GB1584949A - Creation of Inventions and Patents with Artificial Intelligence

GB1584949A – Imaging systems
– Google Patents

GB1584949A – Imaging systems
– Google Patents
Imaging systems

Download PDF
Info

Publication number
GB1584949A

GB1584949A
GB22292/78A
GB2229278A
GB1584949A
GB 1584949 A
GB1584949 A
GB 1584949A
GB 22292/78 A
GB22292/78 A
GB 22292/78A
GB 2229278 A
GB2229278 A
GB 2229278A
GB 1584949 A
GB1584949 A
GB 1584949A
Authority
GB
United Kingdom
Prior art keywords
field
slice
pulsed
pulse
resonance
Prior art date
1978-05-25
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)

Expired

Application number
GB22292/78A
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)

EMI Ltd

Original Assignee
EMI Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
1978-05-25
Filing date
1978-05-25
Publication date
1981-02-18

1978-05-25
Application filed by EMI Ltd
filed
Critical
EMI Ltd

1978-05-25
Priority to GB22292/78A
priority
Critical
patent/GB1584949A/en

1979-05-16
Priority to US06/039,650
priority
patent/US4315216A/en

1979-05-25
Priority to DE19792921252
priority
patent/DE2921252A1/en

1979-05-25
Priority to JP6551579A
priority
patent/JPS54156596A/en

1981-02-18
Publication of GB1584949A
publication
Critical
patent/GB1584949A/en

Status
Expired
legal-status
Critical
Current

Links

Espacenet

Global Dossier

Discuss

Classifications

G—PHYSICS

G01—MEASURING; TESTING

G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES

G01R33/00—Arrangements or instruments for measuring magnetic variables

G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance

G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]

G01R33/48—NMR imaging systems

G01R33/483—NMR imaging systems with selection of signals or spectra from particular regions of the volume, e.g. in vivo spectroscopy

G01R33/4833—NMR imaging systems with selection of signals or spectra from particular regions of the volume, e.g. in vivo spectroscopy using spatially selective excitation of the volume of interest, e.g. selecting non-orthogonal or inclined slices

G—PHYSICS

G01—MEASURING; TESTING

G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES

G01R33/00—Arrangements or instruments for measuring magnetic variables

G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance

G01R33/28—Details of apparatus provided for in groups G01R33/44 – G01R33/64

G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field

G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils

G—PHYSICS

G01—MEASURING; TESTING

G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES

G01R33/00—Arrangements or instruments for measuring magnetic variables

G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance

G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]

G01R33/48—NMR imaging systems

G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console

G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution

G01R33/565—Correction of image distortions, e.g. due to magnetic field inhomogeneities

G01R33/56572—Correction of image distortions, e.g. due to magnetic field inhomogeneities caused by a distortion of a gradient magnetic field, e.g. non-linearity of a gradient magnetic field

G—PHYSICS

G01—MEASURING; TESTING

G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES

G01R33/00—Arrangements or instruments for measuring magnetic variables

G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance

G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]

G01R33/48—NMR imaging systems

G01R33/58—Calibration of imaging systems, e.g. using test probes, Phantoms; Calibration objects or fiducial markers such as active or passive RF coils surrounding an MR active material

