Arterial spin labelling (ASL) is a noninvasive magnetic resonance imaging (MRI) modality, capable of measuring blood perfusion without the use of a contrast agent. While ASL implementation for imaging the brain and monitoring cerebral blood flow has been reviewed in depth, the technique is yet to be widely used for ocular tissue imaging. The human retina is a very thin but highly stratified structure and it is also situated close to the surface of the body which is not ideal for MR imaging. Hence, the application of MR imaging and ASL in particular has been very challenging for ocular tissues and retina. That is despite the fact that almost all of retinal pathologies are accompanied by blood perfusion irregularities. In this review article, we have focused on the technical aspects of the ASL and their implications for its optimum adaptation for retinal blood perfusion monitoring. Retinal blood perfusion has been assessed through qualitative or invasive quantitative methods but the prospect of imaging flow using ASL would increase monitoring and assessment of retinal pathologies. The review provides details of ASL application in human ocular blood flow assessment.
1. Ocular Blood Perfusion Quantification
Our sense of vision is critically dependent on all the components of our eye to function cohesively, so we will have a clear image of the outside world. The retina is the light-sensitive tissue that is lined on the inside surface of the eye and contains nerve cells, which convert incoming light into electrical impulses (Figure 1). Anatomically, retina is a highly stratified tissue, consisting of multiple cell types organized into its layered structure. Each layer of the retina performs distinct and yet interdependent functions, which in conclusion support the phototransduction process [1]. Briefly and moving from inside in contact with the vitreous outside, these are the inner limiting membrane, nerve fibre layer, ganglion cell layer, the inner plexiform layer, inner nuclear layer, the outer plexiform layer, outer nuclear layer, the external limiting membrane inner/outer segment of photoreceptors, and the retinal pigment epithelium. Like all the other tissues in the human body, the retinal layers of different cell types need oxygen, and hence blood supply, to survive.
The layered structure of the retina. (a) General anatomy of the eye, including the retina lining the back of the eye; and (b) the cellular component of retinal stratified structure. (c) The segmented raw retinal OCT image overlaid with seven identified boundaries. (d) Raw OCT image of the retina.
The two major sources of blood supply to the mammalian retina are the retinal and the choroidal blood vessels [2]. The choroidal vascular bed receives the bigger blood flow of about 65–85% of the total blood flow and the remaining 15–35% flows to the retina through the central retinal artery [3]. While the choroidal circulation is vital for the maintenance of the outer retina and particularly the photoreceptors, the retinal vasculature nourishes the inner retinal layers. The arterial input to the eye is derived from the internal carotid artery and includes central retinal artery, the short and long posterior ciliary arteries, and the anterior ciliary arteries. Venous outflow from the eye is primarily via the vortex veins and the central retinal vein. The choroidal arteries arise from long and short posterior ciliary arteries and each of the posterior ciliary arteries breaks up into fan-shaped lobules of capillaries that supply localized regions of the choroid. The arteries pierce the sclera around the optic nerve and fan out to form the three vascular layers in the choroid: outer (most scleral), medial, and inner (nearest Bruch’s membrane of the pigment epithelium) layers of blood vessels [4, 5]. Any deficiency of either of these two retinal circulations could result in blood perfusion alterations in the retina which is linked to several retinal pathologies [6].
Perfusion allows for the delivery of oxygen and nutrients to tissues by means of blood flow and it is one of the most fundamental physiological parameters [7]. Disorders correlated with blood perfusion such as stroke account for much of the medical morbidity in industrialized nations, and blood flow alterations also commonly accompany other pathophysiological changes such as cancer, epilepsy, and neurodegenerative diseases [8]. Hence, the measurements of perfusion have direct diagnostic value. Tissue perfusion is usually measured using a diffusible tracer that can be exchanged between the vascular compartment and tissue [9]. Conventional fluid flow describes the volume of liquid passing a given point per unit of time and has a unit of mL/min. However, perfusion flow is a more useful physiological measure. Perfusion flow is the volume of fluid (i.e., blood) passing in and out of a given weight of tissue per unit of time. That is because the cerebral and retinal blood flow should be distinguished as a rate for a specific tissue weight [10].
There are many methods of measuring blood perfusion, including methods based on computed tomography (CT), laser Doppler, single-photon emission computed tomography (SPECT), and MRI. The majority of these techniques require the injection of an exogenous tracer that acts to alter the signal intensity as the contrast agent moves through the blood, allowing the quantification of tissue perfusion. Both CT and SPECT techniques provide high sensitivity to perfusion [11] but are unsuitable for serial studies requiring multiple examinations owing to the use of ionising radiation. MRI techniques using gadolinium based contrast agents (GBCA) also provide high sensitivity while avoiding the use of ionising radiation. However, the risks associated with GBCA such as nephrogenic systemic fibrosis (NSF) make such techniques unsuitable in at-risk patients. The use of contrast agents that are not gadolinium based such as fluorinated halocarbons [12], deuterated water (2H2O) [13, 14], and 17O-water [14] has been investigated. The use of arterial spin labelling (ASL) techniques eliminates the requirement for externally administered agents and exploits the advantages offered by MRI-based techniques [15, 16].
2. ASL
The primary benefit of ASL over other MRI-based techniques is that the use of the blood itself as a tracer eliminates the risks associated with GCBA and other exogenous tracers. As a result, ASL is of most use in cases where the use of an exogenous contrast agent is contraindicated [17] or in cases where patients require multiple perfusion assessments in a single study [18]. In studies of the eye, for example, it may be appropriate to assess perfusion under a variety of conditions during the same study, making techniques based on exogenous contrast agents undesirable [19, 20].
ASL requires that the arterial blood supplying the tissues of interest is labelled by modifying its magnetization. Image contrast is affected by the presence of the labelled blood in the imaging volume. Acquiring an image of the tissues of interest after a sufficient delay time to allow the labelled blood to enter the imaging volume results in a decrease in signal related to the local tissue perfusion. Comparing the labelled images to those acquired without the labelled blood allows regional variations in tissue perfusion to be identified. Further, this signal can be modelled to determine the tissue perfusion at each voxel. In both the qualitative and the quantitative applications of ASL, the resulting signal depends on the tissue properties, timing considerations, and imaging parameters. For this reason, ASL techniques used in any study need to be specifically optimized for the tissue of interest [21, 22].
2.1. Applications of ASL
In a clinical setup, ASL can be grouped with other anatomical (e.g., spin-lattice T1 or spin-spin T2) or functional (e.g., fMRI) imaging sequences in order to provide a comprehensive assessment of the imaged organ [23]. To date, the major clinical applications of the ASL have been focused on studying the brain and its disorders [24]. Several studies have used ASL to detect regional hypoperfusion in patients suffering from Alzheimer’s dementia ([25, page 2000], [26]) or frontotemporal dementia [27, 28]. Epilepsy is another neurological disorder in which ASL can be applied for diagnosis and management. Interictal hypoperfusion measured by ASL has been shown to correlate with interictal hypometabolism ([29, 30], [31, page 200]). ASL has also been used in conjunction with other modalities to monitor the diagnosis and treatment effects of several brain affective disorders such as depression [30, 32], schizophrenia [33], Parkinson [34], and hypoperfusion of prefrontal cortex [35]. Furthermore and combined with fMRI, ASL is proved to be an appealing approach for imaging brain activations during long time scale processes and more ecological paradigms such as motor learning [36], emotion or mental states [37–39], mood changes [40, 41], and natural vision [42]. The utility of ASL in detection of migraine [43, 44] and focal seizure [44] has also been demonstrated in several case reports. ASL can be combined with fMRI to look at brain’s oxygenation and functionality since it provides absolute quantification of brain blood perfusion and is less susceptible to baseline drift and motion artefact [45, 46]. Finally, since ASL is reagent-free it has become an appealing technique in paediatric studies, as a biomarker for functional brain development in both healthy populations and developmental disorders [47, 48].
Apart from the field of brain research, new applications of ASL are being investigated around the world. Preliminary studies of the applicability of ASL in the cardiovascular investigations [49] and its related pathologies such as stroke have been looked at [50, 51]. ASL has also been obtained from postischemic extremities in patients with peripheral vascular disease [49]. The kidney is another highly perfused tissue where ASL has also been used [52]. Lastly, since tumorous tissue usually has higher perfusion than healthy tissue, ASL has been applied for detection and grading of tumours [53, 54]. One reason for the spread of ASL’s clinical usage has been the verification of its measurements against previously stablished flowmetry methods.
