METHOD AND APPARATUS FOR OBTAINING N.M.R. SPECTRA

Abstract: A method of obtaining an N.M.R. spectrum from a specific volume within a sample volume comprises: maintaining along an axis Z of the sample a static homogeneous magnetic field Bo; applying to the sample a first magnetic field gradient Gx in a first direction X and an rf pulse to effect selective saturation of all spins of a particular type within the sample except for those lying in a slice of a limited width normal to said first direction X; applying a respective second magnetic field gradient Gy and a second rf pulse relative to a second direction Y normal to said first direction X; applying a respective third magnetic field gradient Gz and a third rf pulse relative to a third direction Z normal to said first and second directions X, Y; finally, the free induction decay FID of all of the spins of the particular type contained in the specific volume defined by the magnetic field gradients Gx, Gy, Gz and the rf pulses respectively, is monitored after the third magnetic field gradient Gz and the third rf pulse have been removed, and thus in the presence of the static magnetic field Bo only.

Description: -n ~ Method and Apparatus for obtaining N.M.R. Spectra The invention relates to a method of obtaining N.M.R. spectra from a specific volume within a sample volume, which method comprises: OMPI maintaining along an axis of the sample a static homogeneous magnetic field; applying to the sample a first magnetic field gradient in a first direction and an rf pulse to effect selective saturation of all spins of a particular type within the sample, except for those lying in a slice of a limited width normal to said first direction; applying a respective second magnetic field gradient and a second rf pulse relative to a second direction normal to said first direction; applying a respective third magnetic field gradient and a third rf pulse relative to a third direction normal to said first and second direc¬ tions. U.S.-A.-4021 726 describes alternative methods for obtaining information of two- and three-dimensional images of the spin density distribution in materials containing nuclear spins. These two alternative methods are specified by "tailored saturation" and "tailored excitation", respectively. To select a specific volume of spins, the "tailored saturation" uses a method in which the width of the envelope of prepara¬ tory radiation rf pulses is relatively long, of the order of the spin-lattice relaxation time . , and those irradiated spins have their magnetization destroyed. Tailoring by this method is achieved by frequency and/or amplitude modulation of the pulse envelope. It is an object of the present invention to enhance the information, obtainable by the known method in that high resolution N.M.R. spectra may be obtained from specific volumes of minimum dimensions within a sample rather than obtaining only information about spin density profiles. According to a first aspect of the invention, this goal is achieved in that the free induction decay of all of the spins of the particular type, contained in the specific volume defined by the magnetic field gradients and the rf pulβes, respectively, is monitored after the third magnetic field gradient and the third rf pulse have been removed, and thus in the presence of the static homogeneous magnetic field only. The main advantage of this new method is thus that high resolution N.M.R. spectra may be obtained from specific points within a sample, e.g. a living human body. It is, therefore, possible to take advantage of any of the known preparatory N.M.R. methods to obtain additional information pointwise within the living sample. For example, information may be obtained about the chemical configuration of the specific measuring point or physical properties may be determined, for example the value of pH or the specific temperature which are known to influence the chemical shift within an N.M.R. spectrum. The invention relates further to an apparatus for obtaining H.M.R. spectra of a sample, comprising means for applying to a sample a homogeneous magnetic field, means for successive¬ ly applying to the sample magnetic field gradients in each of three mutually orthogonal directions, at least one rf transmitter for applying rf pulses to the sample, and means for controlling the timing an waveform of the output from the said at least one rf transmitter, to apply to the sample selected rf pulses in synchronization with the said success¬ ively applied magnetic field