheral parts of the radiation image, and which are spaced a plurality of distances rij, where j=1, 2, ..., m, from the picture element P0. A representative value, which is representative of the differences Δij, is then found for each of the lines Li. A mean level value of two representative values for each set of two lines, which extend from the picture element P0 in approximately opposite directions, is then calculated. From the mean-­ level values, which have been calculated for a plurality of the sets of lines, a judgment is made as to whether the picture element P0 falls or does not fall within the region corresponding to a circular pattern in the radiation image.

Description: BACKGROUND OF THE INVENTION Field of the Invention This invention relates to a method for classifying picture elements in a radiation image into those belonging to a certain image pattern and those not belonging to a certain image pattern and an apparatus for carrying out the method. This invention particularly relates to a method and apparatus for classifying picture elements such that, from an image signal representing a radiation image of an object, a judgment can be made as to whether a predetermined picture element P0 in the radiation image falls or does not fall within the region corresponding to a predetermined pattern in the radiation image. Description of the Prior Art Techniques for reading out a recorded radiation image in order to obtain an image signal, carrying out appropriate image processing on the image signal, and then reproducing a visible image by use of the processed image signal have heretofore been known in various fields. For example, as disclosed in Japanese Patent Publication No. 61(1986)-5193, an X-ray image is recorded on an X-ray film having a small gamma value chosen according to the type of image processing to be carried out, the X-ray image is read out from the X-ray film and converted into an electric signal (image signal), and the image signal is processed and then used for reproducing the X-ray image as a visible image on a copy photograph or the like. In this manner, a visible image having good image quality with high contrast, high sharpness, high graininess, or the like can be reproduced. Also, when certain kinds of phosphors are exposed to radiation such as X-rays, α-rays, β-rays, γ-rays, cathode rays or ultraviolet rays, they store part of the energy of the radiation. Then, when the phosphor which has been exposed to the radiation is exposed to stimulating rays such as visible light, light is emitted by the phosphor in proportion to the amount of energy stored thereon during its exposure to the radiation. A phosphor exhibiting such properties is referred to as a stimulable phosphor. As disclosed in U.S. Patent Nos. 4,258,264, 4,276,473, 4,315,318, 4,387,428, and Japanese Unexamined Patent Publication No. 56(1981)-11395, it has been proposed to use stimulable phosphors in radiation image recording and reproducing systems. Specifically, a sheet provided with a layer of the stimulable phosphor (hereinafter referred to as a stimulable phosphor sheet) is first exposed to radiation which has passed through an object such as the human body in order to store a radiation image of the object thereon, and is then scanned with stimulating rays, such as a laser beam, which cause it to emit light in proportion to the amount of energy stored during exposure to the radiation. The light emitted by the stimulable phosphor sheet, upon stimulation thereof, is photoelectrically detected and converted into an electric image signal. The image signal is then used to reproduce the radiation image of the object as a visible image on a recording material such as photographic film, on a display device such as a cathode ray tube (CRT), or the like. Radiation image recording and reproducing systems which use stimulable phosphor sheets are advantageous over conventional radiography using silver halide photographic materials, in that images can be recorded even when the energy intensity of the radiation to which the stimulable phosphor sheet is exposed varies over a wide range. More specifically, since the amount of light which the stimulable phosphor sheet emits when being stimulated varies over a wide range and is proportional to the amount of energy stored thereon during its exposure to the radiation, it is possible to obtain an image having a desirable density regardless of the energy intensity of the radiation to which the stimulable phosphor sheet was exposed. In order to obtain the desired image density, an appropriate read-out gain is set when the emitted light is being detected and converted into an electric signal to be used in the reproduction of a visible image on a recording material, such as photographic film, or on a display device, such as a CRT. Recently, in the radiation image recording and reproducing systems which use X-ray film or stimulable phosphor sheets, particularly in such radiation image recording and reproducing systems designed to facilitate medical diagnoses, not only have image signals been produced in ways which ensure that the visible images produced from them will be of high quality, but image signals have also been processed in ways which allow certain image patterns to be extracted from radiation images. One type of processing which results in the extraction of an image pattern is disclosed in, for example, U.S. Patent No. 