- Open Access
Comparing imaging capabilities of spectral domain and swept source optical coherence tomography angiography in healthy subjects and central serous retinopathy
Eye and Vision volume 5, Article number: 19 (2018)
There are two forms of system implementation of optical coherence tomography angiography (OCTA) in ophthalmic imaging, i.e., spectral domain (SD-) and swept source OCTA (SS-OCTA). The purpose of this paper is to compare the SD-OCTA and SS-OCTA for elucidating structural and vascular features associated with central serous retinopathy (CSR), and to evaluate the effects of CSR on SD- and SS-OCTA’s imaging capabilities.
Normal subjects and CSR patients were imaged by SD- and SS-OCTA using 3 × 3 mm and 6 × 6 mm scan patterns. OCT signal strengths at the superficial retina, deep retina, Sattler’s layer and Haller’s layer were used to compare the ability of SD- and SS-OCTA to image structural features. In addition, the ability to acquire angiograms were discussed by evaluating retinal vessel density. Central serous volume (CSV) was measured and it was correlated with difference in signal strengths (∆S) between two OCTA devices.
Seven normal eyes and seven diseased eyes were recruited. Results showed no significant differences between SD- and SS-OCT in detecting structural features of the retinal layer according to the paired t-test. However, when imaging the Sattler’s layer for normal eyes, a significant difference is found between SD- and SS-OCT (p < 0.0001 for 3 × 3 mm scan, and p = 0.0002 for 6 × 6 mm); while for CSR eyes, the corresponding values were p < 0.0001 and p = 0.0003, respectively. At Haller’s layer for normal eyes, the corresponding values were p = 0.0004 and p = 0.0014; and for CSR eyes, p = 0.0004 and p < 0.0001, respectively. A strong correlation between ∆S and CSV was observed in the Sattler’s layer (3 × 3 mm – p = 0.0031 and R2 = 0.951; 6 × 6 mm – p = 0.0075 and R2 = 0.911) and Haller’s layer (3 × 3 mm – p = 0.0026 and R2 = 0.955; 6 × 6 mm – p = 0.0013 and R2 = 0.972).
The results suggest no differences between SD- and SS-OCTA for imaging the retinal layers however, when imaging beyond retinal layers, SS-OCTA appears advantageous in detecting returning signals. In CSR cases, the CSV may have an impact on sub-CSR tissue imaging and appears to have more impact on SD- than SS-OCTA.
Central serous retinopathy (CSR), characterized by serous retinal detachment in the macular area, is an eye disease commonly found in young to middle-aged adults [1, 2]. Typically, the disease first presents itself through blurred or distorted vision caused by the accumulation of fluid resulting from retinal detachment. Currently, CSR diagnosis is commonly initiated through bio-microscopy and confirmed by fluorescein angiography (FA) however, the requirements for intravenously injected dye and the associated side-effects of such a dye have prompted the search for an alternative diagnostic technique. Additionally, while CSR can spontaneously resolve within several months without the need for treatment , a number of complications are known to occur alongside the disease such as bullous retinal detachment, retinal pigment epithelial atrophy and choroidal neovascularization (CNV) [4,5,6]. The ability to diagnose such cases becomes increasingly difficult in the presence of CSR because achieving good quality images is difficult for many conventional imaging modalities. Therefore, the need exists for a non-invasive imaging tool that can visualize both CSR and complications.
