Deep Vascular Imaging in the Eye with Flow-Enhanced Ultrasound

Christian Damsgaard; Henrik Lauridsen

doi:10.3791/62986

Biology

Deep Vascular Imaging in the Eye with Flow-Enhanced Ultrasound

Published: October 4, 2021 doi: 10.3791/62986

Christian Damsgaard^1,2, Henrik Lauridsen³

¹Aarhus Institute of Advanced Studies, Aarhus University, ²Zoophysiology, Department of Biology, Aarhus University, ³Department of Clinical Medicine, Aarhus University

Summary

We present a non-invasive ultrasound technique for generating three-dimensional angiographies in the eye without the use of contrast agents.

Abstract

The retina within the eye is one of the most energy-demanding tissues in the body and thus requires high rates of oxygen delivery from a rich blood supply. The capillary lamina of the choroid lines the outer surface of the retina and is the dominating source of oxygen in most vertebrate retinas. However, this vascular bed is challenging to image with traditional optical techniques due to its position behind the highly light-absorbing retina. Here we describe a high-frequency ultrasound technique with subsequent flow-enhancement to image deep vascular beds (0.5-3 cm) of the eye with a high spatiotemporal resolution. This non-invasive method works well in species with nucleated red blood cells (non-mammalian and fetal animal models). It allows for the generation of non-invasive three-dimensional angiographies without the use of contrast agents, and it is independent of blood flow angles with a higher sensitivity than Doppler-based ultrasound imaging techniques.

Introduction

The high metabolism on the vertebrate retina imposes an intrinsic tradeoff between two contrasting needs; high blood flow rates and a light path devoid of blood vessels. To avoid visual disturbance of perfusing red blood cells, the retina of all vertebrates receives oxygen and nutrients via a sheet of capillaries behind the photoreceptors, the choriocapillaris¹^,²^,³. However, this single source of nutrients and oxygen imposes a diffusion limitation to the thickness of the retina⁴^,⁵, so many visually active species possess a variety of elaborate vascular networks to provide additional blood supply to this metabolically active organ⁶. These vascular beds include blood vessels perfusing the internal retinal layers in mammals and some fishes⁴^,⁷^,⁸^,⁹^,¹⁰, blood vessels on the inner (light-facing) side of the retina found in many fishes, reptiles, and birds⁴^,¹¹^,¹²^,¹³, and countercurrent vascular arrangements of the fish choroid, the choroid rete mirabile, that allows for the generation of super-atmospheric oxygen partial pressures¹⁴^,¹⁵^,¹⁶^,¹⁷^,¹⁸^,¹⁹^,²⁰. Despite that these additional non-choroidal paths for retinal nutrient supply play an essential role in fueling the metabolic requirements of superior vision⁴, the three-dimensional anatomy of these vascular structures is poorly understood, limiting our understanding of the morphological evolution of the vertebrate eye.

Traditionally, retinal blood supply has been studied using optical techniques, such as fundus ophthalmoscopy. This category of techniques provides high-throughput non-destructive information on non-choroidal blood vessel anatomy in high-resolution²¹ and is therefore readily used in clinical diagnosis of abnormalities in retinal vessel structure²². However, the retinal pigment epithelium absorbs the transmitted light and limits the depth of view in these optical techniques, providing reduced information on choroidal structure and function without the use of contrast agent²¹. Similar depth limitations are experienced in optical coherence tomography (OCT). This technique can generate high-resolution fundus angiographies using light waves at the technical expense of depth penetration²³, while the enhanced depth imaging OCT can visualize the choroid at the expense of retinal imaging quality²⁴. Magnetic resonance imaging overcomes the optical limitations of ophthalmoscopy and OCT and can map vascular layers in the retina, albeit at a low resolution²⁵. Histology and microcomputed tomography (µCT) maintain the high-resolution of the optical techniques and provide information on whole-eye vascular morphology⁴, but both techniques require ocular sampling and are therefore not possible in the clinic or rare or endangered species. To overcome some of the limitations of these established retinal imaging techniques, the study here presents an ultrasound protocol on anesthetized animals, where blood movement is mapped in silico on a series of equally-spaced two-dimensional ultrasound scans spanning a whole eye by applying a comparable technique as described previously for embryonic and cardiovascular imaging²⁶^,²⁷^,²⁸ and in OCT angiography²⁹. This approach allows for the generation of non-invasive three-dimensional deep ocular angiographies without using a contrast agent and opens up new avenues for mapping blood flow distribution within the eye across species.