4,769,850. Specifically, an image pattern can be detected in a complicated radiation image by processing the image signal representing it in various ways. The image signal is made up of a series of image signal components, and with appropriate processing the image signal components corresponding to a particular image pattern can be found. For example, from a very complicated radiation image, such as an X-ray image of the chest of a human body, which includes various linear and circular patterns, an approximately circular image corresponding to a tumor, or the like, can be detected. After a pattern, for example, a tumor image, is detected in a complicated radiation image, such as an X-ray image of the chest of a human body, a visible image is reproduced and displayed such that the detected pattern can be viewed clearly. Such a visible image can serve as an effective tool in, particularly, the efficient and accurate diagnosis of an illness. U.S. Patent No. 4,769,850 discloses a method for finding a circular pattern, wherein an image signal representing an X-ray image of the chest of a human body, or the like, is processed with a spatial-domain filter composed of three concentric circles. However, radiation images of human bodies have very complicated configurations. For example, the sizes of tumor images in X-ray images of chests are multifarious. Also, the shapes of some tumor images are not circular, but may be, for example, approximately elliptic. With the method for finding a circular pattern, wherein a spatial-domain filter composed of three concentric circles is utilized, tumor images cannot be detected accurately in cases where several tumor images having different sizes are present together or in cases where the shape of a tumor image is not circular. After an image pattern is detected and a visible image showing the detected image pattern is reproduced in, for example, a radiation image recording and reproducing system designed to facilitate medical diagnoses, a physician will base his diagnosis primarily on how the detected pattern looks. If a certain pattern (a certain tumor image) is not detected accurately, a physician may fail to find a tumor. This is a very serious problem. A method having the features of the preamble of claim 1 and an apparatus having the features of the preamble of claim 6 are known from EP-A-0225151 (belonging to the patent family of U.S. Patent No. 4,769,850). The primary object of the present invention is to provide a method and apparatus for determining whether a picture element is in a circular pattern even if several circular patterns having different sizes are present in a radiation image and even if the shapes of the circular patterns deviate slightly from circles, with the judgment being made accurately as to whether a predetermined picture element P0 in the radiation image falls or does not fall within the region corresponding to a particular circular pattern in the radiation image. Another object of the present invention is to provide a method and apparatus for classifying picture elements as belonging to or not belonging to a circular pattern wherein an accurate judgment is made as to whether a predetermined picture element P0 in a radiation image falls or does not fall within the region corresponding to a circular pattern in the radiation image, with the judgment being based on the shape of the circular pattern, instead of being based on the level of contrast of the circular pattern with the surrounding image areas. A further object of the present invention is to provide a method and apparatus for classifying picture elements wherein a circular pattern and a linear pattern, which may be present in a radiation image, can be accurately discriminated from each other with a single filter, and a judgment can be made accurately as to whether a predetermined picture element P0 in the radiation image falls or does not fall within the region corresponding to a circular pattern in the radiation image. A still further object of the present invention is to provide a method and apparatus for classifying picture elements wherein the adverse effects from noise in a radiation image are eliminated, and the contour of a predetermined pattern in the radiation image, which pattern is to be found, can be detected accurately. These objects are achieved by a method and apparatus having the features of claims 1 or claim 6. In the method and apparatus for classifying picture elements as belonging or not belonging to a circular pattern in accordance with the present invention, the number of lines Li, where i=1, 2, ..., n, i.e. the value of n, is not limited to a specific value, but may take any value which will satisfy the level of accuracy required of the judgment, which will allow the operations to be completed within a specified time, or the like. Also, the number of predetermined distances rij, where j=1, 2, ..., m, i.e. the value of m, is not limited to a specific value. The term "representative value" as used herein for the method and apparatus for classifying picture elements in accordance with the present invention means a value which is suitable for expressing the presence or absence or amount of the differences Δij between the value of the image signal component f0 representing the predetermined picture element P0 and the values of the image signal components fij representing the picture elements Pij, which are located