Millimeter-scale wide-field mid-infrared photothermal imaging enabled by a broadly tunable picosecond optical parametric oscillator

Anju Jose; Anooj Thayyil Raveendran; Christoph Krafft; J\"urgen Popp; Supatcharee Cael

arxiv: 2607.06208 · v1 · pith:YHLONZ2I · submitted 2026-07-07 · physics.optics · physics.app-ph· physics.bio-ph· physics.ins-det

Millimeter-scale wide-field mid-infrared photothermal imaging enabled by a broadly tunable picosecond optical parametric oscillator

Anooj Thayyil Raveendran , Supatcharee Cael , Anju Jose , J\"urgen Popp , Christoph Krafft This is my paper

Reviewed by Pith T0 review T1 audit T2 compute T3 formal T4 kernel 2026-07-08 13:05 UTCglm-5.2pith:YHLONZ2I record.json open to challenge →

classification physics.optics physics.app-phphysics.bio-phphysics.ins-det PACS 07.60.Pb07.57.Ty87.64.-t

keywords imagingwide-fieldmid-infraredphotothermalplatformspectralviewbelow

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The pith

OPO-driven photothermal microscope images 1 mm fields in mid-infrared

A machine-rendered reading of the paper's core claim, the machinery that carries it, and where it could break.

This paper claims that a commercially available picosecond optical parametric oscillator (OPO), delivering pulse energies up to 360 microjoules across a tuning range of 625–4327 cm⁻¹, can drive a fluorescence-detected mid-infrared photothermal (F-MIP) microscope to achieve a field of view approximately 1 mm in diameter — about 3.6 times larger in area than the prior state of the art. The central mechanism is straightforward: photothermal imaging quality at wide fields scales with mid-infrared fluence, and no previously reported wide-field MIP source has exceeded 80 microjoules per pulse. By combining this high pulse energy with fluorescence-based detection, which yields roughly 100-fold larger modulation depth than scattering-based schemes, the system captures chemically specific images over millimeter-scale areas while preserving spectral fidelity. The authors demonstrate the platform on fluorescent polystyrene beads, showing that the F-MIP spectrum matches a reference FTIR spectrum across the 2800–3100 cm⁻¹ range, and report what they believe is the first wide-field MIP imaging below 900 cm⁻¹ (down to 625 cm⁻¹), accessing the deep fingerprint region. They then image tuberculosis-infected tissue sections, producing tiled mosaics spanning more than 2 mm that resolve lipid and protein distributions at 1740 cm⁻¹ and 1660 cm⁻¹ respectively, showing spatially distinct lipid-enriched regions consistent with infection pathology. The paper positions this combination of high pulse energy, low repetition rate (100 Hz), and broad spectral tunability in a single commercial laser source as a scalable platform for high-throughput vibrational imaging of large biological specimens and advanced materials.

Core claim

The core discovery is that the long-standing trade-off between field of view, pulse energy, and spectral tunability in wide-field mid-infrared photothermal imaging can be substantially broken by pairing a high-pulse-energy commercial OPO (up to 360 µJ, roughly 4.5 times more than any prior wide-field MIP source) with fluorescence-detected readout. The result is a field of view of approximately 1 mm diameter at high-wavenumber frequencies and the first reported wide-field MIP imaging below 900 cm⁻¹, all from a single tunable source covering 625–4327 cm⁻¹. The authors verify spectral fidelity against FTIR reference spectra and demonstrate a temperature rise of only 4.6 K at the sample plane,确认

What carries the argument

The central object is the F-MIP platform: a fluorescence-detected mid-infrared photothermal microscope driven by a picosecond OPO. The OPO provides up to 360 µJ per pulse at 100 Hz across 625–4327 cm⁻¹. A 450 nm LED excites fluorescence in the sample, and a synchronized CMOS camera captures alternating mid-IR-on (hot) and mid-IR-off (cold) frames. The photothermal effect — vibrational absorption causing a local temperature rise that modulates fluorescence intensity — provides the chemical contrast. Off-axis parabolic mirrors tailor the mid-IR beam diameter at the sample plane, with different focal-length configurations for large-area high-wavenumber imaging versus tighter focusing for the指纹

