Abstract:
A method of assessing a spatial frequency distribution within a sample comprising subjecting the sample to magnetic resonance excitation, receiving an echo signal from the sample while the sample is subjected to a magnetic field gradient, applying an invertible linear transform to the echo signal, identifying a region of interest in the transformed echo signal and deriving a corresponding window function, applying the window function (in the signal or transform domain) to the echo signal to remove echo signal coming from regions of the sample outside of the region of interest, and analyzing the one dimensional spatial frequency content in the windowed echo signal in order to access a one dimensional spatial frequency distribution within the region of interest within the sample without creating an image.

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
       [0001]    This application is a continuation of International Application No. PCT/US2012/068284 filed Dec. 6, 2012 which claims the benefit of U.S. Provisional Patent Application No. 61/567,511 filed Dec. 6, 2011. 
     
    
     BACKGROUND OF THE INVENTION 
       [0002]    1. Field of the Invention 
         [0003]    The present invention relates to the field of fine structures characterized by magnetic resonance and to a method for processing magnetic resonance signals. 
         [0004]    2. Prior Art 
         [0005]    U.S. Pat. No. 7,932,720 describes a method for measurement of biologic textures too fine to be resolved by conventional magnetic resonance imaging, providing a quantitative measure of the characteristic spatial wavelengths of these textures. In its simplest form the method consists of acquiring finely-sampled spatially-encoded magnetic resonance echoes along an axis of a selectively-excited inner-volume positioned within the biologic tissue to be analyzed. Signal analysis yields spectra of textural wavelengths within various sub-regions along the spatially encoded axis of the selected tissue volume. 
         [0006]    Filtering techniques have been used in the prior art to selectively analyze sub-regions (regions of interest) by windowing within the selectively excited internal volume but they are non-linear as the method involves taking the magnitude of the signal to produce a signal intensity as a function of location. This prior art method (U.S. Pat. No. 7,932,720) describes a method wherein the basic steps are as follows:
       1. Subject the sample to a magnetic field;   2. Subject the sample to magnetic resonance excitation;   3. Receive an echo signal from the sample while the sample is subjected to a magnetic field gradient;   4. Fourier transform the echoes and take the magnitude to convert them into a signal intensity versus position,   5. Select a region of interest by multiplying the transformed data by a windowing function;   6. Fourier transform again, converting back into the echo domain;   7. Display the result as the magnitude of the resulting derived spectrum treating it as a measure of frequency content.       
 
         [0014]    While the approach in the &#39;720 patent provides insight into underlying structure, particularly for biological samples, it is limited due to being non-linear and restricted to the use of the nonlinear magnitude function and two Fourier transforms. 
         [0015]    Other prior art methods based on magnetic resonance for analyzing fine textures are similar to that of the &#39;720 patent in that they also are nonlinear as a result of taking the magnitude to generate a signal intensity vs. location. They differ from the &#39;720 patent in that they are based on the analysis of magnetic resonance image data rather than a one dimensional signal intensity. In general the steps used by these methods are as follows:
       1. Receive a multiplicity of echoes (as a result of a 2D or 3D magnetic resonance acquisition sequence),   2. Fourier transform and then take the magnitude of the echoes to convert them into a signal intensity versus position (i.e., create an image or a set of images),   3. Select a region of interest by multiplying the transformed data by a windowing function (wherein the shape and the width have been carefully chosen to optimize the signal extraction without introducing truncation artifacts, and to minimize the decrease in spectral resolution),   4. Use a Fourier or other transform again to convert back into the echo domain which is a measure of frequency content,   5. Display the result as the magnitude of the resulting derived spectra.       
 
     
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0021]      FIG. 1  is an example of a magnetic resonance technique for selectively exciting an internal volume and imposing a one dimensional spatial encode along r. A sub-region of the selectively excited internal volume is indicated by ROI (region of interest). 
           [0022]      FIG. 2  shows an approach described in U.S. Pat. No. 7,932,720 to generate a window function based upon an identified Region of Interest (ROI). 
           [0023]      FIG. 3  shows a linear method utilizing two Fourier transformations and a complex multiplication to localize the signal to a region of interest. 
           [0024]      FIG. 4  shows a Linear method utilizing convolution for filtering an echo signal to localize the signal to a region of interest. 
       
