Abstract:
Radiation damping effects in NMR are compensated by splitting the amplified NMR signal induced in the main probe coil to obtain a correction signal, phase shifting the correction signal to obtain a feedback signal and impressing the feedback signal onto the sample through means independent of the main probe coil.

Description:
FIELD OF THE INVENTION 
     The present invention is in the area of NMR probe technology and relates primarily to the reduction of radiation damping effects upon NMR measurements. 
     BACKGROUND OF THE INVENTION 
     In an NMR experiment, coherent periodic collective motions of nuclear spins induce RF current in the surrounding probe coil. This current in the probe coil, in turn, applies an RF magnetic field upon those nuclear spins. This type of effect is known in the art as &#34;radiation damping&#34;. A common manifestation of radiation damping occurs in the case of liquids in the form of broadening of the solvent line. In the time domain, the time constant of the free induction decay signal is appreciably shortened by the radiation damping effect. 
     In the prior art, it is known to suppress radiation damping effects by deriving a negative feedback signal from the output of the usual RF amplifier and applying that signal with suitable phase shift, to the probe coil. In this manner, the signal induced in the coil by the periodic motions of the nuclear spins may be substantially canceled. One result of this prior art approach is the reduction of all signals and associated noise by a factor (related to the loop gain for the feedback loop). 
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS 
     FIG. 1 illustrates a typical NMR instrument incorporating the present invention. 
     FIG. 2 is a schematicized illustration of an NMR probe of the present invention. 
     FIG. 3 is a schematicized illustration of another embodiment of the invention. 
    
    
     DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     Turning now to FIG. 1, there is shown a typical NMR instrument forming the context for the operation of the present invention. Portions of a typical NMR data acquisition instrument are schematically illustrated in FIG. 1. An acquisition/control processor 10 communicates with an RF transmitter 12, modulator 14 and receiver 16, including analog-to-digital convertor 18 and a further digital processor 20. The modulated RF power irradiates an object 23 in a magnetic field 21 through a probe assembly 22 and response of the object is intercepted by probe assembly 22 communicating with receiver 16. The response typically takes the form of a transient time domain waveform or free induction decay. This transient waveform is sampled at regular intervals and samples are digitized in adc 18. The digitized time domain wave form is then subject to further processing in processor 20. The nature of such processing may include averaging the time domain waveform over a number of similar of such waveforms and transformation of the average time domain wave form to the frequency domain yields a spectral distribution function directed to output device 24. Alternatively this procedure may thus be repeated with variation of some other parameter and the transformation(s) from the data set may take on any of a number of identities for display or further analysis. 
     The magnetic field 21 is directed parallel to the z axis, which polarizes the sample and defines the Larmor frequency thereof, is established by an appropriate means, not shown. Saddle coil(s) 19 are employed for imposing a desired spacial and time dependence of magnetic field. 
     FIG. 2 shows a feedback arrangement of the present invention. Resonant circuit 30 includes a probe coil 42 which is ordinarily disposed to surround sample 32 and which coil has a well defined axis, X. When resonance is excited in sample 32, a circulating current representing that signal is set up in resonant circuit 30 and this signal is coupled through output coupling circuit 34 to a pre-amplifier 36. An inductive coupled circuit is illustrated, but other coupling is well known in the art. The amplified signal with the concomitant noise is split in network 38 and the major portion of the signal is directed toward the rf receiver. A portion defined by splitter network 38 is shifted in phase by phase shifter 40 and the phase shifted resulting signal, the &#34;feedback&#34; signal is directed toward inductance L3 which has an axis Y orthogonal to the X axis of coil 42. Coil 44 is loosely coupled to the sample 32, producing fields along the Y axis within sample 32. 
     As a result of the precession of nuclear spins of the sample, a current is induced in the coil 42, which in turn produces a field B 1  =B X  u x  cosωt, where u x  is a unit vector) along the x axis 50 of sample 32 which is physically contained in the interior of coil 42. 
     The periodic field B 1  acting on the sample spins may be decomposed into two contra-rotating fields, 
     
