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Article

Simultaneous Myopic Defocus for Myopia Control: Effect on Accommodation, Peripheral Refraction and Retinal Image Quality in Non-Presbyopic Patients

by
Alina Fritschi
1,
Chloe Gerber
2,
Damian Eggler
3 and
Martin Loertscher
4,5,*
1
Falco-Linsen AG, Talackerstrasse 14, 8274 Tägerwilen, Switzerland
2
Spörri Optik, Nidaugasse 70, 2502 Biel, Switzerland
3
Art of Optic, Stickereistrasse 4, 9320 Arbon, Switzerland
4
Fachhochschule Nordwestschweiz, Institut für Optometrie Riggenbachstrasse 16, 4600 Olten, Switzerland
5
Pallas Kliniken, Bahnhofplatz 4, 5001 Aarau, Switzerland
*
Author to whom correspondence should be addressed.
Optics 2021, 2(4), 200-215; https://doi.org/10.3390/opt2040019
Submission received: 31 August 2021 / Revised: 26 September 2021 / Accepted: 27 September 2021 / Published: 30 September 2021
(This article belongs to the Special Issue Novel Research on Optometry and Vision Sciences)
Browse Figures
Versions Notes

Abstract

:
Exposing the retina to a simultaneous myopic defocus is an optical method that has shown a promising effect in slowing the progression of myopia. Optical treatments applying a simultaneous defocus are available in the form of soft contact lenses or multifocal lenses originally designed to correct presbyopia. Orthokeratology is another optical method that slows down the progression of myopia. With orthokeratology, it is hypothesized that a change in peripheral refraction could slow the progression of myopia. We aimed to measure the accommodation response between monofocal and multifocal contact lenses in young subjects. Additionally, we performed a ray-tracing simulation to visualize the quality of the retinal image and the refractive status in the retinal periphery. The accommodation and pupil size measurements were performed on 29 participants aged 24.03 ± 2.73 years with a refractive error (spherical equivalent) of −1.78 ± 1.06 D. With the multifocal lens in situ, our participants showed less accommodation in comparison to the monofocal contact lens (mean difference, 0.576 ± 0.36 D, p > 0.001) when focusing on a near target at 40 cm. Pupil size became smaller in both contact lens groups during an accommodation of 0.29 ± 0.69 mm, p ≤ 0.001 and 0.39 ± 0.46 mm, p ≤ 0.001 for monofocal and multifocal contact lenses, respectively. The ray-tracing model showed a degradation for central and peripheral vision with the multifocal contact lens. The peripheral refraction was relatively myopic in both contact lens conditions up to 30°. Even if the accommodation ability is without fault, parts of simultaneous myopic defocus are used for the near task. The peripheral refraction in the ray-tracing model was not different between the two contact lenses. This is contrary to the proposed hypothesis that myopic peripheral refraction slows down the progression of myopia in current optical methods.

1. Introduction

The rising prevalence of myopia in children [1,2,3] is of great concern. Therefore, methods to control and slow the progression of myopia have been developed or are presently under development. Currently, atropine eyedrops are a pharmaceutical therapy that shows promising effects depending on the concentration [4,5,6,7]. The effects of atropine are dose-dependent, and low-dose atropine is not efficient in slowing the elongation of the eyes’ axial length [8]. With a higher concentration of atropine, the slowing effect increases, but so does the effect of atropine on the ciliary muscle and the sphincter muscle, which causes blurred near vision and photophobia [9]. One way to reduce the progression of myopia seems to be through natural means, such as via frequent exposure to bright natural sunlight while playing outdoors, for example [10]. The effect of being outdoors seems to be a stronger factor in slowing myopia progression but with a difference in efficacy between the ethnicities [11]. Based on the optical properties of light, blue light may play a role in slowing myopia progression compared to red light [12]. Optical treatment is based on the assumption of changes in the peripheral retina refraction [13]; such changes are obvious when orthokeratology is used as a method of vision correction [14]. However, the hypothesis that peripheral refraction plays a role in emmetropization is under debate [15]. Another hypothesis regarding optical treatment methods is that exposing the retina to an on-axis simultaneous myopic defocus slows the progression of myopia. This optical method shows good results in slowing the progression of myopia in children [16,17,18,19,20]. On-axis simultaneous myopic defocus is also applied in multifocal contact lenses for the correction of presbyopia [21,22]. In presbyopia, the aim of the defocus is as a substitute for the insufficient accommodation. However, myopia control is mainly applied to children who have sufficient accommodation abilities. A study using monovision in children showed that the far-correction eye accommodates normally [22]. Additionally, with soft contact lenses [18] and multifocal orthokeratology [20], accommodation is not highly affected in children when a simultaneous defocus is applied. Apart from a slight image degradation that comes with the use of multifocal optics [23], such optical correction methods are well tolerated. Thus, the question remains of how accommodation is influenced by an on-axis myopic defocus during near tasks. Our aim was to measure the accommodation response in non-presbyopic participants when using a contact lens with a simultaneous myopic defocus of 2.00 dpt. Additionally, we performed a ray-tracing simulation with both contact lens types, generating images that showed the image quality for the central vision and peripheral vision up to an angle of 30°.

