Magnetic resonance imaging methods and apparatus

Abstract: An incomplete set (42, 44, 42′, 44′) of magnetic resonance image data is collected and stored in a view memory (40). The incomplete set of image data includes a central or first set of data values (42, 42′) and a side or second set of data values (44, 44′). The central data set (42, 42′) is operated on by a roll-off filter (64) and a Fourier transform means (66) to create a normalized phase map (72). The first and second data sets (42, 42′, 44, 44′) are Fourier transformed by means (82) and phase corrected by being multipled by means (86) with a complex conjugate (88) of the corresponding phase map (72) data value to produce a first phase corrected image representation (f1(x,y)e -i(x,y) ). A third data set (46, 46′) is generated by means (90) by determining the complex conjugate (F*(kx,ky)) of the second or side data set (44, 44′). The third data set (46, 46′) is Fourier transformed by means (94) and multipled by means (98) by a corresponding value from the phase map (72) to produce a second phase corrected image representation (f2(x,y)e +i(x,y) ). The first and second phase corrected image representations are summed by means (100) and stored in a resultant image (f(x,y)) memory (102).

Description: This invention relates to magnetic resonance imaging methods and apparatus. More especially, the invention relates to medical diagnostic magnetic resonance imaging methods and apparatus and finds particular application in conjunction with Fourier transform imaging and will be described with particular reference thereto. It is to be appreciated, however, that the present invention may also find application in other imaging and spectroscopy techniques in which only a partial or incomplete data set is available. Heretofore, medical diagnostic magnetic resonance imaging has included the sequential pulsing of radio frequency signals and magnetic field gradients across a region to be imaged. In two dimensional imaging, a patient is disposed in a region of interest in a substantially uniform main magnetic field. An RF excitation pulse is applied as a slice select gradient is applied across the field to select a slice or other region of the patient to be imaged. A phase encode gradient is applied along one of the axes of the selected slice to encode material with a selected phase encoding. In subsequent repetitions of the pulse sequence, the phase encode gradient is stepped in regular intervals from a negative maximum phase encode gradient through a zero phase encode gradient to a positive maximum phase encode gradient. Theoretically, the pair of views corresponding to positive and negative phase encode gradients have a symmetric relationship. However, in practice the symmetry relationship is rendered unpredictable by sequence and field dependent phase considerations and in order to overcome these difficulties, conventionally both positive and negative phase encode views are collected in order to form a phase independent magnitude image. Magnetization manipulation pulses are applied to cause a magnetic resonance echo. During the echo following each pulse sequence, one set of data points, generally termed a view or step, is sampled. The data points within each view correspond to a preselected range of frequencies fo ± Δ f, where fo is the frequency of the center data value of the view. For the zero phase encoding view, a datum frequency fo + Δ f₁ is related to that of fo - Δ f₁. The data values for a positive phase encode view corresponding to a frequency fo + Δ f₁ are also related to the corresponding negative phase encode view at frequency fo - Δ f₁ by conjugate symmetry. In this manner, each data point in k space is related to another point by the underlying property of conjugate symmetry. The complete set of views is operated on by a two dimensional inverse Fourier transform to derive an image representation. Other known systems have reconstructed images utilizing only half a set of views, i.e. only the positive views or only the negative views. In one such half data reconstruction, about eight additional views were collected adjacent the zero or minimum phase encoding. The sixteen central views about the zero phase encoding were utilized to derive a phase map. The acquired data was filtered and the data set was completed by filling with zeros. The Fourier transform of this data set was then phase corrected by the phase map to yield the final reconstruction. However, this technique produced less than satisfactory images which were particularly sensitive to artifacts caused by motion-induced errors in phase. It is an object of the present invention to provide a magnetic resonance imaging method and apparatus wherein this problem is overcome. According to a first aspect of the present invention there is provided a method of magnetic resonance imaging comprising the steps of: (a) exciting magnetic resonance of nuclei in an image region; (b) after each excitation of magnetic