Method for measuring the magnetic resonance (NMR) by driven equilibrium

Abstract

A method of MRT according to the principle of signal generation in the driven equilibrium (DE) or also steady state free precession (SFP) wherein a periodic sequence of RF pulses with a flip angle α is applied with a time delay TR wherein the phase of these pulses is alternated in subsequent steps, is characterized in that the periodic sequence of RF pulses is preceded by a sequence of (n+1) pulses for which the following conditions are valid:

Description

BACKGROUND OF THE INVENTION

[0001] The invention concerns a method of NMR (=nuclear magnetic resonance) tomography (=MRT) for generating NMR gradient echo signals according to the principle of signal generation in the driven equilibrium (DE) or also called steady state free precession (SFP) wherein a periodic sequence of radio frequency pulses with a flip angle α is applied with a time delay TR, wherein the phase of these radio frequency pulses is alternated in subsequent steps.

[0002] A SFP signal is generated by a continuous sequence of radio frequency pulses and was introduced by Carr as early as 1958 (Phys.Rev.112, 1693 (1958)). Carr was able to show that implementation of the method with equidistant radio frequency pulses with constant amplitude and alternating phase produces a particularly high signal intensity of the SFP signal of on-resonance spins.

[0003] In 1986, this principle was converted by a FISP method (in the meantime called true FISP) into a method of MR imaging (A. Oppelt et al. electromedica 54, 15 (1986)). All gradients are switched such that their integral from the center of a pulse to the center of the subsequent pulse is zero. Subsequent pulses have flip angles α and alternating phases: P1, P3, P5 . . . =α, P2, P4, P6 . . . =−α. The temporal separation between 2 pulses is called repetition time TR.

[0004] The problem with implementation is thereby the fact that the transition into the resulting signal steady state is effected only gradually within a time period determined by T1 relaxation. Until this steady state has been reached, periodic signal fluctuations occur which produce strong image artefacts when using the sequence for MRT (see FIG. 2).

[0005] Suppression of this initial signal fluctuation is achieved in that before the continuous sequence of radio frequency pulses, one single pulse with a flip angle α/2 is applied with a time delay of TR/2 (Deimling, M. DE 44 27 497 A1). This suppresses the initial signal modulations and merely a monotonic signal change into the steady state takes place (FIG. 3).

[0006] Suppression of signal modulation is explained on the basis of observation of the subsequent signals according to FIG. 4, wherein the radio frequency pulses are chosen to be applied each with a radio frequency field with a phase parallel to the y-axis of the transverse plane. The diagram of transverse magnetization Mx vs. Mz shows that the magnetization vector of the steady state magnetization Mss is tilted relative to the z-axis by an angle α/2 such that Mss of subsequent radio frequency pulses is flipped between +−Mss. Initialization with α/2 brings the original z-magnetization M0 to the correct tilting angle and the magnetization vector is transferred to Mss in subsequent radio frequency pulses corresponding to T1 and T2 relaxation wherein the signals (=absolute amount of the Mx-magnetization) decay monotonously towards Mss(x) and show no modulation.

[0007] This is true only for so-called on-resonance spins which experience no phase-change during TR. In MR tomography applications (=MRT) this condition is not met even for very small repetition times TR wherein TR is determined substantially by the switching speeds of the magnetic field gradients.

[0008] The magnetic field homogeneities dephase the spins by a phase angle of Δφ between two excitations. With TR=4 ms, Δφ=90° for an off-resonance frequency is e.g. ΔΩ of Δφ/(TR*360°)=66 Hz. This corresponds to an inhomogeneity of 1 ppm at a resonance frequency of 63 MHz at 1.5 tesla field strength. Such inhomogeneities cannot be avoided in applications on humans due to the occurring susceptibility effects.

[0009] FIG. 5 shows the signal development in a method optimised according to DE 44 27 497 A1 as a function of Δφ. It can be clearly seen that spins with ΔΩ unequal 0 experience modulation over the first excitation periods.

[0010] The corresponding signal intensities for Δφ=0°, 180° and 360° are shown in FIG. 6. Transfer of the modulations into the steady state amplitude which is characteristic for Δφ is very slow. These modulations produce image artefacts. The behavior differences of the spins which are characterized by Δφ=0° and Δφ=360° can be explained in that these spins are mutually dephased by 180° in the initial period TR/2 according to the method of DE 44 27 497 A1.

