Abstract:
An object ( 14 ) is positioned on an object support ( 16 ). A radiation source ( 10 ) projects a beam of radiation through a region of interest ( 12 ) of the object. A plurality of focal planes (F 1 , F 2 , . . . , F n ) mark the center of selected slice images through the region of interest. A gantry ( 20 ) rotates the radiation source ( 10 ) around a circular trajectory ( 22 ) as an encoder ( 26 ) monitors a radius (r) of the trajectory and an angular position (φ) of the radiation source ( 10 ) around the trajectory ( 22 ). A look-up table ( 40 ) is addressed with the selected focal plane(s) (F 1 , F 2 , . . . , F n ) and (r, φ) to generate a correction or shift value (S 1 , . . . , S n .) for each selected focal plane (F 1 , F 2 , . . . , F n ). A flat panel detector ( 18 ) is read out a plurality of times to generate a plurality of electronic data views as the radiation source rotates. Each view is corrected with a corresponding correction or shift value and integrated in a summation circuit ( 50 ) with preceding views to generate an image representation of the slice(s) through the selected focal plane(s) (F 1 , F 2 , . . . , F n ) or a 3D volume. The slice image or 3D volume image representation is converted into a human-readable display ( 56 ) substantially in real-time, e.g., each time a preselected number of views has been summed.

Description:
BACKGROUND OF THE INVENTION 
     The present invention relates to the diagnostic imaging arts. It finds particular application in conjunction with the real-time display of medical diagnostic images and will be described with particular reference thereto. However, it is to be appreciated that the invention may find application in conjunction with non-medical imaging, volumetric imaging, and the like. 
     Heretofore, x-rays have been projected through a patient onto a flat film box on the other side of the patient. X-ray film mounted in the film box was exposed with a projection of the radiation opacity of the tissue or other internal structure of an examined subject. Because all of the internal structure was projected into a common plane, such images were difficult to read. 
     Conventional x-ray tomo systems have a similar construction, but include structure for moving the x-ray tube and the film box counter-cyclically in planes parallel to the x-ray film. More specifically, a center ray of the x-ray beam was projected through the region of interest to the detector. The x-ray source and the detector were then moved such that the central ray pivots about a fixed point in the plane of interest. With this process, not only does the central ray pivot about the plane or slice of interest, the other rays from the x-ray source to the film box do as well. In this manner, the x-ray attenuation contribution to the final image from volumetric elements within the selected plane remains constant during the imaging procedure. However, outside of the selected slice, each of the rays pass through different surrounding tissue or structures as the source and detector move. In this manner, the contributions to the final image from structures outside of the plane of interest become blurred and averaged. With a sufficiently long exposure and motion through a relatively wide range, the out-of-slice structures can be reduced to background noise while the in-slice structures are displayed crisp and clear. Such systems required a significant time lag before the diagnostic image could be viewed. First, there was a delay while the x-ray source and the film box and the film box were moved back and forth to expose the film. This was followed by a further delay as the film was developed. 
     Real-time images were available from fluoroscopy systems. In a fluoroscopy system, the x-rays are projected through the patient onto an image intensifier, i.e., a fluorescent screen and electronics to make the resultant image brighter. A video camera was mounted to view the image generated by the image intensifier. The video camera was connected by a closed-circuit TV system with a monitor for viewing the fluoroscopic images. Although these images were real-time, they were again projection images which superimposed all the structure in the field-of-view onto a common plane. Moreover, image intensifiers were subject to non-uniform brightness across the field-of-view and significant image distortions. Fluoroscopic images typically had much less resolution than projection x-ray. 
     CT scanners have been utilized to generate images of internal structures quickly. However, CT scanners typically view the patient in slices which are orthogonal to those of the tomographic x-ray systems. That is, with the patient positioned prone on his back in the scanner, the tomographic x-ray systems generated an image of a horizontal slice. With the same orientation of the patient, CT scanners generate a vertical slice. Of course, CT scanners can be utilized to generate a large multiplicity of slices to define a volume from which a horizontal slice can be extracted. However, taking a large number of slices again introduces a time delay. Moreover, CT scanners are expensive and capable of performing only a limited number of diagnostic tasks. 
     The present invention contemplates a new and improved imaging technique which overcomes the above-referenced problems and others. 