G—PHYSICS

G05—CONTROLLING; REGULATING

G05F—SYSTEMS FOR REGULATING ELECTRIC OR MAGNETIC VARIABLES

G05F7/00—Regulating magnetic variables

Description

PATENT SPECIFICATION
( 11) 1 584 949 ( 21) ( 44) ( 51) Application No 22292/78 ( 22) Filed 25 May 1978
Complete Specification Published 18 Feb 1981
INT CL 3 GO O N 24/08 24/02 ( 19) ( 52) Index at Acceptance Gi N 508 512 522 523 524 525 527 571 ( 72) Inventors: HUGH CLOW PETER ERNEST WALTERS ( 54) IMPROVEMENTS IN OR RELATING TO IMAGING SYSTEMS ( 71) We, EMI LIMITED, a British company of Blyth Road, Hayes, Middlesex, do hereby declare the invention, for which we pray that a patent may be granted to us, and the method by which it is to be performed, to be particularly described in and by the following statement:
The present invention relates to systems for providing images of distributions of a quantity, in a chosen region of a body, by gyromagnetic resonance, particularly nuclear magnetic resonance Such techniques may be used for examining bodies of different kinds However, a particularly beneficial application is the examination of patients for medical purposes.
Nuclear magnetic resonance is known for the analysis of materials, particularly by spectroscopy Recently it has been suggested that the techniques be applied to medical examination to provide distributions of water content or relaxation time constants in sectional slices or volumes of patients Such distributions are similar to, although of different significance from, the distributions of X-ray attenuation provided by computerised tomography systems.
Practical NMR systems operate by applying suitable combinations of magnetic fields to the body being examined, via coil systems, and detecting induced currents in one or more detector coil systems A suitable sequence of pulsed magnetic fields and apparatus to operate that sequence have been devised and are the subject of our co-pending applications nos 22291/78 and 22295/78 (Serial Nos 1584948 and 1584950).
It is an object of this invention to provide an improvement to the systems described therein.
According to one aspect of the invention, there is provided an NMR apparatus, for examining a slice of a body, including means for applying magnetic fields to cause resonance preferentially in said slice, means for applying a pulsed magnetic field having a gradient across the slice to produce phase dispersion in said resonance, and means for sensing a resonance signal induced during said pulsed field, wherein the means for applying the pulsed field is arranged to cause a pulse which does not have a constant level throughout its duration and the means for sensing is caused to sample the induced signal at intervals such that the field integral with respect to time for the pulsed field is substantially the same in each interval between successive samples.
According to another aspect of the invention, there is provided a method of examining a slice of a body by nuclear magnetic resonance, including the steps of: applying magnetic fields to induce resonance preferentially in said slice, applying magnetic fields, including a pulsed field having a gradient across the slice in one direction, to cause phase dispersion of said resonance and sampling a resonance signal in the slice, wherein the gradient field pulse does not have a constant level throughout its duration and the resonance signal is sampled at intervals such that the field integral with respect to time for the pulsed gradient field is substantially the same in each of said intervals.
In order that the invention may be clearly understood and readily carried into effect, it will now be described by way of example with reference to the accompanying drawings, of which:Figure 1 shows the form of the HR field,
Figure 2 shows the relationship of the HR field to the other fields,
Figure 3 a shows the preferred field pulse sequence, Figure 3 b shows the effects of the pulses of Figure 3 a on the proton spin vectors, Figures 4 a and 4 b show in two views the Ho, H and Hy field coils, of a practical NMR or c 1,584,949 machine, Figure 5 shows the Hi field coils of that machine, Figure 6 shows the HZ field coils of that machine, and Figures 7 a and 7 b show the sampling periods in accordance with the invention for two practical gradient pulse shapes.
For the examination of a sample of biological tissue NMR primarily relates to protons, (hydrogen nuclei) of water molecules in the tissue In principle, however, other nuclei could be analysed; for example, those of deuterium, tritium, fluorine or phosphorus.
Protons each have a nuclear magnetic moment and angular momentum (spin) about the magnetic axis If then a steady magnetic field HO is applied to the sample, the protons align themselves with the magnetic field, many being parallel thereto and some being anti-parallel so that the resultant spin vector is parallel to the field axis Application of an additional field Hi which is an R F field of frequency related to
H., in a plane normal to H, cause resonance at that frequency so that energy is absorbed in the sample The resultant spin vectors of protons in the sample then rotate from the magnetic field axis (z-axis) towards the plane orthogonal thereto (x,y) The R F.
field is generally applied as a pulse and if f Hi dt for that pulse is sufficient to rotate the resultant spin vectors through 900 into the x,y plane the pulse is termed a 900 pulse.
On removal of the Hi field the equilibrium alignments restablish themselves with a time constant Ti, the spin-lattice relaxation time.
In addition, a proportion of the absorbed energy is re-emitted as a signal which can be detected by suitable coils, at the resonant frequency This free resonance signal decays with a time constant T 2 and the emitted energy is a measure of the water content of the sample.
