Scanning laser ophthalmoscopy was invented about 3 decades ago by Webb.1 Its basic principles of operation are the same as the scanning laser microscope, which was invented in 1955 by Minsky,2 the only difference being that, in the ophthalmoscope, the eye's optics serve as the objective and the retina is always the sample. The scanning laser ophthalmoscope (SLO) was a major development in ophthalmoscopy in the 20th century and SLOs now form the basis for many commercially available ophthalmoscopes (e.g., Optos PLC, Dumfermline, Scotland, UK; Heidelberg Engineering, Heidelberg, Germany; Carl Zeiss Meditec, Dublin, CA).
How Does an SLO Work?
Like a scanning laser microscope, the image in an SLO is generated over time by recording the scattered light from a focused spot as it is raster scanned across the region to be imaged. As such, it does not collect an image using a film or a CCD array. Rather, the intensity of each pixel is recorded using a single, light sensitive detector, and the location of each pixel is inferred by outputs from the scanning mirrors. Typically, this information is combined by computer or frame grabber that is used to render the final image.
What are the Limits of SLO?
Manufactured optical systems do not come close to matching the performance of the eye and visual system. But in terms of optical quality, the eye operates at a fraction of its potential. Irregularities in the corneal and lens surfaces as well as misalignments and relative tilts between the components generate aberrations that cannot be corrected by conventional methods. Like any ophthalmoscope, these imperfections impose limits on the highest resolution that can be achieved in an SLO. Most conventional SLO applications are not seriously limited by aberrations, however, as their resolution demands have traditionally not been high. But with improved resolution, the scope of applications for SLO can be expanded greatly, as I hope to demonstrate in this article.
Putting the AO into AOSLO
The first attempt to use Adaptive optics (AO) in an SLO was made by Dreher et al. in 1989.3 At that time, a key component of an AO system, the wavefront sensor, was not used, and the AO system was capable only of correcting defocus and astigmatism. As such, the concept was laid out, but the improvements in image quality were modest. A short time later, out of the same laboratory, Liang et al.4 demonstrated for the first time a Shack Hartmann wavefront sensor for the eye. With such a device, which could measure the eye's aberrations quickly and accurately, all the pieces were finally in place. In 1996, David Williams at the University of Rochester assembled a team including Junzhong Liang and Donald Miller (PhD student at the time), who built the first AO ophthalmoscope, capable of correcting higher order aberrations.5 The system used a conventional imaging modality, using a flash lamp to illuminate the retina and a science grade CCD camera to record the image.
Extensive descriptions can be found in the literature on how an AO system works in general,6 or specifically for vision applications.7,8 In brief, an AO system uses a wavefront sensor to measure the eye's aberrations and a wavefront corrector to compensate for them. In most working instruments, the wavefront sensor and the wavefront corrector are a Shack Hartmann sensor and a deformable mirror (DM), respectively.
A schematic showing the details on how AO is implemented in AOSLO is shown on Fig. 1. But before explaining the actual system, it's worth first discussing how resolution is mediated in AOSLO. In an SLO, a light beam focuses to illuminate a small region of the retina. The light scatters from the illuminated region back out of the eye, passes through the system, and is sensed by the detector, yielding the intensity value (or pixel value) for that location. It follows that the resolution is governed, in part, by the size of the illuminated spot on the retina.
As shown in Fig. 1, there is a long train of elements between the eye and the light delivery and detection arms of the system. The light beam entering the system reflects off the DM and two scanning mirrors before entering the eye. The returning light passes through the same scanning mirrors and DM before reaching the detector. By virtue of the reversibility of light, this returning light is “descanned” before its arrival at the detector so that, even though the beam may be scanning across the retina, it is rendered stationary by the time it reaches the detector. This feature allows for placement of a key component, the confocal pinhole, before the detector in a plane that is conjugate to the focused spot on the retina. The confocality of SLO allows for optical sectioning. The basic concept of optical sectioning is illustrated in Fig. 2, which shows how only the light returning from the plane of focus can pass through the pinhole and reach the detector. Most of the light from other layers gets blocked.
