METHOD AND ARRANGEMENT FOR SUPPRESSING COHERENT INTERFERENCE EFFECTS IN MAGNETIC RESONANCE SIGNALS

Abstract: IN NMR images, which are constructed from resonance signals, for examples using Fourier zeugmato­ graphy, coherent interference effects resulting, for example, from "Leak-through" of NMR signals from one sequence to a next sequence of resonance signals, can cause artefacts to occur in the images, which, depending upon the kind of interference, become manifest in the image as interference lines, ghost images or conspicuouc dots. A method is proposed for reducing the effect of this interference by smearing the artefacts out over the image as noise. For this purpose, the phase of the reference signals is randomly modulated between successive measure­ ment cycles of the resonance signals. The reference signal is used to form excitation pulses for producing resonance signals in a body and further for the synchronous detection of the resonance signals.

Description: The invention relates to a method of determining the nuclear magnetization distribution from magnetic resonance signals which are produced in sequences in a body located in a steady magnetic field, a sequence comprising at least one high-frequency electromagnetic pulse produced by means of a reference signal, after which the magnetic resonance signal produced is detected in the presence of the reference signal, and the nuclear magnetization distribution is determined from the detected resonance signals by means of a Fourier transformation. The invention further relates to an apparatus for determining a nuclear magnetization distribution in a part of a body, the apparatus comprising means for producing a steady magnetic field, means for producing magnetic field gradients and means for producing a reference signal, as well as transmitter means for transmitting a high-frequency electromagnetic pulse formed in the transmitter means by means of the reference signal and receiver means for receiving and detecting by means of the reference signal a resonance signal which is produced by at least one high-frequency electromagnetic pulse in the body, and processing means for processing the detected resonance signals. The term "nuclear magnetization distribution" is to be interpreted in a wide sense, while inter alia terms like "spin nuclei density distribution", "longitudinal relaxiation time (T₁) distribution", "transversal relaxiation time (T₂) distribution" and "nuclear magnetic resonance frequency spectrum distribution" (NMR position-dependent spectroscopy) are to be understood to be included in the term" nuclear magnetization distribution." Such a method and such an arrangement are known from the article by Locher in "Philips Technical Review", Volume 41, 1983/84, No. 3. In such a method, a body to be examined is arranged in a steady magnetic field B O , whose direction coincides with the axis of a stationary Cartesian coordinate system. The presence of the magnetic field B O has the result that a small excess number of the spin nuclei present in the body has the same direction, magnetically, as the field B O . The fact that there is only a small excess with respect to the theoretically possible saturation value (all spins having the same direction) is due to thermal motion, as a result of which a large number of spin nuclei assume a direction opposite to that of the field. The small excess is to be interpreted, considered macroscopically, as a magnetization M of the body or as a small polarization of the spin nuclei present in the body. After irradiation of the body arranged in the magnetic field by a high-frequency electromagnetic pulse, which should have a given frequency, the magnetization M is unbalanced and will perform a precessional motion about the direction of the magnetic field B O . When the precessional motion is considered from a rotating Cartesian coordinate system (x, y, z) whose z axis coincides with the z axis of the said stationary Cartesian coordinate system, and when the angular velocity of the rotating Cartesian coordinate system is chosen to be equal to the angular frequency of the high-frequency electromagnetic pulse, the magnetization M is to be interpreted as a vector, which due to the irradiation moves in a plane at right angles to the direction of irradiation. The component of the magnetization M at right angles to the z axis, i.e. the so-called transversel magnetization, has the result that after irradiation a resonance signal is obtained. For the angular frequency of the high-frequency electromagnetic pulse, the relation ω O = γ.B O must hold in order that the spin nuclei will perform a "Larmor" precessional motion about the direction of the magnetic field M, wherein ω O is the precessional angular frequency (of protons if a spin nuclei density distribution of protons is desired), γ is the gyromagnetic ratio (of the proton) and B O is the strength of the steady magnetic field. The high-frequency electromagnetic pulses are formed by transmitter apparatus in which the pulse is produced by modulation of a reference signal which is supplied by an oscillator and has a frequency (in the proximity of) ω O with a low-frequency signal determining the pulse shape, after which the pulse is transmitted by the transmitter apparatus by means of a transmitter coil located near the body. The magnitude of the transverse magnetization is determined by the surface area below the