resonance, causing a magnetic resonance echo during which a magnetic resonance echo signal is generated; (c) applying a phase encode gradient between a maximum positive phase encode gradient (G max) and a maximum negative phase encode gradient (- G max) such that the resultant magnetic resonance echo signal is phase encoded in accordance with the phase encode gradient; and (d) quadrature detecting and digitizing the magnetic resonance echo signal to create a view of digital data values, characterised by the steps of: (e) repeating steps (a), (b), (c) and (d) with each of a plurality of phase encode gradients centered around a central phase encode gradient (0) to create centrally encoded data values; (f) repeating steps (a), (b), (c) and (d) with each of a plurality of phase encode gradients to create actually collected side data values between the centrally encoded data values and a view corresponding to one of the maximum positive and maximum negative phase encode gradients (G max, - G max); (g) generating a phase map ((x,y)) from the centrally encoded data values; (h) generating a set of synthesized data values corresponding to non-collected views between the centrally encoded data values and a view corresponding to the other one of the maximum positive and maximum negative phase encode gradients (G max, - G max); (i) Fourier transforming the centrally encoded and the actually collected side data values to form a first image representation (f1(x,y)); (j) determining complex conjugate values from the phase map ((x,y)) and correcting each data value of the first image representation (f1(x,y)) with the complex conjugate of a corresponding value of the phase map ((x,y)) to create a phase corrected first image representation (f1(x,y))e -i(x,y) ); (k) Fourier transforming the synthesized data values to create a second image representation (f2(x,y)); (l) phase correcting the second image representation (f2(x,y)) in accordance with corresponding values from the phase map ((x,y)) to create a phase corrected second image representation (f2(x,y)e +i(xy) ); and (m) combining the first and second phase corrected image representations (f1(x,y)e -i(x,y) , f2(x,y)e +i(x,y) ). According to a second aspect of the present invention there is provided a method of magnetic resonance imaging comprising the steps of: (a) exciting magnetic resonance in an image region; (b) after each excitation of magnetic resonance, causing a magnetic resonance echo during which a magnetic resonance echo signal is generating; and (c) applying a phase encode gradient such that the resultant magnetic resonance echo signal is phase encoded in accordance with the phase encode gradient, characterised by the steps of: (d) collecting a central portion of the magnetic resonance echo signal surrounding a central frequency and a side portion of the magnetic resonance echo signal between the central portion and one extreme of a resonance signal bandwidth; (e) digitizing the collected magnetic resonance echo signal portions to create digital central and side data values; (f) repeating steps (a), (b), (c), (d) and (e) with each of a plurality of phase encode gradients; (g) generating a phase map from the central data values; (h) generating a set of synthesized data values corresponding to frequencies between the central portion and the other extreme of the resonance signal bandwidth; (i) Fourier transforming the central and side data values to form a first image representation; (j) determining complex conjugate values of the phase map and correcting each data value of the first image represenation with the complex conjugate of a corresponding value of the phase map to create a phase corrected first image representation; (k) Fourier transforming the synthesized data values to create a second image representation; (l) phase correcting the second image representation in accordance with corresponding values from the phase map to create a phase corrected second image representation; and (m) combining the first and second phase corrected image representations. According to a third aspect of the present invention there is provided a method of magnetic resonance imaging characterised by the steps of: generating magnetic resonance data including a first set of encoded data values and a second set of encoded data values; generating a phase map ((x,y)) from the first data value set; generating a conjugately symmetric third data set from the second data set; Fourier transforming the first and second data value sets; phase correcting the Fourier transformed first and second data sets (f1(x,y), f2(x,y)) in accordance with the phase map ((x,y)); Fourier transforming the third data set; phase correcting the Fourier transformed third data set in accordance with the phase map ((x,y)); and combining the phase corrected, Fourier transformed data sets (f1(x,y)e -i(,y) , f2(x,y)e +i(x,y) ) to produce an image representation (f(x,y)). According to a fourth aspect of the present invention there is provided a