CN1245406A - 用于改进视力及视网膜图象分辨力的设备 - Google Patents

用于改进视力及视网膜图象分辨力的设备 Download PDF

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CN1245406A
CN1245406A CN97181504A CN97181504A CN1245406A CN 1245406 A CN1245406 A CN 1245406A CN 97181504 A CN97181504 A CN 97181504A CN 97181504 A CN97181504 A CN 97181504A CN 1245406 A CN1245406 A CN 1245406A
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aberration
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CN1184926C (zh
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戴维·R·威廉姆斯
梁俊中
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University of Rochester
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/103—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining refraction, e.g. refractometers, skiascopes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/14—Arrangements specially adapted for eye photography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/14—Arrangements specially adapted for eye photography
    • A61B3/15—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing
    • A61B3/156—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing for blocking
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
    • G01J9/00—Measuring optical phase difference; Determining degree of coherence; Measuring optical wavelength

Abstract

一种用于改进视力及视网膜图象分辨力的设备,包括由激光束(102)在活眼(100)的网膜(101)上产生的点光源。从该视网膜反射的激光束在哈特曼－夏克波阵面传感器(148)的小透镜阵列上被接收,以使每个小透镜在与该小透镜阵列相邻设置的CCD摄象机(146)上形成该视网膜上点光源的空间图象。由CCD摄象机输出的信号被计算机(150)获取,该计算机处理该信号并产生可被用于控制光学补偿装置或波阵面补偿装置(如可变形反射镜(118))的矫正信号。它还可被用来制造接触透镜或眼内透镜,或用于引导外科处置以便矫正眼睛象差。所有这些方法可矫正除散焦及散光之外的象差,允许改进视力及改进眼睛内部的成象。

