Abstract
Microscopy of biological specimens often requires low light levels to avoid damage. This yields images impaired by shot noise. An improved measurement accuracy at the Heisenberg limit can be achieved exploiting quantum correlations. If sample damage is the limiting resource, an equivalent limit can be reached by passing photons through a specimen multiple times sequentially. Here we use selfimaging cavities and employ a temporal postselection scheme to present fullfield multipass polarization and transmission micrographs with variance reductions of 4.4±0.8 dB (11.6±0.8 dB in a lossless setup) and 4.8±0.8 dB, respectively, compared with the singlepass shotnoise limit. If the accuracy is limited by the number of detected probe particles, our measurements show a variance reduction of 25.9±0.9 dB. The contrast enhancement capabilities in imaging and in diffraction studies are demonstrated with nanostructured samples and with embryonic kidney 293T cells. This approach to Heisenberglimited microscopy does not rely on quantum state engineering.
Similar content being viewed by others
Introduction
Quantum enhanced metrology allows subshot noise measurements by exploiting quantum correlations between probe particles^{1}. This has been demonstrated in microscopy in scanning configurations applying N00N states^{2,3} or squeezed light^{4}. Fullfield shadow imaging was demonstrated using entangled photons from parametric downconversion^{5}. Experimentally, these studies relied on postselection and the reduction in variance was <3.3 dB, mainly due to the difficulties in creating the necessary correlations between the photons. On the other hand, it has also been shown that, under conditions of equivalent sample damage, a single probe particle that interacts m times sequentially with the sample can be used to reach the same (Heisenberg) noise limit, and that this represents an optimal parameter estimation strategy^{6,7,8}. In this way a variance reduction of >10 dB was achieved in a phaseshift measurement^{9}. Contrast enhancement in fullfield doublepass transmission microscopy was demonstrated using a phaseconjugated mirror to pass light twice through a sample^{10}.
In the following, we generalize these techniques to fullfield multipass microscopy by placing a sample in a selfimaging cavity^{11,12,13}. The setup allows us to form an image of enhanced contrast by reimaging a pulse of light m times onto the sample. Although continuous wave cavityenhanced techniques have increased measurement resolution in various fields of science, recently, for example, at LIGO^{14} or in a scanning cavity microscope^{15}, counting the exact number of interactions allows for a precise parameter estimation and an enhanced sensitivity also for phase shifts larger than . At a constant number of photon sample interactions and employing a temporal postselection scheme, we show both retardance and transmission measurements with a sensitivity beyond the singlepass shotnoise limit, which we define as the resolution obtained in our setup using only a single pass through the sample. It is limited by the shot noise on the number of detected photons. We show micrographs of nanostructured and biological samples, as well as the signalenhancing capabilities in diffraction studies.
Results
The setup
Our setup is depicted in Fig. 1. A pulse of light (see Methods) is coupled into the cavity via the incoupling mirror M_{i}. Four lenses L_{1–4} form a microscope on either side of the sample. After the first light–sample interaction, an image is formed on the outcoupling mirror M_{o}. Most of the light is reflected back onto the sample, which is now illuminated by an image of itself. An image of enhanced contrast will then be formed on M_{i} and will again be reflected onto the sample. This process is repeated multiple times. Every time an image is formed on M_{o}, a fraction of the light is outcoupled and imaged onto a gated intensified CCD (chargecoupled device) camera. The gating time of the CCD camera is much shorter than the cavity roundtrip time (<500 ps and 2.7 ns, respectively), such that light can be postselected that interacted with the sample exactly m times.
Polarization microscopy
To demonstrate contrast enhancement and subshotnoise imaging, a wedged quartzsilica depolarizer is placed in the sample plane S. Every interaction with the quartz crystal leads to a positiondependent rotation of the polarization vector on the Poincaré sphere. For a properly cut and oriented quartz crystal (see Methods), the detected number of photons in a crosspolarized setup is expected to be , where N_{m,0}(x, y) is the number of photons detected without the polarization analyser P_{o}. η(x) is the retardance of the sample, which is proportional to the local thickness of the wedged quartz crystal. Although on a single interaction the transmitted intensity varies slowly across the field of view, more rapid signal oscillations are observed for m=3, 13 and 29 interactions (Fig. 2a). It is noteworthy that the ambiguity that arises from having m fringes instead of a single fringe can be resolved by acquiring images for different numbers of interactions.
