GB2079463A - NMR imaging method - Google Patents
NMR imaging method Download PDFInfo
- Publication number
- GB2079463A GB2079463A GB8107961A GB8107961A GB2079463A GB 2079463 A GB2079463 A GB 2079463A GB 8107961 A GB8107961 A GB 8107961A GB 8107961 A GB8107961 A GB 8107961A GB 2079463 A GB2079463 A GB 2079463A
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- Prior art keywords
- gradient
- reversed
- magnetic field
- time
- plane
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- 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
- G01R33/4818—MR characterised by data acquisition along a specific k-space trajectory or by the temporal order of k-space coverage, e.g. centric or segmented coverage of k-space
- G01R33/482—MR characterised by data acquisition along a specific k-space trajectory or by the temporal order of k-space coverage, e.g. centric or segmented coverage of k-space using a Cartesian trajectory
-
- 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
- G01R33/561—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution by reduction of the scanning time, i.e. fast acquiring systems, e.g. using echo-planar pulse sequences
- G01R33/5615—Echo train techniques involving acquiring plural, differently encoded, echo signals after one RF excitation, e.g. using gradient refocusing in echo planar imaging [EPI], RF refocusing in rapid acquisition with relaxation enhancement [RARE] or using both RF and gradient refocusing in gradient and spin echo imaging [GRASE]
-
- 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
- G01R33/561—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution by reduction of the scanning time, i.e. fast acquiring systems, e.g. using echo-planar pulse sequences
- G01R33/5615—Echo train techniques involving acquiring plural, differently encoded, echo signals after one RF excitation, e.g. using gradient refocusing in echo planar imaging [EPI], RF refocusing in rapid acquisition with relaxation enhancement [RARE] or using both RF and gradient refocusing in gradient and spin echo imaging [GRASE]
- G01R33/5616—Echo train techniques involving acquiring plural, differently encoded, echo signals after one RF excitation, e.g. using gradient refocusing in echo planar imaging [EPI], RF refocusing in rapid acquisition with relaxation enhancement [RARE] or using both RF and gradient refocusing in gradient and spin echo imaging [GRASE] using gradient refocusing, e.g. EPI
Abstract
To produce image information from an object it is subjected to a continuous static magnetic field along a Z axis and to sets of sequences of magnetic field gradients Gx, Gy and Gz. Spins in a selected plane X-Z are excited by rf pulses and an associated Gy gradient. The selected spins are subjected to a reversed Gy gradient together with a Gx gradient. The Gy gradient is then switched off and the direction of the Gx gradient is then repeatedly reversed. During the action of each subsequent reversal of the Gx gradient, a small Gz gradient is provided. Each reversed Gx gradient is held constant for a sufficient time for a free induction decay signal to be generated, providing a multiple echo of the spins in the selected plane. Alternate signals are time-reversed, then both the time- reversed and non time-reversed signals are subject to Fourier transformation. <IMAGE>
Description
SPECIFICATION
Method of producing image information from objects
The present invention relates to methods of producing image information from objects. It is concerned with producing images of samples containing nuclear or other spins whose spatial distribution of density or relaxation time is detected by magnetic resonance techniques. More particularly, it describes methods for producing images from free induction decays (FID's) and spin echoes of the sample in the presence of static magnetic fields and switched magnetic field gradients.
It has been proposed in U.S. Patent No. 4,165,479 that image information can be derived from a series of spin echoes following a single excitation of the sample. The spin echoes are derived by employing switched magnetic field gradients or switched radiofrequency magnetic field pulses. This method may be referred to as the echo planar technique.
The echo planar technique is in some sense an improvement over the method described in U.S. Patent No.
4,070,611. In the echo planar method imaging information is derived from a number of spin echoes following a single excitation of the sample. The echoes may be produced by successively reversing-a magnetic field gradient along one direction. A much smaller gradient at right angles to the first gradient is constantly present to produce a varying phase shift along the second direction which serves the purpose of providing spatial discrimination along the second direction. This technique produces a two-dimensional image in the plane defined by these two gradient directions.
However, the echo planar method as described above seems to have certain difficulties. First, successive echoes produced by the switching of the first gradient mentioned in the previous paragraph must be time reversed with respect to each other. Failure to time reverse successive echo signals before performing the required Fourier transformations will result in mixing up information from the positive and negative directions associated with the first gradient and thus produce aliasing.
