arteriovenous malformations avm are identified in fig1 a ). a microcatheter k inserted selectively into the supplying artery introduces tissue adhesive g ( e . g . onyx ) in order to close the arteriovenous short - circuits or malformations . a ) shows the native fluoroscopic image , fig1 b ) shows the correspondingly subtracted frame ( roadmap ), on which are visible only the differences from a specific mask image . roadmap images are mainly composed of “ neutral ” background ( namely the parts in which the live image ( image frame during the intervention ) is identical to the mask and which hence “ cancel themselves out ”), and the changes in the live image compared with the mask , which stand out as dark areas ( see illustration b ). artifacts may also show up as white points . according to the invention , it is noted for each image pixel the time instant at which the image pixel becomes “ dark ” for the first time , which in the intervention corresponds to an accumulation of embolizing material or embolic agent ( e . g . tissue adhesive ) at this location . fig2 shows this clearly . a ) shows by way of example a “ time / color curve ” for each pixel ( over seven time steps or time instants ). b ) shows schematically an image segment in time step t = 4 . each of the pixels shown contains the piece of information on when it became dark initially ( where “ 0 ” is used to code the background pixels in the example .) some of the pixels have become dark in the current time step 4 ( hence tissue adhesive has accumulated here ). they bear the number “ 4 ” as the piece of information . some of the pixels have been dark for a longer time ; they consequently bear the numbers “ 1 ” to “ 3 ” as the piece of information . the pixels are assigned a color in accordance with the color curve . c ) shows the same segment one time step later . one of the pixels that was stained in step “ 4 ” is “ light ” again in the current image ; the piece of information is then reset to “ background ” ( i . e . “ 0 ”). otherwise the information remains the same , with the color coding moving in the “ red ” r direction in accordance with the color curve . expressed formally , let “ pixel ( i , j , t )” be an image pixel at the image point ( i , j ) at time instant t , and f ( i , j ) be the corresponding “ color index ”. then the color coding comprises simply the following queries if pixel ( i , j , t ) “ is darker than ” pixel ( i , j , t - 1 ) then f ( i , j ) := t ; if pixel ( i , j , t ) “ corresponds to background ” then f ( i , j ) := h ; for visualization at time instant t , each pixel ( i , j , t ) is now simply coded according to its color index f ( i , j ) and the corresponding color curve k ( t ) ( fig2 ). the principle that applies here is that the coloring of a pixel reflects how may time intervals ago t - t it became stained . in the present embodiment , pixels that are just becoming “ dark ” are coded “ blue ” b . the longer they remain dark , the “ redder ” they become . if a pixel becomes light again , the color coding is also reset to “ background ” i . e . white or number “ 0 ”. fig3 shows in a ) by way of example a corresponding time / color curve for each pixel and in b ) an example from an embolization view . if tissue adhesive accumulates in a location , the image area ( i . e . the corresponding pixels ) becomes dark , this time instant is saved for each pixel , the color coding of these pixels na is initially set to “ blue ”. the color coding now continues to show how long the tissue adhesive has already been accumulating . the longer the region remains stained , the more the color changes from “ blue ” towards “ red ”. if a pixel becomes “ light ” again , e . g . because the adhesive was only briefly and temporarily in the area , the color coding is reset to background . in further embodiments , the color coding can be superimposed on the live fluoroscopic image , as is shown in c ) in fig3 for instance . the superposition can be faded in or out using a slide control . in further embodiments , the color coding can also be combined with a re - initialization of the roadmap masks . fig4 a ) shows an example of a corresponding “ time / color curve ”. b ) shows a corresponding image from an embolization sequence , where the color coding is superimposed on the live image . if the mask is re - initialized , all of the pixels vla stained up until this time change color , in this example to “ purple ”. for all other pixels la , color coding now continues as proposed above , i . e . the change after a re - initialization is documented . if an intensity changes in the mask area ( for instance if areas that are already embolized become “ more ” concentrated with tissue adhesive ), this can additionally be shown by a color change in the mask pixels . in addition , the gray level of a pixel of the subtracted image can be coded as the brightness level for the color - coded pixel . fig5 shows an image sequence ( native fluoroscopy image , subtracted image , superimposed live image ) over the course of time , which illustrates the color