     SUMMARY OF THE INVENTION 
     In accordance with the present invention, an apparatus for real-time diagnostic imaging of an object is provided. A support supports a region of interest of an object to be examined. A radiation source projects a beam of penetrating radiation through the region of interest. A movable gantry causes relative motion between the radiation source and the support. A radiation detector detects the beam of penetrating radiation and converted the detected radiation into electronic data. The radiation detector is repeatedly sampled as the radiation source moves to generate a plurality of electronic views. An image processing circuit processes the plurality of electronic views to generate an electronic image representation of a selected slice through the region of interest, which image representation is continuously updated as the radiation source moves. 
     In accordance with a more limited aspect of the invention, the moveable gantry rotates the radiation source in an annular trajectory of different radii so that different horizontal slice thicknesses of the object can be monitored in real-time and controlled in real-time by the user. 
     In accordance with a more limited aspect of the invention, the radius is controlled through a user input device which takes a selected thickness for a region of interest to be depicted in a slice image representation, converts the selected thickness into a corresponding radius value, and adjusts the radiation source to a radius corresponding to the selected radius value. 
     In accordance with a more limited aspect of the invention, a focal plane selection input device allows an operator to designate a focal plane corresponding to the selected slice, through use of a look-up table, to generate an appropriate section from the plurality of views for display. 
     A first advantage of the present invention is that it provides a new imaging modality for diagnostic imaging. 
     Another advantage of the present invention is that it provides a real-time display of slices taken longitudinally through a patient. 
     Other advantages of the present invention reside in the ready adjustability of the slice thickness and position. 
     The present system is amenable to imaging in other modes including tomographic, fluoroscopic, and projection x-ray modes. 
     Other advantages of the present invention reside in the ability to enhance and manipulate images easily. 
     Still further advantages of the present invention will become apparent to those of ordinary skill in the art upon reading and understanding the following detailed description of the preferred embodiments. 
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS 
     The invention may take form in various components and arrangements of components, and in various steps and arrangements of steps. The drawings are only for purposes of illustrating a preferred embodiment and are not to be construed as limiting the invention. 
     FIG. 1 is a diagrammatic illustration of an imaging system in accordance with the present invention; 
     FIG. 2 is a detailed view of an image processor of FIG. 1; 
     FIG. 3 is a diagrammatic illustration of the geometric principles responsible for structures in the focal plane contributing coherently to the resultant image while structures outside of the focal plane contribute non-coherently and blur; 
     FIG. 4 is a diagrammatic illustration illustrating x-ray tube placement and principles behind generating thin slices; and, 
     FIG. 5 is a diagrammatic illustration illustrating the geometry and principles behind thick slice image generation. 
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     With reference to FIG. 1, a radiation source  10 , such as an x-ray tube, projects a beam of x-rays or other penetrating radiation through a region of interest  12  of a subject  14 , such as a patient or an object in a manufacturing environment, supported on a support  16 . Radiation which has passed through the region of interest impinges upon a flat panel radiation detector  18 . In the preferred embodiment, the radiation detector is a grid of amorphous silicon elements on the order of a millimeter square, with the overall detector being on the order of 45 cm x 45 cm. Each element of the amorphous silicon detector integrates the intensity of received radiation over a sampling period and generates an electronic data value indicative of the intensity of received radiation. Typically, all of the elements are read out concurrently or in close temporal proximity to generate a view representative of x-ray intensity variation, which, in turn, is indicative of a projection of radiation opacity of the region of interest taken in the direction of the x-ray beam. 
     The radiation source  10  is mounted on a rotational gantry  20  which rotates the radiation source  10  in an annular, preferably circular, trajectory  22  of adjustable radius. For clarity of illustration, the gantry  20  is illustrated as a concave dish of constant radius relative to a center point of the detector  18 . It is to be appreciated that other, more complex mechanical arrangements can be provided for rotating the x-ray source  10  in a circular trajectory  22  of selectable radius along the surface of the dish. For example, the x-ray source  10  can be mounted to a dish segment supported by rollers or bearings with an adjustment drive (not shown) for adjusting the position of the radiation source  10  radially. Once the radius of the circular trajectory  22  is selected, another drive motor  24  rotates the x-ray source  10  around the selected trajectory. A position encoder  26  measures the radius r of the trajectory  22  and the angular position φ of the x-ray source  10  around the trajectory  22 . 