gradients to selectively inter¬ act with spin3 of a particular type in a small volume of the said sample volume. It is another object of the invention to provide an appara¬ tus with enhanced possibilities to investigte the physical characteristics of a microscopic volume within a sample volume, using N.M.R. spectroscopy. This goal is achieved by using within the above-mentioned apparatus, mean3 for obtaining from the said small volume an output signal indicative of the free induction decay of the said selectively affected spins in the absence of said magnetic field gradients and the rf pulses, respectively, and in the presence of the static homogeneous magnetic field only. Further embodiments of the invention are described in the dependent claims. The invention will be more readily understood by explanation with reference to the accompanying drawings, in which: Fig. 1 illustrates in diagrammatic form a sample to be analyzed, Fig. 2 illustrates in schematic form vaveforms to be applied in carrying out a method according to the invention; Fig. 5 illustrates in schematic form various alternative waveforms; and Fig. 4 is an illustration of desired frequency envelopes for various rf pulses. Referring to Fig. 1 , a small volume in a sample is repre¬ sented as a cube 1 , positioned with its sides parallel to three orthogonal axes X, Y and Z. Cube 1 is placed in a static homogeneous magnetic field B , as illustrated in Fig. 1. In the simplest case, the third direction along which the field gradient is applied is the Z direction (i.e. the direction of B ), and the said first and second directions may, for example, be vertical and horizontal directions in the laboratory frame. There is, however, no necessity that the three directions X, Y and Z should be coincident with any particular direction of the magnet, and, for example, mutually orthogonal gradients may be produced by the use of combinations of gradient coils as used in a conventional N.M.R. spectrometer. For simplicity, however, the invention will be illustrated for the case when the Z direction is coincident with the direction of B . A field gradient (_ ■ is applied along the X direction of a sufficient magnitude to provide a measurable difference in rf resonance frequency for nuclei of a particular type in the volume 1. Typical values for the magnitude of the field gradient would be of the order of 0.5 gauss/cm. OMPI Λ/ , WIPO » rfhilst the magnetic field gradient G- is applied, an rf pulse is applied to the sample so as to effect the selective saturation of spins in the sample. The saturation is selec¬ tive in that all the nuclei of a particular type ("typically protons, although any nuclei having a suitable magnetic moment, such as 13 Q or 31 p could be utilized) within the volume 1 are saturated by the pulse, with the exception of those within a slice Δx in the Y, Z plane, i.e. orthogonal to the X axis. Fig. 2 illustrates schematically the time scale over which the rf pulse 10 is applied, in comparison with the field gradient G . To produce the desired saturation of all spins except those within the slice 2 of thickness ._-_ x, the radio-frequency pulse applied must have a frequency distribution somewhat of the type illustrated in Fig. 4(a), in which the horizontal axis now represents radio-frequency, and the vertical axis represents amplitude. It can be seen that, in effect, the waveform has a "notch", at a frequency corresponding to the resonant frequency of the slice 2. Such a waveform can be produced by calculating the desired frequency distribution, and applying Fourier transform techniques, to produce the appropriate amplitude modulation for the rf pulse. This technique of pulse shaping is commonly used in Nuclear Magnetic Resonance, and is referred to, for example, in papers by R.J. Sutherland and J.M.S. Hutchison (J. Phys. E. Sci. Instrum., Vol. 11, 1973), and by J.M.S. Hutchison, R.J. Sutherland, and J.R. Mallard (J. Phys.'E. Sci. Instrum., Vol. 11, 1978). The saturated nuclear spins in the portion of the volume no in the slice 2 are initially in phase, and the gradient G is maintained for a period of time sufficient to permit the spins to dephase. A second field gradient represented by block 14 in Fig. 2 is then applied to the magnetic field in the Y direction, rfhilst the magnetic field is applied, an rf pulse 11 is applied to the sample, such as to saturate all the spins of the particular type of nuclei under investigtion in the volume, with the exception of those in a slice 3 of thick¬ ness *t y, in the