Ординатура / Офтальмология / Учебные материалы / Retinal Vascular Disease Joussen Springer
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8 I
I Pathogenesis of Retinal Vascular Disease
8.2MRI Studies of Blood-Retinal Barrier: New Potential for Translation of Animal Results to Human Application
B.A. Berkowitz
Core Messages
Blood-retinal barrier breakdown can contribute to abnormal accumulation of water in the retina
Traditional methods for clinical evaluation of macular edema include fluorescein angiography, optical coherence tomography, and vitreous fluorophotometry
Dynamic contrast enhanced MRI (DCE-MRI) with gadolinium diethylenetriaminepentaace-
tic acid (Gd-DTPA) allows for in vivo quantitative measurement of blood-retinal barrier breakdown
DCE-MRI was assessed in a variety of experimental and clinical conditions (e.g., focal retinal photocoagulation, endophthalmitis, diabetic retinopathy)
DCE-MRI allows for an exact determination of blood-retinal breakdown
8.2.1 Introduction
Abnormal accumulation of water in the retina (i.e., retinal edema) is commonly associated with retinal vessel diseases such as diabetes. Edema that develops in the macula secondary to diabetes is often linked with major visual loss [21]. However, despite decades of study, current treatment options for retinal edema remain limited to, primarily, laser photocoagulation. However, photocoagulation is destructive, does not restore lost vision, and is helpful in only about 50 % of the patients [1]. Better appreciation of the underlying pathophysiology associated with edema formation is likely to improve diagnosis and medical care for retinal edema. Currently it is understood that fluid buildup in the retina can develop in intracellular and/or extracellular compartments. The blood-retinal barrier (BRB) refers to tight cell-cell junctions of the retinal vascular endothelium (also known as inner BRB) as well as tight junctions of the retinal pigment epithelium (or outer BRB). Intracellular edema (or cytotoxic edema) is defined as cellular swelling that occurs without opening of the BRB. Extracellular (or vasogenic) edema is characterized by retinal thickening in association with loss of BRB integrity [35]. Consequently, the development of optimal strategies for treating retinal edema may depend on determining the ratio of the contribution of intraand extracellular mechanisms to edema and measuring how this ratio changes between patients, between different retinopathies, and during disease progression [32].
Traditional methods for evaluating the efficacy of medical therapy for retinal edema or deciding on endpoints for therapeutic intervention (e.g., visual acuity and seven-field stereoscopic fundus photography) detect only gross changes that occur late in the course of the disease. With these endpoints, studies require large numbers of patients with many years of follow-up before evidence-based conclusions can be drawn [35]. Fluorescein angiography (FA), an essential tool in the current clinical diagnosis and management of retinal diseases, is a rapid and straightforward photographic technique that allows localization of fluorescein leakage due to BRB breakdown, but cannot quantify BRB damage in physiologic terms, such as the permeability surface area product (PS). In other words, only subjective determination of the magnitude of BRB damage is possible with FA and this prevents analytic staging of treatment efficacies (using, for example, BRB PS) within and between patients over time. Furthermore, as a tracer, fluorescein is far from ideal because, among other variables, it is bound to serum protein, has a complex pharmacokinetic profile that complicates evaluating the fluorescein concentration plasma integral, is metabolized to different fluores- cein-based metabolites which can confound interpretation, and enters the vitreous through a passive mechanism but is actively removed from vitreous to choroid [49, 50, 51]. Importantly, the location of BRB damage, as measured by FA, is not always linked with regions of edema [37]. For these reasons, FA remains
8.2 MRI Studies of Blood-Retinal Barrier: New Potential for Translation of Animal Results to Human Application 155
a suboptimal approach for quantitatively evaluating new or existing treatment responses. Alternatively, retinal fluid buildup in either intraor extracellular compartments can produce an increase in retinal thickness that is measurable using analytic techniques such as ocular coherence tomography (OCT). Because it only measures retinal thickness, OCT is unable to determine whether the type of edema is intraor extracellular [32]. In addition, interrogating the exact same retinal region during repeated exams using clinically available OCT machines can be difficult. This registration problem may limit the accuracy and applicability of OCT measurement of longitudinal changes in retinal thickness. Therefore, while the methods mentioned have a proven usefulness in the clinic, they are also somewhat limited in their diagnostic and prognostic applicability.