on each of a plurality of lines Li extending from the predetermined picture element P0 to peripheral parts of the radiation image, and which are spaced a plurality of predetermined distances rij from the predetermined picture element P0. By way of example, in cases where, typically, the circular pattern has the characteristic that the value of the image signal component corresponding to the center positions of the circular pattern is smaller than the values of the image signal components corresponding to the peripheral portions of the circular pattern, the maximum value of the differences Δij may be employed as the representative value. In cases where the circular pattern has the characteristic that the value of the image signal component corresponding to the center position of the circular pattern is larger than the values of the image signal components corresponding to the peripheral portions of the circular pattern, the minimum value of the differences Δij may be employed as the representative value. However, in cases where the maximum value of the differences Δij is employed as the representative value, if, for example, all of the differences Δij between the value of the image signal component f0 representing the predetermined picture element P0 and the values of the image signal components fij representing the picture elements Pij, which are located on a certain line Lk among a plurality of the lines Li extending from the predetermined picture element P0 to peripheral parts of the radiation image, and which are spaced a plurality of predetermined distances rij from the predetermined picture element P0, are negative, no effective maximum value of the differences Δij can be found for the line Lk. In such cases, a maximum value of the differences Δij may be found from some extra simple calculations and then employed as the representative value. Alternatively, for example, a value of 0.0 may be employed as the representative value. Accordingly, the term "representative value" as used herein for the method and apparatus for classifying picture elements in accordance with the present invention can also mean a value employed in lieu of a representative value in cases where a representative value is obtained, which does not effectively represent the differences between the value of the image signal component f0 representing the picture element P0 located at the center position of a circular pattern and the values of the image signal components fij representing the picture elements Pij located at peripheral portions of the circular pattern. The term "representative value" as used herein for the method and apparatus for classifying picture elements in accordance with the present invention further means a value which substantially represents the maximum value or the minimum value of the differences Δij, for example, a value calculated from a formula expressed as (maximum value)-(predetermined value) or (minimum value)+(predetermined value). In the method and apparatus for classifying picture elements in accordance with the present invention, the differences are calculated from a formula expressed as Δij=fij-f0 . Such embodiments are substantially identical with embodiments wherein the differences are calculated from a formula expressed as Δij'=f0-fij , except that the maximum values and the minimum values of the differences are reversed . The method and apparatus for classifying picture elements in accordance with the present invention are meant to embrace within their scopes embodiments which are substantially identical. The term "mean-level value" as used herein for the method and apparatus for classifying picture elements as belonging to or not belonging to a circular pattern in accordance with the present invention means a value which is suitable for expressing the presence or absence or amount of the differences between the value of the image signal component f0 representing the picture element P0 located at the center position of the circular pattern and the two representative values found for each set of two lines, which extend from the picture element P0 in approximately opposite directions. By way of example, the mean-level value may be the arithmetical mean or the geometric mean of the two representative values. Alternatively, the two representative values may be weighted, and the mean value of the weighted representative values may be employed as the mean-level value. With the method and apparatus for classifying picture elements in accordance with the present invention, the differences, Δij=fij-f0 , are found between the value of an image signal component f0 representing a predetermined picture element P0 and the values of the image signal components fij representing the picture elements Pij. The picture elements Pij are located on each of a plurality of lines Li, where i=1, 2, ..., n, extending from the predetermined picture element P0 to peripheral parts of the radiation image, and are spaced a plurality of predetermined distances rij, where j=1, 2, ..., m, from the predetermined picture element P0. Thereafter, a representative value, which is representative of the differences Δij, is found for each of the lines Li. Therefore, even when circular patterns having different sizes are present in a radiation image and even when the shapes of the circular patterns deviate slightly from circles, for example, are elliptic, a judgment can be made