method of magnetic resonance imaging characterised by the steps of acquiring a magnetic resonance data set in which the data value (0,fo) of maximum magnitude is off set in one of a phase encode direction and a frequency direction; generating a phase map ((x,y)) by: filtering the acquired data set to remove data values not in the neighborhood of the data value (0,fo) of maximum magnitude to create a filtered acquired data set, loading the filtered acquired data set with zeroes to create a complete data set and inverse Fourier transforming the completed data set to give a complex phase map image ((x,y)) with unit magnitude; generating an acquired data image (f1(x,y)) by inverse Fourier transforming the acquired data set; generating a symmetric data image (f2(x,y)) by creating a symmetric data set (F*(kx,ky)) which completes the acquired data set by using a conjugate symmetry relationship therebetween and inverse Fourier transforming the symmetric data set (F*(kx,ky)) to generate the symmetric data image (f2(x,y)); correcting the acquired and symmetric data images (f1(x,y), f2(x,y)) with the phase map image ((x,y) to create phase map corrected acquired and symmetric data images (f1(x,y)e -i(x,y) , f2(x,y)e +i(x,y) ); summing the phase map corrected acquired and symmetric data images (f1(x,y)e -(x,y) , f2(x,y)e +i(x,y) ) to create a complex resultant image (f(x,y)); and displaying at least one of real, imaginary and magnitude components of the complex resultant image (f(x,y)). According to a fifth aspect of the present invention there is provided a magnetic resonance imaging apparatus characterised by: magnetic resonance data means for generating a first set of encoded data values and a second set of encoded data values; a phase map generating means for generating a phase map ((x,y)) from the first data set; a conjugate symmetry means for generating a third data set from complex conjugate values of the second data set; a Fourier transform means for Fourier transforming the first and second data sets to create a first image representation (f1(x,y)) and the third data set to create a second image representation (f2(x,y)); a phase correcting means for phase correcting the first (f1(x,y)) and second (f2(x,y)) image representations in accordance with the phase map to create phase corrected first (f1(x,y)e -i(x,y) ) and second (f2(x,y)e +i(x,y) ) image representations; and a combining means for combining the phase corrected first (f1(x,y)e -(x,y) ) and second (f2(x,y)e +i(x,y) ) image representations to create a resultant image (f(x,y)). One advantage of the present invention is that it can be used to reduce the data collection time by reducing the number of phase encoded views. Another advantage of the present invention is an improved NMR sequence capability by selecting slightly more than half the echo to sample. Another advantage of the present invention is that it improves the resultant image. One magnetic resonance imaging method and apparatus will now be described, by way of example, with reference to the accompanying drawings in which:- Figure 1 is a diagrammatic illustration of a magnetic resonance imaging apparatus in accordance with the present invention; Figure 2 is a graphic representation to assist in conceptualizing synthesizing additional views by conjugate symmetry; and Figure 3 is a graphic representation to assist in conceptualizing frequency spectrum data expansion by conjugate symmetry. Referring to Figure 1, nuclear spins of hydrogen in an image region of a magnetic resonance imaging apparatus are excited to magnetic resonance. More specifically, a main magnetic field means, including a main magnetic field controller 10 and a plurality of electromagnets 12, generates a substantially uniform, main magnetic field through the image region. In a superconducting magnet, the controller 10 is only used to ramp up to field or down. A gradient field control means 20 selectively controls the application of gradient fields across the main magnetic field by gradient field coils 22. By selectively applying current pulses to appropriate ones of the gradient field coils, slice select, phase encode, and read gradients are selectively applied along mutually orthogonal axes. The slice select gradients define an image slice or region and the phase encode and read gradients encode the magnetic resonance along mutually orthogonal axes within the slice. A transmitter 30 selectively applies radio frequency pulses to RF coils 32 excite dipoles in the image region to magnetic resonance and to manipulate or orient the magnetization of the resonating dipoles. Magnetic resonance signals generated by the resonating dipoles, particularly when the magnetization is refocused into an echo, are received by the RF coils 32. A radio frequency receiver 34 demodulates the received radio frequency signals to a bandwidth of fo ± Δf, where the center frequency fo of the bandwidth or spectrum ±Δ f is preferably zero. The received magnetic resonance signals are