As a non-invasive, depth-resolved imaging technology [7, 8], optical coherence tomography (OCT) has already been successfully employed to elucidate the pathological features of CSR [9,10,11,12]. In addition to structural details, blood flow imaging is also interesting and necessary in some studies of CSR [13, 14], which can be performed using OCT-based angiography (OCTA), a new imaging extension of OCT that provides blood flow information via motion contrast created by moving red blood cells within active vessels [15,16,17]. While this technique has the potential to significantly improve our diagnostic capacity for CSR cases and others, it still has room for improvement. To further refine OCTA and its potential for clinical uses, various configurations and reiterations have been developed. A number of studies have been conducted to compare two of the most commonly used system designs, spectral domain (SD)- and swept source (SS)-OCTA, using various pathological features such as CNV [18, 19] and choroidal thickening [20,21,22]. Thus far, all have shown SS-OCTA to be the superior technology when imaging deep choroid due to its longer wavelength and better sensitivity roll-off [21, 23]. There are, however, no prior studies that we are aware of that has used CSR as a model for comparative purposes, nor any studies that have used signal strength as a comparative tool. CSR offers a particularly interesting case for comparing OCTA systems because central serous volume (CSV), a common feature of the disease, extends the optical path for penetrating light, making it more difficult to detect the returning signal from deep tissues. This characteristic makes it necessary to evaluate how CSR would affect both SD- and SS-OCTA when imaging deep retinal layers.
In this study, we conducted a comparison between SD- and SS-OCTA’s capability of providing structural and angiographic information. The metrics of OCT signal strength and vessel density obtained from CSR and normal subjects were used in the comparison. For CSR cases, CSV was calculated as a parameter to evaluate how the CSV, respectively, affects SD- and SS-OCTA’s capability when imaging beyond the retinal layers.
Patient enrollment and scanning protocol
Normal volunteers and CSR patients were recruited and imaged by both the SD- and SS-OCTA systems. The diagnosis of CSR was defined as an idiopathic detachment of the neurosensory retina on slit-lamp observation secondary to one or more focal leaks at the level of the retinal pigment epithelium (RPE) layer on FA. An initial scan size of 3 × 3 mm was used to provide optimal scanning parameters however, given the varying sizes of CSR lesions, 3 × 3 mm scans could not cover the whole lesion therefore, an additional scan pattern of 6 × 6 mm was used. For continuity, both devices were used at the same visit for each subject. This study was conducted under an investigational clinical study approved by the Institutional Review Board of the University of Washington, and informed consent was obtained from each subject prior to imaging. The study followed the tenets of the Declaration of Helsinki and was in compliance with the Health Insurance Portability and Accountability Act.
SD-OCTA was performed using a commercially available AngioPlex instrument (Carl Zeiss Meditec Inc., Dublin, USA) that employed a light source with a central wavelength of 840 nm and a bandwidth of 45 nm. The imaging speed was 68 kHz A-line rate, axial resolution was ~ 5 μm in tissue and lateral resolution was ~ 15 μm. Two scanning patterns were used to collect the OCT structure and angiogram: 3 × 3 mm and 6 × 6 mm. For the 3 × 3 mm scans, 245 A-lines produced one B-scan, and B-scans were acquired at 245 different spatial locations and repeated four times at each location. This scanning protocol resulted in a uniform spacing of 12.2 μm between pixels in the final en face projected OCTA images. For the 6 × 6 mm scans, 350 A-lines produced one B-scan, and B-scans were acquired at 350 different spatial locations and repeated two times at each location, resulting in a uniform spacing of 17.1 μm between pixels in the final en face projected OCTA images.
SS-OCTA data were acquired using a PlexElite 9000 device (Carl Zeiss Meditec Inc., Dublin, USA), which had a central wavelength of ~ 1050 nm, a bandwidth of 100 nm, and a 100 kHz A-line rate. Axial resolution was ~ 5 μm in tissue while lateral resolution was ~ 14 μm. Again, two scanning patterns were used to image subjects. For the 3 × 3 mm scan, a 300 × 300 pixel-array was used (10 μm spacing between pixels), while the 6 × 6 mm scan used a 500 × 500 pixel-array (12 μm). The repetition strategy was the same as that used for SD-OCTA: four repetitions in 3 mm × 3 mm scans and two repetitions in 6 × 6 mm scans. Both SD-OCTA and SS-OCTA datasets were processed using the complex optical microangiography (OMAG) algorithm [24,25,26,27] to generate angiograms.