If this is right

Large-area, chemically specific imaging of tissue sections with minimal tiling could enable faster digital histopathology workflows, where contiguous millimeter-scale chemical maps are needed rather than stitched sub-200-µm fields.
Access to the deep fingerprint region (625–900 cm⁻¹) in wide-field mode opens chemical imaging of vibrational modes previously inaccessible to wide-field MIP, potentially expanding the range of distinguishable biomolecular and material signatures.
The platform's combination of millimeter-scale fields with microscale resolution could support high-throughput microplastic detection and classification in environmental samples, where large-area screening is currently bottlenecked by small fields of view.
If beam homogenization and automated wavelength-dependent focusing are implemented, the system could perform multispectral imaging across the full 625–4327 cm⁻¹ range without manual reconfiguration, making broad-spectrum chemical mapping practical for routine use.

Load-bearing premise

The claim that this is a scalable platform for quantitative high-throughput imaging rests on the assumption that the Gaussian beam profile of the mid-IR excitation — which reduces signal intensity toward the edges of each field — does not systematically bias the chemical contrast ratios used to interpret tissue composition. The paper acknowledges this inhomogeneity but does not quantify its effect on the lipid-protein overlay maps used to identify infection-associated regions

What would settle it

If the Gaussian beam falloff at field edges systematically distorts the ratio of photothermal signals at 1660 cm⁻¹ and 1740 cm⁻¹ by a clinically or chemically significant margin, then the spatially distinct lipid-enriched regions identified in tuberculosis tissue could partly reflect illumination geometry rather than sample chemistry, undermining the biological interpretability of the mosaic images.

Figures

Figures reproduced from arXiv: 2607.06208 by Anju Jose, Anooj Thayyil Raveendran, Christoph Krafft, J\"urgen Popp, Supatcharee Cael.

**Figure 1.** Figure 1: Optical and electronic layout of the wide-field F-MIP microscope. LED illumination is filtered (F2) and relayed by lens L1 to the back focal plane of the microscope objective (MO). The excitation light is reflected by a dichroic mirror (DM) onto the sample. Fluorescence emission is collected by the MO, transmitted through the DM and emission filter (F1), and detected by a CMOS camera. The mid-IR beam is di… view at source ↗

read the original abstract

Wide-field mid-infrared photothermal (MIP) imaging enables chemically specific microscopy with submicron spatial resolution but remains fundamentally limited by the trade-off between field of view, mid-infrared pulse energy, and spectral tunability. As a result, current wide-field implementations are typically restricted to fields of view below 200 {\mu}m and to either the fingerprint or high-wavenumber spectral regions. Here, we overcome these limitations by developing a wide-field fluorescence-detected mid-infrared photothermal (F-MIP) imaging platform driven by a commercial picosecond optical parametric oscillator (OPO). The system provides pulse energies of up to 360 {\mu}J together with a broad tuning range from 625 to 4327 cm-1, enabling millimeter-scale wide-field imaging in the high-wavenumber regions. We demonstrate a field of view of approximately 1 mm in diameter for fluorescently labeled polystyrene beads while preserving spectral fidelity. Furthermore, the platform enables, to our knowledge, the first wide-field MIP imaging below 900 cm-1. To demonstrate its applicability to biomedical imaging, we performed large-area mosaic imaging of fluorescent tuberculosis-infected tissue sections, providing chemically resolved maps over millimeter-sized sample areas. These results establish broadly tunable OPO-driven F-MIP as a scalable platform for high-throughput vibrational imaging of large biological specimens and advanced materials.

Editorial analysis

A structured set of objections, weighed in public.