ASL MRI has been validated against other quantitative technologies such as Dynamic Susceptibility-Weighted Contrast-Enhanced MRI [55–57], PET scan, and using different exogenous contrast agents [58, 59]. Furthermore, since ASL image contrast is not based on susceptibility effects, it could be used to study regions of high static field inhomogeneity [60–62]. This property of ASL is especially valuable while imaging highly layered structures such as the eye’s retina [63, 64].
ASL implementations are now commercially available on all major MRI platforms and their reproducibility has been confirmed by several multicentre studies [46, 65]. However, before applying this technique in the clinic, many of its technical parameters have to be studied and optimized. Here we are going to review the effects of a number of these factors on the quality of the ASL measurements.
2.2. Technical Considerations
Early implementations of ASL used a series of short labelling pulses (PASL), to label the arterial blood [66–68]. The shorter pulses mitigate the SAR issues and high power deposition, but the nonadiabatic nature of the labelling pulses results in decreased labelling efficiency and lower ASL signal.
The next generation of ASL implementations is known as continuous ASL (CASL) [16]. In CASL schemes, the blood that passes through the labelling slab is continuously affected and allows blood magnetization to reach a steady-state, maximising the signal difference between the labelled and control conditions [69]. However, this labelling scheme leads to increased magnetization transfer effects that would decrease the accuracy of the measurements. The long labelling pulses used in CASL are particularly problematic in higher field strength systems. At these higher fields, specific absorption rate (SAR) is increased, leading to higher amounts of RF energy being absorbed and potentially increasing local heating in tissues. Longer RF pulses, like those used in CASL, also lead to increased SAR, exacerbating any potential heating occurring in patients [44, 70].
The latest implementation of ASL in many modern applications is the pseudo-continuous ASL (pCASL) (Figure 2), which is used to overcome the limitations of PASL and CASL [15, 60]. Rather than using a single continuous labelling pulse like CASL, 1000 or more shaped magnetization pulses are very rapidly applied to label the arterial blood. Compared to CASL, pCASL provides superior labelling efficiency and is compatible with modern body coil RF transmission hardware that is now ubiquitous on clinical MRI scanners. In practice, the signal-to-noise ratio (SNR) of the pCASL implementation is higher than other methods due to two reasons. Firstly, in pCASL implementation the temporal duration of the labelled slab is longer which in turn leads to larger volume of labelled blood that is delivered to the tissue, leading to an increased SNR. Secondly, even for an interval of equal temporal duration, it has been shown that the labelled magnetization delivered to the blood is higher using pCASL [71].
Different implementations of ASL pulse sequence for MR, continuous (CASL), pulsed (PASL), and pseudo-continuous (pCASL) technique.
Over the past decade, there has been a general trend to the use of higher field strength systems owing to the higher overall SNR. Theoretically, the expected ASL signal will increase proportional to the strength of the main magnetic field. Wang et al. [69] studied the effects of the magnet field strength on the implementation of ASL to quantify the cerebral blood flow. They reported that, using similar pulse sequences, a 4 T magnet generated more than twice the amount of ASL signal compared to a 1.5 T magnet, consistent with the theoretical expectations. Other studies have used 7 T magnet strength to apply ASL to human brain [72, 73]; however, it has been noted that since these high strengths are much more susceptible to off-resonance fields especially at the tagging location, a robust prescan procedure is needed to optimize the ASL parameters [74].
In all forms of ASL, ideally the labelling pulse will result in perfect and complete labelling of the arterial blood. In this ideal case, all of the blood passing through the imaging volume will contribute to the ASL signal. However, in magnets with clinical field strengths, the lifetime of the magnetically tagged blood is about 1300–1750 ms. The labelling lifetime along with the timing delays used in the pulse sequence will influence labelling efficiency. The postlabelling delay time (the delay between the labelling pulse train and acquisition) needs to be set so that the labelled blood arrives at the tissue of interest when it is acquired. Shorter delays can be used to reduce scan time but come at the expense of potentially inefficient labelling since the labelled blood has not had sufficient time to arrive at the imaging slice. A longer delay could be used to ensure that more labelled blood perfuses the tissues of interest but labelling efficiency may be reduced owing to T1 relaxation effects [75].
Aside from timing and protocol-specific effects, labelling efficiencies in ASL also depend on the hardware used. Higher magnetic field strength systems provide increased efficiency in ASL studies [76] owing to the increase in overall SNR as well as the lengthening of T1 in tissues [70]. The multichannel head coils have been shown to increase the SNR of the ASL scans [77] and allow for the use of parallel imaging techniques [45]. The coil arrays used in parallel imaging can be exploited to decrease the echo time (TE) and maximise the signal from tissues with very short T2, such as the retina [78]. The higher SNR achieved by using multichannel coils has also been shown to provide more accurate quantification of tissue perfusion [79–81]. The gain in SNR is also mentioned when surface coils are used in conjunction with standard head coils, imaging the brain, the kidney, and the eye [82].
Similar to other MRI techniques, ASL is also sensitive to motion and susceptibility artefacts. Motion artefacts are an issue in all MR imaging techniques owing to the effectively long scan times, resulting in difficulties for some patients to remain still throughout the examination. In ASL, misregistration resulting from motion between the control and labelled data can cause local or global changes in ASL signal not related to tissue perfusion [83–85]. Magnetic field inhomogeneities are problematic in EPI-based protocols such as ASL where the long echo trains used can result in image distortions or significant signal loss. Field inhomogeneities will also affect the labelling efficiency, particularly in pCASL techniques owing to the nonadiabatic nature of the labelling pulses [22]. Artefacts specific to ASL studies, such as enhanced T1 shortening owing to the presence of gadolinium based contrast agents, and insufficient suppression of intravascular spins can also result in suboptimal image quality [83–85].
Fortunately, many of these issues can be partially mitigated by the use of background suppression [86, 87]. Blood labelling in ASL is inherently inefficient with only 1-2% of the spins in the blood contributing to the signal, so the use of effective background suppression will increase ASL signal-to-noise ratio and sensitivity and result in improved quantification of perfusion measures. In order to incorporate background suppression in ASL implementation, an initial saturation pulse is applied to the imaging region. This saturation pulse is then followed by carefully timed magnetization inversion pulses. Such combination results in the longitudinal magnetization of the static target tissue being close to zero at the time of image acquisition. Meanwhile, the tagged arterial blood water molecules that are passing through the target tissue have not experienced the initial saturation pulse, but only the inversion pulses [88–90]. Hence, the ASL perfusion signal is preserved, while the static tissue signal is nearly eliminated.
2.3. Applicability of ASL in the Eye
The mammalian retina is found to have a high rate of perfusion [91–94], which is required for the maintenance of the physiological homeostasis in the highly compartmented ultrastructure of the retina. Retina is the most metabolically active tissue in the human body [95] and is highly sensitive to the local perfusion rates of the retinal and choroidal circulations. The choroidal arteries, which feed the outer retina, arise from the posterior ciliary arteries that penetrate the sclera around the optic nerve [4]. Simultaneously, the retinal vasculature network is branched from the central retina artery and feeds the deeper layers of the retina. The central retina artery itself receives its blood supply from the Circle of Willis, which is formed by an arterial polygon and supplies the blood of the eye and the brain.
The retinal circulation has no autonomic innervation and is regulated by local factors [6] while the choroidal circulation is not autoregulated and is mainly controlled by sympathetic innervation [96]. Using a 9 T Phillips magnet in a preliminary study, we have previously shown that ASL can be applied to image this nonregulated blood flow in the retina (Figure 3). The perfusion rates of the blood in retina have been tried to be measured using other methods, including laser speckle [97], ultrasound combined with enhanced depth imaging OCT [98], high frequency immersion ultrasound [99], OCT Angiography [100, 101], Doppler OCT [102], ultrahigh speed swept source/Fourier domain OCT [103], and laser Doppler flowmetry [104]. Most of these techniques have not been transformed to the clinical setup, due to their limitations in sensitivity, reproducibility, and accuracy. However, the perfusion rates of the retinal and choroidal circulations are of clinical importance as they are altered and affected in many of the common retinal pathologies.