quadrature detected then digitized by an analog-to-digital converter 36 with the digitized signals from each echo commonly being denoted as a view or line of data. A timing and control means 38 controls the timing and application of the gradient and radio frequency pulses to perform spin echo, gradient echo, inversion recovery, and other imaging sequences as are well known in the art. In a single slice spin echo imaging sequence, for example, the gradient field control means 20 applies a slice select gradient to change the magnetic field strength as a function of position along the main magnetic field. The transmitter 20 generates a radio frequency magnetic resonance excitation pulse to excite magnetic resonance between the spin system and the RF field. Thereafter, the spin system relaxes, during which only the magnetization is away from the main magnetic field axis. The gradient field control means encodes the resonating data along mutually orthogonal axes within the slice by applying read and phase encode gradient pulses. The radio frequency transmitter 30 then applies an inversion pulse to cause diverging or dephasing magnetization vectors of the excited resonance to converge and form an echo. The magnetic resonance signal generated during the echo is received by the receiver 34 which filters out frequency components outside of the selected slice and heterodynes the received data to the bandwidth ±Δ f about the preselected central frequency fo. The data is digitized to form a first view or line of data. The imaging sequence is repeated with different phase encode gradients to generate additional lines of data which are stored in an acquired view memory 40. Although the preferred embodiment is described in terms of single slice imaging, it is to be appreciated that the invention is also applicable to volume imaging, multi-slice imaging, and the like. With reference to FIGURE 2, each view is commonly identified by the value of the phase encoding gradient with which the resonance data is encoded. Commonly, a preselected number of views, e.g. 256 views, corresponding to phase encode gradients that vary in like steps from -Gmax to +Gmax are generated by repeating the imaging sequence with different phase encode gradients. Each view or data line is frequency encoded by the read gradient pulse and includes a plurality of frequency components. The frequency component in the center of each view should be fo, those at one extreme fo - Δf and those at the other extreme fo + Δf. A datum value at a frequency fo + Δ f₁ of a positive phase encode view is related by conjugate symmetry to a datum value at a frequency fo - Δ f₁ of the corresponding negative phase encode view. For the zero phase encode view, the datum values are symmetric about fo. In the preferred embodiment, the imaging sequence is repeated to collect data over a contiguous phase encoded central set of views 42 surrounding th zero or minimum phase encode gradient. Data for side view 44 are also acquired for half of the remaining views, preferably the contiguous views between the central views 42 and either -Gmax or +Gmax. The side views 46 between the central views and the other of ±Gmax are not acquired. Rather, as described below, this data is synthesized from the acquired data using the symmetry properties of the data. With reference to FIGURE 3, a full set of partial views for -Gmax to +Gmax may be acquired but which views are incomplete. Specifically, each view includes data in a central frequency region 42′ about the fo or center frequency of the views. Data from a first peripheral region 44′ between the central region and one of the ±Δ f frequencies is acquired. The peripheral data 46′ between the central region and the other of the ±Δ f limit of the views is not acquired. The not acquired fraction of the data is again synthesized from the symmetric properties of the magnetic resonance data. The fractional data set described above in conjunction with FIGURES 2 or 3 or combinations thereof is stored in the view memory 40. A centering means 50 centers the data. For spin echo or gradient echo imaging, the magnitude of the acquired data is maximum at the center of the data set, i.e. the datum value acquired with the zero or minimum phase encoding angle and with the zero or fo center frequency. The data within the view memory 40 is shifted such that the center data value whether determined by its large magnitude or otherwise is moved to the memory coordinate corresponding to a zero phase angle and fo frequency. This may involve shifting data lines up or down or left to right. Any data lines or portion of data lines for which there is no data are filled with zeros. Optionally, an amplitude correction may be made in the frequency direction to correct for T2 decay. A global phase correction means 52 may perform a phase correction on all the acquired data to compensate or correct for possible T2 decay. However, the same phase correction information is in the phase map discussed