Desk editor's note, referee report, simulated authors' rebuttal, and a circularity audit. Tearing a paper down is the easy half of reading it; the pith above is the substance, this is the friction.

Desk Editor's Note private letter to a colleague

Solid engineering advance in wide-field MIP; tissue demo is preliminary but honest about it

read the letter

This paper combines fluorescence-detected MIP with a high-pulse-energy commercial OPO (360 µJ, 625–4347 cm⁻¹) to achieve a ~1 mm diameter FOV — roughly 3.6× the area of the prior best (ref 14, 700×400 µm). It also demonstrates wide-field MIP imaging below 900 cm⁻¹ for the first time. The core engineering achievement is real and well-documented: the polystyrene bead data includes FTIR spectral comparison, a measured spatial resolution consistent with diffraction, and a temperature rise estimate (4.6 K) well below the PS glass transition. Table 1 provides a fair and useful comparison to prior wide-field MIP systems. The spectral fidelity at both high-wavenumber and fingerprint regions is convincingly shown. Credit is earned here — this is a genuine step forward in FOV and spectral coverage for wide-field MIP, and the authors are transparent about the trade-offs (100 Hz rep rate, Gaussian beam profile, wavelength-dependent beam divergence requiring manual realignment). The stress-test concern about FOV definition has some merit: the tissue mosaics use tiles smaller than the full Gaussian diameter (756 µm tiles from a ~1 mm field at 2920 cm⁻¹; 130×162 µm tiles from a ~220 µm field at 1660/1740 cm⁻¹). This is standard microscopy practice — you image the central, more uniform region — but it means the headline 3.6× comparison would be more convincing if the paper stated an explicit uniformity criterion (e.g., SNR threshold or % of peak signal) for the FOV boundary. Without that, we can't be sure the comparison to ref 14 is apples-to-apples. The more substantive concern is the tissue imaging. The 1660/1740 cm⁻¹ ratio map could be affected by beam profile differences between wavelengths, since the hot-cold/cold normalization corrects fluorescence intensity but not mid-IR fluence inhomogeneity. The lipid-protein assignments are unvalidated — no histological correlation, no orthogonal lipid stain. The authors acknowledge this, noting that future studies will employ additional biomarkers. So they're not overselling, but the biological claims are currently at the level of 'consistent with expected chemistry,' not demonstrated. These are not fatal flaws. The paper is an engineering demonstration with a preliminary biological application, and it reads as such. The main gaps — flat-field correction, quantitative validation of tissue contrast, automated beam conditioning — are addressable in revision or follow-up work. This deserves a serious referee. The reviewer should push for an explicit FOV definition, a flat-field correction or at minimum a characterization of edge signal falloff, and some form of histological correlation for the tissue images. would_accept_peer_review = true.

Referee Report

2 major / 6 minor

Summary. This manuscript presents a wide-field fluorescence-detected mid-infrared photothermal (F-MIP) imaging platform driven by a commercial picosecond OPO. The system delivers up to 360 µJ pulse energy across a broad tuning range (625–4327 cm⁻¹). The authors demonstrate imaging of polystyrene (PS) beads with a field of view (FOV) of approximately 1 mm diameter in the high-wavenumber region, and ~220 µm in the fingerprint region (down to 698 cm⁻¹). They also present mosaic imaging of tuberculosis-infected tissue sections, mapping lipid and protein distributions at 1740 cm⁻¹ and 1660 cm⁻¹, respectively. The central claims regarding FOV, spectral range, and pulse energy are benchmarked against prior literature (Table 1) and supported by experimental measurements.