2. Materials and Methods

The study adhered to the tenets of the Declaration of Helsinki, received approval from the Northwestern Switzerland Health Ethics Committee (Approval No. 2019-00329), and was prospectively registered with the National Clinical Trial Registry (BASEC). Participants gave written consent to participate.
To introduce a simultaneous myopic defocus to the retina, we used the contact lens Proclear Multifocal Type “D” with the distance correction in the center. The same lens was previously used for myopia control [22], and the power profile of the lens was also familiar [24]. The monofocal control lens was Proclear Monofocal. Both contact lenses were made of the same hydrogel material: “omafilcon A”.
To test the accommodation response, we compared the objective refraction between a measurement at 40 cm and a measurement at 1 m. The difference was taken as the amount of accommodation. The measurement was taken using binocular infrared photo retinoscopy (Plusoptix A16, Plusoptix, Nürnberg, Germany) [25,26]. The Plusoptix A16 used an infrared measurement beam with a wavelength of 870 nm and a maximum intensity of 135 mW/sr. Furthermore, we simulated the optical concept with ray-tracing software to demonstrate the optical results on the retina.

2.1. Experimental Setup

The measurement setup was fixed, and was composed of a near target at 40 cm and a distant target at 6 m distance from the participant’s eye (Figure 1A,B). The binocular retinoscope was placed at a 1 m distance from the participant. The luminance in the room was kept constant at 140 lux. The measurements were taken in the afternoon between 2:00 and 5:00 pm.
The accommodation target was a printed text at 40 cm (VA size 0.2 LogMAR) positioned on the subject’s midline in all cases. A similar setup was previously used for another type of open-filed autorefractor [27]. The experimental setup was used as described in Figure 1. The participant wore binoculars, either the Proclear multifocal lens or the Proclear monofocal lens. We took autorefractor measurements when viewing at a distance and at 40 cm. The autorefractor value was transformed to the spherical equivalent. The difference of near value minus distance value was taken as the accommodation. We used a binocular setup; therefore, we took the mean value of both eyes to analyze the accommodation response. In previous validation measures, we did not find a difference between the right and left eyes. The order in which each lens type was worn was randomly generated. The experiment was double-masked, and neither the participant nor the operator at the autorefractor knew which lens was being used at each given time. Additional data measured included pupil size when viewing near and distant targets and changes in interpupillary distance between near and distant targets.

2.2. Participants

We included 29 participants in the study.
The inclusion criteria were as follows:
  • Aged between 20 and 30 years;
  • Refraction error between −0.50 and −4.00 D;
  • Maximum astigmatism of −1.00 D;
  • Corrected visual acuity of at least LogMAR 0.0 (20/20) or better.
Exclusion criteria were as follows:
  • Amblyopia;
  • Strabismus;
  • Active eye disease that does not allow for wearing contact lenses;
  • Pseudophakia.
There were no restrictions regarding gender.

