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Logo of nihpaAbout Author manuscriptsSubmit a manuscriptHHS Public Access; Author Manuscript; Accepted for publication in peer reviewed journal;
 
J Magn Reson. Author manuscript; available in PMC 2012 April 1.
Published in final edited form as:
PMCID: PMC3065959
NIHMSID: NIHMS271822

Straightforward, effective calibration of SPINAL-64 decoupling results in the enhancement of sensitivity and resolution of biomolecular solid-state NMR

Abstract

We describe a simple yet highly effective optimization strategy for SPINAL-64 1H decoupling conditions for magic-angle spinning solid-state NMR. With adjustment of the phase angles in a coupled manner, the optimal conditions resulting from three parameter optimizations can be determined with adjustment of a single phase. Notably, echo T2 relaxation times for 13C and 15N show significant enhancement (up to 64%), relative to the previous described SPINAL-64 conditions, under the moderate 1H decoupling levels (60 – 100 kHz) and MAS rate (13.3 kHz) commonly employed for high-resolution SSNMR spectroscopy of proteins. Additionally, we also investigated the effect at higher spinning rate (33.3 kHz) and compared the results with other 1H decoupling schemes (TPPM, XiX), as well as SPINAL-64 with the originally reported optimal values.

Keywords: magic-angle spinning, solid-state MMR, proton decoupling, SPINAL-64

1. Introduction

High-resolution spectra are essential for the study of large biological systems by magic-angle spinning (MAS) solid-state NMR (SSNMR) spectroscopy. One of the main limitations for such studies are imposed by the lifetimes of transverse magnetization (T2) [1] for the observed nuclei, due to the strong dipolar coupling interactions between 1H and X (usually 13C or 15N) [2]. As a result, considerable research effort has resulted in a plethora of 1H decoupling sequences[36].

Continuous-wave (CW) [7] decoupling was for many years the only effective heteronuclear 1H method for rigid solids, but for most applications has been supplanted by two pulse phase-modulation (TPPM) [8], which consists of a series of near π pulses with alternating phases (see Fig. 1b). A variety of 1H decoupling methods with phase and/or frequency modulations extending upon the TPPM approach were subsequently developed [36]. Among these, we have observed that SPINAL-64 (small phase incremental alternation with 64 steps, Fig. 1b) [9], is particularly robust with respect to radio-frequency (RF) inhomogeneity and/or pulse width imperfection and has better compensation for resonance offsets, arising from the compensatory super cycles of the basic SPINAL element. SPINAL-64 has also been described to be superior in performance under some regimes of decoupling power than TPPM [10]. The benefits of SPINAL are particularly evident, in comparison with CW decoupling, for magnetically aligned samples [11].

Fig. 1
Part of the arrays of the variable parameters for 13C detection with (a) SPINAL-64 and (b) TPPM and 15N detection with (c) SPINAL-64 and (d) TPPM 1H decoupling for NAV. All arrays were acquired with 85 kHz of decoupling power at 750 MHz 1H frequency and ...

In the original publication describing SPINAL-64, Fung et al. note the optimal values for the flip angle θ, phase angle ϕ, and phase increments α and β to be, 11/12 π, 10°, 5° and 10° [9], respectively. Thakur et al. reported improvements in performance and efficiency upon modification of the phase (from 1 to 5°) and angle increments (from 3–16°) on crystalline glycine [12]. In the course of utilizing the SPINAL-64 sequence for studies of biomolecular samples including nanocrystalline, fibrillar and membrane proteins, at different moderate MAS rates (10–16.7 kHz), we found that different phase angles from the ones previously reported were consistently preferred. Although we arrived at these values by empirical, experimental optimization in three dimensions, we have also identified trends that enable the global optimum solution to be found in a small fraction of the total optimization time. The results yield an improved decoupling performance, as shown in Figure 1 for N-acetyl valine (NAV). The changes in phase parameters are modest, but yield substantial benefits in relaxation times and resolution for 2D MAS NMR spectra.