As so far described, the resonance signal detected related to the entire sample If individual resonance signals can be determined for elemental samples in a slice or volume of a patient then a distribution of proton densities, in effect of water content, can be determined for that slice or volume.
Additionally, or alternatively, it is possible to determine a distribution of T or T 2.
In general, the principles of analysing proton density by NMR in a slice of a body have been extensively discussed The known techniques have been reviewed by P Mansfield in Contemp Phys 17 (b) 1976, 553-
576 Consequently the techniques will only be discussed in detail herein to the extent necessary to understand the improved arrangement of this invention.
In the embodiment discussed herein, the examination is particularly of a crosssectional slice of the patient, although examination of a larger volume is possible at least by examination of a plurality of adjacent slices, or by a specifically volume scan.
The first step is to ensure that resonance 70 occurs (at the chosen frequency) only in the selected slice Since the resonance frequency (the Larmor frequency) is related to the value of HO, the slice selection is achieved by imposing a gradient on HO SO 75 that the steady field is of different magnitude in different slices of the patient The steady and uniform HO field is applied as before, usually longitudinal to the patient.
An additional magnetic field H is also 80 applied, being a gradient Hz = a H If then a z the pulsed Hi field is applied at the appropriate frequency, resonance only occurs in that slice in which the resonance frequency as set by H O and the local value of HZ, is 85 equal to the frequency for Hi If the Hi pulse is a 900 pulse, it brings the spin vectors into the x, y plane only for the resonant slice.
Since the value of the field is only significant during the Hi pulse, it is only necessary that 90 Hz be applied when Hi is applied, and in practice H 2 is also pulsed The Hi and HZ fields are therefore then removed It is still, however, possible to change the resonant frequencies of the spin vectors which are 95 now in the x, y, plane This is achieved by applying a further field HR (actually ‘ which is parallel to HO The intensity of HR, however, varies from a maximum at one extreme of the slice, through zero in the 100 centre to a maximum in the reverse direction on the opposite surface The HR field is illustrated in Figure 1, the arrows indicating only magnitudes at points on a rectangle 1.
There will, of course, be a smooth variation 105 through and between the magnitudes illustrated The fields are also illustrated diagrammatically in the side elevation of Figure 2 in relation to a patient 2 Correspondingly, the resonant frequencies will vary smoothly 110 across the slice from one side to the other.
As mentioned before, the signal which now occurs is at the resonant frequency.
Consequently, the signals received from the slice will also have frequencies which vary 115 across the slice in the same manner The amplitude at each frequency then represents inter alia the proton density in a corresponding strip parallel to the zero plane of HR.
The amplitude for each strip can be 120 obtained by varying the detection frequency through the range which occurs across the slice Preferably, however, the total signal at all frequencies is measured This is then Fourier analysed by well known techniques 125 to give a frequency spectrum The frequency appropriate to each strip will be known from the field values used and the amplitude for each frequency is given by the spectrum.
As discussed, for the field HR illustrated 130
1,584,949 in Figure 1, the individual signals derived from the frequency spectrum, for increments of frequency, correspond to incremental strips parallel to the zero plane of HR These signals are similar in nature to the edge values derived and analysed for X-ray beams in computerised tomography (CT).
The X-ray edge values are obtained for sets at a plurality of different oreintations in an examined slice and then are processed by a suitable method, such as that described in British Patent No 1283915 and the further development thereof described in British Patent No 1471531.
It will be apparent that by changing the orientation, relative to the x, y plane, of the zero plane of HR, further sets of FID signals can be obtained representing proton densities along lines of further sets of parallel lines at corresponding further directions in the examined slice The procedure is therefore repeated until sufficient sets of “edge values” have been derived to process by methods like those used in CT for sets of X-ray beams In practice, the HR field is provided by combination of two fields Hx and Hy, which are both parallel to H but have gradients in orthogonal directions The direction of the gradient of the resultant HR is therefore set by the relative magnitudes of Hx and Hy At many points in the following description reference will be made to the creation of HR field pulses and it should be remembered even where H and Hy fields are not individually discussed that reference is to the resultant of H, and Hy field pulses.
The full examination for one direction of the HR gradient is achieved by applying, via appropriate coils, the sequence of field pulses shown in Figure 3 a Figure 3 b shows the effect which each pulse has on the spin vector It will be realised that the Hi field is a rotating field about the z-axis Correspondingly, the spin vectors thereafter precess about the z-axis For clarity of explanation, the spin vectors are shown in Figure 3 b on a co-ordinate system which rotates with Hi.