The Role of AO
As mentioned at the beginning of this section, resolution is achieved, in part, by making the illuminated spot small. The lateral and axial resolution is improved further by making the confocal pinhole small, but that is only realizable if the light from the retina that is re-imaged onto the confocal pinhole plane is compact, otherwise very little light will make it to the detector. In fact, it is the double pass point spread function (PSF) that reaches the confocal pinhole9 and the more compact it is, the better the axial and lateral resolution. So, AO is used in both directions; to make the focused light on the retina more compact, and to reimage the returning light back onto the confocal pinhole. The resolution of the confocal SLO is given by:
where PSFin and PSFout are the point spread functions in and out of the eye, respectively, and D (x,y) represents the confocal pinhole and ⊗ represents the convolution operator. If the pinhole is tiny, then the PSF is simply the product of the ingoing and outgoing PSF, making the PSF smaller than the diffraction limit! When the confocal pinhole is optimized, the lateral and axial resolutions for a 6 mm pupil and 600 nm light are 1.9 and 33 μm, respectively. With larger pupils or shorter wavelengths, the resolution improves further.
The scanning/descanning feature of SLO allows for unique implementation of wavefront sensing. Fig. 1 shows how the returning light is divided between the detector and the wavefront sensor. The beam is stationary at this point, so although the beam scans an extended field, the wavefront sensor sees the light as though it is coming from a single direction. As such, any wavefront sensor exposure that is longer than one frame period will average the wavefront over the field. This does not improve the fidelity of the wavefront measurement (the wave aberration is nearly anisoplanatic over a typical imaged field) but it does offer the following advantages:
- Scanning the beam during the integration time of the wavefront sensor exposure improves the fidelity of the wavefront measurement by eliminating speckle and retinal feature artifacts from the wavefront sensor image.
- Because a large aperture beam is corrected on the entry path, the improvement in focus offered by AO renders the Shack Hartmann spots sharper once the AO system has closed the loop.
- Using the same light source for wavefront sensing and imaging, obviates the need to compensate for chromatic aberration.
The principle of reversibility of light mean that the single wavefront measurement can be used to correct the aberration in both directions—to sharpen the focused spot on the retina as well as to sharpen the image of that focused spot on the confocal pinhole in the return path.
Advantages of AOSLO
Since our original 2002 article,10 many of the stated advantages of the AOSLO imaging modality have been realized by our laboratory as well as others. The remainder of this article will demonstrate these advantages through a series of examples.
High Resolution Imaging
The obvious and direct outcome of using AO in an ophthalmoscope is retinal images and video with high lateral resolution. This benefit is common to all ophthalmoscopic imaging modalities. There are limits on the light that can be used to record a single image, so the highest signal to noise images are often obtained by averaging multiple images from the same location. But averaging multiple frames in AOSLO is not straightforward. The scanning nature of the system means that each pixel and each line is obtained in sequence. At 30 fps, each frame takes about 30 ms to acquire. During that time the eye will move by significant amounts in unpredictable directions. As a result, each frame is distorted by the unique eye motions that transpired during its acquisition, not unlike the distortions you see when a page that is being scanned or photocopied is moved. With some effort, these distortions can be corrected, after which multiple frames can be added.11,12 Fig. 3 shows a sequence of images of a photoreceptor mosaic that illustrates the motion correction procedure as well as the final product. (Also see Supplemental Digital Content 1, http://links.lww.com/OPX/A20, which shows the raw AOSLO movie with typical fixational eye movements used to generate the images in Fig. 3 and Supplemental Digital Content 2, http://links.lww.com/OPX/A21, which shows a stabilized version of the same movie.) The contrast of AOSLO images is high for two reasons. First, the illuminated spot on the retina is small. Second, the confocal aperture blocks out of focus light from other layers that would otherwise reduce the contrast of the image. The upcoming section titled Confocal Sectioning describes other benefits of the confocal pinhole.
Using the Stabilized Movies to Generate Retinal Perfusion Maps
The stabilized video itself offers additional benefits. As can be seen from the example movie, blood flow is visible in the AO-corrected retinal video. With well stabilized movies, we can extract the part of the field where the motion is highest, revealing the capillary network.13 This is done by looking at the variance of each pixel in a processed version of the stabilized video. Static features like photoreceptors vary little, while scattering changes by flowing blood cells change a lot. The resultant motion-contrast image reveals the entire network of retinal capillaries. These images rival some of the best fluorescein angiographic measures and are done noninvasively.