Normalization and segmentation
Since the OCT reflectance signal is dependent on how much energy is impinging on the tissue surface, it requires normalizing OCT scans acquired from both systems to make a fair comparison. In this study, the SD- and SS-OCTA data from a single subject was normalized, in which we assumed that the retinal tissue was irradiated with the same total light energy of unity for both the SD- and SS-OCT. Assuming the light absorption is negligible we then may approximate the total light energy by summing all the backscattered light (i.e. OCT signals) from the scanned tissue volume, Ssum. Thus, the normalized OCT signal, Snorm(x,y,z), can be expressed as:
where Sm(x,y,z) is the measured voxel signal located at (x,y,z) position within the 3D OCT scan.
To evaluate and compare the ability of the system to detect signal at different depths, depth resolved layers in the retina and choroid were segmented by a semi-automatic segmentation software  (Fig. 1). Here, the retinal layer is defined as the region from the inner limiting membrane (ILM) to the outer plexiform layer (OPL). Superficial retinal layer is defined as the region from the ILM to the inner plexiform layer (IPL) inclusive. Deep retinal layer is defined as the region from the inner nuclear layer (INL) to the OPL inclusive, and the outer retinal space is defined as the region from the OPL to Bruch’s membrane (BM). Sattler’s and Haller’s layers are defined as medium- and larger-sized vessel layers, respectively [29, 30]. However, automatic segmentation of Sattler’s and Haller’s layers may lead to failure of the comparison in our study because there is no evidence that automatic segmentation would give the same results between SD- and SS-OCTA. Instead, fixed thickness was used to manually segment Sattler’s and Haller’s layers considering the published thickness results [29, 30] (Fig. 1). The CSV is defined as the region from the photoreceptor inner segment and outer segment layers (IS/OS) to the RPE.
Signal strength calculations
Signal strength of structural images in different depths were calculated to compare the abilities of structural imaging between SD- and SS-OCTA. For each of the eyes scanned, both the 3 × 3 mm and 6 × 6 mm scans from the SD-OCTA and SS-OCTA were analyzed. Four layers (superficial and deep retinal layers, Sattler’s and Haller’s layers) were segmented, as mentioned above. The signal strength of each layer was defined using Eq. (2):
where Ssd and Sss represent the signal strength of each layer from SD- and SS-OCT, respectively. Slayer_sum is the summation of all backscattered signal within each layer and Nlayer_voxel represents the number of voxels in that layer.
Retinal layer vessel density measurements
In addition to structure-based signal strength comparison, angiographic capacities were compared between SD- and SS-OCTA in the retinal layer. For retinal layer, maximum intensity projection en face images were used for vessel density measurements; both the 3 × 3 mm and 6 × 6 mm scans from SD- and SS-OCTA were analyzed. Registration between SD- (Fig. 2a) and SS-OCTA (Fig. 2b) angiograms was carried out prior to the comparison, resulting in an identical circular region centered on the central fovea (Fig. 2c and Fig. 2d). From this circular region, vessel density was calculated through vessel binarization and excluding the foveal avascular zone .
Signal strength difference and CSR volume measurements
To investigate how CSR affects the imaging capability of SD- and SS-OCTA, both the 3 × 3 mm and 6 × 6 mm scans from SD- and SS-OCTA were analyzed. Firstly, SD- and SS-OCT signal strength differences, ∆S, were defined in each layer using Eq. (3):
CSV measurements were acquired separately based on the 3 × 3 mm and 6 × 6 mm scans. CSR region was manually segmented on every OCT B-scan as mentioned in section “Normalization and segmentation”. CSV was then achieved by calculating the segmented 3D volume.
Paired sample t-tests  were performed to detect differences in signal strength and vessel density between SD- and SS-OCTA for all groups (including 3 × 3 mm and 6 × 6 mm scans on SD- and SS-OCTA imaging, normal and CSR eyes). Linear regression  and Bland-Altman analyses [34,35,36,37] were performed to investigate the correlation between SD- and SS-OCTA on CSV measurement (including 3 × 3 mm and 6 × 6 mm scans). Linear regression was also performed to evaluate the relationship between ∆S and CSV measurements. P values below 0.05 were considered statistically significant.