[0011] A further disadvantageous property of the method according to DE 44 27 497 A1 consists in that application of the small flip angle α/2 for initialisation of the steady state sequence renders access to only a relatively small part of the originally present magnetization M0 corresponding to M0 sin α/2).

[0012] In contrast thereto, it is the object of the present invention to further improve a method of the above-described type such that the above-discussed disadvantages can be eliminated.

SUMMARY OF THE INVENTION

[0013] In accordance with the invention, this object is achieved in an effective fashion, in that the periodic sequence of radio frequency pulses is preceded by a sequence of (n+1) radio frequency pulses with the following valid conditions:

[0014] a first excitation pulse with preferred flip angle α0=90° precedes the subsequently equidistant sequence of radio frequency pulses at a preferred separation TR/2,

[0015] the flip angle α1 of the subsequent radio frequency pulse is larger than α and equal or approximately equal to 180°,

[0016] the flip angle αi of the i-th radio frequency pulse in the region i=2 . . . n is selected such that αi is smaller or equal to αi-1 and larger or equal to α and

[0017] the phases of these radio frequency pulses alternate.

[0018] Further advantages of the invention can be extracted from the description and the drawing. The features mentioned above and below can be used in accordance with the invention either individually or collectively in any arbitrary combination. The embodiments shown and described are not to be understood as exhaustive enumeration but rather have exemplary character for describing the invention.

[0019] The invention is shown in the drawing and explained in more detail with reference to embodiments.

BRIEF DESCRIPTION OF THE DRAWINGS

[0020] FIG. 1 shows a scheme of a trueFISP sequence, wherein HF, GS, GR and GP characterize the radio frequency pulses P1, P2, P3 and the signals S1, S2; GS is the slice selection gradient, GR is the read gradient and GP is the phase encoding gradient;

[0021] FIG. 2 shows the intensities I of the signals S1 . . . n as a function of n, wherein for the simulation calculations, the following parameters were selected: TR=4 ms, T1=50 ms, T2=25 ms, α=60°;

[0022] FIG. 3 equals FIG. 2, however, with an initial pulse with a flip angle of 30° which is applied 2 ms before the sequence;

[0023] FIG. 4 shows the position of the magnetization vectors M in the x-z plane during application of RF pulses whose B1 field is oriented along the y axis (perpendicular to the plane of the image) during application of the method according to DE 44 27 497 A1; wherein the ellipse characterizes the signal steady state for the selected parameters of T1=50 ms and T2=25 ms as a function of α, and wherein the steady state for a certain α (here α=60°) corresponds exactly to the point of intersection of the ellipse with a straight line inclined relative to the z axis by +−α/2;

[0024] FIG. 5 shows the x (broken lines) and y (dotted line) magnetization and the signal intensity I (full line) as a function of dephasing Δφ (in degrees) during TR over the first 8 signals. I corresponds to the amount of transverse magnetization. The B1 field of the excitation pulse is oriented along y;

[0025] FIG. 6 shows Mx as function of n for Δφ=0° (full line, corresponding to FIG. 3), 180° (broken line) and 360° (dotted line);

[0026] FIG. 7 shows the position of the magnetization vectors M in the x-z plane during application of RF pulses whose B1 field is oriented along the y axis (perpendicular to the plane of the image) with flip angles α0=90°, α1 . . . n=−160°, 140°, −120°, 100°, −80°, 60°, −60°, 60° . . . ;

[0027] FIG. 8 shows Mx as function of n for Δφ=0° (full line), 180° (broken line) and 360° (dotted line) for a sequence of FIG. 7;

[0028] FIG. 9 shows the position of the magnetization vectors M in the x-z plane during application of RF pulses whose B1 field is oriented along the y axis (perpendicular to the plane of the image) with flip angles which approach α=60° in 5° steps: α0=90°, α1 . . . n=−175°, 170°, −165°, 160°, −155°, . . . , 70°, −65°, 60°, −60°, 60° . . . ;

[0029] FIG. 10 shows Mx as function of n for Δφ=0° (full line), 180° (broken line) and 360° (dotted line) for a sequence of FIG. 9;

