METHOD OF OBTAINING X-RAY CT IMAGE AND APPARATUS FOR UTILIZING THE SAME METHOD

Abstract: An X-ray CT diagnostic apparatus includes an unit (40B) for producing a scannogram of an object (24) under exami­ nation, an unit (44A) for designating a plurality of slice posi­ tions on the scannogram by utilizing a line/marker genera­ tor (46B), an unit (44C) for designating an interest region of the designated slice position in the scannogram, which is to be enlarged, by defining a center of the interest region by means of the line/marker generator (46B), and an unit (40D) for enlarging and reconstructing the interest region of the designated slice position in such a manner that a center of the enlarged and reconstructed interest region is concident with the center of the interest region which has been desig­ nated in the scannogram.

Description: This invention relates to a method of obtaining an X-ray computerized-tomographic image and an apparatus for utilizing the above method, in which a desirable region of interest within a tomographic image of an object is automatically enlarged and displayed at a correct position on the monitor screen. The conventional X-ray computerized-tomographic apparatus set forth in the preamble has a function of displaying a scanned X-ray shadow image hereafter referred to as scannogram and a tomographic image. That is, before data acquisition of the tomographic images of a diseased portion of the object under examination, the scannogram, which covers a wide region including that portion, is produced based upon the X-ray transmission detection signal. By observing the scannogram, positions for imaginary slices of the object, i.e., slice positions, for which the tomographic images are to be obtained are determined, and the tomographic images are obtained by reconstructing the other detection signal based upon the determined slice positions. Further, when reconstructed tomographic images of the slice positions are observed, there may arise a necessity of enlarging part of an image (which is referred to as an "interest region") for the purpose of diagnosis. In this case, enlarged images are obtained from the other projection data (detection signal), which has been acquired in advance, by determining a center of the interest region for each tomographic image. As previously described, in the conventional computerized-tomographic apparatus, when it is desirable to observe an enlarged tomographic image for the purpose of diagnosis, a center of the enlarged image of the interest region must be determined for each of the tomographic images, which is a cumbersome task. Further, the operation of obtaining the enlarged image of the interest region is also cumbersome. More particularly, first a scannogram is obtained, then slice positions are determined by observing the scannogram, and thereafter tomographic images are reconstructed. Subsequently a center of the tomographic image of the interest region which is to be enlarged is determined to obtain the enlarged image by observing the reconstructed tomographic images. Therefore, a long operation time is required until the enlarged image of the interest region is obtained from the projection data. Moreover, the patient must endure for this long examination time. Documents Siemens Druckschrift: Bedienungsanleitung "SOMATOM 2N", R 36-061.201.03.02.01, and Siemens Druckschrift: Bedienungsanleitung "SOMATOM 2/2N", R 36-061.203.12.01.01, disclose implicitly an apparatus similar to that as described in the precharacterizing part of claim 1 although they do not describe explicitly all the features defined in the precharacterizing parts of claims 1 and 4. It is an object to provide an X-ray CT diagnostic apparatus and method which may overcome the conventional drawbacks described above and may permit a display of the enlarged tomographic image of the interest region within the slice position of the object in such that the center of the enlarged interest region is always at the center of the display screen. To solve this object the present invention provides an apparatus and a method as defined in claims 1 and 4, respectively. According to the invention, the imaginary slice position to be scanned can be designated by displaying a line on a displayed scannogram, and the center of the interest region within the displayed scannogram can be designated by displaying a marker superimposed on the line on the scannogram, and further a size of enlarging the interest region can be determined by observing the scannogram. Thus, an enlarging and reconstruction operation can be done with respect to the desirable interest region. The enlarged and reconstructed tomographic image of the desirable interest region can be displayed with its center at the center of the display screen, so that it is possible to permit accurate tomographic image diagnosis. Further, the target tracking can be done directly on the scannogram, so that the time required for enlarging the CT images can be greatly reduced, thereby shortening the entire diagnostic time period. The above and other objects and features of the present invention