The clinical outcome of corneal collagen crosslinking (CXL) is typically evaluated several weeks after treatment. An earlier assessment of its outcome could lead to an optimization of the treatment, including an immediate re-intervention in case of failure, thereby, avoiding additional discomfort and pain to the patient. In this study, we propose two-photon imaging (TPI) as an earlier evaluation method. CXL was performed in human corneas by application of riboflavin followed by UVA irradiation. Autofluorescence (AF) intensity and lifetime images were acquired using a commercial clinically certified multiphoton tomograph prior to CXL and after 2h, 24h, 72h, and 144h storage in culture medium. The first monitoring point was determined as the minimum time required for riboflavin clearance from the cornea. As control, untreated samples and samples treated only with riboflavin (without UVA irradiation) were monitored at the same time points. Significant increases in the stroma AF intensity and lifetime were observed as soon as 2h after treatment. A depth-dependent TPI analysis showed higher AF lifetimes anteriorly corresponding to areas were CXL was most effective. No alterations were observed in the control groups. Using TPI, the outcome of CXL can be assessed non-invasively and label-free much sooner than with conventional clinical devices.
Corneal collagen crosslinking (CXL) is a medical procedure used in clinical practice to strengthen the mechanical stability of the cornea1,2. The process is based on the photodynamic interaction between a photosensitizer, typically riboflavin, and ultraviolet A (UVA) light which creates reactive oxygen species (ROS). These induce the formation of new crosslink bounds between collagen molecules and fibrils, thereby strengthening the tissue1,2. In clinical practice, CXL is commonly applied to patients diagnosed with keratoconus and ectasia secondary to laser refractive surgery. Recently, its feasibility to treat myopia, corneal edema, and infectious keratitis has also been demonstrated1,2,3,4.
Although the safety and reliability of CXL for halting the progression of keratoconus has been demonstrated in several clinical trials5,6,7,8,9,10, in the past years, reports of treatment failure have been presented11,12,13. The treatment outcome can be evaluated by assessing the patient’s corneal topography as well as the uncorrected and best corrected visual acuities1 over a period of several months. The first examination is performed not earlier than a one month after CXL. The outcome of CXL can also be assessed, several weeks after treatment, based on in vivo confocal microscopy (IVCM) by evaluating the corneal stroma reflectivity, corneal edema, and keratocyte apoptosis1,14,15,16, or based on anterior-segment optical coherence tomography (AS-OCT) through the detection of a hyperreflective line, i.e., the “corneal demarcation line”, which marks the transition between CXL and non-CXL areas17,18,19.
CXL failure is considered when the progression of disease cannot be halted. The reported rates of treatment failure go up to 16.5%11,12. Although, the course of treatment in case of failure is not yet defined, a second CXL procedure is one of the options13. This requires again corneal de-epithelialization which leads to patient’s pain, burning sensation, and tearing discomfort for several days1. An earlier evaluation of the outcome of CXL could lead to a faster intervention, such as immediate CXL redo, thereby, avoiding additional pain for the patient.
In this study, we propose two-photon imaging (TPI) to early evaluate the outcome of CXL. In our previous publications we have demonstrated that TPI can provide valuable information on the cornea20,21,22, inaccessible with current clinical devices, that can improve the evaluation of corneal donor buttons prior to transplantation23 or corneal disease diagnosis24. In this study, we show that based on TPI, CXL-induced changes to the corneal stroma can be assessed non-invasively, label-free, shortly after treatment, and with fast acquisition times.
Material and Methods
Human corneal donor buttons, unsuitable for transplantation, were obtained from the Lions Cornea Bank Saar-Lor-Lux, Trier/Westpfalz at the Department of Ophthalmology, Saarland University Medical Center, Homburg/Saar, Germany. A total of 39 donor buttons with average storage times of (17 ± 14) weeks were used. From stroma to endothelium, the samples were on average 962 μm thick, with thicknesses varying between approximately 675 and 1190 μm. No significant changes were observed during the experiment duration (thickness changes below 10% in 144 h). Thickness data were obtained using multiphoton tomography. Prior to the experiments, samples were stored in culture Medium II with Dextran T500 (#F9017, Biochrom GmbH, Berlin, Germany) supplemented with 5% new-born calf serum (#S0415, Biochrom GmbH, Berlin, Germany) at 34 °C in a 5% CO2 atmosphere.
This study was approved by the ethics committee of the University of Saarland and it was conducted according to the principles for research use of human tissue of the World Medical Association Declaration of Helsinki. Written and informed consent for the use of their tissue for scientific research was obtained for all subjects.