2.3. Optical Simulation

To simulate the retinal image through the contact lenses, we used the ray-tracing software OpTaliX OpTaliX-Pro 64-bit V 9.25 (Optenso, Igling, Germany). As a basis eye, we used a modified Gullstrand eye. We fitted the monofocal and multifocal contact lens to the modified Gullstrand eye and generated the point spread function on the retina for distance and near vision. Pupil size and lag of accommodation were incorporated into the model based on the values of our participants.

2.4. Statistical Analysis

Data analysis was carried out with IBM SPSS software, version 25. First, we prepared a descriptive summary of the data. Then, the normality was tested with the Shapiro–Wilk test. When the data followed a normal distribution, a t-test was applied to compare the accommodation data between multifocal contact lenses and monofocal contact lenses. Power calculation showed that 29 participants were required in the accommodation experiment in order to achieve an alpha level of 5% and a power of 95%; therefore, a significant result was reported when p ≤ 0.05.
Ray-tracing simulation and image generation were carried out with OpTaliX-Pro 64-bit V 9.25 (Optenso, Igling, Germany).

3. Results

3.1. Accommodation

In the accommodation experiment, the participants were 24.03 ± 2.73 years old with a refractive error of −1.78 ± 1.06 D. In this experiment, the contact lenses (one-time multifocal and one-time monofocal) were worn binocularly. The data followed a normal distribution. With the multifocal lens in place, the participants used less accommodation. The results (Figure 2) showed a mean difference of 0.576 ± 0.36 D, 95%CI (0.43/0.71), t 8.549, df 28, p > 0.001. In Figure 3, the scatter plot showed that less accommodation was needed for a viewing at 40 cm with the multifocal lens in place.

3.2. Pupil Size

The change in pupil size when changing the focus from the distant to the near target was significant with both types of contact lenses. When wearing monofocal lenses, the pupil diameter became smaller when viewing at 40 cm with a mean difference of 0.29 ± 0.69 mm, 95%CI (0.03/0.55), t 2.303, df 28, p = 0.029. Additionally, with multifocal lenses, pupil size was smaller during the near task, with a mean difference of 0.39 ± 0.46 mm, 95%CI (0.22/0.57), t 4.641, df 28, p < 0.001. Figure 4 shows that the diameter of the pupil decreased with the increasing accommodation.

3.3. Interpupillary Distance

When changing the gaze from a target at a distance to a nearer target, the eye has to converge. This yoked effect of convergence is visible in a smaller interpupillary distance. This was found in both wearing conditions. Monofocal lenses showed a mean difference of 0.94 ± 0.25 mm, 95%CI (0.84/1.04), t 19.74, df 28, p < 0.001, while multifocal lenses showed a mean difference of 0.92 ± 0.20 mm, 95%CI (0.83/0.99), t 23.79, df 28, p < 0.001.

3.4. Optical Visualization

To visualize the optical content of our experiment, we carried out optical modeling with our data. We used a ray-tracing model based on the values in Table 1. The reference wavelength was 546 nm.
First, we generated a ray-tracing model of the central and peripheral refraction. We simulated the tangential and sagittal lines of focus (Figure 5 and Figure 6). We used the refraction data and the accommodation data. Therefore, a lag of accommodation was visible in all the pictures with the model focusing on the near target (Figure 7 and Figure 8). The rays entering the eye from the periphery were simulated from 30° temporal to 30° nasal. In both focusing distances (infinity and 40 cm), as well as with both contact lenses, a relative myopic defocus compared to the fovea was present.
The quality of the retinal image is represented by the computer-generated image of the point spread function. We generated the image for the central foveal image and then in 5° increments up to 30° nasal and temporal. We completed this for the Proclear monofocal and multifocal lenses with light rays entering the eye from infinity (Figure 9 and Figure 10) and when focusing on a target at 40 cm. The corresponding Strehl ratio for each eccentricity is in Table 2.