pulse. A 90° pulse is concerned when the magnetization rotates through 90° with respect to the direction of the magnetic field B O as a result of the pulse. The resonance signal produced by the high-frequency electromagnetic pulse can be detected with a receiver coil by means of receiver apparatus employing so-called quadrature phase-sensitive detection, the reference signal and a signal obtained by shifting the phase of the reference signal through 90° being employed. It can be simply demonstrated that the detected resonance signal, except for a constant factor, represents the transverse magnetization. When resonance signals are produced in a given manner in sequences in the body, it is possible, for example, by processing means to reconstruct a proton density distribution from the information obtained from the resonance signals. For example, in general and also from the said article by Locher the so-called spin echo sequence is known for producing the resonance signals, and the technique of so-called "Fourier zeugmatography" is known for image formation from the resonance signals. For example, in order to obtain information about a local proton density in the body, it is necessary not only to irradiate the body by high-frequency electromagnetic pulses, but also to apply magnetic field gradients, whose field direction coincides with that of the magnetic field B O . It is shown in the article by Locher that there is a direct relation between a frequency component of the resonance signal and a local proton density (position). By the application of a magnetic field gradient to the magnetic field B O having a given gradient direction, a resonance signal is obtained whose spectrum (Fourier transformation of the resonance signal) is, for example, the image of the proton density in the gradient direction. Bidimensional Fourier zeugmatography utilizes this phenomenon. Two gradients are applied for encoding the position-dependent proton density in the body, a so-called preparation gradient, whose gradient direction coincides with the y axis of, for example, a stationary Cartesian coordinate system (x, y, z), assuming in each sequence a different value, and the so-called measurement gradient, whose gradient direction coincides with the x axis, having the same form for each sequence. In cooperation with high-frequency electromagnetic pulses (mostly selectively, i.e. with another magnetic field gradient, whose direction coincides with the z axis, only spin nuclei are selected in a layer at right angles to the z axis), resonance signals are obtained, which after sampling yield sample values. After bidimensional (discrete) Fourier transformation (for example "Fast Fourier transformation") in the processing apparatus, image elements are obtained from the sample values formed, and these image elements together constitute an image, in this case a proton density of a slice of the body. By a suitable choice of magnetic field gradients and high-frequency electromagnetic pulses, tridimensional proton density distributions of frequency spectra can be obtained for each image element (from which an interpretation of the metabolic state of the image element can be given). Due to different causes, when deriving an image by, for example, Fourier zeugmatography, unwanted components occur in the resonance signals, which become manifest in the image as interference lines and/or ghost images (artefacts). The usual NMR equipment has the disadvantage that stringent requirements should be imposed thereon; for example, 180° pulses should have a high degree of perfection and phase shifts between sequences should be optimal in order to prevent signals formed in a sequence from "leaking through" to a following sequence in which a resonance signal is produced. Coherent forms of interference are connected here. Other interference sources also give rise to (coherent) interference effects. Interference sources are inter alia : cross-talk in the high-frequency electronic circuits of transmitter and receiver, coherence between the reference signal and the clock of analog-to-digital converters in the processing means, periodic variations in the gradient strengths, mechanical oscillations of the NMR system. The invention has for an object to considerably reduce the effect of said interference effects, or to ensure that satisfactory use can be made of NMR equipment to which much less stringent requirements have been imposed than on NMR equipment in which the invention is not used. A method according to the invention is characterized in that, for smearing out artefacts obtained due to coherent interferences in the nuclear magnetization distribution, between the respective sequences the value of the phase of the reference signal is varied. A preferred embodiment of a method according to the invention is characterized in that the variation in value is random. Thus, it is achieved that the artefacts, such as interference lines, ghost images (artefacts) or conspicuous dots, caused by in the image coherent interference effects are smeared out over the image as noise having a considerably lower intensity than the intensity of the artefact. It is a matter of course that the additional noise contribution to the image thus obtained must not be large. The invention is based on the recognition of the fact that the phase of the resonance signal to be measured is solely determined by the phase relation of the