System for correcting extension rate of images

Abstract: Positions of marker images included in two images obtained by a digital radiography system are detected by a marker position detecting section (10). The marker image intervals in each image are calculated by an extension rate correcting section (11) in accordance with the detected positions of the marker images. Reducing/extension for one image is performed in accordance with the extension rate of the image obtained by a ratio of the calculated marker image intervals, thereby coinciding extension rates of two images.

Description: The present invention relates to an X-ray diagnosis apparatus according to a one-shot method for taking X-ray images in use for an energy subtraction process according to the pre-characterzing part of claim 1. In the digital radiography system, there has been employed an energy subtraction process. In the process, two images formed by different energies are subtracted from each other, and the difference thus obtained is visually presented. Two methods, a one-shot method and a two-shot method, have been used for taking X-ray images in use for the energy subtraction process. In the two-shot method, an X-ray tube is set at a low voltage, and an object is irradiated with the X-rays emitted from the X-ray tube. Then, the X-ray tube is set at a high voltage, and the object is irradiated with the X-rays emitted from the X-ray tube. By the above process, two images by different energies are obtained. In the one-shot method, a pair of imaging plates (IPs) sandwiching an X-ray absorption material such as copper are used. The X-ray tube radiates one shot of X-rays to an object. Accordingly, as existence of the x-ray absorption material between the IPs causes a difference between the energies radiated to the IPs, two images by different energies are obtained. By the above two methods, an image of the soft part tissue except for the bone or an image of the bone except for the soft part tissue can be obtained. The larger the energy difference between two images is, the easier the subtraction process is. To perfectly separate the bone from the soft part tissue, therefore, the two-shot method is superior to the one-shot method. Apparatuses for switching the X-ray tube voltage at a high speed and moving the two IPs at a high speed to obtain two images, are necessary to the two-shot method. When an object respires, a motion of the object causes a position shift between two images. In the one-shot method, an energy difference between the two images is small. However, as the images are formed on the basis of one-shot radiation of X-rays, the position shift between the images does not occur. Further, switching apparatus and IP moving apparatus are not required. To apply the subtraction process to the two images, the image position fitting process is performed by moving and rotating one image with respect to the other image. In the two-shot method, a distance between the X-ray tube and the IP is constant for the two shot radiations. Accordingly, the two images are equal in size, or extension rate. Therefore, the images can be position-fit by the above fitting process. In the one-shot method, a distance between one IP and an object is different from that between the other IP and the object by the thickness of the X-ray absorption material. Accordingly, the extension rate or size of one image is different from that of the other image. For this reason, the images cannot be position-fit by only the above fitting process. If the subtraction process is applied to the images having different extension rates, a contour of the tissue, which is to be removed is left according to the extension rate, thereby reducing a resolution of the image. It is demanded that an apparatus capable of improving the resolution of the images by correcting a position shift in accordance with different extension rates of the images is provided. US-A-4 736 399 discloses an X-ray imaging apparatus in which the unavoidable spacial coordinate distortion of the picked up image obtained by emitting a fan-shaped X-ray beam towards a subject is corrected by obtaining data representative of the distortion amount, storing said data and correcting the coordinates of the pixels of the image using distorted data. The above-mentioned problem in the one-shot method using a pair of imaging plates sandwiching X-ray absorption material is not addressed by this prior art correcting process. EP-A-0 137 465 discloses an apparatus for reading out individiual X-ray images recorded on both surfaces of a radiographic film. So as to avoid distortions caused by the different distances of said two surfaces of the film from the X-ray source which emits a fan-shaped X-ray beam, an interpolation circuit is provided for obtaining substantial coincidence between the pixels of both images. In a specific embodiment there is provided a film holder having circular cross-section so as to avoid distortions caused by the fan-shaped beam. It is the object of the present invention to provide an apparatus according to said one-shot method in