For the measurement of accommodation and vergence behavior in response to targets at different depths, infants underwent photorefraction with a remote haploscopic photorefractor (
Fig. 1 , designed by Israel Abramov and Louise Hainline, Infant Study Center, Brooklyn College of the City University of New York). The apparatus has been described in detail elsewhere.
23 24 It consists of a conventional off-axis photorefraction system as described by Abramov et al.
38 The camera used in this system (
Fig. 1 , J) views the infant’s eyes through a periscope arrangement consisting of a beam splitter (
Fig. 1 , F) and a first surface mirror (
Fig. 1 , G).
The target is presented on a flat-screen monitor that can be moved to positions between 2 and 0.25 m from the infant along a motorized beam. In this study, the target moved among five viewing distances (2, 1, 0.5, 0.33, and 0.25 m). Infants viewed the target at each distance in the same pseudorandom order (0.33, 2, 0.25, 1, and 0.5 m). The target monitor moved between each new depth position at a constant velocity of 0.4 m/s. Thus, transitions between targets took between 0.2 and 0.7 second. Photographs were usually taken within 0.5 second of the target reaching its final position. This took longer only if the infant was inattentive. Infants were very interested in the movement of the target between positions, however, and maximum attention was usually obtained during and immediately after target movement.
The target in this study was a colored picture of a clown’s face subtending 4.2° by 2.8° at 2 m (the farthest distance tested) and containing a range of spatial frequencies.
23 24 The optical pathway for target viewing was separate from the optical pathway used for photorefraction. The target was viewed through two concave mirrors (
Fig. 1 ; C, D) positioned so that a virtual image of the target appeared directly in front of the infant. The infant saw the approaching and receding target, immediately followed by the camera flash. Enough time was given after each flash for any initial after-image of the flash to subside. Each infant viewed the target while sitting on his or her caregiver’s lap, and a photograph of the infant’s eyes was taken by the photorefractor immediately after target stopped moving and when the infant was seen to be attentive (through a separate video monitor of the infant’s face).
The optical pathway of the fixation target was arranged so that occlusion of one eye could take place remote from the subject, in front of the upper concave mirror (
Fig. 1 , C). An image of the infant’s face was projected onto this mirror through the virtual imager (
Fig. 1 , E), resulting in a virtual infant. Occluding one eye of the virtual infant is identical with occluding the infant’s eye directly; however, both of the real infant’s eyes could still be photographed by the photorefractor. This setup is particularly suitable for working with infants, because the occluder is invisible to the participant and is not close to the infant’s face. This allows us to test for changes in vergence position when no retinal disparity cues are available to the infant.
Photographs were measured with image-analysis software (Photoshop; Adobe Systems, Mountain View, CA). An estimation of the accommodative response of the infant was obtained by measurement of the size of the fundal crescent in relation to the pupil (for details of calibration, see Refs.
23 ,
24 ). Measurement accuracy in our laboratory for this method, accounting for interscorer reliability, is ±0.3 D of accommodation, with a “dead zone” around 0 D of approximately ±0.5 D where no crescents are detectable. Vergence was calculated from the position of the corneal reflection of the flash in relation to the pupil center. As convergence occurred, the pupil center moved nasally in relation to the corneal reflection (first Purkinje image). By applying the Hirschberg ratio (1-mm corneal reflection change per 12.2° of vergence change
10 39 ) we derived an angular estimate of vergence. An average value for the Hirschberg ratio was used because the number of infants who did not complete testing would increase if we attempted to obtain individual Hirschberg ratios. Vergence angle was adjusted for angle λ, with account taken of the developmental change in this value.
39 Measurement accuracy for vergence in our laboratory is ±1.1° (approximately 2Δ) of vergence change. In this study, vergence was measured in meter angles (MA: 1/distance at which the eyes are converged) to be directly comparable to accommodation measured in diopters (1/distance to plane of focus).
At each visit, the parents were also asked about the ocular misalignments that they had seen at home. Questions were identical with those used by Horwood
8 so that direct comparisons could be made with previous data. Infants were given basic orthoptic tests including cover test, ocular motility, fixation behavior, convergence to near point, and 20Δ base-out prism test.
40