Improving the Way We See: Adaptive Optics Based Optical Microscopy for Deep-Tissue Imaging

Introduction

In confocal microscopy the 3D resolution is mainly achieved from the light originating from focus and not from the scattered light, a common problem associated mainly while imaging deep tissues [1–3]. Light scattering could be reduced using longer excitation wavelengths [4–6], however, it is limited to certain wavelengths. Linear (one-photon) excitation microscopy is mainly suited for near-surface (<100 μm) imaging. While non-linear (two-photon fluorescence) microscopy provides the advantage of imaging brain regions >100 μm with minimal scattering and better resolution. Deep tissue imaging at the single-cell level has provided adequate information on synaptic activity and function. Table 1 compares the with and without adaptive optics based confocal and two photon fluorescence microscopy. Conventional functional visualization neuroimaging techniques such as magnetic resonance imaging (MRI), positron emission tomography (PET), computerized tomography (CT) is currently used for imaging the human brain in vivo are usually expensive and have a poor spatial and temporal resolution [7]. The improvements in the optical approach have developed techniques that allow non-labeled imaging of tissues with high sensitivity, specificity, and spatial resolution under in vivo and in vitro conditions. Non-linear microscopy, in particular, TPF supplemented by the recent advances in optical labeling of deep tissues has become the method of choice for imaging intact tissues and live animals [4, 5, 8]. Principally, the TPF technique utilizes near-infrared wavelength and ultrashort pulses where the interaction of two photons usually of higher-order is responsible for contrast generation [9, 10]. Due to its high fluorescence intensity and depth resolution [2], TPF has drawn substantial attention for the study of deeper structures and vital functions of the brain and eye. Indeed, TPF coupled with fluorescence lifetime imaging (FLIM) has shown promising data on vitamin A metabolism in the eye to study the early onset of retinal diseases [11]. Owing to the heterogeneity of biological samples under investigation and the optical setup used, wavefront distortions limit the fluorescence signal-to-noise ratio and resolution with increasing depth [12]. AO based TPF overcomes such a loss in resolution by detecting and correcting the type of wavefront aberration generated while imaging scattering samples [13]. In the following sections, we will discuss some of the applications of AO in TPF based brain imaging.

TABLE 1

Table 1. Comparison of microscopy techniques with and without Adaptive optics.

Over the past decades, there have been great improvements in the field of ophthalmoscopy which has not only allowed scientists to successfully resolve fine retinal structures but also improved the clinical interventions for different eye diseases. This was mainly possible from the development of optical systems and recent advances in aberration correcting systems. However, when augmented with existing ophthalmoscopes such as conventional fundus imaging, SLO and spectral domain-optical coherence tomography (SD-OCT), AO enhances both structural and functional retinal imaging. First developed by David Williams and coworkers at the University of Rochester, AO-fundus imaging was used to overcome wavefront aberrations in <0.5 s and to obtain dynamic correction of fluctuations in Zernike mode [14]. SLO was first applied in the 1980s and is known to be the method of choice for clinical imaging with superior contrast and resolution. In SLO, retinal images are generated over time by measuring the scattered light as the focused beam scans across the retina surface. SLO provides enhanced image contrast mainly due to the “confocality” wherein light not originating from focus is rejected via a pinhole. Reflectance imaging is an application of SLO where the scattered light within an optically aberrated biological sample like an eye is measured. Such a technique, when used along with different wavelength lasers, could be used in clinical settings for multicolour imaging like fundus autofluorescence (FAF) [15]. Although, being routinely used in clinical imaging of the eye, contrast and depth of imaging obtained in conventional SLO methods are limited. In the later part of the review, we highlight some of the recent advances in AO based retinal imaging.

