the x - ray system 1 shown in fig1 consists of a schematic diagram of an x - ray tube 2 , an anti - scatter grid 3 and an image detector 4 arranged below the anti - scatter grid . on illumination of an object 5 , which is located between the x - ray tube 2 and the anti - scatter grid 3 , direct information - bearing primary radiation 6 passes through the object 5 to reach the detector 4 . a part of the radiation however is deflected by inhomogeneities , for example bones , in the object and thus becomes scattered radiation which disturbs the image . this is subsequently blocked off by the lead laminations of the anti - scatter grid 3 . in this way scattered radiation 7 which disturbs the image is prevented from reaching the detector 4 . with the x - ray system 1 the x - ray tube 2 is adjustable vertically so that different distances between the x - ray tube 2 and the detector 4 can be set . since the individual lead strips from which the anti - scatter grid is constructed are inclined at a slight angle , the anti - scatter grid 3 is only optimally aligned to the x - ray tube 2 at a specific focal length , which is 1500 mm in the exemplary embodiment shown . if the x - ray system is operated with a different distance between the x - ray tube 2 and the detector 4 so that it is defocused , shadowing occurs in the edge area with conventional image recording methods . fig2 shows a flowchart of the method in accordance with the invention . the method for correction of image faults is based on calculating the intensity reduction profile of the anti - scatter grid 3 . to this end different blank images are included in step 8 . to record a blank image there is no object between the x - ray tube 2 and the anti - scatter grid 3 . the blank images thus reflect the intensity reduction of the radiation by the anti - scatter grid 3 . for a specific distance between the x - ray tube 2 and the anti - scatter grid 3 or the detector 4 it is sufficient to record one blank image . the method however provides for a number of blank images to be produced at different focal lengths f and / or for different sideways deflections of the tube ( defocusing ) so that it is possible to correct all x - ray images , regardless of the relevant focal distance . the computation of the intensity reduction profile for the fixed focal distance f will be explained below . the digital image is available as a matrix with x columns and y rows of intensity values m ( ij ). the equation below sums the columns of the image matrix vertically and a one - dimensional vector is obtained which is smoothed by multiple lowpass filtering ( steps 9 , 10 ): in procedural step 11 the vector is scaled , so that all values lie between 0 and 1 . these values correspond to the percentage intensity reduction . it is assumed here that the intensity reduction is 0 % in the center and 100 % at the shielded edges . the intensity reduction profile is as follows : the scaling of the vector is shown in the flowchart of fig2 as procedural step 11 . the resulting intensity reduction profile is at its minimum in the vicinity of the center of the anti - scatter grid 3 , which can be determined in procedural step 13 by the following equation : in procedural step 14 the intensity reduction profile is divided up into a left - hand part and a right - hand part and a linear regression of both parts is computed , then the corresponding parameters of the two individual equations are averaged . in this way the intensity reduction profile can be expressed by a straight line equation . the equation of the profile line is : in this equation m is the gradient of the linear intensity reduction profile . with the boldingh formula the expected intensity reduction of the radiation can be calculated as a function of the distance f between the x - ray tube and the detector for a known decentering ( shift ) z for each point c : in fig1 the intensity reduction profile v ( x ) is shown below the detector 4 in qualitative terms . with r being a characteristic value of the anti - scatter grid , known as the shaft ratio which describes height to width of the paper strip . is a variable which allows the formula to be used on pixels instead of on “ millimeters ”. this value is the opposite value of the pixel density . with equation ( 6 ) and equation ( 3 ) the decentering in millimeters can be defined ( procedural step 15 ): z ( x m )= f ·( x m − xc )·| 1 − f / f o | ( 8 ) the main factor here is that it is of no significance how the shift is triggered . since the computation method starts from the actual intensity reduction method , both the influences of the heel effect and also the decentering of the x - ray tube 2 or other influences can be taken into account . after the variables x m and m have been determined the image can be corrected in procedural step 16 by multiplying each column by the correction factor : a description is given below of how the intensity reduction profile can be computed for any given distances between the x - ray tube and the detector . so that different focal distances f can be taken into account for image correction , a series of calibration images are recorded for different states f , then the required correction parameters are calculated . to calculate the decentering x m for any given focal distances f , a number of blank images are recorded with an anti - scatter grid and x m and z are determined . the images can be recorded with different radiation doses . it has been discovered that a linear relationship exists between the decentering and the distance f between the x - ray tube and the image detector . on the basis of the blank images for the calibration the decentering z ( f ) is determined for each blank image as well as subsequently the linear adaptation of the decentering defined over the distance f . with this linear adaptation the decentering x m can now be determined for any given distance f , i . e . between the calibration points . to enable the image to be corrected the gradient of the intensity reduction profile for given distances f must also be calculated . there are two possible options for calculating the profile gradient . the first variant is based on the boldingh formula and calibration is with reference to the measurement data . calibration consists of calculating the linear relationship with m d being the gradient of the measurement data . k is a calibration factor and specifies the relationship between the profile calculated from the measured data and the boldingh formula . in this case the peripheral condition that m d = 0 for f = f 0 should apply is to be taken into account . for any given distances f the intensity reduction profile is calculated by first determining the decentering . subsequently the intensity reduction is calculated using the boldingh formula and multiplied by k . this produces the intensity reduction profile for the relevant focal distance f . the radiological image is then corrected with equation ( 9 ). with the second variant the boldingh formula is not used , but the model is based entirely on the measured data . from the different calibration images the gradients for the right and left half m r and m l are calculated by a linear approximation separately for f & lt ; f 0 and f & gt ; f 0 . if the x - ray tube is at its optimum focus the peripheral condition m r ( f 0 )= m l ( f 0 )= 0 applies , meaning that no correction is necessary . for a given distance f the intensity reduction profile is determined by calculating the decentering . subsequently the gradient of the intensity reduction profile is calculated from the linear approximation of the calibration images . this produces the intensity reduction profile for this focal distance f . the radiological image can again be corrected with equation ( 9 ). fig3 a to 3 c show the measured and calculated intensity reduction profile for different distances between the x - ray tube and the detector . the horizontal axis corresponds to the x - axis shown in fig1 . the intensity reduction is entered on the vertical axis , and this can be between 0 and 1 . three curves are also shown in each of fig3 a to 3 c . curve a represents the smoothed profile ( ix ). curve b represents the intensity reduction according to the boldingh formula . curve c shows the intensity reduction calculated in accordance with the inventive method . in fig3 a the focal distance is f = 1500 mm . it can be seen that the differences are comparatively small between profile of curve a based on the measured values and the curves b and c . fig3 b represents the case in which the focal distance amounts to f = 1150 mm . it can be seen that curve c delivers a significantly better approximation of the intensity reduction than does the boldingh formula ( curve b ). the same applies to the focal distance f = 1000 mm shown in fig3 c . the differences between curves a and c only amount to a few percent . since the anti - scatter grids are currently constructed from lead strips and the intensity reduction is thus constant in one direction , the direction of the lead laminations , the one - dimensional correction in the direction of the columns is sufficient . the method can however usefully be expanded to two dimensions if another scanning method , for example a grid , requires this .
method for compensating for image faults in a digital image recording which has been created by an x - ray system consisting of a radiographic source , an anti - scatter grid and a digital x - ray detector such as an image amplifier or a solid - state image detector , said image faults resulting from decentering , defocusing or defects in the anti - scatter grid or by the heel effect and causing an intensity reduction of the primary radiation falling on the x - ray detector , characterized in that the actual reduction in intensity is measured through the anti - scatter grid and correction parameters are determined based on the measured values recorded which are then used to correct the x - ray image recording .