Once the necessity for time-reversing successive echoes is appreciated, it becomes evident that the time reversal will be rendered problematic if the second gradient mentioned above is kept on during the signal readout. Consider a small volume element of the sample at co-ordinates (X, Z). Assume that Gx is the first gradient mentioned above and G, is the second. Then for successive intervals k and (k+ 1) the successive signals Sk (X,Z,t) and Sky 1 (X,Z,t) from the element will be
Ap(Z) = YG,ZT, where l is the length of one interval (all N are the same length), and tk and tk+1 are reference times within the intervals k and (k+1).Thus Gx and G, act in opposite ways in the two signals, and it is not at all clear how to sort out the imaging information in the X and Z directions.
The principal object of the present invention is to provide an improved method of gyromagnetic resonance imaging employing trains of free induction decays and spin echoes.
According to the present invention a method of deriving image information from an object using nuclear magnetic resonance signals comprises subjecting an object to a continuous static magnetic field along an axis and carrying out the following sequence of steps:
1) exciting nuclear spins in a selected plane,
2) applying a first gradient of the magnetic field which has a gradient direction parallel to the said plane together with a second gradient of the magnetic field having a gradient direction perpendicular to the said plane.
3) repeatedly applying the said first gradient with successive reversals of gradient direction, applying a third gradient of the magnetic field which has a gradient direction parallel to the said plane and orthogonal to the direction of the first gradient during each successive reversal of said first gradient, and holding the said first gradient with its successively reversed gradient directions for time intervals during which successive echoing free induction decay signals are read out.
In carrying out the invention alternate free induction decay signals are time-reversed and the time-reversed and non time-reversed free induction decay signals are then subject to Fourier transformation.
In order that the invention may be more fully understood reference will now be made to the accompanying drawings in which the single Figure shows pulse sequences for an embodiment of the invention.
For the purpose of the following description a static magnetic field B0 lies along the Z axis and the radiofrequency (rf) field lies along the Y axis. There are coils to produce magnetic field gradients Gx, 6y and
G, in the X, Y and Z directions. The production of a two-dimensional image of a thin slab perpendicular to the Y axis is considered. Where the method is applied to human whole body imaging it is convenient to position the patient horizontally with the Z axis vertical and the Y axis along the length of the patient. The X axis then extends across the patient.
The pulse sequence used to form an image from multiple spin echoes following each excitation is shown in the Figure. The time axis is divided into ten successive intervals repeated cyclically. The fields which are applied in each of these intervals are as follows: Interval 1. A1800 rf pulse is applied simultaneously with a magnetic field gradient G+y.This selectively inverts the nuclear spins in and close to the plane Y=YO. The value of Y0 can be altered by a change in the frequency of the 1800 pulse. Alternatively, a non-selective 1800 pulse can be applied with no gradients present. In this case, they-dimension selection is done entirely by the events in interval 3.Alternatively again, non-selective spin inversion can be obtained by an adiabatic fast passage in which the rf field is swept through a frequency range.
Interval 2. The nuclear spin system is allowed to relax by spin-lattice relaxation for a chosen time T. No fields other than B0 are applied during this interval.
Interval 3. A weak 90" rf pulse is applied simultaneously with a magnetic field gradient Guy+. This selectively excites nuclear spins in and close to the plane Y=YO. The value of Y0 can be altered by a change in the frequency of the 90" pulse.
Interval 4. A negative magnetic field gradient G; is applied to rephase the nuclear spins along the Y direction. Simultaneously a negative magnetic field gradient Gx is applied to dephase the nuclear spins along the X direction.
Interval 5. A positive magnetic field gradient G+X is applied during this interval. During this interval, the nuclear spins rephase to form a spin echo, when the free induction signal is a maximum, and then dephase.
It is desirable that Gxf be constant during the signal collection period. Also during this interval is the start of a short positive magnetic field gradient pulse 6+,. This pulse continues into the next interval (interval 6) but only comes on after the signal collection in interval 5 has been completed. The duration of the 6+, signal is
T*, and its purpose is to dephase the spins along the Z direction.
Interval 6. The gradient pulse G zf begun in interval 5 is completed. A negative magnetic field gradient G-x is applied during this interval. During this interval, the nuclear spins again rephase to form a spin echo, when the free induction signal is a maximum, and then dephase. Again, G; should be constant during signal collection. The collection must begin after the G zf pulse begun in interval 5 has been completed. Another short positive magnetic field gradient pulse G zf is started at the end of this interval after signal data collection has been completed. The pulse continues into the next interval (interval 7), and its purpose is to dephase the spins along the Z direction.