Optical imaging is the foremost important method of choice for imaging biological specimens. With the recent developments in optical methods, three-dimensional and highly resolved structures from biological samples can be achieved. One of the limitations of deep brain imaging is the scattering of light through the heterogeneous tissues, which affects the penetration depth and image resolution. The advances in the TPF microscopy techniques provide a powerful tool for overcoming scattering of light, for in vivo neuro-imaging with sub-cellular resolution, endogenous contrast specificity, pinhole less optical sectioning capability, high penetration depth, and so on. The NIR light source is usually the choice for excitation source as it avoids water absorption, thus, reducing photo-bleaching and photo-toxicity in the biological optical window, and also increases the penetration depth within the thick tissue [2, 3, 16]. Ability to image deeper brain regions with the single-cell resolution has refined the establishment of synaptic activity and its functions. The high fluorescence intensity and depth resolution assist in studying the structure and vital functions of the brain.

An optical system incorporates three major components, the laser system (pulsed), optical modalities (lenses, mirrors and objective etc.) and the specimen under investigation. Each of these components contributes toward the optical aberrations which in turn affects the imaging time and resolution. Although using aberration-corrected optical components reduce the imaging limitations when scanning deeper regions of a biological specimen, sample induced aberrations and scattering yet remains substantial. One such tool very quickly realized and implemented in optical imaging of biological samples is AO. For thick biological specimens, the optical signal strength reduces due to the aberration caused by the scattering medium (sample) and optical components used in the system [17, 18]. The ability to correct the aberration and improve the signal strength has been demonstrated using adaptive optics integrated into a wavefront sensor (WS) or sensor-less AO [19]. In the case of sensor-based AO, a WS estimates the aberration present in the imaging system and either a liquid crystal spatial light modulator (LC-SLM) or deformable membrane mirror membrane (DMM) corrects the aberration. Whereas, in sensor-less AO, the wavefront of the excitation beam is modulated and the optimal wavefront is determined through quantifying the properties of the acquired image in the form of intensity or sharpness in a feedback loop [18]. Sensorless corrections have particularly suffered from long optimization time and the introduction of fluorescent fiducial markers. In the following sections, we will briefly discuss the applications of AO in biological imaging using TPF and SLO.

Application of TPF-AO in Biological Imaging

AO in Brain Imaging

Biological information from 3D structures such as the mammalian brain has consistently intrigued scientists over decades. However, it is quite challenging to achieve higher-resolution images with optimum spatial and temporal resolution. Light from deeper regions of the brain often suffers aberration due to tissue heterogeneity or the optical setup. In recent years, scientists have successfully measured and overcome such aberrations using special optical elements, such as a deformable mirror (DM) or liquid crystal spatial light modulators (LC-SLM), along with Shack-Hartmann wavefront sensor (SH-WS) [20–22]. Wavefront distortions could be corrected directly by measuring the wavefront of the emanating signals using WS and SLM before allowing it to enter the detector [19, 23]. Direct wavefront corrections serve well for in vitro cell models or transparent samples due to an ample amount of unscattered light reaching the wavefront sensor. More recently, a multi-actuator based adaptive lens (AL) was implemented in specimens derived from wavefront corrections [24]. Comparing the image quality between SLM based multiphoton imaging and AL-based imaging, Bueno and colleagues demonstrated an alternative AO-based approach to improve two-photon deep-tissue imaging. DM and LC-SLM used for wavefront correction when combined with algorithms provide ample opportunities for scientists to obtain better images using TPF. AO based TPF is a versatile tool that not only improves the optical distortions but can improve the image quality from sparsely labeled samples at greater depths. Recently, Champelovier et al. demonstrated that AO can be applied to heterogeneously labeled cell populations such as CA1 neurons of the hippocampus to measure neuronal activity effectively. Using axial-lock modality authors were able to measure neuronal activity from hippocampal neurons that were conveniently filtered based on low or high fluorescence intensity [18]. Liu et al. investigated in vivo TPF imaging of fine dendritic structures in deep cortical layers of adult mice making use of a closed cranial window and a two-photon microscope. The full AO correction of TPF images of neurons with a yellow fluorescent protein (YFP) (Thy1-YFP SLICK A mice) was obtained at a depth of 690 and 770 μm below the pia mater in the brain. This method efficiently corrects all aberrations including that of the microscope, cover glass, and brain tissue [25]. TPF serves as a valuable tool for the analysis of neuronal structures and functions, like long term potentiation, calcium signaling pathway, microglial movement, calcium dysregulation, synaptic plasticity, etc., which can all be used to study neurodegenerative disorders such as AD. TPM supplemented with improved invasive optical tools further allows imaging in awake behaving mammals in an unprecedented manner [4, 5]. Use of high numerical aperture GRIN lens along with TPF-AO allows resolving minute synaptic structures from CA1 hippocampal neurons enabling recovery of diffraction-limited resolution. Moreover, AO based TPF enabled simultaneous calcium imaging from different hippocampal cells with a greater spatiotemporal resolution [26]. Two-photon Ca²⁺ imaging with the subcellular and temporal resolution is an important platform providing neuroscientists to visualize the cellular changes upon brain stimulation. To achieve greater resolution while imaging complex brain regions in brain slices or live mammals are challenging. Indeed, AO based TPF has been applied for Ca²⁺ imaging in live animals or fixed samples.

