Blue arrows indicate the optical coherence tomographic scan beam; green arrows, backscattered light. The reflection is higher for perpendicular erythrocytes than for parallel erythrocytes. Adapted from Cimalla et al.3
The contrast of the intraluminal pattern on optical coherence tomography increased from low flow velocity (<1.5 mm/s) (A), over medium flow velocity (1.5-3.0 mm/s) (B), to high flow velocity (>3.0 mm/s) (C). D, The responsible erythrocyte alignment is schematized under each optical coherence tomographic image (adapted from Cimalla et al3). Black arrows indicate flow velocity; blue arrows, shear stress.
Each optical coherence tomographic scan was positioned perpendicular to the temporal retinal artery. Arrow indicates the position of the scan beam. The backscattering intensity was measured at half the vessel diameter. In vessels with high flow velocity, this resulted in bimodal intensity curve modeling. AU indicates arbitrary units.
While the profiles in the vessels with low flow velocity were irregular (A), those with medium (B) and high (C) flow velocity exhibited a characteristic bimodal profile. This pattern also seemed more pronounced in vessels with higher velocities within a single category. Dashed lines indicate mean backscattering intensity for each category; AU, arbitrary units.
In 1 artery with high blood flow velocity, the scan position (arrow) at a bend close to a retinal vein resulted in low contrast in the inferior half of the vessel and a lacking middle hump on the intensity profile. AU indicates arbitrary units.
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Seidel G, Aschinger G, Singer C, et al. Estimating Retinal Blood Flow Velocities by Optical Coherence Tomography. JAMA Ophthalmol. 2016;134(10):1104–1110. doi:10.1001/jamaophthalmol.2016.2507
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Can retinal blood flow velocity be estimated from structural optical coherence tomographic scans?
In this cross-sectional study of 30 eyes from 30 patients, retinal blood flow velocity could be visually graded as low, medium, or high flow velocity via assessment of the intraluminal backscattering pattern on optical coherence tomography by 3 independent graders. When discriminating low flow velocities from medium or high flow velocities, sensitivity ranged from 88.2% to 100% and specificity ranged from 97.6% to 100%.
These data suggest that a low retinal blood flow velocity reflects in a visually distinct contrast reduction of the intraluminal pattern of retinal vessels on optical coherence tomography.
While optical coherence tomography (OCT) angiography has been considered to evaluate retinal capillary blood flow instead of fluorescein angiography, the reflectance pattern of blood vessels on structural OCT might also provide retinal capillary flow data in the absence of fluorescein angiography. This potential has been insufficiently explored, despite promising data concerning a possible relationship between the reflectance pattern of blood vessels and their perfusion velocity in a laboratory setting.
To evaluate the potential of retinal blood flow velocity estimation by structural OCT.
Design, Setting, and Participants
Cross-sectional observational study conducted from June to November 2015 at a tertiary clinical referral center. Sixty arteries (the superior and inferior temporal arteries) from 30 eyes of 30 patients (17 female, 13 male) were included in the study.
Main Outcomes and Measures
Based on the intraluminal contrast patterns of retinal arteries on OCT, 3 independent graders categorized the blood flow velocities as low, medium, or high. These results and the results from a software-based intraluminal contrast analysis were compared with the retinal blood flow velocities measured by video fluorescein angiography.
Among the 30 eyes of 30 patients (mean [SD] age, 72.6 [12.3] years; 17 female, 13 male), 15 were controls without retinal occlusion, 6 had a branch retinal artery occlusion, and 9 had a central retinal artery occlusion. When discriminating between low flow velocities and medium or high flow velocities, the graders’ sensitivity ranged from 88.2% to 100% (grader 1: 88.2%; 95% CI, 63.6%-98.5%; grader 2: 88.2%; 95% CI, 63.6%-98.5%; and grader 3: 100%; 95% CI, 69.8%-100%) and their specificity ranged from 97.6% to 100% (grader 1: 100%; 95% CI, 87.7%-100%; grader 2: 97.6%; 95% CI, 87.4%-99.9%; and grader 3: 100%; 95% CI, 87.7%-100%). The κ coefficients of the comparison between the 3 graders and the angiography were 0.77 (95% CI, 0.60-0.93; P < .001), 0.64 (95% CI, 0.44-0.83; P < .001), and 0.87 (95% CI, 0.74-0.99; P < .001). In the computer-based assessment, the contrast reduction of the intraluminal pattern could be numerically expressed in a specific coefficient in the model (I2, describing the angular change of the backscattering intensity in the model), which presented nonoverlapping intervals between low flow velocities and medium or high flow velocities (mean [SD] I2, 0.3 [5.3], 20.4 [6.4], and 21.7 [4.0], respectively).