may be best understood by reference to the specification and the accompanying drawings, in which: Fig. 1 is an illustration on an X-ray projection in a gantry; Fig. 2 is a side view of an object and the gantry shown in Fig. 1; Fig. 3 is a block diagram of an X-ray CT apparatus, except an X-ray radiation construction, according to one preferred embodiment; Fig. 4 is a block diagram of the main circuit construction of the apparatus shown in Fig. 3; Figs. 5A to 5D illustrate the entre operation of the enlarging and reconstructing as executed in the apparatus shown in Fig. 3; Fig. 6 shows a scannogram displayed on a picture monitor; Fig. 7 is a schematic diagram of the enlarging and reconstructing image operation; Fig. 8 is an illustration of the projection data with reference to the enlarging operation in Fig. 7; Fig. 9 is an illustration of the enlarged CT image with reference to the enlarging operation in Fig. 7; and Fig. 10 is another scannogram displayed on the TV monitor according to another preferred embodiment. Fig. 1 illustrates relative positions of main components which constitute an X-ray computerized-tomographic apparatus (referred to as an "X-ray CT apparatus") according to one preferred embodiment. Referring to the drawing, the X-ray CT apparatus 100 comprises a gantry 22, which includes an X-ray tube 14 and an X-ray detector 16, having a plurality of detector elements. The X-ray tube 14 and X-ray detector 16 face each other and can be rotated along a circle with the center thereof at a center 18A of a data acquisition region. The X-ray tube 14 can project fan-shaped X-ray beams 26 onto an object 24 under investigation, e.g., a patient, disposed on a couch 12 in the data acquisition region 18. The apparatus 100 can reconstruct a tomographic image of the object 14 at an interest region within the slice position by a tomographic image reconstruction device (will be described later), and display the tomographic image on a picture monitor, also described later. A detailed description of the gantry 22 and the relevant components will now be given with reference to Fig. 2. As shown in Fig. 2, the X-ray tube 14 and X-ray detector 16 of the gantry 22 face each other and are rotated along a circle with the center thereof at the center 18A of the data acquisition region 18, while the fan-shaped X-ray beams 26 are interruptedly projected from the X-ray tube 14 onto the object 24 under investigation, which is disposed in the data acquisition region 18 with the couch 12. The gantry 22 as a whole can be tilted with respect to the longitudinal axis of the object 24, and also can be rotated in a plane perpendicular to the longitudinal axis. Fig. 3 shows an entire system of the X-ray CT apparatus 100. A gantry drive device 32 controls the relative revolution movement between the X-ray tube 14 and the detector 16 provided in the gantry 22. An X-ray projection-control device 34 can receive a control signal from a system control and data processing device 40 and applies a predetermined voltage and current to the X-ray tube 14 at a predetermined time. The X-ray tube 14 is thus controlled to project the X-ray beams 26 toward the object 24. The couch 12 is slidable by a couch drive device 38 within the data acquisition region 18 of the gantry 22 in a direction parallel to the longitudinal axis of the object 24. The system control and data processing device 40 (which is hereinafter referred to merely as "processing device"), as shown in Fig. 4, is composed of a system control unit 40A, a scannogram producing unit 40B, a reconstruction unit 40C, and an enlarging and reconstruction unit 40D. The system control unit 40A controls the entire system of the X-ray CT apparatus 100 according to a control signal from an operation control device 44. It can also provide the control signal to the gantry drive device 32 and the couch drive device 38 to permit X-ray projection with respect to the imaginary slices, designated by a tomographic slice designation unit 44A in the control operation device 44. The scannogram producing unit 40B can produce a transmission image (a scannogram) of the object 24 based upon X-ray transmission data produced from the detector 16 by analogue-to-digital converting the detection signal (a first detection signal) when the X-ray projection is executed in such a manner that the X-ray tube 14 and the detector 16 are held at a fixed angular position with respect to the object 24 while interruptedly moving the object 24 disposed on the couch 12 in a direction parallel to the longitudinal axis of the object 24. The reconstruction circuit 40C reconstructs tomographic images of the designated imaginary slice according to projection data obtained from the detector 16 as a second detection signal, which detects the X-ray beams which are projected from the X-ray tube 14 revolving about the object 24 and transmitted therethrough. The enlarging and reconstruction unit 40D can reconstruct and enlarge a particular area (= an interest region) of an imaginary slice according to the projection data as the second detection signal, which has been designated