**Purpose**:
To determine if the lens volume changes during accommodation.

**Methods**:
The study used data acquired on 36 cynomolgus monkey lenses that were stretched in a stepwise fashion to simulate disaccommodation. At each step, stretching force and dioptric power were measured and a cross-sectional image of the lens was acquired using an optical coherence tomography system. Images were corrected for refractive distortions and lens volume was calculated assuming rotational symmetry. The average change in lens volume was calculated and the relation between volume change and power change, and between volume change and stretching force, were quantified. Linear regressions of volume-power and volume-force plots were calculated.

**Results**:
The mean (±SD) volume in the unstretched (accommodated) state was 97 ± 8 mm^{3}. On average, there was a small but statistically significant (*P* = 0.002) increase in measured lens volume with stretching. The mean change in lens volume was +0.8 ± 1.3 mm^{3}. The mean volume-power and volume-load slopes were −0.018 ± 0.058 mm^{3}/D and +0.16 ± 0.40 mm^{3}/g.

**Conclusions**:
Lens volume remains effectively constant during accommodation, with changes that are less than 1% on average. This result supports a hypothesis that the change in lens shape with accommodation is accompanied by a redistribution of tissue within the capsular bag without significant compression of the lens contents or fluid exchange through the capsule.

^{1–4}Contraction of the ciliary muscle decreases the tension on the zonule, which relaxes the forces applied on the lens. As a result, lens diameter decreases, lens thickness increases, and the anterior and posterior surfaces of the lens become steeper. The change in lens shape with accommodation is the product of an intricate mechanical process that has been studied using experimental techniques and computational models.

^{5–9}This assumption is consistent with the results of in vivo biometric studies using Scheimpflug and magnetic resonance imaging (MRI) that found that the volume of the lens and lens nucleus is constant with accommodation.

^{10,11}On the other hand, there are also studies suggesting that the lens volume increases with accommodation.

^{12–15}Two hypotheses have been proposed to explain how the lens volume could change during accommodation. The first hypothesis is that the lens substance is slightly compressible.

^{12,15}The change in lens volume with accommodation is then due to changes in the compressive force exerted by the capsule on the lens substance. The second hypothesis is that there is fluid exchange between the lens and its surroundings through the lens capsule during accommodation.

^{13,14,16}

^{15}to an average of 5.9% measured in vitro in bovine lenses.

^{13,14}However, Wendt et al.

^{17}showed that these changes are near or below the measurement uncertainty. In addition, the volume change reported in vivo was highly variable and irregular.

^{15}On average, volume was found to decrease in response to a 4-diopter (D) stimulus, but to increase in response to an 8-D stimulus. A study on a larger sample size or one with lower measurement uncertainty is needed to establish with greater confidence if the lens volume changes with accommodation.

*Macaca fascicularis*; age 1.4–14.3 years, average = 6.4 ± 2.8 years) that had been subjected to lens-stretching experiments in our second-generation custom-built lens stretcher (EVAS II).

^{18,19}All eyes were from different animals (i.e., there were no paired eyes). The eyes were selected by excluding tissues with any detectable rotational asymmetry in stretching, any lateral shift of the lens, or insufficient stretching force. The selection criteria helped ensure that the lenses underwent rotationally symmetric stretching with no systematic decentration. Asymmetry and decentration were assessed independently by two observers by examination of top views of the lens recorded at each step during stretching.

^{18–21}In summary, eight attachments (shoes) fitting the scleral curvature of the test eye are bonded to the globe. The posterior pole, cornea, and iris are then removed, and full-thickness incisions are made in the sclera between the shoes to produce eight segments for stretching. The prepared tissue sample, consisting of the intact crystalline lens, zonular fibers, ciliary body, and the segmented sclera, is mounted in the tissue chamber of EVAS II. The tissue chamber is filled with Dulbecco's modified Eagle's medium (DMEM) until the tissue is completely immersed. The lens-stretching system simulates disaccommodation/accommodation by applying and releasing a radial force on the eight scleral shoes.

^{18–22}The lens stretcher provides measurements of the stretching force at each step. Lens power was measured by finding the focus of a ring-shaped beam with a ray height of 1.5 mm from the lens center using an optical system based on the Scheiner principle.

^{19–21}The lens shape was obtained from cross-sectional images acquired with a custom-built time-domain OCT system. A detailed description of the system and imaging protocol have been published previously.

^{19,21,23}Images were recorded with 5000 points per A-line at a rate of 20 A-lines per second, with 500 A-lines per B-scan and a total lateral scan length of 10 mm. The axial resolution of the system, defined as the full-width half-maximum of the measured axial point-spread function was 12 μm in air (corresponding to 8 μm in tissue). The lateral resolution, defined as the calculated 1/e

^{2}beam diameter in the lens plane, was 60 μm. The lens shape and lens power recorded at each step were used for the present study.

