Method and apparatus for magnetic resonance imaging

Abstract: In a magnetic resonance imaging method multiple refocusing RF-pulses (22-26) are applied and spin-echo signals (62-66) obtained following an excitation RF-pulse (21). Imperfections in the applied RF-pulses (21-26) and the switched gradient magnetic fields (31-36, 42-46, 51-56) cause deviations from the desired phases of the nuclear dipole moments which appear as artefacts or ghosts in a resulting image. By a suitable arrangement of the application of the phase encoding values (242-248; 342-348) imposed during the measurements and/or the addition of supplemental measurements, the effects of the phase deviations in an image are significantly reduced, resulting in images in which less artefacts and ghosts are visible. Reduction of artefacts is also obtained by weighting of measured NMR-signals.

Description: The invention relates to a method for magnetic resonance imaging of a body placed in a stationary and substantially homogeneous main magnetic field, the method comprising the application of an excitation radio-frequency pulse (RF-pulse) for excitation of nuclear dipole moments in at least a portion of the body, the application of a plurality of refocusing RF-pulses following said excitation RF-pulse and of gradient magnetic fields for generating position dependent magnetic resonance signals in the excited portion, the gradient magnetic fields and/or refocusing RF-pulses providing phase encoding of nuclear dipole moments with actual phase encoding values having deviations from nominal phase encoding values, the measurement of a set of magnetic resonance signals, the set comprising signals which follow at least a number of said refocusing RF-pulses, the transformation of said set of measured magnetic resonance signals into an image, the set of signals being altered prior to said transformation for reducing the effect on said image of the deviations between said actual and said nominal phase encoding values. The invention also relates to an apparatus for magnetic resonance imaging using such a method. Such a method for imaging is known from US 5,068,609. The known method is used to reduce the presence of ghosts in the reconstructed image. In the known method the alteration of the set of measured magnetic resonance signals comprises a division of the set in two sub-sets. A first subset containing the even-number rows of said set and a second subset containing the odd-number rows of said set, setting the entries in the remaining rows of the subsets to zero. After Fourier transformation two intermediate images are reconstructed which intermediate images are combined to a single resulting image. It is, inter alia, an object of the invention to provide an alternative magnetic resonance method in accordance to the introductory paragraph in which artefacts in the resulting image are significantly suppressed. Thereto the method according to the invention is characterised in that the alteration of the set of measured signals comprises the measurement of equivalent signals for a substantial fraction of the measured signals to provide two measurements for each phase encoding value and the averaging of measurements of the signal and the equivalent signal for each phase encoding value, the difference between the actual phases and the nominal phases for said signals and said equivalent signals being substantial opposite. The invention is based upon the realisation that artefacts in the image largely result from incorrect phases and angles imposed locally upon the magnetisation vector and the realisation that small phase errors may cause artefact levels comparable to those due to relatively large amplitude modulations. The invention is also based upon the further realisation that the imperfect RF-pulses and gradient field pulses cause not a random phase deviation but a phase modulation that can largely be compensated for by alteration of the total set of measurements input to the image forming transformation. The alteration of the set of measurements includes addition of a further measurements by providing two measurements for each phase encoding value, the two measurements having opposite phase deviations. The effects of the deviation in the phase encoding values is thereby mitigated. In a first embodiment of the method according to the invention, wherein signals are measured in a plurality of sequences, each sequence comprising an excitation RF-pulse, a plurality of refocusing RF-pulses alternated with measurements of magnetic resonance signals and switched gradient magnetic fields for phase encoding, wherein for a substantial fraction of the sequences an equivalent sequence is executed in which the same gradient magnetic fields are applied to the body in time-reversed order for time-reversed detection of equivalent measured signals, the same phase encoding value occurring in one sequence in an odd rank number and in the equivalent sequence in an even rank number. In this realisation, as an additional advantage, the decrease in signal amplitude due to spin-spin relaxation, the T 2 -decay, within a sequence is compensated by providing identical measurements but with different signal amplitudes. The effect of amplitude modulation due to the T 2 -decay, leading to blurring and ringing artefacts in the resulting image, is reduced. In a second embodiment of the method according to the invention, wherein