The confocal pinhole is typically aligned to be conjugate to the focused spot on the retina (i.e., an object at the focused spot will be imaged at the confocal pinhole and vice versa). Moreover, the conjugacy is maintained, even if the focused spot is adjusted axially on the retina, provided that the focus is adjusted by an element (or elements) in the double pass part of the optical path (Fig. 1). In the AOSLO, such a change in focus can be made by the DM. These focal changes allow one to image different layers of the retina as shown in Fig. 4. (Also see Supplemental Digital Content 3, http://links.lww.com/OPX/A22, which is a movie showing the entire through focus video sequence that was used to generate the images in Fig. 4).
A byproduct of solving the problem of image distortion caused by eye motion is that the eye can be tracked with an accuracy and at a frequency that is unrivaled by the best eye tracking systems available today. In a sense, the distortions that appear in each image are a chart record of the motion that has occurred during its acquisition. Owing to the high resolution of the image, the correction can be very accurate, yielding local eye position estimates that are a fraction of the size of a cone photoreceptor. The frequency of the tracking is limited only by the number of eye position estimates that are made within each frame. In our laboratory, we frequently use 30 estimates per frame to give eye traces close to 1 kHz.
However, the full recovery of eye motion from AOSLO videos is still a work in progress, as the correction for the distortion in the reference frame as well as eye torsion remain issues that need to be dealt with fully. Nevertheless, Fig. 5 shows an estimate obtained from a 20-s AOSLO video (Supplemental Digital Content 4, http://links.lww.com/OPX/A23, shows the original movie from which the eye motion traces were computed).
Laser Modulation for Stimulus Delivery
The possibility of modulating the scanning laser in an SLO to project an image directly on the retina was appreciated since the time of its invention.1 In addition, the exact position of the modulation could be encoded directly into the video, because in many cases, it was the imaging laser that was modulated to generate the image. Implementing this feature in AOSLO therefore, was not new, but the scope of applications of this feature was expanded considerably by being able to deliver AO-corrected stimuli over small regions of the retina. Such stimuli can be localized on the scale of cone photoreceptors.14 The following sections describe applications involving laser modulation and stimulus delivery.
The AOSLO can project aberration- corrected beams directly onto the retina. As such, it can be used to test improvement in visual acuity with aberration correction. We completed a study where we compared AO-corrected acuity in emmetropes and low-to-moderate myopes and found that myopes do not perform as well after AO-correction.15 Was the deficit because the cone spacing in myopes is larger, imposing a retinal limit to vision?16 At that time, we were unable to measure the cone spacing in each subject, because the task was done at the foveal center. However, with improvements to our AO control system, we are now able to resolve cones very close to the foveal center. In a recent study examining cone spacing and axial length, we reported that there was no correlation between axial length and cone spacing near the foveal center.17 If fact, axial myopes are more likely to have more cones sampling the retinal image than emmetropes. So, we are left to conclude that the myope's diminished acuity for AO-corrected images has to be postreceptoral.
Fixation Tracking and Apparent Motion.
The nature of the stimulus that can be delivered is only limited by the technology in the AOSLO system. In our system, we can deliver animations, gray scale images, and even stabilized images (more on that later). The animated stimulus has been used for experiments on fixation tracking and apparent motion detection. In the former experiment, we asked what part of the retina was used to place the image of moving objects that were being tracked as opposed to stationary objects that were being fixated. The moving and the stationary fixation targets were generated by modulating the raster-scanning laser. Surprisingly, the loci of each were different and neither was necessarily located at the point of maximum cone density.18 In the latter experiment, we studied the eye's ability to correctly judge apparent motion (moving of a fixed object to a new location between frames, like a motion picture) in the presence of continuous eye movements. Our interests in the eye's ability to judge motion stems from the fact that the motion of objects on the retina is the difference between the motion of the eye's line of sight and the actual motion of the object in the world. In some cases, eye motion might cause objects moving in a certain direction in the world to move in an inconsistent direction on the retina. By using the stimulus delivery feature of the AOSLO, we presented a series of frames to our subjects where a stimulus pattern was shifted between two frames in an upward or downward direction within the raster. We found that when given a frame of reference, the eye manages to judge correctly how objects move in the world, even when eye movements had generated a confounding retinal motion. When the frame of reference is removed (i.e., the eye is looking at a moving object in the absence of any other visual cues) the eye still retains some of this ability, suggesting that visual system uses some non-visual cues to know which way its eyes are pointing (Fig. 6).19
Multichannel Imaging and/or Stimulus Delivery
Like a scanning laser microscope, the AOSLO can be equipped with multiple sources.20 This feature is used for a multitude of applications, which will be described below.