Vitreous fluorophotometry (VFP), a fluoresceinbased method, was developed to address some of these concerns [12]. Unlike FA, which presents a twodimensional map of fluorescence across the retina, but not fluorescein concentrations, VFP measures a one-dimensional spatial profile of fluorescein concentration in the vitreous that can be used to quantitate BRB damage. However, VFP is not widely avail-
able, it cannot be performed in the presence of opti-
cal opacities (such as cataract), its interpretation can I 8 be confounded by changes in vitreous fluidity, and it suffers from the problems associated with fluoresce-
in that are listed above [35, 50, 51]. Additionally, data must be carefully collected to take into account the influence of the potentially confounding variables associated with the use of fluorescein that can confound physiologic interpretation of the VFP data.
8.2.2 Magnetic Resonance Imaging
Magnetic resonance imaging (MRI) provides a panretinal measure of ocular anatomy from inferior to superior (or nasal to temporal) ora serrata and is not dependent upon the clarity of the ocular media. Therefore, optical distortions such as diabetic cataracts do not degrade MRI images. MRI has been successfully adapted to laboratory animal, as well as human, subjects, making it possible to conduct translational research between humans and a wide range of species including mice and rats (Fig. 8.2.1). In the mid to late 1980s, proof-of-concept principle with this technique was achieved in studies of mon-
Fig. 8.2.1. Representative high resolution images [in-plane resolution is 0.39×0.39 mm2 (human) and 23.4 μm2 (rat and mouse)] measured from a single slice (white line, upper images) in humans (left panels) and rodents (right panels). Note that the rodent images are scaled differently than the human images and that the dissimilar appearance of the lens in the human and rat images is due to the different pulse sequences used. The white line in the posterior region of the eye represents the retina/choroid complex (white arrow). Acquisition of artifact-free high resolution images in both clinical and preclinical settings highlights the ability of MRI to be used to conduct translational research between humans and other species including rats and mice, as well as other species
156 I Pathogenesis of Retinal Vascular Disease
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keys and rabbits where damage to the blood ocular barriers was quantified using a non-fluorescein based method: dynamic contrast enhanced MRI (DCE-MRI) with gadolinium diethylenetriaminepentaacetic acid (Gd-DTPA, 590 Da) [22, 48]. In this experiment, Gd-DTPA, also known as Gad, was injected intravenously and delivered by the blood supply to the retina (Fig. 8.2.2). Gd-DTPA is a relatively safe tracer to administer intravenously, has a plasma half-life of about 1.5 h, and, unlike fluorescein, Gad does not cause yellowing of the skin and urine [53, 54]. In addition, Gd-DTPA is freely diffusible (i.e., is a non-specific extracellular marker) and follows a well defined biexponential plasma decay (i.e., it is not bound to plasma protein and is excreted mainly by the kidneys) [53, 54]. Note that gadolini-
um can also be bound to larger molecules, such as albumin, if necessary [59] and that gadoliniumbased contrast agents are paramagnetic. Normally, Gd-DTPA does not penetrate non-fenestrated blood vessels or barriers, such as in the inner and outer BRB; thus the vitreous space remains unenhanced (Fig. 8.2.2) [8, 72]. However, when BRB becomes damaged, Gd-DTPA enters into the vitreous space via a passive diffusion mechanism. Gd-DPTA shortens the vitreous water spin-lattice (T1) relaxation time such that by collecting a T1 weighted image, the presence of Gd-DTPA can be readily detected as an increase (i.e., an enhancement) in signal intensity (Fig. 8.2.3). Alternatively, vitreous T1 can be measured but this is usually a relatively longer procedure than simply collecting a T1 weighted image. Another
8.2 MRI Studies of Blood-Retinal Barrier: New Potential for Translation of Animal Results to Human Application 157
I 8
Fig. 8.2.4. Top row: Photographs of pigment rabbit fundus 2 days after argon laser panretinal photocoagulation procedure. Rabbit eyes were treated with the laser power set as indicated below each fundus photograph [8]. These photographs were obtained just prior to MRI examination. Left panel: Representative real-time, T1-weighted, coronal proton images acquired during before (left image) and post (right image) contrast injection. In this animal, both eyes were treated with a similar panretinal photocoagulation procedure, except the laser powers were different between OS and OD, as indicated [8]. Note that the signal intensity change in the anterior chamber is similar for each eye. This is used as an internal check of the goodness of the intravenous injection. Right panel: Representative time course of the mean vitreous signal intensity from OS (solid squares) and OD (solid circles) of the animal in the left panel. Linear analysis of the first 20 min post Gd-DTPA injection is presented as solid lines [8]. The resulting slope was called the leakiness parameter since it reflects the amount of Gd-DTPA entering the vitreous space through the disrupted retina