Conclusions and Relevance
This study suggests that a low retinal blood flow velocity reflects in a visually distinct contrast reduction of the intraluminal pattern of retinal vessels on OCT. Larger studies are required to assess the clinical benefits.
Since 1991, optical coherence tomography (OCT) sweepingly spread throughout ophthalmology and thereby revolutionized noninvasive imaging of ocular structures. However, a major limitation of structural OCT is that it apparently provides no direct functional information, such as perfusion. This issue is addressed by OCT angiography and Doppler OCT.1,2 Devices for OCT angiography are not yet widely adopted, and devices for Doppler OCT are not even commercially available. Thus, today in many practices, fluorescein angiography is used for the imaging of retinal perfusion.
Compared with fluorescein angiography, OCT is faster, easier to perform, and less unpleasant to the patient and, most important, has a better safety profile because it is noninvasive. These advantages warrant a closer look at the diagnostic potential of structural OCT images. While functional information cannot be assessed directly from a frozen image, some information, blood flow velocity in particular, can be assessed indirectly. For this purpose, the intraluminal backscattering pattern on OCT cross sections from retinal vessels can serve as a marker for the blood flow velocity.3
In such scans, an hourglass-shaped pattern arises from the erythrocyte’s orientation within the vessel’s lumen. When erythrocytes travel in a tubelike structure, they align themselves with their disk plane parallel to the vessel wall. Thus, when these erythrocytes are scanned by the light beam of OCT, they are oriented perpendicular on the top and bottom of the vessel, parallel on the sides, and relatively loose in the center (Figure 1). Because most reflection occurs when the beam meets a perpendicular interface, healthy retinal vessels exhibit higher backscattering on their top and bottom than on their sides and in their center. This generates the hourglass-like appearance. The faster the blood flows, the tidier the erythrocytes align, which in turn leads to a more pronounced demarcation between high- and low-reflecting areas. A slower blood flow, on the other hand, correlates with a lower contrast or even absence of this pattern (Figure 2). This has been shown experimentally in glass tubes and in the saphenous artery of mice.3 The presence of this pattern has been confirmed in a clinical setting by Willerslev et al,4-6 who also indicated a relationship between an altered intraluminal reflectivity and altered blood flow circumstances such as vessel branching, emboli, or ocular ischemic syndrome.
The aim of this study was to assess the potential of the hourglass-shaped intravascular pattern on OCT to serve as a tool for estimating the retinal blood flow velocity in humans.
After a planning phase in January 2015, the study was conducted at a tertiary referral center from June to November 2015. Patients with a branch retinal artery occlusion, with a central retinal artery occlusion, and without a retinal artery occlusion were included. The latter group comprised patients who underwent fluorescein angiography for abnormalities in the fellow eye such as retinal vein occlusions or age-related macular degeneration. All patients underwent an ophthalmologic examination including medical history, best-corrected visual acuity assessment, intraocular pressure measurement (Goldmann tonometer AT 900; Haag-Streit AG), slitlamp examination, indirect ophthalmoscopy, fundus photography (FF450 fundus camera; Carl Zeiss Meditec), optical biometry (IOLMaster; Carl Zeiss Meditec), OCT (Spectralis OCT; Heidelberg Engineering), and video fluorescein angiography (Heidelberg Retina Angiograph 2; Heidelberg Engineering). Prior to the study initiation, the institutional review board of the Medical University of Graz approved all study procedures, the study protocol, and the informed consent form. The latter was signed by all study participants in case of agreement to participate in the study after a personal colloquium with the principal investigator (G.S.). All participants were recruited from patients presenting at the study hospital. The study adhered to the Declaration of Helsinki.7
We used Spectralis OCT with version 6.0.9 software (Heidelberg Engineering) to record 20° single line scans perpendicular to the inferior and superior temporal retinal arteries. The scan’s distance to the optic disc measured approximately 1 disc diameter. Each of these vessel cross sections comprised 100 averaged images (100 frames) in the high-resolution mode of the device. To assess a potential influence of a varying amount of averaging, a subgroup of patients was additionally imaged with 50 frames. For all recordings, the built-in eye tracking software ensured exact position correspondence.