In this application, an infrared channel is used to image the retina while a visible light channel is used to stimulate a patch of the same field. When the photoreceptors are stimulated, many changes will occur; photopigment molecules will be photoisomerized, ions will be transported in and out of the photoreceptor cells and other retinal neurons, and choroidal and retinal blood flow will be redirected. Any or all of the changes may cause changes in the scattering of infrared light. The location, time course, and magnitude of the scattering changes in response to visible light stimulation will encode details of these changes, much like the electroretinogram encodes the electrical changes in the retina. As such, monitoring these changes holds promise to be an effective non-invasive way to measure retinal function. To date, several groups have made these recordings without AO modalities.21–23 Performing measures of this type with AOSLO allows for good optical sectioning and high lateral resolution to localize the changes, but much more work has to be done before this to validate intrinsic signals as a clinical or basic science tool.24
Although it is not a strict requirement, the use of multiple imaging wavelengths has facilitated some very innovative fluorescence imaging in the retina of human and animal eyes. In cases where the fluorescence signal is very weak (e.g., autofluorescence from retinal pigmented epithelium cells), a simultaneous infrared reflectance video is crucial to provide eye motion correction for registration of multiple frames. In fact, simultaneous acquisition of a high signal to noise reflectance video allows for collecting and integrating any weak retinal signal, whether it is autofluorescence, phase contrast, two-photon, or any of the multitude of imaging techniques in the microscopist's arsenal that generate useful, but weak signals. To date, the only fluorescent imaging results are coming from the University of Rochester. Fig. 7 shows two results, one from fluorescent agents injected into ganglion cells25,26 and a second where the autofluorescence of lipofuscin was used to reveal the cellular structure of the retinal pigment epithelial cells.27
Stabilized Stimulus Delivery for Sensitivity Mapping and Electrophysiology
In collaboration with a group at Montana State University, we have sped up our eye tracking algorithms so that they can operate in real-time. Moreover, combining realtime eye tracking with the multiwavelength operation and stimulus delivery, we have used the real-time tracking information from an infrared video to place a visible light stimulus at a targeted retinal location. This technology has the potential for careful microperimetry on the scale of single cones or could even be used for targeting therapeutic laser delivery to the retina. While a laboratory has yet to demonstrate either of the aforementioned applications, we describe two unique applications below.
Local Measurements of Retinal Sensitivity.
The retina is tiled with three classes of cone, sensitive to long (L), medium (M), and short (S) wavelengths. As such, we would expect that the sensitivity of the retina to a small spot of a specific wavelength should vary according to the cone type that it is stimulating. In a pilot experiment, we performed local sensitivity tests on a region of a retina whose cones had been previously characterized.28 The wavelength of the imaging light was 840 nm, which provided a dim red background (∼40 Td) and the stimulating wavelength was 680 nm. We measured sensitivity of a small patch of retina comprising about 200 cones. As expected, the variations in sensitivity correlated with the three cone types on the retina. However, the correlation was worse than expected because it proved difficult to control the transverse chromatic aberration (TCA) during the course of the experiment (TCA will change as the beam location in the pupil changes20).
Combining Stimulus Delivery and Electrophysiology.
Under the right imaging conditions, the ability to monitor the transverse aberration between the imaging and the stimulus beam is much improved. In an experiment done in collaboration with Lawrence Sincich and Jonathan Horton at UC San Francisco, we tracked and stimulated individual cones while recording activity of associated neurons in the lateral geniculate nucleus (LGN) of a macaque. Although neuroscientists have been measuring from single cells for decades, this represents the first time that single photoreceptors have been optically stimulated on the input end. Before this demonstration, control of the stimulation in these experiments has always been hampered by either eye motion or optical blur, and most often both. Our experiments revealed that receptive field centers of LGN neurons close to the foveal center are comprised of multiple cones.29 Fig. 8 shows the result of one of the measurements (see Supplemental Digital Content 5, http://links.lww.com/OPX/A24, for a stabilized video from the receptive field shown in Fig. 8). Future experiments promise to reveal the trichromatic inputs to LGN receptive field centers in the fovea.
AOSLO has many potential applications but there are drawbacks as well. Some of the challenges may be overcome as new technology comes available, whereas others are more fundamental.