Seven eyes (OS: 4/7) from 5 CSR patients (Male: 2/5) and 7 normal eyes (OS: 4/7) from 7 volunteers (Male: 3/7) were imaged at the University of Washington Eye Institute from June 2016 to September 2017. Mean patient age was 60.5 years and ranged from 56 to 65 years.
Structural signal strength comparisons
Both SD- and SS-OCT systems display similar signal strength values in the deep retina layer of both normal and CSR eyes. However, a significant difference becomes apparent in the Sattler’s layer of both normal eyes (paired t-test, p < 0.0001 for 3 × 3 mm scans, and p = 0.0002 for 6 × 6 mm scans) and CSR eyes (paired t-test, p < 0.0001 for 3 × 3 mm scans, and p = 0.0003 for 6 × 6 mm scans). This trend continues in the Haller’s layer of normal eyes (paired t-test, p = 0.0004 for 3 × 3 mm scans, and p = 0.0014 for 6 × 6 mm scans) and CSR eyes (paired t-test, p = 0.0004 for 3 × 3 mm scans, and p < 0.0001 for 6 × 6 mm scans), as shown in Fig. 3.
Angiographic capacity comparisons
Table 1 summarizes the measurements of retinal layer vessel density obtained by SD- and SS-OCTA, respectively. No significant differences were detected between either system for normal eyes (paired t-test, p = 0.33 for 3 × 3 mm scans, and p = 0.14 for 6 × 6 mm scans) and CSR eyes (paired t-test, p = 0.08 for 3 × 3 mm scans, and p = 0.15 for 6 × 6 mm scans).
Relationship between ∆S and CSV
The CSV measurements show a significant correlation between SD- and SS-OCTA (linear regression analysis, p < 0.001 and R2 = 0.995 for 3 × 3 mm scans; p < 0.001 and R2 = 0.999 for 6 × 6 mm scans, Fig. 4a and b). Bland-Altman analysis shows there is a data point (highlighted with dashed square) exceeding the 95% limits of agreement (bottom dashed line, Fig. 4c). In this case, CSR volume is so substantial that a field of view (FOV) of 3 × 3 mm was insufficient to cover the entire CSR area while for 6 x 6 mm scans, the FOV is large enough to cover the entire CSR volume. The mean difference between SS- and SD-OCT measurements was just 0.0009 mm3 (Fig. 4d).
Linear regression analysis was carried out between ∆S and CSV measurements (Fig. 5). In the deep retina layer, p = 0.340 and R2 = 0.065 for 3 × 3 mm scans, and p = 0.388 and R2 = 0.003 for 6 x 6 mm scans, indicating there is no correlation. ∆S of the Sattler’s and Haller’s layers, however, both show strong correlations with CSV measurements. In the Sattler’s layer, p = 0.0031 and R2 = 0.951 for 3 × 3 mm scans, and p = 0.0075 and R2 = 0.911 for 6 x 6 mm scans. In the Haller’s layer, p = 0.0026 and R2 = 0.955 for 3 × 3 mm scans, and p = 0.0013 and R2 = 0.972 for 6 x 6 mm scans. In the deep layers beneath the CSR area, ∆S linearly increases as CSV increases.
