a tomosynthesis apparatus 30 according to the invention for mammography examinations is schematically shown in fig1 . the tomosynthesis apparatus 30 has a support arm 9 that is mounted such that it can pivot in a bearing around a horizontal axis a ( see double arrow and angle α ). the bearing is arranged on a stand 3 and can be vertically adjusted as indicated with the double arrow b . an arm 6 provided with an x - ray source 5 , a flat panel detector 7 and a compression device ( consisting of a compression plate 10 and a support plate 11 ) are arranged on the support arm 9 . schematically shown in fig1 is a female breast 12 compressed by the compression plate 10 and the bearing plate 11 . the arm 6 can pivot around the axis a relative to the support arm 1 , the detector 7 and the compression device 10 , 11 . electromotors 13 through 15 of the tomosynthesis apparatus 30 are provided for height adjustments and pivot motions . a control of the tomosynthesis apparatus 30 takes place via an operating device 6 of the tomosynthesis apparatus 30 which is connected with a controller 17 and an image computer 22 of said tomosynthesis apparatus 30 . specific methods ( among these the methods according to the invention ) can be loaded into the controller 17 and the operating device 16 by means of a dvd 21 . a basic workflow according to the invention of a dual - energy image acquisition , image processing and image presentation is shown in fig2 , beginning with the contrast agent administration . after the administration of the contrast agent , the acquisition of a two - dimensional low - energy image 1 of the female breast ( of the predetermined volume segment ) most often takes place in the form of a standard screening projection ( cc or mlo ). multiple two - dimensional high - energy images 2 are subsequently generated with the same acquisition angle ( cc or mlo ) of the female breast . a registration of the low - energy image 1 with a respective one of the high - energy images 2 takes place using earlier low - energy images 31 of the same breast of the patient . after this registration 8 the low - energy image 1 is subtracted from each of the high - energy images 2 , so a dual - energy image ( difference image ) results for each subtraction . this subtraction is also designated as a non - temporal dual - energy subtraction . the concentration of the contrast agent is visible in each of these difference images , such that the contrast agent course results from the multiple difference images . the acquisition of the two - dimensional low - energy image 1 and the acquisition of the two - dimensional high - energy images 2 take place in the enrichment phase of the contrast agent since the generation of the two - dimensional images 1 , 2 can take place fast enough in order to generate these two - dimensional images 1 , 2 even given a temporally short enrichment phase of only 10 s . after the creation of the two - dimensional high - energy images 2 ( approximately 2 to 4 minutes after the contrast agent administration ), a high - energy tomosynthesis 4 of the same breast is implemented . with the use of the two - dimensional low - energy image 1 , the image data resulting from the high - energy tomosynthesis 4 are registered with image data of an earlier low - energy tomosynthesis 18 implemented with regard to the same breast . after the registration 38 , the image data of the high - energy tomosynthesis 4 that are created from different tomosynthesis angles are adapted to one another such that a three - dimensional image data set of the female breast is created . a subtraction 39 subsequently occurs in which the image data of the earlier low - energy tomosynthesis 18 are subtracted from the image data of the high - energy tomosynthesis 4 , which is also known as a temporal dual - energy subtraction . the high - energy tomosynthesis 4 occurs in the wash - out phase in which the contrast agent flows out of the lesions or tumors , such that the concentration of the contrast agent decreases . this wash - out phase normally has a smaller ( negative ) slope of the contrast agent concentration per time unit in comparison to the ( positive ) slope of the contrast agent concentration in the enrichment phase , such that more time is available to implement the high - energy tomosynthesis . an additional workflow according to the invention of a dual - energy image acquisition , image processing and presentation is shown in fig3 , beginning with the contrast agent administration , wherein two different volume segments ( both breasts ) are examined . after the administration of the contrast agent , a two - dimensional low - energy image is first created from the right breast of the patient and multiple two - dimensional high - energy images 2 are subsequently created . the right breast is subsequently released and a two - dimensional low - energy image 1 ′ ( and following this multiple two - dimensional high - energy images 2 ′) of the left breast is created . after the generation of the two - dimensional high - energy images 2 ′, a high - energy tomosynthesis scan 4 ′ of the left breast is implemented . the left breast is subsequently released and a high - energy tomosynthesis scan 4 of the right breast is implemented . with the method shown in fig3 , both breasts of a patient can accordingly be examined with the with the same administration of a contrast agent . since a low - energy image 1 , 1 ′ of multiple high - energy images 2 , 2 ′ and a high - energy tomosynthesis scan 4 , 4 ′ are thus created both for the right breast and for the left breast , a non - temporal dual - energy subtraction 9 and a temporal dual - energy subtraction 39 can be implemented for both the right breast and the left breast , as is shown in detail