by an interest-region designating unit 44B and an enlarged size designating unit 44C in the control operation device 44. A memory device 42 can store a first data signal which is derived from the first detection signal for the scannogram of the object and a second data signal which is derived from the second detection signal for the tomographic image, and also first and second image data signals for the scannogram and the tomographic images obtained by the scannogram producing unit 40B, the reconstruction unit 40C and the enlarging and reconstruction unit 40D. The operation control device 44 has a keyboard for inputting an operation start command and X-ray projection conditions, and it includes the tomographic slice designating unit 44A, the interest region designating unit 44B, and the enlarged size designating unit 44C. The projection conditions involve the slice positions, the position of the interest region and the enlarged size of the interest region. The tomographic slice designating unit 44A serves to superimpose the lines S₁~S n on a scannogram displayed on the screen of the picture monitor 46A of the image display device 46. Those lines are generated by a line/marker generator 46B under the control of this unit 44A. Also, the designating unit 44A provides co-ordinate data for designating a tomographic slice. This data is necessary for driving the couch drive device 38, gantry drive device 32 and X-ray protection control device 34 through the system control unit 40A. The interest-region designating unit 44B provides co-ordinate data for setting the center of the interest region by displaying a marker P₁~P n on the given line displayed on the screen (the scannogram) of the picture monitor 46A. The marker is also generated by the line/marker generator 48 under the control of this unit 44B. The enlarged size designating unit 44C determines the enlarged size of the interest region in the designated tomographic slice. The tomographic-slice designating unit 44A and interestregion designating unit 44B may be constructed with a track ball, for instance. The image display unit 46 includes the picture monitor 46A and the above-described line/marker generator 46B. The picture monitor 46A displays scannograms and tomographic images selectively. The line/marker generator 46B produces luminance signals for displaying the lines S₁~S n and markers P₁~P n on the picture monitor 46A from the co-ordinate data received from the tomographic slice designating unit 44A and interest region designating unit 44B. The operation of the X-ray CT apparatus 100 shown in Fig. 4 will now be described with reference to Fig. 5. First, a scannogram is produced and displayed as shown in a step 1 in the left column (operation flow) of the flow chart of Figs. 5A through 5D. More specifically, referring to Figs. 1 to 4, the fan-shaped X-ray beams 26 are projected from the X-ray tube 14 mounted in the gantry 22 onto the object 24, i.e., patient lying on the couch 12, by intermittently moving the object 24 in the data acquisition region 18 in the horizontal direction (=the longitudinal axis of the object 24) in Fig. 2, while the X-ray tube 14 and the detector 16 are held fixed at a predetermined position with respect to the object 24. A transmitted X-ray detection signal from the detector 16 is first supplied to the memory device 42 as a first (projection) data signal, and then supplied to the scannogram producing unit 40B in the system control and data processing device 40. The scannogram producing unit 40B produces a scannogram from the first data signal. This first data signal is again supplied to the memory device 42 to be stored in a file 2 therein. At the same time, the unit 40B supplies it to the image display device 46 to display the scannogram of the object 24 on the picture monitor 46A, as shown in the center column (hardware) of Figs. 5A and 5B. More specifically, setting the position of the X-ray tube 14 and setting the couch 12 relative to the X-ray tube 14 are executed according to scannogram production software, as shown in the right column of Fig. 5A and hardware in the center column thereof. More particularly, the X-ray projection control device 34 and couch drive device 38 are controlled by reading out the position data stored in the file 1 of the memory device 42 according to the software (see Fig. 5A). Then, the scannogram data signal (first detection signal) is obtained from the X-ray detector 16 by projecting the fan-shaped X-ray beams 26 from the X-ray tube 14 onto the object 24 several times (e.g., 320 times) while holding the X-ray tube 14 and the detector 16 at a fixed position and transporting the object 24 in the direction parallel to the longitudinal axis of the object 24. That is, the first detection signal is A/D converted into a corresponding detection signal in a digital form, which is then processed into the scannogram data signal. The resultant data signal is stored in the file 2 of the memory device 42. Then, based upon the scannogram data stored in the file 2, the scannogram of the object 24 is displayed on the picture monitor 46A