X, Z plane (i.e. normal to the Y direc¬ tion). The waveform of the rf pulse 11 may similarly be calculated by Fourier transform techniques. The net effect of the two pulses 10 and 11 is thus to leave unsaturated only the nuclear spins in a column 4 f which is common to both slice 2 and slice 3« Thi3 column 4 extends in the Z direction. A field gradient G ia now applied in the Z direction, as illustrated in Fig. 2, and an rf pulse 12 is applied to selectively interact with nuclei in a short length of the column 4« The pulse 12 does not interact with those nuclei lying outside column 4, since the spins of those nuclei are already saturated by pulses 10 and 11. Pulse 12 is selected to have a similar frequency distribution to that of pul3es 10 and 11, so that it interacts only with those nuclei lying within a slice 5 orthogonal to the Z axis. Thus, only those nuclei lying in a 3mall element 6 of column 4, where column 4 and slice 5 coincide, interact with pulse 12. OMPI The field gradient Z is then removed, and the spins in element 6 are allowed to decay in the absence of any mag¬ netic field gradients, that is to say in the homogeneous static magnetic field B only. The resulting free induction decay (FID) signal will thus represent almost entirely the transient response from the element 6, and not from any other part from the volume represented by the block 1. The ree induction decay signal can be subjected to Fourier transformation in conventional manner, to yield spectral information about the element. The cycle represented by Fig. 2 is repeated a sufficient number of times to obtain information of the desired accuracy about element 6, and is then repeated with a pulse waveform 12 having a notched "shape" (represented by Fig. 4(a)) corres¬ ponding to a different position along the Z axis for the slice 5- Thus, the length of the column 4 is "scanned", and data obtained for each of the series of element 6 along column 4. In a similar way, the X and Y directions can be scanned, to build up a three-dimensionl spectrum for the whole of the volume represented by the block 1. Although the cycle illustrated in Fig. 2 is relatively simple from a conceptual point of view, the tailoring of pulse waveform to produce a frequency distribution as shown in Fig. 4(a) is in practice quite difficult to achieve. This is because the amplitude envelope produced by Fourier trans¬ formation of the frequency distribution of Fig. 4(a) con¬ sists of a fairly sharp pulse of large amplitude, with a number of side pulses of much lower amplitude. Thus, in order to reproduce the waveform accurately, a radio- frequency transmitter with a very large dynamic range ij required. Therefore, in a preferred method according to the invention, the selective saturation is achieved using two rf pulses. A first rf pulse saturates substantially all of the spins of the appropriate type in the block 1. This pul3e can be of relatively short duration (for example from 1 to 500 microseconds, typically 0 microseconds), and high ampli¬ tude. The saturation is made selective by a restoring pulse, which is adapted to reverse in the region of the respective slice 2 or 3 the effect of the saturating pulse. This is illustrated schematically in Fig. 3 » and the frequency distribution envelopes of the pulses 20 and 21 in Fig. 3 are illustrated schematically in Figs. 4(b) and 4(c). By the use of two separate pulses, it is possible either to use two separate radio-frequency transmitters, one adapted for high amplitude and one for low amplitude modulation, or alternatively a single radio-frequency transmitter able to operate in a high amplitude mode, or a low amplitude mode. Thus, significantly better control over the frequency enve¬ lope can be obtained. The saturating pulses 20 and 23 will typically have a duration of approximately 50 microseconds, and may be applied either before the application of the respective gradients 22 and 25, or in the presence of these gradients. The presence of gradients during the saturation pulses 20 and 23 will, however, have the effect of broaden¬ ing the frequency spectrum over which excitation is re¬ quired, and thus it is preferred that the saturating pul3es 20 and 23 are applied in the absence of field gradients. Restoring pulses 21 and 24 may be thought of as representing a frequency distribution somewhat as shown in Fig. 4(c) and, will be 130° out of phase with the saturating pulses 20 and 23« Restoring pulses 20 and 21 will typically have a duration of from 1 to 5 milliseconds, for example 2 