METHOD OF RECONSTRUCTING A NUCLEAR MAGNETIZATION DISTRIBUTION FROM A PARTIAL MAGNETIC RESONANCE MEASUREMENT

Abstract: Methods are known for reconstructing magnetic resonance images from a magnetic resonance measurement performed on a body, which methods utilize only one half (or slightly more) of the data of the complete resonance measurement for reaching a resolution corresponding to a complete resonance measurement. Such methods utilize an estimation of the phase of the image from data known as sampling values from a central part of a data matrix filled with the sampling values, the partly filled data matrix being supplemented by zeroes prior to the reconstruction of the image. The known methods offer reasonable results, subject to the condition that the phase of the image varies smoothly and changes slowly in the relevant image dimensions. A method is proposed for reducing the residual artefacts, such as blurring, which occurs in the image when the known methods are used for example due to phase errors. In accordance with the proposed method, a number of steps are performed per column in the data matrix so as to produce an ever better estimation for the data not known from sampling. After the reconstruction, the image will have a phase which at least approximates the phase estimated from the central part of the data matrix. In the case of phase errors, substantially no residual artefacts will remain and at the same time the signal-to-noise ratio in the image will be superior to that obtained by means of the known methods.

Description: The invention relates to a method of reconstructing an image of a nuclear magnetization distribution in a body by a complex Fourier transformation of a data matrix which is filled with sampling values of resonance signals obtained from a magnetic resonance measurement performed on the body, the data matrix in one dimension being filled at least by half with sampling values, a real and an imaginary image component being obtained after the complex Fourier transformation, the reconstruction utilizing a phase which is estimated from data of a central part of the data matrix which is known as sampling values. The term nuclear magnetization distribution is to be understood to mean a broad meaning in the present context; inter alia terms such as spin density distribution, longitudinal relaxation time distribution, transverse relaxation time distribution and spin resonance frequency spectrum distribution (NMR location-dependent spectros-copy) are considered to be covered by the term nuclear magnetization distribution. A method of this kind is known from the "Book of Abstracts" of the "Fourth Annual Meeting of the SMRM", held in London in 1985; page 1024 contains an abstract of a method of image reconstruction for MR images disclosed by P.Margosian. The known method has been presented as a poster at the "Fourth Annual Meeting of the SMRM" on August 22, 1985. In the method disclosed by Margosian, for example a reconstruction is performed on a two-dimensional data matrix, half of which is filled in one dimension with sampling values of resonance signals obtained from a magnetic resonance measurement performed on the body. The magnetic resonance measurement is, for example a so-called spin echo measurement where the body is arranged in a steady, uniform magnetic field and spin nuclei in the body are excited by high-frequency pulses in the presence of magnetic field gradients, thus producing spin echo resonance signals. One of the magnetic field gradients, the so-called preparation gradient, assumes a different value for each spin echo resonance signal. The spin echo resonance signals are sampled and the sampling values are stored in the data matrix. For the description of a magnetic resonance apparatus and a spin echo measurement, reference is made to an article by P.R. Locher "Proton NMR Tomography" in "Philips Technical Review", Vol. 41, No. 3, 1983/84, pages 73-88. The description of the equipment, pulse sequences and image reconstruction methods is given in the article by Locher. For the known method Margosian assumes that the phase of the image varies smoothly and changes slowly in the relevant image dimension; he also estimates the phase from the data of a central part of the data matrix which is known as sampling values. The known method fills half the data matrix, for example by performing half the number of steps of the preparation gradient which would be required for filling the entire data matrix. In terms of the Fourier transformation to be performed on the data matrix in order to reconstruct an image, the stepping of the preparation gradient may be considered as the stepping of a pseudo-time. The "real" time can then be considered as the stepping caused by signal sampling. The dimensions of the data matrix can then be considered as dimensions in "real time" and "pseudo-time". Addition of another dimension to the data matrix (3D) can be considered as stepping in another pseudo-time. The known method fills the remainder of the data matrix with zeroes and performs a reconstruction by executing a complex Fourier transformation on the data matrix, performs a phase correction on the complex image obtained, utilizing the estimated phase, and takes the real image component of the result as the image. Margosian demonstrates that, after multiplication of the image matrix obtained after the complex Fourier transformation by the inverse of the estimated phase, the real image component thereof approximates the desired image and that the imaginary image component thereof represents the image blurring. The desired image has the same resolution