accurately as to whether the predetermined picture element P0 falls or does not fall within the region corresponding to a circular pattern. Also, with the method and apparatus for classifying picture elements in accordance with the present invention, a representative value, which is representative of the differences Δij, is found for each of the lines Li, and a calculation is made to find a mean-level value of two representative values for each set of two lines which extend from the predetermined picture element P0 in approximately opposite directions. Thereafter, from the mean-level values, which have been calculated for a plurality of the sets of lines, a judgment is made as to whether the predetermined picture element P0 falls or does not fall within the region corresponding to the circular pattern. Accordingly, even when the circular pattern is present in a region of a radiation image where the background image density changes sharply, for example, even when a tumor image is present in the vicinity of a rib image in an X-ray image of the chest of a human body, a judgment can be made accurately as to whether the predetermined picture element P0 falls or does not fall within the region corresponding to the circular pattern. With the method and apparatus for classifying picture elements in accordance with the present invention, a judgment is made as to whether a predetermined picture element P0 in a radiation image falls or does not fall within the region corresponding to a circular pattern. If the judgment operation is repeated for all the image signal components representing the radiation image, i.e. if each of the image signal components is processed with the filter in accordance with the present invention, it is possible to detect the circular pattern in the radiation image. BRIEF DESCRIPTION OF THE DRAWINGS Figure 1 shows imaginary lines drawn around a predetermined picture element P0 in an X-ray image as an aid in explaining how a spatial-domain filter works, which spatial-domain filter is employed to detect a circular tumor image in embodiments of the first method and apparatus for classifying picture elements in accordance with the present invention, Figure 2 is a graph showing an example of a profile of the X-ray image around a predetermined picture element P0 in the direction (x direction) along which the lines L1 and L5 shown in Figure 1 extend, Figure 3 is a graph showing how a characteristic value is determined which is used during a judgment as to whether a predetermined picture element P0 falls or does not fall within the region corresponding to the tumor image, Figure 4 is a schematic view showing an example of an X-ray image recording apparatus, Figure 5 is a perspective view showing an example of an X-ray image read-out apparatus and a computer system which is provided with the embodiment of the apparatus for classifying picture elements in accordance with the present invention, Figure 6 is a schematic view showing an example of an X-ray image recording apparatus, DESCRIPTION OF THE PREFERRED EMBODIMENTS The present invention will hereinbelow be described in further detail with reference to the accompanying drawings. Embodiments of the method and apparatus for classifying picture elements as belonging to or not belonging to a circular pattern in accordance with the present invention will be described below. In the embodiments, an X-ray image is stored on a stimulable phosphor sheet, and an image of a tumor, which typically has an approximately spherical shape in the lungs of a human body, is detected from the X-ray image. In a visible image reproduced from the X-ray image, the tumor image typically appears as an approximately circular pattern having a lower density than the areas of the image surrounding the tumor image. Figure 4 is a schematic view showing an example of an X-ray image recording apparatus. With reference to Figure 4, X-rays 12 are produced by an X-ray source 11 of an X-ray image recording apparatus and irradiated to the chest 13a of a human body 13. X-rays 12a, which have passed through the human body 13, impinge upon a stimulable phosphor sheet 14. In this manner, an X-ray image of the chest 13a of a human body 13 is stored on the stimulable phosphor sheet 14. Figure 5 is a perspective view showing an example of an X-ray image read-out apparatus and a computer system which is provided with the embodiment of the apparatus for classifying picture elements in accordance with the present invention. With reference to Figure 5, a stimulable phosphor sheet 14, on which an X-ray image has been stored, is placed at a predetermined position in an X-ray image read-out apparatus 20. The stimulable phosphor sheet 14 is then conveyed in a sub-scanning direction indicated by the arrow Y by a sheet conveyance means 22, which is constituted of an endless belt or the like and which is operated by a motor 21. A laser beam 24, which serves as stimulating rays, is produced by a laser beam source 23, and is reflected and deflected by a rotating polygon mirror 26 which is quickly rotated by a motor 25 in the direction indicated by the arrow. The laser beam 24 then passes through a converging lens 27 constituted of an f lens or the like. The direction of the optical path of the laser beam 24 is then changed by a mirror 28, and the laser beam 24 impinges upon the stimulable phosphor sheet 14 and scans it in a main scanning direction