NMR IMAGING METHOD

Abstract: The NMR imaging method performs the imaging using a non-square scan matrix suitable for the sectional shape of a material to be examined, maintaining isotropic pixel resolution within a short scanning time. The method comprises setting a non-square scanning matrix having dissimilar vertical and lateral lengths to be suitable for the sectional shape of the material to be examined. Scan data is collected by the two-dimensional Fourier method with the long side of the matrix employed as a direction of projection axis and the short side as a direction of warp axis. The image is displayed using the non-square image matrix that has as one side the length which corresponds to a projection width (A) and that has as the other side the length which is M/N times (wherein M is the number of views, N is the number of samples in the direction of projection, and M less than N) as large as the projection width A.

Description: This invention generally relates to an improved NMR imaging method used to develop a sectional image of a subject using scan data collected from the subject based on a nuclear magnetic resonance phenomenon. More specifically, this NMR imaging method enables imaging by using a non-square scan matrix with different vertical and horizontal dimensions, while maintaining isotropic pixel resolution. An NMR imaging device consists of a magnet section that includes a static magnetic field coil that provides a homogeneous static magnetic field, and a gradient magnetic field coil that provides a magnetic field having a linear gradient in each direction (x, y, and z) in a magnetic field with the same direction as the static magnetic field. Also included are transmission and reception sections that apply a high-frequency pulse (high frequency electromagnetic wave) to a subject placed in a magnetic field formed by the magnet section to detect NMR signals from the subject, and control and image processing sections that control the operation of the transmission, reception, and the above magnet sections to process the detected data and display images. An NMR imaging device with the above mentioned configuration is driven in the pulse sequence of a two-dimensional Fourier method as shown in Figure 4. This device collects data from the desired section of a subject. In other words, the imaging device applies slice gradient magnetic field G z and a 90° pulse (excitation RF signal) simultaneously to selectively excite the nuclear spin within a specific slice area of the subject. Then the device applies rephase gradient magnetic field G z to recover the spin phase deviation generated during slicing, while simultaneously applying dephase gradient magnetic field G x to provide spin with a phase difference to generate a spin echo signal. The device then applies warp gradient G y . Then, all gradients are nullified and a 180° pulse is applied to invert the spin phase. Then, if read gradient G x is applied, a spin whose phase was dispersed due to the dephase gradient magnetic field has the phase matched again to enable an NMR signal to be observed as a so-called "spin echo signal." This NMR signal is equivalent to one line (one view) of the spin distribution of a subject after two-dimensional Fourier transformation. Because line selection is determined by the product of the size of warp gradient magnetic field G y and the application time, the data required for image configuration can be collected by repeating the sequence shown in Figure 4, while varying the size of the gradient magnetic field. A scan matrix used for scanning a desired field of view (FOV) in a pulse sequence of the above mentioned two-dimensional Fourier method is generally a square matrix (matrix having four equal sides) of 64 Ch x 64 views, 128 Ch x 128 views, 256 Ch x 256 views, or 512 Ch x 512 views, where Ch denotes data in the readout direction. Moreover, an image matrix used for reconfiguring images using such data is either a square matrix of 512 x 512, 256 x 256, etc., or their cutouts in a circular shape. For such a matrix, the vertical and horizontal resolution of an image becomes isotropic so that a natural image can be obtained. However, if the field of view is oval, the device may scan a wide area of air where no subject exists, and the data on sections not related to the image is collected, while taking a longer scan time than actually needed. Conversely, the scanning time in Fourier transformation is known to be roughly proportionate to the number of samples (number of views) in the warp direction. Therefore, it is understood that to reduce the scanning time, the number of samples in the warp direction should be reduced, that is, scanning should be done using a non-square matrix. Actually, certain data is collected according to the scanning method of 512 x 256 or 256 x 128 (sample number x view number) for example. In such cases, when the scan time is reduced, no isotropy can be obtained for the vertical and horizontal pixel resolution of an image. Moreover, a large amount of data on air not related to the image is included. Prior art document EP-A-0 246 327 according Art. 54(3) discloses a method and apparatus for NMR imaging