As a noninvasive technique, OCT is capable of generating in vivo cross-sectional volumetric images of anatomical structures with microscopic resolution (< 15 μm) in real-time, and it has been verified useful for our understanding of disease pathogenesis as well as clinical diagnosis and management of various ocular diseases [38,39,40,41]. Now, SD-OCT is already commercially available and has been widely used for quantitative examination of pathological eyes in patients  however, the short wavelength of light used by such a device reduces its light penetration into deep tissue, subsequently reducing its ability to accurately evaluate deep tissue. To overcome such a limitation, enhanced depth imaging (EDI)-OCT  was introduced to visualize the structural information within cross-sectional images representing regions below the RPE layer. Yet, current EDI-OCT only provides cross-sectional scans and averaging is often carried out on many repeated single-location B-frames by setting the choroid adjacent to the zero-delay line where the system has maximal sensitivity. These limitations make 3D scanning difficult. More recently, SS-OCT devices are becoming popular as they have shown to improve the visualization of structure and flow due to an improved sensitivity roll-off and attenuation of OCT signal from deeper tissues. A number of prior studies were designed to compare SD- with SS-OCT for use in assessing ophthalmologic parameters [20,21,22, 44]. One study demonstrated that the choroidoscleral interface can be clearly visualized in 19/19 (100%) of eyes imaged by SS-OCT, compared to 14/19 (73.6%) and 13/19 (68.4%) eyes imaged by SD-OCT, with and without EDI, respectively . In another study by Matsuo et al., SS-OCT was shown to measure a thicker sub-foveal choroid than that measured by SD-OCT instruments on normal eyes (273.2 μm by Spectralis-SD-OCT, 269.1 μm by Topcon-SD-OCT and 280.5 μm by DRI-SS-OCT) . As a further development to OCT technology, OCTA was introduced to the field of clinical ophthalmology, which can provide blood flow information via motion contrast algorithm. It utilizes the flowing red blood cells as an intrinsic contrast agent to generate blood flow signals thereby allowing the visualization of functional vascular networks without the need for a dye injection. Several studies were also conducted to compare SD- and SS-OCTA on vessel imaging e.g. the CNV quantification [18, 19]. The results revealed that SS-OCTA measured significantly larger CNV sizes than SD-OCTA. Considering these studies, SS-OCTA did appear to encourage improved light penetration into deeper tissues, which in turn resulted in improved OCT/OCTA signal detection. This was thought to be attributed to several factors. Firstly, SS-OCTA operates at a longer wavelength, ~ 1050 nm, compared with SD-OCTA, ~ 840 nm, which allows more light to penetrate deeper tissue due to the reduced scattering properties of tissue. Secondly, a balanced detector was used within the SS-OCTA system instead of the charge-coupled device (CCD) camera used in the SD-OCTA system, giving a higher signal to noise ratio (SNR). Furthermore, the narrow linewidth of swept-laser source corresponds to a relatively longer coherence length, leaving SS-OCTA with a delayed sensitivity roll-off thus boosting the detection of the signals from deep regions when compared with SD-OCTA. Taken together, SS-OCTA is advantageous over SD-OCTA when acquiring structural and flow information from deeper tissues.
CSR is characterized by an acute or chronic form of retinal disorder, which involves a detachment of the neurosensory retina secondary to one or more focal fluorescein angiographic leaks at the level of the RPE layer. Although acute CSR can sometimes recur, it generally resolves spontaneously with minimal sequelae. However, chronic CSR can result in widespread RPE damage. These patients have longstanding subretinal fluid that cannot be absorbed efficiently because of choroidal dysfunction and loss of RPE. The presence of fluid leads to photoreceptor death and may result in a series of complications in deep region e.g. the CNV. Considering that central serous bump further extends the depth of the lesion, CSR can be a potential disease group that could benefit from improved deep tissue imaging. Thus, comparisons between SD- and SS-OCTA using structural and angiographic features associated with CSR were addressed in this study. The results of signal strength comparisons suggest that there is no significant difference between either OCT method in terms of information quality when imaging superficial tissues, however, SS-OCTA can detect more structural signals from deep tissue compared to SD-OCTA either in normal subjects or CSR patients. In CSR patients, we further evaluated how the CSV affects SD- and SS-OCTA’s imaging abilities. Our data has revealed that said advantages, ∆S, of using SS-OCTA over SD-OCTA linearly increases with the increase of CSV, meaning the limiting influences of the central serous bump are more detrimental when using SD-OCTA. This is an important conclusion. Thus, SS-OCTA may be recommended for accurate diagnosis of CSR patients, especially in big CSV cases.