Accelerated corneal collagen crosslinking
The samples were divided into 3 groups and treated as illustrated in Fig. 1:
CXL (n = 14): CXL was performed, after corneal de-epithelialization using a blunt hockey knife, through the application of 0.1% riboflavin solution (Vibex rapid™ Avedro, Inc., MA, USA) every 2 min for 20 min followed by irradiation with an UVA light source for 10 min using an in-house adapted CXL system consisting of a 365 nm light-emitting diode (LED) mounted on an inverted microscope. A total energy dose of 7.2 J/cm2 was applied (irradiance of 12 mW/cm2). The feasibility of our setup to perform CXL was confirmed by comparing with samples treated using a commercial CXL system. Both systems yielded similar results, which showed the capability of our setup to induce CXL25.
RFN (n = 9): de-epithelialized corneal donor buttons were infused with 0.1% riboflavin solution (every 2 min for a total of 20 min) without UVA irradiation.
Control (n = 10): the epithelial layer was removed using a blunt hockey knife without further treatment.
TPI acquisition was performed for all groups immediately after epithelial removal (baseline) and after 2 h, 24 h, 72 h, and 144 h storage. Riboflavin clearance from the tissue was achieved by 2 h immersion in culture Medium II with Dextran T500 supplemented with 5% new-born calf serum. Between measurements, samples were stored as described above. For image acquisition, samples were mounted on an artificial anterior chamber. Live cell imaging solution (#A14291DJ, Life Technologies, USA) was used to hydrate them.
Image acquisition was performed using the commercial tomograph MPTflex (JenLab GmbH, Berlin, Germany; Fig. 2) clinically certified for human skin imaging. The system consists of a movable housing that includes the laser and other optoelectronic components (optoelectronic housing), a flexible 360° measurement head that enables TPI measurement in multiple angles, and an articulated mirror-arm that guides the laser light of a 80 MHz tunable near infrared (NIR) Ti:sapphire laser with pulse widths of 100 femtosecond (fs) (Fig. 2). The laser beam is focused onto the sample by a 20x NA 1.0 water immersion objective with long working distance (1700 μm) which allows to image the entire corneal thickness. The measurement head contains galvanometric x-y scanners and stepper motors to change the imaged regions in x, y, and z directions, respectively. Signals are collected in reflection geometry by the objective and detected in two spectral channels by photomultiplier tubes (PMT) also placed inside the measurement head. With this configuration second-harmonic generation (SHG) and autofluorescence (AF) signals are detected simultaneously (Fig. 2B). The PMT in the AF channel is coupled to a time-correlated single photon counting (TCSPC) module. Image acquisition of the cornea samples was performed using a fixed excitation wavelength of 760 nm.
At each time point, six x-z cross-sectional images and en-face images of two non-overlapping regions were acquired. For the latter, images up to a depth of 300 μm, with 5 μm z-steps in-between were recorded. Image acquisition times were typically 6.2 s for each en-face image with 512 × 512 pixels, and 68 s for each cross-sectional image with 512 × 1024 pixels (field-of-view = 600 × 1200 μm2). The laser power was varied between 20 and 50 mW as a function of imaging depth. Images were acquired with a lateral and axial resolutions of 450 nm and of 2–3 μm, respectively.
The influence of the CXL on the corneal stroma was evaluated using the stroma AF intensity and lifetime. Variations in the stroma AF intensity (ΔI) were computed as:
where Ii and It are the initial stroma AF intensity (baseline) and the AF intensity at a time t, respectively. CXL-induced changes to ΔI were measured at t = 2, 24, 72, 144 h after treatment. At each time point, the AF intensity was obtained from to total number of photons collected. To determine ΔI during riboflavin clearance from the tissue, the signal intensity was measured at t = 0, 30, 60, 90, 120 min after riboflavin application.
The corneal stroma mean AF lifetime was computed using the commercial software SPCImage (Becker & Hickl GmbH, Berlin, Germany). Briefly, to retrieve the AF lifetime, the obtained TCSPC histogram was fitted, after deconvolution with the instruments response function (IRF), by an exponential function in the form:
where F(t) is the fluorescence intensity at time t, and ai is the relative contribution of the fluorescence lifetime τi. The mean AF lifetime (τm) was computed as the average of all lifetime components (τi) weighted by their relative contributions (ai). The IRF was deduced from the measured SHG signal profile generated by crystallized urea.
The statistically significance of alterations on the stroma AF intensity variation (ΔI) and lifetime due to CXL were determined using the commercial software GraphPad Prism version 6.05 (GraphPad Software Inc., California, USA). The results are shown as averages and standard deviations (SD). The parametric t-test was used. In the cases where data did not follow a Gaussian distribution, the non-parametric equivalent, Mann-Whitney U test, was used instead. We considered p values lower than 0.05 as being significant.