below. If the global phase correction is performed, it is preferably of the form: where Fo(kx,ky) is the centered data and Fo*(0,0) is the complex conjugate of the central datum value of th data set. The acquired data which has been centered and which may also have been T2 amplitude and globally phase corrected is stored in a corrected acquired data memory means 54 or returned to the view memory 40. A phase map reconstructing means 60 reconstructs a phase map from the central data portion 42, 42′ of the data as acquired. More specifically, a central data selecting means 62 selects the largest available matrix of data which is centered on the zero phase view, e.g. a 32 x 256 data matrix centered at (0,0). The remainder of th data values, such as the remainder of a 256 x 256 array, is loaded with zeros. A roll-off filter means 64 rolls-off the data values of the selected centermost matrix smoothly to the loaded zeroes. Various roll-off filters may be utilized such as a Hanning filter, a Hamming filter, or the like. The roll-off filter provides a smooth transition from the actually collected data to the surrounding zeros and eliminates any discontinuities which might cause ringing or artifacts. A two dimensional Fourier transform means 66 performs an inverse Fourier transform on the filtered data to construct a phase map 68, e.g. a 256 x 256 array of complex data values fp(x,y). The phase map may be either the complex number phase of the resultant complex image or the complex image normalized to a magnitude of 1.0. A phase determining means 70 determines the phase (x,y) of each of the complex data values of the 256x 256 matrix for storage in a phase memory 72, such as a 256 x 256 memory. The values for the phase memory 72 may be determined by calculating the arctangent of the real and imaginary parts of each data value. Alternately, the phase determining means may normalize each complex data value such that it becomes a vector of unit length which is stored in the phase memory means 72. The actually collected data from the first and second regions 42 and 44 or 42′ and 44′ is filtered with a roll-off filter 80, such as a Hamming filter, to ramp down the data past zero in the first region 42. The filtered data is inverse Fourier transformed by a two dimensional Fourier transform means 82 to form a first image representation fl(x,y) which is stored in a first image representation memory means 84. A first phase correction means 86 phase corrects the first image representation in accordance with the phase information in phase memory means 72. More specifically, a phase correction complex conjugate means 88 calculates the complex conjugate of each value in the phase memory means 72. For example, the complex conjugate of the unit vector e i(x,y) is e -i(x,y) . The phase correction means 86 multiplies each (x,y) value of the first image representation by the complex conjugate of the value in the phase memory means 72 for the corresponding (x,y) position. In the preferred embodiment, the correction is of the form: fl(x,y)e -i(x,y) (2). A complex conjugate means 90 generates a third data set corresponding to side data values in region 46, 46′ by calculating the complex conjugate for each corresponding data value (kx, ky) of the collected side data values in region 44, 44′. A filter means 92 ramps up the symmetrized data at a rate that is the complement of the filter 80. A Fourier transform means 94 performs an inverse, two dimensional Fourier transform on the complex conjugate data to create a second image representation f2(x,y) for storage in a second image representation memory 96. A second phase correction means 98 corrects each data value of the second image representation in accordance with the phase of the corresponding (x,y) point from the phase memory 72. In a preferred embodiment, the second phase correction is of the form: f2(x,y)e i(x,y) (3). In this manner, the first and second correction means 86, 98 perform a phase correction in which the resultant data or image representation is corrected with a phase map generated from the same data. Utilizing the same data to create the phase mpa protects against the introduction of phase errors which might arise if different data were utilized such as data from a subsequent scan or subsequent echo of the scan. An adding means 100 sums the phase corrected first and second image representation in a complex addition process to create a resultant or composite image representation f(x,y) for storage in a resultant image memory 102. The resultant image is, of course, a complex image in which each image data value is a complex number having a real and imaginary part. A display means 104 is operatively connected with resultant image memory means 102 to display the real component of the resultant image, the imaginary component,or combinations thereof. Other data storage means and image representation enhancement circuitry may, of course, be interconnected with the resultant image memory means 102.