         B.sup.(+).sub.1/2 =B.sub.x (u.sub.x cos ωt+u.sub.y sin ωt)/2 
    
     
         B.sup.(-).sub.1/2 =B.sub.x (u.sub.x cos ωt-u.sub.y sin ωt)/2 
    
     The precessing nuclear spins are physically responsive to one of the above field components, e.g., that component rotating in the same sense as the nuclear spin precession, for example, B.sup.(+) 1/2   The other component B.sup.(-) 1/2   has only a higher order effect upon the spins and may be safely neglected for the purposes of this explanation. 
     Consider now the portion of the signal output from preamplifier 36 which is directed through splitter network 38 to phase shifter 40. The amplitude of the portion is selectable through this splitter network and the phase is adjusted to produce a signal from coil 46, -B x  sin ωt. This field can also be decomposed into two contra-rotating components: 
     
         B&#39;.sup.(+).sub.1/2 =-B.sub.x (u.sub.x cos ωt+u.sub.y sin ωt)/2 
    
     
         B&#39;.sup.(-).sub.1/2 =-B.sub.x (-u.sub.x cos ωt+u.sub.y sin ωt)/2 
    
     The first of the above expressions is in the same sense as the precessing nuclei and combined with B.sup.(+) 1/2   above produces a null while the other components have no effect upon the precessing nuclei. Thus the reactive effect of the spins upon themselves is canceled. One observes that the feedback in the present invention is coupled back to the sample and not to the coil. 
     In the case of the present invention as well as the probe coil feedback arrangement of prior art, oscillation is avoided by careful attention to phase shifts around the loop. For this reason, a signal having the same sense with respect to the signal processed through the splitter network) is avoided (positive feedback). Phase shifter 40 provides an adequate range of phase shift to avoid the undesirable, and achieve the desirable phase shift to produce the optimum compensation. In some instances the cumulative effect of phase shifts occurring over the entire loop may suffice to provide the requisite effect in lieu of a discrete phase shifter 40. 
     FIG. 3 shows another embodiment of the invention wherein the feedback coupling to the resonating nuclei is isolated from the probe pickup coupling by frequency offset. This frequency offset embodiment incorporates a field modulation arrangement comprising oscillator 52 which provides an AC field for superposition onto DC polarizing field of the NMR apparatus. The signal path through the probe pickup coil 42, the coupling coil 44, the preamplifier 36 and splitter 38 and phase shifter 40 is identical with the previously described embodiment. The signal derived from the splitter network 38 contains (for low modulation index=γB m  /ω 0  &lt;&lt;1) frequency components at the Larmor frequency ω 0 , and at the sidebands ω 0  ±ω m . A narrow band filter 60 selects one of these sidebands, say ω 0  -ω m . This sideband is then modulated by a balanced modulator 62 with the signal ω m  derived from the oscillator 52. The output of balanced modulator 62 contains outputs at lower sideband ω 0  -2ω m  and upper sideband ω 0 . Let the upper sideband (ω 0 ) be selected by narrow band filter 64 and applied to feedback coil 66 which imposes a correcting field B 2  on the resonating nuclei. The field B 2  may be parallel to the axis of the probe coil 42 and oppositely directed to the nuclear magnetism to counter the damping of the free induction decay signal. Alternatively, with the appropriate phaseshift, the field B 2  from coil 60 may be applied at an angle with respect to the axis of coil 42. With a 90° phase shift the field B 2  may be applied along the y axis as shown in FIG. 2. 
     Regenerative feedback is avoided since any signal from coil 66, after being detected by coil 42 and coil 34, will have its frequency shifted by ±ω m  after passing through balanced modulator 62. The shifted frequencies will then be blocked by one of the narrow band filters 60 or 64. The small magnetic field modulation by coil 51 is capable of modulating only the nuclear resonance signals. 
     Many modifications and variations are possible within the scope of the invention. For example coil 42 could be coupled electrically to preamplifier 36 rather than magnetically as shown in FIGS. 2 and 3. Although the invention is described as applied to a Fourier Transform (FT) NMR it can be applied to other types of NMR spectrometer. In FTNMR a short pulse from the transmitter is used to excite resonance. Other forms of excitation include wideband excitation using a random or pseudo-random pulse sequence, and continuous wave (CW) excitation. It is understood that all such variations and modifications will be apparent to one of average skill in the art and are within the scope of the invention. 
     The foregoing description has been limited to specific embodiments of the invention. It is apparent that variations and modifications may be made to the invention with the attainment of some or all of the advantages described. Therefore, it is an object of the appended claims to cover all such variations and modifications as come within the true scope and spirit of the claims.