indicated by the arrow X, which direction is approximately normal to the sub-scanning direction indicated by the arrow Y. When the stimulable phosphor sheet 14 is exposed to the laser beam 24, the exposed portion of the stimulable phosphor sheet 14 emits light 29 in an amount proportional to the amount of energy stored thereon during its exposure to the X-rays. The emitted light 29 is guided by a light guide member 30 and photoelectrically detected by a photomultiplier 31. The light guide member 30 is made from a light guiding material such as an acrylic plate and has a linear light input face 30a, positioned so that it extends along the main scanning line on the stimulable phosphor sheet 14, and a ring-shaped light output face 30b, positioned so that it is in close contact with a light receiving face of the photomultiplier 31. The emitted light 29, which has entered the light guide member 30 at its light input face 30a, is guided through repeated total reflection inside of the light guide member 30, emanates from the light output face 30b, and is received by the photomultiplier 31. In this manner, the amount of the emitted light 29, which amount represents the X-ray image, is converted into an electric signal by the photomultiplier 31. An analog output signal S0 generated by the photomultiplier 31 is logarithmically amplified by a logarithmic amplifier 32, and digitized by an A/D converter 33 into an electric image signal S1. The image signal S1 is then fed into a computer system 40. The computer system 40 is provided with an embodiment of the apparatus for classifying picture elements as belonging to or not belonging to a circular pattern in accordance with the present invention. The computer system 70 comprises a main body 41 in which a CPU and an internal memory are incorporated, a disk drive unit 42 which operates a floppy disk serving as a subsidiary memory, a keyboard 43 from which necessary instructions, or the like, are fed into the computer system 40, and a CRT display device 44 which displays necessary information. From the image signal S1, which is made up of a series of image signal components representing the X-ray image and which has been fed into the computer system 40, a judgment is made as to whether a predetermined picture element P0 in the X-ray image falls or does not fall within the region corresponding to a tumor image (circular pattern) in the X-ray image. Each of the picture elements in an X-ray image may be assigned as the predetermined picture element P0, and the judgment operation may be repeated for the image signal components representing each of the picture elements of the X-ray image. In this manner, the tumor image in the X-ray image can be detected. Figure 1 shows imaginary lines drawn around a predetermined picture element P0 in an X-ray image as an aid in explaining how a spatial-domain filter works, which spatial-domain filter is employed to detect a circular tumor image in the embodiments of the method and apparatus for classifying picture elements as belonging to or not belonging to a circular pattern in accordance with the present invention. Judgment is made as to whether a predetermined picture element P0 in the X-ray image falls or does not fall within the region corresponding to the tumor image in the X-ray image. The tumor image in the X-ray image can be detected by processing the image signal components representing the picture elements of the X-ray image with the filter illustrated in Figure 1. Figure 2 is a graph showing an example of a profile of the X-ray image around a predetermined picture element P0 in the direction (x direction) along which the lines L1 and L5 shown in Figure 1 extend. In this example, the predetermined picture element P0 is located approximately at the middle of a tumor image 7, which is close to a rib image 6. Typically, the profile of a tumor image (i.e. the distribution of the values of the image signal components representing the tumor image) is approximately symmetric bilaterally. However, in cases where, for example, the tumor image 7 is close to a rib image 6 as in the illustrated example, it often occurs that the profile of the tumor image 7 is not symmetric bilaterally. It is important that the tumor image 7 can be detected even in such cases. In Figure 2, the broken line 8 represents an example of the profile of an X-ray image including no tumor image. As shown in Figure 1, a plurality of (in this case, eight) imaginary lines Li, where i=1, 2, ..., 8, extend from the predetermined picture element P0 in the X-ray image to peripheral parts of the X-ray image. Also, imaginary circles Rj, where j=1, 2, 3, having radii r1, r2, and r3 extend around the predetermined picture element P0. The image signal component f0 representing the predetermined picture element P0 is found. Also, the image signal components fij are found which represent the picture elements Pij located at the intersections of each of the lines Li and the circles Rj. (In Figure 1, P11, P12, and P13 denote picture elements located at the intersections of a line L1 and circles R1, R2, and R3. Also, P51, P52, and P53 denote the picture elements located at the intersections of a line L5 and the circles R1, R2, and R3.) Thereafter, differences Δij between the value of the image signal component f0 representing the predetermined picture element P0 and the values of the image signal components fij representing the