signals are measured in a plurality of sequences, each sequence comprising an excitation RF-pulse, a plurality of refocusing RF-pulses alternated with measurements of magnetic resonance signals and switched gradient magnetic fields for phase encoding, the equivalent measurements are obtained in an equivalent sequence in which the same gradient magnetic fields are applied to the body in pairwise swapped order. Also in this embodiment the even/odd behaviour of phase deviations over NMR-signals is averaged. This embodiment provides good results, in particular, if the phase variation is not a simple phase alternation. In such circumstances averaging is useful only between signals that are near each other and subject to approximately the same phase deviations. If the number of NMR-signals measured in each sequence is odd one signal remains unpaired and unswapped, this has only little effect upon the quality of the resulting image. In a third embodiment of the method according to the invention, the equivalent measurements are obtained with the same gradient magnetic field and following subsequent refocusing RF-pulses. If a measurement with the same phase encoding value is to be repeated, for example, because of signal to noise considerations, the measurements with identical phase encoding values are made in the same sequence. Again, the disturbances in phase encoding values due to eddy currents and RF-pulse imperfections are averaged because of the even-odd behaviour of the phase deviation. The number of measurements at each phase encoding value is preferably even for optimum cancelation. An additional advantage of this embodiment is that if the variation in the magnitude of the gradient pulses is gradual, the effect upon the phases of the spins due to eddy currents caused by switching the gradient magnetic fields are to a large extend compensated in subsequent spin-echoes. In the method according to the invention wherein the refocusing RF-pulses have a value deviating from 180°, and have preferably a value of around 150°. By using a flip-angle other than 180° for the refocusing RF-pulses an exchange between phase and amplitude modulation in the NMR-signals is possible. As artefacts due to phase modulation are suppressed in the invented method, a total reduction of the presence of artefacts can be obtained. The invention also relates to an apparatus for performing such a method. An apparatus according to the invention for magnetic resonance imaging of a body placed in a stationary and substantially homogeneous main magnetic field according to a method as claimed in any of the method claims, the apparatus comprising means for establishing the main magnetic field, means for generating gradient magnetic fields superimposed upon the main magnetic field, means for radiating RF-pulses towards a body placed in the main magnetic field, control means for steering the generation of the gradient magnetic fields and the RF-pulses, and means for receiving and sampling magnetic resonance signals generated by sequences of RF-pulses and switched gradient magnetic fields, said control means being arranged for applying an excitation radio-frequency pulse for excitation of nuclear dipole moments in at least a portion of the body, applying a plurality of refocusing RF-pulses following said excitation RF-pulse and gradient magnetic fields for generating position dependent magnetic resonance signals in the excited portion, measurement of a set of magnetic resonance signals, the set comprising signals which follow at least a number of said refocusing RF-pulses, the apparatus further comprising means for transforming the set of measured magnetic resonance signals into an image, and means altering the set of signals prior to said transformation for reducing the effect on the image of deviations between actual and nominal phase encoding values, deviations which are due to the refocusing RF-pulses and/or switched gradient magnetic fields characterised in that the means altering the set of measured signals being further arranged for the measuring of equivalent signals for a substantial fraction of the measured signals to provide two measurement for each phase encoding value and the averaging of the measurements of the signals and the equivalent signals for each phase encoding value, the difference between the actual phases and the nominal phases for said signals and said equivalent signals being substantial opposite. The alteration of the set of measurements for reduction of artefacts has as an advantage that it is not necessary to modify the construction of the MRI apparatus. In particular, shielding of the coils for generating the gradient magnetic fields in order to reduce the effects of eddy currents can be reduced or done away with completely. These, and other more detailed aspects of the invention will now be elucidated by way of example with reference to the accompanying drawings. The drawings show in Figure 1 diagrammatically a magnetic resonance imaging apparatus, suitable for the method according to the invention; Figure 2 a sequence of an excitation RF-pulse, a plurality of refocusing RF-pulses, gradient magnetic fields and the occurrence of NMR-signals as a function of time; Figures 3a and 3b two sequences of RF-pulses and gradient magnetic fields according to a first embodiment of the invention; Figures 4a and 4b the relative T 2 -decay of a single sequence