[0030] FIG. 11 shows the position of the magnetization vectors M in the x-z plane during application of RF pulses whose B1 field is oriented along the y axis (perpendicular to the plane of the image) with flip angles α0=90°, α1 . . . n=−180°, 180°, −120°, 60°, −60°, 60° . . . ;

[0031] FIG. 12 shows Mx as function of n for Δφ=0° (full line), 180° (broken line) and 360° (dotted line) for a sequence of FIG. 11;

[0032] FIG. 13 shows Mx as function of n for Δφ=0° (full line), 180° (broken line) and 360° (dotted line) for a sequence with α0=90°, α1 . . . 20=+−180°, α21=120° and α22 . . . 50=+−60°;

[0033] FIG. 14 shows the position of the magnetization vectors M in the x-z plane during application of RF pulses whose B1 field is oriented along the y axis (perpendicular to the plane of the image) with flip angles α0=90°, α1 . . . 12=α13 . . . 24= . . . =−180, 120, −60, 60, −60, 60, −60, 60, −60, 60, −60, 120;

[0034] FIG. 15 shows Mx as function of n for Δφ=0° (full line, corresponds to FIG. 3), 180° (broken line) and 360° (dotted line) for a sequence according to FIG. 14.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

[0035] The inventive method refers to the generation of NMR signals according to the principle of signal generation in the driven equilibrium (DE) or also steady state free precession (SFP). In contrast to prior art, the inventive method permits transfer from the steady state into the DE after a few excitation periods such that fluctuating signals from off-resonance spins are largely prevented and moreover, in the transition to DE, signals of a higher amplitude are generated in correspondence with DE which can be used in particular during application of the method in MRT for optimising the image quality and the contrast.

[0036] In the inventive method, a steady state (=balanced state) sequence with flip angles α and alternating phase are preceded by n+1 pulses with different flip angles α0 . . . n wherein the following features are met in the preferred implementation:

[0037] initialisation of the sequence is effected with a radio frequency pulse of a flip angle of α0>α/2. Generally α0=90°. This radio frequency pulse preferably precedes the sequence with a time delay of TR/2 analogously to the method described in DE 44 27 497 A1.

[0038] all α1 . . . n are larger than α and are selected such that the transverse magnetization Mtr1 . . . n formed at each reading time is formed symmetrically or almost symmetrically to the z axis. After initialisation with a 90° pulse, α1 is set to 180° or at least close to 180°. The flip angles of the subsequent radio frequency pulses drop monotonically to α wherein their phase alternates.

[0039] Accurate selection of α1 . . . n thereby depends on the desired signal intensities such that there are a plurality of possible and reasonable values for α1 . . . n within the scope of the defined conditions.

[0040] In a particularly simple and hence often preferred implementation, linear variation between α1=180° and αn=α is possible, wherein n is a freely selectable parameter.

[0041] FIG. 7 shows the advantage of this implementation compared to conventional implementation: On the one hand, Mss is obtained in a few steps, wherein the signal amplitudes in the first n excitation steps are considerably higher than those with conventional implementation.

[0042] FIG. 8 shows that this also drastically reduces the modulations of the off-resonance spins such that the image artefacts, which currently occur during use of these signals are highly reduced.

[0043] The quality of this particularly favorable off-resonance behavior can be explained such that with flip angles in the vicinity of 180°, the spin echo character of the signals increases which is known to be characterized by a particularly favorable behavior compared to off-resonance spins.

[0044] FIGS. 9 and 10 show that with a slow transition of the flip angles whose contribution is changed here by merely 5°, the signal behavior is further improved and the signal intensities approach monotonically Mss.

[0045] A quantitative analysis of the signal behavior is possible by means of the numerical solutions of the Bloch equation. The person skilled in the art can easily calculate therefrom corresponding flip angles for other suitable implementations.

[0046] A second and often advantageous approach for a selection of α1 . . . n consists in setting the flip angles α1 . . . n-1 to exactly or almost 180° after preparation by a 90° pulse. It is thereby important to set the nth radio frequency pulse to 90°+α/2 to transfer the spins which are present as purely transverse magnetization after each α1 . . . n to the plane valid for Mss (FIG. 11).

[0047] Selection of n which is suitable for a given application thereby depends mainly on the relaxation time T2. FIG. 12 shows the intensities for the pulse sequence shown in FIG. 11 for the selected values of T1=50 ms, T2=25 ms.

