the basic steps of the inventive method are schematically illustrated in fig1 . at the right of fig1 , the steps relating solely to the patient examination are shown , and at the left of fig1 the steps relating to the evaluation of a single topogram are shown . the patient examination begins with the generation of a single topogram , and the single topogram is then read out and evaluated as raw data . the maximum attenuation is determined from the topogram raw data and the patient extension orthogonal to the projection direction is determined by evaluation of threshold values . the tube current ( ma ) and modulation per revolution are determined from the maximum attenuation and the patient extension , plus additional information relating to the patient examination , as needed . scan parameters are then determined at least as a result of the topogram evaluation , but also possibly by manually entering other scan parameters . the scan is then conducted . the following quantities can be directly determined from a single topogram : for a . p . topogram maximum attenuation in a . p . direction ( sa . p .) and geometrical expanse in lateral direction ( dlat ) for lateral topogram maximum attenuation in lateral direction ( slat .) and geometrical expanse in a . p . direction ( da . p .) the maximum attenuation was previously determined from the absolute maximum of the attenuation of a projection . the procedure causes unusable results given subjects with highly attenuating details ( metals ). in order to be able to blank out such strong local attenuations , for example due to metallic implants , nails , screws and clips , a sliding averaging over a number of channels is implemented before the determination of the maximum attenuation in each projection . the use of 64 channels (= 2 6 ) is suitable . this corresponds to a geometrical expanse of approximately 42 mm in the rotational center . the expanse of the patient perpendicular to the transirradiation direction is estimated from the corresponding attenuation profile . a simple determination of the outside contour leads to results that are in part misleading , for example a . p . topograms in the thigh region . all channels whose attenuation value lies above a defined threshold therefore are determined . air and bed regions as well as regions with very little attenuation are blanked out by means of this threshold . the missing , second attenuation value , s a . p . ( given an a . p . topogram ) or , respectively , s lat . ( given a lateral topogram ) is calculated with the following equation via the subject expanse identified in this way and an assumed , average attenuation coefficient { overscore ( μ )}: the minimum of the controlled tube current in % is calculated with the “ root equation ”: i min = s a . p s lat · 100 ⁢ % when the attenuation maximum is greater in the a . p . direction than in the lateral direction , then i min & gt ; 100 % applies . this means that scanning is carried out with the maximum tube current at 90 ° and 270 °. pronounced discontinuities in the boost between two table positions are adequately reduced or eliminated by weighted averaging over three or , respectively , five values . the flowchart shown in fig2 provides an overview of the calculation of the control curve with the data from an a . p . topogram . ten topograms of patients ( head , shoulder , lung , abdomen , pelvis ) were evaluated with the method shown in fig2 . insofar as possible , he results of the evaluation were compared to the actual attenuation values from spiral or sequence scans of the corresponding table positions . the average attenuation coefficient { overscore ( μ )} for calculating the attenuation s from the geometrical expanse is highly dependent on the organ examined . it fluctuates between approximately 0 . 15 cm − 1 for lung and 0 . 23 cm − 1 for slices with a relatively high proportion of bone ( shoulder , head ). despite an organ - specifically adapted average attenuation coefficient , the minimum tube current calculated from the topogram deviates on average by ± 10 - 30 % from the optimum parameters that were determined from spiral and sequence data ( see fig3 ). it could be partly observed that the maximum of the tube current was shifted by 90 °, which would lead to a deterioration of the image quality ( see fig3 ). fig3 shows , first , the control curve calculated from the a . p . topogram and , second the control curve that was acquired from the spiral data . when the two curves are compared , it is clear that the switch between the individual body sections ( lung → abdomen ) is not recognized given a nearly constant width of the patient . a deviation in the boost of & gt ; 20 % as well as an incorrect position of the maximum tube current are the consequences . an a . p . and a lateral topogram were available for calculating this control curve / these control curves . in the determination of the control curve , the two topograms were separately analyzed with the algorithm described in point 2 . the control curve calculated with the attenuation maximums determined from both topograms served as comparison or , respectively , reference curve . when the tendencies of the individual curves are viewed in fig4 , then the curve calculated from the a . p . topogram has a course similar to the reference curve , but with an average deviation of approximately 10 - 15 %. the control curve that was calculated from the lateral topogram , in contrast , exhibits a totally different course . in part , the dose power maximum for this curve is also shifted by 90 ° ( tube current & gt ; 100 %). the information acquired from the topogram only serve as a default for the tube load computer and the first scan in a sequence or , respectively , the first revolution in the spiral . for all further scans or , respectively , revolutions , the a . p . and lat . attenuation values from the most recent 180 ° or 360 ° revolution are used for calculating the minimum tube current for the next revolution and , thus , the sinusoidal control curve is parameterized anew . by prescribing the minimum tube current for only the first scan ( for example , as parameter in the mode table tfo ), the transfer of the values for all other table positions can also be omitted . thus , an addition of a further table for the attenuation conditions for each table position can be omitted in the host software or , respectively , firmware . an attenuation coefficient is no longer required for the further determination . scanning for “ additional scans ” that lie outside the region that was covered by the topogram can also be done here with dose regulation . gantry lilting and the administration of contrast agent are recognized . an unusual patient geometry as well as patient positioning , however , can only be compensated by a true regulation . fig5 shows examples of control curves that are obtained in accordance with the inventive method . as can be seen in comparison to the control curves shown in fig3 and 4 , the precision of the control is significantly improved . although modifications and changes may be suggested by those skilled in the art , it is the intention of the inventors to embody within the patent warranted hereon all changes and modifications as reasonably and properly come within the scope of their contribution to the art .
in a method for controlling the modulation of the tube current of an x - ray tube in the production of images using computed tomography , a single topogram of the examination subject is obtained and an orthogonal attenuation value is calculated therefrom , also making use of geometrical information associated with the position of the table on which the examination subject is disposed . in a subsequently - obtained computed tomography scan , the tube current is controlled using the orthogonal patient attenuation .