Claims: A method of magnetic resonance imaging comprising the steps of: (a) exciting magnetic resonance of nuclei in an image region; (b) after each excitation of magnetic resonance, causing a magnetic resonance echo during which a magnetic resonance echo signal is generated; (c) applying a phase encode gradient between a maximum positive phase encode gradient (G max) and a maximum negative phase encode gradient (- G max) such that the resultant magnetic resonance echo signal is phase encoded in accordance with the phase encode gradient; and (d) quadrature detecting and digitizing the magnetic resonance echo signal to create a view of digital data values, characterised by the steps of: (e) repeating steps (a), (b), (c) and (d) with each of a plurality of phase encode gradients centered around a central phase encode gradient (0) to create centrally encoded data values (42); (f) repeating steps (a), (b), (c) and (d) with each of a plurality of phase encode gradients to create actually collected side data values (44) between the centrally encoded data values (42) and a view corresponding to one of the maximum positive and maximum negative phase encode gradients (G max, - G max); (g) generating a phase map ((x,y)) from the centrally encoded data values (42); (h) generating a set of synthesized data values (46) corresponding to non-collected views between the centrally encoded data values (42) and a view corresponding to the other one of the maximum positive and maximum negative phase encode gradients (G max, - G max); (i) Fourier transforming the centrally encoded (42) and the actually collected side (44) data values to form a first image representation (f1(x,y)); (j) determining complex conjugate values from the phase map ((x,y)) and correcting each data value of the first image representation (f1(x,y)) with the complex conjugate of a corresponding value of the phase map ((x,y)) to create a phase corrected first image representation (f1(x,y)e -i(x,y) ); (k) Fourier transforming the synthesized data values (46) to create a second image representation (f2(x,y)); (l) phase correcting the second image representation (f2(x,y)) in accordance with corresponding values from the phase map ((x,y)) to create a phase corrected second image representation (f2(x,y)e +i(xy) ); and (m) combining the first and second phase corrected image representations (f1(x,y)e -i(x,y) , f2(x,y)e +i(x,y) ). A method of magnetic resonance imaging comprising the steps of: (a) exciting magnetic resonance in an image region; (b) after each excitation of magnetic resonance, causing a magnetic resonance echo during which a magnetic resonance echo signal is generated; and (c) applying a phase encode gradient such that the resultant magnetic resonance echo signal is phase encoded in accordance with the phase encode gradient, characterised by the steps of: (d) collecting a central portion (42') of the magnetic resonance echo signal surrounding a central frequency (fo) and a side portion (44') of the magnetic resonance echo signal between the central portion (42') and one extreme (fo - Δ f) of a resonance signal bandwidth; (e) digitizing the collected magnetic resonance echo signal portions (42', 44') to create digital central (42') and side (44') data values; (f) repeating steps (a), (b), (c), (d) and (e) with each of a plurality of phase encode gradients; (g) generating a phase map ((x,y)) from the central data values (42'); (h) generating a set of synthesized data values (46') corresponding to frequencies between the central portion (42') and the other extreme (fo + Δ f) of the resonance signal bandwidth; (i) Fourier transforming the central (42') and side (44') data values to form a first image representation (f1(x,y)); (j) determining complex conjugate values of the phase map ((x,y)) and correcting each data value of the first image representation ((f1(x,y)) with the complex conjugate of a corresponding value of the phase map ((x,y)) to create a phase corrected first image representation (f1(x,y)e -i(x,y) ); (k) Fourier transforming the synthesized data values (46') to create a second image representation (f2(x,y)); (l) phase correcting the second image representation (f2(x,y)) in accordance with corresponding values from the phase map (o(x,y)) to create a phase corrected second image representation (f2(x,y)e +i(x,y) ); and (m) combining the first and second phase corrected image representations (f1(x,y)e -i(x,y) , f2(x,y)e +i(x,y) ). A method of