Randomized, masked, in vitro comparison of three commercially available tear film osmometers
Authors Rocha G, Gulliver E, Borovik A, Chan CC
Received 8 November 2016
Accepted for publication 10 January 2017
Published 27 January 2017 Volume 2017:11 Pages 243—248
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 3
Editor who approved publication: Dr Scott Fraser
Guillermo Rocha,1 Eric Gulliver,1 Armand Borovik,2 Clara C Chan2
1Department of Ophthalmology, University of Manitoba, Winnipeg, 2Department of Ophthalmology and Vision Sciences, University of Toronto, Toronto, Ontario, Canada
Purpose: The purpose of this study was to compare the precision and accuracy of commercially available tear film osmometers.
Methods: Contrived tear solution target values representing the physiological range of tear osmolarity (normal eyes 297 mOsm/L, moderately dry eyes 342 mOsm/L, and severe dry eyes 383 mOsm/L) were constructed using a mix of mono- and divalent electrolytes, metabolites, serum albumin, and pH balanced to 7.4. Solution values were randomized and masked from the investigators during testing. Osmometers (Wescor 5520 Vapro Pressure Osmometer: device A, TearLab Osmolarity System: device B, and i-Med Pharma i-Pen: device C) were calibrated according to manufacturer instructions. Each level was tested 64× on each osmometer across two sites. Accuracy was reported as a correlation coefficient against expected linear dilutions, precision was calculated as percent coefficient of variation.
Results: Device A reported a correlation with known solutions of r2=0.98, with averages of 305.6±4.0, 352.2±5.5, and 389.8±4.0 mOsm/L, and coefficient of variations (CVs) of 1.3%, 1.6%, and 1.0%, respectively. Device B reported an r2=0.96, with averages of 300.6±3.7, 341.4±7.9, and 376.8±5.1 mOsm/L, and CVs of 1.2%, 2.3%, and 1.4%, respectively. Device C reported an r2=0.03, with averages of 336.4±21.5, 342.0±20.7, and 345.7±22.0 mOsm/L, and CVs of 6.4%, 6.1%, and 6.4%, respectively.
Conclusion: In this randomized, masked, in vitro study, device A and device B had significantly better accuracy and precision in measuring osmolarity of contrived tear solutions of known target values compared to device C. Device C showed insufficient performance to accurately and precisely delineate osmolarity levels in the physiological range. Furthermore, in vivo studies would be required to compare performance in human subjects.
Keywords: tear osmolarity, TearLab Osmometer, i-Pen Osmometer, electrical impedance, Wescor Osmometer, precision
Dry eye disease (DED) is a multifactorial disease of the tears and ocular surface that results in symptoms of discomfort, visual disturbance, and tear film instability with potential damage to the ocular surface. It is accompanied by increased osmolarity of the tear film and inflammation of the ocular surface.1 According to the 2007 TFOS DEWS report, tear osmolarity and tear instability are recognized as core mechanisms of the disease.1 Osmolarity above the homeostatic range causes damage to the ocular surface, a loss of goblet cells, disturbance of mucin expression and initiates a release of inflammatory mediators into the tears.1 As a global marker for DED, tear osmolarity is known to increase in both aqueous deficient and evaporative dry eye, correlates with disease severity, and is superior in overall accuracy to any other single test for dry eye diagnosis.2–5 Furthermore, it is a useful metric to monitor disease course after a specific treatment in the clinic and in clinical trials.6–10
Measurement of tear osmolarity, however, is a nontrivial exercise. The volume of tear fluid available for analysis in a dry eye patient is well below the ~10 μL volume required by traditional laboratory osmometers. Although, the osmolarity on the central cornea has been theorized to transiently attain levels upward of 1,000 mOsm/L11 the physiological range of tear osmolarity in the lower meniscus is highly compressed, ranging from 275 to 400 mOsm/L.3 Clinically, relevant differences of ~11 mOsm/L indicate a therapeutic change,12 while the expected difference between mean values of normal and DED patients is ~20 mOsm/L,13 and inter-eye differences of ≥8 mOsm/L are considered diagnostic of tear film instability.14 Accordingly, tear osmometers require a high degree of precision and accuracy.
This study compares the analytical performance of three commercially available devices: Wescor 5520 Vapro Pressure Osmometer (Wescor Inc, Logan, UT, USA – device A), TearLab Osmolarity System (TearLab Corp, San Diego, CA, USA – device B), and i-Pen (i-Med Pharma, Dollard-des-Ormeaux, Quebec, Canada – device C). Device A works by measuring the electrical resistance of a thermocouple, on which fluid condenses and changes the local temperature when exposed to the sample fluid. Device B and Device C, per their respective manufacturer’s instruction manual, work by measuring electrical impedance and have been commercialized as point-of-care diagnostics.