     With reference to FIG. 3, the region of interest  12  is divisible into a series of focal planes F 1 , F 2 , . . . , F n . With the x-ray source  10  starting at an arbitrary initial position (x 0 , y 0 , z 0 ) on the trajectory  22 , the image of incremental element  32  on a first focal plane F 1  is located at an initial position (X 0 , Y 0 , Z 0 ) on the detector plane, where the z-coordinate of the radiation detector has been arbitrarily selected as z 0 =0 for simplicity of calculation. As the x-ray source  10  moves around the trajectory  22  to other positions (X i , Y i , Z 0 ), the image of the incremental element  32  now impinges on a point (x i , y i , z 0 ) on the radiation detector  18 . In fact, the image of the incremental elements  32  traverses a complementary trajectory  22 ′ on the detector  18 . 
     It will be seen that for any point outside of the focal plane F 1 , such as a point  34  on focal plane F 2 , different rays will pass through element  34  and the trajectory of the projection of element  34  onto the detector  18  will follow a different trajectory from trajectory  22 ′. More specifically, by simple geometry, it can be seen that when the image read out on the detector  18  is translated or shifted such that the point on the trajectory  22 ′ that corresponds to the projection of element  32  are aligned, the images can be enhanced with elements  32  adding coherently. More specifically, all of the points on plane F 1  will integrate substantially coherently such that incremental elements of the region of interest lying in plane F 1  are integrated coherently and will be strong and clear in the resultant image. On the other hand, the projection of point  34  and other incremental elements of the region of interest that are off the focal plane F 1  will sometimes contribute to one pixel of the integrated image and sometimes to others, thus blurring and becoming de-emphasized. With sufficient variation, the out of plane contribution to the image can be reduced to background noise. For any radius r of the circle, and any angular position φ along the circular trajectory  22 , the trajectory  22 ′ can be precalculated. In this manner, for any given position (r, φ) of the x-ray source around the trajectory  22 , the offset (x 0 −x i , y 0 −y i , z o −z i ) can be determined geometrically and stored. It is further to be appreciated that the same principle holds true for elements on focal plane F 2  and the other focal planes through F n . 
     With reference again to FIG. 1, as the motor  24  rotates the radiation source  10  along the trajectory  22 , the encoder  26  monitors the radius r of the trajectory and the angular position φ of the radiation source  10  around it. The coordinates (r, φ) are used to address a look-up table  40  which stores the offset or shift S i =(x 0 −x i , y 0 −y i , z o −z i ). The look-up table  40  is also addressed with the location of the focal plane to be imaged as input by an operator on a slice or focal plane selection input device  42 . 
     With reference to FIG. 2, and continuing reference to FIG. 1, each time a view is read out of the detector  18 , it passes to a view memory or buffer  44 . An image translation or shift circuit  46  shifts and interpolates the resultant image by the amount S to create a shifted view which is stored in a shifted view memory or buffer  48 . Although buffers  44  and  48  are shown separately for simplicity of illustration, it is to be appreciated that they may be the same element of hardware as may other memories described hereinbelow. 
     Each shifted image is integrated in summation circuit  50  with precedingly taken images and stored in a first slice memory  52 . In the preferred embodiment, the first slice memory  52  is used to accumulate the sum of the views taken over 180° of rotation about the trajectory  22 . Once 180° of views are integrated, the first slice memory  52  is interconnected with a video processor  54  which converts the slice image representation from the memory  52  into appropriate format for display on a video monitor  56 . While the first slice is being displayed, the x-ray source  10  is rotating through the next 180° and another image is being built in a second slice memory  58 . Once the next 180° slice is completed, the second slice  58  memory is connected with the video processor  54  and the first slice memory  52  is erased and commences building the next view of the slice. 
     Preferably, the x-ray source  10  is rotated at 15 rotations per second such that there is a frame rate of  30  images of the slice generated per second to match a standard video image frame rate. Of course, other frame rates may be selected such as 4-8 images per second. In that case, the x-ray source  10  is rotated at 2-4 rotations per second. Analogously, images may be built based on shorter arc segments such as 120°. As another option, the image may be built in a single memory with the oldest view being subtracted back out as the newest view is added in. As yet another alternative, the views can be continuously accumulated in the slice image memory with no deletions, possibly with the accumulated image and the new view being weighted that more recent views have greater prominence than older views. 