^{19,21}(Fig. 1). The contour provides the position of the anterior and posterior lens boundaries measured along each A-line, in optical path length units. The contour is scaled in the axial direction to convert optical distances to geometrical distances using the measured group refractive index of DMEM (

*n*= 1.345 at 825 nm

^{24}and an estimate of the average group refractive index of nonhuman primate lenses (

*n*= 1.414 at 825 nm

^{21}).

**Figure 1**

**Figure 1**

^{25}Lens tilt was corrected using the value of the angular tilt obtained from the fit and the curve fit was repeated for the corrected lens contour (see details in Urs et al.

^{25}). The axis of symmetry of this second fit was taken as the position of the axis of symmetry of the crystalline lens. The

*z*-position of the equatorial axis was taken as the average of the

*z*-coordinates of the two points of the curve fit with the most positive and most negative

*y*-coordinates. The center of the coordinate system was placed at the intersection of the lens equatorial axis and the axis of symmetry (Fig. 1).

^{19,21,24,26}Refractive distortions were corrected using a computational ray-trace that calculates the correct position of the posterior lens surface along each A-line. The lens is assumed to be a homogeneous medium (no gradient index), with a refractive index equal to the average group refractive index.

^{24}Potential sources of error resulting from this assumption are discussed below, in the Discussion section.

^{25}with a total of 21 Fourier terms (Fig. 2): where

*b*is the Fourier series coefficient of order

_{k}*k*and

*θ*is the angle with respect to the

*y*-axis. The Fourier model closely fit the lens shape (Fig. 2) with a root mean square (RMS) fit error that ranged from 10 to 48 μm (mean = 18 ± 6 μm).

**Figure 2**

**Figure 2**

*y*,

*z*) using the following discrete integration formula (rectangle method, see Fig. 3): where

*z*is the axial position along the axis of symmetry of the

_{k}*k*sample,

_{th}*y*is the radial distance from the axis of symmetry to the lens contour, and

_{k}*N*is the number of contour points. For this calculation, the contour was sampled with a period of approximately 5 μm in the

*y*-direction (i.e.,

*y*

_{k+1}−

*y*

*= 5 μm) starting with the point closest to the axis of symmetry (i.e.,*

_{k}*y*

_{1}= 0). Comparison of lens volume calculated using the rectangle method of Equation 2 and the trapezoidal rule shows that the difference between the two methods is less than 0.2 mm

^{3}for the lens volume and less than 0.01 mm

^{3}for the change in lens volume.

**Figure 3**

**Figure 3**

^{3}(±1.1% of the lens volume). The worst-case expected uncertainty in the difference between stretched and unstretched lens volume is therefore ±2.2%.

*t*-test was used to determine if the difference between unstretched and stretched lens volume is statistically significant at the 0.05 level. One-sample

*t*-tests were performed to determine if the volume-power and volume-load slopes were significantly different from zero. Data acquired during the first 0.75 mm of radial displacement of the translation stages were excluded from these analyses because these initial stretching steps compensate for changes in geometry due to dissection and for postmortem tissue slackness. These steps place the tissue under tension without producing significant changes in lens shape or power. In all results shown below, the unstretched state of the lens is the state of the lens when the radial displacement of the EVAS II shoes is 1 mm.

**Figure 4**

**Figure 4**

^{27,28}The diameter-load and thickness-load graphs were found to be nonlinear (Fig. 4B).

**Table 1**

**Table 2**

^{3}) increased with age, with values ranging from 77 mm

^{3}at 1.4 years to an average of 109 mm

^{3}for the three lenses from 13- to 14-year-old monkeys. To determine if lens volume is affected by stretching, volume-power (mm

^{3}/D), and volume-load (mm

^{3}/g), slopes were obtained from linear regressions for each lens. Both positive and negative slopes are observed (Fig. 5). The mean value is −0.018 ± 0.058 mm

^{3}/D for the volume-power slope and 0.16 ± 0.40 mm

^{3}/g for the volume-load slope. On average, these values correspond to a small increase in lens volume with stretching (volume-power slope:

*P*= 0.09; volume-load slope:

*P*= 0.03).

**Figure 5**

**Figure 5**

^{3}/D to 0.002 mm

^{3}/D for the volume-power slopes and from 0.02 mm

^{3}/g to 0.31 mm

^{3}/g for the volume-load slope. An estimate of the total volume change was obtained by multiplying the slopes by the mean change in power (−22 D) or stretching force (3.3 g). Based on this approach, we found that the 95% confidence interval for the change in volume with stretching ranges from −0.04 mm

^{3}to +0.8 mm

^{3}when calculated using the volume-power slope and from +0.07 mm

^{3}to +1.0 mm

^{3}when calculated using the volume-load slope.