high-frequency electromagnetic pulses with respect to the reference signal after excitation (rotation of the magnetization vector) and does not depend upon the phase of the reference signal before excitation. The phase of the reference signal may therefore be varied between the sequences, unexceptionally, without disturbing a phase encoding provided by the preparation gradient in the resonance signal. Interference signals whose phase during detection of the resonance signal does depend upon the phase of the reference signal before excitation are therefore no longer coherent with the resonance signals over a large number of sequences and discrimination of the interference signals with respect to the resonance signals occurs. Interference effects becoming manifest in the image as ghost images (artefacts) or interference lines are smeared out as noise, while interference effects which become manifest in the image as conspicuous dots are smeared out to a line having a considerably lower intensity. An embodiment of a method according to the invention is characterized in that the variation in the phase value is systematic. When, for example, the phase between the sequences is increased by a fixed amount, this may result in the artefacts being smeared out in the image as noise. It should be noted that it is known per se from US-A-3,968,424 to influence by means of a magnetic resonance arrangement for spectroscopy phases of high-frequency electromagnetic pulses. The arrangement described in US-A-3,968,424 is designed to determine NMR spectra of a sample to be analysed. For this purpose, pulse trains of high-frequency electromagnetic pulses are produced, while an unequal phase can be given to successive pulses. FID signals originating from many successive pulses are averaged in time and a spectrum of the sample is determined from the resulting signal by means of Fourier transformation. In US-A-3,968,424, no mention is made of image formation by Fourier transformation of resonance signals, which are produced in a number of successive sequences, and of the then occurring coherent interferences between the sequences, these coherent interferences giving rise to image artefacts, such as interference lines, phantom images or conspicuous dots in an image. In US-PS 3,968,424 the object is to avoid artefacts in spectra, which are obtained by too rapid a succession of pulses. Therefore, smearing-out of image artefacts over an image does not occur. An apparatus according to the invention is characterized in that the arrangement comprises means for varying the value of the phase of the reference signal before the transmission of the at least one high-frequency electromagnetic pulse. With such an apparatus, the methods according to the invention can be carried out, as a result of which artefacts are smeared out as noise; for the explanation thereof reference is made to the explanation given for the methods. The invention will be further described with reference to an embodiment shown in the drawings, in which: Fig. 1 shows diagrammatically an NMR arrangement comprising a transmitter and a receiver apparatus for carrying out the method according to the invention, and Fig. 2 shows spin echo sequences for producing resonance signals together with an embodiment for phase variation of the reference signals between the sequences. Fig. 1 shows diagrammatically an NMR arrangement comprising a transmitter and a receiver apparatus 1 , this NMR arrangement further comprising magnet coils 2 fed by a direct voltage supply source 3 for producing a steady magnetic field B O , gradient coils 4 for producing a magnetic field gradient G x , gradient magnet coils 5 for producing a magnetic field gradient G y , gradient magnet coils 6 for producing a magnetic field gradient G z and a transmitter and receiver coil 7. In the embodiment shown, the arrangement of the coils is such that the field direction of the magnetic field gradients G x , G y and G z coincides with the direction of the magnetic field B O and that the gradient directions are at right angles to each other. Furthermore, a transmitter coil and receiver coil required for an NMR arrangement are constructed as the transmitter and receiver coil 7, which should not be considered as a limitation; transmitter coils and receiver coils, which may be combined with each other, are available in a large number of variations. The NMR arrangement further comprises a feeding device 8 for feeding the gradient coils. The feeding device 8 for this purpose comprises outputs 40, 41, 42. The transmitter and receiver apparatus 1 comprises a transmitter device 9 and a receiver device 10 and further an oscillator 11 for producing a reference signal. The transmitter device 9 comprises a modulator 12 for forming a high-frequency electromagnetic pulse, this modulator 12 having a first input 13 for supplying the reference signal and further a second input 14 for supplying a pulse-forming low-frequency signal to be produced by a processing device 15 and a control unit 16. The modulator 12 is coupled by an output 17 to a power amplifier 18, which is coupled to a directional coupler 19. The directional coupler 19 comprises an input/output 51, which is coupled to the transmitter and receiver coil 7. The receiver device 10 comprises a preamplifier 20 for supplying a resonance signal to be produced via an output 50 of the directional coupler 19 with the transmitter coil 