Abstract: In a magnetic resonance method and system to acquire an MR image using a pulse sequence that sets the magnetization vector in the steady state into a stable oscillation under RF excitation pulses radiated at a time interval of time TR, the phase coding gradients for coding a k-space line in k-space of the pulse sequence (which k-space corresponds to the desired MR image) are switched such that the first moment of the phase coding gradient is minimal at the point in time of the radiation of an RF excitation pulse without the repetition time TR being extended relative to pulse sequences with unminimized phase coding gradients.

Abstract: In a method to create an image data set by operating a magnetic resonance system, at least two phase coding gradients are switched in respective spatial directions, an RF excitation pulse is radiated and a raw data point in a k-space data set belonging to the image data set is read out a predetermined time period after the radiation of the RF excitation pulse. The predetermined time period thereby corresponds to the maximum of a set of a respective minimum time period for each of the at least two phase coding gradients. The minimum time period of the respective at least one of the at least two phase coding gradients is determined depending on the strength of the respective phase coding gradient such that the Nyquist theorem is complied with.

Abstract: A method for contrast-agent-free non-triggered angiographic imaging in magnetic resonance tomography that includes the steps of (S1) 2D or 3D measurement of a bodily region having a flow of blood, using a flow-insensitive SSFP sequence, (S2) measurement of the same bodily region using a flow-sensitive SSFP sequence, (S3) registration of the measurement results obtained in steps S1 and S2 to one another, (S4) unweighted or self-weighted subtraction of the registered measurement result obtained in step S2from the registered measurement result obtained in step S1, (S5) execution of a 2D or 3D image correction of the image obtained in step S4by removing image distortions caused by gradient field inhomogeneities and/or magnetic basic field inhomogeneities, and (S6) representation of the angiogram obtained in step S5 in the form of an MIP or segmented 2D or 3D vessel tree representation.

Abstract: A series of image data sets of a region of an organism is acquired while the acquired region of the organism moves dependent on breathing and heartbeat, and supplied to a processor. The processor determines a first contour that moves depending on the breathing in the acquired image data sets. The acquired image data sets are distorted elastically in the processor into singly distorted image data sets such that the first contours of the singly distorted image data sets spatially correspond with one another. A second contour is determined in the processor in the acquired image data sets or in the singly distorted image data sets, this second contour moves depending on the heartbeat. The singly distorted image data sets are distorted elastically into doubly distorted image data sets such that the second contours of the doubly distorted image data sets spatially correspond with one another.

Abstract: In a method and apparatus to generate MR images of an examination region containing tissue with a first T2 time and tissue with a second, significantly longer T2 time are contained, as series of pulse sequences is employed the following pulse sequences: an overview pulse sequence to generate MR overview images, a T1-weighted pulse sequence to generate T1-weighted MR images and a multiple contrast pulse sequence in which at least two groups of magnetic resonance signals are acquired. A first group of magnetic resonance signals is acquired after excitation of a magnetization in a first time period and at least one second group of magnetic resonance signals is acquired in a second time period after the first time period in which the tissue with the significantly longer T2 time delivers the significant signal contribution. An MR image is calculated based on a pixel-by-pixel difference of the absolute values from the magnetic resonance signals of the first group and the second group.

Abstract: In a method to generate an MR angiography image of an examination region of a subject without the use of contrast agent, a first MR image of the examination region is acquired with a first imaging sequence in which a gradient-induced phase development for unmoved and moved spins is essentially completely rephased at the end of a repetition interval TR, and a second MR image of the examination region is acquired with a second imaging sequence in which the gradient-induced phase development for unmoved spins is likewise essentially completely rephased at the end of the repetition interval TR and a rest phase ?rest for moved spins remains at the end of the repetition interval TR. The second MR image is subtracted from the first MR image to generate the MR angiography image.