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
       [0025]    This invention is based on the fact that the magnetic resonance echo signal from a one dimensional frequency encoded excitation is nominally the one dimensional Fourier transform of the structure. Furthermore the one dimensional Fourier transform of the structure is the distribution (spectrum) of spatial frequencies and phases contained in the structure. 
         [0026]    The current invention method initially proceeds like that of the &#39;720 patent, namely by:
       1. Subject the sample to a magnetic field;   2. Subject the sample to magnetic resonance excitation;   3. Receive an echo signal from the sample while the sample is subjected to a magnetic field gradient;       
 
         [0030]    However, the current invention although similar to the prior art described in the &#39;720 patent differs in a key and significant way in that the invented method uses only linear signal processes to generate spatial frequency spectra from samples of structure. Taking the magnitude of a complex signal is a non-linear operation, which loses information and introduces artifacts. To avoid these effects, the current invention utilizes a linear set of signal processing steps, which provides significant advantages including the ability to readily calculate noise statistics and an opportunity to further optimize signal to noise. Linear signal processing methods are an improvement over the prior art for a number of reasons including:
       Preserving the Gaussian distribution of the noise component of the echo signal, which facilitates subsequent quantitative analysis in terms of signal-to-noise, as well as providing a basis for quantitative statistical confidence measurements.   Linearity preserves the underlying signal&#39;s complex structure, particularly in the phase space, where position is encoded. In contrast, non-linear processes, particularly magnitude operations, discard useful phase information.   Non-linear analyses can introduce artifacts in the resulting dataset which were not present in the original dataset. In contrast, linear approaches do not.   Through the use of linear transforms, the dataset can be projected into a so-called Transform Domain which can facilitate further analysis and feature identification. These, in turn, can provide direction as to how to best extract signals of interest from the original echo.       
 
         [0035]    In general, the noise received as part of the MR acquisition can be well modeled as complex-valued Additive White Gaussian Noise. 
         [0036]    As part of the MR acquisition process, an echo e[k] sequence of K samples, k=1,2, . . . , K−1, K from MR is frequently modeled as 
         [0000]    
       
      
       e[k]=s[k]+n[k] 
      