Since a point source is imaged onto the retina, it will have some coherence, even if it comes from a low coherent light source. The coherence of the source gives rise to speckle and interference artifacts. These will only be overcome with broader band light sources or by using techniques to vary the phase between adjacent cones. Overcoming the interference from the light source is one aspect of ongoing research in our laboratory.
The SLO relies on detecting the magnitude of scattered or fluorescent light to determine intensity. Many of the sources of retinal scatter and fluorescence are very weak and so signal:noise for many retinal features are often too low for visualization. Interference-based detection methods, such as those used in optical coherence tomography systems, have proven to be vastly more sensitive and reveal some of the dimmest retinal structures. Fortunately, interference-based detection techniques can be implemented in SLO systems and some early results are being demonstrated.30
AOSLO imaging is inefficient in the sense that the data is collected serially. Images are constructed pixel-by-pixel and optical section by optical section. Spectral domain optical coherence tomography systems, by comparison, acquire an entire axial scan at once and so a volume is generate in a single raster scan. In defense of the AOSLO, high frequency scanners and fast detectors make the pixel rates very high, but there is much room for improvement. The AO line scanning ophthalmoscope represents an example of how one can make the system much more efficient, with moderate compromises in resolution.31
This article is intended to show the advantages and applications of AOSLO for basic and clinical science. As imaging and AOs technology advances, systems will become more robust and more common, and new advances and discoveries will be inevitable.
I thank all those who contributed directly to the work presented in this paper. David Arathorn, Dan Gray, Kate Grieve, Jonathan Horton, Girish Kumar, Kaccie Li, Jessica Morgan, Ethan Rossi, Lawrence Sincich, Scott Stevenson, Johnny Tam, Curt Vogel, David Williams, and Qiang Yang.
SUPPLEMENTAL DIGITAL CONTENT (SDC)
Movie 1: http://links.lww.com/OPX/A20
Movie 2: http://links.lww.com/OPX/A21
Movie 3: http://links.lww.com/OPX/A22
Movie 4: http://links.lww.com/OPX/A23
Movie 5: http://links.lww.com/OPX/A24
School of Optometry
University of California-Berkeley
Berkeley, California 94720-2020
1.Webb RH, Hughes GW, Pomerantzeff O. Flying spot TV ophthalmoscope. Appl Opt 1980;19:2991–7.
2.Minsky M. Memoir on inventing the confocal scanning laser microscope. Scanning 1988;10:128–38.
3.Dreher AW, Bille JF, Weinreb RN. Active optical depth resolution improvement of the laser tomographic scanner. Appl Opt 1989;28:804–8.
4.Liang J, Grimm B, Goelz S, Bille JF. Objective measurement of wave aberrations of the human eye with the use of a Hartmann-Shack wave-front sensor. J Opt Soc Am (A) 1994;11:1949–57.
5.Liang J, Williams DR, Miller DT. Supernormal vision and high-resolution retinal imaging through adaptive optics
. J Opt Soc Am (A) 1997;14:2884–92.
6.Tyson RK. Principles of Adaptive Optics
, 2nd ed. Boston, MA: Academic Press; 1998.
7.Porter J, ed. Adaptive Optics
for Vision Science: Principles, Practices, Design, and Applications. Hoboken, NJ: Wiley-Interscience; 2006.
8.Miller DT, Roorda A. Adaptive optics
in retinal microscopy and vision. In: Bass M, ed. Handbook of Optics, 3rd ed. Vol III. Rochester, NY: Optical Society of America; 2009:Chapter 17.
9.Artal P, Marcos S, Navarro R, Williams DR. Odd aberrations and double-pass measurements of retinal image quality. J Opt Soc Am (A) 1995;12:195–201.
10.Roorda A, Romero-Borja F, Donnelly III W, Queener H, Hebert T, Campbell MCW. Adaptive optics scanning laser ophthalmoscopy
. Opt Express 2002;10:405–12.
11.Stevenson SB, Roorda A. Correcting for miniature eye movements in high resolution scanning laser ophthalmoscopy
. In: Manns F, Soderberg P, Ho A, eds. Ophthalmic Technologies XV: Proceedings of the SPIE. Bellingham, WA: SPIE; 2005:145–51.
12.Vogel CR, Arathorn DW, Roorda A, Parker A. Retinal motion estimation in adaptive optics scanning laser ophthalmoscopy
. Opt Express 2006;14:487–97.
13.Tam J, Martin JA, Roorda A. Non-invasive visualization and analysis of parafoveal capillaries in humans. Invest Ophthalmol Vis Sci 2009;doi:10.1167/iovs. 09-4483.