4. Discussion

Studies show an effect of retarding myopia progression in children using optical therapies, such as simultaneous myopic defocus [16,18,28] or introducing relative peripheral myopia to the retina [29]. However, through both correction methods, it is not clear how the eye detects a myopic defocus, central or peripheral, and how strong in diopters such a defocus should be. In this work, we address two research questions. First, how does accommodation change in young non-presbyopic participants; and second, what does the optical ray-tracing simulation look like on the retina through an eye wearing a multifocal contact lens?

4.1. Accommodation

Accommodation response is related with age. Young children can change the refractive power of the crystalline lens much more than older people [30]. However, studies for myopia control in children show that accommodation response does not change when children wear multifocal contact lenses [18] or use monovision [22] (one eye wearing distance correction and the contralateral eye wearing near correction). In our study we used participants aged 24.03 ± 2.73. At this age accommodation ability is still sufficient to perform near tasks without any help from an optical near addition such as a multifocal contact lens. With the retina exposed to a simultaneous myopic defocus in the form of the Proclear multifocal contact lens, our subject accommodated +1.40 D (95%CI 1.22/1.57 D), while the accommodation with the monofocal distance correction lens was +1.97 D (95%CI 1.78/2.16 D). The accommodation demand for a target placed at a 40 cm distance equated to +2.50 D; therefore, in both cases, a lag of accommodation was present. With the monofocal contact lens, our measured accommodation lag was in agreement with a recent study that measured the lag of accommodation in real time in young adults [31]. A lag of accommodation is often present in myopic subjects [32], and is measured by others in subjects wearing multifocal contact lenses [33]. A lag of accommodation is suggested as a potential risk factor for myopia [34] and may stimulate the progression of myopia, although a relationship between the lag of accommodation and myopia progression over time could not be established in [35]. With the hypothesis that hyperopic defocus is a myopia promoter and a myopic defocus is an inhibitor of myopia progression [36], the effect of a reduced accommodation with multifocal contact lenses could mean that it lowers the potential therapeutic effect of slowing myopia progression with multifocal contact lenses. Thus, if the subjects reduced their accommodation accuracy with multifocal contact lenses [37,38], this would result in central/foveal hyperopic defocus. This kind of optical treatment could be more successful if no lag of accommodation was present. We found a difference in accommodation of 0.576 ± 0.36 D between monofocal and multifocal lenses. This could have been influenced by the measurement protocol. As shown by others [39], it is complex to achieve an objective measure of the accommodation with a multifocal contact lens in place. The variability of the optical power over the participant pupil area can lead to an over- or underestimation of the measurement.
However, short-term [33] and long-term [40] results in patients using a simultaneous myopic defocus contact lens for the purpose of controlling the progression of myopia indicated no negative side effects in terms of the accommodation performance, compared to single-vision contact lenses.
The size of the pupil diameter is linked to the accommodation status and age [41]. The size of the pupil is also influenced by mental and cognitive work [42]. With accommodation, it is known that the pupil becomes smaller. Therefore, the change in pupil size can be used as an indirect control of accommodation during visual tasks. In our population we measured a reduction in pupil diameter during near tasks, as expected. We did not find a difference between male and female pupil size, although our sample size was too small to make a general comment on this aspect.