     
         [0000]    where s[k] represents the k th  sample value of the signal, and n[k] represents the k th  sample value of the noise received as part of the MR acquisition process. Both the signal and noise sample values are complex-values. The complex-valued nature can be made more explicit as 
         [0000]        e   r   [k]+je   i   [k ]=( s   r   [k]+js   i   [k] )+( n   r   [k]+jn   i   [k] ) 
         [0000]    where the subscript ‘r’ indicates the “real” component”, the subscript ‘i’ indicates the imaginary component, and ‘j’ is the imaginary number √{square root over (−1)}. 
         [0037]    The noise samples are well-modeled as having a Gaussian distribution which are independent, identically distributed, and with zero mean. More specifically, the so-called probability density function of the noise term can be expressed as 
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         [0000]    where σ represents the standard deviation, for any noise sample n r [k] or n i [k], independent of k. Further, the independence of the individual noise terms means that the value of any one of the noise samples has no influence on any of the other noise sample values. 
         [0038]    All of this can be described more concisely in a multivariate probability density function as 
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         [0000]    where n is a 2K dimensional vector (K real values, K imaginary values). 
         [0039]    If then e[k] is subjected to a linear filtering process, the resulting noise distribution is modified, but it remains Gaussian distributed. It can be shown that the resulting multivariate probability density function can be now expressed as 
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         [0040]    Where now Σ represents the covariance matrix, and |Σ| represents its determinant. 
         [0041]    The value of Σ can be calculated with knowledge of the linear filter, and the variance σ 2  of the input noise process. Alternatively, Σ can be estimated, using a variety of well-established estimation algorithms. Note too that the noise distribution is independent of the signal. In other words, aside from shifting the mean of the noise to the value of the signal, the input noise variance and the linear filter determine the noise covariance; it is not affected by the signal. 
         [0042]    The importance of being able to derive the statistics of the noise contribution is a key factor in the use of linear filtering processes, because from these, it is relatively straightforward to quantify post-processing signal-to-noise, error-bars, confidence intervals, and the like. This facilitates the use of structural spectrum analysis in a quantitative sense, which is particularly relevant for e.g. medical applications. 
         [0043]    Finally, while it may be possible to admit certain non-linear processing steps, in addition to contending with the potential distortion of the signal itself due to the non-linearity, an additional challenge is presented in the derivation of the resulting noise distribution, and its associated dependence on the underlying signal. While there are closed-form solutions of the resulting noise distribution for some “simple” non-linear processes, they are almost always dependent upon the underlying signal in some non-trivial manner. In general, noise distributions that result from a non-linear process are frequently intractable and cannot be easily expressed in a closed-form solution. 
         [0044]      FIG. 1  illustrates one method of performing a selective inner volume excitation and spatial encode which produces and echo from the entire inner volume. The inner volume is defined by the intersection of the two slice selective excitations and the bandwidth of the MRI scanner receiver. The Region of Interest (ROI) in this case is a segment of the inner volume which is relevant for the analysis. 
         [0045]      FIG. 2  illustrates one method for identifying a Region of Interest (ROI) from a one dimensional plot of the signal intensity along the selectively excited internal volume (r) and then calculating a window function to filter the echo signal so that the resultant echo contains spatial frequencies exclusively from the ROI. Window functions can be generated in other ways including simply by specifying a value of “r” and window width along the selectively excited inner volume. 
         [0046]      FIG. 3  illustrates one method which can be used to select a specific ROI using a previously derived window function. The complex echo is converted to a generally complex-valued one dimensional profile using the Fourier Transform. The profile ROI is then selected by multiplying it by the previously derived window function. The resulting sequence is then extended in length by prepending and appending a sequence of zeroes which is used to eliminate wrap-around artifacts associated with circular convolution and to provide a “smoother” spectral representation. The resulting sequence is then converted to a generally complex-valued one-dimensional spectrum using the Inverse Fourier Transform. 
         [0047]      FIG. 4  illustrates another method which can also be used to select a specific ROI using a previously derived window function. In this case, the calculated window function is converted to an equivalent impulse response using zero padding followed by a Fourier Transform. The impulse response is then applied to the complex echo either directly using a complex linear convolution, or indirectly through the use of a linear filter whose impulse response is as specified. 
         [0048]    In the above illustrations, the Fourier Transform is used as a means to convert between the echo domain and an associated Transform domain, which in this specific example nominally corresponds to the spatial distribution of the material under study. Then a “Region of Interest” is selected in that Transform domain, then the resulting spectrum is extracted. 
         [0049]    However, both the Transform, and indeed the selection of a “Region of Interest” within that transform space, is not limited to just the selection of a subset of a region of the Fourier Transform of the echo. 
         [0050]    In actuality, any invertible linear transformation can be used as a means to project the echo into a corresponding transform domain. An equivalent Region of Interest within that transform domain can be selected (i.e. windowed), and the residual transformed back into the echo domain, which in turn can be interpreted as the spectrum of the underlying physical representation. 
         [0051]    Some commonly used invertible transforms include various so-called Wavelet Transforms, or z-Transforms. 
         [0052]    The use of transforms can be useful, not only in terms of physical localization, but also for noise reduction as well. 
         [0053]    The present invention is applicable to the assessment of any anatomical structure, whether of hard or soft tissue. Thus the present invention has a number of aspects, which aspects may be practiced alone or in various combinations or sub-combinations, as desired. While a preferred embodiment of the present invention has been disclosed and described herein for purposes of illustration and not for purposes of limitation, it will be understood by those skilled in the art that various changes in form and detail may be made therein without departing from the spirit and scope of the invention as defined by the full breadth of the following claims.