Dynamic B0 field detection by magnetic resonance navigators, and correction for multichannel reception and/or transmission RF coil configurations

1. Field of the Invention

The present invention concerns methods and devices for correcting four field inhomogeneities in the basic magnetic field (B 0 ) field in magnetic resonance imaging systems, particularly in such imaging systems using a multichannel reception and/or transmission RF (radio-frequency) coil configuration.

2. Description of the Prior Art

Functional magnetic resonance imaging (fMRI) is implemented by repeatedly acquiring image volumes, particularly of the brain, with fast imaging sequences such as echo-planar imaging (EPI) or spiral imaging. A sequence known as BOLD (Blood Oxygen Level Detection) generates a so-called BOLD signal that changes dependent on the oxygen level in blood in the detected region, this oxygen level, in turn being indicative of brain activity in the region. The detection of changes in the BOLD signal, which includes changes in Two*, CBF and CBV, relies on a statistical analysis of the time series implemented for each voxel in the examination region. For example, correlation analysis or General Linear Model (GLM) analysis of the time series with the paradigm that is employed (e.g., active and baseline conditions) convoluted with a hemodynamic response function is a basic procedure for fMRI. The underlying assumption is the stability of the measured signal in the spatial domain as well as in the temporal domain. Such preconditions are valid as well for other fast imaging applications, such as diffusion imaging and perfusion imaging.

Spatial stability can be disturbed by gross subject motion, and many techniques are known for correcting for spatial instability.

Temporal stability is maintained by fitting theoretical model functions of drifts (e.g., sine expansion terms) to the voxel-based time courses. Global frequency changes in the magnetic resonance system (Dynamic Off-Resonance changes in K-space, DORK) also can be monitored and corrected. Physiological signals such as respiration and heartbeat can be recorded by extracorporeal devices, and used as regressors in the fMRI analysis, such as in the GLM statistics.

Static and dynamic image deterioration in EPI images and spiral images has its source in a non-uniform B 0 field, typically caused by the object itself brought into the B 0 field (static B 0 field distortion) or by external dynamic changes (dynamic B 0 field change) caused by physiological changes, movement of the object, or system instabilities.

Mapping of the B 0 field is a known technique resulting in B 0 field maps, which are translated into image distortion maps or voxel displacement maps that are used for image correction in the image processing procedures that are employed.

The measurement of a high-quality B 0 field map, however, requires at least multiple scan repetitions (TRs) lasting between 6 and 10 seconds a piece, and often resulting in a mapping procedure lasting between 1 and 2 minutes. These additional sources for dynamic noise and image deterioration hamper the detection of reliable MR images (fMRI, DWI, perfusion) and therefore it is essential to monitor such sources and to take their effect into consideration in the image correction, for example in the statistical analysis of and fMRI series. These noise sources exist in real time, and can be directly used for image correction during the progress of the data acquisition (in-line). Most often, however, more complicated statistical analysis is implemented after the measurement (data acquisition) has been completed (off-line post-processing).

Examples of known procedures for correction of temporal change due to physiological noise are described in “Retrospective Estimation and Correction of Physiological Artifacts in fMRI by Direct Extraction of Physiological Activity from MR Data,” Le et al., Magnetic Resonance in Medicine, Vol. 35, No. 3 (1996) pgs 290-298; “image-Based Method for Retrospective Correction of Physiological Motion Artifacts in fMRI: RETROICOR,” Glover et al., Magnetic Resonance in Medicine, Vol. 44, No. 1 (2000) pgs 162-167; “Functional MR Imaging in the Awake Monkey: Effects of Motion on Dynamic Off-Resonance and Processing Strategies,” Pfeuffer et al., Magnetic Resonance in Medicine, Vol. 25, No. 6 (2007) pgs 869-882 and “Correction of Physiologically Induced Global Off-Resonance Effects in Dynamic Echo-Planar and Spiral Functional Imaging,” Pfeuffer et al., Magnetic Resonance in Medicine, Vol. 47 (2002) pgs 344-353. EPI distortion correction (static and dynamic) is described in “Real-Time Autoshimming for Echo Planar Timecourse Imaging,” Ward et al. Magnetic Resonance in Medicine, Vol. 48 (2002) pgs 771-780; “Point Spread Function Mapping with Parallel Imaging Techniques and High Acceleration Factors: Fast, Robust, and Flexible Method for Echo-Planar Imaging Distortion Correction, Zaitsev et al., Magnetic Resonance in Medicine, Vol. 52 (2004) pgs 1156-1166 and Correction for Geometric Distortion and N/2 Ghosting in EPI by Phase Labeling for Additional Coordinate Encoding (PLACE),” Xiang et al. Magnetic Resonance in Medicine, Vol. 57 (2007) pgs 731-741.

It is an object of the present invention to improve B 0 mapping for use in image correction and/or recalculation of imaging parameters from scan repetition-to-scan repetition in magnetic resonance data acquisition procedures using a multichannel RF coil configuration for transmission (emitting) RF excitation signals and/or receiving the resulting RF signals following excitation.

