US 20020167316 A1 Abstract A method and apparatus for increasing the signal-to-noise ratio in a magnetic resonance image generated with a system including at least two receiver coils where the data acquisition period is reduced by increasing the space between k-space raster data rows such that image wrapping occurs and an unwrapping algorithm is required, the method including identifying a sensitivities matrix corresponding to the receiver coils, acquiring NMR signals and converting those signals to image pixel intensities, defining a correction matrix, altering the sensitivities matrix as a function of the correction matrix, combining the altered sensitivities matrix and the intensity matrix to generate an estimated spin density matrix and using a spin density matrix to generate the final image.
Claims(19) 1. A method for use with a multiple receiver coil magnetic resonance imaging (MRI) system used to generate a two dimensional slice image through an object where the field of view during data acquisition is smaller than the object cross section to be imaged such that upon transforming acquired k space data into image data, the resulting wrapped images include wrapped image sections where wrapped pixel intensities include intensity from each of a properly located pixel and at least one wrapped pixel, each receiver coil receiving an MRI signal from each location within the object cross section and having a coil specific sensitivity that indicates how the coil reacts to signals from the different points within the slice, the method for increasing the signal to noise ratio of image pixels upon unwrapping of wrapped image sections, the method comprising the steps of, for each pixel in the wrapped images:
identifying the coil sensitivities for each coil in the multiple coil system and arranging the coil sensitivities to form a sensitivities matrix S for the pixel; arranging the intensities from each coil corresponding to the image pixel into an intensity matrix; generating a modified coil sensitivities matrix S′ by modifying sensitivities matrix S; inverting the modified sensitivities matrix; multiplying the inverted matrix by the intensity matrix to generate a spin densities matrix including unwrapped pixel spin densities corresponding to the pixel; and using the spin densities matrix to generate a final image. 2. The method of 3. The method of 4. The method of 5. The method of 6. The method of 7. The method of 8. The method of 9. The method of 10. The method of 11. The method of 12. An apparatus for use with a multiple receiver coil magnetic resonance imaging (MRI) system used to generate a two dimensional slice image through an object where the field of view during data acquisition is smaller than the object cross section to be imaged such that upon transforming acquired k space data into image data, the resulting wrapped image includes wrapped image sections where wrapped pixel intensities include intensity from each of a properly located pixel and at least one wrapped pixel, each receiver coil receiving an MRI signal from each location within the object cross section and having a coil specific sensitivity that indicates how the coil reacts to signals from the different points within the slice, the apparatus for increasing the signal to noise ratio of final image pixels upon unwrapping of at least one wrapped pixel, the apparatus comprising, for each pixel in a wrapped image:
means for identifying the coil sensitivities for each coil in the multiple coil system and arranging the coil sensitivities to form a sensitivities matrix S; means for arranging the intensities corresponding to the pixel into an intensity matrix; means for generating a modified coil sensitivities matrix S′ by modifying sensitivities matrix S; means for inverting the modified sensitivities matrix; means for multiplying the inverted matrix by the intensity matrix to generate a spin densities matrix for final image pixels corresponding to the pixel; and using the spin densities matrix to generate the final image. 13. The apparatus of 14. The apparatus of 15. The apparatus of 16. The apparatus of 17. The apparatus of 18. The apparatus of 19. An apparatus for use with a multiple receiver coil magnetic resonance imaging (MRI) system used to generate a two dimensional slice image through an object where the field of view during data acquisition is smaller than the object cross section to be imaged such that upon transforming acquired k space data into image data, the resulting wrapped image includes wrapped image sections where wrapped pixel intensities include intensity from each of a properly located pixel and at least one wrapped pixel, each receiver coil receiving an MRI signal from each location within the object cross section and having a coil specific sensitivity that indicates how the coil reacts to signals from the different points within the slice, the method for increasing the signal to noise ratio of image sections upon unwrapping of the wrapped image sections, the method comprising, for each pixel in a wrapped image:
identifying the coil sensitivities for each coil in the multiple coil system and arranging the coil sensitivities to form a sensitivities matrix S; arranging the intensities corresponding to the wrapped image pixel from each coil into an intensity matrix; generating a modified coil sensitivities matrix S′ by modifying sensitivities matrix S; inverting the modified sensitivities matrix; multiplying the inverted matrix by the intensity matrix to generate a spin densities matrix for final image pixels corresponding to the wrapped image pixel; and using the spin densities matrix to generate the MR image. Description [0001] Not applicable. [0002] Not applicable. [0003] The field of the invention is nuclear magnetic resonance imaging (“MRI”) methods and systems. More particularly, the invention relates to systems and methods for increasing the signal to noise ratio in MRI images where image data has to be unwrapped during data processing. [0004] When a substance such as human tissue is subjected to a uniform magnetic field (polarizing field B [0005] When utilizing these signals to produce images, magnetic field gradients (G [0006] Thus, the intensity of each pixel in an MR image is generally a function of two factors. First, pixel signal intensity is a function of the spin density m at a point in an object slice being imaged that corresponds to the particular pixel in the image. Second, pixel signal intensity is also a function of the operating characteristics of the receiving coil that receives the NMR signal and converts the signal to an analog signal and then to a digital signal for storage in k-space. Specifically, the coil operating characteristic that affects the end pixel intensity the most is referred to as coil sensitivity s. Thus, intensity i for a pixel y can be expressed by the following Equation: [0007] There are several different factors that can be used to judge the value of any imaging system but two of the most important factors are the quality of the resulting images and the speed with which imaging data can be acquired. Higher quality images increase diagnostic value. Acquisition speed increases system throughput (i.e., the number of imaging sessions that can be performed in a given period) and can also increase image quality as patient movement is reduced when the acquisition period is chortened (i.e., patient movement is less likely during a shorter period than during a longer period. With MRI systems, throughput is extremely important as MRI systems are relatively expensive and the expense is in part justified by the amount of use a system receives. [0008] One way to increase system throughput is to reduce the amount of data collected during an imaging session. For example, one way to reduce the amount of collected data is to increase the space between phase encoding lines in k-space. Referring to FIG. 3, an exemplary k-space raster [0009] By reducing the number of phase encoding lines employed during data acquisition, the field of view (FOV) along the phase encoding axis Y of the resulting image is also reduced. Referring again to FIG. 3, the FOV for the image [0010] Unfortunately, where the object being imaged extends outside the reduced FOV, the image sections that correspond to the out-of-FOV object sections “wrap around” on the image and are overlaid on other image sections. Thus, in FIG. 3, out-of-FOV image sections [0011] Where the reduction factor R is greater than 2 additional image wrapping can occur thereby causing wrapped image pixels to include intensity corresponding to more than two (e.g., 3, 4, etc.) unwrapped pixels. This additional wrapping further reduces the diagnostic value of the resulting image. [0012] The industry has devised ways to effectively “unwrap” wrapped images like the exemplary image in FIG. 3. It has been recognized that by providing several NMR signal receiving coils where the sensitivities of each coil are known, a permutation of Equation 1 above can be used to separate the intensity of a wrapped pixel into the in-FOV intensity and the out-of-FOV intensity. To this end, along a phase encoding axis the intensity of a wrapped pixel y corresponding to first and second receiver coils can be expressed as: [0013] respectively, where D is the phase encoding FOV (see FIG. 3). [0014] Referring still to Equations 2 and 3, assuming that the sensitivities s [0015] By increasing the reduction factor R, the amount of data acquired is reduced and therefore throughput is accelerated. The number of unknowns, however, that can be resolved in any system is equal to the number of separate receiver coils in the system. Thus, in any given system the maximum reduction factor R is equal to the number of receiver coils N. For example, in the exemplary system described above that includes four receiver coils the maximum reduction factor R is 4. [0016] In general terms, the intensity of a particular wrapped pixel y with a reduction factor R can be expressed by the equation:
[0017] where j refers to coil number and s [0018] In a system including N coils, intensity, spin density and sensitivity matrices I, M and S can be defined as having dimensions N×1, R×1 And N×R, respectively, and Equation 4 can be rewritten in matrix form as: [0019] Again, assuming S is known, S can be inverted and Equation 5 can be rewritten and solved for an estimated spin density M as: [0020] A solution of Equation 6 that can be relied upon should minimize the spin density estimate error. Thus, a typical solution to Equation 6 minimizes |S{circumflex over (M)}−I| [0021] where + denotes the Hermitian conjugate. [0022] Obviously the value of the solution to Equation 7 is only as good as the preciseness with which the sensitivities of the coils can be determined. Unfortunately, while the industry has devised several ways to determine coil sensitivities, there are many factors that affect sensitivities such that noise often occurs upon inversion of the sensitivity matrix S that propagates and is exacerbated in resulting images. Thus, while solving Equation 7 in theory provides a way to unwrap image data, in practice the resulting image has a relatively low signal to noise ratio (SNR). [0023] The present invention is a method for reducing the noise in an unwrapped image by modifying the coil