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Protocol

The protocol below was performed with permission from the Danish Inspectorate for Animal Experimentation within the Danish Ministry of Food, Agriculture, and Fisheries, Danish Veterinary and Food Administration (Permit number 2016-15-0201-00835).

1. Anesthesia and ultrasound medium

Anesthetize the research animal.
NOTE: Type and dose of appropriate anesthesia are highly species-dependent. In general, immersion-based anesthetics such as MS-222 (ethyl 3-aminobenzoate methanesulfonic acid), benzocaine (ethyl 4-aminobenzoate), and propofol (2,6-diisopropyl phenol) are useful in fish and amphibians which readily absorbs the anesthetic over gills or skin (e.g., 0.05 mg·L^-1 benzocaine in rainbow trout). A range of dissolved compounds that can be administered intravenously, intramuscularly, intraperitoneally is available for amniotes, as are gas-based anesthetics. Alfaxalon administered intramuscularly is useful in reptiles (e.g., 30 mg·kg^-1 in lizards), and isoflurane administered as gas is useful in birds (e.g., 2% in air for pigeons). Refer to the published literature³⁰^,³¹^,³² for a full overview of available anesthetics across species.
Test reflexes in the animal to confirm an optimal level of anesthesia. Ensure that the animal is completely motionless during the procedure as the flow-enhanced ultrasound procedure is sensitive to motion noise.
1. Too deep anesthesia can alter blood flow patterns, so conduct a dose titration in the start-up phase of an experiment.
2. Increase the anesthesia dosage in steps and observe blood flow in the eye aided by simple brightness mode (B-mode) ultrasound.
  NOTE: An optimal level of anesthesia is obtained when the animal is motionless (except respiration) with visible ocular blood flow.
If the type/dose of anesthetic is not permissive for respiratory movements, then ensure adequate ventilation of the animal, e.g., using an air pump to oxygenate the water for aquatic species or a ventilator for air-breathing species.
Position the animal in a posture that allows direct access from above to the eye.
NOTE: Depending on species, this can be in either a supine or lateral position. It can be useful to construct a simple holding device using a small piece of non-reactive metal (e.g., stainless steel) and loose rubber bands (see Figure 1).
Place appropriate ultrasound medium on the eye of the animal. If scaled eyelids (ultrasound impermeable) cover the eye, then displace these gently with a cotton swab.
NOTE: For aquatic species, the best ultrasound medium is clean tank water in which the animal usually lives. For terrestrial species, a generous amount of ultrasound gel ensures free movements and imaging of the ultrasound transducer (i.e., linear array probe) across the entire surface of the eye. Vet ointment on the contralateral eye is required for terrestrial species.

