the x - ray device 1 shown in diagram form in fig1 comprises an x - ray beam emitter 2 , a digital x - ray detector 3 and likewise a control system 4 . in the direction of the x - ray beam 5 , a collimator 6 and ( optionally ) a scattered - ray grid 7 are connected in series to the x - ray beam emitter 2 and the x - ray detector 3 . in this arrangement , the function of the collimator 6 is to cut out a part of a desired size of the beam of the x - ray radiation r produced by the x - ray beam emitter 2 , which passes through a person 8 who is to be examined or an object that is to be examined , and through the scattered - ray grid 7 , onto the x - ray detector 3 . in this arrangement , the function of the scattered - ray grid 7 is to cut out lateral scatter , which would distort the x - ray image that is incident on the x - ray detector 3 . the x - ray beam emitter 2 and the x - ray detector 3 are adjustably fixed to a support 9 or adjustably fixed above or below an examination table . the control system 4 comprises a power unit 10 to actuate the x - ray beam emitter 2 and / or the x - ray detector 3 and also to produce a tube current that is supplied to the x - ray beam emitter 2 to create the x - ray radiation r . the power unit 10 is connected by data and power lines 11 to the x - ray beam emitter 2 . the control system 4 further comprises a data processing device 13 . the data processing device 13 comprises routines for the control and operation of the x - ray device 1 and also routines for the evaluation of the image data b taken by the x - ray detector 3 . the data processing device 13 is connected by data and system bus lines 14 to the power unit 10 and the x - ray detector 3 . for the input and output of data , it is further connected to peripheral devices , in particular to a screen 15 , to a keyboard 16 and to a mouse 17 . the x - ray detector 3 is in particular a digital x - ray detector , as is in fact known from m . spahn , et al ., “ flachbilddetektoren in der röntgendiagnostik ” ( flat screen detectors in x - ray diagnosis ), radiologe , 43 ( 2003 ), p . 340 - 350 . the control system 4 comprises a user interface 18 , which is shown in diagram form in fig2 . the user interface 18 that is shown in fig2 is a virtual user interface , which is displayed on a section of the screen 15 . the user interface 18 comprises a plurality of controls 19 to 24 , which are modeled on slide controls . the function of each control 19 to 24 is to set a parameter ( x ) ( x = d , p , u , i , sid , fdd ) that influences the image quality of an x - ray image that is to be taken by the x - ray device 1 . these parameters x include the dose of radiation d impinging on the x - ray detector 3 , the electrical power p from the tube current provided by the power unit 10 , the tube voltage u , the intensity of the tube current ( referred to below in short as i ), the sdi ( source image distance ) between the x - ray beam emitter 2 and the person 8 or object that is to be examined and the fdd ( focus detector distance ) between the x - ray beam emitter 2 and the x - ray detector 3 . each control 19 to 24 comprises a setting zone 25 that is shown as a ba r , a cursor 26 , which displays the current setting x act ( x act = d act , p act , u act , . . . ) of the respective parameter ( x ) that is assigned thereto . by operating the mouse 17 or the keyboard 16 , the cursor 26 can be moved between a lower stop 27 and an upper stop 28 . depending on the position of the cursor 26 in relation to the setting zone 25 , the respective parameter ( x ) is adjusted between a lower limit x min ( x min = d min , p min , u min , . . . ), corresponding with the lower stop 27 , and an upper limit x max ( x max = d max , p max , u max , . . . ), corresponding with the upper stop 28 . each control 19 to 24 further comprises an identification field 29 , that has an inscription showing the respective parameter ( x ) and an activation box 30 , through the activation of which ( using a mouse 17 or keyboard 16 ) each respective parameter can be maintained at a constant level . the user interface 18 can be minimized or maximized in relation to the screen surface in a manner that is in fact known , as desired by a user , and can be arranged anywhere on the screen 15 and , where necessary , can also be blanked out . in this way , the user interface 18 can always be arranged such that it does not cover any essential zones of an image zone 31 that forms the screen background , said zone being provided to display an x - ray image . in order to allow intuitive use of the x - ray device 1 , the setting zone 25 of each control 19 to 24 is divided into three sub - zones 32 , 33 and 34 which are differentiated from each other by color . the first sub - zone 32 marks a range of settings of the respective parameter ( x ), in which an acceptable image quality is guaranteed . the opposite sub - zone 34 marks a range of parameter settings , in which the image quality of the x - ray image is significantly restricted . the intermediate sub - zone 33 marks an intermediate range of parameter settings , in which a slight restriction in image quality has to be expected . according to the usual convention , the non - critical sub - zone 32 is preferably