4.2. Peripheral Refraction and Image Quality

Our ray-tracing-generated result of peripheral refraction showed a relative myopic peripheral refraction in both distance and near vision for both monofocal and multifocal contact lenses. Peripheral refraction is hypothesized to play an important role in the process of emmetropization, and animal models of myopia [43,44] deliver evidence for this hypothesis. However, this effect is not always found in chicken models of myopia [45]. It appears that the effect of the peripheral refraction on myopia inhibition depends on the retinal location, which should be relatively central [46]. A recent publication showed the highest effect in monkeys when the central unrestricted vision was small (1.5°, 5.8°, or 9.8°, respectively) and the periphery was exposed to a simultaneous defocus (+3.00 D) [42,47]. The strength of the effect increased when the central unrestricted part of vision decreased in size. The lens with 9.8° of unrestricted vision still showed a statistically significant shortening of the vitreous body, but the data showed a large variation, with approximately half of the monkeys showing the opposite effect. In humans, a longitudinal study [48] investigated the change in the peripheral refraction and the risk of developing myopia as very little (−0.024 D per year more myopia per 1 D peripheral hyperopia), but a significant risk of myopia for certain ethnicities, with Asian people exposed to the highest risk. With the Proclear multifocal contact lens, which was used for myopia control [24], we found a simulated myopic peripheral refraction outside the central 12° for distance and 24° for near vision (Figure 6 and Figure 8). Our simulation in the periphery opposed an in situ measurement of peripheral refraction [13]; this study found a relative hyperopic peripheral refraction with the same multifocal contact lens. However, Lopes-Fereira et al. [29] used the same autorefractor and the same contact lens as Ticak and Walline (2013) but found a relative myopic peripheral refraction in their participant. This may indicate the variation and precision of peripheral refraction measures in practice. Our simulated peripheral refraction data show even more peripheral myopia. Surprisingly, for the monofocal Proclear contact lens, our simulation also showed a myopic peripheral refraction outside the central 12° (distance) and 24°(near). This counter-intuitive effect of a myopic peripheral refraction with a monofocal contact lens was also found by Bachhouse et al (2012). who measured the peripheral refraction in practice with an open-field autorefractor in university students [49,50]. With monofocal contact lenses, there was no report of influencing the progression of myopia; therefore, such a finding was in conflict with the hypothesis that a relative myopic defocus has an inhibitory effect on myopia progression. The obvious change in peripheral refraction with orthokeratology [14,51], from relatively hyperopic to relatively myopic, is generally thought to be responsible for the effect of slowing down the progression of myopia in children when they are treated with orthokeratology contact lenses [52,53,54,55,56,57]. On the basis of the peripheral refraction hypothesis, which extends back many years [58], and the promising results with orthokeratology and the evidence from animal models, new optical treatment options based on changing the peripheral refraction were developed, especially spectacle lenses [59,60]. These optical treatments had a slowing effect on the progression of myopia, but the change in peripheral refraction responsible for this effect is not fully understood. The axial length measured prospectively in a paired-eye study using standard orthokeratology in one eye and multifocal orthokeratology, showed significantly less axial length elongation in the eye fitted with multifocal orthokeratology, but with no significant difference in the peripheral refraction change between the two lenses in children [20]. Additional longitudinal studies have so far not been able to correlate the progression of myopia in humans with a change in the peripheral refraction in children [61,62].
Based on our generated point-spread function, blur could also be a factor that prompts the eye to change its growth response. The used and modified Gullstrand eye showed a high Strehl ratio of 0.701 with the monofocal lens, for viewing at infinity and a reduced Strehl ratio with the multifocal lens of 0.027. A Gullstrand eye model depends on the pupil size, with a Strehl ratio of 0.938 to 0.017 [63]. The receptors in the retina which detect blur and decode the blur sign (myopic or hyperopic) have yet to be discovered, but we know that there is such a mechanism because the eye reacts quickly, defocusing with a swelling or deswelling of the choroid in animals [64] and humans [65,66]. It appears that the mechanism that prompts the eye to respond to a defocus (central or peripheral) is more complex than it appears when reporting peripheral refraction results based on the power vectors [67]. We did not measure the peripheral refraction in our participants. We reported ray-tracing-generated figures in the peripheral refraction. In our study, this was intended to visualize the effect of monofocal and multifocal contact lenses. We used a modified Gullstand eye which was symmetrical, and thus did not represent real data of the eyes of our participants. Therefore, those data should be interpreted more as a description of what the peripheral optics could look like based on Snell’s law.

5. Conclusions

We showed that non-presbyopic participants accommodated approximately 0.50 less D when using a multifocal contact lens. Therefore, it can be hypothesized that the positive effect of the use of multifocal contacts on the slowing of myopia progression was not initiated by gross changes to accommodation. Optical ray-tracing simulation showed no change in the peripheral refraction between multifocal and monofocal contact lenses, but showed a clear retinal image degradation with multifocal contact lenses.

Supplementary Materials

The following are available online at https://www.mdpi.com/article/10.3390/opt2040019/s1.