Referring to Figures 3 a and 3 b together, the pulse cycle comprises six phases, AB to FG, and a recovery period shown by the broken line The H field is continuously present throughout the cycle.
Prior to the first pulse, or after the recovery period if an earlier cycle has been implemented, the mean spin moments are substantially aligned with the z-axis (A).
The gradient field Hz pulse and Hi pulses (AB), simultaneously applied, respectively select the slice and bring the resultant spin moments into the x, y plane (still, of course, precessing about the z-axis) Although the resonant frequency is the same throughout the slice selected, there is a phase dispersion introduced because the excitation occurred in a field gradient Thus the spin moments are shown at B, though dispersed between limits much greater than can be satisfactorily illustrated The limits shown at L are merely indicative of the nature of the dispersion It has been found that this phase 70 dispersion can be reversed by the application of a negative field gradient pulse, that is a pulse of the correct relative magnitude as Hz but 180 WC displaced (in practice the relation being about 55 %) This pulse BC is 75 therefore applied to bring the spin moments in the x, y plane into phase as at C The Hi field need not be continued into the negative gradient pulse (Hz’) but it can be continued during that pulse if required to 80 ensure that the spin moments go into the x, y plane.
At that time a signal could be sensed to give proton density for the whole slice.
However, in this sequence, the signal is 85 sensed in the presence of an HR pulse CD which gives frequency dispersion in a selected direction (r) in the slice as previously described The change to the new frequencies is almost instantaneous with the 90 application of the HR pulse and is maintained proportionately throughout the pulse As discussed, the signal is sensed and frequency analysed to give the proton densities for a plurality of adjacent parallel 95 strips of the slice After the HR pulse the spin moments, which are still largely in the x, y plane despite some relaxation, have a considerable phase dispersion as shown at D (which is illustrative as the actual disper 10 ( sion is nr radians (n being 100 or more)).
At that stage, if a further cycle as described so far were to be required, it would be necessary to wait for spin lattice relaxation to realign the spin moments with the z-axis 10 ‘ This could take as much as 5 seconds which, since several hundreds or perhaps several thousand of cycles are required, is much too long.
It is proposed to return the spin moments 11 ( substantially back to the starting position (A) by repeating the pulse sequence up to D in the reverse order and reverse sense Since the -HR is substantially the same as the HR pulse except for its sense, further signals 11 ‘ may be detected during it These will be for the same r direction as for the forward pulse and help to improve the signal to noise ratio.
After the reverse pulse sequence the spin moments still show some deviation from the 12 ( z-axis due to phase dispersion caused by spin-spin coupling This cannot be reversed by this pulse sequence, nor it is believed by any other The period GA therefore allows some relaxation to thermal equilibrium 12 (time constant Ti) which eliminates the effect of the phase dispersion and also reduces the effects of any mismatching between the forward and reverse pulses.
Although the relaxation period GA is still 13 ) ) 1,584,949 necessary, the use of the reversed pulse sequence D to G has much reduced that period and allows faster repetition of the total sequence for other r-directions The length of the signal measurement period CE is determined by the phase dispersion caused by H field inhomogeneity and also by the dispersion caused by spin-spin coupling If the effect of H field inhomogeneity is considered to excessively shorten the period CE then pulse FG may be a 1800 r f pulse rather than a 900 pulse Turning the spin moments through 1800 produces a so-called “spin-echo” of known form and the HR pulses similar to CD and DE can be repeated to give a further signal measurement period The spin-echo procedure is known to reverse the dispersion due to field inhomogeneity and can be repeated here several times until sufficient signal has been obtained or until spin-spin dispersion, which cannot be reversed, becomes excessive As in the sequence of Figure 3 A, a spin-echo sequence should end with pulses EF, FG and recovery period GA.
The ratio of period GA to period AG should preferably be approximately the ratio of T 1 to T 2 for maximum sensitivity.
Typically, the total period AGA is 40 m sec where AG is approximately 5 5 m sec, AB is 300,tsec and CD is 2 m sec The Hi pulse is typically of 0 6 Oe and has a frequency of 4.26 M Hz for an HO of 1000 Oe All other pulses are at envelope frequencies, H, being typically + 300 e to -300 e HR being 15 Oe to 15 Oe.
In the preferred embodiment HZ’ is less than HZ; typically f H ‘ dt = 0 55 J HZ dt to 0 57 f HZ dt Figures 4 a and 4 b show in end and side elevation respectively a practical coil arrangement to provide the H field and HR field pulses To show approximate dimensions the patient 2 is shown in cross-section in the end elevation of Figure 4 a A suitable couch or other supporting means for the patient 2 may readily be provided and has not been shown in the figure.
As mentioned hereinbefore, the HR field pulses are the resultant of H and Hy components The H components are provided by four coils 3 and the Hy components by four coils 4 The steady Ho field is provided by four coils 5 connected in series, although a smaller number could be used Further details of the coil windings will not be given since suitable coils can readily be devised, by those with the appropriate skills, to provide the fields required.