AO corrections have shown to improve in vivo Ca²⁺ imaging for monitoring neural activity [27]. Ca²⁺ imaging of neurons in the primary visual cortex of the mouse brain was performed without and with AO corrections (Figure 1) through a cranial window. An increase of 5-fold and 3-fold signal enhancement was observed while imaging fine structures and neuronal functionality, respectively. AO-based TPF benefits the studies of densely packed and labeled neuronal populations due to the ability to improve the signal-to-noise ratio and reduce the excitation volume at a depth. Being able to resolve brain structure and function not only by correcting wavefront distortions with AO but also shaping the excitation beam in 3D (holography) to target different neuronal populations in the intact brain is vital. Using TPF-AO based holography, Yang and Yuste developed a method wherein using SLMs to generate hologram to optically manipulate and image multiple neurons in 3D [21]. In TPF based brain imaging, sequential scanning of a laser beam across the entire sample slows down the imaging speed. This issue could be resolved by computer-generated holograms to image multiple cells at any given time. More importantly, AO can be now applied to achieve a lateral resolution which was not possible before to resolve individual rod and cone cells in the retina.

FIGURE 1

Figure 1. Adaptive optics (AO) based image correction in vivo. (A) Two photon fluorescence lateral and axial images of OGB-1 AM labeled neurons at 155 μm below the brain surface in absence of AO correction. (B) With AO correction. (C) Shows the measured aberration of excitation wavelength. (D) Fluorescence signal (black) and its percentage change (red) for four cells indicated in Figure (A) without and with AO correction. Time periods are denoted wit gray bars. Black-and-white gratings drift in eight different directions, from left to right, 0, 45, 90, 135, 180, 225, 270, and 315°. This image is adapted with permission from [27].

AO-Based Retinal Imaging

The human eye is an optical system where aberration is generated from the difference between a reference wavefront and an actual wavefront from every individual point on the pupil [28]. Since the human eye suffers from optical monochromatic aberrations, developing optical strategies to enhance the spatial resolution in retinal imaging became inevitable. Some of the early in vivo retinal imaging techniques were based on spectral and directional reflectance averaged 1–2 degrees of the retina which allowed studying structural and physiological aspects of the retina [29]. The first imaging modality developed to study retinal reflectance was the use of multi-wavelength video reflectometers [30] and scanning laser ophthalmoscopes developed by Robert Webb and coworkers [31]. Direct imaging of the retina at the cellular level (restricted only to sparsely distributed cones) was possible with a basic flood illuminated fundus camera. However, to achieve images of rods and cones with greater resolution from a broader population was only possible through AO based optical corrections. The first evidence of AO based retinal imaging came from a group in Heidelberg where SLO was previously developed [32]. Using deformable mirrors along with SLO, scientists were able to obtain much improved retinal images. Although the resolution generated by conventional SLO is hindered by the ocular aberrations, AO-SLO is the method of choice for overcoming ocular generated wavefront aberrations to enhance the imaging resolution of the mammalian eye (Figure 2). Conventional fundus imaging techniques such as fundus fluorescein angiography (FFA), optical coherence tomography (OCT) and fundus autofluorescence are insufficient in resolving fine structures like individual rods and cones or vessel and capillaries [34]. AO-SLO overcomes this limitation to resolve fine structures due to enhanced transverse resolution (~2.5 μm) while imaging the retina [35]. Studies have shown that while using a 50 μm confocal pinhole axial resolution as low as 71 μm could be achieved [36]. Moreover, the axial and lateral resolution in AO-SLO can be refined by adjusting the pinhole size of the system. Owing to its confocal nature, AO-SLO is widely used for visualizing different layers within the retina such as photoreceptors, nerve fibers, retinal pigment epithelium (RPE) [37].