according to the scannogram display software, as shown in the center column of Fig. 5B. Subsequently, slice positions for tomographic images and the center of region of interest are set in a step 2. More specifically, the operator manipulates the operation control device 44 while watching the scannogram to supply co-ordinate data Xi, Yi (i=1 ~ n) from the tomographic slice designating unit 44A to the line/marker generator 46B. Thus, line S₁, S₂, ..., S n designating the slice positions for tomographic images, as shown in an enlarged scale in Fig. 6, are displayed on the picture monitor 46A according to the luminance signals provided from the line/marker generator 46B. The co-ordinate data Xi, Yi is also supplied to the system control unit 40A. The system control unit 40A calculates data necessary for the X-ray projection on the designated slice positions, such as the scanning intervals m₁, m₂, ..., m n , the driving timing of the couch 12, and the drive timing and tilt angles ϑ₁, ϑ₂,..., ϑ n of the gantry 22, according to the input co-ordinate data. The operator also uses the operation control device 44 while watching the scannogram to supply co-ordinate data from the interest region designating unit 44B to the line/marker generator 46B. Thus, the markers P₁, P₂, ..., P n for designating the centers of the interest regions are superimposed on the lines S₁, S₂, ..., S n which have been displayed on the picture monitor 46A according to a luminance signal provided from the line/marker generator 46B as shown in Fig. 6. More specifically, in the step 2, the scan positions (corresponding to co-ordinate data Xi) are determined by the line/marker generator 46B while the lines S₁, S₂, ..., S n are displayed on the scannogram. Also, the number of CT images necessary for data acquisition, their scanning positions, and scanning intervals m₁, m₂, ..., m n are stored in the file 3 of the memory device 42. Then the centers of interest regions are determined on the scannogram on the picture monitor 46A while the markers are displayed as P₁, P₂, ..., P n on the scannogram by means of the line/marker generator 46B. In this embodiment, a series of the operation of determining the slice positions S₁, S₂, ..., S n and then determining the centers of the interest regions P₁, P₂, ..., P n is referred to as "target tracking". The sequence of operations of such target tracking is referred to as a scan plan (the right column of Figs. 5A and 5B). It is one of the features according to the invention that the target tracking can be executed directly on the scannogram. Subsequently, the step 3 of deciding to enlarge the size of the designated interest region is executed. More specifically, in the step 3, the operator manipulates the control operation device 44 to supply data to enlarge the size of the interest region of the tomographic slice, which is stored in a file 5 of the memory device 42, from the enlarged-size designating unit 44C to the enlarging and reconstructing unit 40D. By the above operation, the tomographic position, center of interest region and enlarged size are determined as shown in Fig. 5C. The couch 12 is interruptedly moved by the couch drive device 38 in a direction parallel to the longitudinal axis of the object 24 by a control signal, provided from the system control unit 40A in the system control and data processing device 40 according to the scanning hardware in the right column in Fig. 5C. The couch movement is carried out in such that a plane involving a tomographic slice of the object 24, designated by the line S₁ (corresponding to the first slice position) is coincident with the plane of rotation of the X-ray tube 14. Then the gantry 22 is rotated around the object 24 by the gantry drive device 32, and the X-ray protection control device 34 causes the X-ray tube 14 to project the X-ray beams 26 intermittently onto the object 24 while rotating the gantry 22. This X-ray projection is done for the purpose of the known CT image acquisition. The projection data or scanning data derived from the detector 16 every time the X-ray projection is converted by the A/D converter, to be described later, into a digital value, which is transferred to the enlarging and reconstruction unit 40D. When the X-ray projection on that first tomographic slice position of the object 24 specified by the line S₁ is completed, the couch 12 is moved by a given distance, and the succeeding X-ray projection is done on a second tomographic slice position of the object 24, specified by the line S₂. Then, further X-ray projection is done on a third tomographic slice position specified by the line S₃. This sequential projection operation is carried out up to the last slice position specified by the line S n . All projection data obtained for the individual slice positions (S₁, S₂, ..., S n ) are dealt with in the enlarging and reconstruction unit 40D for enlarging and reconstruction, which will be described later in detail. The image data that is obtained in the above enlarging and reconstruction unit 40D is stored in a file 7 of the memory device 42. Thereafter, a last step 6 is