approach, the quantification of increased intraretinal Gd-DTPA concentration, is considerably more difficult because at low spatial resolution plasma based-GD-DTPA cannot be easily distinguished from retinal tissue-only Gd-DTPA. Thus, most efforts have investigated changes in vitreous signal intensity following Gd-DTPA injection. Berkowitz et al. validated the use of DCE-MRI to sensitively and accurately measure BRB PS in rabbits and humans [8 – 10, 61, 62, 71]. In rabbits, grid photocoagulation was applied to inferior retina at different power levels (200, 400, 600, and 800 mW) producing progressively larger disruption of BRB that could be readily detected using DCE-MRI (Fig. 8.2.4) [8]. Vitreous signal intensities were measured at each time point and the initial change in signal intensity with time analyzed to produce a slope (Fig. 8.2.4) that could be interpreted as a measure of BRB “leakiness” and was correlated with laser power (Fig. 8.2.5) [8]. In humans, retinas of patients with proliferative diabetic retinopathy were examined by both FA and DCEMRI [71]. As shown in Fig. 8.2.6, the location and severity of enhancement, judged by visual inspection
of the images, corresponded to the fluorescein angiographic and/or clinical appearance of preretinal neovascularization.
Studies in the early 1990s demonstrated that the increase in vitreous signal intensity was linearly related to Gd-DTPA concentration (Fig. 8.2.3) [8, 9]. Knowing the Gd-DTPA vitreous level and the Gd-DTPA plasma concentration time course allows one to determine the extent of the leak in the retina, or, in other words, BRB PS [8, 9]. To calculate PS, the Simplified Early Enhancement method of Tofts and Berkowitz was used [9, 61]. This method requires estimates of the vitreous T1 in the absence of Gd-DTPA (T10), the relaxivity of Gd-DTPA (R1, s–1 mM–1), and the Gd-DTPA concentration plasma time course parameters [9, 61]. Vitreous T10 was previously reported to be approximately 3.5 s. This value has been verified in control rodents using a homogenous excitation and surface coil reception while collecting gradient recalled echo images at different flip angles. As expected for a T10 of approximately 3.5 s, a maximum vitreous signal intensity was found at a flip angle of 12°–13° (based on the
158 I Pathogenesis of Retinal Vascular Disease
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Fig. 8.2.5. Top graph: The relationship between the leakiness parameter (defined in Fig. 8.2.4) and the laser power setting described in Fig. 8.2.4 for the vitreous. Note that a similar analysis of signal intensity changes in the anterior chamber was also performed (not shown) and no discernible correlation was found [8]. Bottom graph: In a separate experiment we developed and applied the theory of converting the leakiness parameter into a measure of BRB PS. The accuracy and precision of this approach was investigated in rabbits pretreated with sodium iodate (30 mg/kg intravenously) and summarized here [9]. The MRI-derived PS normalized to the area of leaky retina (PS’) was compared to a similarly normalized PS calculated using a classical physiologic method and agreement was found between the two methods (P > 0.05). Furthermore, PS’ values in eyes with normal vitreous were not different (P > 0.05) compared with that from contralateral gas-compressed vitrectomized eyes (data not shown) [10]
Ernst angle formula, data not shown) [47]. GdDTPA relaxivity is constant at a set temperature and field strength and so the previously reported value of 4.5 s/mM was used [9]. To determine the pharmacokinetic parameters after a bolus of Gd-DTPA in rats, blood samples were obtained in separate experiments in heparinized tubes during the precontrast period, and 1, 3, 7, 15, 30, and 60 min postinjection. Following centrifugation, the plasma fraction was obtained for NMR analysis. Inversion recovery T1 experiments were performed on the water signal of the plasma fraction at room temperature. From the T1 value, the amount and thus concentration of Gd-DTPA was determined from a cali-
Fig. 8.2.6. Representative comparison of FA and DCE-MRI localization of BRB damage. Top panel: Early and late FA of a 41- year-old man with a 22-year history of insulin dependent diabetes (20/20 OD, 20/20 OS) and no history of photocoagulation. Bottom panel: Preand postcontrast administration of same patient in top panel. Note agreement in location and severity of enhancement on FA and DCE-MRI
bration curve obtained at room temperature in a separate phantom study. The unidirectional rate constant, k, is given by:
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