milli¬ seconds. After application of the pulses 21 and 24 » gradients G and G are maintained for a period of time sufficient to allow * s dephasing of the saturated spins in the volume block 1. The length of time required will be of the same order as the duration of the pulses 21 and 24, for example 2 milli¬ seconds. Fig. 3 also illustrates a further preferred technique in accordance with the method of the invention, that of "re- focussing" the signal evolution to produce a spin-echo. The refocussing technique is well-known in Nuclear Magnetic Resonance, and is described, for example, in the Sutherland and Hutchison papers mentioned above. Refocus3ing can be achieved by applying to the sample after the pul3e 26 which is applied in the presence of a gradient 27 in the Z direction, a further pulse 28, such as to cause 180° nutation of the nuclear spins under investigation. In addition, a gradient 29 in the Z direction is applied following the refocussing rf pulse 23. Not only does this method have the effect of producing a spin-echo, but al9o it has the advantage of removing signal evolution due to magne¬ tic field inhomogeneity, and rephasing the signal evolution from nuclei with different chemical shifts. The free infac¬ tion decay following will, therefore, appear to commenc-2 from a zero time origin as illustrated in the lower part of Fig. 3- The techniques of refocussing are adequately described elsewhere, and such references should be considered to be incorporated herein by reference. It should be noted that the pulse 26 should be tailored so as to enable refocussing of the signal evolution to produce spin-echo. An alternative method of refocussing signal evolution is to reverse t e direction of the magnetic field gradient G z , after a predetermined period of time. To produce the desired waveforms, a digital-to-analogue converter may be provided to produce the radio-f equency waveforms, and because of the complexity of the radio- frequency pulses required, it should be noted that a parti¬ cularly large memory requirement is imposed in respect of the electronics responsible for driving the radio-frequency transmitter. The strengths or slopes of the gradients to magnetic field B should be strong in comparison with any residual gradients from inhomogeneities in field B 0 . Some of the criteria for determining the strength of the gradients are discussed below. In a high resolution N.M.R. experiment each nucleus reso¬ nates at a field of magnitude B' given by B 1 = (1 -6>)B (1) where O is the chemical shift. If this experiment is re¬ peated in the presence of a linear field gradient G χ then for one dimension equation (1) has to be modified a3 fol¬ lows: O PI where for the i nucleus '.,g and x. are the resonant field, chemical shift nd spatial location, respec¬ tively. Equation (2) can be rearranged to give: B './B « 1 -ft + ^x x 1 /B (3) The term G x./B can be considered as a pseudo chemical 3hift term. The presence of the gradient G , therefore, extends the chemical shift range. Consequently, the spectral band width of the transmitter mu3t be increased accordingly if all the spins are to be excited. If, however, a narrow part of the chemical shift range is excited by selective irradiation then only nuclei in a slice of thickness _£^ x and mean location xm_, will resonate. In other words, the effect of applying the gradient G has been to spatially label the spins. In general, the sample will produce a multi-line spectrum with each line resonating at a particu¬ lar chemical shift 5^ within a range + 6 " > where 2£ is the expected total width of the spectrum. In a homogeneous static magnetic field the spectra that would be obtained from successive slices ____. x would be identical but in the presence of a linear gradient G the resonant frequency now depends not only on Q . but also on x. so that the relative positions of the spectral lines within each slice Δ.x will be distorted. Furthermore, the rela¬ tive proportions of these lines may also be altered by linas being frequency shifted outside the selective irradiation band/ridth and by lines from adjacent slices being shift-el to be inside the irradiation bandwidth. Additionlly in the presence of a field gradient the indivi¬ dual line shapes will inevitably be broadened so that over¬ lap from adjacent slices can be caused not only by frequency shifts but also by line broadening. Both of these effects can be minimized by choosing G such that the irradiation frequency depends only on the pseudo chemical shift term. If