which collects data on each subject in the shortest possible scanning time. Namely, projection data on the subject are collected in a plurality of directions, a direction is found in which the number of samples is the smallest in the warp direction based upon the projection data, and the data are collected by the Fourier method while turning the scan coordinate along the above-found direction. Prior art document EP-A-0 172 345 relates to an NMR apparatus, comprising means for controlling of registration of Fourier-lines of the measure matrix depending on a breathe-signal. There is a line counter influencing switching means so that the measure signal registration is always released enabled for all lines out off a predetermined range, but for lines within this range depending on a breathe phase signal. The predetermined line range may comprise about 10 % of all lines to be measured and should be symmetrical relating to the middle of the measure matrix. A more comprehensive reduction of measuring time is realized by completely dispensing with the measurement in the line border range of the matrix. It is an object of this invention to provide an NMR imaging method that achieves isotropic pixel resolution and imaging within a short scan time by using a non-square scan matrix matched with the sectional form of a subject. To solve this object the present invention provides a method as specified in the claim. According to the NMR imaging method of this invention, a non-square scan matrix with different vertical and horizontal dimensions corresponding to the sectional form of a subject is set. Scan data is collected under two-dimensional Fourier transformation by setting the longer sides of the matrix in the readout direction and the shorter sides in the warp direction, while simultaneously displaying the image in a non-square image matrix whose length corresponds to projection width A on one side and a length corresponding to M/N time of projection width A (where M: number of view, N: number of sample in the direction of projection, and M < N) on the other side. The invention will be more better understood from the enclosed drawings wherein: Figure 1 shows the block diagram of the NMR imaging device used as the preferred application mode of according to the method provided by this invention, Figures 2 and 3 explain the operation of the application mode of this invention, and Figure 4 shows an example of a pulse sequence under two-dimensional Fourier transformation. An example of an application mode of this invention is described in detail by referring to the drawings as follows. In Figure 1, "1" indicates a magnet assembly having an inner space section for inserting a subject. The space section is surrounded by a static magnetic field coil that applies a constant static magnetic field to the subject, gradient magnetic field coils (x, y, and z) for generating a gradient magnetic field, an RF transmission coil for providing high-frequency pulses to excite the spinning of specified nucleuses inside the body system of the subject, and a receiving coil for detecting NMR signals sent from the subject (diagram omitted). The static magnetic field coil, gradient magnetic field coils, RF transmission coil, and receiving coil are respectively connected to main magnetic field power supply 2, gradient magnetic field drive circuit 3, RF power amplifier 4, and preamplifier 5. Sequence memory circuit 10 operates according to a present sequence, gradient magnetic field drive circuit 3 and gate modulation circuit 6 according to instructions issued by computer 13 to generate a gradient magnetic field and high-frequency pulse signal in the preferred application mode according to the method provided by this invention. Sequence memory circuit 10 also operates the gradient magnetic field drive circuit 3, the gate modulation circuit 6, and an A/D converter 11 in a Fourier-based sequence. Phase detector 8 uses the output from RF oscillation circuit 7 as a reference signal to detect the phase of an NMR signal detected by the receiving coil, and then sends the data via preamplifier 5 to A/D converter 11. A/D converter 11 sends the NMR signals obtained through phase detector 8 after A/D conversion to computer 13. To exchange information with operation console 12 and enable various scan sequences, the computer 13 switches operation of sequence memory circuit 10, reloads its memory and operates the image reconfiguration by using data sent from A/D converter 11, and outputs reconfiguration image data to display unit 9. Sequence information may be stored by the computer 13, and be written as required to the memory of sequence memory circuit 10. The configuration described above is operated in the preferred application mode according to the method provided by this invention as follows: In Figure 2, if section 21 of a subject has a general oval shape and field of view 22 for imaging, it is matched with oval shaped section 21 of the subject, field of view 22 becomes a non-square shape with different vertical and horizontal lengths. Then, operation console 12 is used to set up a scan matrix of M₁ x N₁ according to the vertical and horizontal lengths of field of