Abstract: A magnetic resonance tomography (MRT) method with spectral fat saturation or spectral water excitation in a tissue region that is to be represented of a patient who is to be examined, includes the following steps: (Step 1) frequency adjustment measurement of a region of a patient that is to be represented with a selected first partial coil of the MRT system, (Step 2) precise determination of the resonance frequency of water with the aid of the spectrum obtained in Step 1 exhibiting the resonance frequencies of fat and water, (Step 3) repetition of Steps 1 and 2 with at least one additionally selected second partial coil of the MRT system adjacent to the first partial coil, (Step 4) measuring of a k space data record with a partial coil or a partial coil combination on the basis of the water resonance frequency assigned to these partial coils, (Step 5) repetition of Step 4 with other partial coils or other partial coil combinations until the entire tissue region to be represented has been measured, (Step 6) co

Abstract: In a method for selective presentation of a movement of the lung, magnetic resonance images (MR images) of the lung are acquired in a temporal progression, i.e. MR images of the lung are acquired over multiple breathing cycles. The acquired MR images are registered with regard to a reference position and the signal curve over time is determined in the acquired MR images. The frequency spectrum of the determined signal curves is then determined, such as by a Fourier transformation. A specific frequency spectrum is filtered with a frequency band filter, wherein the frequency range of the frequency band filter is adapted to the movement to be shown. The filtered frequency spectrum is transformed back into a filtered signal curve of the MR images, and the magnetic resonance images obtained via this back-transformation are displayed in the temporal progression with the filtered signal curve. A computer readable medium, an image processing unit and a magnetic resonance apparatus implement such a method.

Abstract: In a magnetic resonance method and system to acquire an MR image using a pulse sequence that sets the magnetization vector in the steady state into a stable oscillation under RF excitation pulses radiated at a time interval of time TR, the phase coding gradients for coding a k-space line in k-space of the pulse sequence (which k-space corresponds to the desired MR image) are switched such that the first moment of the phase coding gradient is minimal at the point in time of the radiation of an RF excitation pulse without the repetition time TR being extended relative to pulse sequences with unminimized phase coding gradients.

Abstract: An imaging apparatus is disclosed that displays an image acquired from an examination object. The apparatus includes an acquisition unit that determines image acquisition parameters and acquires the signal values of the examination object; a conversion unit that uses a transfer function to convert the acquired signal values into brightness values that are displayed in the image; a unit for extracting the image acquisition parameters; and a storage unit that has data records in which at least one transfer function is stored in relation to the image acquisition parameters. The conversion unit compares the image acquisition parameters with the image acquisition parameters stored in the storage unit and selects the transfer function as a function of the comparison.

Abstract: In a method and apparatus for generating a fat-reduced, spatially resolved magnetic resonance spectrum of an examination subject, first measurement data are acquired to generate a spatially resolved spectroscopy measurement, second spatially resolved measurement data are generated that essentially have only fat signal contributions, and the second measurement data are subtracted from the first measurement data to generate the fat-reduced, spatially resolved magnetic resonance spectrum.

Abstract: A series of image data sets of a region of an organism is acquired while the acquired region of the organism moves dependent on breathing and heartbeat, and supplied to a processor. The processor determines a first contour that moves depending on the breathing in the acquired image data sets. The acquired image data sets are distorted elastically in the processor into singly distorted image data sets such that the first contours of the singly distorted image data sets spatially correspond with one another. A second contour is determined in the processor in the acquired image data sets or in the singly distorted image data sets, this second contour moves depending on the heartbeat. The singly distorted image data sets are distorted elastically into doubly distorted image data sets such that the second contours of the doubly distorted image data sets spatially correspond with one another.

Abstract: In a method to create an image data set by operating a magnetic resonance system, at least two phase coding gradients are switched in respective spatial directions, an RF excitation pulse is radiated and a raw data point in a k-space data set belonging to the image data set is read out a predetermined time period after the radiation of the RF excitation pulse. The predetermined time period thereby corresponds to the maximum of a set of a respective minimum time period for each of the at least two phase coding gradients. The minimum time period of the respective at least one of the at least two phase coding gradients is determined depending on the strength of the respective phase coding gradient such that the Nyquist theorem is complied with.

Abstract: In a method to generate an MR angiography image of an examination region of a subject without the use of contrast agent, a first MR image of the examination region is acquired with a first imaging sequence in which a gradient-induced phase development for unmoved and moved spins is essentially completely rephased at the end of a repetition interval TR, and a second MR image of the examination region is acquired with a second imaging sequence in which the gradient-induced phase development for unmoved spins is likewise essentially completely rephased at the end of the repetition interval TR and a rest phase ?rest for moved spins remains at the end of the repetition interval TR. The second MR image is subtracted from the first MR image to generate the MR angiography image.