(a) Statistical map extracted from our ASL dataset is showing the correlation map of voxels (arrow) activated to the visual stimulus (Z>3.23). (b) ASL perfusion signal in mL/100 g/min units is extracted from active voxels shown on (a) over the time course of our experiment. Red blocks denote the periods of light stimulation.
Several studies have shown that, within retina, the outer segments of the photoreceptors are the most metabolically active [105, 106]. Due to such high demand of blood perfusion, the ability to regulate steady blood flow in the retina is essential for the health of this tissue. Normal blood flow within the retina and choroidal vasculatures is altered in a number of retinal disorders that affect the overall vision.
Diabetic retinopathy (DR) is an ocular manifestation of diabetes which disturbs the normal retinal vasculature function and often leads to capillary occlusion and if left untreated to vascular proliferation [107, 108]. By the time that the manifestation of DR becomes clinically observable, irreversible changes to the retinal vasculature network have already occurred. These changes (i.e., proliferation of the retinal vasculature) are in response to the tissue hypoxia which is known to occur in DR; however, the exact time when hypoxia begins is as yet unknown [109]. In ophthalmic clinical studies, it has been shown that retinal blood flow is reduced before and in the early stages of DR [110–112]. This initial flow reduction is then followed by an increase in retinal blood flow, possibly due to the release of vascular endothelial growth factor (VEGF), which in turn leads to proliferative retinopathy [113, 114].
Glaucoma is a term encompassing a group of disorders of the eye which generally damage the optic nerve. Often the onset and progression of glaucoma are accompanied by an increase in the intraocular pressure (IOP) of the patient. There is evidence that there is a relationship between ocular perfusion and damage progression in patients with glaucoma [115]. There is further evidence that an eye with elevated IOP could experience conditions similar to those suffering from reduced retinal perfusion [105, 116]. Due to the effective autoregulation in the retinal circulation, the decreased perfusion pressure of the eye suffering from glaucoma does not affect the PO2 of the inner retina [117]. On the other hand, the choroidal blood flow was shown to be decreased in glaucoma, resulting in hypoxic conditions at the photoreceptors [116].
Retinopathy of prematurity (ROP) is affecting premature infants and it is marked by abnormal growth of blood vessel in the retina. ROP progresses firstly by delayed retinal vascular growth after birth and partial regression of existing vessels. This is then followed by neovascularization induced by hypoxia [118]. ROP was first associated with exposure to high levels of oxygen after the initial description of the disease [119]. In order to maintain healthy and sufficient blood perfusion levels in premature infants, currently supplemental oxygen is closely monitored [120]. The current clinical treatment to stop the progression of this condition is the indirect laser photocoagulation to bring the perfusion rates of the retina towards normal levels [121].
Retinal detachment is a condition that could occur due to various often advanced pathologies of the retina. In this condition, the retinal tissue peels away from the RPE [122]. During retinal detachment progression, the photoreceptor segments are separated from their supporting vasculature. This process leads to lower oxygen values at the photoreceptors site, inducing local hypoxic conditions and increasing the cell death rate under this condition. It has been shown that retinal detachment is correlated by altered choroidal perfusion rates [123].
3. Application of ASL in Animal Models
The ASL modality is capable of noninvasively quantifying blood perfusion in scanned tissues. A recent study showed that ASL could provide sufficient resolution and SNR to accurately measure the different blood flow of the retinal and choroidal circulations in mice eyes [63]. Furthermore, the same study showed that ASL can correctly quantify the changes of blood flow modulated by anaesthetics in their animal model. It was mentioned that the retinal blood flow changed from 1.3 ± 0.44 to 0.88 ± 0.22 mL/g/min and choroidal blood flow changed from 7.7 ± 2.1 to 4.3 ± 1.9 mL/g/min due to anaesthesia.
In a following study, a mouse model of diabetic retinopathy was imaged with ASL [124]. The blood flows of the mice were quantified at early and late time points after onset of hyperglycemia. It has been reported that the choroidal blood flow was reduced by 20% in the diabetic group compared with the control group after 10 weeks. After 30 weeks, it was observed that both choroidal and retinal blood flows were notably lower in the mice model of diabetic retinopathy. The visual performance of these animals was also found to be significantly worsened.
In the third study from the same authors, changes in retinal and choroidal blood flows of the mouse model of retinitis pigmentosa were measured with ASL [125]. Here it was observed that the retinal blood flow was decreased consistently and significantly through the course of the study. The same effect was not observed in the choroidal blood flow though.
Reference [126] measured the retinal and cerebral blood flows in rats under light and dark adapted conditions using ASL. These measurements were then reconfirmed with fluorescent microspheres. The choroidal blood flow was measured at 64.8 ± 29 μL/min during dark adaptation and 66.0 ± 17.8 μL/min during light adaptation condition. Retinal BF was 11.6 ± 2.9 μL/min during light adaptation and between 8.2 and 9.9 μL/min under dark adapted environment. A 10 Hz flickering light stimulation was also applied which led to significantly higher retinal blood flow but not the choroidal blood flow 13.5 ± 3.2 μL/min.
ASL was utilized to obtain high resolution blood flow measurements of rat models of retinitis pigmentosa [127]. A CASL pulse sequence and an 11.7 T small animal MRI were combined with customized surface coil to implement the ASL technique here. It was hence possible to have 44 ∗ 44 μm in-plane resolution and differentiate between retinal and choroidal circulations in rats’ retinas. This study found that choroidal and retinal circulations have different susceptibility to progressive retinal degeneration in this animal model.
A follow-up study looked at applying ASL to look at the effects of acute hypertension on the choroidal and retinal blood flows, in a rat model [128]. In this study, an autoregulatory behaviour was observed in the retinal blood circulation, while a baroregulation response was imaged in the choroid vasculature. The authors believe that their animal model was useful in studying retinal and choroidal vascular dysregulation.
The most human-like implementation of ASL in animal models was done using eight baboons and a 3-Tesla clinical scanner [129]. The retinal blood flow was measured under normal and hypercapnia conditions in these animals. It was found that base blood flow from the posterior retina was 83 ± 30 mL/100 g/min while in hypercapnia this was increased by 25 ± 9%.
The above-mentioned studies have established the applicability and accuracy of ASL blood in studying the models of different retinal conditions. Next, we are reviewing the application of the ASL to human tissue.
4. Application of ASL in Human Retinal Tissue
One of the first studies that have used a conventional standard and commercially available 3 T clinical magnet to investigate the feasibility of measuring blood flow of the human retina using ASL was done by [130]. Here, the blood flow measurements were obtained in five healthy individuals using an 8-channel array head coil. A CASL was used in this study and the labelling was placed 5 cm below the optic nerve to invert the magnetization of the blood in the carotid arteries below the Circle of Willis. The inverting pulse duration was varied between 500 and 2000 ms to optimize the sequence for achieving maximum SNR. Additionally, background suppression technique was also employed in order to improve the quality of the obtained results. The two main sources of image artefact in ophthalmic MRI are ocular motion artefact and partial volume effects [131, 132]. The former is due to involuntary eye movement and the latter is due to the proximity of the eye to the surface of the body. In the [130] study, these artefacts are minimized by usage of a fixation target and blink-synced image acquisition. The blood flow estimation was performed using a single-compartment model [133, 134]. Using this model and assuming labelling efficiency of 0.85, brain-blood water partition coefficient of 0.9 g/mL [135], and longitudinal relaxation rate of 0.67 s−1 for the retinal tissue [136, 137], the measured blood flow to a section of the retina around the fovea was measured at 1.75 ± 0.54 μL/mm2/min.
A follow-up investigation tried to differentiate between the human retinal and choroidal blood flow, in a clinical setup [138]. Four healthy individuals were scanned by ASL under normocarbia (partial end-tidal pressure values = 40 mmHg) and hypercarbia (partial end-tidal pressure values = 50 mmHg) conditions. The MRI setup was similar to a previous study [130] but a pCASL pulse sequence was applied here. Using a similar single-compartment model and parameter assumption as before, the baseline blood flow was measured at 1.55 ± 0.17 μL/mm2/min. This value increased during hypercarbia to 1.96 ± 0.18 μL/mm2/min. Overall, hypercarbia caused a 26% relative increase of blood flow from the normal condition which is calculated to be 6.7% increase in the blood flow per 1 mmHg. This study, by controlling the breathing conditions, showed that when the clinical ASL does not have the spatial resolution to differentiate the retinal and choroidal blood flows, the obtained measurements are dominated by the latter vascular blood flow.