There are still a few limitations in our study. Although our sample size is small, we find it to be acceptable because signal strength was shown to be a robust parameter when comparing SD- and SS-OCTA. The results gave a clear conclusion that SS-OCTA detected a stronger structural signal strength in deep choroid compared to SD-OCTA, suggesting that SS-OCTA has an advantage over SD-OCTA on angiographic imaging in deep layers. Yet, a larger sample size is necessary if the study is required to compare signals beyond the RPE layer e.g. in the choriocapillaris [45,46,47,48]. In addition, the sample resolutions of 3 × 3 mm and 6 × 6 mm scanning protocols are different and unchangeable between SD- and SS-OCTA due to the highly integrated systems used in our study, which might have an impact on the final image quality, but it is unclear how differences in sample resolution might have an effect on the results.
In the present study, signal strength has been shown to be a robust parameter when comparing SD- and SS-OCTA, based on evidence that SS-OCTA is able to improve deep tissue imaging compared to SD-OCTA, especially when CSR is present. The possible clinical advantage of SS-OCTA in terms of diagnosis and disease monitoring should be reviewed in further studies with a large sample size and comprising various retinal and choroidal diseases.
Maia A. A new treatment for chronic central serous retinopathy. Retina Today. 2010;1:62–4.
Nicholson B, Noble J, Forooghian F, Meyerle C. Central serous chorioretinopathy: update on pathophysiology and treatment. Surv Ophthalmol. 2013;58(2):103–26.
Gass JD. Pathogenesis of disciform detachment of the neuroepithelium. Am J Ophthalmol. 1967;63(3):Suppl:1–139.
Gass JD, Little H. Bilateral bullous exudative retinal detachment complicating idiopathic central serous chorioretinopathy during systemic corticosteroid therapy. Ophthalmology. 1995;102(5):737–47.
Yannuzzi LA, Shakin JL, Fisher YL, Altomonte MA. Peripheral retinal detachments and retinal pigment epithelial atrophic tracts secondary to central serous pigment epitheliopathy. Ophthalmology. 1984;91(12):1554–72.
Chan WM, Lai TY, Liu DT, Lam DS. Intravitreal bevacizumab (avastin) for choroidal neovascularization secondary to central serous chorioretinopathy, secondary to punctate inner choroidopathy, or of idiopathic origin. Am J Ophthalmol. 2007;143(6):977–83.
Huang D, Swanson EA, Lin CP, Schuman JS, Stinson WG, Chang W, et al. Optical coherence tomography. Science. 1991;254(5035):1178–81.
Tomlins PH, Wang RK. Theory, developments and applications of optical coherence tomography. J Phys D-Appl Phys. 2005;38:2519–35.
Hee MR, Puliafito CA, Wong C, Reichel E, Duker JS, Schuman JS, et al. Optical coherence tomography of central serous chorioretinopathy. Am J Ophthalmol. 1995;120(1):65–74.
Montero JA, Ruiz-Moreno JM. Optical coherence tomography characterisation of idiopathic central serous chorioretinopathy. Br J Ophthalmol. 2005;89(5):562–4.
Yang L, Jonas JB, Wei W. Optical coherence tomography–assisted enhanced depth imaging of central serous chorioretinopathy. Invest Ophthalmol Vis Sci. 2013;54(7):4659–65.
Imamura Y, Fujiwara T, Margolis R, Spaide RF. Enhanced depth imaging optical coherence tomography of the choroid in central serous chorioretinopathy. Retina. 2009;29(10):1469–73.
Bonini Filho MA, de Carlo TE, Ferrara D, Adhi M, Baumal CR, Witkin AJ, et al. Association of Choroidal Neovascularization and Central Serous Chorioretinopathy with Optical Coherence Tomography Angiography. JAMA Ophthalmol. 2015;133(8):899–906.
Costanzo E, Cohen SY, Miere A, Querques G, Capuano V, Semoun O, et al. Optical coherence tomography angiography in central serous chorioretinopathy. J Ophthalmol. 2015;2015:134783.