Author Contributions

Conceptualization, M.L.; methodology, A.F., C.G. and M.L.; formal analysis, M.L. and D.E.; investigation, A.F. and C.G.; resources, M.L.; data, M.L., A.F. and C.G.; writing—original draft preparation, M.L.; writing—review and editing, M.L.; visualization. D.E.; supervision, M.L.; project administration, A.F. and C.G.; funding acquisition, M.L. All authors have read and agreed to the published version of the manuscript.

Funding

This research received no external funding.

Institutional Review Board Statement

The study adhered to the tenets of the Declaration of Helsinki, received approval from the Northwestern Switzerland Health Ethics Committee (Approval No. 2019-00329), and was prospectively registered with National Clinical Trial Registry (BASEC).

Informed Consent Statement

Participants gave written consent to participate.

Data Availability Statement

Data are available by reasonable request through the corresponding author.

Conflicts of Interest

The authors declare no conflict of interest.

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Figure 1. Setup to acquire accommodation data. Both eyes looked through binoculars either into the distance or at the movable near chart. The acquisition of the data with the autorefractor was simultaneous in both eyes under the binocular condition. (A) Setup overview. (B) Movable near target at 40 cm as seen by the participant.
Figure 1. Setup to acquire accommodation data. Both eyes looked through binoculars either into the distance or at the movable near chart. The acquisition of the data with the autorefractor was simultaneous in both eyes under the binocular condition. (A) Setup overview. (B) Movable near target at 40 cm as seen by the participant.
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Figure 2. Boxplot of binocular accommodation at 40 cm.
Figure 2. Boxplot of binocular accommodation at 40 cm.
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Figure 3. The scatterplot shows that less accommodation was used to focus on a near target at 40 cm with multifocal contact lenses in place.
Figure 3. The scatterplot shows that less accommodation was used to focus on a near target at 40 cm with multifocal contact lenses in place.
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Figure 4. Change of pupil size with accommodation.
Figure 4. Change of pupil size with accommodation.
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Figure 5. Peripheral refraction with Proclear monofocal correction −2.00 D of myopia, viewing distance at infinity: sagittal and tangential focal lines. Within the central 12° is a plano-refraction; after the central 12° both focal lines become myopic relative to the center (Fovea).
Figure 5. Peripheral refraction with Proclear monofocal correction −2.00 D of myopia, viewing distance at infinity: sagittal and tangential focal lines. Within the central 12° is a plano-refraction; after the central 12° both focal lines become myopic relative to the center (Fovea).
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Figure 6. Peripheral refraction with Proclear multifocal correction −2.00 D of myopia, viewing distance at infinity: sagittal and tangential focal lines. Within the central 12° is a plano-refraction; after the central 12° both focal lines become myopic relative to the center (Fovea).
Figure 6. Peripheral refraction with Proclear multifocal correction −2.00 D of myopia, viewing distance at infinity: sagittal and tangential focal lines. Within the central 12° is a plano-refraction; after the central 12° both focal lines become myopic relative to the center (Fovea).
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Figure 7. Peripheral refraction with Proclear monofocal correction −2.00 D of myopia, viewing distance at 40 cm: sagittal and tangential focal lines. Within the central 18° a lag of accommodation is visible that refers to a hyperopic defocus. Outside the central 18° both focal lines become myopic relative to the center (Fovea).
Figure 7. Peripheral refraction with Proclear monofocal correction −2.00 D of myopia, viewing distance at 40 cm: sagittal and tangential focal lines. Within the central 18° a lag of accommodation is visible that refers to a hyperopic defocus. Outside the central 18° both focal lines become myopic relative to the center (Fovea).