2. Results and discussion

A comparison of the 13C and 15N transverse magnetization lifetimes (T2) for the originally reported optimal values [9] and the values we obtain on our samples following optimization is depicted in Figure 2. An increase for the T2 values up to 64% (15N) and 25% (13C) were noted for uniformly 13C-15N enriched A30P alpha-synuclein (AS) in fibrillar form (Figure 2). A comparison of two frequently used 2D correlation experiments is depicted in Figure 3, using the originally reported optimal values [9] (left) and the optimized values (right), with a 1H decoupling power of 80 kHz. These spectra (13C-13C with 50 ms DARR mixing and 15N-13C with specific CP) demonstrate an improved sensitivity (up to 80% enhancement of the S/N or 125% of the peak height for Ala CA-CB cross-peaks and 63% of the S/N or 100% of the peak height for Thr CA-CB cross-peaks) and linewidths (up to 67% for the 15N and 44% for 13C in the 15N13CA 2D), as shown in expanded regions in Figure 3.

Fig. 2
Schematic representation of (a) the pulse sequence used for the determination of the T2 values with (b) TPPM and SPINAL-64 1H decoupling (flip angle (θ), phase angle (ϕ) and phase increments α and β for the phase angle). ...
Fig. 3
Comparison of expanded regions of A30P AS fibrils 2D spectra acquired with (left) optimal reported values (θ =(11/12)π, [var phi]= 10°, α=5° and β=10°) [9] and (right) optimized values of the SPINAL-64 ...

We optimized SPINAL-64 1H decoupling with respect to the flip angle (θ), the phase angle (ϕ) and the phase increments α and β (see arrays in Figure 4 for A30P AS fibrils). During optimization, θ was varied from 150° to 210°, ϕ from 0° to 10°, and α from 0° to 10°. These optimizations, conducted on a variety of biological samples, demonstrated that the best values, under the moderate 1H decoupling levels and MAS rate commonly employed for high-resolution SSNMR, occur when the parameters [var phi] and α add up to 10° (as shown for A30P AS fibrils and NAV in Tables 1 and and2,2, respectively), which corresponds to arrays located in the diagonal of the plots (indicated with darker background in Figure 1 and and4).4). Thus, the most efficient optimization of SPINAL-64 would include a 3D array of θ, ϕ from 0° to 10° and α from 10° to 0°, where ϕ and α add to 10° in each step in a single dimension of the array. In all these experiments the variable parameter β was set to two times α, which corresponds to the optimum or very close to the optimum, as shown in Figure 4.

Fig. 4
(a) Array of the SPINAL-64 parameters (θ, [var phi] and α; β=2α) for A30P AS fibrils at 80 kHz 1H decoupling for 13C detection. Soft pulses were used to select the 13CA. Spectra labeled with (*) correspond to the closed ...
Table 1
Optimized parameters for SPINAL-64 1H decoupling for A30P AS fibrils at different 1H decoupling power levels with 13C and 15N detection acquired at 13.3 kHz MAS and 600 MHz 1H frequency.
Table 2
Optimized parameters for SPINAL-64 1H decoupling for NAV at different 1H decoupling power levels (70–100 kHz) and MAS rates (13.3 – 33.3 kHz) MAS for 13C and 15N detection acquired at 750 MHz 1H frequency.

The improvement of transversal magnetization lifetimes of 13C and 15N is clearly shown using NAV (Figure 2), but also demonstrates an improvement of SPINAL-64 versus TPPM or XiX, when the variable parameters are optimized at a moderate MAS rate (13.3) and commonly employed power levels (70–100 kHz) for high-resolution SSNMR [10] (see Figure 1). In the optimization arrays, θ was varied from 150° to 210° for SPINAL-64 and TPPM, ϕ from 0° to 10° and α from 0° to 10° for SPINAL-64 and ϕ from 0° to 30° for TPPM. These arrays also demonstrate a smaller dependence of the signal intensity on the decoupling pulse duration for SPINAL-64 and thus more experimental stability with respect to changes in pulse widths for a selected conditions than TPPM over the same range of θ and ϕ, which is an important requirement for conducting long multidimensional experiments in biomolecular SSNMR.

Finally, we also explored the effect of the optimization at a higher MAS rate (33.333 kHz), as reported on Tables 24. Our results demonstrate a considerable improvement in the performance of SPINAL-64 over the originally optimal reported [9] variable parameters and shows that SPINAL-64 with the optimized parameters behaves similarly or better than TPPM or XiX for 1H decoupling powers between 70–100 kHz. At high MAS rate (33.333 kHz), the optimization arrays showed slightly different preferred values for the variable parameters than observed for moderate spinning rates. The best values occur when the parameters [var phi] and α add up to 8° and/or 10°, depending on the power level.