7 on a body 21 to be introduced via a patient table 22 into the NMR arrangement and further comprises a quadrature phase-sensitive detector 23 coupled to the preamplifier 20 for demodulation of a resonance signal modulated with the reference signal. The quadrature phase-sensitive detector 23 comprises a first input 24 for supplying the resonance signal to be produced by the oscillator 11 and a second input 25 for supplying a signal to be produced by means of the oscillator 11, this signal being formed from the reference signal by shifting the phase of the reference signal through 90°. The quadrature phase-sensitive detector 23 is adapted to form a first and a second modulated signal from the modulated resonance signal to be supplied by the preamplifier 20 to the quadrature phase-sensitive detector 23 at outputs 26, 27 of the quadrature phase-sensitive detector 23, the first demodulated signal at the output 26 representing a component MLx of a transverse magnetization vector ML (in a rotating coordinate system rotating with the frequency of the oscillator 11) resolved along an x axis and the second demodulated signal at the output 27 representing a component MLy of the transverse magnetization vector ML resolved along a y axis. The outputs 26, 27 of the quadrature phase-sensitive detector 23 are coupled to analog-to-digital converters 28 and 29, respectively, in the processing device 15 . The processing device 15 comprises programmed computer means 30 for reconstructing a nuclear magnetization distribution from demodulated resonance signals sampled via the analog-to-digital converters 28, 29. A display screen 31 coupled to the programmed computer means 30 is intended inter alia to display the nuclear magnetization distribution to be represented, for example via intensity differences, on the display screen 31. The control unit 16 is coupled to the processing device 15 . Furthermore, the control unit 16 is coupled to the input 32 of the oscillator 11. Via the programmed computer means 30 and the control unit 16, the frequency of the oscillator 11 can be modified. When a frequency modified with respect to a frequency ω O is maintained for a given time and this frequency is then reset to the frequency ω O of the oscillator 11, a phase jump can be obtained in the signal to be produced at the output 33 of the oscillator 11. Furthermore, the control unit 16 is coupled via outputs 43, 44, 45 to inputs 46, 47, 48 for driving the feeding device 8. In Fig. 2, spin echo cycles are shown for producing resonance signals, the phase of a reference signal 60 obtained by the oscillator 11 being modified between a sequence n and a sequence n + 1 in the time interval n′. The frequency of the reference signal 60 is not drawn to scale with respect to the sequences n and n + 1 and to the time interval n′ for the sake of clarity. By way of example, the spin echo sequence n shown for producing a resonance signal 61 will be described, after which there is indicated how a phase variation between the sequences n and n + 1 is obtained. A method of determining a nuclear magnetization from magnetic resonance signals 61 produced in sequences in a body 21 is carried out with an NMR arrangement described with reference to Fig. 1. The method comprises the repetition of a spin echo sequence (or any other pulse gradient sequence), the sequence being repeated so frequently that a sufficient quantity of information is collected by means of resonance signals 61 about, for example, (a part of) the body 21 so that, for example, a spin nuclei density distribution may be reconstructed therefrom by the programmed computer means 30 in the processing device 15 . For this purpose, in the embodiment shown, a number of spin nuclei are resonantly selectively excited in the body 21 in a number of cycles by exciting in the presence of a magnetic field gradient 62 in the z direction G z produced from the central unit 16 driven by the programmed computer means 30, the spin nuclei by means of a high-frequency electromagnetic pulse 63 (having a given band width around the frequency ω O of the oscillator 11) produced by the transmitter device at the instant t₁ and also from the control unit 16 driven by the programmed computer means, which pulse is, for example, a so-called 90° pulse, that is to say a pulse which rotates through 90° a magnetization vector M (not shown) in a plane at right angles to the z axis. The spin nuclei rotated (selectively) at right angles to the z axis will perform a precessional movement around the magnetic field B O , but will be shifted in phase (lose their coherence) between the instants t₁ and t₂. After excitation with the high-frequency electromagnetic pulse 63, the magnetic field gradients G x and G y , 64, 65, are activated for encoding the resonance signal 62. G x is then fixed and G y , the so-called preparation gradient, assumes a different value for each sequence. Subsequently, G z is activated again (66) and the body 21 is (selectively) excited with a 180° pulse (67). Due to the fact that the excited spin nuclei are brought into phase again, after the instant t₂ the resonance signal 61 will occur (echo) around the instant t₃, which resonance signal 61 is sampled after demodulation by the quadrature phase-sensitive detector 23 by the analog-to-digital converters 28, 29, which are driven via the programmed computer means 30. Subsequently, the frequency of the oscillator 11 is