Two-photon excited autofluorescence and riboflavin fluorescence
In the corneal stroma, endogenous sources of fluorescence include collagen reduced coenzymes nicotinamide adenine dinucleotide and nicotinamide adenine dinucleotide phosphate (NAD(P)H) and negligible amounts of flavin mononucleotide and flavin adenine dinucleotide (flavins). These fluorophores have fluorescence emission maxima around 485 nm, 460 nm, and 525 nm respectively26,27,28. Riboflavin’s fluorescence, with a maximum emission around 530 nm, spectrally overlaps with that of endogenous fluorophores of the cornea. Thus, changes of the AF intensity and lifetime were analyzed after riboflavin clearance from the tissue.
The minimum time required for riboflavin to completely clear out from the tissue was determined in 4 corneal donor buttons using TPI. The AF intensities and lifetimes were monitored prior to riboflavin application and every 30 min for a period of 2 h. The observed changes in ΔI and AF lifetime are shown in Fig. 3.
Prior to the application of the photosensitizer, the tissue had a bi-exponential AF decay with mean AF lifetime of (1.24 ± 0.03) ns. Immediately after its application (t = 0 min), significant increases in both the average AF lifetime and average ΔI were observed (Fig. 3). Additionally, at t = 0 min, the tissue exhibited a single exponential decay of (3.12 ± 0.06) ns. This is good agreement with the fluorescence lifetime recorded for the pure 0.1% riboflavin solution ((3.37 ± 0.06) ns). After 30 min of storage, riboflavin clearance from the cornea become noticeable. Two areas with distinct lifetimes were visible which indicated shorter AF lifetimes anteriorly than posteriorly (Fig. 3A). The average lifetime and ΔI at t = 30 min were significantly lower than those measured at t = 0 min, but still significantly higher than those observed prior to riboflavin application (Fig. 3B,C). The average AF lifetime and ΔI continued to considerably decrease after 60 min and 90 min storage and values equivalent to initial AF values were reached after 120 min storage (Fig. 3).
CXL-induced alterations to the corneal stroma AF
The changes induced by the CXL to the corneal stroma AF intensity and AF lifetime are depicted in Figs 4 and 5, respectively. Figure 4A shows 3D representations, reconstructed from individual and sequential en-face AF intensity images, of corneas in CXL, RFN, and control groups after 72 h storage. The average changes in ΔI are shown in Fig. 4B. For control and RFN corneas, the AF intensity was constant over time, whereas after CXL, ΔI was significantly higher as soon as 2 h after treatment and remained significantly higher during subsequent measurements.
Representative cross-sectional AF lifetime images of corneas of control, RFN, and CXL groups, and their average mean AF lifetime over time are shown in Fig. 5. Following CXL treatment, a significant increase in the tissue mean AF lifetime was observed. This increase was observed for all measured time points. No significant changes on the average AF lifetime of consecutive measurements were observed for samples in the control and RFN groups (Fig. 5).
Figure 6 shows depth-dependent changes on the AF lifetime and intensity induced by CXL. Interestingly, 2 h after CXL, both the tissue AF lifetime and intensity increased uniformly with depth. However, with time both parameters become progressively higher in the anterior than posterior stroma (Fig. 6A,B). Additionally, for the same corneal depth the AF intensity and lifetime increase progressively with time (Fig. 6C).
In this study, we evaluated the outcome of CXL for corneal donor buttons using TPI. We showed that CXL induces significant increases in AF intensity and lifetime of the corneal stroma. No significant alterations were observed for control and RFN groups. Moreover, a depth analysis of the stroma AF demonstrated the feasibility of TPI to determine the transition between crosslinked and non-crosslinked areas.
So far, the clinical evaluation of the outcome of CXL is typically performed several weeks after treatment. Methods capable of assessing CXL outcome soon after treatment are important, since they could provide a faster determination of treatment efficiency which may allow immediate CXL redo in case of failure. In the recent years, efforts to obtain such an examination tool have been carried out. Namely, the feasibility of Brillouin microscopy to assess corneal alterations soon after CXL was been shown ex vivo29,30,31. Based on this imaging modality the Young’s modulus of the tissue can be retrieved, and a significant increase in the corneal stiffness (associated with an increase in the Brillouin shift) has been reported soon after CXL29,30,31,32. Nevertheless, Brillouin microscopy has a major drawback, since long acquisition times are necessary to obtain a single image (between 30 min and 120 min per image)29,30,31. The feasibility of SHG imaging to evaluate changes to the collagen fibers organization due to CXL has also been demonstrated3,33,34,35,36. The increase in stromal stiffness due to the creation of new crosslinks between collagen induced by CXL leads to changes in the collagen fibers organization. In 2011, Bueno et al. observed such changes in SHG images of porcine and bovine corneas immediately after CXL33. The evaluation of the collagen fibers of forward-detected SHG images showed an increase in the fiber waviness after treatment34. Recently, the collagen-fiber orientations of healthy, keratoconus, and keratoconus corneas after CXL have also been evaluated and compared36,37.