picture elements Pij are calculated from Formula (3), which is expressed as Δij = fij - f0 (i = 1,2,....,8; j = 1,2,3) For each of the lines Li, the maximum value of the differences Δij, which have been calculated from Formula (3), is then found. Specifically, for the line L1, the maximum value of the differences between the value of the image signal component f0 representing the predetermined picture element P0 and the values of the image signal components f11, f12, and f13 representing the picture elements P11, P12, and P13 is found. The differences can be expressed as Δ11 = f11 - f0 Δ12 = f12 - f0 Δ13 = f13 - f0 In this example, as illustrated in Figure 2, Δ13<Δ12<Δ11<0, and therefore the difference Δ11 is found to be the maximum value. In this embodiment, typically, a circular pattern is detected which has the characteristic that the value of the image signal component corresponding to the center position of the circular pattern is smaller than the values of the image signal components corresponding to the peripheral portions of the circular pattern. However, for the line L1, the differences Δ13, Δ12, and Δ11 are negative. Therefore, the maximum value Δ11 which was found for the line L1 is not one which would be effective in the method and apparatus for classifying picture elements in accordance with the present invention. Accordingly, in this case, a value of 0.0 is taken as the representative value, which is representative of the differences Δ11, Δ12, and Δ13, for the line L1. Alternatively, a maximum value, which is not negative and which has been found from the aforesaid differences, may directly be employed as the representative value. For the line L5, the maximum value of the differences between the value of the image signal component f0 representing the predetermined picture element P0 and the values of the image signal components f51, f52, and f53 representing the picture elements P51, P52, and P53 is also found. The differences are expressed as Δ51 = f51 - f0 Δ52 = f52 - f0 Δ53 = f53 - f0 In this example, the difference Δ53 is found to be the maximum value and is employed as the representative value, which is representative of the differences Δ51, Δ52, and Δ53, for the line L5. In the manner described above, for each of the lines Li, the differences Δij between the value of the image signal component f0 representing the predetermined picture element P0 and the values of the image signal components fij representing the picture elements Pij are calculated, and the maximum value of the differences is found. In cases where the maximum value of the differences thus found is an effective one, the maximum value is taken as the representative value with respect to the corresponding line. In cases where the maximum value of the differences thus found is not an effective one, a value of 0.0 is taken as the representative value with respect to the corresponding line. Thereafter, calculations are made to find the mean-level value, for example, the mean value, of two representative values, which have been found for each set of two lines extending from the predetermined picture element P0 in opposite directions. Specifically, mean values M15, M26, M37, and M48 are calculated respectively for the set of lines L1 and L5, the set of lines L2 and L6, the set of lines L3 and L7, and the set of lines L4 and L8. For the set of lines L1 and L5, the mean value M15 is given by the formula As described above, two lines extending from the predetermined picture element P0 in opposite directions are grouped into a single set. Therefore, a tumor image can be detected accurately even when, as shown in Figure 2, it is present in the vicinity of, for example, a rib image and the distribution of the values of the image signal components representing the tumor image is asymmetric. From the mean values M15, M26, M37, and M48, which have been calculated in the manner described above, a judgment is made as to whether the predetermined picture element P0 falls or does not fall within the region corresponding to the tumor image. In the method and apparatus for classifying picture elements in accordance with the present invention, no limitation is imposed on how the judgment is made from the mean values M15, M26, M37, and M48. By way of example, the judgment may be made in the manner described below. Figure 3 is a graph showing how a characteristic value C1 is determined which is used during the judgment as to whether the predetermined picture element P0 falls or does not fall within the region corresponding to the tumor image. In Figure 3, the horizontal axis represents the mean values M15, M26, M37, and M48, which have been calculated in the manner described above. The vertical axis represents rating values C15, C26, C37, and C48, which correspond respectively to the mean values M15, M26, M37, and M48. A rating value of zero is assigned to the mean values M15, M26, M37, and M48 in cases where they are smaller than a certain value M1. A rating value of 1.0 is assigned to the mean values M15, M26, M37, and M48 in cases where they are larger than a certain value M2. In cases where the mean values M15, M26, M37, and M48 fall within the range of M1 to M2, a rating value falling within the range of 0.0 to 1.0 is assigned to the mean values M15, M26, M37, and M48, depending upon their values. In this manner, the rating values C15, C26, C37, and C48 are found, which correspond