Interval 7. The gradient pulse G+z begun in interval 6 is completed. A positive magnetic field gradient G+X is applied during this interval, and another spin echo is formed. Another short gradient pulse G z+ is begun at the end of this interval after data collection from the signal in this interval.
Interval 8. This interval consists of a number of sub-intervals similar to intervals 5, 6 and 7, in which the gradient Gx is alternatively applied positively and negatively and during which a number of spin echoes are formed. Short pulses Gz are also applied in the appropriate places.
Interval 9. System recovery time until the occurrence of interval 1 of the next sequence. This should be long compared with the spin-lattice relaxation time T1 and is the order of a second in the whole-body N MR imaging machine described in reference 4.
Two different sets of free induction signals SA and SB, are obtained using this pulse sequence for any one value of the altered high frequency of interval 1 and any particlar set of values of JT"dt G zf between intervals 5 and 6, intervals 6 and 7, and so on. fT*dt indicates the integral over the time periods lasting T*. SB: The relaxation interval (2) is comparable with the spin-lattice relaxation time being measured. That is, T=T1, which is a few hundred milliseconds for human soft tissue at 1.7 MHz. SA: The events of intervals 1 and 2 are omitted, but the rest of the sequence is identical.
SA sets of signals contain mostly proton density information, and SB sets of signals contain both spin-lattice relaxation time (T1) information and proton density information.
To obtain an NxN proton density image, N SA signals must be collected. It may be assumed for the moment that all N required signals are obtained after a single excitation of the sample. Such a complete set could be obtained, for example by having all the G zf identical with the restriction that
where L, is the length of the sample in the Z direction. That is, the spins at the top of the sample must be rotated through a phase angle of at most 2sI relative to the spins at the bottom during each T* period. N points must be collected from each echo, with due regard for bandwidth requirements.
It might be helpful to consider some of the effects of this sequence on a volume element at co-ordinates (X,Z). For successive intervals k and (k+1) the respective signals Sk(X,Z,t) and SK+1 (X, Z,t) are given by
where
tk and tk+1 are the reference times within the kth and (k+1)th intervals when the maximum spin echoes occur.
Thus if Sk+ is time reversed relative to tk+1, the x location spatial information (given by the extra precession caused by Gx) is exactly the same as in Sk. The additional phase shift A0(Z) in Sk+1 compared to Sk enables the spatial distribution in the Z direction to be sorted out, and indeed, the total information available is identical to that obtained in the method described with reference to Figure 1.
To analyse the data, the N echo signals must be Fourier transformed. However, it is first necessary to time reverse every second signal. A new set of signals can be defined.
g0 (t) = (fn (T), n = 2,4,..., n-2.n n-i where f,(t) is the nth echo observed at time T relative to t=tn. A two-dimensional Fourier transformation is performed on g,(t) to give a final image. An example of such a transformation is given by equation (3).
An image containing most T1 information can be obtained by collecting SB sets of echo signals along with SA sets of echo signals, deriving an SA image array and an S8 image array as outlined above, and calculating the T1 values (from these arrays) ccrresponding to each imaging element. An image containing a mixture of
T1 information and proton density information can be obtained from Sg sets of echo signals alone.
The complete set of N echoes necessary to produce an image need not be collected in a single pulse train.
Partial sets can be collected after separate excitations, with appropriate adjustments to the values of fT*dt G to produce the desired phase shifts along Z for that particular set of echoes.
Claims (13)
1. A method of deriving image information from an object using nuclear magnetic resonance signals comprising subjecting an object to a continuous static magnetic field along an axis and carrying out the following sequence of steps:
1) exciting nuclear spins in a selected plane,
2) applying a first gradient of the magnetic field which has a gradient direction parallel to the said plane
together with a second gradient of the magnetic field having a gradient direction perpendicular to the said
plane,
3) repeatedly applying the said first gradient with successive reversals of gradient direction, applying a
third gradient of the magnetic field which has a gradient direction parallel to the said plane and orthogonal
to the direction of the first gradient during each successive reversal of said first gradient1 and holding the
said first gradient with its successively reversed gradient directions for time intervals during which
successive echoing free induction decay signals are read out.
