fig2 schematically illustrates a medical imaging system 10 for acquiring projected 2d images to reconstruct a 3d image of a region of interest . the medical imaging system 10 comprises an image acquisition unit 12 , an image processing unit 13 and a display system 15 . the acquisition unit 12 allows a plurality of 2d projections to be obtained of a region of interest o — of an organ — in a patient . the acquisition unit 12 is notably formed by a detector 11 positioned facing an x - ray source 9 . the detector 11 is a digital camera for example . the acquisition unit 12 is an x - ray acquisition system for example , the latter comprising any known means allowing the emitting of x - rays onto the object o and the acquisition of resulting images . the display unit 15 can be integrated in the image acquisition unit 12 or the image processing unit 13 , or it can be separate from the acquisition unit 12 and the processing unit 13 . the display unit 15 , for example , is a computer screen , a monitor , flat screen , plasma screen or any type of known commercially available display device . the display unit 15 enables a radiological practitioner to monitor the reconstruction and / or display of the acquired 2d images . the processing unit 13 is adapted for implementing a processing method ( e . g . the reconstruction of a 3d image from 2d images ). the processing unit 13 can be integrated in the acquisition unit 12 or it can be separate from the acquisition unit 12 . the processing unit 13 , for example , is one or more computer ( s ), processor ( s ), microcontroller ( s ), micro - computer ( s ), programmable logic controller ( s ), application - specific integrated circuit ( s ), other programmable circuits or other devices which include a computer such as a work station . the processing unit 13 is coupled to memory means 14 which may be integrated in or separate from the processing unit 13 . these memory means may be formed by a hard disk or any other removable storage means ( cd - rom , floppy disc , etc .). these memory means may be used to store a 3d image of the region of the organ visualized as an acquired or processed 2d image . this may be a rom / ram memory of the processing unit 13 , a cd - rom , usb key , a memory of a central server 16 . the processing unit 13 may comprise a read device ( not illustrated ) e . g . a floppy disc reader or cd - rom reader , to read the instructions of the processing method ( described in the remainder hereof ) from an instruction medium ( not illustrated ) such as a floppy disc or cd - rom . in an embodiment , the processing unit 13 executes the instructions of the processing method ( described in the remainder hereof ) that are stored in firmware ( not illustrated ). at a first step s 1 , a plurality of projected 2d images 30 are acquired of the object of interest o in a plurality of orientations around the object ( scanning between − 12 ° and + 12 ° for example , or between − 25 ° and + 25 °). the method further comprises a step s 2 to apply a filter to the acquired , projected 2d images 30 so as to obtain filtered , projection images 40 of the object of interest o . to increase the quality of the reconstructed images , the filtering used on the projected pixels is adaptive filtering . different types of adaptive filters can be envisaged , in relation to the types of desired improvements . in particular , to reduce blurring which may be generated in projection images by structures of large size ( reference can be made to fig1 in which the object gs of large size generates a large fan - shaped artefact via its back projection ), the adaptive filter can be chosen so as to enhance the amplitude of the high frequencies relative to the low frequencies . for this purpose , the filtering used may be filtering of “ unsharp masking ” type , each pixel p of ( x , y ) coordinates in the plane of projection being filtered in the following manner : p ′( x , y )= lp σ ( x , y )+ α ·[ p ( x , y )− lp σ ( x , y )], where p ′( x , y ) is the value of this filtered pixel , a being an amplification factor , lp , being a low - pass filter applied to the value of the pixels around the pixel of ( x , y ) coordinates in the direction corresponding to scanning by the x - ray beams when the source switches from one acquisition position to another , and for example being : l ⁢ ⁢ p σ ⁡ ( x , y ) = ∫ - win win ⁢ p ⁡ ( x , y + v ) · g σ ⁡ ( v ) · ⅆ v where g σ is a gaussian of standard deviation σ , win is a parameter defining the size of the neighbourhood it is desired to take into account for the filter around the pixel of ( x , y ) coordinates . with said filter , it is therefore possible to enhance the high frequencies relative to the low frequencies . in an embodiment , this low - pass filter can be replaced by a bilateral filter , so as to avoid the effects of under - exposure which may otherwise exist on the edges of highly contrasted structures . in addition , the amplification factor may itself be a function of the x , y coordinates of the points in the projection images . it can therefore be adapted to the local contrast of the objects / structures appearing in the processed projection image , in order to attenuate the impact of highly contrasted objects / structures in the reconstructed volume . the local contrast in a projected pixel may be given by the difference between the value of the pixel and the value filtered by a low - pass filter for this pixel ; in an embodiment , it can be given by the difference between the value of the pixel and the value filtered by a bilateral filter for this pixel . in mammography , images may contain some contrast artefacts on the edges of the breast where the skin is thinner . the use of an amplification factor itself varying spatially , allows these effects to be corrected or attenuated . for example , in the case of an adaptive low - pass filter , this can be expressed as : p ′ ( x , y )= lp σ ( x , y )+ α ( x , y ) ·[ p ( x , y )− lp σ ( x , y )], α ( x , y )= f ( p ( x , y )− lp σ ( x , y )), where f is a function dependent on the local contrast and chosen to optimize the image quality of the reconstructed slices , and where f may depend on local contrast and depend on the distance from the pixel ( x , y ) to the edge of the breast . in addition , the frequency on and after which the amplification is applied may depend on the thickness of the breast , the emission angle of the tube or the target angle thereof it will effectively be appreciated that these different parameters also have an effect on reconstruction artefacts . for example , the thicker the breast the greater the impact obtained by backprojection of a structure therein over the entire volume . lower cut - off frequencies for example are therefore used for large breast thicknesses as well as higher coefficients of amplification . the same applies to the angle of emission or target angle of the x - ray tube . for example , the larger these angles are , the greater the increase in the cut - off frequency of the filter used or in the amplification factor . at a step s 3 , reconstruction slices 50 are determined of the object of interest o . this determination s 3 particularly consists of a backprojection of the filtered , projected 2d images 40 . this backprojection may in particular be non - linear of the type “ order statistics based backprojection ”. in linear backprojection , each voxel of the volume is reconstructed using n data pixels , each pixel being determined by reprojection of the voxel in each of the n projections . in non - linear backprojection , the pixel of maximum intensity among the ns is not used , which makes it possible to obtain a distinct reduction in replication artefacts caused by the most intense objects . it is noted that the reconstruction slices of the object of interest o represent the reconstructed volume of the object of interest o . optionally , at a step s 4 , the reconstruction slices 50 are re - projected in a given determined direction . examples of such reprojection processing have been described for example in patent application us 2011 / 0150178 . this makes it possible to obtain an intermediate 2d image 60 of the object of interest o . at a step s 5 , this then gives a final 2d image of the object of interest by combining the intermediate 2d image 60 with a projection image initially acquired in a given orientation of the source ( e . g . the orientation in which the said source emits perpendicular to the plane of the detector ). the combination is , in an embodiment , pixel by pixel linear combination . the final 2d image thus obtained is then an image similar to a mammography image and can be displayed ( step s 6 ). in this manner , with one single reconstruction , it is possible to obtain both reconstructed slice images and a 2d image resembling a 2d radiography image of the object of interest . as will be appreciated however ; steps s 4 , s 5 and s 6 are optional . it will be noted that the sampling of the images of reconstructed slices can be identical to that of a projection image , the backprojection and reprojection being performed in a single computing step , making it possible substantially to reduce the computing time . in an embodiment , the reconstruction of an image of a sectional plane can be made in relation to the ratio between the zoom applied during backprojection and the zoom required for reprojection at one or more given incidences . in this manner , a better definition is potentially obtained of some small objects , in particular of microcalcifications for example . the different steps just described and in particular the processing steps s 2 and s 3 ( and optionally s 4 and s 5 ) are implemented using code instructions of a programme recorded on a medium integrated in the processing unit or associated therewith . a two - dimensional image 2d obtained from images of reconstructed slices using a prior art method is illustrated in fig5 a . it can be seen that this image , fig5 a , has a sizeable artefact ( encircled region in this figure ). fig5 b illustrates the same image but obtained using the method which has just been described . as can be seen in this figure , the artefact has been reduced therein and even eliminated . this written description uses examples to disclose the invention , including the preferred embodiments , and also to enable any person skilled in the art to practice the invention , including making and using any devices or systems and performing any incorporated methods . the patentable scope of the invention is defined by the claims , and may include other examples that occur to those skilled in the art . such other examples are intended to be within the scope of the claims if they have structural elements that do not differ from the literal language of the claims , or if they include equivalent structural element with insubstantial differences from the literal languages of the claims .