For each image in Fig. 2a, a total number of N_{m}=∑_{x}∑_{y}N_{m}(x, y)=1.4 × 10^{6} photons were detected. Figure 2b compares the measured (left) and calculated (right) ratio ∑_{y}N_{m}(x, y)/∑_{y}N_{m,0}(x, y), where the summation is carried out in between the dashed lines in Fig. 2a. The visibility of the intensity modulation is reduced from 0.98 after 1 interaction to 0.52 after 29 interactions. As a figure of merit (FOM) for multipass microscopy, we define the reduction in variance of the retardance measurement , where Δη_{m} is the s.d. of η_{m}, which can be obtained from the measured s.d. of N_{m}(x)=∑_{y}N_{m}(x, y) via error propagation as . The FOM at is plotted in Fig. 2c (grey data points) and shows a variance reduction by 25.9±0.9 dB after 27 interactions. This is slightly lower than the theoretically expected value FOM=m^{2} (grey line, see Methods) due to residual birefringence of the optical setup, reflections and misalignment. This variance reduction has been obtained for a constant number of detected photons. It is the relevant FOM if the accuracy of a measurement is limited by a finite detection rate, for example, due to the dead time of a detector. Assuming a low loss setup, it is also the relevant FOM if the number of detected photons is limited by either the collection and detection efficiency or by the number of available probe particles.
Multipass microscopy also offers an advantage when the number of probe particle–sample interactions has to be limited due to probe particleinduced damage. Under this constant damage condition, assuming a lossless cavity and sample, a FOM=m is expected (red line, see Methods). The total number of detected photons now depends on the number of roundtrips such that the total number of interactions is independent of m. This implies an mfold damage reduction if Δη is kept constant. α_{Po,m} gives the fraction of light blocked by the polarization analyser P_{o} and is close to .The measurements (red data points) show a maximum variance reduction of 11.6±0.8 dB, which is observed after 25 interactions. It is noteworthy that under the assumption of constant damage, the measurement error for a single multipassed particle is equivalent to the error obtained in a Heisenberglimited measurement with m entangled particles and a single pass.
Photon loss due to absorption, reflection or scattering in the sample (α_{s}=1−t_{s}=0.039 per interaction) or in the cavity (α_{c}=1−t_{c}=0.189 per interaction) reduce the efficiency of multipass microscopy, as only a total number of photons will be detected for operation at constant damage. Here, t=t_{c}t_{s}=1−α and m_{α}<m is the mean number of interactions of a photon with the sample before it is either lost or the mth interaction is reached (see Methods). Taking this into account, a maximum variance reduction of 4.4±0.8 dB after three interactions is observed (blue data). This could be improved significantly in an optimized setup, as the losses in the cavity optics are mainly due to the finite reflectivity of the in and outcoupling mirror, which, for this proofofprinciple experiment, were chosen to outcouple a considerable fraction of the beam intensity after every interaction.
Transmission measurements and diffraction studies
Transmission measurements can also benefit from multipassing as long as the total losses due to the sample and the cavity are small (see Methods). Measuring the optical density of a spatially homogeneous sample shows signal amplification and a variance reduction by 4.8±0.8 dB (Fig. 3a, again at constant damage). Owing to the photon losses in the sample and in the cavity no further decrease in variance is observed when the number of interactions is increased to beyond 7.
The imaging and contrastenhancement capabilities of the setup are further exemplified with microfabricated grating structures and with embryonic kidney 293T cells. Figure 3b shows multipass (m=1, 3, 5) micrographs of a hexagonal hole pattern in a carbon membrane. The resolution of the microscope is ∼5 μm due to the finite numerical aperture of the employed lenses (f=50 mm). The photon loss due to the carbon membrane is amplified by multiple passes, which leads to a significant contrast enhancement. This also becomes apparent in the images shown in Fig. 3c, which were taken in the Fourier plane of the imaging optics. Although the single pass image is dominated by the diffraction pattern caused by the foursided copper support structure of the carbon membrane, the hexagonal symmetry of the holes in the membrane becomes clearly visible after multiple interactions. In addition, for embryonic kidney 293T cells a clear contrast enhancement is observed (Fig. 3d). Although cells and other phase objects are hardly visible in single pass brightfield microscopy, the outline of single cells becomes clearly visible in multipass microscopy images. Both absorption and phase shifts need to be taken into account in the analysis of such images and future highresolution multipass microscopy studies will aim at exploring fine details in the interior of cells.
