Super-resolution processing is performed on an MRI image by using an NMR signal as a point spread function (PSF) . Image processing of increasing a resolution is performed on a reconstructed image by using the point spread function. The point spread function is a signal obtained by, after a phantom disposed in an imaging space is irradiated with a high-frequency magnetic field, acquiring a nuclear magnetic resonance signal from the phantom without applying frequency encoding and phase encoding, and performing Fourier transform on the acquired nuclear magnetic resonance signal.

Systems and methods for performing ungated magnetic resonance imaging are disclosed herein. A method includes producing magnetic resonance image MRI data by scanning a target in a low magnetic field with a pulse sequence having a spiral trajectory; sampling k-space data from respective scans in the low magnetic field and receiving at least one field map data acquisition and a series of MRI data acquisitions from the respective scans; forming a field map and multiple sensitivity maps in image space from the field map data acquisition; forming target k-space data with the series of MRI data acquisitions; forming initial magnetic resonance images in the image domain by applying a Non-Uniform Fast Fourier Transform to the target k-space data; and forming reconstructed images with a low rank plus sparse (L+S) reconstruction algorithm applied to the initial magnetic resonance images.

Devices, systems, and methods for enhancing MRI image quality and tracking accuracy in MR-guided treatment systems are described.

A computer-implemented magnetic resonance image optimisation method is disclosed. An image of an object is mapped using a static magnetic field and divided into a plurality of voxels. Each voxel is represented in a Euclidean n-dimensional space, where n≥3, and clustered by grouping together voxels having similar characteristics to create homogenous clusters. The centre or centroid of each cluster is determined, and used, or the voxel closest to either the centre or the centroid is used, as a super-voxel in an optimisation procedure. An optimised diagnostic image of the object is then generated.

A magnetic resonance tomography unit and a method is provided in which a patient couch may be moved in relation to the longitudinal direction into the patient tunnel in the transversal direction into a left-hand side extreme position and an opposite-lying right-hand side extreme position. Using an image acquisition facility in the left-hand side extreme position a right-hand side part is acquired and in the right-hand side extreme position a left-hand side part of the outer contour of the predetermined object is acquired. Using the image acquisition facility, the outer contour of the object is subsequently created from the left-hand side part of the outer contour and also from the right-hand side part of the outer contour.

Some embodiments of the present disclosure disclose systems and methods for robust magnetic resonance image reconstruction that can model for all or nearly all components in the magnetic resonance imaging system, that possess compressibility features to speed up reconstructions, and that can be optimized such that the reconstruction can be performed within a short period of time.

The devices, systems, and methods can improve magnetic resonance imaging (MRI), MR spectroscopy (MRS), MR spectroscopic imaging (MRSI) measurement(s), thereby providing more reliable quantification. The method may include a method for correcting MR image(s)/spectrum. The method may include providing an inhomogeneity field/response map of a region of interest; and providing MR image(s)/spectrum of the region of interest. The method may include determining an intravoxel/voxel inhomogeneity correction coefficient for each voxel of at least one subregion of the region of the interest using the inhomogeneity field/response map. The method may include correcting each voxel of the MR image(s)/spectrum of the region of interest using the intravoxel/voxel inhomogeneity correction coefficient. The MR image(s)/spectrum may include chemical exchange saturation transfer (CEST)/magnetization transfer (MT) imaging with Z-spectrum, CEST/MT imaging without Z-spectrum, CEST spectroscopy, CEST MRS, MRS, MRSI, or any combination thereof.

A training method for training neural networks to determine a magnetic susceptibility distribution of a sample may include: storing a simulated magnetic susceptibility map of the sample, generating a modified magnetic susceptibility map by combining an influence of one or more external magnetic susceptibility sources with the simulated magnetic susceptibility map and storing the modified magnetic susceptibility maps. The method may include generating a first training image by applying a quantitative susceptibility mapping model the modified magnetic susceptibility map and storing the first training image, applying the first neural network to the first image and a second neural network to an output of the first neural network and changing network parameters of the first and the second neural network depending on a deviation of an output of the second artificial neural network from the simulated magnetic susceptibility map.

In order to improve fat saturation in magnetic resonance technology (MRT) methods, a method for spectral saturation that includes specifying or ascertaining a first resonance frequency of a first substance and a first saturation frequency for a second substance is provided. A saturation pulse that causes no saturation of the first substance at the first resonance frequency is generated. The saturation pulse has a first spectral peak for saturation of the second substance at the first saturation frequency and a second spectral peak at a second saturation frequency. This allows a widening of a spectral saturation bandwidth of a dynamic saturation.

In a method for automatic control of an examination sequence in magnetic resonance (MR) system during recording of MR signals in an examination segment of a person being examined, which has two tissue components with two different MR resonant frequencies, an examination sequence for examination of the examination segment is determined. Further, whether the examination sequence includes an imaging sequence in which one of the two tissue components is to be suppressed and for which at least two different suppression options exist to reduce the one of the two tissue components during the recording of the MR signals is determined. In response to the determination that the examination sequencing included the imaging sequence, the method can include determining a sequence parameter of the examination for the imaging sequence; and selecting one of the at least two suppression options as a function of the sequence parameter determined for the imaging sequence.