Significance. The manuscript reports a substantial experimental advance in wide-field MIP imaging. The combination of millimeter-scale FOV, broad spectral tunability spanning fingerprint to high-wavenumber regions, and first demonstration of wide-field MIP below 900 cm⁻¹ is a significant hardware achievement. The spectral fidelity claim is supported by comparison of the F-MIP spectrum of PS with FTIR reference (Fig. 2g, Fig. S2). The temperature rise estimate (4.6 K, Fig. S5) is below the PS glass transition, supporting nondestructive imaging. The tissue imaging demonstration (Fig. 3) shows practical applicability of the platform to biomedical samples.

major comments (2)

§4 (text discussing Fig. 3), Fig. 3f: The 1660/1740 cm⁻¹ overlay is a ratio of two images acquired at different wavelengths with potentially different beam profiles. The paper notes that wavelength-dependent beam divergence requires manual OAP1 repositioning. The hot-cold/cold normalization corrects for fluorescence intensity variations but does not correct for mid-IR fluence inhomogeneity. If the beam profiles differ between 1660 and 1740 cm⁻¹, the ratio map could reflect illumination artifacts rather than sample chemistry. The authors should either apply a flat-field correction or demonstrate that the beam profiles are sufficiently similar at these two wavelengths to not bias the chemical contrast maps. This is load-bearing for the biological conclusions about lipid-enriched regions.
§3 (text discussing Fig. 2) and Table 1: The 1 mm FOV claim and the 3.6× improvement over prior work (ref 14: 700×400 µm) are central quantitative claims. However, the paper does not state the criterion used to define the FOV boundary (e.g., SNR threshold, % of peak signal). The paper acknowledges that the Gaussian beam profile 'reduces signal uniformity toward the edges.' In the tissue imaging (§4), the 3×3 mosaic at 2920 cm⁻¹ uses 756×756 µm tiles from the ~1 mm FOV, and at 1660/1740 cm⁻¹, tiles shrink to 130×162 µm from a ~220 µm FOV. This suggests the usable quantitative FOV is smaller than the headline figure. The authors should explicitly state the FOV definition criterion and discuss whether the comparison to prior work (Table 1) is apples-to-apples, particularly if prior work defined FOV by signal uniformity rather than full beam diameter.

minor comments (6)

§2: The text states the OPO offers broad tunability across '625–4347 cm⁻¹' while the abstract states '625 to 4327 cm⁻¹.' Please reconcile.
Table 1: The entry for ref 15 (Schnell et al.) lists '500 mW^a' with footnote 'a' indicating author approximation. It would be helpful to clarify how this approximation was derived.
§4: The text references 'Fig. S7c' and 'Fig. S7d' regarding the Gaussian beam profile and camera sensor fill, but the supplementary figures are not available in the main text. Ensure these are clearly labeled and accessible in the supplement.
§4: The sentence 'The overlay of the 1660 cm⁻¹ and 1740 cm⁻¹ absorption maps highlighted regions of spectral contrast' contains a formatting artifact ('cm⁻¹f'). Please correct.
§3: The text states 'No previously reported wide-field MIP source – QCL, FEL, or OPO – has exceeded 80 µJ per pulse energy' citing refs 13-15. Ref 13 is a self-citation describing an FEL with 1 µJ pulse energy. The claim is accurate but the citation grouping is slightly misleading since ref 13's FEL is well below 80 µJ; consider citing the specific source characteristics more precisely.
Fig. 2: The figure caption states pulse energy at the sample plane was '~280 µJ' for panels (c-d) and '~20 µJ' for panels (e-f). It would be helpful to also state the pulse energy used for panel (a) in the caption for completeness.

Simulated Author's Rebuttal

2 responses · 0 unresolved

We thank the referee for a thorough and constructive assessment. Both major comments identify legitimate gaps in our manuscript that we will address in revision.

read point-by-point responses

Referee: §4, Fig. 3f: The 1660/1740 cm⁻¹ overlay may reflect illumination artifacts from differing beam profiles rather than sample chemistry. The hot-cold/cold normalization does not correct for mid-IR fluence inhomogeneity. Authors should apply flat-field correction or demonstrate beam profiles are sufficiently similar.

