fig1 is a schematic illustration of a magnetic resonance system 5 ( a magnetic resonance imaging or magnetic resonance tomography apparatus ). a basic magnetic field 1 generates a temporally constant , strong magnetic field for polarization or , respectively , alignment of the nuclear spins in an examination region of a subject o , for example of a portion of a human body ( the head , for example ) that is to be examined which , situated on a table 23 , is moved into the magnetic resonance system 5 for data acquisition . the high homogeneity of the basic magnetic field that is required for the magnetic resonance measurement ( data acquisition ) is defined in a typically spherical measurement volume m . shim plates made of ferromagnetic material are mounted at a suitable point to assist the homogeneity requirements to eliminate temporally invariable influences . temporally variable influences are eliminated by shim coils 2 . a cylindrical gradient coil system 3 composed of three sub - windings is located in the basic field magnet 1 . each sub - winding is supplied with current by an amplifier to generate a linear ( and temporally variable ) gradient field in the respective direction of the cartesian coordinate system . the first sub - winding of the gradient field system 3 generates a gradient g x in the x - direction ; the second sub - winding generates a gradient g y in the y - direction ; and the third sub - winding generates a gradient g z in the z - direction . each amplifier has a digital / analog converter which is activated by a sequence controller 18 for time - accurate generation of gradient pulses . one ( or more ) radio - frequency antennas 4 that convert the radio - frequency pulses emitted by a radio - frequency power amplifier into an alternating magnetic field for excitation of the nuclei and alignment of the nuclear spins of the subject o to be examined or , respectively , of the region of the subject o that is to be examined are located within the gradient field system 3 . each radio - frequency antenna 4 is composed of one or more rf transmission coils and one or more rf reception coils in the form of an annular , advantageously linear or matrix - like arrangement of component coils . the alternating field emanating from the precessing nuclear spins — i . e . normally the spin echo signals caused by a pulse sequence made up of one or more radio - frequency pulses and one or more gradient pulses — is also converted by the rf reception coils of the respective radio - frequency antenna 4 into a voltage ( measurement signal ) which is supplied via an amplifier 7 to a radio - frequency reception channel 8 of a radio - frequency system 22 . the radio - frequency system 22 furthermore has a transmission channel 9 in which the radio - frequency pulses are generated for the excitation of the nuclear magnetic resonance . the respective radio - frequency pulses are digitally represented in the sequence controller 18 as a series of complex numbers based on a pulse sequence predetermined by the system computer 20 . this number sequence is supplied as a real part and imaginary part to a digital / analog converter in the radio - frequency system 22 via respective inputs 12 and from the digital / analog converter to a transmission channel 9 . in the transmission channel 9 , the pulse sequences are modulated on a radio - frequency carrier signal whose base frequency corresponds to the resonance frequency of the nuclear spins in the measurement volume . the switching from transmission operation to reception operation takes place via a transmission / reception diplexer 6 . the rf transmission coils of the radio - frequency antenna ( s ) 4 radiate ( s ) the radio - frequency pulses for excitation of the nuclear spins into the measurement volume m and scans resulting echo signals via the rf reception coil ( s ). the correspondingly acquired nuclear magnetic resonance signals are phase - sensitively demodulated at an intermediate frequency in the reception channel 8 ′ ( first demodulator ) of the radio - frequency system 22 and digitized in an analog / digital converter ( adc ). this signal is further demodulated to a frequency of 0 . the demodulation to a frequency of 0 and the separation into real part and imaginary part occurs in a second demodulator 8 after the digitization in the digital domain . an mr image can be reconstructed by the image computer 17 from the measurement data acquired in such a manner . the administration of the measurement data , the image data and the control programs takes place via the system computer 20 . based on a specification with control programs , the sequence controller 18 monitors the generation of the respective desired pulse sequences and the corresponding scanning of k - space . in particular , the sequence controller 18 thereby controls the time - accurate switching of the gradients , the emission of the radio - frequency pulses with defined phase amplitude and the reception of the magnetic resonance signals . the time base for the radio - frequency system 22 and the sequence controller 18 is provided by a synthesizer 19 . the selection of corresponding control programs to generate an mr image ( which control programs are stored on a dvd 21 , for example ) and the presentation of the generated mr image take place via a terminal 13 which comprises a keyboard 15 , a mouse 16 and a monitor 14 . how three respective diffusion gradients ( and therefore diffusion - weighted mr images 31 ) can be associated with a group ( and therefore a trace - weighted mr result image 32 ) is schematically depicted fig2 . in each of the three depicted variants a through c , the diffusion - weighted mr images 31 are associated with the respective trace - weighted mr result images 32 such that the diffusion gradients associated with the three diffusion - weighted mr images 31 are arranged optimally orthogonal to one another . in variant a ( see fig2 a ), no diffusion gradients are apportioned to the individual groups 32 ( mr result images 32 ) ( no diffusion - weighted mr images 31 ); in variant b ( see fig2 b ), one diffusion - weighted mr image 31 is respectively apportioned to the individual mr result images 32 ; and in variant c ( see fig2 c ), two diffusion - weighted mr images 31 are respectively apportioned to the individual mr result images 32 . a method according to the invention to generate diffusion information is presented in fig3 as a workflow diagram . in a first step s 1 , numerous diffusion gradients ( 60 , for example ) are determined . a diffusion - weighted mr image is then created in step s 3 with each of these diffusion gradients . if each of these diffusion gradients begins at the origin and intersects a spherical surface of a sphere , wherein this sphere has its center point at the origin , each diffusion gradient then generates an intersection point on the spherical surface . the diffusion gradients are now selected such that these intersection points cover the spherical surface as uniformly as possible so that , for example , the distance between an intersection point and its nearest neighbor is optimally the same for each intersection point . in a next step s 2 , diffusion gradients are sorted into an order such that three diffusion gradients arranged one after another according to the order respectively form a group . the three diffusion gradients of the same group are thereby mutually as orthogonal to one another as possible , such that the absolute value of the scalar product of any two of these three diffusion gradients of the same group is as small as possible . in the following step s 3 , three diffusion - weighted mr images are generated using the three diffusion gradients of the same group . these three diffusion - weighted mr images are combined in step s 4 into a trace - weighted mr result image . since the mr result images 32 are respectively created by means of diffusion gradients which are mutually arranged optimally orthogonal to one another , all mr result images are the same in terms of their contrast . this means that the mr result images generated according to the invention advantageously have only slight contrast differences . with respect to this current mr result image and the previous mr result image , in step s 5 a spatial transformation is determined which is also known as part of a registration . by means of this spatial transformation , subjects within the mr result image can be transformed into corresponding subjects in the previous mr result image , whereby a movement of these subjects between the previous mr result image and the current mr result image is taken into account . since all mr result images are the same with regard to their contrast , at most a slight contrast difference exists between an mr result image and its predecessor mr result image , wherein the determination of the spatial transformation between the mr result image and its predecessor mr result image is advantageously facilitated . in the next step s 6 , this spatial transformation determined in step s 5 is now used in order to accordingly correct or adapt corresponding positions and orientations ( in particular of subjects ) in those three mr images from which the current mr result image has been created . expressed in a different way : the spatial transformation determined in step s 5 is used in order to register the mr images . in the event that it is determined at the query s 7 that unprocessed diffusion gradients still exist ( thus diffusion gradients with which no diffusion - weighted mr image has yet been created ), the method returns to step s 3 . otherwise , the method continues at step s 8 . in this step s 8 , a diffusion information is generated using the corrected or adapted mr images . 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 .