^{13,14}the effect of stretching on lens volume was evaluated by comparing the volume measured in the unstretched and stretched states. In our study, the mean difference between stretched and unstretched lens volumes is 0.8 ± 1.3 mm

^{3}, corresponding to a slight increase in volume with stretching that is statistically significant (two-sample paired

*t*-test, 0.05 level,

*P*= 0.002). The 95% confidence interval for the mean difference between stretched and unstretched lens volume is 0.3 to 1.2 mm

^{3}. These values obtained from the endpoints are consistent with the estimate obtained from the slopes.

^{3}, with an average of 0.15 ± 0.78 mm

^{3}. This range is comparable with the estimated measurement variability (±2.2 mm

^{3}). Regression analysis indicates that there is no relationship to the power change over a large range of powers (

*R*= −0.025,

*P*= 0.73). This analysis suggests that the measured volume change reflects the experimental variability rather than a true change in lens volume.

**Figure 6**

**Figure 6**

^{3}(0.8%). Overall, our results provide support for the assumption that the lens is nearly incompressible. They are in agreement with observations that the lens volume is approximately constant with accommodation,

^{10,11}or that the changes are within the uncertainty of the measurement techniques.

^{17}Given the small magnitude of its effect, it is probable that a change in lens volume is not a biologically relevant component of the physiology of accommodation.

^{13}estimated that the human lens volume increases with accommodation by 2.6% for a 20-year-old lens and 1.7% for a 40-year-old lens. There are several sources of error that limit the accuracy of this estimate. In particular, the lens has an aspheric shape with an asphericity that changes with accommodation. A spherical model cannot produce reliable estimates of the volume or its changes. In the same study, measurements on 13 bovine lenses produced an average decrease in lens volume of 5.8% with stretching, with values ranging from 1.7% to 12.5%. The changes in thickness and diameter with stretching were minimal, on average −2.8% and +2.2%, respectively, consistent with the expectation that bovine lenses do not undergo significant accommodation. These small changes in lens shape measured by Gerometta et al.

^{13}are inconsistent with the large (6%) decrease in lens volume that they measured on the same lenses, as discussed below.

*V*will be of the general form

*V = A × d*

^{2}

*× t*, where

*d*is the lens diameter,

*t*is the lens thickness, and

*A*is a parameter that depends on the shape of the lens. For instance

*A*= π/6 = 0.524 for a sphere or ellipsoid and

*A*= π/4 = 0.785 for a cylinder. For the monkey lenses in our study, the coefficient

*A*increased from an average of 0.443 ± 0.010 in the unstretched state to an average of 0.478 ± 0.012 in the stretched state, corresponding to a 7.3% increase with stretching. This change is consistent with the pronounced change in shape of the monkey lens with stretching, as can be seen in Figure 1. Because there were no significant changes in the shape of the bovine lenses with stretching in the study of Gerometta et al.,

^{13}the coefficient

*A*of these lenses should remain approximately constant with stretching. With a constant coefficient

*A*, the −2.8% thickness change and +2.2% diameter change of the bovine lenses with stretching corresponds to a 1.5% increase in volume, as opposed to the 5.8% decrease measured by Gerometta et al.

^{13}Alternatively, the coefficient

*A*would have to decrease by 7.3% with stretching to reconcile the volume change of the bovine lenses with their thickness and diameter change. In other words, the bovine lens would have to undergo pronounced changes in lens shape, similar to those observed in our study. This finding is inconsistent with the observation that there were no significant changes in the shape of the bovine lenses.

^{15}used a 3 Tesla three-dimensional MRI to measure lens volume in 19 subjects at three different accommodative states. They found a non–statistically significant decrease of lens volume in response to a 4D stimulus, but a statistically significant increase in response to an 8D stimulus. The results were highly variable, with a mean volume increase of 2.4% ± 5.9% between relaxed accommodation and the 8D stimulus. If the lens is compressible, one would expect an increase in lens volume at all accommodative levels, not a decrease (or no change) at 4 D and an increase at 8 D. It is therefore not possible to conclude with confidence from these data that the lens volume changes with accommodation.

^{12,15}and that there is fluid exchange through the lens capsule.

^{13,14,16}In either case, the change in lens volume is expected to be directly correlated with the force of accommodation. In our study, contrary to these hypotheses, the volume did not decrease on stretching.

^{15}shadow-photogrammetry

^{25,29}or photography

^{13,14}to quantify lens volume. Optical coherence tomography provides measurements with much higher resolution (typically <10 μm) than MRI (>100 μm), but unlike MRI, OCT images suffer from distortions that must be corrected to produce accurate lens biometry. Optical coherence tomography images must be scaled to convert optical path length into physical distance, and they must be corrected for distortions due to refraction of light rays. In our study, refractive distortions had a minimal effect on the calculated change in lens volume. We find that the change in volume is slightly underestimated if the refractive distortions are not corrected. Without distortion correction, the average change in lens volume is 0.2 ± 1.3 mm

^{3}for the 36 monkey lenses, instead of 0.8 ± 1.2 mm

^{3}obtained from the distortion-corrected images.