magnetic resonance imaging characterised by the steps of: generating magnetic resonance data including a first set of encoded data values (42, 42') and a second set of encoded data values (44, 44'); generating a phase map ((x,y)) from the first (42, 42') data value set; generating a conjugately symmetric third data set (46, 46') from the second data set (44, 44'); Fourier transforming the first (42, 42') and second (44, 44') data value sets; phase correcting the Fourier transformed first and second data sets (f1(x,y), f2(x,y)) in accordance with the phase map (o(x,y)); Fourier transforming the third data set (46, 46'); phase correcting the Fourier transformed third data set (46, 46') in accordance with the phase map ((x,y)); and combining the phase corrected, Fourier transformed data sets (f1(x,y)e -i(,y) , f2(x,y)e +i(x,y) ) to produce an image representation (f(x,y)). A method according to Claim 3 further including, prior to the phase map ((x,y)) generating step, the step of centering and aligning the data values of the first and second data sets (42, 42', 44, 44'). A method according to Claim 3 or Claim 4 wherein the step of generating the phase map ((x,y)) includes the steps of: filtering the first set of data values (42, 42') and zero data values therearound; and performing a two dimensional Fourier transform on the filtered first set of data values (42, 42') and the surrounding zero data values to form the phase map ((x,y)). A method according to Claim 5 wherein the phase map ((x,y)) generating step further includes the step of normalizing the complex data values of the phase map ((x,y)) to determine their relative phase. A method according to Claim 6 wherein the step of phase correcting the Fourier transformed first and second data sets (f1(x,y), f2(x,y)) includes the step of combining the data values of these sets with the complex conjugates of the normalized phase map ((x,y)) data values. A method according to Claim 6 or Claim 7 wherein the step of phase correcting the Fourier transformed third data (46, 46') set includes the step of combining the data values of this set with the normalized phase map ((x,y)) data values. A method according to any one of Claims 3 to 6 wherein the step of phase correcting the Fourier transformed first and second data sets (f1(x,y), f2(x,y)) includes the step of operating on these data sets with the complex conjugates of phase map ((x,y)) data values; and the step of phase correcting the Fourier transformed third data set (46, 46') includes the step of operating on this data set with phase map ((x,y)) data values. A method according to any one of Claims 3 to 9 wherein the step of generating the first data set (42) includes the steps of generating a plurality of magnetic resonance echoes which are phase encoded by central phase encode gradients around a minimum phase encode gradient (0) and digitizing these magnetic resonance echo signals to create the first data set (42). A method according to Claim 10 wherein the step of generating the second set (44) of data values includes the steps of creating magnetic resonance echo signals which are phase encoded with phase encode gradients between the central phase encode gradients and one of a positive maximum and a negative maximum phase encode gradient (G max, -G max) and digitizing these created magnetic resonance echo signals to create the second data set (44). A method according to any one of Claims 3 to 9 wherein the step of generating the first set of data values (42') includes the steps of generating magnetic resonance echoes during each of which magnetic resonance echoes signals having a preselected bandwidth (fo+ Δ f to fo- Δ f) and bandwidth center frequency (fo) are generated, and digitizing components of the magnetic resonance echo signals adjacent the central frequency (fo) to form the first set of data values (48'). A method according to Claim 12 wherein the step of generating the second set of data values (44') includes the steps of digitizing components of the magnetic resonance echo signals between said central frequency components and one extreme (fo-Δf) of said preselected bandwidth. A method of magnetic resonance imaging characterised by the steps of acquiring a magnetic resonance data set (42, 42', 44, 44') in which the data value (0,fo) of maximum magnitude is off set in one of a phase encode direction and a frequency direction; generating a phase map ((x,y)) by filtering the acquired data set to remove data values