A similar but separate study was performed on 5 healthy subjects under normal and hypercapnia conditions [139]. Eye fixation and queued breathing techniques were employed to minimize the motion artefact. The ASL labelling plane was placed 7 cm below the optic nerve, and ASL background suppression was also employed. The background suppression pulse timing for ASL of the human retina is investigated in depth and optimized in a later publication [90]. Here it was measured that the group-averaged peak blood flow value was at 93 ± 31 mL/(100 mL min). Furthermore, profiles of blood flow from sclera to vitreous and across the thickness of the retina showed that under hypercapnia condition flows were increased from 93 ± 31 to 104 ± 35 mL/(100 mL min).
One study investigated the levels of blood perfusion in retina during rest and exercise [140]. This study used a 3 T magnet combined with a custom-made surface coil and a pCASL pulse sequence. Using this ASL setup and measuring four young healthy volunteers, it was found that, compared to the resting state (60 ± 5 beats per minute and arterial pressure of 78 ± 5 mmHg), the retinal blood perfusion increased by 25%±7% and ocular perfusion pressure increased by 25%±6% in the exercise mode.
The same authors investigate the patients suffering from retinitis pigmentosa with similar ASL implementation [141]. The authors measured basal blood flow of 142 ± 16 mL/100 mL/min (or 1.14 ± 0.13 μL/mm2/min) in the posterior retinal-choroid in the control group and 70 ± 19 mL/100 mL/min (or 0.56 ± 0.15 μL/mm2/min) in the retinitis pigmentosa group. This revealed a significant reduction of blood perfusion in patients compared to controls.
A recent study looked at the effect of aging on choroidal blood circulation, using pCASL and 3 T magnet, scanning 17 normal subjects (24–68 years old) [142]. This study found that choroidal blood flow was negatively correlated with age, declining 2.7 mL/100 mL/min each year, while it was not correlated with perfusion pressure, arterial pressure, or intraocular pressure. This age dependence of choroidal perfusion was only observed in central retina, but not at its periphery.
5. Conclusion
ASL is a versatile and noninvasive imaging technique that is used to estimate tissue perfusion without the use of endogenous tracers. Although the main application of ASL remains the measurement of cerebral blood perfusion, this technique is gradually being adopted in other organs as well. Owing to the nature of the tissues, noninvasive techniques are required to assess pathologies of the eye. While other MRI-based techniques such as T1 and T2 weighted imaging [143], diffusion tensor imaging [144, 145], and contrast-enhanced imaging [146–148] have been used to look at the dynamic physiology of the ocular tissue, ASL shows promise as a technique to assess pathologies of the retina. Here at the University of Auckland, we are implementing new pCASL modalities in our Siemens SKYRA 3 T magnet. While we are still optimizing our approach, our preliminary data are promising (Figure 4).
(a) High resolution T2 weighted anatomical image, used to locate the tissue of interest (i.e., the retina) in order to apply the ASL sequence. (b) The perfusion-weighted image calculated from the application of 2D ASL sequence. The choroid layer in the back of the eye is clearly highlighted, showing the detection of blood perfusion into this vasculature bed.
We are aiming to study the blood perfusion of the retina in healthy and diseased subjects, by using our optimized ASL routine in the very near future. This review article sets the scene for our upcoming research articles, presenting novel research into ocular perfusion.
Competing Interests
The authors of this paper do not have any association with a commercial organisation or any financial interest in a product that may give rise to the perception of a potential conflict of interests.
Acknowledgments
The authors wish to thank Dr. Monica Acosta from the Department of Physiology, University of Auckland, for her insights into compilation of this paper.
ReynoldsJ. D.OlitskyS. E.2010SpringerLensA.NemethS. C.LedfordJ. K.2008Thorofare, NJ, USASLACK IncorporatedAbramsonD.2012Academic PressZhangH. R.Scanning electron-microscopic study of corrosion casts on retinal and choroidal angioarchitecture in man and animals199413124327010.1016/1350-9462(94)90012-42-s2.0-0028220322KielJ. W.2010San Rafael, Calif, USAMorgan & Claypool Life SciencesIntegrated Systems Physiology: From Molecule to Function to DiseasePournarasC. J.Rungger-BrändleE.RivaC. E.HardarsonS. H.StefanssonE.Regulation of retinal blood flow in health and disease200827328433010.1016/j.preteyeres.2008.02.0022-s2.0-43149104360JahngG.-H.LiK.-L.OstergaardL.CalamanteF.Perfusion magnetic resonance imaging: a comprehensive update on principles and techniques201415555457710.3348/kjr.2014.15.5.5542-s2.0-84907198365BarkerP. B.GolayX.ZaharchukG.2013Cambridge University Press10.1017/cbo9781139004053WebsterJ. G.2014Philadelphia, Pa, USACRC PressCunha-VazJ. G.2011World ScientificMarianiG.BruselliL.KuwertT.KimE. E.FlotatsA.IsraelO.DondiM.WatanabeN.A review on the clinical uses of SPECT/CT201037101959198510.1007/s00259-010-1390-82-s2.0-79952110645EleffS. M.SchnallM. D.LigettiL.OsbakkenM.SubramanianV. H.ChanceB.LeighJ. S.Jr.Concurrent measurements of cerebral blood flow, sodium, lactate, and high-energy phosphate metabolism using 19F, 23Na, 1H, and 31P nuclear magnetic resonance spectroscopy19887441242410.1002/mrm.19100704042-s2.0-0023678464DetreJ. A.SubramanianV. H.MitchellM. D.SmithD. S.KobayashiA.ZamanA.LeighJ. S.Jr.Measurement of regional cerebral blood flow in cat brain using intracarotid 2H2O and 2H NMR imaging199014238939510.1002/mrm.19101402232-s2.0-0025163986AckermanJ. J. H.EwyC. S.BeckerN. N.ShalwitzR. A.Deuterium nuclear magnetic resonance measurements of blood flow and tissue perfusion employing 2H2O as a freely diffusible tracer198784124099410210.1073/pnas.84.12.40992-s2.0-0023214572DetreJ. A.LeighJ. S.WilliamsD. S.KoretskyA. P.Perfusion imaging1992231374510.1002/mrm.19102301062-s2.0-0026508892WilliamsD. S.DetreJ. A.LeighJ. S.KoretskyA. P.WilliamsD. S.Magnetic resonance imaging of perfusion using spin inversion of arterial water199289121221610.1073/pnas.89.1.212LiA.WongC. S.WongM. K.LeeC. M.Au YeungM. C.Acute adverse reactions to magnetic resonance contrast media—gadolinium chelates20067994136837110.1259/bjr/884696932-s2.0-33646412592ParadisoS.JohnsonD. L.AndreasenN. C.O'LearyD. S.WatkinsG. L.Boles PontoL. L.HichwaR. D.Cerebral blood flow changes associated with attribution of emotional valence to pleasant, unpleasant, and neutral visual stimuli in a PET study