     The angular position of the x-ray source  10  is monitored by a frame rate controller  60  which changes the position of a switch  62  after each 180° or other selected distance along the trajectory  22 . The switch  62  switches which of the memories  52 ,  58  is connected with the video processor  54  and which is receiving the additional views from the summation circuit  50 . 
     As another alternative, a plurality of planes or slices can be reconstructed. For simultaneous reconstruction of multiple planes, the look-up table  40  is addressed with each of the focal planes selected with the slice selection control  42 . The appropriate displacements for each of the focal planes S 1 , S 2 , . . . , S n  are outputted to a respective image shifting circuit  46   2 , . . . ,  46   n . The shifted views are conveyed to shifted view memories or buffers  48   2 , . . . ,  48   n . The shifted views are summed  50   2 , . . . ,  50   n . into the accumulating image in buffer  52   2 , . . . ,  52   n. or  58   2 , . . . ,  58   n . The switch circuits  62   2 , . . . ,  62   n  convey the most recently completed slice images to a volumetric image memory  64 . The volumetric image memory  64  then conveys the completed slice images through a digital enhancer  66  after the video processor  54  accesses the volumetric image memory  64  to retrieve operator selected slices, an oblique slice, volume renderings, volume images, or the like. 
     With continuing reference to FIGS. 1 and 2, there are shown a plurality of image processing systems  68   1 ,  68   2 , . . . ,  68   n . The image processing systems  68   1 ,  68   2 , . . . ,  68   n  receive inputs from the view memory  44  and Look-Up-Table  40 , which are sent to the image transition/shift circuit  46 , and they receive inputs the frame rate controller  60  which is sent to the switch  62 . The image processing systems  68   1 ,  68   2 , . . . ,  68   n  then outputs the volume image generated to the volume image memory  64 . 
     With references to FIGS. 4-5, the operator can select a desired slice thickness with a slice thickness selection input device  70 . The selected slice thickness is used as an input into a thickness/radius look-up table  72 . Based on the selected slice, the look-up table  72  retrieves the corresponding trajectory radius r. A radius adjustment driver  74  moves the radial position of the radiation source  10  inward or outward in accordance with the selected slice thickness and adjusts the direction of a collimator  76  such that a central ray of the radiation beam is aligned with the center of the detector  18 . 
     As illustrated in FIG. 4, when the radius of the trajectory  22  is relatively large, the radiation beam crosses the point  32  on the selected focal plane at a sharp angle. Due to the sharp angle, incremental elements only a relatively short distance off the focal plane are not held focused with the point  32  as the radiation source moves. In this manner, only data which spans a relatively narrow region to either side of the focal plane remains coherent, hence the resultant image is of a relatively thin slice. As illustrated in FIG. 5, when the radius of the trajectory  22  is very small, the central rays intersect at point  32  at very close angles. When the central ray oscillates about a very narrow range, structures that lie over a more significant distance to either side of the focal plane remain coherently focused on the detector as the radiation source  10  rotates. Hence, the resultant image represents a relatively thick slice. The exact thickness of the slice versus the radius is a relatively straightforward geometric calculation based on the size of the detector elements, the displacement between the detector and the focal plane, the distance between the focal plane and the radiation source, and the radius of the trajectory  22 . 
     Although the radiation source  10  is below the subject  14  in the preferred embodiment, for mechanical simplicity it is contemplated that the radiation source  10  may be disposed above the patient  14  with the detector  18  disposed below or built into the patient support  16 . 
     Although the trajectory  22  is defined along a spherical surface segment, for mathematical simplicity in operating on the resultant data, it is to be appreciated that the trajectories of various sizes could be defined on a flat surface or other surface. Also for mathematical simplicity, each view is subject to the same shift vector S. In some circumstances, it may be advantageous to shift different portions of each view differently. Such differential shifting may reduce edge distortion, may be used to generate oblique plane views, and the like. 
     It is also to be appreciated that the slice images built in slice image memories  52  and  54  are digital images which can be enhanced using any of a variety of image enhancement techniques. Such techniques include edge enhancement, smoothing, background noise suppression, and the like. 
     The invention has been described with reference to the preferred embodiments. Obviously, modifications and alterations will occur to others upon reading and understanding the preceding detailed description. It is intended that the invention be construed as including all such modifications and alterations insofar as they come within the scope of the appended claims or the equivalents thereof.