[0048] Even for n=0, i.e. initialisation with a 90°, 90°+α/2 sequence, off-resonance behavior is obtained which is advantageous compared to the conventional sequence. If N is selected such that n*TR>=T2, the signal decays towards zero and recovers again only slowly in the subsequent alternating pulse sequence with α with T1 towards Mss (FIG. 13). In this manner, signals with short T2 can be very effectively suppressed for tissue with T1>>T2.

[0049] Appropriate selection of n permits variation of the T2 contrast of the signals and with corresponding selection of phase encoding, of the corresponding images: A long sequence of initial 180° pulses produces a strong T2 contrast whereas a less distinct T2 contrast is formed with only a few initial 180° pulses.

[0050] Finally, it should be noted that the magnetization which is in or close to the steady state Mss can be transferred back to a purely transverse magnetization by a radio frequency pulse with a flip angle of 90+α/2 to be transferred back into the steady state by a subsequent sequence of radio frequency pulses which again meet the above typical criteria of the method.

[0051] Such repetition of several periods of pure 180° pulses with alternating phase is shown in FIG. 14. FIG. 15 shows the corresponding magnetizations.

[0052] The method can be combined with the additional contrast modifications shown in DE 44 27 497 A1 by corresponding preparation pulses or pulse sequences. In addition to the frequently used two-dimensional Fourier transformation, phase encoding can be effected in a three-dimensional phase encoding method.

[0053] Recordings of several slices by sequential excitation of parallel slices are also possible and can be realized for obtaining images of corresponding contrast and in a manner straightforward to the expert.

[0054] Change of the phase relation of subsequent radio frequency pulses different from the phase alternation up to now is possible which can be used for optimising signals of off-resonant spins (e.g. for separating fatty vs. water signals). Towards this end, the phase offset Δφ=TRΔΩ of the pulses corresponding to the off-resonance spins to be observed is subtracted from the alternating phase (corresponds to 180° of the phase change of subsequent radio frequency pulses).

[0055] Logical transfer of the method to methods for image encoding according to other methods as e.g. filtered back projection is also within the scope of the present invention.

Claims

1. Method of NMR (=nuclear magnetic resonance) tomography for producing NMR gradient echo signals according to the principle of signal generation in the driven equilibrium (DE) or also steady state free precession (SFP) wherein a periodic sequence of radio frequency pulses with a flip angle α is applied with a time delay TR wherein the phase of these radio frequency pulses is alternated in subsequent steps, characterized in that

2. Method according to claim 1, characterized in that in addition to the sequence of radio frequency pulses, magnetic field gradients are applied for encoding an MR image corresponding to a two- or multi-dimensional Fourier transform method such that through application of a slice selection gradient during the radio frequency pulses a slice is selected; a gradient echo is formed by application of a read gradient which is initially switched like a gradient echo method and then amplitude-reversed, phase encoding is performed before reading of the gradient echo.

3. Method according to claim 2, characterized in that phase encoding is effected through application of a phase encoding gradient perpendicular to the read gradient in the sense of a two-dimensional Fourier transform method.

4. Method according to claim 2, characterized in that phase encoding is effected through application of several phase encoding gradients in perpendicular directions to the phase encoding in the sense of a multi-dimensional Fourier transform method.

5. Method according to claim 1, characterized in that with alternating phase, the flip angles α1 . . . n of the radio frequency pulses drop linearly from 180° to α.

6. Method according to claim 1, characterized in that with alternating phase, the flip angles of the radio frequency pulses α1 . . . (n-1) are set to 180° and αn to 90°+α/2.

7. Method according to claim 1, characterized, in that after m radio frequency pulses with m>n initially a radio frequency pulse with flip angle 90°+α/2 is applied such that the formed magnetization in or close to the steady state is transferred into transverse magnetization and subsequently transferred through repetition of the sequence of radio frequency pulses back into the steady state.

8. Method according to claim 7, characterized in that return of the magnetization into transverse magnetization is repeated several times.

9. Method according to claim 1, characterized in that the sequence is preceded by a spin preparation through an inverted pulse for signal weighting with T1.

10. Method according to claim 1, characterized in that application of the magnetic field gradients is performed corresponding to image encoding according to the method of filtered back projection.