The proper functioning of living systems and physiological phenotypes depends on molecular composition. Yet simultaneous quantitative detection of a wide variety of molecules remains a challenge1,2,3,4,5,6,7,8. Here we show how broadband optical coherence opens up opportunities for fingerprinting complex molecular ensembles in their natural environment. Vibrationally excited molecules emit a coherent electric field following few-cycle infrared laser excitation9,10,11,12, and this field is specific to the sample’s molecular composition. Employing electro-optic sampling10,12,13,14,15, we directly measure this global molecular fingerprint down to field strengths 107 times weaker than that of the excitation. This enables transillumination of intact living systems with thicknesses of the order of 0.1 millimetres, permitting broadband infrared spectroscopic probing of human cells and plant leaves. In a proof-of-concept analysis of human blood serum, temporal isolation of the infrared electric-field fingerprint from its excitation along with its sampling with attosecond timing precision results in detection sensitivity of submicrograms per millilitre of blood serum and a detectable dynamic range of molecular concentration exceeding 105. This technique promises improved molecular sensitivity and molecular coverage for probing complex, real-world biological and medical settings.
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The data that support the findings of this study are available from the corresponding author upon reasonable request.
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We thank D. Gerz, A. Zigman Kohlmaier, L. Fuerst and I. Kosse for their contributions and help with the measurements. We acknowledge the support of the Max Planck Society, the Center for Advanced Laser Applications of the Ludwig-Maximilians University and the King Saud University via the Researchers Supporting Project (NSRSP-2019/1).
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Extended data figures and tables
a, Schematic of FTS. b, Schematic of FRS. c, Portions of the background signal contributed by the sample response to the FTS (blue, first right-hand-side term of equation (1a)) and to the FRS (red, first right-hand-side term of equation (1b)) signals at a fixed delay (τ = 1,500 fs). For illustration purposes, the nonlinear upconversion efficiency was set to 1 and the ‘carved out’ effective window time length to 50 fs (without loss of generality). Example parameters: 190-fs Gaussian excitation pulse and 1,139-cm−1 DMSO2 absorption (see Extended Data Table 1). Source Data
a, Infrared excitation pulse (normalized to maximum), recorded with attenuating optical density (OD) filters instead of the cuvette in the beam path, for increasing attenuation and measurement time T. A 1,200-fs scan range and T = 16 s and T = 1,600 s were considered. Small variations of the pulse shape for different attenuations are attributed to slight dispersion variations among the OD filters. The attenuation-independent pulse shape confirms the instrument linearity over the entire parameter range considered. b, c, Spectral intensity (normalized to the maximum of the attenuation-free measurement) and phase of the signals in a, respectively. The detection noise floors in b were obtained by blocking the MIR signal and evaluating the mean of the (white) noise in the considered spectral range, and confirm the linear decrease of the noise floor with T. For the data in c, for all time-domain waveforms a super-Gaussian filter (width 700 fs, order 20) was applied. Source Data
See subsection ‘High-power femtosecond oscillator and generation of waveform-stable MIR Pulses’ in Supplementary Information section I for details. a, HWP, half-wave plate; QWP, quarter-wave plate; IDFG, intra-pulse difference frequency generation; IDT, interferometric delay tracking; Ge, germanium beam combiner. All steering mirrors for the MIR beam were gold-coated. In the bandwidth-optimized instrument setting, four custom dispersive mirrors were added to the MIR beam path (see text). The pulse was temporally compressed with customized dispersive optics. Pulse compression. EOS traces of the excitation pulse transmitted through water in the bandwidth-optimized instrument setting, with (blue) and without (red) four dispersive mirrors in the MIR beam path. c, As in b but on a logarithmic scale, visualizing the improved roll-off of the signal achieved with the dispersive optics. Source Data
a, Frequency-resolved measurement of the noise of the balanced detection (black), and calculated shot noise (red). The dashed line indicates the lock-in frequency, and its peak stems from the chopper. b, Comparison of MIR power depletion after EOS crystal for the two different crystal thicknesses. The oscillations originate from interferences of the MIR pulse incident to the EOS crystal and MIR radiation generated therein (these oscillations do not affect the performance of EOS detection). Source Data
Extended Data Fig. 5 Measurement of noise contributions for the estimation of the performance of FTS with our femtosecond-laser-based source, our mechanical scan, and state-of-the-art infrared detection.