executed (see Fig. 5D). In this step, the enlarged and reconstructed image data is read out from the file 7 and supplied to the picture monitor 46A. In this way, the enlarged CT images of the first to the last interest regions designated by the lines S₁ to S n are successively displayed on the picture monitor 46A. Now, the enlarging and reconstruction operation of the step 5 just desired will be described in more detail. Fig. 7 shows a basic construction of the enlarging and reconstruction operation which is substantially the same as that shown in Fig. 1, and like components are not furthermore described. The fan-shaped X-ray beams 26, projected from the X-ray tube 14, is transmitted through the object 24 to be incident on the X-ray detector 16. In this embodiment, the detector 16 has 512 channels, and therefore 512 detection signals (= the first detection signal) are supplied from 512 channels of the detector 16 to an A/D converter 50. In other words, in the acquisition of projection data for producing X-ray CT images as well as the scannogram, 512 pieces of projection data signals (i.e., the first or second detection signal) are obtained in one projection. As is known, in the production of the scannogram (step 1), the X-ray tube 14 and detector 16 are set at fixed positions relative to the object 24, and X-ray projection is done, for example, 250 times, at a predetermined transfer pitch of the couch 12 in a direction parallel to the longitudinal axis of the object 24. That is, 250 pieces of projection data signal (= the first data signal) are acquired for obtaining one scannogram. In contrast with this, in the CT image data acquisition, the projection data signal ( = the second data signal) is obtained by rotating the X-ray tube 14 and detector 16 by 360° about the object 24 in a relative revolution movement between them. In this embodiment, the tilt angle of the gantry 22 is set to 0°, the revolution pitch angle is to 0.6°, and the X-ray beams 26 is projected 600 (i.e., 360°÷0.6°=600) times onto the first slice position S₁. In other words, in this embodiment, to obtain one CT image for one slice position, (307,200) detection signals (= the second detection signal) are obtained from the 512-channel detector 16 by effecting the X-ray projection 600 times (512x600=307,200). One set of projection data signal is constituted by 512 detection signals as schematically shown in Fig. 8. The A/D converted projection signal ( = the second detection signal) in a digital form is subsequently dealt with in the enlarging and reconstruction unit 40D as previously described in conjunction with the step 5. The enlarged and reconstructed image data is stored in the file 7 of the memory device 42. Thereafter, enlarged CT images are displayed in turn on the picture monitor 46A as described in connection with the step 6. The enlarging will now be described in more detail. In the step 2, a center of enlarging is determined for each interest region of the slice positions S₁, S₂, ..., S n while observing the scannogram, that is, the above-described target tracking is executed, and the data thus obtained is stored in the file 4 of the memory device 42. The center of enlarging position varies for each projection with representing a sine wave (see Fig. 8). As previously described in detail, according to the invention the center of the enlarged interest region can be determined by executing the target tracking directly in the scannogram, not the CT images. The projection data obtained in the step 4 is enlarged and reconstructed in the step 5 based upon the target tracking data stored in the file 4 and enlarged size data obtained in the step 3. Fig. 9 schematically illustrates the enlarging system of the interest region of the object according to the invention. While the invention has been described in terms of certain preferred embodiments and exemplified with respect thereto, those skilled in the art will readily appreciate that various modifications, changes, omissions and substitutions may be made without departing from the scope of the invention. For example, in the above embodiment, setting of the interest region with respect to the backbone has been done using solely the side scannogram of the object. Where the backbone position changes three-dimensionally, the centers of the enlarging in the interest regions P₁, P₁′, P₂, P₂′, can be determined more accurately in the following way. As shown in Fig. 10, a top scannogram 58, of the object 24 obtained by the first X-ray projection from the X-ray tube 14 which is set right above the object 24, and a side scannogram 60 thereof, obtained by the second X-ray projection from the X-ray tube 14 set on one side of the object 24, are simultaneously displayed on the picture monitor 46A. The center of the interest region is specified by displaying two markers P and P′ on each of the lines S₁, S₂,... which are common to both top and side scannograms 58 and 60. With the centers of the interest region designated by displaying two markers, the enlarged and reconstructed image for the interest region can be displayed more accurately.

