Through-focus modulation transfer function (MTF) and phase transfer function (PTF) were measured in the Average Corneal Model (ACE) model which reproduces the average spherical aberration and longitudinal chromatic aberration of the cornea [14 (link)]. MTF and PTF can be calculated by the modulus and phase, respectivey, of the Fourier transform of the line spread function measured in the ACE model. Data were collected for six IOL designs (Table 1 Designs considered in the study. All the designs are from Abbott Medical Optics Inc (Santa Ana, California).
) of 20 D power in white light from 0 to −3 D. Additionally, the US Air Force (USAF) pictures were recorded under the same conditions. A pupil size of 3 mm was used to evaluate the optical performance based on the average age of cataract patients and the changes in pupil size related to age under photopic conditions [21 (link),22 ].
Based on the optical bench data, the preclinical metrics were calculated for each defocus position for two monofocal IOLs, three multifocal IOLs with different add powers ( +2.75, +3.25 and +4 D) and an extended-range-of-vision (ERV) IOL of 20 D power. These IOL models as well as a description of their base technology are listed inTable 1 .
Four different preclinical metrics were evaluated to determine how well they estimate the clinically measured defocus curves and compared to the MTF at 50 and 100 cpmm.
Spatial frequencies in the image plane of 50, 100 and 150 cpmm measured in the ACE model for 20 D IOLs correspond to approximately 15, 30 and 60 cycles per degree respectively in the object plane of a real eye [26 (link)].
To evaluate the performance at intermediate distances, the area under the through-focus VA (AU defocus) was used [27 (link),28 (link)]. The AU defocus was defined as the area under the clinical VA (in decimal units) from −0.5 to −2 D in 0.5 D steps. The AU clinical defocus was correlated with the area under the through-focus curves of the different metrics for the same defocus range (between −0.5 and −2 D).
IOL model | Design | Optics material | Technology | Spherical aberration | Add power at IOL plane (D) |
---|---|---|---|---|---|
ZCB00 | Monofocal | Acrylic | Refractive, aspheric | −0.27 | NA |
911A | Monofocal | Silicone | Refractive, spheric | + 0.17 | NA |
ZM900 | Multifocal | Silicone | Diffractive, aspheric | −0.27 | + 4.00 |
ZLB00 | Multifocal | Acrylic | Diffractive, aspheric | −0.27 | + 3.25 |
ZKB00 | Multifocal | Acrylic | Diffractive, aspheric | −0.27 | + 2.75 |
ZXR00 | ERV | Acrylic | Diffractive, aspheric | −0.27 | NA |
Spherical aberration (Zernike coefficient Z12) for a pupil diameter of 6 mm
Spherical aberration provided for a 21.5 D lens and 6 mm pupil.
ERV = extended-range-of-vision IOL.
Based on the optical bench data, the preclinical metrics were calculated for each defocus position for two monofocal IOLs, three multifocal IOLs with different add powers ( +2.75, +3.25 and +4 D) and an extended-range-of-vision (ERV) IOL of 20 D power. These IOL models as well as a description of their base technology are listed in
Four different preclinical metrics were evaluated to determine how well they estimate the clinically measured defocus curves and compared to the MTF at 50 and 100 cpmm.
Spatial frequencies in the image plane of 50, 100 and 150 cpmm measured in the ACE model for 20 D IOLs correspond to approximately 15, 30 and 60 cycles per degree respectively in the object plane of a real eye [26 (link)].
To evaluate the performance at intermediate distances, the area under the through-focus VA (AU defocus) was used [27 (link),28 (link)]. The AU defocus was defined as the area under the clinical VA (in decimal units) from −0.5 to −2 D in 0.5 D steps. The AU clinical defocus was correlated with the area under the through-focus curves of the different metrics for the same defocus range (between −0.5 and −2 D).