The focus of this paper is to demonstrate the potential of analyzing the stroma AF as a tool for early assessment of the outcome of CXL. So far, a quantitative time- and depth-dependent analysis of CXL-induced changes to the human stroma AF intensity and lifetime has not yet been performed, although one group reported on stroma AF lifetime alterations in rabbit eyes38 two-weeks after performing CXL.
The fluorescence of the photosensitizer used to perform CXL (riboflavin) must be separated in order to evaluate CXL-induced changes on the stroma AF. Riboflavin fluorescence emission overlaps with that of the tissue endogenous fluorophores, thus making a spectral separation of the fluorescent components difficult. Nevertheless, fluorophore’s separation based on their fluorescence lifetime is, in principle, possible. Whereas riboflavin has a fluorescence lifetime of (3.37 ± 0.06) ns, NAD(P)H has two AF lifetime components, a fast one in the picosecond range associated with its free component and typical lifetimes of 2.2 ns to 2.4 ns associated with its protein-bound component39. For collagen, a fast lifetime component around 0.3 ns and a slow component between 2.0 and 2.5 ns have been reported40. In this study, CXL-induced changes to the stroma AF were evaluated after riboflavin was absent from the tissue. Riboflavin clearance was monitored based on the fluorescence intensity and lifetime. This fluorophore leads to a strong increase in the measured fluorescence intensity and lifetime (Fig. 3). At t = 0 min, an 9-fold signal intensity increase was observed due to the riboflavin fluorescence. After 30 min, larger lifetimes were observed posteriorly, indicating a decreasing riboflavin concentration in the anterior stroma. Intensity and lifetime values returned to values equivalent to those of stromal intrinsic fluorescence after 120 min (Fig. 3) indicating the waiting time required for the riboflavin to clear out of the tissue under our experimental conditions. The time point of first CXL evaluation was set to fit this condition. For an in vivo application, the time required for riboflavin clearance in patients must also be quantified in the future.
The stroma AF intensities and lifetimes were evaluated prior to CXL (baseline) and 2 h, 24 h, 72 h, and 144 h after the procedure. Additionally, untreated corneas (control) and corneas treated only with riboflavin (RFN) were monitored at the same time points. For control and RFN groups no changes were observed in the stroma AF intensity and lifetime over time. However, in CXL corneas, significant increases in the AF intensity and in the AF lifetime were observed as soon as 2 h after treatment, which remained elevated in subsequent measurements (Figs 4 and 5). An increase in both values has also been observed in the stroma of rabbit’s corneas 2 weeks after CXL38. The observed increases are correlated to an increase in the number of crosslink bounds between collagen molecules. It has been found in vitro that collagen gels with reduced crosslinks have lower AF lifetimes, whereas models of enhanced CXL exhibit a mean AF increase of 9%41,42. Therefore, the observed increase in the stroma AF lifetime after CXL indicates an increase in the number of new crosslinks bound between collagen, i.e., a positive treatment outcome. Although alterations to keratocytes metabolic activity may also influence the stroma AF lifetime, we have observed that these cells had a small contribution to the overall stroma AF signal.
A depth-dependent analysis of the AF intensity and lifetime demonstrated the feasibility to discriminate between crosslinked and non-crosslinked areas (Fig. 6). A generalized increase in the AF intensity and AF lifetime was observed 2 h after CXL. After 24 h, 72 h, and 144 h the increase in both parameters was more pronounced for the anterior stroma. This indicates that a higher number of new crosslink bounds were induced anteriorly, corresponding to the areas were CXL was most effective. Higher CXL efficiencies anteriorly are also typically observed using IVCM and AS-OCT and are related to the limited penetration depths of UVA in the tissue. Interestingly, increases in the AF intensity and lifetime were observed over time for the same corneal depth (Fig. 6). These alterations may also shed some light into the mechanism by which CXL induces corneal stiffening.
In conclusion, we have demonstrated that corneal stroma changes induced by CXL can be observed, in ex vivo tissue, as soon as 2 h after treatment based on the stroma AF intensity and lifetime. TPI imaging can provide a non-invasive, label-free, and fast evaluation of CXL outcome sooner than conventional clinical devices. Currently, the main limitations of TPI imaging in vivo are the need of contact interface, the high price, and the need for clinical certification in ophthalmology. Nevertheless, we hope to overcome these limitations and pave the way to introduce new devices based on TPI for clinical imaging of the human cornea. Such devices could highly improve ophthalmologic imaging, including an earlier assessment of expected CXL efficiency.
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The authors would like to acknowledge the support by the European Union’s Horizon 2020 research and innovation program under grant agreement No. 726666 (LASER-HISTO), the European project FLIM-VERTICO, and support by the Deutsche Forschungsgemeinschaft (DFG, German Research Foundation) and Saarland University within the funding programme Open Access Publishing.
The authors declare no competing interests.
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