Claims: 1. An apparatus (100) for obtaining a scanned X-ray shadow image and an X-ray computerized tomographic image of a given imaginary slice of an object (24), comprising: a couch (12) for supporting the object (24) under examination; couch drive means (38) for controlling an intermittent transportation of the couch (12) along a longidutinal axis of the object (24); a source (14) for emitting a fan-shaped X-ray beam; means (34) for controlling projection of the fan-shaped X-ray beam toward the imaginary slice of the object (24) through the X-ray source (14); means (16) for detecting the X-rays which have penetrated through the imaginary slice of the object (24) so as to produce selectively first and second detection signals; a gantry (22) for mounting the X-ray source (14) and the detection means (16) in such a manner that the X-ray source (14) is positioned opposite the detection means (16) with respect to the imaginary slice of the object (24) and for performing a revolution movement of the X-ray source (14) and the detection means (16) about the object (24) in a plane perpendicular to the longitudinal axis of the object (24) and parallel to the imaginary slice of the object (24); system control means (40A) for performing control of the couch drive means (38), the gantry (22) and the projection control means (34) in such a manner that a first scanning mode for obtaining a scanned X-ray shadow image of the object (24) is effected by the intermittent transportation of the couch (12) while the X-ray source (14) and the detection means (16) remain at a given fixed position, and a second scanning mode for obtaining a computerized tomographic image of the imaginary slice of the object (24) is effected by stopping the transportation of the couch (12) in combination with the revolution movement of the X-ray source (14) and the detection means (16) in said plane; operation control means (44) for designating an imaginary slice of the object (24) in the scanned X-ray shadow image and a center of an interest region in the imaginary slice which is to be enlarged; memory means (42) for storing a first data signal which is derived from the first detection signal for the scanned X-ray shadow image of the object (24), and a second data signal which is derived from the second detection signal for the computerized tomographic image of the object (24); data processing means (40B, 40C, 40D) for processing the first data signal which is read out from the memory means (42) so as to produce the scanned X-ray shadow image of the object (24) in case of the first scanning mode and for processing the second data signal which is read out from the memory means (42) so as to reconstruct and enlarge the interest region of the imaginary slice of the object (24) which has been designated by the operation control means (44), whereby the center of the enlarged computerized tomographic image of the interest region is coincident with the center of the interest region in the imaginary slice of the object (24); and monitor means (46) for displaying the scanned X-ray shadow image of the object (24) and the enlarged computerized tomographic image of the interest region selectively, characterized in that: the center of the interest region is freely determined on the scannogram on said monitor means (46) while markers (P₁, P₂, ...) are displayed on the scannogram by means of a line marker generator (46B). 2. An apparatus (100) as claimed in claim 1, wherein the operation control means (44) includes: a tomographic slice designating unit (44A) for performing the designation of the imaginary slice of the object (24) in such a manner that a line (S₁, S₂, ..., S n ) generated from the line/marker generator (46B) is superimposed on the scanned X-ray shadow image displayed on the monitor means (46), an interest region designating unit (44B) for performing the designation of the center of the interest region of the imaginary slice in the scanned X-ray shadow image in such a manner that a marker (P₁, P₁′, P₂, P₂′, ..., P n ) generated from the line/marker generator (46B) is superimposed on the center of the interest region which is to be enlarged, and an enlarged size designating unit (44C) for performing the designation of a size of the interest region which is to be enlarged in conjunction with the designation of the center of the interest region by the interest region designating unit (44B); and the data processing means includes: a scanned X-ray shadow image producing unit (40B) for processing the first detection signal, which is derived from the detection means (16) during the first scanning mode, so as to produce the scanned X-ray shadow image of the object (24), and an enlarging/reconstruction unit (40D) for processing the second detection signal, which is derived from the detection means during the second scanning mode, so as to reconstruct and also enlarge the interest region of the imaginary slice which has been designated by the line (S₁, S₂, ..., S n ) and marker (P₁, P₁′, P₂, P₂′, ...; P n ) on the scanned X-ray shadow image. 