Abstract: A magnetic resonance tomography (MRT) method with spectral fat saturation or spectral water excitation in a tissue region that is to be represented of a patient who is to be examined, includes the following steps: (Step 1) frequency adjustment measurement of a region of a patient that is to be represented with a selected first partial coil of the MRT system, (Step 2) precise determination of the resonance frequency of water with the aid of the spectrum obtained in Step 1 exhibiting the resonance frequencies of fat and water, (Step 3) repetition of Steps 1 and 2 with at least one additionally selected second partial coil of the MRT system adjacent to the first partial coil, (Step 4) measuring of a k space data record with a partial coil or a partial coil combination on the basis of the water resonance frequency assigned to these partial coils, (Step 5) repetition of Step 4 with other partial coils or other partial coil combinations until the entire tissue region to be represented has been measured, (Step 6) co

Abstract: In a method and apparatus to generate MR images of an examination region containing tissue with a first T2 time and tissue with a second, significantly longer T2 time are contained, as series of pulse sequences is employed the following pulse sequences: an overview pulse sequence to generate MR overview images, a T1-weighted pulse sequence to generate T1-weighted MR images and a multiple contrast pulse sequence in which at least two groups of magnetic resonance signals are acquired. A first group of magnetic resonance signals is acquired after excitation of a magnetization in a first time period and at least one second group of magnetic resonance signals is acquired in a second time period after the first time period in which the tissue with the significantly longer T2 time delivers the significant signal contribution. An MR image is calculated based on a pixel-by-pixel difference of the absolute values from the magnetic resonance signals of the first group and the second group.

Abstract: A method for contrast-agent-free non-triggered angiographic imaging in magnetic resonance tomography that includes the steps of (S1) 2D or 3D measurement of a bodily region having a flow of blood, using a flow-insensitive SSFP sequence, (S2) measurement of the same bodily region using a flow-sensitive SSFP sequence, (S3) registration of the measurement results obtained in steps S1 and S2 to one another, (S4) unweighted or self-weighted subtraction of the registered measurement result obtained in step S2 from the registered measurement result obtained in step S1, (S5) execution of a 2D or 3D image correction of the image obtained in step S4 by removing image distortions caused by gradient field inhomogeneities and/or magnetic basic field inhomogeneities, and (S6) representation of the angiogram obtained in step S5 in the form of an MIP or segmented 2D or 3D vessel tree representation.

Abstract: In a magnetic resonance tomography apparatus and method for determination of T2-weighted images of tissue with short T2 time, in the framework of a steady-state free precession sequence with non-slice-selective RF excitation pulses and projection-reconstruction methods, in each sequence repetition a first steady-state is read out in the form of a half echo and a second steady-state signal is read out in the form of a further half echo with very short echo times TE1 and TE2=2TR?TE1, and are combined by weighted addition such that an MRT image of tissue with very short T2 time is obtained with the sequence.

Abstract: In a method for selective presentation of a movement of the lung, magnetic resonance images (MR images) of the lung are acquired in a temporal progression, i.e. MR images of the lung are acquired over multiple breathing cycles. The acquired MR images are registered with regard to a reference position and the signal curve over time is determined in the acquired MR images. The frequency spectrum of the determined signal curves is then determined, such as by a Fourier transformation. A specific frequency spectrum is filtered with a frequency band filter, wherein the frequency range of the frequency band filter is adapted to the movement to be shown. The filtered frequency spectrum is transformed back into a filtered signal curve of the MR images, and the magnetic resonance images obtained via this back-transformation are displayed in the temporal progression with the filtered signal curve. A computer readable medium, an image processing unit and a magnetic resonance apparatus implement such a method.

Abstract: In a method and apparatus for generating a fat-reduced, spatially resolved magnetic resonance spectrum of an examination subject, first measurement data are acquired to generate a spatially resolved spectroscopy measurement, second spatially resolved measurement data are generated that essentially have only fat signal contributions, and the second measurement data are subtracted from the first measurement data to generate the fat-reduced, spatially resolved magnetic resonance spectrum.