of normal subjects1999156101618162910.1176/ajp.156.10.16182-s2.0-0032823039LongoA.GeiserM.RivaC. E.Subfoveal choroidal blood flow in response to light-dark exposure2000419267826832-s2.0-0033861497Fuchsjäger-MayrlG.PolskaE.MalecM.SchmettererL.Unilateral light-dark transitions affect choroidal blood flow in both eyes200141222919292410.1016/S0042-6989(01)00171-72-s2.0-0034755695AlsopD. C.DetreJ. A.GolayX.GüntherM.HendrikseJ.Hernandez-GarciaL.LuH.MacintoshB. J.ParkesL. M.SmitsM.van OschM. J. P.WangD. J. J.WongE. C.ZaharchukG.Recommended implementation of arterial spin-labeled Perfusion MRI for clinical applications: a consensus of the ISMRM perfusion study group and the European consortium for ASL in dementia201573110211610.1002/mrm.251972-s2.0-84919839320AslanS.XuF.WangP. L.UhJ.YezhuvathU. S.Van OschM.LuH.Estimation of labeling efficiency in pseudocontinuous arterial spin labeling201063376577110.1002/mrm.222452-s2.0-77649122097BrownM. A.SemelkaR. C.2003Hoboken, NJ, USAJohn Wiley & Sons10.1002/0471467936PetersenE. T.ZimineI.HoY.-C. L.GolayX.Non-invasive measurement of perfusion: a critical review of arterial spin labelling techniques20067994468870110.1259/bjr/677059742-s2.0-33747590330AlsopD. C.DetreJ. A.GrossmanM.Assessment of cerebral blood flow in Alzheimer's disease by spin-labeled magnetic resonance imaging20004719310010.1002/1531-8249(200001)47:1<93::AID-ANA15>3.0.CO;2-82-s2.0-0033976957JohnsonN. A.JahngG.-H.WeinerM. W.MillerB. L.ChuiH. C.JagustW. J.Gorno-TempiniM. L.SchuffN.Pattern of cerebral hypoperfusion in Alzheimer disease and mild cognitive impairment measured with arterial spin-labeling MR imaging: initial experience2005234385185910.1148/radiol.23430401972-s2.0-13844298168DuA. T.JahngG. H.HayasakaS.KramerJ. H.RosenH. J.Gorno-TempiniM. L.RankinK. P.MillerB. L.WeinerM. W.SchuffN.Hypoperfusion in frontotemporal dementia and Alzheimer disease by arterial spin labeling MRI20066771215122010.1212/01.wnl.0000238163.71349.782-s2.0-33749848175HuW. T.WangZ.LeeV. M.-Y.TrojanowskiJ. Q.DetreJ. A.GrossmanM.Distinct cerebral perfusion patterns in FTLD and AD2010751088188810.1212/WNL.0b013e3181f11e352-s2.0-77957066544WolfR. L.AlsopD. C.Levy-ReisI.MeyerP. T.MaldjianJ. A.Gonzalez-AtavalesJ.FrenchJ. A.AlaviA.DetreJ. A.Detection of mesial temporal lobe hypoperfusion in patients with temporal lobe epilepsy by use of arterial spin labeled perfusion MR imaging2001227133413412-s2.0-0034907799LuiS.ParkesL. M.HuangX.ZouK.ChanR. C. K.YangH.ZouL.LiD.TangH.ZhangT.LiX.WeiY.ChenL.SunX.KempG. J.GongQ.-Y.Depressive disorders: focally altered cerebral perfusion measured with arterial spin-labeling MR imaging2009251247648410.1148/radiol.25120815482-s2.0-66149137601LimY.-M.ChoY.-W.ShamimS.SolomonJ.BirnR.LuhW. M.GaillardW. D.RitzlE. K.TheodoreW. H.Usefulness of pulsed arterial spin labeling MR imaging in mesial temporal lobe epilepsy2008822-318318910.1016/j.eplepsyres.2008.08.0012-s2.0-56449126967DuhameauB.FerréJ.-C.JanninP.GauvritJ.-Y.VérinM.MilletB.DrapierD.Chronic and treatment-resistant depression: a study using arterial spin labeling perfusion MRI at 3 Tesla2010182211111610.1016/j.pscychresns.2010.01.0092-s2.0-77952645949ScheefL.MankaC.DaamenM.KühnK.-U.MaierW.SchildH. H.JessenF.Resting-state perfusion in nonmedicated schizophrenic patients: a continuous arterial spin-labeling 3.0-T MR study2010256125326010.1148/radiol.100912242-s2.0-77953952439BlackK. J.KollerJ. M.CampbellM. C.GusnardD. A.BandakS. I.Quantification of indirect pathway inhibition by the adenosine A2a antagonist SYN115 in Parkinson disease20103048162841629210.1523/jneurosci.2590-10.20102-s2.0-78649740959FreudenmannR. W.KölleM.HuweA.LusterM.ReskeS. N.HuberM.LeppingP.WolfR. C.Schönfeldt-LecuonaC.Delusional infestation: neural correlates and antipsychotic therapy investigated by multimodal neuroimaging2010347121512222-s2.0-84855357660OlsonI. R.RaoH.MooreK. S.WangJ.DetreJ. A.AguirreG. K.Using perfusion fMRI to measure continuous changes in neural activity with learning200660326227110.1016/j.bandc.2005.11.0102-s2.0-33645022103WangJ.RaoH.WetmoreG. S.FurlanP. M.KorczykowskiM.DingesD. F.DetreJ. A.Perfusion functional MRI reveals cerebral blood flow pattern under psychological stress200510249178041780910.1073/pnas.05030821022-s2.0-29144506257WangJ.KorczykowskiM.RaoH.FanY.PlutaJ.GurR. C.McEwenB. S.DetreJ. A.Gender difference in neural response to psychological stress20072322723910.1093/scan/nsm0182-s2.0-34548640745LimJ.WuW.-C.WangJ.DetreJ. A.DingesD. F.RaoH.Imaging brain fatigue from sustained mental workload: an ASL perfusion study of the time-on-task effect20104943426343510.1016/j.neuroimage.2009.11.0202-s2.0-73749088479GillihanS. J.RaoH.WangJ.DetreJ. A.BrelandJ.SankoorikalG. M. V.BrodkinE. S.FarahM. J.Serotonin transporter genotype modulates amygdala activity during mood regulation20095111010.1093/scan/nsp0352-s2.0-77953989319WangD. J. J.RaoH.KorczykowskiM.WinteringN.PlutaJ.KhalsaD. S.NewbergA. B.Cerebral blood flow changes associated with different meditation practices and perceived depth of meditation20111911606710.1016/j.pscychresns.2010.09.0112-s2.0-78650174967RaoH.WangJ.TangK.PanW.DetreJ. A.Imaging brain activity during natural vision using CASL perfusion fMRI200728759360110.1002/hbm.202882-s2.0-34447335063PollockJ. M.DeiblerA. R.BurdetteJ. H.KraftR. A.TanH.EvansA. B.MaldjianJ. A.Migraine associated cerebral hyperperfusion with arterial spin-labeled MR imaging20082981494149710.3174/ajnr.a11152-s2.0-51649091195PollockJ. M.DeiblerA. R.WestT. G.BurdetteJ. H.KraftR. A.MaldjianJ. A.Arterial spin-labeled magnetic resonance imaging in hyperperfused seizure focus: a case report200832229129210.1097/rct.0b013e31814cf81f2-s2.0-41749090515GriswoldM. A.JakobP. M.HeidemannR. M.NittkaM.JellusV.WangJ.KieferB.HaaseA.Generalized autocalibrating partially parallel acquisitions (GRAPPA)20024761202121010.1002/mrm.101712-s2.0-0036263907PetersenE. T.MouridsenK.GolayX.The QUASAR reproducibility study, part II: results from a multi-center arterial spin labeling test-retest study2010491104113WangJ.LichtD. J.JahngG.-H.LiuC.-S.RubinJ. T.HaselgroveJ.ZimmermanR. A.DetreJ. A.Pediatric perfusion imaging using pulsed arterial spin labeling200318440441310.1002/jmri.103722-s2.0-0141841839OguzK. K.GolayX.PizziniF. B.FreerC. A.WinrowN.IchordR.CasellaJ. F.Van ZijlP. C. M.MelhemE. R.Sickle cell disease: continuous arterial spin-labeling perfusion MR imaging in children2003227256757410.1148/radiol.22720209032-s2.0-0037406939WuW.