Patent Number: 048667447
Section: description

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT As shown in FIG. 4, X-ray beam 34 emitted from X-ray tube 30 has its opposite edges defined by upper and lower collimators 32 and 38, respectively, to provide a fan-shaped beam pattern having a somewhat small width in slice direction 1 as indicated by dash-dot lines. X-ray beam 34 is input to X-ray detector 40 where the intensity of the X-ray beam is converted to an electric signal. Between X-ray tube 30 and X-ray detector 40 a bed, not shown, is located which extends in slice direction 1 and on which patient 36 lies. X-ray tube 30 and X-ray detector 40 are each located opposite to the patient such that they are rotated around rotation axis 3 with the patient as a center, noting that the rotation axis through the patient is parallel to the slice direction. In X-ray detector 40, as shown in FIGS. 5 and 6, plate-like electrodes 42 are arranged, as an array of detection elements, in a parallel fashion, such that they are located in a direction substantially parallel to slice direction 1 and rotation axis 3. Electrodes 42 are disposed in closed housing 44 where, for example, an xenon gas is sealed. Upon the entry of an X-ray into an area between the adjacent electrodes, the xenon gas is ionized to yield xenon ions and electrons. The resultant ion current is detected by the electrodes where the incident X-ray is converted to an electric signal. Window 46 is provided on an X-ray entrance surface of detector 40 and is arcuately curved in fan-out direction 2 with the focus of X-ray tube 30 at its center. The detection signals of X-ray detector 40, after having been converted to a digital signal, are input to an image processing device, not shown, to reconstruct a tomographic image This reconstruction may be implemented by a known method. This method is disclosed, for example, in U.S. Pat. Nos. 4,206,359, 4,212,062 or 4,219,876. Scattering beam eliminating member 50 is comprised of plate-like grids 52 and X-ray transmission (penetrating) areas 54, each of which is located between the grids. Grids 52 are made of an X-ray absorbing metal, i.e., X-ray transmission inhibiting metal, such as lead, molybdenum or tungsten X-ray transmission areas 54, on the other hand, are made of an X-ray transmitting metal, such as aluminum. Scattering beam eliminating member 50 can be formed as follows: For example, lead and aluminum plates are stacked as a 20- to 30-layered structure and mutually bonded to provide a block. In order for the respective plates to be arcuately curved in the width direction with the focus of X-ray tube 30 at its center, the aforementioned block is bent such that the outer arcuate surface 56 is formed with the same curvature as that of window 46 of X-ray detector 40. Scattering beam eliminating member 50 is fixedly bonded to X-ray detector 40 with the outer arcuate surface face 56 placed in intimate contact with window 46 of X-ray detector 40. In this way, the X-ray exit surface (outer arcuate surface 56) of scattering beam eliminating member 50 is curved with substantially the same curvature as that of window 46 (X-ray entrance surface) of X-ray detector 40 and bonded to window 46 of X-ray detector 40 to provide an integral structure. As a result, no displacement due to, for example, oscillation, occurs at that bonded area, whereby it is possible to prevent a variation in sensitivity characteristics at the respective cell of X-ray detector 40, energy characteristics or channel characteristics such as linearity. Scattering beam eliminating member 50 is, for example, 2 to 3 mm in height in the X-ray irradiation direction, 20 to 30 mm in width in slice direction 1 and 600 to 1000 mm in length in fan-out direction 2. Grids 52 are 30 to 80 .mu.m each in thickness and arranged at a pitch of 100 to 200 .mu.m which is a thickness of the X-ray transmission area 54. The operation of the device so arranged will be described below. X-ray 34 from X-ray tube 30 is narrowed through upper collimator 32 to a predetermined width (slice width S) and irradiated onto patient 36. The direct component of the X-ray beam transmitted through patient 36 passes through X-ray transmission areas 54 between grids 52 into X-ray detector 40. However, a scattering beam portion (see scattering beam 26 in FIG. 3) produced in slice direction 1 of X-ray beam 34 at the location of patient 36 impinges onto grids 52 and is absorbed there, since the scattering beam portion is never parallel to grids 52, so that it cannot therefore enter into X-ray detector 40 through grids 52. For this reason, even if the slice width S of X-ray 34 is adequately narrowed the amount of scattering beam incident to X-ray detector 40 will not be increased. The tomographic image of patient 36 which has been reconstructed based on transmission X-ray information so detected by X-ray detector 40 is free from any influence from the scattering beam, thus adequately improving a spatial resolution. It is therefore possible to obtain an image very useful for medical diagnosis. In this embodiment, grids 52 are arranged in only slice direction 1, not in fan-out direction 2, the reason for which is as follows. In fan-out direction 2, the channel spacing of X-ray detector 40 is about 1 mm and, according to the current grid array technique, it is possible to insert about 50 plate-like grids for that spacing of 1 mm. If one of the plate-like grids is missing in any one of a plurality of channels of X-ray detector 40, then a variation of 1/50 (2%) in uniformity occurs among all the channels. In the so-called third generation X-ray CT apparatus, a interchannel uniformity of below 0.05 to 0.2% is required and thus a variation of 2% fails to satisfy the aforementioned requirement. The presence of such a defect necessarily produces an artifact on the image. In the slice direction, on the other hand, the beam width on the X-ray entrance surface of the X-ray detector for a slice width of 10 mm is about 20 mm within which about 1000 plate-like grids are arranged. In this case, a variation in the aforementioned uniformity corresponding to one plate-like grid is 0.1%, an allowable value range. A plurality of grids is adequately implementable only in the slice direction without impairing the interchannel uniformity. This offers an effective means for enhancing a spatial resolution on the image. Needless to say, this invention can also be applied to a solid-state X-ray detector, not to mention a gas detector. In an X-ray CT apparatus employing such a solid-state X-ray detector an array of scintillation elements are located in a fan-out direction and a collimator plate made of a material which permits no ready transmission of an X-ray is located between the respective scintillation elements. The X-ray penetrating the patient is converged by the collimator plates and incident to the scintillation elements. Upon the incidence of the X-ray to the scintillation element, light is induced and converted to an electric signal by a corresponding diode in an array of photodiodes. The scattering beam eliminating device of this invention can be intimately bonded to the X-ray entrance surface of the solid-state detector, whereby it is possible to eliminate the scattering beam.