An L, Wang RK. In vivo volumetric imaging of vascular perfusion within human retina and choroids with optical micro-angiography. Opt Express. 2008;16(15):11438–52.
Spaide RF, Fujimoto JG, Waheed NK. Optical coherence tomography angiography. Retina. 2015;35(11):2161–2.
Chen CL, Wang RK. Optical coherence tomography based angiography [invited]. Biomed Opt Express. 2017;8(2):1056–82.
Zhang Q, Chen CL, Chu Z, Zheng F, Miller A, Roisman L. Automated quantitation of choroidal neovascularization: a comparison study between spectral-domain and swept-source OCT angiograms. Invest Ophthalmol Vis Sci. 2017;58(3):1506–13.
Novais EA, Adhi M, Moult EM, Louzada RN, Cole ED, Husvogt L, et al. Choroidal neovascularization analyzed on ultrahigh-speed swept-source optical coherence tomography angiography compared to spectral-domain optical coherence tomography angiography. Am J Ophthalmol. 2016;164:80–8.
Tan CS, Ngo WK, Cheong KX. Comparison of choroidal thicknesses using swept source and spectral domain optical coherence tomography in diseased and normal eyes. Br J Ophthalmol. 2015;99(3):354–8.
Adhi M, Liu JJ, Qavi AH, Grulkowski I, Lu CD, Mohler KJ, et al. Choroidal analysis in healthy eyes using swept-source optical coherence tomography compared to spectral domain optical coherence tomography. Am J Ophthalmol. 2014;157(6):1272–81.
Ting DS, Cheung GC, Lim LS, Yeo IY. Comparison of swept source optical coherence tomography and spectral domain optical coherence tomography in polypoidal choroidal vasculopath. Clin Exp Ophthalmol. 2015;43(9):815–9.
Xu J, Song S, Wei W, Wang RK. Wide field and highly sensitive angiography based on optical coherence tomography with akinetic swept source. Biomed Opt Express. 2016;8(1):420–35.
Huang Y, Zhang Q, Thorell MR, An L, Durbin MK, Laron M, et al. Swept-source OCT angiography of the retinal vasculature using intensity differentiation-based optical microangiography algorithms. Ophthalmic Surg Lasers Imaging Retina. 2014;45(5):382–9.
An L, Subhush HM, Wilson DJ, Wang RK. High-resolution wide-field imaging of retinal and choroidal blood perfusion with optical microangiography. J Biomed Opt. 2010;15(2):026011.
Zhang A, Zhang Q, Wang RK. Minimizing projection artifacts for accurate presentation of choroidal neovascularization in OCT micro-angiography. Biomed Opt Express. 2015;6(10):4130–43.
Wang RK, An L, Francis P, Wilson DJ. Depth-resolved imaging of capillary networks in retina and choroid using ultrahigh sensitive optical microangiography. Opt Lett. 2010;35(9):1467–9.
Yin X, Chao JR, Wang RK. User-guided segmentation for volumetric retinal optical coherence tomography images. J Biomed Opt. 2014;19(8):086020.
Esmaeelpour M, Kajic V, Zabihian B, Othara R, Ansari-Shahrezaei S, Kellner L, et al. Choroidal Haller’s and Sattler’s layer thickness measurement using 3-dimensional 1060-nm optical coherence tomography. PLoS One. 2014;9(6):e99690.
Esmaeelpour M, Ansari-Shahrezaei S, Glittenberg C, Nemetz S, Kraus MF, Hornegger J, et al. Choroid, Haller’s, and Sattler’s layer thickness in intermediate age-related macular degeneration with and without fellow neovascular eyes. Invest Ophthalmol Vis Sci. 2014;55(8):5074–80.
Chu Z, Lin J, Gao C, Xin C, Zhang Q, Chen CL, et al. Quantitative assessment of the retinal microvasculature using optical coherence tomography angiography. J Biomed Opt. 2016;21(6):66008.
Hsu H, Lachenbruch PA. Paired t test. In: D'Agostino RB, Sullivan L, Massaro J, editors. Wiley encyclopedia of clinical trials. Hoboken: John Wiley & Sons, Inc.; 2008. p. 1–3.