Discussion
Multipass microscopy is a technique for signal amplification and allows for optimal parameter estimation in the presence of noise sources that are not significantly amplified by multipassing (such as shot noise or read noise). For the images acquired at constant damage, the technique presented above relies on temporal postselection of a few percent of the light that interacted with the sample. Although this degree of postselection is orders of magnitude less stringent than the postselection required in comparable N00Nstate microscopy experiments, we note that there are at least two technologically feasible ways of overcoming this need for postselection: on the one hand, an optical switch could be incorporated into the cavity, which would allow for outcoupling all light at once. This could be achieved using a Pockels cell and a polarizing beam splitter. On the other hand, even without an outcoupling switch a metrological advantage can be gained, if a detector is used that records the detection time, and thus the number of interactions, of each individual photon.
Postselection free multipass microscopy will benefit applications that are sensitive to photoinduced damage, such as livecell microscopy^{16}, the labelfree detection of single proteins^{17}, the detection of single molecules via their absorption^{18} or low damage imaging of exotic quantum states of matter^{19}. Apart from increasing the detectability of such weak signals^{17,18}, an improved signaltonoise ratio would also lead to better spatial accuracy in superresolution techniques that rely on these weak signals. Increased accuracy is also obtained if a measurement is limited by the number of detectable particles, for example, at wavelengths where there are no highintensity light sources, or also in measurements that involve massive particles as probe particles (electron or ion microscopy, measurements involving antimatter). Multipass electron microscopy especially seems worth considering, as sample damage limits the spatial resolution achieved in imaging biological specimens^{20,21}.
Methods
Experimental setup
Two different laser systems were used for the experiments:
For the data in Fig. 3, a titanium sapphire laser was used (Venteon, 10 fs pulse width, 5 nJ per pulse, 100 MHz repetition rate, spectrally centred at λ=780 nm). The pulses are spectrally filtered (Semrock LL0181012.5) to reduce the effect of chromatic aberrations in the selfimaging cavity. This inevitably broadens the temporal width of the pulses; however, the pulses are still short compared with the cavity round trip time. A resonantly driven electrooptic modulator is used to reduce the laser repetition rate to 50 MHz with an extinction ratio of about 16 dB.
A lower repetition rate laser was required for the data in Fig. 2, to allow for more interactions before the advent of the consecutive laser pulse. The laser diode (783 nm) was driven with fast voltage pulses. Pulse widths <1 ns at a peak power of about 100 mW were achieved. The repetition rate was controlled using a direct digital synthesizer (Novatech 409B) and set to 25 MHz.
The alignment of the selfimaging cavity is done element by element (starting from the outcoupling mirror) by maximizing the light that is backreflected into the single mode fibre.
Jones matrix representation of quartzsilica depolarizer
The quartzsilica depolarizer consists of a wedged plate of optical quartz cemented to a wedged plate of synthetic fused silica (OptoSigma DEQ 2S). The quartz crystal is cut and oriented such that it has the fast axis at a 45° angle with respect to the polarization of the incoming beam. The fused silica wedge has negligible birefringence and prevents beam deviation. The Jones matrix of the quartz crystal can be written as , where η is the phase retardance due to the birefringence of the crystal. The retardance is proportional to the thickness of the crystal, which varies spatially, as the crystal is cut with a wedge angle of β∼2°: η∼βΔxΔn/λ, where Δn∼0.009 is the difference in index of refraction of light polarized along the fast or slow axis of the crystal. In the experiment horizontally polarized light enters the multipass microscope (I_{0}=E_{0}^{2} is the intensity of the incoming light), interacts with the quartz crystal m times and is finally projected onto the vertical polarization axis and detected. This can be written as .
Measurement error in retardance measurements
The error in retardance measurements is obtained from error propagation as . For a constant number of detected particles the s.d. is independent of m, whereas the slope increases linearly with m. This leads to a , which scales with the square of the number of roundtrips. If the number of probe particle–sample interactions is to be kept constant, for a lossless setup and sample, and . The slope would still increase linearly with m, leading to a . For , the setup could be adapted to reach optimal sensitivity^{3}.