and of two combined sequences according to the first embodiment; Figures 5a and 5b the central part of the modulus of the point spread function for a single sequence and for two combined sequences according to the first embodiment; Figures 6a and 6b sequences of RF-pulses and gradient magnetic fields according to another embodiment of the invention; Figure 7 a sequence of RF-pulses and gradient magnetic fields according to a further embodiment of the invention; and in Figures 8a and 8b an illustration of phase variations between different NMR-signals. In figure 1 is a magnetic resonance apparatus 1 diagrammatically shown. The apparatus comprises a set of main magnetic coils 2 for generating a stationary homogeneous main magnetic field and several sets of gradient coils 3, 4 and 5 for superimposing additional magnetic fields with controllable strength and having a gradient in a selected direction. Conventionally, the direction of the main magnetic field is labelled the z direction, the two directions perpendicular thereto the x and y directions. The gradient coils are energised via a power supply 11. The apparatus further comprises emitting means 6 for emitting radio-frequency pulses (RF-pulses) to an object or body 7, the radiation means being coupled to modulating means 8 for generating and modulating of the RF-pulses. Also provided are means for receiving the NMR-signals, these means can be identical to the emitting means 6 or be separate. If the emitting and receiving means are identical, as shown in the figure, a send-receive switch 9 is arranged to separate the received signals from the pulses to be emitted. The received NMR-signals are input to receiving and demodulating means 10. The emitting means 6 and 8 and the power supply 11 for the gradient coils 3, 4 and 5 are steered by a control system 12 to generate a predetermined sequence of RF-pulses and gradient field pulses. The demodulation means is coupled to a data processing unit 14, for example a computer, for transformation of the received signals into an image that can be made visible, for example on a visual display unit 15. If the magnetic resonance apparatus 1 is put into operation with an object or body 7 placed in the magnetic field, a small excess of nuclear dipole moments (nuclear spins) in the body will be aligned in the direction of the magnetic field. In equilibrium, this causes a net magnetisation M 0 in the material of the body 7, directed in parallel with the magnetic field. In the apparatus 1 the macroscopic magnetisation M 0 is manipulated by radiating to the body RF-pulses having a frequency equal to the Larmor frequency of the nuclei, thereby bringing the nuclear dipole moments in an exited state and re-orienting the magnetisation M 0 . By applying the proper RF-pulses, a rotation of the macroscopic magnetisation is obtained, the angle of rotation is called the flip-angle. The introduction of variations in the magnetic field by applying gradient magnetic fields influences the behaviour of the magnetisation locally. After the application of RF-pulses, the changed magnetisation will strive to return to a state of thermal equilibrium in the magnetic field, emitting radiation in the process. A well chosen sequence of RF-pulses and gradient field pulses causes this radiation to be emitted as NMR-signals which provide information about the density of a certain type of nuclei, for example hydrogen nuclei, and the substance in which they occur. By analysis of the emitted signals and presentation of it in the form of images, information about the internal structure of the object or body 7 is accessible. For a more detailed descriptions of magnetic resonance imaging (MRI) and MRI-devices reference is made to the extensive literature on this subject, for example to the book "Practical NMR Imaging", edited by M.A. Foster and J.M.S. Hutchinson, 1987, IRL Press. Figure 2 shows a known sequence of RF-pulses and magnetic field gradients for obtaining multiple spin-echo NMR-signals following a single excitation pulse. In the upper line RF the start of the sequence is indicated with an excitation RF-pulse RF-pulse 21 having a flip-angle α, followed after an interval τ 1 by a first refocusing 22 having a flip-angle β. Normally, the values of a and β are 90° and 180°, respectively. Following the excitation RF-pulse 21, a free induction decay (FID) nuclear magnetic resonance signal 61, indicated on the lower line NMR, is generated which dies out rapidly when the individual precessing nuclear magnetic dipole moments lose phase coherence due to local variations in the magnetic field. The refocusing RF-pulse 22 reverses the direction of these individual magnetic dipole moments without affecting the local magnetic field. Consequently, the dephasing is reversed into a rephasing resulting after an equal interval τ 1 in the occurrence of a NMR spin-echo signal 62. After the spin-echo signal 62 the dipole moments dephase again. Repetition of refocusing RF-pulses 23, 24, 25 and 26 cause subsequent reversals of the dephasing and the repeated occurrence of NMR spin-echo signals 63, 64, 65 and 66. Due to non-compensated effects, mainly spin-spin relaxation with a time constant T 2 , the magnitude of subsequent echoes decreases in time. The interval lengths τ 2 , τ 3 , τ 4 and τ 5 between an NMR-signal and the next refocusing RF-pulse are normally chosen to be equal in length. The effect of the