FIGURE 2

Figure 2. Comparison of a conventional fundus photograph. SD-OCT cross sectional image obtained (green line) was overlaid on the fundus photograph and a montage of confocal AO-SLO images acquired (white box) was overlaid on the fundus image in the right eye of a 31 year old normal male. Magnified photoreceptor mosaic images from AO-SLO montage has been represented in colored boxes. This images has been adapted from [33] with permission.

Retinal ganglion cells are the primary cells that process visual information and conveys it to the brain. In clinical settings, loss or death of ganglion cells is the major cause of glaucoma. AO-SLO provides a crucial imaging modality thus improving retinal ganglion cell imaging both for research and clinical purposes in a non-invasive manner [35]. Split-detector is a modality used in AO-SLO to image retinal structures such as rods and cones in the living eye of the patient and healthy control [38]. Alternatively, in vivo TPF used for functional retinal imaging has turned out to be an important tool to study individual retinal cells in primates when supplemented with an AO-based ophthalmoscope. It is now evident that TPF-AO-SLO could be implemented to detect fluorescence from retinal cells of a live animal with minimal photodamage to the fundus [39]. Thus, the AO based SLO approach is now widely applied for studying and monitoring age-related macular degeneration and vascular diseases with ease (reviewed elsewhere by [40]). Pinhas et al., applied AO-SLO in combination with both oral (7 mg/mL) and intravenous (500 mg) fluorescein to investigate microvasculature in humans at different retinal depths [41]. This study, one of many shows the clinical application of AO-SLO in improved lateral resolution to resolve fine retinal capillaries (average eye focal length of ~17 mm; pupil diameter of 7.75 mm and axial resolving limit of 20 μm).

AO-based OCT on the other hand is a label-free technique that improves lateral resolution (~4 μm) of the human eye while maintaining axial resolution (~6 μm) of the OCT alone. Huang and colleagues first showed the application of OCT in optical sectioning of biological samples such as the retina, which thereafter revolutionized the ophthalmoscopy field [42]. Importantly, in AO-OCT the axial and lateral resolution are decoupled, unlike SLO. The axial resolution of OCT is theoretically limited by the coherence properties of the imaging light source. As the human eye suffers from significant longitudinal aberration, i.e., different wavelengths focus on different planes, AO provides a way out to improve lateral resolution and sensitivity of OCT [43]. Such an improvement within the optical system has been widely used in 3D-imaging of photoreceptors and other cellular components within the retina [44, 45]. Recently, a group from the School of Engineering Science in Canada implemented sensorless adaptive optics (SAO) guided by low-coherence gated OCT to improve two-photon excitation fluorescence image brightness and sharpness of mouse retina in vivo [46]. Using low-coherence guided optical plane selection, scientists were able to optimize the system in 60 s followed by TPF image acquisition at 100 ms per frame. A short optimisation protocol and improved image quality after aberration correction allowed imaging mouse retina in vivo in an unprecedented manner. Such AO based applications of optical imaging modalities are now paving their way into clinical settings to better understand the biological processes involved in disease generation and eventually improving existing therapeutic interventions.