respectively to the mean values M15, M26, M37, and M48. The sum of the rating values C15, C26, C37, and C48, which is expressed as C1 = C15 + C26 + C37 + C48 is taken as the characteristic value C1. The characteristic value C1 will fall within the range of a minimum value 0.0 to a maximum value 4.0. The characteristic value C1 is then compared with a predetermined threshold value Th1. From whether C1≧Th1 or C1<Th1, the judgment is made as to whether the predetermined picture element P0 falls or does not fall within the region corresponding to the tumor image. In cases where the rating values C15, C26, C37, and C48 are calculated from an equation such as the one represented by the single-dot chained line in Figure 3, wherein saturation is reached at a small mean value, e.g. M2', the characteristic value C1 calculated from Formula (5) will take a larger value in cases where the shape of the tumor image is closer to a circle. In cases where the rating values C15, C26, C37, and C48 are calculated from an equation such as the one represented by the double-dot chained line in Figure 3, wherein saturation is reached at a large mean value, e.g. M2'', the characteristic value C1 calculated from Formula (5) will take a larger value in cases where the contrast of the tumor image with respect to the surrounding image regions is higher. Therefore, an appropriate equation for transforming the mean values into the rating values can be selected in accordance with the characteristics of the tumor image which is to be found. The process of making the judgment from the mean values M15, M26, M37, and M48 is not limited to using the characteristic value C1 and may be carried out in various other manners. For example, the mean values M15, M26, M37, and M48 may be compared with a threshold value Th2. In cases where all of the mean values M15, M26, M37, and M48 are larger than the threshold value Th2, it may be judged that the predetermined picture element P0 falls within the region corresponding to the tumor image. Alternatively, in cases where at least three of the mean values M15, M26, M37, and M48 are larger than the threshold value Th2, it may be judged that the predetermined picture element P0 falls within the region corresponding to the tumor image. As another alternative, the sum, M=M15+M26+M37+M48 , of the mean values M15, M26, M37, and M48 may be calculated and compared with a threshold value Th3. In cases where M≧Th3, it may be judged that the predetermined picture element P0 falls within the region corresponding to the tumor image. Figure 6 is a schematic view showing an example of an X-ray image recording apparatus. With reference to Figure 6, X-rays 12 are produced by an X-ray source 11 of an X-ray image recording apparatus and irradiated to the mamma 13a of a human body 13. X-rays 12a, which have passed through the human body 13, impinge upon a stimulable phosphor sheet 14. In this manner, an X-ray image of the mamma 13a is stored on the stimulable phosphor sheet 14. Thereafter, the X-ray image is read out in the same manner as that described above from the stimulable phosphor sheet 14 in the X-ray image read-out apparatus shown in Figure 5. The image signal S1 obtained from the image read-out operation is fed into the computer system 40. From the image signal S1, which is made up of a series of image signal components representing the X-ray image and which has been fed into the computer system 40, a judgment is made as to whether a predetermined picture element P0 in the X-ray image falls or does not fall within the region corresponding to a tumor image (circular pattern) in the X-ray image. Each picture element in the X-ray image may be assigned as the predetermined picture element P0, and the judgment operation may be repeated for each image signal component representing each picture element in the X-ray image. In this manner, the tumor image is detected in the X-ray image. In the embodiments of the method and apparatus for classifying picture elements in accordance with the present invention, which have been described above with reference to Figures 1 through 6, from an X-ray image of the chest or the mamma of a human body, which image has been stored on a stimulable phosphor sheet, a tumor image is detected which appears, typically, as a circular pattern on the X-ray image. However, the method and apparatus for classifying picture elements in accordance with the present invention is not limited to the detection of a tumor image nor to the processing of X-ray images of chests or mammae. Also, recording media other than stimulable phosphor sheets may be used. The method and apparatus for classifying picture elements in accordance with the present invention is applicable widely when, from an image signal representing a radiation image of an object, judgments are made as to whether predetermined picture elements in the radiation image fall or do not fall within the region corresponding to a circular pattern in the radiation image. In the method and apparatus for classifying picture elements in accordance with the present invention, the image signal representing a radiation image need not necessarily be processed with the filter described above. For example, an operator may manually designate a predetermined point in the radiation image and may judge whether the predetermined point falls or does not fall in the region corresponding to a predetermined pattern.

