为获得高分辨率视网膜血管图像，在自适应成像系统中，采用双光源照明模式。由于人眼存在色差，采用双光源照明模式会导致探测到的波前与实际需校正波前不一致。采用36 项Zernike 多项式拟合人眼波前，利用Liou &Brenann、Navarro 模型眼和真实人眼分析了人眼色差对夏克-哈特曼波前探测器的影响：对于Liou & Brenann 和Navarro 模型眼，561 nm 和785 nm 光的波前色差均方根值(RMS)分别为0.09λ 和1.44λ ，去除离焦项后的波前色差RMS 值分别为0.0025λ 和0.01λ ；对于真实人眼，两光源的波前色差RMS 值为1.92λ ，去除离焦项后的波前色差RMS值为0.04λ 。根据Maréchal 判据，除离焦项外，色差对其他波前像差的影响均方根值小于衍射极限(1/14λ) ，故波前像差的影响可忽略。由色差造成的离焦量可通过移动成像相机进行补偿。从结果可以看出采用双光源照明的视网膜血管自适应光学成像方案是可行的。

To obtain the high resolution retinal vessels imaging, illumination mode of double light sources is adopted in the retinal vessels adaptive optics (AO) imaging system. Because of the existence of ocular chromatic aberration in humans, the actual wavefront and the detected wavefront are inconsistent. Adopting 36 Zernike polynomials to fit the human eye′s wavefront, the research is done on the influence of chromatic aberration on Shack- Hartmann wavefront sensor (S- H WFS) using Liou & Brenann eye model, Navarro eye model and the vivo human eye: for Liou & Brenann and Navarro eye model, the chromatic aberration root mean square (RMS) of 561 nm and 785 nm is 0.09λ and 1.44λ respectively with defocus, and is 0.0025λ and 0.01λ without defocus. For the vivo human eye, the chromatic aberration RMS of 561 nm and 785 nm is 1.92λ with defocus, and is 0.04λ without defocus. According to Maréchal Criterion, the influence on the other chromatic aberrations is under diffractive limit level (1/14λ) excluding defocus. So the influence of chromatic aberration without defocus can be neglected. Defocus resulting from chromatic aberration can be compensated by moving imaging charge coupled device (CCD). According to the results, it is feasible to adopt double light sources to obtain the retinal vessels in AO imaging system.