RF-pulses is made selective to a portion of the body 7 by applying, simultaneously with the RF-pulses a slice selection gradient, which is indicated on the second line G s in the figure. As indicated by 31 the slice selection gradient is first applied during the excitation RF-pulse 21. The dephasing caused by this first gradient 31 is compensated by an opposite gradient 31'. Also during the application of the refocusing RF-pulses 22-26 slice selection gradients 32-36 are switched on. For position determination within the selected slice, phase encoding gradient pulses 42, 43, 44, 45 and 46 with the gradient direction within the selected slice, indicated on the third line G p , are applied in the interval between the RF-pulse and the NMR spin-echo signals 62, 63, 64, 65 and 66. In addition, frequency encoding or read gradients 52, 53, 54, 55 and 56, indicated on the fourth line G r , having a gradient direction also within the selected slice but perpendicular to the gradient direction of the phase encoding field, are switched on during the occurrence of the spin-echo signals. The dephasing effects of the phase encoding gradients is removed after the occurrence of the spin-echo signals by applying further gradient field pulses 42', 43', 44', 45' with the same time-integrated size but with the gradient direction opposite compared to the preceding gradient pulses 42, 43, 44, 45, respectively. The dephasing effect of the read gradients 52, 53, 54, 55 and 56 is compensated for by the refocusing RF-pulses. An initial dephasing gradient 51 preceding the first refocusing RF-pulse 22 is then necessary, this initial dephasing gradient 51 has half the time-integrated size of the read gradients 52, 53, 54, 55 and 56. Alternatively, not a slice but a volume portion of the body can be selected. In that case the slice selection gradient G s may be absent or adopted for selection of a thick section of the body. In addition to the mentioned gradient fields, a second phase encoding gradient magnetic field G p , is applied having a gradient direction perpendicular to the gradient directions of the first phase encoding field G p and the read gradient field G r . Like the first phase encoding field G p , this second gradient encoding field is applied as a series of gradient pulses 72, 73, 74, 75, 76, following the RF-pulses and compensating gradient pulses 72', 73', 74', 75', following the NMR-signals. As indicated by horizontal lines in gradient pulses 72-76 and 72'-76', the size of the second phase encoding gradient pulses are kept constant when the first phase encoding gradient pulses are varied. Alternatively, the first phase encoding gradient pulses 42-46 and 42'-45' may be kept constant and the second phase encoding gradient pulses be varied within a sequence. Hereinafter, the embodiments of the invention are described in the two-dimensional slice selection mode. However, extension to three-dimensional volume imaging by the application of a second phase encoding field is straightforward. After acquisition of the NMR-signals, for example 256 spin-echo signals each with a different phase encoding value and each sampled 256 times, the total set of measurements is converted into an image by means of a Fourier transform (FT). As a consequence of the above described procedure two kinds of image errors may appear in the resulting image. The first is that the signal size of subsequent NMR-signals in a sequence reduces due to spin-spin relaxation, the T 2 -decay, this causes blurring in the resulting image. A second, and as it appears, more important source of image errors is that imperfections in the switched gradient magnetic field pulses and the refocusing RF-pulses cause residual phase effects in the spins. These residual phase effects provide a false position information and show as artefacts and ghosts in the image after Fourier transformation. The residual phase effects caused by the refocusing RF-pulses is due to the presence of the slice selection gradient, that prohibits a uniform flip-angle β to occur across the full thickness of the selected slice. The imperfections in the gradient magnetic field pulses are due to timing errors and eddy currents in the gradient coils for generating the gradient fields. These timing errors and eddy currents influence the time-integrated size of the gradient pulses. Consequently, some residual gradient field is left after each measurement cycle, the residual gradient field causing an additional and undesired phase encoding effect. In figures 3a and 3b, two sequences of RF-pulses and gradient magnetic field pulses for obtaining NMR-signals according to a first embodiment of the invention are shown. As the sequences are identical with the sequence shown in figure 2, the phase encoding gradient G P excepted, only the G P gradients and the RF-pulses are shown. The first and last few RF-pulses and accompanying gradient pulses are indicated only. The sequence of phase encoding gradient pulses 242, 243, ..., 248 and 249, shown in figure 3a is linearly decreasing. The sequence of figure 3b has linearly increasing phase encoding gradient pulses 342, 343, ..., 348 and 349, the phase encoding in the two chains being time reversed copies of each other. After executing both sequences there are two measurements for each phase encoding value. If the sequences have an even number of refocusing RF-pulses, one of the two measurements follows