Guidestar-assisted wavefront-shaping methods for focusing light into biological tissue

Journal name:
Nature Photonics
Volume:
9,
Pages:
563–571
Year published:
DOI:
doi:10.1038/nphoton.2015.140
Received
Accepted
Published online

Abstract

In the field of biomedical optics, optical scattering has traditionally limited the range of imaging within tissue to a depth of one millimetre. A recently developed class of wavefront-shaping techniques now aims to overcome this limit and achieve diffraction-limited control of light beyond one centimetre. By manipulating the spatial profile of an optical field before it enters a scattering medium, it is possible to create a micrometre-scale focal spot deep within tissue. To successfully operate in vivo, these wavefront-shaping techniques typically require feedback from within the biological sample. This Review summarizes recently developed 'guidestar' mechanisms that provide feedback for intra-tissue focusing. Potential applications of guidestar-assisted focusing include optogenetic control over neurons, targeted photodynamic therapy and deep tissue imaging.

At a glance

Figures

  1. Principle of wavefront shaping.
    Figure 1: Principle of wavefront shaping.

    a, An unmodified coherent beam of light travels one mean free path (l) with minimal scattering into tissue. A fraction of beam directionality is preserved up to the transport mean free path length, l*. b, By wavefront-shaping the incident field with an SLM, it is possible to focus within tissue beyond l*.

  2. Matrix model of scattering in tissue.
    Figure 2: Matrix model of scattering in tissue.

    a, Forward optical scattering into tissue (distance L, input to target plane). b, Reverse optical scattering out of tissue (target to input plane). c, Transmission matrix model for forward scattering. A discrete input point source at position 3 sets ua[xa] = δ3, the third unit vector. The target field is then t3, the third transmission matrix row. d, Matrix model for scattering from an embedded guidestar point, which sets (column vector). Assuming time-reversal symmetry, the input plane field becomes 4, the fourth transmission matrix column.

  3. Feedback guidestars.
    Figure 3: Feedback guidestars.

    a, Measuring the optical transmission matrix. Rows of T are sampled by scanning one transparent pixel across an input SLM and detecting each target field. From within tissue, an external transducer obtains indirect measurements via the photo-acoustic effect. b, Compiled together, these photo-acoustic measurements form an optical transmission matrix17. c, Feedback guidestar matrix model, with measurements from one discrete location within tissue, ub[3]. d, Photo-acoustic feedback measured via an ultrasound transducer optimizes light delivery to a tight focus20. e, Fluorescence feedback, such as two-photon fluorescence (2PF). After optimization, 2PF feedback focuses light through L = 1 mm of brain tissue56. Figure reproduced with permission from: e, ref. 56, OSA.

  4. Conjugation guidestars.
    Figure 4: Conjugation guidestars.

    a, Matrix model and set-up for detecting an embedded guidestar field. Light from target field spot 3 forms the speckle field 3 at the input plane camera. b, Matrix model and set-up for conjugation guidestar focusing. SLM-shaping an incident wavefront into conjugate field refocuses to δ3. c, Fluorescent conjugation guidestar experiment (0.2 μm bead), with resulting focus and conjugate phase map15. d, Ultrasound conjugation guidestar experiments. iTRUE sharpens the conjugated spot size90 by a factor of three. TROVE reduces the focal spot width91 from 31 μm to 5 μm. e, Kinematic target conjugation guidestar experiments (TRAP/TRACK). The resulting focus enables particle counting25. Figure reproduced with permission from: c, ref. 15, AIP; e, ref. 25, OSA.

  5. Tissue motion dims an OPC focus.
    Figure 5: Tissue motion dims an OPC focus.

    a, Diagram of OPC decorrelation experiment, where wavefront shaping forms a tight focus through pinched, in vivo mouse tissue. b, Focusing light through partially immobilized dorsal skin. Both the speckle autocorrelation (g2(t), black) and OPC focal spot intensity (F(t), red) decay in magnitude over the course of several seconds, with fitted curves. c, In unconstrained skin, decorrelation occurs on a much faster (sub-second) timescale. Figure reproduced with permission from ref. 70, OSA.

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  1. Department of Electrical Engineering, California Institute of Technology, Pasadena, California 91125, USA

    • Roarke Horstmeyer,
    • Haowen Ruan &
    • Changhuei Yang

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All authors contributed equally to this work.

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