This object is achieved in accordance with the present invention by using navigators received from each of the respective channels (or at least multiple channels among the totality of respective channels) for generating the B 0 map. An additional spatial selection (localization) of the signal from each individual RF coil is thereby achieved. This is then combined with navigator signal artifact detection. In accordance with the present invention, spatial encoding in the navigator itself is not needed in order to be able to obtain a spatial map. Instead, the necessary spatial information is obtained from the respective multiple coils in the multichannel coil configuration.

FIG. 1 schematically illustrates an embodiment of a multichannel magnetic resonance (MR) coil array of the type suitable for use in accordance with the present invention.

FIG. 2A schematically illustrates the use of a navigator in the context of an echo planar imaging (EPI) sequence.

FIG. 2B schematically illustrates the use of a navigator in a spiral imaging sequence.

FIG. 3A schematically illustrates the generation of a B 0 field map in accordance with the invention for off-line image correction.

FIG. 3B schematically illustrates the use of B 0 field map in accordance with the invention for a perspective image acquisition correction.

FIG. 4 schematically illustrates corrections that can be made in accordance with the invention using a B 0 field map from repetition-to-repetition in a multi-repetition data acquisition procedure.

FIG. 5 schematically illustrates the generation of a B 0 field map in accordance with the invention to correct four dynamic B 0 field changes.

FIG. 1 schematically illustrates an example of a multichannel RF coil configuration of the type used as a transmission or reception coil for magnetic resonance data acquisition. The multichannel coil array in this embodiment has 32 channels, respectively formed by individual coils of the array arranged in successive annular rings around the generally cylindrical overall configuration. Individual coils 1 . 1 , 1 . 2 , 1 . 3 , 1 . 4 . . . 1 . 8 are shown that form one annular ring, and successive annular rings are also present, designated respectively by individual coils 2 . 1 , 3 . 1 and 4 . 1 .

FIG. 2A schematically illustrates the known use of a navigator in combination with an echo-planar imaging (EPI) sequence, wherein the navigator and an associated gradient are emitted (activated) following RF excitation, possibly with a slice selective gradient. Image acquisition takes place by signal sampling with a gradient of alternating polarity.

In the conventional use of B 0 mapping by means of a navigator in EPI, it is necessary to obtain spatial information from the navigator itself, thereby making the signal acquisition and/or the computational procedures more complicated and possibly more time consuming.

Another known technique making use of a navigator for B 0 mapping is spiral imaging, as schematically illustrated in FIG. 2B . In the case of spiral imaging, the navigator is embedded (a part of) the signal sampling, rather than a separately, earlier-emitted signal.

In accordance with the invention, echoes from the navigator are acquired individually with at least some, and preferably all, of the individual coils of the multichannel coil array. As in the case of parallel imaging, for example, the sensitivity profile of each of these individual coils is known in advance, such as by a determination made in a calibration procedure. In accordance with the invention, the navigator echoes that are individually received by the respective individual coils of the coil array provides the necessary spatial information for using the navigator echoes to formulate a B 0 map.

As schematically indicated in FIG. 3A , the B 0 field map obtained in this manner in accordance with the invention can be used in an off-line correction of the image data, implemented during image reconstruction (post-processing) that follows the completion of the MR image acquisition procedure.

As schematically illustrated in FIG. 3B , the B 0 field map in accordance with the invention can alternatively or additionally be used to make an immediate prospective correction in the image acquisition that follows the navigator echo and the formulation of the B 0 field map.

Moreover, as shown in FIG. 4 , such a correction using the B 0 field map produced in accordance with the invention from the multichannel coil configuration can be used to make corrections in successive repetitions in a multi-repetition data acquisition procedure. As shown in FIG. 4 , MR data and navigator echoes acquired in a first repetition TR 1 , implemented in a multichannel MR system, to generate a B 0 field map, and the B 0 field map can then be used to implement a correction in the next repetition TR 2 . This procedure can be repeated for each subsequent repetition, as desired. The correction can be a change in the frequency or the shimming, or the RF pulse in the next excitation can be newly calculated based on the B 0 field map.

Another example is schematically illustrated in FIG. 5 , for the purpose of making corrections in a B 0 field that exhibits dynamic changes, as schematically illustrated in the upper portion of FIG. 5 . When multiple slices S 1 , S 2 . . . S n are acquired from an examination subject, each in multiple repetitions TR 1 , TR 2 . . . , a sliding window calculation of the B 0 field map can be implemented. The first calculation, for example, can be based only on the slices acquired in the first repetition, and then the window can be moved to eliminate, from the B 0 field map calculation, one or more slices from the repetition TR 1 , while including an equal number of slices from the next repetition TR 2 , and so on.

Although modifications and changes may be made by those skilled in the art, it is the intention of the inventor to embody within the patent warranted hereon all changes and modifications as reasonably and properly come within the scope of his contribution to the art.