a, The setup mimics a FTS setup in the Mach–Zehnder configuration, with balanced lock-in detection. For lock-in frequency modulation, a mechanical chopper is placed in the ‘sample arm’. The two arms are recombined with a 50:50 beam splitter. The two outputs are detected with two independent MIR detectors (see text for details). The power impinging on each detector was limited to 450 mW, corresponding to a detector output voltage of 20 V. The relative intensity noise (RIN) spectrum of the source is recorded with an FFT-Analyzer in the range 0.1–100 kHz (before balanced detection). Balanced lock-in detection is performed with a lock-in amplifier with differential input. The beam block was used in the measurements shown in c. b, RIN spectrum of the free-running (red curve) and intensity-stabilized (blue curve) MIR beam (before the interferometer). The integrated RIN of the stabilized source from 1 Hz and 100 kHz is as low as 0.04%. c, Demodulated (after lock-in detection with a time constant of 1.6 ms and 4th-order filter) time-domain trace of detector noise (grey), local-oscillator signal with sample arm blocked (turquoise) and of the combination of both interferometer arms impinging on the balanced detection (blue). The inset shows a 1-second section of the signals, for a detailed comparison of the local-oscillator noise and the detector noise. Source Data
a, Fit of a Lorentzian oscillator to the 1,139 cm−1 absorption of (low-concentration) DMSO2. Black line, intensity transmission through pure, molecular DMSO2, determined by referencing the transmission spectrum of a 1 mg ml−1 solution to that of water, measured via FTIR, and normalizing to a 1-µm path. Green line, least-squares fit (1,080–1,190 cm−1) of a Lorentzian oscillator to the 1,139 cm−1 absorption, yielding a full width at half depth of 13.47 cm−1 and an absorption coefficient α = 11.96 cm−1. The numerical example shows the instantaneous and resonant parts of the electric field as described by equations (1) to (4) in Supplementary Information section II. The initial pulse is a Gaussian pulse with an intensity envelope (full width at half maximum) of 190 fs. The Lorentzian absorption band has a peak of α2z with α2 = 0.0024 cm−1, corresponding to a 200 ng ml−1 solution of DMSO2 in water, and a width δυ = 13.47 cm−1. These values were obtained from fitting a Lorentzian absorber to the 1,139 cm−1 band of the transmission spectrum of a 1 mg ml−1 solution obtained with FTIR and linear extrapolation to a concentration 5,000 times lower. b, Time-domain representation of the normalized envelope functions of the electric fields described (see key). A value of tB = 1.5 ps is chosen. The green vertical bars indicate the boundaries of the band-pass-filtered resonant response shown in green: 1.5 ps and 4 ps. c, Magnitudes of the Fourier transforms of the envelopes shown in a, normalized to C. At the absorption maximum, the discrepancy between the resonant response as in Supplementary Information section 2 and its approximation as in Supplementary Information section 3 is 1%, justifying this convenient approximation. The error introduced by band-pass filtering the resonant response between 1.5 ps and 4 ps compared to the high-pass time-filtered signal is 4%. Source Data
Spectral intensity is shown for different concentrations, after high-pass-time-filtering at tB = 1,500 fs and subtraction of pure water reference, normalized to the spectral intensity of the reference pulse. Green dashed lines, modelled Lorentzian oscillator with the parameters derived from the fit in Extended Data Fig. 6. This model agrees excellently with the measured fingerprints, and confirms the minimum detectable absorbance predicted by equation (2) as well as the linear response of the instrument. Source Data
a–d, Comparison of the loading vectors for the first principal component for the FTIR data (a) and the FRS data (b) from the serum spiking experiment, with the pre-processed GMF data (see text) of the FTIR (c) and FRS (d) measurements of a 1 mg ml−1 DMSO2 solution. We note that the FRS spectra are complex, so the real and imaginary parts were considered separately (and stitched to single vectors). e, Figure of merit (FOM) (colour scale in arbitrary units; see Supplementary Information section VI) quantifying the separation of classes according to the first principal component (the lower the FOM, the better the separation), evaluated for a large range of the beginning time tB and time window length Δt. The cross indicates parameters yielding optimum separation. f–i, Comparison of the loading vectors for the first principal component for the FTIR data (f) and the FRS data (g) from the sugar mixture experiment, with the pre-processed GMF data of the FTIR (h) and FRS (i). For the latter, the difference of the spectra of the 50/50 mixture and the pure maltose solution is shown. The real and imaginary parts were considered separately. j, FOM quantifying the separation of classes according to the first principal component, in analogy to e. Source Data
Extended Data Fig. 9 Absorption spectra of 10 mg ml−1 aqueous solutions of maltose and melibiose, measured by FRS and FTIR.
The difference in total absorption is due to the differing cuvette thickness. a, FRS; b, FTIR. OD, optical density. Source Data
This file contains Supplementary Information sections 1–7 and Supplementary References.
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Pupeza, I., Huber, M., Trubetskov, M. et al. Field-resolved infrared spectroscopy of biological systems. Nature 577, 52–59 (2020) doi:10.1038/s41586-019-1850-7