an RF-pulse with an even and one with an odd rank number. Consequently, the phase error caused by imperfect RF-pulses and switched gradient fields is in first order opposite and the effect of two measurements is that the errors largely cancel. A second effect is that the T 2 -decay, occurring in the course of a sequence is compensated for as one measurement is taken in the first half of a sequence and one is taken in the second half. In figures 4a and 4b the relative T 2 -decay A(k y ) of a single sequence and of two combined time-reversed sequences is shown as a function of the phase encoding value k y , for 128 different phase encoding values determined in a series of interleaved sequences. As expected, the combined time reversed sequence shows much less amplitude variation. In figures 5a and 5b the central part of the modulus of the point spread function is shown for both situations. As can be seen, the combination of two time-reversed sequences leads to a considerable narrower PSF(y). This indicates that artefacts and blurring due to the phase deviations and T 2 -decay are largely removed in the resulting image. Investigation of the real and imaginary parts of PSF(y) shows that the imaginary part is strongly reduced. Figures 6a and 6b show two sequences of RF-pulses and gradient magnetic field pulses for obtaining NMR-signals according to another embodiment of the invention are shown. Like in figures 3a and 3b, only the G p gradients and the RF-pulses are shown, the other gradient magnetic fields being identical to the ones shown in figure 2. Only the first few RF-pulses and accompanying gradient field pulses are indicated only. The sequence of phase encoding gradient pulses 442, 443, 444, ..., shown in figure 6a is identical to the sequence shown in figure 2. In the sequence of figure 6b the phase encoding gradient pulses 542, 543, 544, ..., are pairwise swapped compared to the earlier sequence. The first (second) phase encoding gradient pulse 542 (543) in the second sequence being equal to the second (first) phase encoding gradient pulse 443 (442) in the first sequence, the third (fourth) phase encoding gradient pulse 544 (545) in the second sequence being equal to the fourth (third) phase encoding gradient pulse 445 (444) in the first sequence, etc. After executing both sequences there are two measurements for each phase encoding value, one following an RF-pulse with an even and one with an odd rank number. If the number of measurements is odd, this method can still be applied by leaving the last measurement unswapped. As in the sequences shown in figures 3a and 3b, the phase errors caused by imperfect RF-pulses and switched gradient fields largely cancel. Despite the fact that the measured NMR-signals have a larger amplitude variation due to the T 2 -decay, this embodiment gives better results in case the phase variation is more complicated than a simple alternation, for example, due to beat causing a phase change effect over a longer portion of a sequence. Examples of such behaviour are shown in figures 8a and 8b, where curve 104 shows a beat pattern with nodes near echo numbers 13 and 26. In figure 7 a further embodiment is shown. As hereinbefore, only the first few RF-pulses and phase encoding gradient pulses are indicated. In this embodiment a, preferably even, number of measurements with identical phase encoding gradients is performed consecutively. In figure 7 the number is two. The first two phase encoding gradient pulses 642 and 643 have identical values, as well as the second two 644 and 645, etc. As the size of the gradient pulses changes only gradually, the effect of eddy currents upon the phase of the nuclear spins is largely compensated due to the refocusing effect of the refocusing RF-pulses. Figures 8a and 8b illustrate phase variations that may occur in a sequence of measuring NMR-signals. A data acquisition sequence, for example, a conventional sequence such as shown in figure 2 or a modified sequence as describe hereinbefore, comprises phase shifts at the level of the nuclear dipole moments, which phase shifts are caused by system imperfections, such as phase errors in the RF-pulses or eddy currents. As the flip angle of the refocussing RF-pulses is not a perfect 180°, the imperfections give rise to oscillations in the NMR-signal phase. The oscillations reduce with increasing rank number of the measured NMR-signal. The same kind of oscillations occur when the flip-angle of the refocusing RF-pulses differ from 180°. In figure 8a curve 101 connects the phases of NMR spin-echo signals occurring in a sequence in which there is a 10° phase deviation between the excitation RF-pulse and the refocusing RF-pulses, and in which the refocusing RF-pulses have a flip-angle of 175°. The curve 102 shows the phase behaviour for measurements with a 170° flip-angle of the refocusing RF-pulse and also a 10° phase deviation between excitation and refocusing RF-pulses. As the flip-angle of the refocusing pulses is not well determined but a distribution of a continuous range of flip-angles, the total contribution vanishes rapidly. This is illustrated in figure 8b, showing the cosine of the total phase contribution cos() for a number of different flip angles as a function of the phase encoding value k y . As the k y values are chosen to be interleaved and increasing with the echoes, the k y value is closely related to the echo number.