Conclusion and Future Perspectives

The introduction of AO-based optical imaging has greatly improved deep-tissue imaging which was previously unattainable using conventional optical imaging microscopes. Since its usage in correcting atmospheric aberrations in telescopes, AO-based optical imaging has now paved its way into biological imaging. With AO, the diffraction-limited resolution could be easily achieved by correcting deep-tissue mediated aberrations. More importantly, the technology has improved the imaging quality and speed at which fine structural and functional aspects of living biological samples can be studied. The direct wavefront corrections (using SH wavefront sensors) provides a rapid and effective imaging modality compared to indirect wavefront sensing methods. Although the latter could be easily applied to any existing microscopes and is suitable for both scattering and transparent samples. Imaging deeper regions within a biological tissue have mostly been overcome by the implementation of AO based corrections. Although imaging complex neuronal populations with an AO-based optical system needs further improvements, there has been considerable improvement in retinal imaging irrespective of the differences arising from refractive index or age. Yet, imaging deeper neuronal populations with enhanced spatial-temporal resolution in a freely moving animal remain challenging. While recording neural activity in awake animals, brain movement remains a serious concern and are corrected by post image processing of 2D images. However, this approach is slow and cannot correct axial movements in a small region of interest and photostimulation. In 2016 Nadella and coworkers developed a 3D random-access two-photon laser scanning microscope using a rapid closed-loop system and acousto-optic lens (AOL). This system improves motion-mediated artifacts and monitors real-time 3D brain tissue movement at up to 1 kHz with submicrometer spatial resolution in behaving mice and zebrafish [47]. In another study, a compact AOL two-photon microscope was used for high-speed line scanning within an imaging volume at 35–50 kHz up to hundreds of micrometers. It was able to monitor cerebellar interneurons sparsely distributed neuronal activity over large depth ranges in awake animals [48].

Miniaturized fluorescence microscopes or miniscopes are becoming a key tool in neuroscience research owing to their high-resolution deep brain imaging in freely behaving animals. Owing to their lightweight, miniscopes utilizing one-photon or two-photon excitation modalities have been reported in the study of cellular activity when coupled to a freely moving animal [49, 50]. Miniscopes provides convenient in vivo deep-tissue imaging in an awake free moving animal due to, i) it's decreased footprint and weight ii) easy mounting on small animals iii) ability to record multiple neuronal activities simultaneously, thereby aiding in better understanding inter-regional signaling in behaving animal models [51].

Two-photon microscopy serves as a method of choice over conventional microscopy techniques for deep-tissue imaging. However, due to the scattering of ballistic photons from deeper samples, an optical method that could limit photon loss is necessary. TPF augmented with AO provides the advantage of limiting photon loss from deep biological samples such as the human brain [3] and eye [35]. AO-TPF has been incorporated in neurobiology and ophthalmology labs across the globe to achieve diffraction-limited contrast in biological imaging [14, 52, 53]. The use of AO-based optical imaging in ophthalmology has greatly changed the way we see the human eye both at the cellular and metabolic level. Integrating sensorless AO along with dispersion compensation of ultrashort laser pulse can improve TPF intensity of endogenous retinal fluorophores. Indeed, the use of ultrashort laser (20-fs pulse) did not show any modifications in function as well as the structure of the retina in vivo. Interestingly, the broad bandwidth of short pulses excites multiple fluorophores which provides better applications while studying cellular metabolism [11]. AO-based ophthalmoscopes also provide a platform to study several genetic diseases of the eye. AO-SLO has not only improved eye imaging but also facilitated its application in clinics for studying and monitoring retina-related conditions such as macular degeneration and Stargardt disease [54]. Above all, with the current advances in the filed of AO and TPF scientists can effortlessly image different regions within the brain or eye of a live organism which was impossible previously. With further improvements in the existing fluorescent probes, AO-based biological imaging modalities would further improve our way of seeing things in vivo.

Author Contributions

PS wrote the manuscript. NM structure the manuscript and wrote the manuscript. Both authors contributed to the article and approved the submitted version.

Funding

NM thank the Department of Science and Technology (DST), Government of India (Project Number - DST/INT/BLG/P-03/2019) for financial support. We thank Manipal School of Life Sciences (MSLS), Manipal Academy of Higher Education (MAHE), Manipal, Karnataka, India, for providing the infrastructure needed. PS thank Euro Bioimaging for the financial support.

Conflict of Interest

The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.

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