accordance with the pre-characterizing part of claim 1 (EP-A-0 137 465), in which both X-ray images have identical size, when they are subjected to the subtraction process. To this end, the present invention provides for an apparatus having the features of claim 1. This invention can be more fully understood from the following detailed description when taken in conjunction with the accompanying drawings, in which: Fig. 1 shows a scheme of a system for correcting extension rates of images according to an embodiment of the present invention; Figs. 2A and 2B are diagrams showing two images to be subjected to the subtraction process; Fig. 3 shows a diagram for explaining the position-fitting of two images by using marker images; Fig. 4 shows a diagram for explaining the difference of extension rates between two images formed by radiation of a fan beam; Fig. 5 shows a diagram for explaining a shift of the marker images by the difference of the extension rates between the two images; Fig. 6 shows an operation flowchart of an extension rate correcting section of the system of Fig. 1; Figs. 7 and 8 show diagrams for explaining the extension rate correcting process for two digitized images; and Fig. 9 shows a schematic illustration of another embodiment of the present invention. Preferred embodiments of the present invention will be described with reference to the accompanying drawings. In the present system according to one shot method, as shown in Fig. 1, an X-ray tube 1 emits a fan beam 2 toward a subject P. A cassette 4 contains IP1 and IP2. An X-ray absorption material 6, for example, a copper plate, is sandwiched between IP1 and IP2. Markers 5a and 5b are attached to the left upper corner and the right lower corner of the cassette 4. An IP scanner 3 reads X-ray information temporarily recorded in the IP1 and IP2. A marker position detecting section 10 detects positions of marker images A, B, a, and b formed at the corners of two images Il and I2, as shown in Figs. 2A and 2B. An extension rate correcting section 11 calculates marker image intervals by using the positions of the marker images A, B, a and b detected by the marker position detecting section 10, as described later. Further, the extension rate correcting section 11 calculates a ratio of the marker image intervals of the two images, to acquire an extension rate. The image is extended or reduced in accordance with the extension rate. A subtraction processing section 12 performs the subtraction process to the two images having extension rates corrected by the extension rate correcting section 11. The operation of the system for correcting extension rates of images will be described. The fan beam 2 generated in the X-ray tube 1 is radiated to the subject P. The IP1 and IP2 of the cassette 4 temporarily record X-ray information. Two images I1 and I2 having subject images 31 and 32, and marker images A, B, a and b are acquired by reading the X-ray information recorded in IP1 and IP2 by the IP scanner 3. The forms of the marker images are recognized by the marker position detecting section 10, thereby to detect the positions of the four marker images. As shown in Fig. 3, positions of the two images I1 and I2 are shifted against each other, and accordingly the positions of marker images A and B in the image I1 are fit to the positions of marker images a and b in the image I2. To fit positions of the images I1 and I2, the image I2 is moved and rotated. In the one-shot method, as the extension rates of the images I1 and I2 change depending on the thickness "t" of the X-ray absorption material 6, as shown in Fig. 4, the marker image interval AB is different from that ab ( AB < ab ). If the subtraction process is performed to the two images formed by the one-shot method, the marker images A and a, and B and b are shifted against each other, as shown in Fig. 5. Therefore, the subject images I1 and I2 are also shifted against each other. In the shift, the following relation equation is obtained. That is, AB /d = ab /(d + t) where d is the distance between the X-ray tube 1 and the IP1. When d = 1 m and t = 1 mm, ab / AB = 1.001. This indicates that the marker image interval AB is shorter by 0.1% than the interval ab . In the digital radiography system, as the interval AB consists of 2000 pixels, 0.1% corresponds to 2 pixels. Accordingly, the marker images A and a are shifted by 1 pixel. The images B and b are also shifted by 1 pixel. In the subtraction process by the subtraction processing section 12, the image I2 is moved and rotated, and the image I2 is reduced by AB / ab in the extension rate correcting section 11. The extension rate correcting process by the extension rate correcting section 11 will be described with reference to a flowchart of Fig. 6. In Fig. 7, note that the image I1 is fixed, and the image I2 is moved and rotated, and it is reduced in size. The images I1 and I2 are based on the digital image data, and coordinates of each image data are expressed by P(i, j) and Q(i, j) where i = X direction and j = Y direction. The marker image intervals AB and ab are calculated by using