Claims: Method for magnetic resonance imaging of a body placed in a stationary and substantially homogeneous main magnetic field, the method comprising the application of an excitation radio-frequency pulse (RF-pulse) for excitation of nuclear dipole moments in at least a portion of the body, the application of a plurality of refocusing RF-pulses following said excitation RF-pulse and of gradient magnetic fields for generating position dependent magnetic resonance signals in the excited portion, the gradient magnetic fields and/or refocusing RF-pulses providing phase encoding of nuclear dipole moments with actual phase encoding values having deviations from nominal phase encoding values, the measurement of a set of magnetic resonance signals, the set comprising signals which follow at least a number of said refocusing RF-pulses, the transformation of said set of measured magnetic resonance signals into an image, the set of signals being altered prior to said transformation for reducing the effect on said image of the deviations between said actual and said nominal phase encoding values, characterised in that the alteration of the set of measured signals comprises the measurement of equivalent signals for a substantial fraction of the measured signals to provide two measurements for each phase encoding value and the averaging of measurements of the signal and the equivalent signal for each phase encoding value, the difference between the actual phases and the nominal phases for said signals and said equivalent signals being substantial opposite. Method according to claim 1, wherein signals are measured in a plurality of sequences, each sequence comprising an excitation RF-pulse, a plurality of refocusing RF-pulses alternated with measurements of magnetic resonance signals and switched gradient magnetic fields for phase encoding, wherein for a substantial fraction of the sequences an equivalent sequence is executed in which the same gradient magnetic fields are applied to the body in time-reversed order for time-reversed detection of equivalent measured signals, the same phase encoding value occurring in one sequence in an odd rank number and in the equivalent sequence in an even rank number. Method according to claim 1, wherein signals are measured in a plurality of sequences, each sequence comprising an excitation RF-pulse, a plurality of refocusing RF-pulses alternated with measurements of magnetic resonance signals and switched gradient magnetic fields for phase encoding, the equivalent measurements are obtained in an equivalent sequence in which the same gradient magnetic fields are applied to the body in pairwise swapped order. Method according to claim 1, wherein the equivalent measurements are obtained with the same gradient magnetic field and following subsequent refocusing RF-pulses. Method according to any one of the preceding claims, wherein the refocusing RF-pulses have a value deviating from 180°, and have preferably a value of around 150°. Apparatus for magnetic resonance imaging of a body (7) placed in a stationary and substantially homogeneous main magnetic field according to a method as claimed in any of the preceding claims, the apparatus comprising means for establishing the main magnetic field (2), means for generating gradient magnetic fields (3,4,5) superimposed upon the main magnetic field, means (6,8) for radiating RF-pulses towards a body (7) placed in the main magnetic field, control means (12) for steering the generation of the gradient magnetic fields and the RF-pulses, and means for receiving (6,10) and sampling magnetic resonance signals generated by sequences of RF-pulses and switched gradient magnetic fields, said control means (12) being arranged for applying an excitation radio-frequency pulse (RF-pulse) for excitation of nuclear dipole moments in at least a portion of the body, applying a plurality of refocusing RF-pulses following said excitation RF-pulse and gradient magnetic fields for generating position dependent magnetic resonance signals in the excited portion, measurement of a set of magnetic resonance signals, the set comprising signals which follow at least a number of said refocusing RF-pulses, the apparatus further comprising means for transforming the set of measured magnetic resonance signals into an image, and means altering the set of signals prior to said transformation for reducing the effect on the image of deviations between actual and nominal phase encoding values, deviations which are due to the refocusing RF-pulses and/or switched gradient magnetic fields characterised in that the means altering the set of measured signals being further arranged for the measuring of equivalent signals for a substantial fraction of the measured signals to provide two measurement for each phase encoding value and the averaging of the measurements of the signals and the equivalent signals for each phase encoding value, the difference between the actual phases and the nominal phases for said signals and said equivalent signals being substantial opposite.

Inventors: MEULEN PETER VAN DER, YPEREN GERRIT HENDRIK VAN, VAN DER MEULEN, PETER, VAN YPEREN, GERRIT HENDRIK
Applicants: KONINKL PHILIPS ELECTRONICS NV, KONINKLIJKE PHILIPS ELECTRONICS N.V.
Application year: 1993
Main classification: G01R33
IPC codes: G01R33