^{3}less than the value obtained with the uncorrected Fourier fit. This analysis suggests that using the Fourier fit produces a slight overestimation of the change in lens volume.

*n*= 1.414) based on published data acquired on human and monkey lenses.

^{21,23,30}To quantify the effect of uncertainties in the refractive index on the estimation of lens volume change, we processed one lens with different values of the refractive index, ranging from 1.400 to 1.420, in 0.05 steps. This analysis shows that an uncertainty of ±0.01 in the refractive index produces an uncertainty on the order of ±1% in the lens volume. An increase in the refractive index produces a comparable decrease in both the stretched and unstretched lens volumes, and therefore the uncertainty in the refractive index has a negligible effect on the estimated change in lens volume.

*IOVS*2011;52:ARVO E-Abstract 816). These sources of error can be eliminated only by using three-dimensional imaging.

^{31,32}To increase the sensitivity of our analysis to detect changes in lens volume, we considered the volume-power and volume-load slopes. The slope analysis produces conclusions that are in good agreement with the analysis of the volumes at the two endpoints of stretching. However, the slope metrics are more robust because they use data from all stretching steps, as opposed to the alternative comparison that considers only the beginning and ending volume.

^{33}using a fluid displacement method. The mean volumes obtained with the OCT method and those reported by Priestley Smith

^{33}were, respectively (in mm

^{3}): 184 (

*n*= 4) and 177 (

*n*= 22) for ages 30 to 39; 187 (

*n*= 5) and 188 (

*n*= 23) for ages 40 to 49, 202 (

*n*= 18) and 203 (

*n*= 21) for ages 50 to 59, and 220 (

*n*= 23) and 223 (

*n*= 23) for ages 60 to 69. This comparison demonstrates that the OCT method produces reliable measurements of lens volume.

**L. Marussich**, None;

**F. Manns**, None;

**D. Nankivil**, None;

**B. Maceo Heilman**, None;

**Y. Yao**, None;

**E. Arrieta-Quintero**, None;

**A. Ho**, None;

**R. Augusteyn**, None;

**J.-M. Parel**, None

*Archiv fuer Ophthalmologie*. 1855; 2: 1–74.

*Adler's Physiology of the Eye*. 10th ed. St. Louis, MO: Mosby; 2002: 197–233.

*Prog Retin Eye Res*. 2005; 24: 379–393.

*Clin Exp Optom*. 2008; 91: 207–225.

*J Physiol*. 1969; 201: 21–47.

*Vision Res*. 1982; 22: 917–927.

*Vision Res*. 1983; 23: 1679–1686.

*Vision Res*. 2002; 42: 2235–2251.

*Exp Eye Res*. 2007; 85: 602–607.

*J Vis*. 2007; 7 (16): 1–10.

*Invest Ophthalmol Vis Sci*. 2009; 50: 281–289.

*Invest Ophthalmol Vis Sci*. 2004; 45: 539–545.

*Am J Physiol Cell Physiol*. 2007; 293: 797–804.

*Am J Physiol Cell Physiol*. 2007; 294: 1430–1435.

*Invest Ophthalmol Vis Sci*. 2011; 52: 3689–3697.

*Prog Retin Eye Res*. 2008; 27: 197–212.

*Exp Eye Res*. 2011; 93: 741–752.

*Clin Exp Optom*. 2008; 91: 302–312.

*Invest Ophthalmol Vis Sci*. 2015; 56: 1751–1760.

*Invest Ophthalmol Vis Sci*. 2009; 50: 4017–4021.

*J Vis*. 2011; 11 (23): 1–13.

*Invest Ophthalmol Vis Sci*. 2007; 48: 3260–3268.

*Vision Res*. 2008; 48: 2732–2738.

*Biomed Opt Express*. 2010; 1: 1331–1340.

*Vision Res*. 2010; 50: 1041–1047.

*Optom Vis Sci*. 2012; 89: E709–E718.

*Exp Eye Res*. 2005; 80: 349–360.

*Invest Ophthalmol Vis Sci*. 2006; 47: 278–286.

*Vision Res*. 2006; 46: 1002–1009.

*Invest Ophthalmol Vis Sci*. 2013; 54: 6197–6207.

*Opt Express*. 2010; 18: 21905–21917.

*Biomed Opt Express*. 2014; 5: 3547–3561.

*Trans Ophthalmol Soc U K*. 1883; 3: 79–99.