14.Poonja S, Patel S, Henry L, Roorda A. Dynamic visual stimulus presentation in an adaptive optics
scanning laser ophthalmoscope. J Refract Surg 2005;21:S575–80.
15.Rossi EA, Weiser P, Tarrant J, Roorda A. Visual performance in emmetropia and low myopia after correction of high-order aberrations. J Vis 2007;7:14.
16.Chui TY, Song H, Burns SA. Individual variations in human cone photoreceptor packing density: variations with refractive error. Invest Ophthalmol Vis Sci 2008;49:4679–87.
17.Li KY, Tiruveedhula P, Roorda A. Adaptive optics
imaging and analysis of cone photoreceptors near the fovea center. Invest Ophthalmol Vis Sci 2009;50:E-abstract 4770.
18.Stevenson S, Kumar G, Roorda A. Psychophysical and oculomotor reference points for visual direction measured with the adaptive optics
scanning laser ophthalmoscope. J Vis 2007;7:137. Available at: http://journalofvision.org/7/9/137/
. Accessed December 30, 2009.
19.Raghunandan A, Frasier J, Poonja S, Roorda A, Stevenson SB. Psychophysical measurements of referenced and unreferenced motion processing using high-resolution retinal imaging. J Vis 2008;8:14.1–11.
20.Grieve K, Tiruveedhula P, Zhang Y, Roorda A. Multi-wavelength imaging with the adaptive optics
scanning laser Ophthalmoscope. Opt Express 2006;14:12230–42.
21.Tsunoda K, Oguchi Y, Hanazono G, Tanifuji M. Mapping cone- and rod-induced retinal responsiveness in macaque retina by optical imaging. Invest Ophthalmol Vis Sci 2004;45:3820–6.
22.Bizheva K, Pflug R, Hermann B, Povazay B, Sattmann H, Qiu P, Anger E, Reitsamer H, Popov S, Taylor JR, Unterhuber A, Ahnelt P, Drexler W. Optophysiology: depth-resolved probing of retinal physiology with functional ultrahigh-resolution optical coherence tomography. Proc Natl Acad Sci U S A 2006;103:5066–71.
23.Nelson DA, Krupsky S, Pollack A, Aloni E, Belkin M, Vanzetta I, Rosner M, Grinvald A. Special report: noninvasive multi-parameter functional optical imaging of the eye. Ophthalmic Surg Lasers Imaging 2005;36:57–66.
24.Grieve K, Roorda A. Intrinsic signals from human cone photoreceptors. Invest Ophthalmol Vis Sci 2008;49:713–9.
25.Gray DC, Merigan W, Wolfing JI, Gee BP, Porter J, Dubra A, Twietmeyer TH, Ahamd K, Tumbar R, Reinholz F, Williams DR. In vivo fluorescence imaging of primate retinal ganglion cells and retinal pigment epithelial cells. Opt Express 2006;14:7144–58.
26.Gray DC, Wolfe R, Gee BP, Scoles D, Geng Y, Masella BD, Dubra A, Luque S, Williams DR, Merigan WH. In vivo imaging of the fine structure of rhodamine-labeled macaque retinal ganglion cells. Invest Ophthalmol Vis Sci 2008;49:467–73.
27.Morgan JI, Dubra A, Wolfe R, Merigan WH, Williams DR. In vivo autofluorescence imaging of the human and macaque retinal pigment epithelial cell mosaic. Invest Ophthalmol Vis Sci 2009;50:1350–9.
28.Hofer H, Carroll J, Neitz J, Neitz M, Williams DR. Organization of the human trichromatic cone mosaic. J Neurosci 2005;25:9669–79.
29.Sincich LC, Zhang Y, Tiruveedhula P, Horton JC, Roorda A. Resolving single cone inputs to visual receptive fields. Nat Neurosci 2009;12:967–9.
30.Pircher M, Zawadzki RJ, Evans JW, Werner JS, Hitzenberger CK. Simultaneous imaging of human cone mosaic with adaptive optics
enhanced scanning laser ophthalmoscopy
and high-speed transversal scanning optical coherence tomography. Opt Lett 2008;33:22–4.
31.Mujat M, Ferguson RD, Iftimia N, Hammer DX. Compact adaptive optics
line scanning ophthalmoscope. Opt Express 2009;17:10242–58.