colored green , whilst the critical sub - zone 34 is red , and the intermediate sub - zone 33 is colored yellow . the allocation of the colors is arbitrary , however . the parameters ( x ) cannot generally be adjusted independently of one another . the current setting 26 of a parameter ( x ) usually depends , rather , on the current settings 26 of the other parameters ( x ). in particular , the equation for the dose of radiation d is approximately here , c is a dimensional function that is dependent on the distances sid and fdd . the variable a stands for the reduction , in other words the absorption of the x - ray radiation r in the tissue of the person to be examined 8 or in the material that makes up an object that is to be examined . the power p again depends , according to the well - known equation as a result of the fact that the parameters ( x ) are internally dependent on one another , a change in the current setting x act of one parameter ( x ) generally leads to a consequential change in other parameter settings . thus , for instance , an increase in the tube current i and / or the tube voltage u leads to an increase in the power p , and this again to an increase in the dose d . by activating an activation box 30 , the respective parameter ( x ) can be maintained at a constant level . in this way , an ( unwanted ) consequential adjustment of said parameter ( x ) can be avoided . the limits x min and x max of each parameter ( x ) are determined by the design of the x - ray device 1 . the way the sub - zones 32 , 33 and 34 are distributed over the whole setting zone 25 has to be determined individually for each parameter ( x ), and for each respective control 19 to 24 , by means of empirical tests with the specific x - ray device 1 and / or by model calculations . the lower limit of the “ green ” sub - zone 32 of the control 19 is preferably set at a predetermined desired value d 0 for the dose of radiation d . the “ yellow ” sub - zone 33 incorporates a reduction in dose of up to 50 % compared with the desired value d 0 . a reduction in dose of over 50 % compared with the desired value d 0 is recorded on the “ red ” sub - zone 34 . for a good image contrast in the x - ray image that is to be taken , the tube voltage u should be maintained as low as possible . the upper limit of the “ green ” sub - zone 32 of the control 21 is preferably set at a threshold value u 0 , at which the desired value d 0 is reached at maximum power p max . the threshold value u 0 can be derived simply from formula 1 and hence : it should be noted that formula 3 depends on the patient - dependent reduction a and the distance - dependent function c . in the determination of the threshold value u 0 , the reduction a is usefully estimated by a constant that corresponds to the reduction in a standard patient . the function c can likewise be estimated using standard values for sid and fdd . alternatively , the limit u 0 can be set so that it can be varied depending on the current settings sid act and fdd act . the lower limit of the “ green ” sub - zone 32 of the control 22 is preferably set at a threshold value i 0 of the tube current i , at which the desired value d 0 of the dose of radiation d is achieved at a maximum output p max and minimum tube voltage u 0 : in a similar manner the sub - zones 32 , 33 and 34 are set for controls 20 , 23 and 24 . in standard operation of the x - ray device 1 , the parameters ( x ) are preset by an automatic mechanism that is not shown in closer detail , such that the current setting x act of each parameter ( x ) falls , where possible , within the respective “ green ” sub - zone 32 . in borderline cases , in particular when examining obese or very obese patients , in whom this target setting cannot be achieved by the automatic mechanism , by moving the cursor 26 of the respective control 19 to 24 , the user of the x - ray device 1 can make a manual adjustment to the parameters ( x ), in order to optimize the image quality of the x - ray image that is to be taken . in order to improve the intuitive ease of operation of the user interface 18 , instead of the alphanumeric designation for the identification fields 29 that is shown in fig2 , designation with pictograms is used at least for individual parameters ( x ). such a pictogram that can be used to designate the control 23 and which shows the distance sid pictorially is shown , for example in fig3 a . a pictogram which shows in a similar manner the distance fdd , and which can be used to designate the identification field 29 for the control 24 is shown in fig3 b .
an intuitively manageable method for adjusting at least one parameter that determines the image quality of an x - ray image produced by an x - ray device is provided , wherein , on a user interface of the x - ray device a setting zone for the parameter is shown pictorially , and in relation to the setting zone the current setting of the parameter is likewise shown pictorially . at least two sub - zones of the setting zone are differentiated from each other by color , wherein a first sub - zone corresponds to a parameter - setting that guarantees good image quality and a second sub - zone corresponds to a parameter - setting that is critical for the image quality .