not in the neighborhood (42, 42') of the data value (0,fo) of maximum magnitude to create a filtered acquired data set, loading the filtered acquired data set with zeroes to create a complete data set and inverse Fourier transforming the completed data set to give a complex phase map image ((x,y)) with unit magnitude; generating an acquired data image (f1(x,y)) by inverse Fourier transforming the acquired data set (42, 42', 44, 44'); generating a symmetric data image (f2(x,y)) by creating a symmetric data set (F*(kx,ky)) which completes the acquired data set (42, 42' 44, 44') by using a conjugate symmetry relationship therebetween and inverse Fourier transforming the symmetric data set (F*(kx,ky)) to generate the symmetric data image (f2(x,y)); correcting the acquired and symmetric data images (f1(x,y), f2(x,y)) with the phase map image ((x,y) to create phase map corrected acquired and symmetric data images (f1(x,y)e -io(x,y) , f2(x,y)e +i(x,y) ); summing the phase map corrected acquired and symmetric data images (f1(x,y)e -(x,y) , f2(x,y)e +i(x,y) ) to create a complex resultant image (f(x,y)); and displaying at least one of real, imaginary and magnitude components of the complex resultant image (f(x,y)). A magnetic resonance imaging apparatus characterised by: magnetic resonance data means (20, 22, 30, 32, 36) for generating a first set (42, 42') of encoded data values and a second set (44, 44') of encoded data values; a phase map generating means (60) for generating a phase map ((x,y)) from the first data set (42, 42'); a conjugate symmetry means (90) for generating a third data set (46, 46') from complex conjugate values of the second data set (44, 44'); a Fourier transform means (82, 94) for Fourier transforming the first (42, 42') and second (44, 44') data sets to create a first image representation (f1(x,y)) and the third data set (46, 46') to create a second image representation (f2(x,y)); a phase correcting means (86, 88, 98) for phase correcting the first (f1(x,y)) and second (f2(x,y)) image representations in accordance with the phase map to create phase corrected first (f1(x,y)e -i(x,y) ) and second (f2(x,y)e +io(x,y) ) image representations; and a combining means (100) for combining the phase corrected first (f1(x,y)e -(x,y) ) and second (f2(x,y)e +i(x,y) ) image representations to create a resultant image (f(x,y)). An apparatus according to Claim 15 further including a display means (104) for displaying the resultant image (f(x,y)). An apparatus according to Claim 15 or Claim 16 wherein the magnetic resonance data means (20, 22, 30, 32, 36) includes: means (30, 32) for exciting magnetic resonance of dipoles in an image region; means (30, 32) for inducing magnetic resonance echoes during which magnetic resonance echo signals are generated; means (20, 22) for applying magnetic field gradients across the image region for phase and frequency encoding the magnetic resonance signals; and an analog-to-digital converter (36) for digitizing the magnetic resonance echo signals to create digital said first (42, 42') and second (44, 44') sets of data values. An apparatus according to Claim 15 or Claim 16 or Claim 17 further including: a memory means (40) for storing a grid of data values including the first (42, 42') and second (44, 44') data value sets; and a centering means (50) for centering the first data value set (42, 42') in the memory means (40). An apparatus according to any one of Claims 15 to 18 wherein the phase map generating means (60) includes: a filter means for operating on the first data set with a twodimensional roll-off filter (64) to create a filtered first data set; a Fourier transform means (66) for performing a two dimensional Fourier transform operation on the filtered first data set; and a phase map memory means (72) for storing the phase map (,(x,y)). An apparatus according to any one of Claims 15 to 19 wherein the phase correcting means (86, 98) includes: a complex conjugate means (88) for determining the complex conjugate of the phase map ((x,y)); and a multiplying means (86,98) for multiplying Fourier transformed data sets (f1(x,y), f2(x,y)) by one of the phase map ((x,y)) and the complex conjugate of the phase map ((x,y)).

Inventors: DEMEESTER GORDON D, HOLLAND NEIL G, PATRICK JOHN L, DEMEESTER, GORDON D., HOLLAND, NEIL G., PATRICK, JOHN L.
Applicants: PICKER INT INC, PICKER INTERNATIONAL, INC.
Application year: 1988
Main classification: G01R33
IPC codes: G01R33, A61B10, A61B5