Figures 4 a and 4 b do not show the Hi and HZ coils so as to reduce the complexity of the drawing.
The Hi coils are shown in Figure 5 in perspective They are two saddle shaped coils 6 which are driven in parallel to provide the rotating Hi field and which are in this embodiment also used to detect the signals which are of approximately the same frequency 70 Figure 6 shows, also in perspective, the two circular coils 7 which provide the H 7 field component for the gradient superimposed on HO.
Also included in the coil system are a set 75 of field measurement probes whose purpose will be discussed further hereinafter Four of these are in this example yttrium iron garnet tuned oscillators (so called “YIG” oscillators) and there is also at least one simple 80 NMR probe.
The NMR apparatus described so far can be constructed by those with experience in this art to provide the required data for a slice of a patient’s body For sufficiently 85 accurate results to give diagnostically useful information it is, however, desirable, and in some cases important, that certain conditions, in particular the magnetic fields, are precisely applied For example, it is desir 90 able that the H O field should be uniform to around 2 parts in 106 over the examined slice This uniformity can be affected by the quality of the coils used and by adjacent ferromagnetic materials, which should there 95 fore be kept to a minimum.
Also requiring great precision are the HR gradient fields, which as discussed before are constructed from HX ( = HR sin 0) and HY ( = HR COS 0) pulses The HR gradient 100 vector should be in the desired direction with the least error possible Furthermore, the -HR pulse should reproduce in the opposite sense, the preceding HR pulse.
Arrangements for the production of the 105 required precision of the HR pulse are-th Ie subject of our co-pending application no.
22295/78 (Serial No 1584950) It is there proposed to provide a continuously operative control system, responsive to field sensi 110 tive probes disposed within the coil system, to respond to changes in the measured field.
It will be observed that the HR and -HR pulses shown in Figure 3 a are flat topped.
This is also true of the HR pulses which have 115 previously been proposed for NMR which have generally been shown as being square.
The resonance signal is sampled during the HR pulses usually for subsequent digital processing According to established sampling 120 theory, the signal should then be sampled and digitised at regular time intervals As discussed, the HR field is providing phase dispersion in the R direction and the sampled signal is Fourier transformed Thus the 125 rate of sampling determines the phase shift between adjacent strips perpendicular to the R direction in the slice being examined, and therefore the maximum frequency seen in the finally derived picture (i e) the picture 130 1,584,949 widths The total sampling determines the resolution limit.
For the square pulse previously proposed, uniform time period sampling would give satisfactorily uniform resolution However, for the practical flat topped pulse shown in Figure 3 a, the uniform sampling would not be satisfactory at the start and end For other pulses, such as sine waves or distorted’ sine waves used in practice, the uniform time spacing is even less suitable.
The sample is a function of fo Pl HR dt for a series of limits Pl which define the sample points If HR is not a square wave, then for regular signal sampling there is introduced the problem of correcting for the actual shape used for HR This is thought to be impossible However, the use of a gradient waveform which is not a square wave, in a NMR apparatus, can be made invisible to the processing by arranging sampling which is non linear in time but is linear in terms of phase shift This can be achieved by choosing Pl appropriately.
This invention provides that samples are taken at intervals such that J Hdt in the intervals between adjacent samples is equal.
This will not correspond to sampling at equal time intervals except for a square pulse.
Figures 7 a and 7 b show how the sampling times are spaced on that basis for two practical pulses Figures 7 a is a half sine wave, although it should be noted that a real pulse is a distorted half sine wave because of other corrections and adjustments which do not affect their invention Figure 7 b is a more practical form of flat topped pulse The sampling points are indicated by vertical lines 8 in both cases It can be seen that the sampling time varies so that f Hdt can be equal, although the Figures are merely exemplary and are not accurately calculated.
The Pl values to give the required sampling times for equal intervals of f Hdt can, of course, be precalculated when the shape of the intended HR pulse is known It is also convenient to measure the field integral for the pulse, using the field probe system provided for other purposes, as described in said co-pending applications A sample can be taken every time a predetermined value is reached or the phase shifts can be counted to determine in real time when the required Pl is fulfilled to give the required sampling instant.
It should be noted that it is preferable for the number of samples taken to be 2 P (where p is an integer) Otherwise O’s may need to be added to the samples to make the number up to 2 P for Fourier processing.
It should be noted that instead of the nomenclature used throughout this specification an alternative, and more strictly correct, form may be encountered In this alternative form all fields longitudinal of the body are denoted H 7; then a gradient in the Z direction is denoted Gz = d Hz, gradient in the x direction is denoted Gx = d H 7 a gradient in the y direction is denoted Gy = d H 7 and Gx and Gy together form GR = d Hz.
dr