-C.MohlerE.IIIRatcliffeS. J.WehrliF. W.DetreJ. A.FloydT. F.Skeletal muscle microvascular flow in progressive peripheral artery disease: assessment with continuous arterial spin-labeling perfusion magnetic resonance imaging200953252372237710.1016/j.jacc.2009.03.0332-s2.0-66949151329WarachS.DasheJ. F.EdelmanR. R.Clinical outcome in ischemic stroke predicted by early diffusion-weighted and perfusion magnetic resonance imaging: a preliminary analysis199616153592-s2.0-0030049425ChalelaJ. A.AlsopD. C.Gonzalez-AtavalesJ. B.MaldjianJ. A.KasnerS. E.DetreJ. A.Magnetic resonance perfusion imaging in acute ischemic stroke using continuous arterial spin labeling200031368068710.1161/01.STR.31.3.6802-s2.0-0034108310RobertsD. A.DetreJ. A.BolingerL.InskoE. K.LenkinskiR. E.PentecostM. J.LeighJ. S.Jr.Renal perfusion in humans: MR imaging with spin tagging of arterial water1995196128128610.1148/radiology.196.1.77845822-s2.0-0029060933WolfR. L.WangJ.WangS.MelhemE. R.O'RourkeD. M.JudyK. D.DetreJ. A.Grading of CNS neoplasms using continuous arterial spin labeled perfusion MR imaging at 3 Tesla200522447548210.1002/jmri.204152-s2.0-26244451600NoguchiT.YoshiuraT.HiwatashiA.TogaoO.YamashitaK.NagaoE.ShonoT.MizoguchiM.NagataS.SasakiT.SuzukiS. O.IwakiT.KobayashiK.MiharaF.HondaH.Perfusion imaging of brain tumors using arterial spin-labeling: correlation with histopathologic vascular density200829468869310.3174/ajnr.a09032-s2.0-42449103401WeberM.-A.GüntherM.LichyM. P.DelormeS.BongersA.ThilmannC.EssigM.ZunaI.SchadL. R.DebusJ.SchlemmerH.-P.Comparison of arterial spin-labeling techniques and dynamic susceptibility-weighted contrast-enhanced MRI in perfusion imaging of normal brain tissue2003381171271810.1097/01.rli.0000084890.57197.542-s2.0-10744225404WeberM.-A.ThilmannC.LichyM. P.GüntherM.DelormeS.ZunaI.BongersA.SchadL. R.DebusJ.KauczorH.-U.EssigM.SchlemmerH.-P.Assessment of irradiated brain metastases by means of arterial spin-labeling and dynamic susceptibility-weighted contrast-enhanced perfusion MRI: initial results200439527728710.1097/01.rli.0000119195.50515.042-s2.0-11144353980WangD. J. J.AlgerJ. R.QiaoJ. X.HaoQ.HouS.FiazR.GuntherM.PopeW. B.SaverJ. L.SalamonN.LiebeskindD. S.The value of arterial spin-labeled perfusion imaging in acute ischemic stroke: comparison with dynamic susceptibility contrast-enhanced MRI20124341018102410.1161/strokeaha.111.6319292-s2.0-84859364248BokkersR. P.BremmerJ. P.van BerckelB. N.LammertsmaA. A.HendrikseJ.PluimJ. P.KappelleL. J.BoellaardR.KlijnC. J.Arterial spin labeling perfusion MRI at multiple delay times: a correlative study with H215O positron emission tomography in patients with symptomatic carotid artery occlusion200930122222910.1038/jcbfm.2009.204XuG.RowleyH. A.WuG.AlsopD. C.ShankaranarayananA.DowlingM.ChristianB. T.OakesT. R.JohnsonS. C.Reliability and precision of pseudo-continuous arterial spin labeling perfusion MRI on 3.0 T and comparison with 15O-water PET in elderly subjects at risk for Alzheimer's disease201023328629310.1002/nbm.14622-s2.0-77949708300KwongK. K.CheslerD. A.WeisskoffR. M.DonahueK. M.DavisT. L.OstergaardL.CampbellT. A.RosenB. R.MR perfusion studies with T1-weighted echo planar imaging199534687888710.1002/mrm.19103406132-s2.0-0028865808WongV. W. Y.LaiT. Y. Y.LamP. T. H.LamD. S. C.Prioritization of cataract surgery: visual analogue scale versus scoring system200575758759210.1111/j.1445-2197.2005.03436.x2-s2.0-22344434935DaiW.GarciaD.De BazelaireC.AlsopD. C.Continuous flow-driven inversion for arterial spin labeling using pulsed radio frequency and gradient fields20086061488149710.1002/mrm.217902-s2.0-57149104587MuirE. R.2010Atlanta, Ga, USAGeorgia Institute of TechnologyKolbH.KolbH.FernandezE.NelsonR.Simple anatomy of the retina1995Salt Lake City, Utah, USAUniversity of Utah Health SciencesGeversS.van OschM. J.BokkersR. P. H.KiesD. A.TeeuwisseW. M.MajoieC. B.HendrikseJ.NederveenA. J.Intra- and multicenter reproducibility of pulsed, continuous and pseudo-continuous arterial spin labeling methods for measuring cerebral perfusion20113181706171510.1038/jcbfm.2011.102-s2.0-79961003493KimS.-G.Quantification of relative cerebral blood flow change by flow-sensitive alternating inversion recovery (FAIR) technique: Application to functional mapping199534329330110.1002/mrm.19103403032-s2.0-0029151256WongE. C.BuxtonR. B.FrankL. R.Implementation of quantitative perfusion imaging techniques for functional brain mapping using pulsed arterial spin labeling1997104-523724910.1002/(SICI)1099-1492(199706/08)10:4/5<237::AID-NBM475>3.0.CO;2-X2-s2.0-0030725989EdelmanR. R.ChenQ.EPISTAR MRI: multislice mapping of cerebral blood flow199840680080510.1002/mrm.19104006032-s2.0-0031724562WangJ.AlsopD. C.LiL.ListerudJ.Gonzalez-AtJ. B.SchnallM. D.DetreJ. A.Comparison of quantitative perfusion imaging using arterial spin labeling at 1.5 and 4.0 Tesla200248224225410.1002/mrm.102112-s2.0-0036325034WangJ.ZhangY.WolfR. L.RocA. C.AlsopD. C.DetreJ. A.Amplitude-modulated continuous arterial spin-labeling 3.0-T perfusion MR imaging with a single coil: feasibility study2005235121822810.1148/radiol.23510316632-s2.0-15944405346WongE. C.BuxtonR. B.FrankL. R.A theoretical and experimental comparison of continuous and pulsed arterial spin labeling techniques for quantitative perfusion imaging199840334835510.1002/mrm.19104003032-s2.0-0031848388RoyB.AwasthiR.BindalA.SahooP.KumarR.BehariS.OjhaB. K.HusainN.PandeyC. M.RathoreR. K. S.GuptaR. K.Comparative evaluation of 3-dimensional pseudocontinuous arterial spin labeling with dynamic contrast-enhanced perfusion magnetic resonance imaging in grading of human glioma201337332132610.1097/rct.0b013e318282d7e22-s2.0-84878882901NordinL. E.LiT.-Q.BrogrenJ.JohanssonP.SjögrenN.HannesdottirK.BjörkC.SegerdahlM.WangD. J. J.JulinP.Cortical responses to amphetamine exposure studied by pCASL MRI and pharmacokinetic/pharmacodynamic dose modeling201368758210.1016/j.neuroimage.2012.11.0352-s2.0-84871650158LuhW.-M.TalagalaS. L.LiT.-Q.BandettiniP. A.Pseudo-continuous arterial spin labeling at 7 T for human brain: estimation and correction for off-resonance effects using a Prescan201369240241010.1002/mrm.242662-s2.0-84872973394PollockJ. M.TanH.KraftR. A.WhitlowC. T.BurdetteJ. H.MaldjianJ. A.Arterial spin-labeled MR perfusion imaging: clinical applications200917231533810.1016/j.mric.2009.01.0082-s2.0-65249115842GolayX.PetersenE. T.Arterial spin labeling: benefits and pitfalls of high magnetic field200616225926810.1016/j.nic.2006.02.0032-s2.0-33646844606PruessmannK. P.WeigerM.ScheideggerM. B.BoesigerP.SENSE: sensitivity encoding for fast MRI199942595296210.1002/(sici)1522-2594(199911)42:5<952::aid-mrm16>3.0.co;2-s2-s2.0-0032712873DuongT. Q.MuirE. R.Magnetic resonance imaging of the retina200953435236710.1007/s10384-009-0688-12-s2.0-70349311182RaoultH.PetrJ.BannierE.StammA.GauvritJ.-Y.BarillotC.FerréJ.