Bartlett RF. Linear Modelling of Pearson’s product moment correlation coefficient: an application of Fisher’s z-transformation. J R Stat Soc. 1993;42(1):45–53.
Bland JM, Altman DG. Measuring agreement in method comparison studies. Stat Methods Med Res. 1999;8(2):135–60.
Bland JM, Altman DG. Statistical methods for assessing agreement between two methods of clinical measurement. Lancet. 1986;1(8476):307–10.
Altman DG, Bland JM. Measurement in medicine: the analysis of method comparison studies. J R Stat Soc. 1983;32(3):307–17.
Giavarina D. Understanding bland Altman analysis. Biochem Medica. 2015;25(2):141–51.
Leung CK. Diagnosing glaucoma progression with optical coherence tomography. Curr Opin Ophthalmol. 2014;25(2):104–11.
Sakata LM, Deleon-Ortega J, Sakata V, Girkin CA. Optical coherence tomography of the retina and optic nerve - a review. Clin Exp Ophthalmol. 2009;37(1):90–9.
Costa RA, Skaf M, Melo LA Jr, Calucci D, Cardillo JA, Castro JC, et al. Retinal assessment using optical coherence tomography. Prog Retin Eye Res. 2006;25(3):325–53.
Caroline CR. Clinical applications of optical coherence tomography. Curr Opin Ophthalmol. 1999;10(3):182–8.
Yi K, Mujat M, Park BH, Sun W, Miller JW, Seddon JM, et al. Spectral domain optical coherence tomography for quantitative evaluation of drusen and associated structural changes in non-neovascular age-related macular degeneration. Br J Ophthalmol. 2009;93(2):176–81.
Spaide RF, Koizumi H, Pozonni MC. Enhanced depth imaging spectral-domain optical coherence tomography. Am J Ophthalmol. 2008;146(4):496–500.
Matsuo Y, Sakamoto T, Yamashita T, Tomita M, Shirasawa M, Terasaki H. Comparisons of choroidal thickness of normal eyes obtained by two different spectral-domain OCT instruments and one swept-source OCT instrument. Invest Ophthalmol Vis Sci. 2013;54(12):7630–6.
Lauermann JL, Eter N, Alten F. Optical coherence tomography angiography offers new insights into choriocapillaris perfusion ophthalmologica. Ophthalmologica. 2018;239(2–3):74–84.
Alten F, Heiduschka P, Clemens CR, Eter N. Exploring choriocapillaris under reticular pseudodrusen using OCT-angiography. Graefes Arch Clin Exp Ophthalmol. 2016;254(11):2165–73.
Zhang Q, Zheng F, Motulsky EH, Gregori G, Chu Z, Chen CL, et al. A novel strategy for quantifying choriocapillaris flow voids using swept-source OCT angiography. Invest Ophthalmol Vis Sci. 2018;59(1):203–11.
Ahn J, Yoo G, Kim JT, Kim SW, Oh J. Choriocapillaris layer imaging with swept-source optical coherence tomography angiography in lamellar and full-thickness macular hole. Graefes Arch Clin Exp Ophthalmol. 2018;256(1):11–21.
This study was supported in part by the National Institutes of Health (R01EY024158 and R01EY028753), WRF David and Nancy Auth Innovation Award, and an unrestricted fund from Research to Prevent Blindness. The funding organizations had no role in the design or conduct of this research.
Ethics approval and consent to participate
This study was conducted under a protocol approved by the University of Washington’s Institutional Review Board.
Dr. RK Wang discloses intellectual property owned by the Oregon Health and Science University and the University of Washington related to OCT angiography, and licensed to commercial entities, related to the technology and analysis methods described in parts of this manuscript. The authors declare that they have no competing interests.
About this article
- Optical coherence tomography
- Spectral domain OCTA
- Swept source OCTA
- Central serous retinopathy
- Signal strength
- Central serous volume