Claims (11)

WHAT WE CLAIM IS:

1 An NMR apparatus, for examining a slice of a body, including means for applying 85 magnetic fields to cause resonance preferentially in said slice, means for applying a pulsed magnetic field having a gradient across the slice to produce phase dispersion in’said resonance, and means for sensing a 90 resonance signal induced during said pulsed field, wherein the means for applying the pulsed field is arranged to cause a pulse which does not have a constant level throughout its duration and the means for 95 sensing is caused to sample the induced signal at intervals such that the field integral with respect to time for the pulsed field is substantially the same in each interval between successive samples 101

2 An apparatus according to Claim 1 including means for sensing the magnetic field during the said pulsed field, means for determining the field integral and means for causing a sample to be taken at a predeter 10 ‘ mined value of the field integral.

3 An apparatus according to Claim 1 including means for causing samples to be taken at predetermined times.

4 An apparatus according to either of 11 ‘ the preceding claims in which the means for applying a pulsed magnetic field is arranged to apply a field pulse of sinusoidal or distorted sinusoidal shape.

An apparatus according to any pre 11 ceding claim arranged to take 2 P samples in each said pulsed field, where p is an integer.

6 An apparatus for examining a body substantially as herein described with reference to the accompanying drawings 12

7 A method of examining a slice of a body by nuclear magnetic resonance, including the steps of: applying magnetic fields to induce resonance preferentially in said slice, applying magnetic fields, including a pulsed 12 field having a gradient across the slice in one direction to cause phase dispersion of said resonance and sampling a resonance signal in the slice, wherein the gradient field pulse does not have a constant level throughout its 13 DO 1 CQA OA O 6 1,Jt I’t 6 duration and the resonance signal is sampled at intervals such that the field integral with respect to time for the pulsed gradient field is substantially the same in each of said intervals.

8 A method according to Claim 7 in which the magnetic field is sensed during the pulsed field and samples taken when a predetermined value is reached.

9 A method according to Claim 7 in which the magnetic field is sensed at times predetermined for the gradient field pulse shape to give the required equal field integrals.

10 A method according to any of Claims 7 9 in which the gradient field pulse shape is a sinusoid or distorted sinusoid.

11 A method of examining a body substantially as herein described with reference to the accompanying drawings.
R.G MARSH, Chartered Patent Agent, Agent for the Applicants.
Printed for Her Majesty’s Stationery Office, by Croydon Printing Company Limited, Croydon, Surrey, 1981.
Published by The Patent Office, 25 Southampton Buildings, London, WC 2 A l AY, from which copies may be obtained.

GB22292/78A
1978-05-25
1978-05-25
Imaging systems

Expired

GB1584949A
(en)

Priority Applications (4)

Application Number
Priority Date
Filing Date
Title

GB22292/78A

GB1584949A
(en)

1978-05-25
1978-05-25
Imaging systems

US06/039,650

US4315216A
(en)

1978-05-25
1979-05-16
Imaging systems

DE19792921252

DE2921252A1
(en)

1978-05-25
1979-05-25

NUCLEAR MAGNETIC RESONANCE DEVICE FOR THE EXAMINATION OF A DISC OF A BODY

JP6551579A

JPS54156596A
(en)

1978-05-25
1979-05-25
Method and device for checking by nuclear magnetic resonance

Applications Claiming Priority (1)

Application Number
Priority Date
Filing Date
Title

GB22292/78A

GB1584949A
(en)

1978-05-25
1978-05-25
Imaging systems

Publications (1)

Publication Number
Publication Date

GB1584949A
true

GB1584949A
(en)

1981-02-18

Family
ID=10177025
Family Applications (1)

Application Number
Title
Priority Date
Filing Date

GB22292/78A
Expired

GB1584949A
(en)

1978-05-25
1978-05-25
Imaging systems

Country Status (4)

Country
Link

US
(1)

US4315216A
(en)

JP
(1)

JPS54156596A
(en)

DE
(1)

DE2921252A1
(en)

GB
(1)

GB1584949A
(en)

Cited By (3)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

EP0076054A1
(en)

1981-09-21
1983-04-06
Peter Mansfield
Nuclear magnetic resonance methods

EP0269146A2
(en)

1986-10-27
1988-06-01
Smit Transformatoren B.V.
Apparatus for mounting coils

US5355086A
(en)

1992-02-04
1994-10-11
Bruker Medizintechnik Gmbh
Method for the generation of an NMR spectrum without side-bands

Families Citing this family (43)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

US4411270A
(en)

1978-11-20
1983-10-25
Damadian Raymond V
Apparatus and method for nuclear magnetic resonance scanning and mapping

USRE32689E
(en)

1978-11-20
1988-06-07

Apparatus and method for nuclear magnetic resonance scanning and mapping

US4442404A
(en)