2. 2D and 3D ocular ultrasound image acquisition

Position the ultrasound transducer medial to the eye in either a dorsal/ventral or rostral/caudal orientation depending on desired image orientation.
In B-mode, with a maximum depth of field, image the medial and deepest portion of the eye and make sure that all structures of interest are visible in the image field.
NOTE: In some species, the crystalline lens takes up a comparatively large proportion of the vitreous humor, which may absorb the ultrasound, especially at higher frequencies.
Slowly translate the transducer to each side while inspecting the real-time images. Make sure all structures of interest are visible in the image field; if not, switch to a transducer with a lower frequency and larger depth of field.
NOTE: The following center frequencies allow for the following maximum depth of field: 21 MHz: 3 cm, 40 MHz: 1.5 cm, 50 MHz: 1 cm (see Table 1). However, these maximum depth of field values can be markedly lower if the eye contains calcified or other ultrasound impermeable structures.
Adjust image depth, depth offset (distance from the top of the image to the structure of interest), image width, as well as number and position of focal zones to cover the desired region of interest in all three spatial dimensions (e.g., 1 cm image depth, 2 mm depth offset, 1 cm image width, one focal zone).
NOTE: Although specific naming of buttons that adjust these parameters may vary between ultrasound systems, most systems will have buttons with logical names for these adjustments. These image parameter settings usually affect the range of possible temporal resolutions of the ultrasound acquisition.
Set frame rate in the range of 50-120 frames·s^-1.
NOTE: The temporal resolution (i.e., the time interval between successive B-scans) must be adequate to display large pixel intensity variability in imaged blood vessels, i.e., the temporal resolution must not be too high. On the other hand, to complete a full 3D recording of the eye in a reasonable time, temporal resolution cannot be too low. A temporal resolution ranging from 50-120 frames·s^-1 is usually adequate for the flow-enhanced procedure in most species. On some ultrasound systems, this desired temporal resolution can be obtained by switching between the "general imaging" (high spatial/low temporal resolution) and "cardiology" (low spatial/high temporal resolution) modes.
Adjust 2D gain to a level (~5 dB), so anatomical structures are only just visible in the B-mode acquisition to increase the signal-to-noise ratio in the subsequent flow-enhanced reconstruction.
To acquire a 2D flow-enhanced image at a single slice position, translate the transducer to this position and continue at step 3.1.
To acquire a 3D recording of an entire region of interest, e.g., the retina, translate the transducer to one extreme of the region of interest.
1. To determine the exact position of the extreme end of the region of interest, increase the 2D gain briefly.
2. After correct transducer placement is complete, lower the 2D gain before recording to ensure maximal signal-to-noise ratio in the subsequent flow-enhanced reconstruction.
For each step (slice) in the 3D recording, acquire ≥100 frames (optimally ≥1000 frames).
Using a micromanipulator or build-in transducer motor, translate the transducer across the entire region of interest in steps of, e.g., 25 µm or 50 µm (remember to note the step size) and repeat the ≥100 frames acquisition for each step.
Euthanize the research animal according to the animal care guidelines of the institution.

3. Flow-enhanced image reconstruction

Export the recordings into digital imaging and communications in medicine (DICOM) file format (little-endian).
To produce a single flow-enhanced image based on a ≥100 frames (T) cine recording, calculate the standard deviation on pixel level (STD(x,y)) using the formula:

Where I_t(x,y) is the intensity of the pixel at the (x,y) pixel coordinate at time t, and Ī_t(x,y) is the arithmetic mean value of I over time.
Repeat step 3.2 for each slice in the 3D recording.
To automate the STD-calculation and image reconstruction process for multiple slices in a 3D recording, conduct this operation in batch mode using, e.g., ImageJ and the supplementary macro script (Supplementary File 1).
Combine all reconstructed slices into one image stack (Images to Stack command in ImageJ).
Specify slice thickness from the step size used during acquisition (Properties command in ImageJ).
Save the image stack as a 3D TIF file.
NOTE: Flow-weighted three-dimensional recordings of ocular blood vessels can subsequently be used to create volume renderings and build digital and physical anatomical models of vascular structures of the eye. These image processing options are outside the scope of this protocol; refer to the previously published articles for more details³³^,³⁴^,³⁵.

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Representative Results

The flow-enhanced ultrasound technique to image vascular beds of the eye can be applied in a range of species and has currently been used in 46 different vertebrate species (Figure 1, Table 1). The presence of nucleated red blood cells in non-adult-mammalian vertebrates provides positive contrast of flowing blood compared to static tissue in cine recordings (Supplementary File 2). However, when analyzed on a frame-by-frame basis, the clear distinction between blood and surrounding tissue is less obvious (Figure 2A). The blood flow enhancement procedure described in this protocol essentially compiles a multi-time point recording in 2D space (a slice made of T frames) into a single image in which the inherent signal value fluctuations in pixels positioned in flowing blood scores a higher standard deviation than surrounding static tissue, hence producing positive contrast (Figure 2B). To perceivably enhance the blood vessel contrast, Look Up Tables can be used to produce pseudocolor images (Figure 2C). In 3D acquisitions, multiple parallel slices with known spacing can be combined into 3D image data (Supplementary File 3 and Supplementary File 4) that can be used for three-dimensional volume rendering (Figure 2D) and anatomical modeling (Figure 2E and Supplementary File 5). Doppler-based ultrasound imaging also provides the option to specifically image blood flow, however with less sensitivity than the described method (compare Figure 2G with Figure 2H and Figure 2I), and importantly not if blood flow orientation is directly or close to perpendicular to the direction of the sound wave. The flow-enhanced procedure described in this protocol is independent of the orientation of blood flow both in-plane and out-of-plane.