3. An apparatus (100) as claimed in claim 2, wherein the data processing means further includes: a reconstruction unit (40C) for processing the second data signal which is derived from the second detection signal obtained during the second scanning mode so as to produce a computerized tomographic image of the imaginary slice of the object (24) which has been designated by the tomographic slice designating unti (44A) of the operation control means (44), whereby a computerized tomographic image of the designated imaginary slice of the object (24) is dislayed on the monitro means (46). 4. A method for obtaining a scanned X-ray shadow image and an X-ray computerized tomographic image of a given imaginary slice of an object (24), comprising steps of: controlling an intermittent transportation of a couch (12) supporting the object (24) under examination along a longitudinal axis of the object (24); controlling projection of a fan-shaped X-ray beam emitted by an X-ray source toward the imaginary slice of the object (24) through the X-ray source (14) by couch drive means (38); detecting the X-rays which have penetrated through the imaginary slice of the object (24) by detection means (16) so as to produce selectively first and second detection signals; mounting the X-ray source (14) and the detection means (16) by a gantry (22) in such a manner that the X-ray source (14) is positioned opposite the detection means (16) with respect to the imaginary slice of the object (24) and performing by said gantry (22) a revolution movement of the X-ray source (14) and the detection means (16) about the object (24) in a plane perpendicular to the longitudinal axis of the object (24) and parallel to the imaginary slice of the object (24); performing control of the couch drive means (38), the gantry (22), and the projection control means (34) in such a manner that a first scanning mode for obtaining a scanned X-ray shadow image of the object (24) is effected by the intermittent transportation of the couch (12) while the X-ray source (14) and the dectection means (16) remain at a given fixed position, and a second scanning mode for obtaining a computerized tomographic image of the imaginary slice of the object (24) is effected by stopping the transportation of the couch (12) in combination with the revolution movement of the X-ray source (14) and the detection means (16) in said plane; designating by operation control means (44) an imaginary slice of the object (24) in the scanned X-ray shadow image and a center of an interest region in the imaginary slice which is to be enlarged; storing a first data signal which is derived from the first detection signal for the scanned X-ray shadow image of the object (24), and a second data signal which is derived from the second detection signal for the computerized tomographic image of the object (24) in a memory means, respectively, processing the first data signal which is read out from the memory means (42) so as to produce the scanned X-ray shadow image of the object (24) in case of the first scanning mode and for processing the second data signal which is read out from the memory means (42) so as to reconstruct and enlarge the interest region of the imaginary slice of the object (24) which has been designated by the operation control means (44), whereby the center of the enlarged computerized tomographic image of the interest region is coincident with the center of the interest region in the imaginary slice of the object (24); and displaying on monitor means (46) the scanned X-ray shadow image of the object (24) and the enlarged computerized tomographic image of the interest region selectively, characterized in that said processing and displaying steps include: freely determining the center of the interest region on the scannogram on said monitor means (46) while displaying markers (P₁, P₂, ...) on the scannogram by means of a line marker generator (46B). 5. A method according to claim 4, further including the step of reconstructing the second data signal which is read out from the memory means (42) so as to produce a tomographic image of the imaginary slice of the object (24) which has been designated in the scanned X-ray shadow image.

Inventors: MURANUSHI, JUN
Applicants: KABUSHIKI KAISHA TOSHIBA
Application year: 1984
Main classification: A61B6
IPC codes: G01N23, A61B6