Abstract: Eddy current fields in a magnetic resonance imaging (MRI) system are mapped by acquiring MRI data from an object located in an imaging volume of the MRI system. An MRI data acquisition sequence is preceded by a pre-sequence including (a) a gradient magnetic field transition that stimulates eddy current fields in the MRI system, and (b) a spatial modulation grid tag module that sensitizes a spatially resolved MR image of the acquired MRI data to the stimulated eddy current fields that existed during the spatial modulation grid tag module. The eddy-sensitized MR image is processed to calculate a spatially resolved map of fields produced by the eddy currents.

Abstract: An MRI MAP prescan data from a predetermined imaged patient volume is decomposed to produce a transmit RF field inhomogeneity map and a receive RF field inhomogeneity map for the imaged patient volume based on a three-dimensional geometrical model of the inhomogeneity maps. At least one of the transmit RF field inhomogeneity map and the receive RF field inhomogeneity map is used to generate intensity-corrected target MRI diagnostic scan image data representing the imaged patient volume.

Abstract: Magnetic resonance imaging (MRI) produces an image representative of flowing nuclei within a subject. For each of plural MRI data acquisition sequences, a non-contrast pulsed ASL (arterial spin labeling) pre-sequence is applied to flowing nuclei in a tagging region during a tagging period (that occurs prior to MRI data acquisition from a selected downstream image region). The ASL pre-sequence includes plural different elapsed tagging times at which a radio frequency (RF) nuclear magnetic resonant (NMR) nutation tagging pulse occurs or does not occur in accordance with different predetermined patterns for corresponding different data acquisition sequences. Acquired MRI data is decoded in accordance with such predetermined patterns to detect MRI signals emanating from different cohorts of flowing nuclei that have been subjected to different combinations of nutation pulses. Acquired MRI data is used to reconstruct at least one image representing flowing nuclei within the selected image region.

Abstract: Frequency filtering of spatially modulated or “tagged” MRI data in the spatial frequency k-space domain with subsequent 2DFT to the spatial domain and pixel-by-pixel arithmetic calculations provide robust data that can be used to derive B1 and/or B0 maps for an MRI system.

Abstract: Magnetic resonance imaging (MRI) produces an image representative of flowing nuclei within a subject. For each of plural MRI data acquisition sequences, a non-contrast pulsed ASL (arterial spin labeling) pre-sequence is applied to flowing nuclei in a tagging region during a tagging period (that occurs prior to MRI data acquisition from a selected downstream image region). The ASL pre-sequence includes plural different elapsed tagging times at which a radio frequency (RF) nuclear magnetic resonant (NMR) nutation tagging pulse occurs or does not occur in accordance with different predetermined patterns for corresponding different data acquisition sequences. Acquired MRI data is decoded in accordance with such predetermined patterns to detect MRI signals emanating from different cohorts of flowing nuclei that have been subjected to different combinations of nutation pulses. Acquired MRI data is used to reconstruct at least one image representing flowing nuclei within the selected image region.

Abstract: A magnetic resonance imaging (MRI) system is used to produce an image representative of the vasculature of a subject by applying a non-contrast MRI pulse sequence to acquire MRI k-space data from non-stationary nuclei flowing in a selected spatial region of a subject after nuclei within the region have been subjected to spatially non-uniform pre-saturation of nuclear magnetic resonance (NMR) magnetization. Such pre-saturation suppresses subsequent MRI signals emanating from background nuclei located within said region during said pre-saturation, while enhancing MRI signal from flowing nuclei therewithin as a function of speed, slice thickness and elapsed time until image capture as a function of the spatially shaped profile of non-uniform pre-saturation across the imaged volume. Thus, acquired MRI k-space data can then be used to reconstruct an image representing vasculature of the subject.

Abstract: An MRI MAP prescan data from a predetermined imaged patient volume is decomposed to produce a transmit RF field inhomogeneity map and a receive RF field inhomogeneity map for the imaged patient volume based on a three-dimensional geometrical model of the inhomogeneity maps. At least one of the transmit RF field inhomogeneity map and the receive RF field inhomogeneity map is used to generate intensity-corrected target MRI diagnostic scan image data representing the imaged patient volume.

Abstract: A variable flip angle (VFA) MRI (magnetic resonance imaging) spin echo train is designed and/or implemented. For example, a target train of detectable spin-locked NMR (nuclear magnetic resonance) echo signal amplitudes may be defined and a corresponding designed sequence of variable amplitude (i.e., variable NMR nutation angle) RF refocusing pulses may be determined for generating that target train of spin echoes in an MRI sequence (e.g., used for acquiring MRI data for a diagnostic imaging scan or the like). Such a designed VFA sequence may be output for study and/or use by an MRI system sequence controller.

Abstract: When performing repetitive scans of a patient using a magnetic resonance imaging machine or the like, patients often tend to move as they relax during a lengthy scanning session, causing movement in the volume or portion of the patient being scanned. A prospective motion correction component accounts for patient movement by calculating transformation data representative of patient movement in multiple planes, as well as rotational movement, and a host evaluates the change in position relative to a most recent scanning geometry of the patient or dynamic volume. In this manner, correction or adjustment to the scanning geometry employed by an associated scanner is made only for the differential between the current geometry and the most recent geometry, to mitigate redundant adjustment that can result in oscillatory over—and under—compensation during adjustments.