The flow-enhanced ultrasound procedure allows for blood flow imaging in a range of species with nucleated red blood cells (Figure 3A-D). Deep ocular vascular beds such as the choroid rete mirabile in some fish can be imaged if present in the species (yellow arrowhead in Figure 2, Figure 3B, Figure 4). The method is limited by the absence of nucleated red blood cells in adult mammals in which the flow enhancement procedure produces some degree of blood flow contrast but is not as distinct as in species with nucleated red blood cells (Figure 3E,F).

Flow-enhanced ultrasound is sensitive to motion noise, and, e.g., respiratory movements can cause image blurring and artifacts such as tissue border enhancement (Figure 4A-C, Supplementary File 6). Prospective or retrospective gating can be used to adjust for motion noise (Figure 4D,E).

Figure 1: Examples of the variety of species suitable for flow-enhanced ultrasound imaging of ocular vasculature. (A) Goldfish (Carassius auratus). (B) Siberian sturgeon (Acipenser baerii). (C) European seabass (Dicentrarchus labrax). (D) Clown featherback (Chitala ornata). (E) Crucian carp (Carassius carassius). (F) Embryonic domestic chicken (Gallus gallus domesticus). It can be useful to construct a simple holding device using a non-reactive metal weight and loose rubber bands (A,C,D). Both large, immobile lab-based ultrasound imaging systems can be used for the procedure (A-D,F) as well as small field operative systems (E). When imaging small and highly temperature-sensitive species that cannot be retained in a temperature-controlled water bath like embryonic birds, imaging can be performed while the sample is inside the incubator (F). Please click here to view a larger version of this figure.

Figure 2: Effect of flow enhancement on ocular ultrasound scans. (A) Examples of raw B-mode ultrasonographic images of the eye of a goldfish in a 1000 frame cine recording. Whereas blood flow can be observed in the cine recording (Supplementary File 2) it is difficult to see in static frames. (B) Flow-enhanced grayscale image (same slice as in A). Both retinal and post-retinal vascular beds are enhanced. (C) Pseudo-colored version of the image in B with ImageJ Fire Look Up Table. (D) Volume-rendered display of blood flow in the eye of the same goldfish as in A-C, based on 3D acquisition. (E) Two-segment (retinal and post-retinal vessels) anatomical model of eye in A-D (for interactive model see supplementary material 5). (F-I) Raw B-mode ultrasonographic image of the eye of another goldfish (F) comparing color Doppler based flow imaging (G) to the flow-enhanced methods described in this protocol (H-I, note I is an overlay of H on F). Green arrows indicate retinal vessels, yellow arrowheads indicate the choroid rete mirabile. Please click here to view a larger version of this figure.

Figure 3: Representative examples of flow-enhanced ocular ultrasound images in a variety of vertebrate species. (A) Senegal bichir (Polypterus senegalus). (B) Red-bellied piranha (Pygocentrus nattereri). (C) Green iguana (Iguana iguana). (D) Embryonic (day 18) domestic chicken (Gallus gallus domesticus). (E) House mouse (Mus musculus). (F) Brown rat (Rattus norvegicus). In species with nucleated red blood cells, the flow-enhancement procedure yields useful images of ocular blood flow (A-D), whereas in adult mammals (enucleated red blood cells), it produces only limited contrast between flowing blood and surrounding tissue (E-F). Green arrows indicate retinal vessels; blue arrowheads indicate post-retinal vessels such as the choriocapillaris; yellow arrowheads indicate choroid rete mirabile. In the late embryonic domestic chicken, blood flow in the pecten oculi can be observed (lower green arrow in F). Please click here to view a larger version of this figure.