for one breast in fig2 . a variant of the workflow according to the invention shown in fig3 for the examination of both breasts is shown in fig4 . in comparison to the workflow shown in fig3 , the generation of the two - dimensional high - energy images 2 , 2 ′ of the right and left breast is missing in the workflow shown in fig4 , so the generation of the two - dimensional images 1 , 1 ′ takes place more quickly and the high - energy tomosynthesis scan 4 , 4 ′ can be started faster . the two - dimensional high - energy images 2 ′ of the left breast are generated during the high - energy tomosynthesis scan 4 ′ of the left breast while the two - dimensional high - energy images 2 of the right breast are generated during the high - energy tomosynthesis scan 4 of the right breast . a variant of the embodiment shown in fig2 is depicted in fig5 . in the embodiment shown in fig5 , the high - energy tomosynthesis scan 4 begins directly after the administration of the contrast agent . the two - dimensional low - energy image 1 and the multiple two - dimensional high - energy images 2 are generated during this high - energy tomosynthesis scan 4 . a flow chart diagram of an embodiment of the method according to the invention is presented in fig6 a . in a first step s 1 , a contrast agent is administered to the patient before the breast to be examined is positioned between the bearing plate and the compression plate in a second step s 2 . these two first steps s 1 and s 2 can also be swapped in terms of their order so that the contrast agent is only administered when the breast to be examined is already positioned between the bearing plate and the compression plate . in the following step s 3 a two - dimensional low - energy image is subsequently generated with a correspondingly low x - ray energy as quickly as possible after the administration of the contrast agent . during the enrichment phase of the contrast agent in possible tumors and lesions present in the breast , multiple two - dimensional high - energy images are generated with a correspondingly high x - ray energy in step s 4 . since the generation of the two - dimensional images ( mammography ) is concluded , in step s 5 the detector is switched over from two - dimensional mode into a tomosynthesis mode . in step s 6 a high - energy tomosynthesis scan is subsequently implemented with a correspondingly high radiation energy in order to generate image data of the wash - out phase of the contrast agent before the breast is released in step s 7 . the processing of the images or image data generated in steps s 1 through s 7 takes place in the steps shown in fig6 b . steps s 8 through s 12 can thereby also be implemented in a different order than as shown in fig6 b insofar as the registration of the corresponding images or image data occurs before a reconstruction or subtraction of these images or image data . moreover , steps s 8 through s 12 do not need to occur after steps s 1 through s 7 ; rather , these can be interleaved with these steps s 1 through s 7 insofar as the images or image data required for a processing step s 8 through s 12 are created beforehand via the corresponding generation steps s 3 , s 4 , s 6 . in step s 8 the two - dimensional low - energy image 1 is registered with each of the high - energy images 2 , wherein this registration is implemented depending on a three - dimensional low - energy image created before the administration of the contrast agent . in step s 9 the low - energy image is subsequently subtracted from each high - energy image , whereby a number of dual - energy images or reference images is created which corresponds to the number of two - dimensional high - energy images . the respective subtraction of the low - energy image from the respective high - energy image is also designated as non - temporal dual - energy subtraction . in step s 10 the image data of the high - energy tomosynthesis scan are registered with image data of a low - energy tomosynthesis scan implemented before the administration of the contrast agent , wherein this registration is implemented depending on the two - dimensional low - energy image generated in step s 3 . in step s 11 , three - dimensional image information of the examined breast is reconstructed from the projections generated in the high - energy tomosynthesis scan . arbitrary slice images ( with arbitrary viewing angles ) of the examined breast can be generated with the aid of this three - dimensional image information . to show the contrast agent concentration or the course of the contrast agent concentration in the wash - out phase , the image data of the earlier low - energy tomosynthesis scan are subtracted from the image data of the high - energy tomosynthesis scan ( which is also known as a temporal dual - energy subtraction ). 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 an imaging method and a tomosynthesis apparatus , a two - dimensional low - energy image of the predetermined volume segment is obtained after administration of a contrast agent , followed by a two - dimensional high - energy image and then a high - energy tomosynthesis of the predetermined volume segment is obtained with a high total radiation dose that is significantly higher than the low radiation dose . the two - dimensional low - energy image is subtracted from the two - dimensional high - energy image to generate a result with which the concentration of the contrast agent is visible . additionally , in a time interval in which an enrichment or a washing - out of the contrast agent occurs within the predetermined volume segment , a tomosynthesis of the predetermined volume segment is automatically implemented to show the concentration of the contrast agent in the predetermined volume segment .