Authors: The referee raises a valid concern. Our hot-cold/cold normalization corrects for spatial variations in fluorescence excitation and collection efficiency, but it does not correct for spatial variations in mid-IR fluence. If the beam profiles at 1660 and 1740 cm⁻¹ differ significantly, the ratio map in Fig. 3f could be biased by illumination inhomogeneity rather than reflecting genuine chemical contrast. We note that 1660 and 1740 cm⁻¹ are only 80 cm⁻¹ apart and were acquired without repositioning OAP1 between these two wavelengths, so the beam profiles are expected to be similar. However, this expectation has not been explicitly verified in the manuscript. We will address this in revision by: (1) acquiring and presenting mid-IR beam profile images at 1660 and 1740 cm⁻¹ to demonstrate their similarity, and (2) applying a flat-field correction to the individual F-MIP images before computing the ratio map, or alternatively showing that the ratio map is robust to the residual beam profile differences. We agree this is load-bearing for the biological interpretation and will strengthen the analysis accordingly. revision: yes
Referee: §3 and Table 1: The 1 mm FOV claim and 3.6× improvement lack a stated criterion. The usable quantitative FOV (tile sizes in tissue imaging) is smaller than the headline figure. Authors should state the FOV definition criterion and discuss whether the Table 1 comparison is apples-to-apples.

Authors: This is a fair and important point. In the current manuscript, the ~1 mm FOV is described qualitatively as the diameter of the circular illumination region visible in the F-MIP image (Fig. 2a), without an explicit quantitative criterion such as an SNR threshold or a percentage of peak signal. The referee correctly observes that the tile sizes used in tissue imaging (756×756 µm tiles from the ~1 mm FOV at 2920 cm⁻¹; 130×162 µm tiles from the ~220 µm FOV at 1660/1740 cm⁻¹) reflect a practically usable FOV that is smaller than the full beam diameter, because the Gaussian beam profile reduces signal toward the edges. We will revise the manuscript to: (1) state an explicit FOV criterion — we will define the FOV as the region where the F-MIP signal exceeds a stated fraction of the peak (e.g., 50% of maximum, corresponding to the FWHM of the Gaussian illumination profile), and report both this quantitative FOV and the full illumination diameter; (2) clarify in Table 1 and the main text that the comparison with prior work is based on the FOV values as reported by each group, which may use different criteria, and note this caveat explicitly; (3) discuss the distinction between the full illumination diameter and the usable quantitative FOV, particularly in the context of mosaic tiling where smaller tile sizes are chosen to avoid edge signal degradation. We agree that the current presentation could overstate the practically usable FOV relative to the headline figure, and we will make this distinction transparent. revision: yes

Circularity Check

0 steps flagged

No significant circularity; the paper is an experimental demonstration with measured benchmarks and external comparisons, not a derivation chain.

full rationale

This is an experimental optics paper, not a theoretical derivation. The central claims — ~1 mm FOV, 3.6× area improvement, pulse energies up to 360 µJ, tuning range 625–4327 cm⁻¹, first wide-field MIP below 900 cm⁻¹ — are all measured quantities compared against external benchmarks (FTIR spectra in Fig. S2, prior literature in Table 1). The F-MIP spectrum is validated against an independently measured FTIR reference. The temperature sensitivity calibration (−1.31%/°C for Fluoromax Green, Fig. S5) is an independent measurement used to convert observed fluorescence changes to temperature rise; it is not defined in terms of the target result. Self-citations (refs 13, 17, 25) are used for tissue preparation protocols and stitching algorithms — they support methodology but do not define the central quantitative claims. The FOV comparison to prior work (Table 1) uses externally published values from other groups. No equation or definition in the paper reduces to its own inputs by construction. The paper's limitations (Gaussian beam inhomogeneity, low repetition rate) are openly acknowledged and do not constitute circularity. The derivation chain is self-contained against external benchmarks.