Figure 4: Respiratory movements induce motion noise that can be alleviated by retrospective gating. (A-B) Example of respiratory movements in the eye of a European plaice (Pleuronectes platessa). The red dot is at the same image coordinate in A (slice 54/410) and B (slice 92/410), but it can be observed that the eye has shifted position (see also cine recording in supplementary material 6). (C) Attempt to perform the flow-enhancement operation on the full 410 frames recording fails due to motion noise. Tissue borders are artificially enhanced due to movements. (D) retrospective gating operation based on normalized signal intensity (SI) at the red dot in A-B. Only frames with normalized SI > 50 (in total 38 frames), i.e., indicating that the eye is at the same position as in B, are included for the flow-enhancement procedure. (E) Resulting image of retrospectively gated flow-enhancement procedure. Compare with C. In the gated image, artificial border enhancement is avoided, and blood flow in the choroid rete mirabile (yellow arrowhead) can be observed. Please click here to view a larger version of this figure.

Table 1: List of species on which the flow-enhanced ultrasound technique to image ocular blood flow has been used. The applicability of the method is based on the ability to produce a contrast-rich representation of vascular beds compared to the static background. Please click here to download this Table.

Supplementary File 1: Macro script to automate flow-enhancement calculations. The script is written in IJ1 Macro language and can be executed both using the ImageJ macro function (for single slice recording) or the ImageJ Batch Process (for multiple slice 3D recording). Please click here to download this File.

Supplementary File 2: Raw B-mode cine recording on the eye of a goldfish (Carassius auratus). Blood flow can be observed as the video is playing, but not on a single frame as in Figure 2A. Please click here to download this File.

Supplementary File 3: Slice video through the eye of a goldfish (Carassius auratus) of blood flow-enhanced sections. Please click here to download this File.

Supplementary File 4: Three-dimensional TIF file of the flow-enhanced eye of goldfish (Carassius auratus). Images have been binned by 3 x 3 x 3 to minimize file size (27-fold reduction in spatial resolution and file size).Please click here to download this File.

Supplementary File 5: Interactive 3D model of pre- and post-retinal vessels in the eye of a goldfish (Carassius auratus). Please click here to download this File.

Supplementary File 6: Raw B-mode cine recording on the eye of a European plaice (Pleuronectes platessa). Note respiratory movements. Please click here to download this File.

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Discussion

Vascular imaging using flow-enhanced ultrasound provides a new method for non-invasive imaging of the vasculature of the eye that offers several advantages over present techniques but has its intrinsic limitations. The primary advantage of flow-enhanced ultrasound is the ability to generate ocular angiographies with a depth of field that exceeds the retinal pigment epithelium, which limits the depth of field in optical techniques. In ultrasound imaging, spatial resolution and depth of field are ultimately determined by the ultrasound transducer frequency, where higher frequencies increase the spatial resolution, but at the expense of a shallower depth of field, thus the choice of transducer frequency introduces a tradeoff between image depth and spatial resolution. In our experience, optimal retinal ultrasound imaging is achieved using high-frequency ultrasound transducers (≥50 MHz) in small eyes with image depths of <1 cm and lower frequency transducers (20-40 MHz) in larger eyes with image depths of 1.5-3.0 cm. For a 3D ultrasound scan, the resolution of the additional slice-dimension is set by the step size between scans in the stack of 2D ultrasound scans. In our experience, it is difficult to conduct a 3D scan with a step size smaller than 20 µm.

Flow-enhanced 2D ultrasound has a high temporal resolution. Ideally, ≥1000 frames per image are required for flow-enhanced vascular imaging, so at least 8 s are required per image scan. The temporal resolution is significantly reduced when performing 3D flow-enhanced ultrasounds, where the scanning time increases with the number of images in the 3D stack of scans. Given the high temporal resolution, the flow-enhanced 2D ultrasound workflow shows strong potential as a method for identifying temporal changes in relative blood flow velocities and blood flow distribution during experimental manipulation. Thus, future studies can use the workflow to identify how altered environmental conditions (e.g., temperature, pO₂, pCO₂) or pharmacological administration affect blood flow in the eye and other organs.