1978-12-19
1984-04-10
Bergmann Wilfried H
Method and means for the noninvasive, local, in-vivo examination of endogeneous tissue, organs, bones, nerves and circulating blood on account of spin-echo techniques

USRE32712E
(en)

1979-08-20
1988-07-12
General Electric Company
Moving gradient zeugmatography

US4307343A
(en)

1979-08-20
1981-12-22
General Electric Company
Moving gradient zeugmatography

JPS5669541A
(en)

1979-11-10
1981-06-10
Sanyo Electric Co Ltd
Generation of magnetic field

FR2475282B1
(en)

1980-02-05
1985-10-04
Radiologie Cie Gle

ELECTROMAGNETIC COIL SYSTEM FOR EXAMINATION OF LARGE BODIES BY NUCLEAR MAGNETIC RESONANCE, AND HUMAN BODY IMAGING APPARATUS USING SUCH A SYSTEM

JPH0135652B2
(en)

1980-03-14
1989-07-26
Nat Res Dev

JPS574541A
(en)

1980-06-12
1982-01-11
Toshiba Corp
Nuclear magnetic resonance apparatus

DE3044396A1
(en)

1980-11-25
1982-06-24
Siemens AG, 1000 Berlin und 8000 München
Nuclear magnetic resonance imaging using independent field gradients – in three dimensions and computer for control and evaluation

US4471306A
(en)

1982-02-03
1984-09-11
General Electric Company
Method of NMR imaging which overcomes T2 * effects in an inhomogeneous static magnetic field

US4431968A
(en)

1982-04-05
1984-02-14
General Electric Company
Method of three-dimensional NMR imaging using selective excitation

DE3219832A1
(en)

1982-05-26
1983-12-01
Bruker Medizintechnik Gmbh, 7512 Rheinstetten

METHOD FOR NON-INVASIVELY DETERMINING MEASURED VALUES WITHIN A LIVING BODY

DE3227844A1
(en)

1982-07-26
1984-01-26
Siemens AG, 1000 Berlin und 8000 München

DEVICE FOR ADJUSTING AND HOLDING MAGNETIC COILS OF A MAGNETIC SYSTEM FOR CORE SPIN TOMOGRAPHY

JPS5938637A
(en)

1982-08-28
1984-03-02
Toshiba Corp
Nuclear magnetic resonance apparatus

JPS5938636A
(en)

1982-08-28
1984-03-02
Toshiba Corp
Nuclear magnetic resonance apparatus

JPS5946546A
(en)

1982-09-09
1984-03-15
Yokogawa Hokushin Electric Corp
Inspection method and apparatus by nuclear magnetic resonator

JPS5957147A
(en)

1982-09-27
1984-04-02
Yokogawa Hokushin Electric Corp
Method and apparatus for inspection utilizing nuclear magnetic resonance

FI65862C
(en)

1982-10-11
1984-07-10
Instrumentarium Oy

NMR AVBILDNINGSAPPARAT

JPS5983040A
(en)

1982-11-02
1984-05-14
Yokogawa Hokushin Electric Corp
Inspecting method and apparatus utilizing nuclear magnetic resonance

JPS5998530U
(en)

1982-12-22
1984-07-04
松下電器産業株式会社

switch

JPS59119248A
(en)

1982-12-27
1984-07-10
Toshiba Corp
Nuclear magnetic resonance device

US4556848A
(en)

1983-02-01
1985-12-03
The United States Of America As Represented By The United States Department Of Energy
Point sensitive NMR imaging system using a magnetic field configuration with a spatial minimum

FR2541551A1
(en)

1983-02-21
1984-08-24
Drusch & Cie

DEVICE FOR HOLDING AND FIXING COILS FOR REALIZING A CONSTANT AND HOMOGENEOUS MAGNETIC FIELD

DE3310160A1
(en)

1983-03-21
1984-09-27
Siemens AG, 1000 Berlin und 8000 München

DEVICE FOR GENERATING IMAGES AND LOCALLY RESOLVED SPECTRES OF AN EXAMINATION OBJECT WITH A MAGNETIC CORE RESONANCE

JPS59231438A
(en)

1983-06-15
1984-12-26
Yokogawa Hokushin Electric Corp
Inspection method and apparatus by nuclear magnetic resonance

FI832326A0
(en)

1983-06-23
1983-06-23
Instrumentarium Oy

FOER FARER FOR EXTRACTION OF AEMNETS ELLER MAGNETFAELTETS EGENSKAPER

JPS6024464A
(en)

1983-07-20
1985-02-07
Yokogawa Hokushin Electric Corp
Inspection method by employing nuclear magnetic resonance