Contrived tear solution target values representing the physiological range of tear osmolarity (normal 297 mOsm/L, moderate 342 mOsm/L, and severe 383 mOsm/L) were constructed using a mix of mono- and divalent electrolytes, metabolites, serum albumin and were balanced using NaOH and HCl to pH 7.4. Specifically, sodium chloride (165 mM), potassium chloride (32 mM), sodium bicarbonate (49 mM), sodium phosphate monobasic (5 mM), sodium phosphate dibasic (6 mM), urea (10 mM), bovine serum albumin (0.15 mM) were mixed to a final osmolarity of 479±1.6, as measured on device A. Dilutions of 61.9%, 71.4%, and 80.0% resulted in an expected osmolarity of 297, 342, and 383 mOsm/L, respectively, representing the normal, moderate, and severe ranges in DED. Similar contrived tear fluid formulations have been used in US Food and Drug Administration submissions as valid surrogates for determining the performance of osmometers.15
At each day of testing, device A was calibrated according to manufacturer instructions using National Institute of Standards and Technology (NIST) traceable sodium chloride. The factory calibration of device B was verified each day of testing using manufacturer supplied electronic controls as well as NIST traceable sodium chloride. No calibration was performed for device C as per the user instruction manual.
Solution values were randomized and masked from the investigators during testing. Investigators were trained in clinical ophthalmology, but were not intimately familiar with the osmolarity devices under test. For device A, a 20 μL sample of contrived tear was pipetted onto a pre-cut piece of filter paper loaded in the machine. For device B and device C, 0.5 mL microcentrifuge tubes containing contrived tears of varying osmolarity levels were inverted to collect a small volume of fluid in the cap. After opening the microcentrifuge tube, the tip of each device was placed gently atop the fluid residing in the cap. Care was taken not to immerse the tips of the sensors into the fluid according to manufacturers recommended procedures. Contrived tear levels were tested 64× on each of the three osmometers across two sites, as 64 readings per device would be required to detect a difference of 8±8 mOsm/L between the devices at an alpha error =0.05 to provide a study power of 90%. Temperature was recorded throughout testing and was maintained between 21°C and 25°C. Data were tested for normality using the Kolmogorov–Smirnov test. The statistical analysis of accuracy was estimated as a correlation coefficient against expected osmolarity to provide an unbiased reference for each of the three devices. Given the compressed dynamic range of tear osmolarity, low precision devices will have a very poor correlation coefficient (r2<0.5) in this experiment, whereas devices with r2 >0.7–0.8 will likely be sufficient for therapeutic tracking. The inclusion of device A provides a convenient metric by which to gauge high quality performance. Second, a Bland–Altman analysis for both point-of-care devices (device B and device C) was performed using expected osmolarity as a reference, where the difference from expected is plotted as the dependent variable, and descriptive statistics of these deviations presented. Precision was calculated as percent coefficient of variation (ratio of the standard deviation to the sample mean) as measured against theoretical dilutions, as well as the 95% confidence intervals on the Bland–Altman deviations. Note that as these were prepared samples with a fixed dynamic range, coefficients of variation allow direct comparison of precision.
All data measured at each level across each osmometer were normally distributed using the Kolmogorov–Smirnov test (P>0.10). Descriptive statistics for each osmometer are reported in Table 1. As shown in Figure 1, device A reported a linear regression of 0.98x+16.7 against estimated osmolarity with an r2=0.98, with averages of 305.6±4.0, 352.2±5.5, and 389.8±4.0 mOsm/L, and CVs of 1.3%, 1.6%, and 1.0%, respectively. As shown in Figure 2, device B reported a linear regression of 0.88x+38.2 against estimated osmolarity an r2=0.96, with averages of 300.6±3.7, 341.4±7.9, and 376.8±5.1 mOsm/L, and CVs of 1.2%, 2.3%, and 1.4%, respectively. As shown in Figure 3, device C reported a linear regression of 0.11x+304.77 against estimated osmolarity an r2=0.03, with averages of 336.4±21.5, 342.0±20.7, and 345.7±22.0 mOsm/L, and CVs of 6.4%, 6.1%, and 6.4%, respectively. When device A was used as a reference standard in Figure 4, device B reported a linear regression of 0.90x+26.5 with an r2=0.96, while device C reported a linear regression of 0.12x+300.2 with an r2=0.03.
Table 1 Combined osmolarity data on contrived tear solutions for device A, device B, and device C osmometers
Figure 1 Device A osmometer readings vs ideal dilution osmolarity.
Figure 2 Device B osmometer readings vs ideal dilution osmolarity.
Figure 3 Device C osmometer readings vs ideal dilution osmolarity.
Figure 4 Device B and device C osmometers vs device A measured osmolarity.