-C.Arterial spin labeling for motor activation mapping at 3T with a 32-channel coil: reproducibility and spatial accuracy in comparison with BOLD fMRI201158115716710.1016/j.neuroimage.2011.06.0112-s2.0-79960619645RaoultH.GauvritJ.-Y.PetrJ.BannierE.Le RumeurE.BarillotC.FerréJ.-C.Innovations in functional MR imaging of the brain: arterial spin labeling and diffusion2011921087888810.1016/j.jradio.2011.04.0162-s2.0-80455122895TjandraT.BrooksJ. C. W.FigueiredoP.WiseR.MatthewsP. M.TraceyI.Quantitative assessment of the reproducibility of functional activation measured with BOLD and MR perfusion imaging: implications for clinical trial design200527239340110.1016/j.neuroimage.2005.04.0212-s2.0-23044502323ParkS.-H.WangD. J. J.DuongT. Q.Balanced steady state free precession for arterial spin labeling MRI: initial experience for blood flow mapping in human brain, retina, and kidney20133171044105010.1016/j.mri.2013.03.0242-s2.0-84880759059DeiblerA. R.PollockJ. M.KraftR. A.TanH.BurdetteJ. H.MaldjianJ. A.Arterial spin-labeling in routine clinical practice, part 1: technique and artifacts20082971228123410.3174/ajnr.a10302-s2.0-49749084841DeiblerA. R.PollockJ. M.KraftR. A.TanH.BurdetteJ. H.MaldjianJ. A.Arterial spin-labeling in routine clinical practice, part 2: hypoperfusion patterns20082971235124110.3174/ajnr.a10332-s2.0-49749108227DeiblerA. R.PollockJ. M.KraftR. A.TanH.BurdetteJ. H.MaldjianJ. A.Arterial spin-labeling in routine clinical practice. Part 3. Hyperperfusion patterns20082981428143510.3174/ajnr.a10342-s2.0-51649119606DixonW. T.SardashtiM.CastilloM.StompG. P.Multiple inversion recovery reduces static tissue signal in angiograms199118225726810.1002/mrm.19101802022-s2.0-0025875173YeF. Q.FrankJ. A.WeinbergerD. R.McLaughlinA. C.Noise reduction in 3D perfusion imaging by attenuating the static signal in arterial spin tagging (ASSIST)20004419210010.1002/1522-2594(200007)44:1<92::AID-MRM14>3.0.CO;2-M2-s2.0-0033936617GarciaD. M.DuhamelG.AlsopD. C.Efficiency of inversion pulses for background suppressed arterial spin labeling200554236637210.1002/mrm.205562-s2.0-22744437068DaiW.RobsonP. M.ShankaranarayananA.AlsopD. C.Reduced resolution transit delay prescan for quantitative continuous arterial spin labeling perfusion imaging20126751252126510.1002/mrm.231032-s2.0-84859702444MalekiN.DaiW.AlsopD. C.Optimization of background suppression for arterial spin labeling perfusion imaging201225212713310.1007/s10334-011-0286-32-s2.0-84862641330HickamJ. B.SiekerH. O.FrayserR.Studies of retinal circulation and AV oxygen difference in man19607134442-s2.0-0037889787HickamJ. B.FrayserR.Studies of the retinal circulation in man: observations on vessel diameter, arteriovenous oxygen difference, and mean circulation time196633230231610.1161/01.cir.33.2.302DeloriF. C.Noninvasive technique for oximetry of blood in retinal vessels19882761113112510.1364/AO.27.0011132-s2.0-0023912910AlmA.BillA.Ocular and optic nerve blood flow at normal and increased intraocular pressures in monkeys (Macaca irus): a study with radioactively labelled microspheres including flow determinations in brain and some other tissues1973151152910.1016/0014-4835(73)90185-12-s2.0-0015534943Wangsa-WirawanN. D.LinsenmeierR. A.Retinal oxygen: fundamental and clinical aspects2003121454755710.1001/archopht.121.4.5472-s2.0-0037390258DelaeyC.Van de VoordeJ.Regulatory mechanisms in the retinal and choroidal circulation200032624925610.1159/0000556222-s2.0-0033802949TamakiY.AraieM.KawamotoE.EguchiS.FujiiH.Non-contact, two-dimensional measurement of tissue circulation in choroid and optic nerve head using laser speckle phenomenon199560437338310.1016/s0014-4835(05)80094-62-s2.0-0028951869KimM.KimS. S.KwonH. J.KohH. J.LeeS. C.Association between choroidal thickness and ocular perfusion pressure in young, healthy subjects: enhanced depth imaging optical coherence tomography study201253127710771710.1167/iovs.12-104642-s2.0-84872172247ColemanD. J.SilvermanR. H.ChabiA.RondeauM. J.ShungK. K.CannataJ.LincoffH.High-resolution ultrasonic imaging of the posterior segment200411171344135110.1016/j.ophtha.2003.10.0292-s2.0-3042565175JiaY.BaileyS. T.WilsonD. J.TanO.KleinM. L.FlaxelC. J.PotsaidB.LiuJ. J.LuC. D.KrausM. F.FujimotoJ. G.HuangD.Quantitative optical coherence tomography angiography of choroidal neovascularization in age-related macular degeneration201412171435144410.1016/j.ophtha.2014.01.0342-s2.0-84903821646JiaY.WeiE.WangX.ZhangX.MorrisonJ. C.ParikhM.LombardiL. H.GatteyD. M.ArmourR. L.EdmundsB.KrausM. F.FujimotoJ. G.HuangD.Optical coherence tomography angiography of optic disc perfusion in glaucoma201412171322133210.1016/j.ophtha.2014.01.0212-s2.0-84903814394WangY.BowerB. A.IzattJ. A.TanO.HuangD.Retinal blood flow measurement by circumpapillary Fourier domain Doppler optical coherence tomography200813606400310.1117/1.29984802-s2.0-61549124515BaumannB.PotsaidB.KrausM. F.LiuJ. J.HuangD.HorneggerJ.CableA. E.DukerJ. S.FujimotoJ. G.Total retinal blood flow measurement with ultrahigh speed swept source/Fourier domain OCT2011261539155210.1364/BOE.2.0015392-s2.0-80053985896HaraznyJ. M.RaffU.WelzenbachJ.OttC.RittM.LehmannM.MichelsonG.SchmiederR. E.New software analyses increase the reliability of measurements of retinal arterioles morphology by scanning laser Doppler flowmetry in humans201129477778210.1097/HJH.0b013e328343c27a2-s2.0-79952752114AlderV. A.Ben-NunJ.CringleS. J.PO2 profiles and oxygen consumption in cat retina with an occluded retinal circulation1990316102910342-s2.0-0025195621ButteryR. G.HinrichsenC. F. L.WellerW. L.HaightJ. R.How thick should a retina be? A comparative study of mammalian species with and without intraretinal vasculature199131216918710.1016/0042-6989(91)90110-Q2-s2.0-0026004150PatelV.RassamS.NewsomR.WiekJ.KohnerE.Retinal blood flow in diabetic retinopathy1992305685567868310.1136/bmj.305.6855.6782-s2.0-0026706830KohnerE. M.PatelV.SalwanM. B.Role of blood flow and impaired autoregulation in the pathogenesis of diabetic retinopathy199544660360710.2337/diab.44.6.6032-s2.0-0029038779AdamisA. P.MillerJ. W.BernalM.-T.D'AmicoD. J.FolkmanJ.YeoT.-K.YeoK.-T.Increased vascular endothelial growth factor levels in the vitreous of eyes with proliferative diabetic retinopathy1994118444545010.1016/s0002-9394(14)75794-02-s2.0-0028123090KawagishiT.NishizawaY.EmotoM.KonishiT.MaekawaK.HagiwaraS.OkunoY.InadaH.IsshikiG.MoriiH.Impaired retinal artery blood flow in IDDM patients before clinical manifestations of diabetic retinopathy199518121544154910.2337/diacare.18.12.15442-s2.0-0028786923KonnoS.FekeG. T.YoshidaA.FujioN.GogerD. G.BuzneyS. M.Retinal blood flow changes in type I diabetes. A long-term, follow-up study1996376114011482-s2.0-0029882912ClermontA. C.AielloL. P.MoriF.AielloL. M.BursellS.