Within 30 minutes after OCT was performed, video fluorescein angiography was performed with a confocal scanning laser system (Heidelberg Retina Angiograph 2, version 5.7.4 software; Heidelberg Engineering). The procedure has been described in detail elsewhere.8-11 In short, each patient received a 5-mL bolus of 10% fluorescein dye into the antecubital vein and a video of the posterior pole was digitally recorded with a confocal laser ophthalmoscope with a 50° objective. On the resulting images, we selected the temporal major retinal branch arteries and measured the distance from a location close to the optic rim to a location on the same artery as distant as possible without major arterial branching in between, using the device’s built-in software. The time the fluorescein took to travel this distance was noted and from the resulting 2 parameters the fluorescein’s traveling velocity was calculated as distance over time. This served as an estimate for the true blood flow velocity and was categorized as low flow velocity (<1.5 mm/s), medium flow velocity (1.5-3.0 mm/s), or high flow velocity (>3.0 mm/s).
For software analysis, a self-developed semiautomated approach was implemented in which the user first had to mark the vessel lumen in the OCT B-scan. Then, the software analysis of the intraluminal intensity pattern was carried out based on the method proposed by Cimalla et al.3 For this method, the following function is fitted into the intensity variation along a circular path at half the vessel radius:
I(φ) = I0 + I1 · cos(φ) + I2 · cos(2φ) + I3 · cos(3φ) + I4 · cos(4φ),where φ is the angle of rotation with respect to the direction of the probing beam, I0 is the background intensity, I1 is the OCT signal intensity loss over the vessel depth, I2 and I4 characterize the angular variation in red blood cell backscattering along the circular path, and I3 represents the nonlinear intensity variations along the vessel depth.
The parameter I2 best describes the hourglass-shaped intensity patterns seen in the vessel cross sections and is therefore the most promising indicator for flow velocity. Figure 3 shows an exemplary reflection analysis and the resulting model fit.
To evaluate a retinal specialist’s ability to visually discriminate contrast changes of the intraluminal pattern on OCT, the vessel cross sections were presented to 3 retina specialists (A.H., M.W., and G.S.) who were informed about the concept of the hourglass sign but masked to the diagnosis, to the belonging of any vessel to a particular eye, and to the blood flow velocities of the individual vessels. Each grader evaluated all vessels in a single session independent from the other graders. To preclude an influence by the infrared fundus image of the OCT, a technician loaded each scan and subsequently covered the infrared image on the monitor. The grader could then adjust the OCT image to his preferred magnification and scaling on the device and grade each vessel analogous to the angiography categories as low flow velocity, medium flow velocity, or high flow velocity by his judgment of the intraluminal reflection pattern (Figure 2).
We analyzed the extent of agreement for the categories low flow velocity, medium flow velocity, and high flow velocity between each grader and the angiography by estimating Cohen κ statistics. We estimated the sensitivity and specificity of the graders to identify low flow velocity vs medium or high flow velocity using the angiography categories as gold standard. Results are presented with 95% confidence intervals. Because this study was considered a pilot study, no sample size calculation was performed. Taking the number of patients into account, this is an exploratory analysis. Data are shown as mean (standard deviation) or median (interquartile range [IQR]). All analyses were performed using R version 3.2.2 statistical software (R Foundation).
We included 60 arteries (the superior and inferior temporal arteries) from 30 eyes of 30 patients (17 female, 13 male) with a mean (SD) age of 72.6 (12.3) years. Of the 30 eyes, 15 were controls without a retinal artery occlusion, 6 had a branch retinal artery occlusion, and 9 had a central retinal artery occlusion. The median time from the reported symptom onset to the study procedures was 1.9 days (range, 5 hours to 63 days; mean [SD], 6.3 [13.9] days).
Based on the angiographic flow analysis, 17 arteries (28.3%) showed low flow velocity, 6 (10.0%) showed medium flow velocity, and 37 (61.7%) showed high flow velocity. The median flow velocities for the 3 groups were 0.1 mm/s (IQR, 0.05-0.3 mm/s), 2.4 mm/s (IQR, 2.3-2.5 mm/s), and 6.7 mm/s (IQR, 4.9-8.4 mm/s), respectively.