Measurement error in absorption measurements
Assume N_{0,m} photons are used to probe the transmission of a sample. After m interactions, all photons are outcoupled from the cavity and detected with a photon counting detector. Without the sample, photons will be detected. Uncorrelated repetitions of the measurement of N_{wo} will give a s.d. of . With a partially absorptive sample in the setup, photons will be detected with a s.d. of . It follows that and error propagation yields a s.d. of the measured sample transmission of . We are interested in the s.d. as a function of m at constant damage. This implies that the number of incoupled photons N_{0,m} will be a function of m, such that the number of absorbed photons D_{m} is independent of m. For a symmetric setup, in which the cavity losses are the same on both sides of the sample, we get and D_{m}=D_{1} yields and
For mα<<1, this yields a FOM of multipass absorption microscopy that scales linearly with m, just as it did for the retardance measurements.
When studying living samples, it might be more important to look at the damage reduction at constant s.d. (Δt_{s,1}=Δt_{s,m}, but D_{m}≠D_{1}), which yields
and scales with m for mα<<1.
Image acquisition and noise analysis
To assess the singlepass shotnoise limit, the spatially resolved photon counting capabilities of the ICCD camera are exploited. it is noteworthy that they are not required to benefit from multipass microscopy.
For the retardance measurements in Fig. 2, the exposure is chosen such that ∼140 photons are detected per image. There are fewer than one dark counts per image. For each value of m, 10,000 images were acquired. This total data set, containing roughly 1.4 × 10^{6} detected photons, is divided into N_{p}=100 images, each of them containing N_{m} photons, with N_{1}=1.4 × 10^{4}, which were randomly picked without replacement. For each of these N_{p} images, the , where , is calculated and plotted in Fig. 2c. For this calculation, the slope is obtained from a sinusoidal fit to the sum of all N_{p} images. The above equation can be rewritten as and, as the images are independent of each other, . This allows us to calculate^{22} the s.d. of the variance as , with μ_{2} and μ_{4} being the second and fourth central moment of the distribution of values . The s.d. of the is then obtained from propagating the errors in (Δη_{m})^{2} and (Δη_{1})^{2}.
The equations for the calculation of N_{m} that are given in the main text assume a symmetric setup, with equal loss α_{c} on both sides of the sample plane. For the data and theory shown in Fig. 2, the asymmetry due to the unequal reflectance of M_{i} and M_{o} is taken into account when calculating N_{m} and m_{α}. With α_{i}=1−t_{i} and α_{o}=1−t_{o} being the total losses on the incoupling and outcoupling side of the sample, respectively, we get and , respectively. As the images in Fig. 2 are centred at , the ratio , with a maximum measured deviation of 0.04. For the theoretical curves in Fig. 2c, was assumed for even numbers of interactions, for which α_{Po,m} could not be determined experimentally.
For the optical density measurements in Fig. 3 the process is similar. At m=1, 100 images are recorded, each with a total integration time τ_{1}. For m>1, the integration time is τ_{m}=τ_{1}/m_{α} to operate at constant damage. For each image, the total number of detected photons is integrated. The process is repeated without the sample and the transmission and its variance are calculated. The error bars in Fig. 3 corresponds to the s.d. of the FOM as obtained from error propagation. For the theory curve, the asymmetry of the setup is again taken into account, which can result in kinks in the FOM between odd and even interaction numbers.
Data availability
The data that support the findings of this study are available from the corresponding author upon request.
Additional information
How to cite this article: Juffmann, T. et al. Multipass microscopy. Nat. Commun. 7:12858 doi: 10.1038/ncomms12858 (2016).
References
Giovannetti, V., Lloyd, S. & Maccone, L. Quantumenhanced measurements: beating the standard quantum limit. Science 306, 1330–1336 (2004).
Israel, Y., Rosen, S. & Silberberg, Y. Supersensitive polarization microscopy using NOON states of light. Phys. Rev. Lett. 112, 103604 (2014).
Ono, T., Okamoto, R. & Takeuchi, S. An entanglementenhanced microscope. Nat. Commun. 4, 2426 (2013).
Taylor, M. A. et al. Biological measurement beyond the quantum limit. Nat. Photonics 7, 229–233 (2013).
Brida, G., Genovese, M. & Ruo Berchera, I. Experimental realization of subshotnoise quantum imaging. Nat. Photonics 4, 227–230 (2010).