sensitivity matrix and using the modified matrix instead of the original matrix to determine the spin densities of image pixels by solving an equation similar to Equation 7 above. [0024] More specifically, one way to increase the SNR is to minimize the function A({circumflex over (M)})+λB({circumflex over (M)}) where A({circumflex over (M)})=|S{circumflex over (M)}−I| [0025] Because high noise often results in large pixel values a simple solution to Equation 8 is to minimize the magnitude of {circumflex over (M)} so that B({circumflex over (M)})={circumflex over (M)} [0026] Upon solving Equation 9 the resulting spin density estimates {circumflex over (M)} can be used to generate an unwrapped image with relatively high SNR. [0027] In addition to several methods the invention also includes an apparatus for performing each of the methods. [0028] These and other aspects of the invention will become apparent from the following description. In the description, reference is made to the accompanying drawings which form a part hereof, and in which there is shown a preferred embodiment of the invention. Such embodiment does not necessarily represent the full scope of the invention and reference is made therefore, to the claims herein for interpreting the scope of the invention. [0029]FIG. 1 is a schematic view of a MR imaging system that performs the method of FIG. 5; [0030]FIG. 2 is a schematic view of a k-space raster and a resulting image; [0031]FIG. 3 is similar to FIG. 2, albeit illustrating a k-space raster with relatively greater space between k-space data rows and a resulting reduced FOV image; [0032]FIG. 4 is a schematic view of a receiver coil configuration, an imaging plane and an enlarged point within the imaging plane; [0033]FIG. 5 is a flow chart illustrating an exemplary method according to the present invention; [0034]FIG. 6 is a flow chart illustrating a manual method for identifying image sectors having disparate replicates; and [0035]FIG. 7 is a flow chart similar to FIG. 6, albeit being an automated method. [0036] Referring first to FIG. 1, there is shown the major components of an exemplary MRI system that incorporates the present invention. Operation of the system is controlled from an operator console [0037] The system control [0038] Pulse generator module [0039] The gradient waveforms produced by pulse generator module [0040] Referring also to FIG. 4, the exemplary magnet assembly [0041] To this end, each of coils [0042] Referring to FIG. 2, where a large number of k-space rows of data [0043] Referring now to FIG. 5, an exemplary inventive method [0044] Continuing at block [0045] Because the magnetic resonance characteristics of the test object are known, the spin densities of the materials that form the object are known. Therefore, referring to equation 1 above, after the test images corresponding to each coil are completed and pixel intensities have been determined, Equation 1 can be solved for sensitivity s (i.e., each of intensities i and spin density m are known) and therefore the sensitivities corresponding to each coil for each point within the imaging space inside the imaging volume can be determined. At block [0046] Referring still to FIGS. 1 and 5, after commissioning has been completed and the sensitivities matrices S have been formed, a data acquisition procedure can commence. At process block [0047] At process block [0048] At process block [0049] At block [0050] At block [0051] The exemplary method described above improves SNR substantially, especially at the maximum acceleration factor where reduction factor R is equal to the number of receiver coils N in an imaging system. During testing of a system using the method described above where the reduction factor R was set to 4, it was determined that a reasonable trade-off between SNR and uncorrected aliasing was achieved with a scalar value λ set equal to 10 [0052] Referring again to FIG. 3, it should be appreciated that in a wrapped image certain parts of the image will include more noise than other image parts. For example, wrapped image section [0053] Because noise in pixels including greater numbers of replicates is relatively higher than in pixels including lesser numbers of replicates, an optimal system should attenuate the noise to a greater degree when unwrapping higher replicate pixels than when unwrapping lower replicate pixels. [0054] To this end, according to one embodiment of the invention boundaries of objects within a wrapped image are determined so that image areas including higher numbers of replicates and hence higher noise can be distinguished from areas of lower relative noise (i.e., lower number of replicates). Thereafter different scalar λ values can be set or automatically selected for the areas of low and high relative noise so that, upon unwrapping the SNR throughout the resulting image is similar. [0055] Referring to FIG. 6, a method [0056] At block [0057] At block [0058] At block [0059] While the manual process above for identifying image sections can be used, other more automated processes can be used. For example, given the reduction factor R, processor [0060] One automated method [0061] A similar process is performed to identify space [0062] In the present example, after identifying the separate sections [0063] It should be understood that the methods and apparatuses described above are only exemplary and do not limit the scope of the invention, and that various modifications could be made by those skilled in the art that would fall under the scope of the invention. [0064] To apprise the public of the scope of this invention, the following claims are made: Classifications
Legal Events
Rotate |