varied in the period n′ by the control unit 16, which is driven from the programmed computer means 30, as a result of which a phase shift is obtained in the resonance signal produced by the oscillator 11. When either the duration of the period n′ or the frequency sweep Δω is varied from the programmed computer means 30, the extent of the phase shift can be controlled. Subsequently, a next sequence n + 1 is started and the pulse/gradient sequence described for the period n is repeated. The programmed computer means 30 reconstruct from sampled values (not shown) obtained by a large number of resonance signals 61 the spin nuclei density distribution with, for example, a bidimensional discrete Fourier transformation (in the embodiment shown, two dimensions are obtained: by variation of the preparation gradient and by sampling); this is a generally known method of reconstructing images from sampled values, in NMR. (FFT Fast Fourier Transform is a known algorithm in this context). Preferably, in the method described, the value of the phase of the reference signal 60 is varied randomly, as a result of which coherent interference effects, which become manifest, for example, as interference lines in an image without the use of the method, are smeared out as noise in the image with the use of the method. The class of interference effects reduced by the method according to the invention comprises NMR signals, which "leak through" from one sequence to a next sequence, for example from the sequence n to the sequence n+1. This may be due, for example, to pulse imperfections or non-optimal phase shifts (after the echo 61, all the excited spin nuclei should return after a waiting time to a state of equilibrium in the direction of B O ; in practice, there is not time to wait until all the spin nuclei have returned to the state of equilibrium. Spin nuclei which have not returned to the state of equilibrium and also those which have not correctly shifted in phase can both provide a contribution to the resonance signal 61 in the next cycle). With coherence over several sequences, these interference effects become manifest as interference lines or ghost images (artefacts) in the reconstructed image. Thus, coherent interference effects may be obtained by cross-talk in the transmitter and receiver apparatus 1 . If, for example, there is coherence between the reference signal and the drive of the analog-to-digital converters 28, 29, interference effects occur, which become manifest in the reconstructed image as conspicuous dots. The method according to the invention smears these conspicuous dots out into a line having a considerably lower intensity. Furthermore, there is a reduction in the coherent interference effects which is caused, for example, by hum from the feeding STET device 8 for the gradient coils 4, 5, 6, and also in the coherent interference effects caused by mechanical oscillations in the NMR arrangement (for example typically having a frequency of 8 Hz; for example vibrations in the floor or vibrations in the patient table 22). The last-mentioned interference effects cause phantom images in the absence of the method according to the invention herein described.

Claims: 1. A method of determining a nuclear magnetization distribution from magnetic resonance signals which are produced in sequences in a body located in a steady magnetic field, a sequence comprising at least one high-frequency electromagnetic pulse which is produced by means of a reference signal, after which the magnetic resonance signal produced is detected in the presence of the reference signal and the nuclear magnetization distribution is determined from the detected resonance signals by means of a Fourier transformation, characterized in that, for smearing out artefacts obtained due to coherent interferences in the nuclear magnetization distribution, between the respective sequences the value of the phase of the reference signal is varied. 2. A method as claimed in Claim 1, characterized in that the variation in value is random. 3. A method as claimed in Claim 1, characterized in that the variation in value is systematic. 4. A method as claimed in Claim 1, 2 or 3, characterized in that the phase of the reference signal is varied between the sequences by giving the reference signal a predetermined frequency sweep for a predetermined period of time. 5. An apparatus for determining a nuclear magnetization distribution in a part of a body, this arrangement comprising means (2) for producing a stationary magnetic field, means (4, 5, 6) for producing magnetic field gradients and means for producing a reference signal (11), as well as transmitter means (9) for transmitting a high-frequency electromagnetic pulse which is formed in the transmitter means by means of the reference signal, and receiver means (10) for receiving and detecting by means of the reference signal a resonance signal which is excited in the body by at least one high-frequency electromagnetic pulse, and processing means (15) for processing the detected resonance signals, characterized in that the apparatus comprises means (16, 30) for varying the value of the phase of the reference signal before the transmission of the at least one high-frequency electromagnetic pulse.

Inventors: VAN DER MEULEN, PETER
Applicants: N.V. PHILIPS' GLOEILAMPENFABRIEKEN
Application year: 1988
Main classification: G01R33
IPC codes: A61B10, G01R33, A61B5