JPS6029684A
(en)

1983-07-27
1985-02-15
Yokogawa Hokushin Electric Corp
Inspecting method and device by nuclear magnetic resonance

DE3333755A1
(en)

1983-09-19
1985-04-18
Siemens AG, 1000 Berlin und 8000 München

MAGNETIC DEVICE OF A SYSTEM OF CORE SPIN TOMOGRAPHY WITH A SHIELDING DEVICE

US4689562A
(en)

1983-10-11
1987-08-25
Elscint Ltd.
NMR Imaging method and system

US4585992A
(en)

1984-02-03
1986-04-29
Philips Medical Systems, Inc.
NMR imaging methods

JPS60185148A
(en)

1984-03-02
1985-09-20
Shimadzu Corp
Nmr imaging appratus

US4628264A
(en)

1984-03-14
1986-12-09
Advanced Nmr Systems, Inc.
NMR gradient field modulation

EP0177869B1
(en)

1984-10-12
1989-08-16
Siemens Aktiengesellschaft
Magnet arrangement with a screen device for a nuclear spin tomography installation

DE3563800D1
(en)

1984-11-15
1988-08-18
Siemens Ag
Magnet device for a nuclear spin resonance tomography system with an approximately cylindrical shielding arrangement

US4656026A
(en)

1984-12-10
1987-04-07
University Of Iowa Research Foundation
Magnetic resonance (MR) image enhancement compounds for specific areas of the brain

US4703275A
(en)

1985-07-25
1987-10-27
Picker International, Inc.
Method and apparatus to compensate for eddy currents in magnetic resonance imaging

IL80727A
(en)

1986-11-21
1990-06-10
Elscint Ltd
Noise reduction in magnetic resonance images

FR2612641B1
(en)

1987-03-19
1989-06-09
Oreal

APPARATUS FOR EXAMINING A BODY BY NUCLEAR MAGNETIC RESONANCE BY SLOW AND FAST METHODS, PARTICULARLY FOR EXAMINING THE SURFACE LAYER OF THIS BODY, DEVICE FOR CREATING A GRADIENT OF MAGNETIC FIELD FOR SUCH APPARATUS, AND APPLICATION TO THE SAME HUMAN BODY SKIN IMAGING

JPH02264636A
(en)

1988-12-23
1990-10-29
Picker Internatl Ltd
Nuclear magnetic resonance method

US4982162A
(en)

1989-07-14
1991-01-01
Advanced Nmr Systems, Inc.
Method for reconstructing MRI signals resulting from time-varying gradients

US5099208A
(en)

1989-10-05
1992-03-24
Vanderbilt University
Method for magnetic resonance imaging and related apparatus

Family Cites Families (5)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

GB1283915A
(en)

1968-08-23
1972-08-02
Emi Ltd
A method of and apparatus for examination of a body by radiation such as x or gamma radiation

JPS49103693A
(en)

1973-02-02
1974-10-01

GB1471531A
(en)

1973-04-25
1977-04-27
Emi Ltd
Radiography

US4021726A
(en)

1974-09-11
1977-05-03
National Research Development Corporation
Image formation using nuclear magnetic resonance

GB1596160A
(en)

1976-12-15
1981-08-19
Nat Res Dev
Nuclear magnetic resonance apparatus and methods

1978

1978-05-25
GB
GB22292/78A
patent/GB1584949A/en
not_active
Expired

1979

1979-05-16
US
US06/039,650
patent/US4315216A/en
not_active
Expired – Lifetime

1979-05-25
DE
DE19792921252
patent/DE2921252A1/en
active
Granted

1979-05-25
JP
JP6551579A
patent/JPS54156596A/en
active
Granted

Cited By (4)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

EP0076054A1
(en)

1981-09-21
1983-04-06
Peter Mansfield
Nuclear magnetic resonance methods

EP0269146A2
(en)

1986-10-27
1988-06-01
Smit Transformatoren B.V.
Apparatus for mounting coils

EP0269146A3
(en)

1986-10-27
1988-06-15
Smit Transformatoren B.V.
Apparatus for mounting coils

US5355086A
(en)

1992-02-04
1994-10-11
Bruker Medizintechnik Gmbh
Method for the generation of an NMR spectrum without side-bands

Also Published As

Publication number
Publication date

JPS6363225B2
(en)

1988-12-06

DE2921252A1
(en)

1979-12-13

DE2921252C2
(en)

1992-07-09

JPS54156596A
(en)

1979-12-10

US4315216A
(en)

1982-02-09

Contact information