The ultrasound workflow relies on the positive contrast of nucleated red blood cells from most non-mammalian vertebrates. Thus, the enucleated red blood cells of adult mammals and some salamander species³⁷ provide too little contrast to effectively enhance blood flow using the present workflow (Figure 3E,F). In traditional ultrasound workflows, vascular injection of microbubbles provides high enough contrast to identify the vasculature in mammals³⁸, which has been used to generate vascular angiographies of the retrobulbar vessels within the rat eye³⁹. However, the microbubbles burst within minutes, so the generation of 3D angiographies requires successive microbubble injections.

Flow-enhanced ultrasound depends on sequential recordings in the same position of the eye, so the technique is not possible in awake animals, where minor random movements may offset the image and undermine flow-enhancement calculations. Thus, the present method must be performed under proper anesthesia for immobilization to enhance image quality by reducing random movements. However, regular movements of the eye that occur during regular respiratory movements can be offset by prospectively or retrospectively gating to the ventilation pattern of the animal, so only scan recording from the same time interval within the ventilation cycle is used in the data analysis. While the retrospective gating approach to offset ventilatory movements of the image significantly improves the image stability, it pronouncedly reduces the number of frames included in calculating the standard deviation of signal intensity leading to a decrease in signal-to-noise ratio (compare Figure 4E to Figure 2C and Figure 2I). This effect is alleviated using prospective gating at the ultrasound scanner, in which image data is only acquired when the animal is in the desired phase of respiration. However, this causes a marked increase in acquisition time if the desired number of frames ≥1000 must be acquired.

We see multiple applications in zoological and veterinarian research for the flow-enhanced ultrasound workflow to map the physiology and anatomy of the eye's vasculature. The vasculature of ray-finned fishes, mammals, and birds are relatively well-described¹^,³^,⁴^,⁸^,⁹^,¹²^,¹⁵^,⁴⁰, but this is not the case for non-bony fishes (jaw-less vertebrates and chondrichthyans), amphibians, and reptiles, that represent their respective earlier diverging sister groups. Implementing flow-enhanced ultrasound on these poorly understood animal groups and integrating these data with knowledge on the more well-studies groups will provide fundamental insight into the evolution of the vasculature of the vertebrate eye. Because the eye's vasculature is similar in closely related species⁴, such detailed information on the ocular vasculature in a broad range of species will provide a point-of-reference for veterinarians to identify malformations in the eye's vasculature due to developmental defects, diseases, or physical injuries. Furthermore, the ability to acquire 2D blood flow information with a high spatiotemporal resolution provides the means for quantifying pharmacokinetic effects on blood flow distribution in deep vascular beds, with vast applications in drug development and testing. Future studies on this technique should focus on identifying injectable compounds that enhance the contrast of blood in species with enucleated red blood cells, which will expand the applicability of this technique to mammals with vast applications in biomedical research and clinical diagnostics of vascular dysfunction in the eye and other deep vascular beds.

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Disclosures

The authors declare that no completing interests exists.

Acknowledgments

This work has received funding from the Carlsberg Foundation (CF17-0778; CF18-0658), the Lundbeck Foundation (R324-2019-1470; R346-2020-1210), the Velux Foundations (00022458), The A.P. Møller Foundation for the Advancement of Medical Science, the European Union's Horizon 2020 research and innovation program under the Marie Skłodowska-Curie grant agreement (No. 754513), and The Aarhus University Research Foundation.

Materials

Name	Company	Catalog Number	Comments
MS-222	Sigma	E10521-50G
Benzocaine	Sigma	E-1501
Propofol	B Braun	12260470_0320
Alfaxalon	Jurox	NA
Isoflurane	Zoetis	50019100
Ultrasound scanner	VisualSonics	Vevo 2100

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