as an image obtained from a complete (2D) magnetic resonance measurement. It is to be noted that it is generally known that in the absence of phase errors, where the image is purely real, only half the data matrix need be filled in order to obtain a completely filled data matrix after simple extrapolation. When the image is purely real, the data matrix is complex Hermitian (the real part thereof is even and the imaginary part thereof is odd). In practical situations, however, there will always be phase errors due to eddy currents, a shift of the centre of a spin echo resonance signal, non-ideal high-frequency pulse, and DC offsets of gradients. The simple extrapolation and the subsequent reconstruction would give rise to serious blurring artefacts in the image. A drawback of the method proposed by Margosian consists in that residual artefacts such as blurring artefacts occur in the image. Margosian proposes a special filtering operation over the central part of the data matrix (requiring some additional resonance signals) in order to reduce so-called ringing artefacts in the image, but the effectiveness of such suppression is insufficient and the signal-to-noise ratio in the image deteriorates due to the attenuation of the image amplitude. It is the object of the invention to provide a method for reconstructing an MR image where the residual artefacts occurring in the known method due to phase errors are substantially reduced, without affecting the signal-to-noise ratio, To achieve this, a method of the kind set forth is characterized in that the complex Fourier transformation is performed first on the sampling values in the other dimensions, in the one dimension a Fourier transformation step being performed on each column partly filled with sampling values in a number of steps after an estimation for the data not known from sampling, the estimation for the data not known from sampling being adapted in each subsequent step in order to obtain, after reconstruction, an image whose phase at least approximates the phase estimated from the central part of the data matrix. Thus, an image is obtained which is substantially free from blurring artefacts when the phase errors are not excessively large. A version of a method in accordance with the invention, involving an initial estimation for the data not known from sampling, is characterized in that in a step after the Fourier transformation step of the column a next estimation is obtained for the data not known from sampling in the column from an image profile thus obtained in the one dimension, said next estimation, after Fourier transformation thereof followed by elimination of the phase, increasing the real image component in the image profile and decreasing the imaginary image component in the image profile, after which in subsequent steps ever smaller imaginary image components and an ever better approximation of the phase of the image profile are obtained. It is thus achieved that each subsequent estimation is a better approximation of the data not known from sampling. For example, zeroes are taken as the initial estimation for the data which are not known from sampling. A preferred version of a method in accordance with the invention is characterized in that the next estimation for the data not known from sampling values is realized by performing a Fourier transformation on the conjugated complex image profile of the preceding estimation with double the phase. Thus, an efficient execution of a method in accordance with the invention is achieved with a suitable convergence towards the desired image. The method is performed, for example by means of programmed arithmetic means in an MR device which is known per se . The invention will be described in detail hereinafter with reference to the accompanying diagrammatic drawings; therein: Figure 1 shows a time axis with different instants which are important for the method in accordance with the invention, as well as an image profile axis, and Figure 2 shows a flowchart of a version of the method in accordance with the invention for an image profile. It is assumed, by way of example, that a two-dimensional data matrix is filled with sampling values from a spin echo measurement and that the one dimension of the data matrix in which half the data matrix is filled is the real time. In practice this means that spin echo resonance signals are sampled for only half the period during which they occur. For the description of a two-dimensional spin echo measurement reference is again made to the cited article by Locher. In the other dimension, being the pseudo time caused by the stepping of the preparation gradient, the data matrix is completely filled. Figure 1 shows a time axis with different instants which are important for the method as well as an image profile axis. The time axis, along which the time t is plotted, shows an interval from t=-t₀ to t=t₀; the one dimension of the data matrix is an image thereof. A spin echo resonance signal S(t) (not shown) will be at least substantially symmetrical with respect to the instant t=0 during a spin echo measurement. During the partial measurement, the spin echo resonance signal S(t) will be sampled only from t=-t₀ to t=t₁ for given values of the preparation gradient (pseudo-time) in the case of the two-dimensional measurement. When the instant t=t₁ coincides with t=0 a half-filled data matrix will be obtained. In the interval from t=t₁ to t=t₀ the data in the data matrix which is not known from sampling is estimated. U j (t) denotes a signal which corresponds, in the interval from t=-t₀ to t=t₁, to the (sampled) spin echo resonance