Giovannetti, V., Lloyd, S. & Maccone, L. Advances in quantum metrology. Nat. Photonics 5, 222–229 (2011).
Giovannetti, V., Lloyd, S. & Maccone, L. Quantum metrology. Phys. Rev. Lett. 96, 010401 (2006).
Luis, A. Phaseshift amplification for precision measurements without nonclassical states. Phys. Rev. A 65, 025802 (2002).
Higgins, B. L., Berry, D. W., Bartlett, S. D., Wiseman, H. M. & Pryde, G. J. Entanglementfree Heisenberglimited phase estimation. Nature 450, 393–396 (2007).
Pégard, N. C. & Fleischer, J. W. in CLEO:2011Laser Applications to Photonic Applications CThW6 Optical Society of America.
Arnaud, J. A. Degenerate optical cavities. Appl. Opt. 8, 189–196 (1969).
Kolobov, M. I. Quantum Imaging Springer: New York, USA, (2007).
Gigan, S., Lopez, L., Treps, N., Maître, A. & Fabre, C. Image transmission through a stable paraxial cavity. Phys. Rev. A 72, 023804 (2005).
Collaboration, L. S. et al. Observation of gravitational waves from a binary black hole merger. Phys. Rev. Lett. 116, 061102 (2016).
Mader, M., Reichel, J., Hänsch, T. W. & Hunger, D. A scanning cavity microscope. Nat. Commun. 6, 7249 (2015).
Frigault, M. M., Lacoste, J., Swift, J. L. & Brown, C. M. Livecell microscopy—tips and tools. J. Cell Sci. 122, 753–767 (2009).
Piliarik, M. & Sandoghdar, V. Direct optical sensing of single unlabelled proteins and superresolution imaging of their binding sites. Nat. Commun. 5, 4495 (2014).
Celebrano, M., Kukura, P., Renn, A. & Sandoghdar, V. Singlemolecule imaging by optical absorption. Nat. Photonics 5, 95–98 (2011).
Andrews, M. R. et al. Direct, nondestructive observation of a bose condensate. Science 273, 84–87 (1996).
Egerton, R. F. Choice of operating voltage for a transmission electron microscope. Ultramicroscopy 145, 85–93 (2014).
Glaeser, R. M. How good can cryoEM become? Nat. Methods 13, 28–32 (2016).
Kenney, J. F. in Mathematics of statistics ed. Keeping E. S. Van Nostrand: New York, USA, (1947).
Acknowledgements
We thank Gernot Neumayer for the preparation of the cell sample. P.H. thanks the Austrian Science Fund (FWF): J3680. This research is funded by the Gordon and Betty Moore Foundation, and by work supported under the Stanford Graduate Fellowship.
Author information
Authors and Affiliations
Contributions
T.J., B.K., P.H. and M.K. conceived the experiment. B.K. and T.J. carried out the experiment. B.K., T.J. and M.K. analysed the data and prepared the manuscript. T.F. analysed alignment constraints for the setup.
Corresponding author
Ethics declarations
Competing interests
The authors declare no competing financial interests.
Rights and permissions
This work is licensed under a Creative Commons Attribution 4.0 International License. The images or other third party material in this article are included in the article’s Creative Commons license, unless indicated otherwise in the credit line; if the material is not included under the Creative Commons license, users will need to obtain permission from the license holder to reproduce the material. To view a copy of this license, visit http://creativecommons.org/licenses/by/4.0/
About this article
Cite this article
Juffmann, T., Klopfer, B., Frankort, T. et al. Multipass microscopy. Nat Commun 7, 12858 (2016). https://doi.org/10.1038/ncomms12858
Received:
Accepted:
Published:
DOI: https://doi.org/10.1038/ncomms12858
This article is cited by

Distributed quantum phase estimation with entangled photons
Nature Photonics (2021)

Electrooptic imaging enables efficient widefield fluorescence lifetime microscopy
Nature Communications (2019)

Super sensitivity and super resolution with quantum teleportation
npj Quantum Information (2019)

Fullfield interferometric imaging of propagating action potentials
Light: Science & Applications (2018)

Multipass transmission electron microscopy
Scientific Reports (2017)
Comments
By submitting a comment you agree to abide by our Terms and Community Guidelines. If you find something abusive or that does not comply with our terms or guidelines please flag it as inappropriate.