Claims: A method for classifying picture elements as belonging to or not belonging to an approximately circular pattern wherein, from an image signal made up of a series of image signal components (fij) representing a radiation image of an object, judgments are made as to whether predetermined picture elements (Po) in the radiation image fall or do not fall within the region corresponding to an approximately circular pattern in the radiation image, characterized by comprising the steps of: i) calculating the differences, Δij = fij-f0 , between the value of an image signal component f0 representing a predetermined picture element P0 and the values of image signal components fij representing the picture elements Pij, which are located on each of a plurality of lines Li, where i=1, 2, ..., n, extending from said predetermined picture element P0 to peripheral parts of said radiation image, and which are spaced a plurality of predetermined distances rij, where j=l, 2, ..., m , from said predetermined picture element P0, ii) finding a representative value, which is representative of said differences Δij, for each of said lines Li, said representative value substantially representing the maximum or the minimum value of said differences Δij, or alternatively an obvious extreme value if no extremum of the differences can be found for a particular line Li, iii) calculating a mean-level value (Mij) of two said representative values for each set of two said lines which extend from said predetermined picture element P0 in approximately opposite directions, and iv) comparing the mean-level values, which have been calculated for a plurality of said sets of lines, or a characteristic value (C1,M), which has been determined from said mean-level values, with a predetermined threshold value (Th1,Th2,Th3) and judging from this comparison whether said predetermined picture element P0 falls or does not fall within the region corresponding to said pattern. A method for classifying picture elements as defined in claim 1 wherein said radiation image of the object (13a) has been stored on a stimulable phosphor sheet (14). A method for classifying picture elements as defined in claim 2, wherein said image signal is obtained form a read-out operation wherein said stimulable phosphor sheet (14) is exposed to stimulating rays (24), which cause said stimulable phosphor sheet to emit light (29) in proportion to the amount of energy stored thereon during its exposure to radiation, and the emitted light is detected photoelectrically. A method for classifying picture elements as defined in claim 3, wherein said stimulating rays (24) are a laser beam. A method for classifying picture elements as defined in claim 1, wherein said radiation image of the object (13a) has been recorded on photographic film. An apparatus for classifying picture elements as belonging to or not belonging to an approximately circular pattern wherein , from an image signal made up of a series of image signal components (fij) representing a radiation image of an object, judgments are made as to whether predetermined picture elements (P0) in the radiation image fall or do not fall within the region corresponding to an approximately circular pattern in the radiation image, characterized by i) a difference calculating means (40) for calculating the differences, Δij=fij-f0 , between the value of an image signal component f0 representing a predetermined picture element P0 and the values of image signal components fij representing the picture elements Pij, which are located on each of a plurality of lines Li, where i=1, 2, ..., n, extending from said predetermined picture element P0 to peripheral parts of said radiation image, and which are spaced a plurality of predetermined distances nj, where j=1, 2, ..., m, from said predetermined picture element P0, ii) a representative value calculating means (40) for finding a representative value calculating means (40) for finding a representative value, which is representative of said differences Δij, for each of said lines Li, said representative value substantially representing the maximum or the minimum value of said differences Δij, or alternatively an obvious extreme value if no extremum of the differences can be found for a particular line Li, iii) a mean-level value calculating means (40) for calculating a mean-level value (Mij) of two said representative values for each set of two said lines which extend from said predetermined picture element P0 in approximately opposite directions, and iv) a judgment means for comparing the mean-level values, which have been calculated for a plurality of said sets of lines, or a characteristic value (C1,M), which has been determined from said mean-level values, with a predetermined threshold value (Th1,Th2,Th3) and judging from this comparison whether said predetermined picture element P0 falls or does not fall within the region corresponding to an approximately circular pattern. An apparatus for classifying picture elements as defined in claim 6, wherein said radiation image of the object (13a) has been stored on a stimulable phosphor sheet (14). An apparatus for classifying picture elements as defined in claim 7, wherein said image signal is obtained from a read-out operation wherein said stimulable phosphor sheet (14) is exposed to stimulating rays (24) which cause said stimulable phosphor sheet (14) to emit light (29) in proportion to the amount of energy stored thereon during its exposure to radiation, and the emitted light is detected photoelectrically. An apparatus for classifying picture elements as defined in claim 8, wherein said stimulating rays (24) are laser beam. An apparatus for classifying picture elements as defined in claim 6, wherein said radiation image of the object (13a) has been recorded on photographic film.

Inventors: HARA SHOJI, ITO WATARU, HARA, SHOJI, ITO, WATARU, HARA, SHOJI, C/O FUJI PHOTO FILM CO., LTD., ITO, WATARU, C/O FUJI PHOTO FILM CO., LTD.
Applicants: FUJI PHOTO FILM CO LTD, FUJI PHOTO FILM CO., LTD.
Application year: 1990
Main classification: G06T7
IPC codes: G06T7, G06K9