coding and its change in accordance with the above explanations . according to the invention , the method can be performed by a computer . as shown in fig6 , such a computer is composed of standard components 1 to 6 . in particular , the computer has a microprocessor 1 , a random access memory ( ram ) 2 , a mass storage device 3 ( for example a hard disk ), a user interface 4 , a data interface 5 and a programming interface 6 . the components 1 to 6 have a standard design and work together in a standard manner . hence , for instance , the user interface 4 can comprise standard input and output devices such as a keyboard , a mouse , a display device etc . the data interface 5 may be an internet interface or a lan interface or a usb interface , for example . also an embodiment as a drive for an interchangeable medium ( for instance a cd - rom or a dvd ) is possible . similar embodiments are possible for the programming interface 6 . if applicable , the data interface 5 and the programming interface 6 can be combined into a shared interface . a computer program 7 is input to the computer via the programming interface 6 . for instance , a data storage medium 8 , on which the computer program 7 is stored in machine - readable form , can be connected to the computer . the computer program 7 is then read from the data storage medium 8 and copied into the mass storage device 3 of the computer , where it is also stored . the computer program 7 contains machine code 9 , i . e . program instructions that can be executed by the computer directly and immediately . a user can start the computer program 7 using standard input commands ( for instance a double mouse - click ). when the computer program 7 is started , it is loaded into the ram 2 of the computer and executed by the computer . the execution of the computer program 7 by the computer results in the computer performing a computation method , which is described in detail above in connection with the other figures . the computer can receive a sequence of fluoroscopic or x - ray images b and their acquisition time instants t , and compute an analysis image a from the sequence . the computer can output the color - coded analysis image a to the user 10 . in a further embodiment , the computer can output to the user simultaneously with the color - coded analysis image another color - coded analysis image . the computer can receive a further temporal sequence of fluoroscopic images and compute the color - coded further analysis image from the further temporal sequence in a similar manner to that for the first said color - coded analysis image . the difference from the procedure described above is that , although the further sequence of x - ray images are x - ray images of the same examination object and of the same examination area of the examination object , and have also been taken with the same frame geometry , the acquisition of the further sequence took place at a different time instant from the acquisition of the first said sequence . the computer can display the two analysis images side - by - side or superimposed on each other for example . it is also possible for the computer to compute the differences between the two analysis images and output the difference image to the user 10 . the present invention has numerous advantages . in particular , it is possible to display primarily visually in a single analysis image the vascular architecture of arteries and veins and moreover the functional information on the embolization . hence the user no longer needs to combine the data mentally . in addition , the changing flow conditions of the embolic agent can also be identified clearly during and after an intervention and can be incorporated in subsequent intervention planning . in general , the method described above can also be used for other vascular malformations ( e . g . fistulas , aneurysms , stenoses etc . ), and even neoplastic changes in the brain and even other regions of the body . the above description is used solely to explain the present invention . the scope of protection of the present invention , however , shall be defined solely by the attached claims .
a method for computing a color - coded analysis image of an examination area of an examination object from a temporal sequence of fluoroscopic images of the examination area comprising a vascular system containing arteries and / or veins is provided . an acquisition time instant has been assigned to each of the fluoroscopic images representing a given distribution of a material embolizing some of the vascular system . the fluoroscopic image spatially corresponds to an analysis image pixel by pixel . a computer receives the fluoroscopic images with a color attribute assigned to each pixel of the analysis image at an image point and a time instant . if a pixel differs from a pixel at a preceding time instant , the color attribute assumes a color attribute of the time instant and the difference . if a pixel corresponds to a background color of the analysis image , the color attribute assumes a background color .