2. The method as claimed in claim 1 in which alternate free induction decay signals are time-reversed.
3. The method as claimed in claim 2 in which the said time-reversed free induction decay signals and the non time-reversed free induction decay signals are subject to Fourier transformation.
4. The method as claimed in any one fo the preceding claims in which the said step of exciting nuclear spins in a selected plane comprises applying the second gradient of the magnetic field with a gradient reversed with respect to step 2) together with a 90 rf pulse.
5. The method as claimed in any one of the preceding claims and including a prior step of inverting the nuclear spins in the selected plane.
6. The method as claimed in claim 5 in which inverting the nuclear spins is achieved by applying a 180 rf pulse.
7. The method as claimed in claim 5 in which inverting the nuclear spins is achieved by an adiabatic fast passage.
8. The method as claimed in claim 5 in which a time interval is interposed between the said prior step and step 1).
9. The method as claimed in claim 8 in which the said time interval is approximately equal to the spin-lattice relaxation time of protons in the object.
10. The method as claimed in any one of the preceding claims in which the sequence of steps is repeated for different selected planes.
11. The method as claimed in claim 10 in which the selected planes are parallel to each other.
12. The method as claimed in claim 11 in which the selected planes are parallel to the said axis.
13. A method of deriving image information from an object substantially as described with reference to the accompanying drawing.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| GB8107961A GB2079463B (en) | 1980-03-14 | 1981-03-13 | Nmr imaging method |
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| GB8008773 | 1980-03-14 | ||
| GB8107961A GB2079463B (en) | 1980-03-14 | 1981-03-13 | Nmr imaging method |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| GB2079463A true GB2079463A (en) | 1982-01-20 |
| GB2079463B GB2079463B (en) | 1984-10-10 |
Family
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Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| GB8107961A Expired GB2079463B (en) | 1980-03-14 | 1981-03-13 | Nmr imaging method |
Country Status (1)
| Country | Link |
|---|---|
| GB (1) | GB2079463B (en) |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0105700A2 (en) * | 1982-10-06 | 1984-04-18 | Peter Mansfield | Nuclear magnetic resonance methods |
| EP0165610A2 (en) * | 1984-06-20 | 1985-12-27 | Hitachi, Ltd. | High speed imaging method with three-dimensional NMR |
| US4607223A (en) * | 1982-08-13 | 1986-08-19 | National Research Development Corporation | Nuclear magnetic resonance imaging method |
| US4651095A (en) * | 1983-08-01 | 1987-03-17 | National Research Development Corporation | Methods of producing images by NMR techniques |
| EP0270320A2 (en) * | 1986-12-03 | 1988-06-08 | Advanced Nmr Systems Inc. | Method of high-speed magnetic resonance imaging |
-
1981
- 1981-03-13 GB GB8107961A patent/GB2079463B/en not_active Expired
Cited By (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4607223A (en) * | 1982-08-13 | 1986-08-19 | National Research Development Corporation | Nuclear magnetic resonance imaging method |
| EP0105700A2 (en) * | 1982-10-06 | 1984-04-18 | Peter Mansfield | Nuclear magnetic resonance methods |
| EP0105700A3 (en) * | 1982-10-06 | 1985-05-02 | Peter Mansfield | Nuclear magnetic resonance methods |
| US4588948A (en) * | 1982-10-06 | 1986-05-13 | Peter Mansfield | Nuclear magnetic resonance methods |
| US4651095A (en) * | 1983-08-01 | 1987-03-17 | National Research Development Corporation | Methods of producing images by NMR techniques |
| EP0165610A2 (en) * | 1984-06-20 | 1985-12-27 | Hitachi, Ltd. | High speed imaging method with three-dimensional NMR |
| EP0165610A3 (en) * | 1984-06-20 | 1986-10-01 | Hitachi, Ltd. | High speed imaging method with three-dimensional nmr |
| EP0270320A2 (en) * | 1986-12-03 | 1988-06-08 | Advanced Nmr Systems Inc. | Method of high-speed magnetic resonance imaging |
| EP0270320A3 (en) * | 1986-12-03 | 1989-05-24 | Advanced Nmr Systems, Inc. | Method of high-speed magnetic resonance imaging |
Also Published As
| Publication number | Publication date |
|---|---|
| GB2079463B (en) | 1984-10-10 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| 732 | Registration of transactions, instruments or events in the register (sect. 32/1977) | ||
| PE20 | Patent expired after termination of 20 years |
Effective date: 20010312 |