-E.Vascular endothelial growth factor and severity of nonproliferative diabetic retinopathy mediate retinal hemodynamics in vivo: a potential role for vascular endothelial growth factor in the progression of nonproliferative diabetic retinopathy1997124443344610.1016/s0002-9394(14)70860-82-s2.0-0030770396FekeG. T.TagawaH.YoshidaA.GogerD. G.WeiterJ. J.BuzneyS. M.McMeelJ. W.Retinal circulatory changes related to retinopathy progression in insulin-dependent diabetes mellitus198592111517152210.1016/S0161-6420(85)33827-72-s2.0-0022367978GrunwaldJ. E.RivaC. E.SinclairS. H.BruckerA. J.PetrigB. L.Laser Doppler velocimetry study of retinal circulation in diabetes mellitus1986104799199610.1001/archopht.1986.010501900490382-s2.0-0022445342GherghelD.OrgülS.GugletaK.GekkievaM.FlammerJ.Relationship between ocular perfusion pressure and retrobulbar blood flow in patients with glaucoma with progressive damage2000130559760510.1016/S0002-9394(00)00766-22-s2.0-0033755581YanceyC. M.LinsenmeierR. A.Oxygen distribution and consumption in the cat retina at increased intraocular pressure19893046006112-s2.0-0024573755RivaC. E.GrunwaldJ. E.PetrigB. L.Autoregulation of human retinal blood flow. An investigation with laser doppler velocimetry19862712170617122-s2.0-0023039171ChenJ.SmithL. E. H.Retinopathy of prematurity200710213314010.1007/s10456-007-9066-02-s2.0-33947308503AshtonN.Pathological basis of retrolental fibroplasia195438738539610.1136/bjo.38.7.3852-s2.0-0006607497KinseyV. E.ArnoldH. J.KalinaR. E.SternL.StahlmanM.OdellG.DriscollJ. M.Jr.ElliottJ. H.PayneJ.PatzA.PaO2 levels and retrolental fibroplasia: a report of the cooperative study1977605655668ChungE. J.KimJ. H.AhnH. S.KohH. J.Combination of laser photocoagulation and intravitreal bevacizumab (Avastin®) for aggressive zone I retinopathy of prematurity2007245111727173010.1007/s00417-007-0661-y2-s2.0-34848909008RegilloC. D.BensonW. E.1998Lippincott-RavenGaudricA.SterkersM.CoscasG.Retinal detachment after choroidal ischemia1987104436437210.1016/0002-9394(87)90226-12-s2.0-0023615868MuirE. R.RenteríaR. C.DuongT. Q.Reduced ocular blood flow as an early indicator of diabetic retinopathy in a mouse model of diabetes201253106488649410.1167/iovs.12-97582-s2.0-84871898419MuirE. R.De La GarzaB.DuongT. Q.Blood flow and anatomical MRI in a mouse model of retinitis pigmentosa201369122122810.1002/mrm.242322-s2.0-84872840429ShihY.-Y. I.WangL.De La GarzaB. H.LiG.CullG.KielJ. W.DuongT. Q.Quantitative retinal and choroidal blood flow during light, dark adaptation and flicker light stimulation in rats using fluorescent microspheres201338229229810.3109/02713683.2012.7565262-s2.0-84873913528LiG.De La GarzaB.ShihY.-Y. I.MuirE. R.DuongT. Q.Layer-specific blood-flow MRI of retinitis pigmentosa in RCS rats2012101909610.1016/j.exer.2012.06.0062-s2.0-84864302474LiG.ShihY.-Y. I.KielJ. W.De La GarzaB.DuF.DuongT. Q.MRI study of cerebral, retinal and choroidal blood flow responses to acute hypertension201311211812410.1016/j.exer.2013.04.0032-s2.0-84878502702ZhangY.WeyH.-Y.NaterasO. S. E.PengQ.De La GarzaB. H.DuongT. Q.Anatomical, blood oxygenation level-dependent, and blood flow MRI of nonhuman primate (baboon) retina201166254655410.1002/mrm.228532-s2.0-79960583983MalekiN.DaiW.AlsopD. C.Blood flow quantification of the human retina with MRI201124110411110.1002/nbm.15642-s2.0-78851470708LemkeA.LaunF. B.SimonD.StieltjesB.SchadL. R.An in vivo verification of the intravoxel incoherent motion effect in diffusion-weighted imaging of the abdomen20106461580158510.1002/mrm.225652-s2.0-78649555277HajnalJ. V.BryantD. J.KasuboskiL.PattanyP. M.De CoeneB.LewisP. D.PennockJ. M.OatridgeA.YoungI. R.BydderG. M.Use of fluid attenuated inversion recovery (FLAIR) pulse sequences in MRI of the brain199216684184410.1097/00004728-199211000-000012-s2.0-0026496309BuxtonR. B.FrankL. R.WongE. C.SiewertB.WarachS.EdelmanR. R.A general kinetic model for quantitative perfusion imaging with arterial spin labeling199840338339610.1002/mrm.19104003082-s2.0-0031821720ZierlerK.A critique of compartmental analysis198110153156210.1146/annurev.bb.10.060181.0025312-s2.0-0019363329HerscovitchP.RaichleM. E.What is the correct value for the brain-blood partition coefficient for water?198551656910.1038/jcbfm.1985.92-s2.0-0021991039LuH.ClingmanC.GolayX.van ZijlP. C. M.Determining the longitudinal relaxation time (T1) of blood at 3.0 Tesla200452367968210.1002/mrm.201782-s2.0-4243184848MalekiN.DaiW.AlsopD. C.A systematic approach to optimizing background suppression for arterial spin labeling perfusion imaging2008161929MalekiN.AlsopD. C.DaiW.HudsonC.HanJ. S.FisherJ.MikulisD.The effect of hypercarbia and hyperoxia on the total blood flow to the retina as assessed by magnetic resonance imaging20115296867687410.1167/iovs.10-67622-s2.0-80055109168PengQ.ZhangY.NaterasO. S. E.van OschM. J. P.DuongT. Q.MRI of blood flow of the human retina20116561768177510.1002/mrm.227632-s2.0-79958259473ZhangY.Emeterio NaterasO. S.PengQ.RosendeC. A.DuongT. Q.Blood flow MRI of the human retina/choroid during rest and isometric exercise20125374299430510.1167/iovs.11-93842-s2.0-84866296514ZhangY.HarrisonJ. M.NaterasO. S. E.ChalfinS.DuongT. Q.Decreased retinal–choroidal blood flow in retinitis pigmentosa as measured by MRI2013126318719710.1007/s10633-013-9374-12-s2.0-84878756163Emeterio NaterasO. S.HarrisonJ. M.MuirE. R.ZhangY.PengQ.ChalfinS.GutierrezJ. E.JohnsonD. A.KielJ. W.DuongT. Q.Choroidal blood flow decreases with age: an MRI study201439101059106710.3109/02713683.2014.8929972-s2.0-84907206614VaghefiE.PontreB. P.JacobsM. D.DonaldsonP. J.Visualizing ocular lens fluid dynamics using MRI: manipulation of steady state water content and water fluxes20113012R335R34210.1152/ajpregu.00173.20112-s2.0-79961063237VaghefiE.DonaldsonP. J.An exploration into diffusion tensor imaging in the bovine ocular lens201343310.3389/fphys.2013.000332-s2.0-84879470789VaghefiE.PontreB.DonaldsonP. J.HunterP. J.JacobsM. D.Visualization of transverse diffusion paths across fiber cells of the ocular lens by small animal MRI200930101061107310.1088/0967-3334/30/10/0072-s2.0-70350444408VaghefiE.WalkerK.PontreB. P.JacobsM. D.DonaldsonP. J.Magnetic resonance and confocal imaging of solute penetration into the lens reveals a zone of restricted extracellular space diffusion201230211R1250R125910.1152/ajpregu.00611.20112-s2.0-84861871637VaghefiE.PontreB. P.WalkerK. L.DonaldsonP. J.Visualisation of solute fluxes in the lens reveals a barrier to extracellular diffusionInternational Conference on the Lens2012Kailua-Kona, Hawaii, USAVaghefiE.JacobsM. D.Uptake and distribution of gadolinium in the ocular lensProceedings of the 30th Annual International Conference of the IEEE Engineering in Medicine and Biology Society (EMBS '08)2008Vancouver, Canada843846