A single OCT cross section of a healthy vessel was excluded owing to poor image quality, leaving 59 vessels to compare with the angiographic findings. The graders could discriminate a vessel with low flow velocity from a vessel with medium or high flow velocity with a sensitivity of 88.2% to 100% (grader 1: 88.2%; 95% CI, 63.6%-98.5%; grader 2: 88.2%; 95% CI, 63.6%-98.5%; and grader 3: 100%; 95% CI, 69.8%-100%) and a specificity of 97.6% to 100% (grader 1: 100%; 95% CI, 87.7%-100%; grader 2: 97.6%; 95% CI, 87.4%-99.9%; and grader 3: 100%; 95% CI, 87.7%-100%).
The κ coefficients of the comparison between the 3 graders and the angiography were 0.77 (95% CI, 0.60-0.93; P < .001), 0.64 (95% CI, 0.44-0.83; P < .001), and 0.87 (95% CI, 0.74-0.99; P < .001), ie, the agreement between the graders’ estimates and the angiography measurements regarding the 3 blood flow categories was good to very good.
There was no difference if the graders rated a 50-frame or 100-frame image. The subset in which both frame rates were available included 49 vessels, and the κ coefficients of the graders when comparing their 50-frame choices with their 100-frame choices ranged from 0.86 to 0.96 (grader 1: 0.87; 95% CI, 0.72-1.01; P < .001; grader 2: 0.86; 95% CI, 0.71-1.01, P < .001; and grader 3: 0.96; 95% CI, 0.87-1.04; P < .001), ie, the agreement between the 2 frame rates was very good. The agreement with the angiographic findings was slightly poorer with 50 frames than 100 frames in 2 graders but slightly better with 50 frames than 100 frames in 1 grader. In any case, the agreement remained high (grader 1: κ = 0.69; 95% CI, 0.48-0.90; P < .001; grader 2: κ = 0.77; 95% CI, 0.57-0.96; P < .001; and grader 3: κ = 0.86; 95% CI, 0.71-1.00; P < .001).
The mean (SD) I2, which describes the angular change of the backscattering intensity in the model, was 0.3 (5.3) in the low flow velocity group, 20.4 (6.4) in the medium flow velocity group, and 21.7 (4.0) in the high flow velocity group. Notably, there was no overlap of the values of the low flow velocity group with the values of the medium or high flow velocity groups. With increasing flow velocity, the model resulted in an increasingly regular bimodal fit. Figure 4 shows the backscattering intensity profiles of all vessels according to their categorization on angiography.
In the high flow velocity group, 1 vessel fell out of line, lacking the middle hump and having the lowest I2, 13.4, as compared with the other vessels in this category. On review, this vessel was measured at a bend adjacent to the corresponding vein (Figure 5). On the grader-based evaluation of this vessel, both graders 2 and 3 incorrectly estimated a medium flow velocity, while grader 1 categorized it correctly as having a high flow velocity. This vessel remained in the statistical analysis.
In this prospective, single-center case series, we evaluated the possibility of estimating retinal blood flow velocity on structural OCT B-scans. Our data show that the intraluminal backscattering profile on such a scan enables the visual estimation of low blood flow velocities in retinal vessels by human graders. The results of a semiautomated approach are promising but should be validated prospectively.
Previously proposed techniques for evaluating retinal blood flow velocity include fluorescein angiography,12 laser Doppler velocimetry,13 color Doppler imaging,14 the laser speckle method,15 motion-contrast velocimetry,16 Doppler OCT,1 and optical angiography.17 While most of these methods focus on a more quantitative assessment, compared with them the blood flow velocity estimation with traditional spectral-domain OCT has its advantages. First, owing to its noninvasive nature and acquisition speed, it is easier and safer to obtain in routine practice than most of the other methods. Second, it is relatively cheap, as most ophthalmic clinics already use spectral-domain OCT. Third, it can be easily repeated within short periods. For example, fluorescein angiography takes 24 hours after initial use until naive imaging can be obtained.
Our data show that a lower flow velocity correlated with reduced contrast of the OCT pattern, and an absent pattern as detected by visual grading highly correlated with a severely diminished blood flow velocity. This was reflected in our study population by a positive predictive value of 0.93 and a negative predictive value of 0.91 for all graders combined. Of all gradings with 100 frames, only once was a vessel incorrectly graded as low flow velocity (false-positive) and 4 times was a vessel of the low flow velocity group missed (false-negative).