the position of the marker image A, B, a, and b in step S1 of Fig. 6. A ratio of the marker image interval AB / ab is obtained as an extension rate in step S2. In the step S3, the image I2 is moved in accordance with the detected positions of marker images, to fit the I2 to I1. In step S4, the coordinates Q(X0, Y0) corresponding to the coordinate P(0, 0) on the image I1 are set on the image I2. In step S5, the coordinates Q(Xi, Yi) on the image I2 are moved. The coordinates are calculated from the coordinates Q(X0, Y0) as a start point. As shown in Fig. 8, when the coordinates Q(Xi, yi) are moved by +1 in the X direction on the image I2, the amounts of change of the coordinates on the image I2 are ΔXx and ΔYx, and when the coordinates Q(Xi,Yi) are moved by +1 in the Y direction on the image I2, the amounts of change of the coordinates on the image I2 are ΔXy and ΔYy. In step S6, the coordinates Q(i, j) of the image I2, corresponding to the coordinates P(i, j) of the image I1, are obtained. The coordinates Q(Xi, Yi) of the image I2 is acquired by selecting four points of coordinates Q(n, m), Q(n+1, m), Q(n, m+1) and Q(n+1, m+1), which are located near the coordinates Q(Xi, Yi), and interpolating the image data of coordinates Q(Xi, Yi) using those coordinates. Here, n ≦ Xi ≦ n+1, m ≦ Yi ≦ m+1. Accordingly, the images I1 and I2 can be properly fit by correcting the extension rate of the image I2. Following the correction of the extension rates of the images by the extension rate correcting section 11, the subtraction process is further performed to the image data of P(i, j) and Q(i, j) by the subtraction processing section 12. The subtraction image does not include image data representing a contour of the tissue, which is to be removed, thereby improving resolution of the image. In the present embodiment, the extension rate of the two images is obtained by the calculation of the marker image intervals of the two images. The extension rate is multiplied to the image data of one of the images. The multiplied image corresponds to the extension or reduction image. In this way, the two images fit each other. Thus, a shift of the images due to the difference of the extension rates, can be corrected. The corrected image does not include image data representing the contour occurred by the shift. Further, by shortening of the distance between the X-ray tube and the IP1 and IP2, a required dosage of X-rays may be reduced, thereby obtaining the distinct image. X-ray absorption materials outside copper and tin can be used. While the present invention has been described in connection with the energy subtraction process, it is evident that the present invention may be embodied in connection with other process outside the subtraction process. The present invention can be applied to the multiple photography where three or more images of different extension rates are added/subtracted. For example, as shown in Fig. 9, a cassette containing IP1, IP2, and IP3 is used. The image data recorded in those IPs is read and added together. Accordingly, a high quality image enough to ensure a diagnosis is obtained by a low dosage of X-rays.

Claims: An X-ray diagnostic apparatus according to a one-shot method for taking X-ray images in use for an energy subtraction process, comprising: a) an X-ray source (1) for emitting a fan-shaped X-ray beam towards a subject (P); b) a cassette (4) including two imaging members (IP1, IP2) each for recording an X-ray image of the subject (P) and an X-ray absorption member (6) sandwiched between the imaging members (IP1, IP2); c) means (3) for reading the X-ray image from the imaging members (IP1, IP2); and d) subtraction means (12) for performing a subtraction process to the two X-ray images read by said reading means (3) characterized by e) at least two markers (5a, 5b) provided on a surface of the cassette (4) that faces the X-ray source (1) so that at least two marker images (A, B, a, b) are included in the X-ray images recorded by the imaging plates (IP1, IP2), the position of the marker images being different according to the distance between the two imaging members; f) means (10) for detecting the marker images from the X-ray images read by said reading means (3); g) means (11) for g1) correcting a positional relationship between the two X-ray images based on the positions of the marker images and g2) enlarging/reducing a size of an X-ray image based on the distance between the two marker images included in the same X-ray image, the corrected X-ray image being supplied to the subtraction means (12). An X-ray diagnostic apparatus according to claim 1, characterized in that said two markers (5a, 5b) are provided on the left upper corner and the right lower corner of the cassette (4). An X-ray diagnostic apparatus according to claim 1, characterized in that said absorption member 86) is a copper plate.

Inventors: YAMADA NAOKI, YAMADA, NAOKI, YAMADA, NAOKI C/O INTELLECTUAL PROPERTY DIVISION
Applicants: TOSHIBA KK, KABUSHIKI KAISHA TOSHIBA
Application year: 1989
Main classification: G06T5
IPC codes: G06T5, H05G1, G03B42, A61B6