view 22, where M₁ and N₁ are positive integers and M₁<N₁. The longer side (N₁) of the selected matrix is matched to a longer side of the field of view, and is set in the direction of projection, while the shorter side (M₁) of the above matrix is matched to a shorter side of the field of view, and is set in the warp direction. By considering a dimension of the longer side of the field of view to be A, the pixel resolution in this direction is set at A/N₁. If a scan sequence is started after setting a scan matrix as described above, NMR signal measurement is done according to a pulse sequence based on the two-dimensional Fourier method shown in Figure 4. Accordingly, NMR signals are collected from section 21 of the subject. The above-mentioned sequence is repeated the number of times determined by the scan matrix of M₁ x N₁. Therefore, the number of samples on the projection axis and warp axis (number of views) will be N₁ and M₁, respectively. Because the number of views is now M₁, the scan time is reduced to M₁/N₁ for data collection using a square scan matrix of N₁ x N₁. Collected scan data is converted into digital signal, then is sent to computer 13. Computer 13 operates the image reconfiguration according to a non-square image matrix whose length corresponds to the longer side of the field of view A of a scanned field of view on one side, and whose length corresponds to A·M₁/N₁ on the other. Computer 13 outputs the result to display unit 9. Therefore, as shown in Figure 3, image 24 (based on the result of the above operation) is displayed in screen size 23), which corresponds vertically to A.M₁/N₁ and horizontally to A. Because the vertical pixel resolution at this time is (A·M₁/N₁)/M₁=A/N₁, the pixel resolution in both vertical and horizontal directions of the screen becomes A/N₁ so that a natural image with isotropy can be obtained. When such imaging is done, the relations between warp gradient G y and readout gradient G x are indicated by following expressions (1) and (2): G y = l/( γ· FOVy·T sw ) G x = l/( γ ·FOVx·T samp ) where γ: gyromagnetic ratio T sw : warp time T samp : readout time Accordingly, in the case shown in Figure 3, the above-mentioned expressions are respectively replaced by expressions (3) and (4): G y = l/( γ ·A·T sw ·M₁/N₁) G x = l/( γ ·A·T samp ) The above application mode describes a sequence (generally called the SE Spin echo method) of Fourier transformation. Needless to say, the application mode can be applied to sequences other than the above. Moreover, if the sectional shape of a subject is oval with a longer vertical direction dimension, a scan matrix with vertical and horizontal lengths of M₂ x N₂ (M₂ and N₂ being positive integers and M₂ > N₂) can be set. For scanning, the longer side (M₂) of this matrix is matched with the longer side of the field of view, and is set in the read out direction, while the shorter side (N₂) of the above matrix is matched with the shorter side of the field of view, and is set in the warp direction.

Claims: An NMR imaging method, involving the steps of exciting the nuclear spins of a desired section (21) of a subject placed within a homogeneous static magnetic field setting a non-square scan matrix of dimension MxN, where M<N, for scanning a desired field of view according to a two-dimensional spin-warp pulse sequence, the longer side of dimension N of said scan matrix being set in the readout direction and the shorter side of dimension M being set in the warp axis direction, collecting MxN scan data from said section (21) according to said two-dimensional spin-warp sequence, where M indicates the number of views and N indicates the number of samples in the readout direction, reconfiguring an image (24) by subjecting said scan data to a two-dimensional Fourier transformation and displaying said image (24), said method being characterized by the steps of matching the field of view (22) with the general oval shape of said section (21) of the imaging subject whereby the field of view (22) adopts a non-square shape with different vertical and horizontal lengths, matching the longer side of said scan matrix to the longer side of said field of view (22) and setting it in the readout direction while matching the shorter side of said scan matrix to the shorter side of said field of view (22) and setting it in the warp axis direction, thereby achieving isotropic pixel resolution in the reconstructed image despite a reduction in the number of views compared with a square scan matrix of dimension NxN, displaying the reconfigured image (24) using a non-square image matrix whose length corresponds to the length A of the longer side of said field of view on one side and to AxM/N on the other side.

Inventors: KOSUGI SUSUMU YOKOGAWA MEDICAL, MIYAZAKI MAKOTO YOKOGAWA MEDIC, SHIMAZAKI TORU YOKOGAWA MEDICA, YAMADA NORIAKI YOKOGAWA MEDICA, KOSUGI, SUSUMU YOKOGAWA MEDICAL SYSTEMS, LTD., MIYAZAKI, MAKOTO YOKOGAWA MEDICAL SYSTEMS, LTD., SHIMAZAKI, TORU YOKOGAWA MEDICAL SYSTEMS, LTD., YAMADA, NORIAKI YOKOGAWA MEDICAL SYSTEMS, LTD.
Applicants: YOKOGAWA MEDICAL SYST, YOKOGAWA MEDICAL SYSTEMS, LTD
Application year: 1987
Main classification: G01R33
IPC codes: G01R33, A61B5, A61B10