Table 4
15N T2 measurements for N-acetylvaline (NAV) at different 1H decoupling power levels and schemes (TPPM, SPINAL-64 with originally reported optimal [9] and optimized variable parameters and XiX). 1H carrier was set at the frequency of the 1HN peak. Error ...

3. Conclusions

By optimizing the variable parameters for SPINAL-64 1H decoupling for a variety of biological samples, we observed a considerable improvement in the performance of SPINAL-64 versus the originally reported parameters (θ=(11/12)π, [var phi]= 10°, α=5° and β=10°) [9]. Here, we have reported a series of experiments to demonstrate the effect on the T2s for A30P AS fibrils and NAV at different power levels, as a comparison with the originally reported values, TPPM and XiX decoupling, as well as the effect in multidimensional SSNMR experiments. Our results show an improvement up to 64 % in the T2s and a sensitivity enhancement up to 80% of S/N of individual peaks in multidimensional experiments of A30P AS fibrils that lead to significant improvement in the spectra resolution.

4. Experimental

U-13C,15N-labeled A30P AS was prepared as described in Kloepper et. al. [13] and fibrils were prepared for SSNMR as recent studies for the wild-type AS fibrils describe elsewhere. Samples were packed into 1.6 and 3.2 mm MAS NMR rotors (Varian, Inc., Palo Alto, CA) and confined to the active sample region of the rotor and kept hydrated by Kel-F and rubber spacers [14].

All experiments were carried out with the variable temperature gas at 10 °C, which corresponded to an actual sample temperature of 14 °C, as determined by ethylene glycol calibration [15]. Experiments were carried out on a 600 MHz Infinity Plus spectrometer (Varian NMR) equipped with a HXY (T3) probe tuned to 1H-13C-15N triple mode at 13.333 kHz MAS rate and on a 750 MHz Wide Bore Vnmrs spectrometer (Varian NMR) equipped with a HFXY probe tuned to 1H-13C-15N triple mode at 13.333 and 33.333 kHz MAS rates. For the 600 MHz spectrometer, the NAV π/2 pulse widths for 1H and 13C were 1.90 and 2.70 μs, respectively, and for A30P AS fibrils, the π /2 pulse widths for 1H, 13C, 15N were 2.25, 2.62 and 3.75 μs, respectively. For the 750 MHz spectrometer, the NAV π/2 pulse widths for 1H, 13C and 15N were 1.90, 2.20 and 3.90 μs, respectively. All experiments utilized tangent ramped cross polarization [16]. TPPM [8], SPINAL-64 [9] and XiX [9] 1H decoupling was applied during acquisition and evolution periods. For the 2D 13C-13C spectra, the dipolar assisted rotational resonance (DARR) scheme [17] was used for 13C-13C mixing. For the 2D NCA experiments, a selective SPECIFIC CP [18] was used for polarization transfer from 15N to 13C. Average echo T2s (typically referred to as T2' [1]) values for 13CA and 15N at different decoupling conditions and optimization conditions were measured using a 1D CP Hahn-echo [19]experiment with a 180° soft pulse on 15CA resonance to remove the effect of 13C-13C J-couplings [20] (no soft pulse was used for the 15N measurement). Chemical shifts were referenced externally with adamantane (assuming the downfield peak to resonate at 40.48 ppm) [21].

Plotting and data analysis were carried out with scripts written in house, using Python 2.5, specifically with the python modules `scipy' and `matplotlib'. 2D spectra were processed with NMRPipe [22] and were analyzed with Sparky program[23]. Back linear prediction and polynomial baseline correction were applied to the direct dimension. Zero filling and Lorentzian-to-Gaussian apodization were used for each dimensions before Fourier transformation.

Table 3
13CA T2 values for N-acetylvaline (NAV) at different 1H decoupling power levels (70–100 kHz) and schemes (TPPM, SPINAL-64 with originally reported optimal [9] and optimized variable parameters and XiX) at 750 MHz 1H frequency. 1H carrier was set ...

Supplementary Material

01

Acknowledgements

This work was supported by the National Institutes of Health (R01-GM073770 and R01-GM073770 ARRA supplement to C.M.R.). The authors would like to thank Dr. Ming Tang for carefully reading the manuscript.

Footnotes

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