the slice has a width d then G must satisfy the condition that G χ r≥ 2 β^B/d (4) The above condition for the magnitude or gradient G Λ. applies equally to the gradients Gy, r and Gz_. As indicated above, the rf pulses are rendered selective by tailoring their pulse shape to suit the required spectral distribution function. An alternative method is to modulate the width of a series of rf pul3es. This method is, however, rather wasteful of rf power, since a great deal appears in undesirable sidebands and harmonics. If the cosine transform c(t) of desired spectral distribution frequency function g {00) is used to amplitude-modulate the rf carrier then the resulting spectral distribution will be a doublet g {+C ) about the carrier frequency GO - One of this pair may be suppre33ed by also modulating with the sine transform s(t) a second carrier wave in quadrature phase with the first, then combining the two channels- The magnet used to generate the magnetic fieldmaybe of any conventional form, for example a superconducting or non- superconducting magnet. It is preferred that the magnet i i of a sufficient size to accommodate at least a portion of the body of a patient, so that the method and apparatus of the invention can be used to obtain an N.M.R. spectrum from a sample which is a living body. To this end the apparatus may be provided with a patient support, for example a chair or bed on which the patient may rest. The magnetic field is preferably homogeneous over a length of at least 10 cm, to enable a spectrum to be obtained from, for example, various elements within a cube of side 10 cms. JtJlEX ** O PI

Claims: * 45 CLAIMS 1. A method of obtaining an N.M.R. spectrum from a specific volume (6) within a sample volume (1), which method comprises: - maintaining along an axis Z of the sample (1) a static homogeneous magnetic field B ; - applying to the sample (1) a first magnetic field gradient G in a first direction X and an rf pulse (10) to effect selective saturation of all spins of a particular type within the sample (1) except for those lying in a slice (2) of a limited width 4 m. x normal to said first direction X; - applying a respective -second magnetic field gradient G and a second rf pulse (11) relative to a second direction Y normal to said first direc- C tion X; - applying a respective third magnetic field gradient G and a third rf pulse (12) relative to a third direction Z normal to said first and second direc¬ tions X, Y; characterized in that the free induction decay of all of the spins of the particular type, contained in the specific volume (6) defined by the magnetic field gra¬ dients G •Λ, GJr , G * t and the rf pulses (10, 11, 12) O PI respectively, is monitored after the third magnetic field gradient G_ and the third rf pulse (12) have been removed, and thus in the presence of the static magnetic field B only. 2. A method as claimed in claim 1 , wherein the gradient G in the said first direction X is maintained for a period of time sufficient to permit dephasing of nuclear spins of the portion of the sample volume (1) not contained within the said slice (2) before appli¬ cation of the next said gradient G . 3« A method as claimed in claims 1 or 2, wherein the rf pulse (12) applied in the presence of the field gra¬ dient G in the third direction said is such as to enable refocussing of the signal evolution to produce a spin echo. 4- A method as claimed in claim 3, wherein a further rf pulse (28) is applied to the sample (1) after the rf pulse (26) applied in the presence of the field gra¬ dient G in the third direction Z, the said further rf pulse (28) being such as to cause 180 nutation of nuclear spins in the column, whereby to cause refocussing of the signal evolution. 5. A method as claimed in claim 4, wherein a field gra¬ dient Gz in the said third direction Z is applied to the sample (1) after application of the said further rf pulse (28) . 6. A method as claimed in claim 3, wherein refocussing of the signal evolution is carried out by reversing the direction of the magnetic field gradient G applied along the said third direction Z after a predetermined period of time. 7- A method as claimed in one of claims 1 to 6, wherein at least one of the rf pulses for effecting the 3aid selective saturation is a restoring pulse (21, 24), adapted to reverse in the region of the said respec¬ tive slice (2, 3), the saturating effect of a radio- frequency pulse (20, 23) adapted to saturate substan¬ tially all of the spins of the said type in the sample volume (1 ) . 