signal S(t) and which is estimated in the interval from t=t₁ to t=t₀. Figure 1 also shows an image profile axis along which an image parameter x is plotted a field of view being indicated from x=-x₀ to x=x₀. A body in which spin nuclei are excited by the spin echo resonance measurement should remain within this field of view in order to prevent aliasing problems during Fourier transformation. For an image profile f(x), for a given value of the preparation gradient, the image profile is the inverse Fourier transform of a data profile U(t) determined partly by sampling of the spin echo resonance signal and for the remainder by estimation, or of a column in the one dimension of the data matrix. In the method in accordance with the invention, the image profiles of all columns of the data matrix are determined in the one dimension in which half the data matrix is filled, after the Fourier transformation steps have first been performed in the other dimensions. Hereinafter, the steps of the method in accordance with the invention will be described for an image profile f(x). The phase of the image profile f(x) is estimated from data of the central part of the data matrix which is known as sampling values. The phase of an image profile arising after Fourier transformation is taken as an estimate (x) for the phase. It is assumed that the estimated phase (x) varies smoothly and changes slowly in the field of view. The image profile f(x) associated with the signal U(t) can be expressed in terms of the estimated phase (x): where r(x) is an unknown complex function of x, i is the square root of -1 and e is the exponential function. r(x) contains a real component (the desired image component) and an imaginary component (the undesirable image component). r(x) should satisfy: where F denotes the Fourier transform. Using the method in accordance with the invention, an estimate is iteratively made for the data which is not known from sampling. Each iteration step j produces an improved estimate, the inverse Fourier transform of the known and estimated data, to be referred to together as U j (t), producing an image profile f j (x) whose real image component increases and whose imaginary image component decreases after elimination of the phase (x). The image profile f j (x) can be written as: where r j (x) and q j (x) are real functions, r j (x) being the desired image component and i.q. j (x) being the undesirable image component. Thus, U j (t) can be written as: where R j (t) generates the desired image component r j (x)e i(x) and Q j (t) generates the undesired image component iq j (x)e i(x) by means of a Fourier transformation. In accordance with the invention, Q j (t) which generates the undesired image component i.q j (t) is modified in each iteration step in the interval from t=t₁ to t=t₀, during which interval the estimation of data is free. In the interval from t=-t₀ to t=t₁, no free choice exists as regards Q j (t), because therein the data of Q j (t), obtained by sampling of the signal S(t), should remain unmodified. When Q j (t) is suitably chosen in each iteration step, the undesired image component i.q j (x) will decrease. In an iteration step j+1, a data profile U j+1 (t) is determined from the preceding iteration step j as follows: where Q j (t) is modified by multiplication by a function V(t). Considering the foregoing, it will be evident that V(t) must be 1 for t<t₁ and can be chosen at random for t>t₁. The image profile f j+1 (x) is the inverse Fourier transformation of U j+1 (t). It is generally known that a product in the t-domain can be written as a convolution in the x-domain. In that case the undesired image component is transformed into the following: where * is the convolution operation and v(x) is the Fourier transform of V(t).R j (t) which generates the desired image component does not change. When the function V(t) is suitably chosen, the convolution in each iteration step will increase the desired image component and decrease the undesired image component. A suitable choice for V(t) is, for example V(t)=1 for t<=t₁ and V(t)=0 for t>t₁. A transformation of the estimated data will occur and the undesired image component will converge towards zero. When t₁=0 is chosen, it is attractive to take V(t)=-sign(t) whose Fourier transform is v(x)=i/(π.x), a strongly peaked function around x=0. Moreover, the phase (x) varies very smoothly. As a result, in each iteration step the convolution will contribute substantially more to the desired image component than to the undesired image component; this will become more evident when the convolution is written in full. When V(t)=-sign(t) is chosen, it can simply be demonstrated that U j+1 (t)=R j (t)+V(t).Q j (t) can be written as: where conj is the conjugated complex, so that a method is obtained which can be simply implemented. The functions r j (t), q j (t), R j (t) and Q j (t) no longer explicitly occur therein. When t₁>0, the transformation of the estimated data cannot be fully executed, but must be restricted to the data in the data matrix for t>t₁. This means that the method is effective only for the high-frequency components of the image. In the method in accordance with the invention, the low-frequency components already have the desired phase (x) because they have been generated from sampling values of the spin echo resonance signal, or Q j (t) will already be approximately zero around t=0, so that the result of the method will not be affected by this restriction. When V(t)=-sign(t) is chosen it will often be sufficient to perform from 1 to 3 iterations per image profile. The undesired image component then