Abstract: An MRI MAP prescan data from a predetermined imaged patient volume is decomposed to produce a transmit RF field inhomogeneity map and a receive RF field inhomogeneity map for the imaged patient volume based on a three-dimensional geometrical model of the inhomogeneity maps. At least one of the transmit RF field inhomogeneity map and the receive RF field inhomogeneity map is used to generate intensity-corrected target MRI diagnostic scan image data representing the imaged patient volume.

Abstract: An MRI MAP prescan data from a predetermined imaged patient volume is decomposed to produce a transmit RF field inhomogeneity map and a receive RF field inhomogeneity map for the imaged patient volume based on a three-dimensional geometrical model of the inhomogeneity maps. At least one of the transmit RF field inhomogeneity map and the receive RF field inhomogeneity map is used to generate intensity-corrected target MRI diagnostic scan image data representing the imaged patient volume.

Abstract: Frequency filtering of spatially modulated or “tagged” MRI data in the spatial frequency k-space domain with subsequent 2DFT to the spatial domain and pixel-by-pixel arithmetic calculations provide robust ratio values that can be subjected to inverse trigonometric functions to derive B1 maps for an MRI system.

Abstract: A variable flip angle (VFA) MRI (magnetic resonance imaging) spin echo train is designed and/or implemented. For example, a target train of detectable spin-locked NMR (nuclear magnetic resonance) echo signal amplitudes may be defined and a corresponding designed sequence of variable amplitude (i.e., variable NMR nutation angle) RF refocusing pulses may be determined for generating that target train of spin echoes in an MRI sequence (e.g., used for acquiring MRI data for a diagnostic imaging scan or the like). Such a designed VFA sequence may be output for study and/or use by an MRI system sequence controller.

Abstract: Frequency filtering of spatially modulated or “tagged” MRI data in the spatial frequency k-space domain with subsequent 2DFT to the spatial domain and pixel-by-pixel arithmetic calculations provide robust data that can be used to derive B1 and/or B0 maps for an MRI system.

Abstract: Frequency filtering of spatially modulated or “tagged” MRI data in the spatial frequency k-space domain with subsequent 2DFT to the spatial domain and pixel-by-pixel arithmetic calculations provide robust ratio values that can be subjected to inverse trigonometric functions to derive B1 maps for an MRI system.

Abstract: When scanning a patient to generate an image thereof, radio frequency (RF) coil modules are scalably coupled to each other using a plurality of clips to form flat or polygonal coil arrays that are placed on or around the patient or a portion thereof. A user assesses the volume to be imaged, identifies a coil array configuration of suitable size and shape and employs clips of one or more pre-determined angles to construct the identified coil array configuration, which is placed on or about the volume. Coil modules are coupled to a preamplifier interface box (PIB), which provides preamplified coil signal(s) to a patient imaging device, such as an MRI scanner. Small arrays are constructible to accommodate pediatric patients and/or smaller animals. Modules are hermetically sealed, can be sanitized between uses, and discarded at end-of-life. In one aspect, the modular coil array, clips, and PIB are maintained in an isolated contamination zone, separate from the patient imaging device.

Abstract: In a magnetic resonance imaging method, inner radial readout lines (100, 200, 300, 400) in an inner portion (102, 202, 302, 402) of k-space are acquired using a first readout magnetic field gradient profile (120, 220, 320, 420). Outer radial readout lines (104, 204, 304, 404) in an outer portion (106, 206, 306, 406) of k-space disposed substantially outside of the inner portion of k-space are acquired using a second readout magnetic field gradient profile (124, 224, 324, 424) different from the first readout magnetic field gradient profile. The acquired inner and outer radial readout lines are reconstructed to produce a reconstructed image.

Abstract: In a magnetic resonance imaging apparatus, a sensor (120, 122, 124, 126, 130) measures a displacement of a feature of interest. A magnetic resonance imaging scanner (10) acquires radial readout lines of magnetic resonance imaging data. A reconstruction processor (58) reconstructs the acquired readout lines into reconstructed image data A coordinating processor (134, 140) coordinates a direction of a radial readout line with the determined displacement. The coordinating processor (134, 140) biases at least one of the magnetic resonance imaging scanner (10) and the reconstruction processor (58) toward a selected relationship between readout magnetic field gradient direction and the determined displacement of the feature of interest.

Abstract: A magnetic resonance scanner includes a main magnet (20) that generates a static magnetic field at least in a scanning region (14), and a gradient system (26, 28) that selectively imposes selected magnetic field gradients on the static magnetic field at least in the scanning region. A structure (40) is provided for supporting a plurality of small subjects (80) in the scanning region. The structure includes a plurality of subject supports (82, 82?) each configured to support a small subject, and a plurality of solenoid coils (44, 44?, 44?) corresponding to the plurality of subject supports. Each solenoid coil is arranged with the corresponding subject support to operatively couple with a small subject supported by the corresponding subject support.

Abstract: When performing repetitive scans of a patient using a magnetic resonance imaging machine or the like, patients often tend to move as they relax during a lengthy scanning session, causing movement in the volume or portion of the patient being scanned. A prospective motion correction component (64) accounts for patient movement by calculating transformation data representative of patient movement in multiple planes, as well as rotational movement, and a host (38, 122) evaluates the change in position relative to a most recent scanning geometry of the patient or dynamic volume. In this manner, correction or adjustment to the scanning geometry employed by an associated scanner (10) is made only for the differential between the current geometry and the most recent geometry, to mitigate redundant adjustment that can result in oscillatory over- and under-compensation during adjustments.