On the semiautomated profile, a faster blood flow translated into a more pronounced double hump pattern. This could be numerically expressed in a specific coefficient in the model (I2), which presented nonoverlapping intervals between low flow velocities and medium or high flow velocities. A slower flow was associated with an irregular shape of the backscattering profile, which contrasted with an increasing regularity of a double hump at faster velocities. This was true not only between the flow categories but also within the categories themselves. In other words, the flow velocity values at the higher end of each category’s spectrum tended to show a more pronounced double hump than those at the lower end of each category.
We did not directly compare the grader-based and semiautomated assessments because no estimates for any of the coefficients had been available for humans. The groundwork by Cimalla et al3 dealt with an in vitro model and the saphenous artery of mice, and extrapolation to the human eye did not seem adequate. However, the values for I2 in the present study could serve as a reference point for future investigations.
The following limitations regarding the presented data need to be considered. First, any categorization of retinal blood flow velocity is arbitrary to some degree. Even in healthy individuals, the retinal blood flow velocity varies greatly and the coefficients of variation of repeated measures for video fluorescein angiography range from 10% to 25%.9 The reported velocities between different methods vary to an even greater extent, probably not least because they measure different aspects of blood movement such as erythrocyte velocity or plasma velocity.9,16,18,19 Moreover, the blood flow velocity is highly dependent on the vessel diameter.20,21
We based our categorization on the values for fluorescein traveling velocities by Wolf et al,9 who reported a mean (SD) velocity of 6.4 (1.7) mm/s in temporal retinal arteries of healthy adults. This means that, given a normal distribution, fewer than 1% of healthy temporal retinal arteries should have blood flow velocities slower than 1.5 mm/s. As our values for the healthy vessels match those previously reported, the cutoff values used in the present study seem to be a reasonable estimate.
Second, while the measurement with OCT is fairly robust, improper positioning of the scan can produce misleading results. This was the case in 1 vessel measurement at a bend that led to poor contrast of the intraluminal pattern and a tendency to underestimate the flow velocity. The reason for the altered contrast might lie in the loss of the parabolic shape of the blood flow velocity profile.22 A fairly straight segment would be the preferred location to measure.
Third, this study provides limited data to conclude whether the discrimination of varying blood flow velocities can be translated to the intermediate range of blood flow variations. However, our results demonstrated no difference in the coefficient between our medium and high velocity groups (mean [SD] I2, 20.4 [6.4] vs 21.7 [4.0], respectively).
Fourth, we cannot fully exclude that other OCT signs that indicate retinal ischemia such as retinal nerve fiber layer swelling or increased hyperreflectivity of the inner portion of the outer plexiform layer may have influenced the graders.23 However, 7 OCT images showed pronounced retinal nerve fiber layer swelling and a prominent inner limiting membrane sign while having medium or high blood flow velocities, and 1 image of a retinal vessel with a low blood flow velocity lacked retinal nerve fiber layer swelling and a prominent inner limiting membrane sign. In all these circumstances, the graders differentiated the vessels with low flow velocities from those with medium or high flow velocities correctly. This emphasizes that the intraluminal backscattering profile is less a tool for diagnosing retinal artery occlusions and more a tool for judging the blood flow velocity at the time of measurement.
A low retinal blood flow velocity is reflected in a visually distinct contrast reduction of the intraluminal pattern of retinal vessels on OCT B-scans.
Corresponding Author: Gerald Seidel, MD, Department of Ophthalmology, Medical University of Graz, Auenbruggerplatz 4, 8036 Graz, Austria (firstname.lastname@example.org).
Accepted for Publication: June 5, 2016.
Published Online: August 4, 2016. doi:10.1001/jamaophthalmol.2016.2507.
Author Contributions: Dr Seidel had full access to all of the data in the study and takes responsibility for the integrity of the data and the accuracy of the data analysis.
Study concept and design: Seidel, Aschinger, Schmetterer, Garhöfer.
Acquisition, analysis, or interpretation of data: All authors.
Drafting of the manuscript: Seidel.
Critical revision of the manuscript for important intellectual content: All authors.
Statistical analysis: Seidel, Herzog.
Administrative, technical, or material support: Seidel, Singer, Weger, Haas, Werkmeister, Schmetterer.
Study supervision: Seidel, Werkmeister, Garhöfer.
Conflict of Interest Disclosures: All authors have completed and submitted the ICMJE Form for Disclosure of Potential Conflicts of Interest and none were reported.
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