The Bland–Altman analysis shown in Figure 5 revealed that the average deviation of device B was −1.6±7.1 mOsm/L from theoretical, with a range of −20 to +19 mOsm/L, while device C (Figure 6) had a deviation of −4.1±36.7 mOsm/L with a range of −91 to +70 mOsm/L. On an absolute scale, device B had 88% (56/64) measurements within 10 mOsm/L from target, while device C had only 15% (10/64) within 10 mOsm/L. Of note, the precision of device B was far better in the low range close to the clinical cutoff, with a standard deviation of ±3.7 mOsm/L in that category. Device C remained imprecise in that range, with a standard deviation of ±21.5 mOsm/L at the low end. Figure 7 shows a histogram of the deviations from ideal for each device.
Figure 5 Bland–Altman plot for device B.
Figure 6 Bland–Altman plot for device C.
Figure 7 Distribution of deviation from ideal osmolarity values.
Elevated tear osmolarity is known to be a central pathogenic cause of ocular surface damage1 and is regarded to be a medically necessary test to assist in the diagnosis of DED. Because of the confounding nature of nerve damage due to hyperosmolarity16 a clinician cannot rely upon symptoms or other clinical signs to determine who in fact, has hyperosmolarity, and whether or not the cornea is under physiological stress as a result. Accordingly, the measurement of tear osmolarity is necessary to fully understand the severity of dry eye and the status of the ocular surface.3 Yet, because of the relatively compressed dynamic range and low volume of tear fluid available, high precision meters (~<2.5% CV) that measure nanoliter volumes of tear fluid are required to properly assess tear film osmolarity.
Device A, being a laboratory osmometer, requires 10 μL of tear, and is not considered viable as a point-of-care instrument, but serves as a reference for this study. Device A and the point-of-care nanoliter device B had similar performance and sufficient resolution to accurately and precisely delineate osmolarity levels consistent with normal, moderately dry, and severely dry eyes. The study data are consistent with previous analysis of device B, which showed a regression of y=0.98x+6.51, with an r2=0.95 from untrained users of the device, with total coefficients of variation ranging from 1.87% to 2.47%.17 Another published study comparing device A to device B found a r2=0.9 correlation with a slightly higher standard deviation ±9.4 mOsm/L than this study,18 although the interpretation was similar; that device A and device B have concordance on tear samples. These data also support independent studies on human tear samples that compared device B to the Clifton freezing point depression osmometer, wherein the majority of test results fell within 95% confidence limits and absolute values differed by <1%.19
In this in vitro study, device C was significantly less accurate and less precise in its ability to identify osmolarity levels. Essentially, device C showed no relationship between the osmolarity of the standard solution and the results it produced. The data had a large spread across the measurement range, as demonstrated by the low correlation coefficient (r2=0.03) and significant overlap between the levels. The user manual for device C states that its intended use is
for the quantitative measurement of osmolarity (concentration of dissolved, active particles in tissue immersed in solution) of human tears in normal and Dry Eye Disease patients.20
The manual also provides reference data on tear osmolarity that matches generally accepted ranges for human tear osmolarity levels,3 including a normal average of 302 mOsm/L, 327 mOsm/L for dry eye, and a full range between 275 and 400 mOsm/L.20 One hypothesis as to why there was such a difference between device C and other osmometers (device A and device B) tested in this study is that the solution resistance values measured in this study (without any tissue presence) are not representative of the impedance values of ocular tissues immersed in solution. However, since the impedance of ocular surface tissues should be far higher than the impedance of tears,21 this hypothesis does not fully explain why the device returns values within the expected range of tear osmolarity. The conductivity of the contrived tear solutions was constructed to match that of tear fluid. It is perhaps the case that the measurement of conjunctival tissue in vivo represents a fundamentally different impedance system than the one studied here. Yet if that is the intended use of device C, it leads one to question the inescapable in vivo scenario where human tear fluid bridges the electrodes of device C while attempting to measure the tissue impedance. As electric fields follow the path of least resistance, one would have to completely dry the conjunctiva prior to measurement to isolate the tissue impedance from of the tear fluid in vivo. If device C is not calibrated to measure impedance within the range of this manuscript, it should not return values within the expected human range on solutions known to represent tear osmolarity. It should be well out of range, yet that is not what was found. Device C provided random values across the full range of human tear osmolarity for each of the tested solutions. Either this is a failure in quality or failure in design of device C. Future studies could involve an impedance model constructed with far higher intrinsic resistance than the contrived tear solutions used in this study to investigate the values returned by device C. If the values are still within the human range, it means the device is incapable of distinguishing systems of different impedance, making the output suspect. If the values are out of range, it means the device is calibrated for the solutions tested here and it is simply too imprecise to be used in the clinic to usefully measure tear osmolarity.
In this randomized, masked, in vitro study, device A and device B performed similarly in their ability to accurately and precisely delineate the osmolarity of contrived tear solutions of known target values; device C, however, demonstrated insufficient performance to precisely and accurately identify and delineate different osmolarity levels within the physiological range. Additional studies on human subjects would be required to compare performance in a clinical setting.
The study was funded by TearLab Corporation. The authors report no other conflicts of interest in this work.
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