8. A method as claimed in claim 7, wherein the saturating pulse is applied in the substantial absence of field gradients. 9« A method as claimed in claim 8, wherein the saturating pulse has a duration of from 1 to 500 microseconds. 10. A method as claimed in one of claims 8 or 9, wherein the saturating pulse has a duration of about 50 micro¬ seconds. 11. A method as claimed in one of claims 1 to 10, wherein the magnetic field gradients have a magnitude of about 0.5 gauss/cm. 12. A method as claimed in one of claims 1 to 11, wherein the said third direction Z is with the said axis of the sample (1) along which the magnetic field B is applied. 13« A method of diagnosis carried out on a living body, which method comprises obtaining an N.M.R. spectrum from the body by a method as claimed in one of claims 1 to 12. 14- Apparatus for obtaining an N.M.R. spectrum of a sample, comprising means for applying to a sample a homogeneous magnetic field, means for successively applying to the sample (1) magnetic field gradients Gx. Gy. Gz_, in each of three mutually orthogonal directions X, Y, Z, at least one rf transmitter for applying rf pulses (10, 11, 12) to the sample (1) and means for controlling the timing and waveform of the output of the said at least one rf transmitter, to apply to the sample selected rf pulses (10, 11, 12) in synchronization with the said successively applied magnetic field gradients G , G , G , to selec- tively interact with the spins of a particular type in a 3mall volume (6) of the said sample volume (1), characterized in that means are provided for obtaining from the said small volume (6) an output signal indi¬ cative of the free induction decay of the said selec¬ tively effected spins in the absence of said magnetio field gradients G , G , and the rf pulses (10, 11, 12), respectively and in the presence of the static homogeneous magnetic field B only. 15- Apparatus as claimed in claim 14, including a first rf generator adapted to generate a relatively high ampli¬ tude rf signal (20, 23) and a second rf generator adapted to generate a relatively low amplitude rf signal (21 , 24) . 16. Apparatus as claimed in claim 14, including an rf transmitter adapted to be switched between a first mode in which its output is relatively high and a second mode in which its output is relatively low. 17. Apparatus as claimed in one of claims 14 to 16, in¬ cluding sequencing mean3 for controlling the field gradient applying means and the third at least one rf transmitter, in the following sequence: (i) to apply a relatively high magnitude rf pulse (20) in the substantial absence of field gra¬ dient G , to saturate substantially all spins of a particular type in the said sample volume (1), (ii) to apply a field gradient G in a first direc- tion X and a relatively low magnitude rf pul33 (21) in the presence of the said field gradient r* to selectively desaturate spins of the said type lying in a slice (2) normal to the said first direction X, (iii) to apply a second relatively high magnitude rf pulse (23) in the substantial absence of magne¬ tic field gradient G to saturate substan- tially all spins of a particular type in the said sample volume (1), (iv) to apply a field gradient in a second direction Y and a relatively low magnitude rf pulse (24) in the presence of the said field gradient G to selectively desaturate spins of the said type lying in a slice (3) normal to the said second direction Y, (v) to apply a field gradient G_, in the third direction Z and a relatively low magnitude rf pul3e (26) in the presence of the said field gradient G to selectively interact with spins of the said type in a small element (6) of the said sample volume (1) . 18. Apparatus as claimed in claim 17, wherein the said at least one rf transmitter is sequenced to produce a further rf pulse (28) after step (v) to cause refo¬ cussing of the signal obtained. 19« Apparatus as claimed in one of claims 14 to 18, wherein the means for applying a magnetic field B is of a size such as to accommodate within the magne¬ tic field B at least a portion of the body of a human patient. 20. Apparatus as claimed in claim 19, incorporating a patient support, for supporting a patient with a portion of the body of the patient in the homogeneous magnetic field B •

Inventors: GORDON ROBERT EMSLIE, ORDIDGE RODGER JOHN, GORDON, ROBERT, EMSLIE, ORDIDGE, RODGER, JOHN
Applicants: OXFORD RESEARCH SYSTEMS LTD, OXFORD RESEARCH SYSTEMS LTD.
Application year: 1983
Main classification: G01N24
IPC codes: A61B5, G01R33