Axiom & Free-Parameter Ledger

3 free parameters · 3 axioms · 0 invented entities

No new physical entities, particles, forces, or postulated objects are introduced. The system is built entirely from commercial components (OPO, CMOS camera, LED, objectives, mirrors).

free parameters (3)

OAP1 focal length (20 cm for large FOV, 5 cm for low-wavenumber, 15 cm for tissue) = 20 cm / 5 cm / 15 cm
Chosen manually based on FOV and spectral range requirements; not derived from a model.
Pulse energy at sample plane = ~280 µJ (high-wavenumber), ~20 µJ (fingerprint), <30 µJ (tissue)
Adjusted via laser attenuation controls for different samples and spectral regions to avoid thermal damage while maintaining signal.
Temperature sensitivity of Fluoromax Green fluorescence = -1.31%/°C
Calibrated experimentally (Fig. S5) to convert fluorescence change to temperature rise.

axioms (3)

domain assumption Fluorescence-detected MIP yields ~100× larger modulation depth than scattering-based detection.
Stated in the introduction citing refs 11-12; used to justify the F-MIP approach. Not independently verified in this paper.
domain assumption The 100 Hz repetition rate provides ample thermal relaxation time for all sample types imaged.
Based on measured decay constants of ~16.8 µs for PS beads (Fig. S6), extrapolated to larger samples. The paper acknowledges that 'for particles larger than 5 µm, the decay time would increase' but does not verify this for tissue sections.
domain assumption The 1740 cm⁻¹ signal in tuberculosis tissue reflects lipid accumulation associated with infection.
Interpreted in the tissue imaging section citing refs 26-27; the paper itself notes this signal 'may reflect contributions from both infection-associated components and endogenous lipids.'

pith-pipeline@v1.1.0-glm · 13372 in / 3136 out tokens · 195668 ms · 2026-07-08T13:05:49.144491+00:00 · methodology

discussion (0)

Reference graph

Works this paper leans on

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3D chemical imaging by fluorescence-detected mid-infrared photothermal fourier light field microscopy

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Bond-selective imaging by optically sensing the mid-infrared photothermal effect

(1) Bai, Y.; Yin, J.; Cheng, J.-X. Bond-selective imaging by optically sensing the mid-infrared photothermal effect. Science advances 2021, 7 (20), eabg1559. (2) Zhang, D.; Li, C.; Zhang, C.; Slipchenko, M. N.; Eakins, G.; Cheng, J.-X. Depth-resolved mid-infrared photothermal imaging of living cells and organisms with submicrometer spatial resolution. Sci...

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Fluorescence-detected mid-infrared photothermal microscopy

(11) Zhang, Y.; Zong, H.; Zong, C.; Tan, Y.; Zhang, M.; Zhan, Y.; Cheng, J.-X. Fluorescence-detected mid-infrared photothermal microscopy. Journal of the American Chemical Society 2021, 143 (30), 11490-11499. (12) Li, M.; Razumtcev, A.; Yang, R.; Liu, Y.; Rong, J.; Geiger, A. C.; Blanchard, R.; Pfluegl, C.; Taylor, L. S.; Simpson, G. J. Fluorescence- dete...

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work page doi:10.1021/acsomega.6c01354 2024

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3D chemical imaging by fluorescence-detected mid-infrared photothermal fourier light field microscopy

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DOI: 10.1364/OE.605038. (26) Blanc, L.; Lenaerts, A.; Dartois, V.; Prideaux, B. Visualization of mycobacterial biomarkers and tuberculosis drugs in infected tissue by MALDI-MS imaging. Analytical Chemistry 2018, 90 (10), 6275-6282. (27) Chen, Z.; Kong, X.; Ma, Q.; Chen, J.; Zeng, Y.; Liu, H.; Wang, X.; Lu, S. The impact of Mycobacterium tuberculosis on th...

work page doi:10.1364/oe.605038 2018