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Figure 8. Peripheral refraction with Proclear multifocal correction −2.00 D of myopia, viewing distance at 40 cm: sagittal and tangential focal lines. Within the central 18° a lag of accommodation is visible that refers to a hyperopic defocus. Outside the central 18° both focal lines become myopic relative to the center (Fovea).
Figure 8. Peripheral refraction with Proclear multifocal correction −2.00 D of myopia, viewing distance at 40 cm: sagittal and tangential focal lines. Within the central 18° a lag of accommodation is visible that refers to a hyperopic defocus. Outside the central 18° both focal lines become myopic relative to the center (Fovea).
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Figure 9. Simulated retinal image quality from the central up to 30° nasal and temporal. (Top row): Proclear monofocal. (Bottom row): Proclear multifocal. Viewing distance at infinity.
Figure 9. Simulated retinal image quality from the central up to 30° nasal and temporal. (Top row): Proclear monofocal. (Bottom row): Proclear multifocal. Viewing distance at infinity.
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Figure 10. Simulated retinal image quality from central up to 30° nasal and temporal. (Top row): Proclear monofocal. (Bottom row): Proclear multifocal. Viewing distance at 40 cm.
Figure 10. Simulated retinal image quality from central up to 30° nasal and temporal. (Top row): Proclear monofocal. (Bottom row): Proclear multifocal. Viewing distance at 40 cm.
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Table
Table 1. Dimension of the data used for the ray-tracing model with the software OpTaliX. The complete description of the model is in the supplemental materials.
Table 1. Dimension of the data used for the ray-tracing model with the software OpTaliX. The complete description of the model is in the supplemental materials.
ObjectRadius (mm)
Anterior radius Proclear MF9.12
Anterior peripheral radius MF8.52
Anterior radius Proclear monofocal9.12
Posterior radius MF and monofocal8.7
Contact lens central thickness0.01
Anterior cornea radius8.1
Posterior corneal radius6.8
Central corneal thickness0.5
Anterior chamber depth3.6
Pupil diameter without accommodation2.4
Pupil diameter with accommodation2.2
Anterior lens radius without accommodation10
Posterior lens radius without accommodation−6.0
Anterior lens radius with accommodation9
Posterior lens radius with accommodation−5.4
Retina radius−11
Axial length27.367
Table
Table 2. Strehl ratio for each eccentricity. Row one and two are for a viewing distance at infinity and row three and four for a viewing distance at 40 cm. Because we used a rotationally symmetric eye model, the Strehl ratio for nasal and temporal eccentricity are equal.
Table 2. Strehl ratio for each eccentricity. Row one and two are for a viewing distance at infinity and row three and four for a viewing distance at 40 cm. Because we used a rotationally symmetric eye model, the Strehl ratio for nasal and temporal eccentricity are equal.
EccentricityProclear Monofocal
Infinity		Proclear Multifocal
Infinity		Proclear Monofocal
40 cm		Proclear Multifocal
40 cm
Central0.7010.0270.0080.161
5°0.3900.0350.0090.045
10°0.0420.0170.0090.021
15°0.0160.0200.0150.018
20°0.0150.0120.0150.028
25°0.0110.0160.0150.021
30°0.0110.0230.0120.019
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Fritschi, A.; Gerber, C.; Eggler, D.; Loertscher, M. Simultaneous Myopic Defocus for Myopia Control: Effect on Accommodation, Peripheral Refraction and Retinal Image Quality in Non-Presbyopic Patients. Optics 2021, 2, 200-215. https://doi.org/10.3390/opt2040019

AMA Style

Fritschi A, Gerber C, Eggler D, Loertscher M. Simultaneous Myopic Defocus for Myopia Control: Effect on Accommodation, Peripheral Refraction and Retinal Image Quality in Non-Presbyopic Patients. Optics. 2021; 2(4):200-215. https://doi.org/10.3390/opt2040019

Chicago/Turabian Style

Fritschi, Alina, Chloe Gerber, Damian Eggler, and Martin Loertscher. 2021. "Simultaneous Myopic Defocus for Myopia Control: Effect on Accommodation, Peripheral Refraction and Retinal Image Quality in Non-Presbyopic Patients" Optics 2, no. 4: 200-215. https://doi.org/10.3390/opt2040019

APA Style

Fritschi, A., Gerber, C., Eggler, D., & Loertscher, M. (2021). Simultaneous Myopic Defocus for Myopia Control: Effect on Accommodation, Peripheral Refraction and Retinal Image Quality in Non-Presbyopic Patients. Optics, 2(4), 200-215. https://doi.org/10.3390/opt2040019

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