quickly converges to zero. Figure 2 shows a flowchart of a preferred version of a method for an image profile. The method for the image profile commences in block 1. Initialization takes place in block 2. Therein j is the iteration step and n is the number of iteration steps. j is initialized at zero and n is initialized at n₀. For t<=t₁ the data profile U j (t) assumes the sampling values of the spin echo resonance signal S(t) and for t>t₁, U j (t) is initialized at zero. In block 3 an image profile f j (x) is determined by inverse Fourier transformation of the data profile U j (t). In block 4 the next data profile U j+1 (t) is estimated. For t<=t₁, U j+1 (t) assumes the sampling values of the spin echo resonance signal S(t) and for t>t₁, U j+1 (t) equals the expression given in (7). In block 5 it is tested whether all iterations have been completed. If this is not the case, the iteration step is incremented in block 6 and the procedure returns to block 3 for the next iteration step. When all iteration steps have been completed, however, in block 7 the image profile f j+1 (x) is determined from the data profile U j+1 (t), determined during the last iteration step, by inverse Fourier transformation. The method for the image profile is completed in block 8 so that a next image profile can be treated. Hereinafter two implemenations in accordance with the invention will be described for different choices of V(t) in which the desired image component r j (x) and the undesired image component i.q j (x) occur explicitly. In an iteration step j+1, the choice V(t)=-sign(t) results in a data profile U j+1 (t) determined by: U j+1 (t)=S(t), t<=t₁ U j+1 (t)=R j (t)-Q j (t), t>t₁. When the transform R j (t) associated with the desired image component r j (x) is subtracted from U j+1 (t) for t<=t₁, as well as for t>t₁, an implementation will be obtained which is equivalent to the version shown: U j+1 (t)=S(t)-R j , t<=t₁ U j+1 (t)=-Q j (t), t>t₁ As can be simply demonstrated, an image profile f j+1 (x) is then determined from an image profile f j (x) in the iteration step j+1: where in the iteration step j r j (x), q j (x), R j (t) and Q j (t) are determined by: IF{U j (t)}={r j (x)+i.q j (x)}.e i.(x) , R j (t)=F{r j (x).e i.(x) }, and Q j (t)=F{i.q. j (x).e i.(x) }, respectively, The choice V(t)=1 for t<t₁ and V(t)=0 for t>t₁ offers: U j+1 (t)=S(t), t<=t₁ U j+1 (t)=R j (t), t>t₁, after which the iteration formulas U j+1 (t)=S(t)-R j (t), t<=t₁ U j+1 (t)=0, t>t₁ are obtained after subtraction of R j (t), an image profile then being determined in the iteration step j+1 in accordance with formula 8. The method is not restricted to the described examples. For example, the method is not restricted to the described spin echo resonance measurement where half the data matrix is filled in the real-time dimension of the data matrix; half the data matrix can also be filled in a pseudo-time dimension. Also, in the real-time dimension, an interval [-t₁,t₀] might be sampled instead of [-t₀, t₁] which is particularly useful in practice to obtain short echo times and low signal bandwidths. The interruption of the iterations can also be determined by an error criterion as an alternative for the choice of a fixed number of steps.

Claims: A method of reconstructing an image of a nuclear magnetization distribution in a body by complex Fourier transformation of a data matrix which is filled with sampling values of resonance signals obtained from a magnetic resonance measurement performed on the body, the data matrix in one dimension being filled at least by half with sampling values, a real and an imaginary image component being obtained after the complex Fourier transformation, the reconstruction utilizing a phase which is estimated from the central part of the data matrix which is known as sampling values, characterized in that the complex Fourier transformation is performed first on the sampling values in the other dimensions, while in the one dimension a Fourier transformation is performed on each column partly filled with sampling values in a number of steps after an estimation for the data not known from sampling, the estimation of the data not known from sampling being adapted in each subsequent step in order to obtain, after reconstruction, an image whose phase at least approximates the phase estimated from the central part of the data matrix. A method as claimed in Claim 1, involving an initial estimation for the data not known from sampling, characterized in that in a step after the Fourier transformation step of the column a next estimation is obtained from the data not known from sampling in the column from an image profile thus obtained in the one dimension, said next estimation, after Fourier transformation thereof followed by elimination of the phase, increasing the real image component in the image profile and decreasing the imaginary image component in the image profile, after which in subsequent steps ever smaller imaginary image components and an ever better approximation of the phase of the image profile are obtained. A method as claimed in Claim 2, characterized in that the next estimation for the data not known from sampling values is realized by performing a Fourier transformation on the conjugated complex image profile of the preceding estimation with double the phase. A method as claimed in any one of the preceding Claims characterized in that each estimation is performed in a fixed number of steps.

Inventors: CUPPEN, JOHANNES JOSEPHUS MARIA
Applicants: N.V. PHILIPS' GLOEILAMPENFABRIEKEN
Application year: 1987
Main classification: G01R33
IPC codes: G01R33, A61B10, A61B5