in some known ct imaging system configurations , an x - ray source projects a fan - shaped beam which is collimated to lie within an x - y plane of a cartesian coordinate system and generally referred to as an “ imaging plane ”. the x - ray beam passes through an object being imaged , such as a patient . the beam , after being attenuated by the object , impinges upon an array of radiation detectors . the intensity of the attenuated radiation beam received at the detector array is dependent upon the attenuation of an x - ray beam by the object . each detector element of the array produces a separate electrical signal that is a measurement of the beam intensity at the detector location . the intensity measurements from all the detectors are acquired separately to produce a transmission profile . in third generation ct systems , the x - ray source and the detector array are rotated with a gantry within the imaging plane and around the object to be imaged such that the angle at which the x - ray beam intersects the object constantly changes . a group of x - ray attenuation measurements , i . e ., projection data , from the detector array at one gantry angle is referred to as a “ view ”. a “ scan ” of the object comprises a set of views made at different gantry angles , or view angles , during one revolution of the x - ray source and detector . in an axial scan , the projection data is processed to construct an image that corresponds to a two - dimensional slice taken through the object . one method for reconstructing an image from a set of projection data is referred to in the art as the filtered backprojection technique . this process converts the attenuation measurements from a scan into integers called “ ct numbers ” or “ hounsfield units ” ( hu ), which are used to control the brightness of a corresponding pixel on a cathode ray tube display . to reduce the total scan time , a “ helical ” scan may be performed . to perform a “ helical ” scan , the patient is moved while the data for the prescribed number of slices is acquired . such a system generates a single helix from a fan beam helical scan . the helix mapped out by the fan beam yields projection data from which images in each prescribed slice may be reconstructed . reconstruction algorithms for helical scanning typically use helical weighing algorithms that weight the collected data as a function of view angle and detector channel index . specifically , prior to a filtered backprojection process , the data is weighted according to a helical weighing factor , which is a function of both the gantry angle and detector angle . the weighted data is then processed to generate ct numbers and to construct an image that corresponds to a two - dimensional slice taken through the object . to further reduce the total acquisition time , multi - slice ct has been introduced . in multi - slice ct , multiple rows of projection data are acquired simultaneously at any time instant . when combined with helical scan mode , the system generates a single helix of cone beam projection data . similar to the single slice helical , weighting scheme , a method can be derived to multiply the weight with the projection data prior to the filtered backprojection algorithm . as used herein , an element or step recited in the singular and proceeded with the word “ a ” or “ an ” should be understood as not excluding plural said elements or steps , unless such exclusion is explicitly recited . furthermore , references to “ one embodiment ” of the present invention are not intended to be interpreted as excluding the existence of additional embodiments that also incorporate the recited features . also as used herein , the phrase “ reconstructing an image ” is not intended to exclude embodiments of the present invention in which data representing an image is generated but a viewable image is not . however , many embodiments generate ( or are configured to generate ) at least one viewable image . referring to fig1 and 2 , a multi - slice scanning imaging system , for example , a computed tomography ( ct ) imaging system 10 , is shown as including a gantry 12 representative of a “ third generation ” ct imaging system . gantry 12 has an x - ray source 14 that projects a beam of x - rays 16 toward a detector array 18 on the opposite side of gantry 12 . detector array 18 is formed by a plurality of detector rows ( not shown ) including a plurality of detector elements 20 which together sense the projected x - rays that pass through an object , such as a medical patient 22 between array 18 and source 14 . a collimator assembly 19 is positioned between array 18 and source 14 . collimator assembly 19 includes a known bowtie filter 21 and a bowtie addition 23 . bowtie addition 23 is fabricated from any material suitable for fabricating known bowtie filters . in one embodiment , bowtie addition 23 is positioned between bowtie filter 21 and array 18 . alternatively , addition 23 is positioned between bowtie filter 21 and source 14 . each detector element 20 produces an electrical signal that represents the intensity of an impinging x - ray beam and hence can be used to estimate the attenuation of the beam as it passes through object or patient 22 . during a scan to acquire x - ray projection data , gantry 12 and the components mounted therein rotate about a center of rotation 24 . fig2 shows only a single row of detector elements 20 ( i . e ., a detector row ). however , multi - slice detector array 18 includes a plurality of parallel detector rows of detector elements 20 such that projection data corresponding to a plurality of quasi - parallel or parallel slices can be acquired simultaneously during a scan . rotation of components on gantry 12 and the operation of x - ray source 14 are governed by a control mechanism 26 of ct system 10 . control mechanism 26 includes an x - ray controller 28 that provides power and timing signals to x - ray source 14 and a gantry motor controller 30 that controls the rotational speed and position of components on gantry 12 . a data acquisition system ( das ) 32 in control mechanism 26 samples analog data from detector elements 20 and converts the data to digital signals for subsequent processing . an image reconstructor 34 receives sampled and digitized x - ray data from das 32 and performs high - speed image reconstruction . the reconstructed image is applied as an input to a computer 36 , which stores the image in a storage device 38 . image reconstructor 34 can be specialized hardware or computer programs executing on computer 36 . computer 36 also receives commands and scanning parameters from an operator via console 40 that has a keyboard . an associated cathode ray tube display 42 allows the operator to observe the reconstructed image and other data from computer 36 . the operator supplied commands and parameters are used by computer 36 to provide control signals and information to das 32 , x - ray controller 28 , and gantry motor controller 30 . in addition , computer 36 operates a table motor controller 44 , which controls a motorized table 46 to position patient 22 in gantry 12 . particularly , table 46 moves portions of patient 22 through gantry opening 48 . in one embodiment , computer 36 includes a device 50 , for example , a floppy disk drive , cd - rom drive , dvd drive , magnetic optical disk ( mod ) device , or any other digital device including a network connecting device such as an ethernet device for reading instructions and / or data from a computer - readable medium 52 , such as a floppy disk , a cd - rom , a dvd or an other digital source such as a network or the internet , as well as yet to be developed digital means . in another embodiment , computer 36 executes instructions stored in firmware ( not shown ). computer 36 is programmed to perform functions described herein , and as used herein , the term computer is not limited to just those integrated circuits referred to in the art as computers , but broadly refers to computers , processors , microcontrollers , microcomputers , programmable logic controllers , application specific integrated circuits , and other programmable circuits , and these terms are used interchangeably herein . although the specific embodiment mentioned above refers to a third generation ct system , the methods described herein equally apply to fourth generation ct systems ( stationary detector - rotating x - ray source ) and fifth generation ct systems ( stationary detector and x - ray source ). additionally , it is contemplated that the benefits of the invention accrue to imaging modalities other than ct . additionally , although the herein described methods and apparatus are described in a medical setting , it is contemplated that the benefits of the invention accrue to non - medical imaging systems such as those systems typically employed in an industrial setting or a transportation setting , such as , for example , but not limited to , a baggage scanning system for an airport or other transportation center , and that addition 23 is used for objects other than organs . herein are described novel methods and apparatus for use in imaging systems . in one aspect , the use of an organ - specific bowtie addition ( e . g ., bowtie addition 23 ) together with bowtie 21 for imaging specific organs results in the use of less dose but equal noise as with the use of bowtie 21 singularly . a set of organ - specific bowtie additions are made to modulate the x - ray flux coming out of the tube - bowtie assembly ( e . g ., collimator assembly 19 ) based on the specific organs that a physician is interested in . in one embodiment , the addition has a smooth surface and can be moved in and out of collimator assembly 19 easily by an operator . in an exemplary embodiment , bowtie addition 23 is mounted within collimator assembly 19 such that the operator can remove bowtie addition 23 without tools . additionally , the operator can replace bowtie addition 23 with another bowtie addition without the use of tools . the additions maintain a majority of the x - ray flux coming out of bowtie 21 for the interested organ area while reducing x - ray flux for other areas , therefore reducing the whole body dose . special bowtie additions may be made for , but certainly not limited to , the ct applications of cardiac , lung , and liver . as illustrated in fig3 , bowtie addition 23 is a specific example of a bowtie addition for cardiac imaging . bowtie addition 23 has a smooth surface and is able to move in and out of collimator assembly 19 easily . for cardiac imaging , one can use a known head bowtie or a modified head bowtie that provides more attenuation of the x - ray towards the edge of the body than the current head bowtie . this modified head bowtie provides more x - ray flux than the current body bowtie near the center of the imaging field of view where the heart is located , while reducing the dose to the whole body by at least 20 %. this modified head bowtie can also be used for the general head and pediatric scans . combined with this modified head bowtie , a bowtie addition for cardiac imaging is also used such as bowtie addition 23 . cardiac bowtie addition 23 is designed to account for the fact that the heart is not located exactly at the center of the imaging field of view , and that x - ray flux requirement for the lung area is substantially less . in the exemplary example of a cardiac bowtie addition as shown in fig3 includes a plurality of thick sections 60 interspersed with a plurality of thin sections 62 . a middle thick section 64 is less thick than the other thick sections 60 . although thick section 64 can be between one - third and two - thirds the thickness of other thick sections 60 , thick section 64 is always about one - half the thickness of the other thick sections 60 . in another example , bowtie addition 23 has more than 5 sections . in yet another example , bowtie addition 23 has 9 sections . in still another embodiment , bowtie addition 23 has 12 sections . in a further embodiment , bowtie addition 23 has at least one but less than 5 sections . in an additional embodiment , bowtie addition 23 has 4 sections . an x - ray modulation 66 is shown in fig4 . x - ray modulation 66 corresponds to bowtie addition 23 having 5 sections . cardiac bowtie addition 23 has been evaluated using patient scans . two sets of cardiac scans were obtained at both 320 ma and 200 ma for clinical evaluation . lower dose scans ( 210 ma average ) with the x - ray modulated according to the cardiac bowtie addition was simulated using a noise addition tool based on the original 320 ma scans . these three sets of scan data were reconstructed using the standard reconstruction algorithm . image noises were measured at three different locations on three sets of images . fig5 shows the image comparison from the three different sets of data . also shown on the images are the noise measurements . the comparison indicates that ( 1 ) using the current body bowtie for cardiac imaging , the noise increases as the ma decreases . the discrepancies of the edge noise numbers were caused by the current fan beam reconstruction algorithm . after the two numbers were averaged , they still follow the inverse square root of the ma rule . and ( 2 ), with the use of bowtie addition 23 , the noise measurements in the heart area of the simulated lower dose scans were about the same as the original scans , even through the average ma ( dose ) has decreased by 30 %. exemplary embodiments of methods , systems , and assemblies for facilitating a reduction in patient dose are described above in detail . the methods , systems , and assemblies are not limited to the specific embodiments described herein , but rather , components of each methods , systems , and assemblies may be utilized independently and separately from other components described herein . in addition , each methods , systems , and assemblies component can also be used in combination with other components described herein . while the invention has been described in terms of various specific embodiments , those skilled in the art will recognize that the invention can be practiced with modification within the spirit and scope of the claims .
a method for obtaining data includes scanning an organ with an imaging system emitting x - rays and modulating the emitted x - rays with an organ specific bowtie addition .