Description

用于改进视力及视网膜图象分辨力的设备
发明背景
本发明目的在于用来改进视力及视网膜图象分辨力的方法与设备。更准确地说，本发明目的在于用于测量与矫正眼睛波象差以使测得的数据可被用于研制用来改进眼睛光学性能的矫正光学元件的方法与设备。
不管在眼镜及接触透镜的设计中有多么显著的进步，现行的眼科透镜仍然只能矫正散焦与散光。眼镜与接触透镜保留有未矫正的附加象差，比如球面象差、彗形象差以及许多不规则象差。眼睛的这些高级象差不仅使得在视网膜上形成的图象变模糊，从而损害视力，而且还使得从活的人体视网膜取得的图象变模糊。有两种障碍阻止了使用特殊设计的光学元件以矫正眼睛中散焦与散光之外的象差。首先，不可能进行眼睛不规则象差的定量测量。其次，除散焦与散光之外矫正眼睛单色象差的机理未得到证明。
验光师的主观屈光法及客观的自动屈光计只测量散焦与散光。它们不能测量包括用传统眼镜未矫正而遗留的所有象差在内的眼睛全部的波象差。由Walsh等人在Journal of the Optical Society of America A，Vol.1，pp.987-992(1984)公开的客观象差镜(objective aberroscope)提供了完整瞳孔的同期波象差测量，但不能以比大约0.9mm更细小的间隔对瞳孔进行取样(见Charman在Optometry and Vision Science，Vol.68，pp.574-583(1991)中的论述)。而且，用该方法对波象差的快速、自动化计算未做说明。
近来，这里的一位共同发明人与其他人一起，开发了一种测量眼体波象差的设备。在题目为“用哈特曼-夏克波振面传感器对人眼波象差进行的客观测量”的报告(Liang等人发表于J.Opt.Soc.Am.A.，Volume11，number 7，pp.1-9，July 1994，其公开内容结合于此作为参考)中，作者公开了一种哈特曼-夏克波振面传感器，它们被用于通过传感从眼睛射出的、由视网膜对聚焦在黄斑上的光反射而产生的波振面来测量人眼的波象差。使用在此处公开的系统，作者只能测量高达四级的多项式函数。适合高达四级多项式的波振面不能提供眼睛象差的完整描述。这种描述对于精确地计算眼睛的光学特性通常是不够的。这种仪器未曾配备来消除由其它表面(如透镜和眼睛角膜)反射的不需要的光。
以前还有一种以改进共焦扫描激光检眼镜轴向分辨力为目标，用以矫正散焦与散光之外眼睛单色象差的尝试。Bartsch等人在Vision Scienceand its Application，1994，Technical Digest Series，VoL.2(OpticalSociety of America，Washington，D.C.)pp.134-137(1994)中使用了一种使角膜第一表面上的折射归零的眼底接触透镜。可是，这种探索遇到的主要问题是眼的波象差依赖于眼的光学系统到处折射率变化的联合效应。或许由于这个原因，所说明的使用眼底接触透镜用以提高共焦扫描激光检眼镜轴向分辨力的尝试仅是不大的改进。
另一种探索是使用可变形的反射镜，一种在地-基望远镜中成功地补偿大气扰动的装置。在Bille的No.4,838,679美国专利中曾预先建议将一种可变形反射镜使用在与人眼相结合的共焦激光扫描检眼镜中，但未曾建议或公开测量人眼波象差的方法。在Applied Optics，Vol.28，pp.804-808中，Dreher，Bille以及Weinreb只是表明将可变形反射镜使用于眼睛，而且仅仅是矫正眼睛的散光，情况不比使用传统眼科透镜提供的矫正更好。使用光学元件矫正高于二级的单色象差从未达到过。在这两个系统中，均未公开测量眼睛高级象差的适当方法。在由Masters，B.R.，Springer-Verlag编辑的Noninvasive Diagnostic Techniques inOphthalmology，pp.528-547(1990)中，Bille等人建议使用与可变形反射镜结合的波振面传感器，但操作系统从未公开或实现。发明概述及目的
考虑到上述情况，显然，在本领域中需要一种用于生产眼科光学元件的方法与设备，该光学元件能提供超过目前可达到的改进的或超常的视力，以及高分辨力的视网膜图象。因此，本发明的主要目的在于提供一种用于精确测量眼睛更高级象差以及使用由此测得的数据与定做的光学元件一起补偿这些象差的方法与设备。
本发明还有一个目的在于提供一种改进的波振面传感器，这种传感器抑制从视网膜以外的组织反射的光并能提供眼体象差的完整测量。
本发明的进一步目的在于利用这种改进的波振面传感器与可变形反射镜相结合的以反馈方式矫正波象差，从而使对象达到标准的或超常的视力。
本发明又一个主要目的在于提供一种产生高分辨力视网膜图象的方法与设备，它容许显微结构成象人体视网膜中的单细胞尺寸。
简要地说，本发明的所有目的通过提供一用于接收来自眼睛视网膜反射光的系统来达到。瞳孔平面中的波振面在哈特曼-夏克波振面传感器的小透镜阵列平面中被重新创造。小透镜阵列中的每个小透镜被用来形成与该小透镜阵列相邻设置的CCD摄象机上视网膜上点光源的空间图象。按照由激光束在视网膜上产生点光源的形式，眼的波象差以正比于每个小透镜上波阵面的局部倾斜的量移动每个光斑。数字式CCD摄象机的输出被送给计算机，然后由该计算机计算波象差并向可变形反射镜提供信号。在累接的程序(iteralive procedure)之后，该可变形反射镜最终获得与开头所测量的波象差相同的形状，但具有一半的幅值。该变形为适合于将畸变的波阵面弄平成平面波的一种变形，它能改进图象质量。
按照其方法方面，如上所述，本发明的系统首先使用计算机取得CCD图象。然后，该计算机计算由波阵面传感器的每个小透镜形成的光斑的质量中心。计算出每个焦斑(focus spot)在X与Y方向的位移，然后用作倾斜数据，以便与65个Zernik多项式的一次微分之和相符合，使用最小平方法来确定每个多项式的权重。
然后，Zernik多项式用计算出的系数进行加权。在波阵面的符合当中65个多项式包括除柱塞项(piston term)之外径向放大率小于或等于10的全部Zernike模式。
然后被加权的Zernike多项式相加在一起，这导致重建的波象差。该波象差然后在可变形反射镜致动器(actuator)的位置上被评定以便产生矫正信号，如上所述，该矫正信号由计算机传送给波阵面补偿装置或可变形反射镜。这样的反馈环持续接收重建的波象差结果，反馈适合的矫正信号，直至重建的波象差信号的均方根值达到一渐近值，在该数值点上可变形反射镜产生的变形将补偿眼睛的全部检测象差。
当重建的波象差信号达到其渐近值时，最终的象差信号(包括所有的预先产生的信号直至均方根误差达到渐近值)可被用于生产接触透镜以便矫正人眼的全部单色象差，或者用于外科处置。
本发明还可被用来提供视网膜的高分辨力图象。产生这种图象的系统使用的是被指定用于向视网膜盘照明以提供视网膜图象的氪闪光灯，该视网膜图象被可变形反射镜反射到一透镜上并通过一孔阑，以使视网膜的反射图象在第二CCD摄象机上聚焦。由该摄象机产生的信号以同上述与第一CCD摄象机相关的类似方式来取得，并存储于计算机中以供后面的应用。
随着本发明的所有目的、优点及特征在后文中会变得更明显，通过参照下面对本发明及所附的权利要求详细描述并参照附图可以更清楚地明白本发明的性质。附图简述
图1为本发明系统的原理图；
图2为使用图1所示设备用于制造接触透镜或提供视网膜图象的本发明方法的流程图；
图3a-3d分别表示使用本发明的系统在进行适宜的补偿之前与之后波象差及相应的点扩散函数；以及
图4表示在适宜的补偿之前与之后眼睛波象差的Zernike衰变，它表明本发明不仅能矫正二极象差(散焦及散光)，而且还能矫正高级象差。优选实施例的详细描述
现在参见图1，这里以原理图形式示出可被用于改进视觉性能及提供眼睛高分辨力视网膜图象两个方面的本发明的设备。如图1所示，本发明的设备利用哈特曼-夏克波阵面传感器测量眼睛象差，然后在带有光学补偿元件如可变形反射镜的闭合反馈环中对其进行矫正。
为测量眼睛的波象差，由激光器102在视网膜上产生一点光源。来自激光器102的光通过一快门(未示出)进行控制。该激光通过空间滤波器104并由消色差双合透镜106准直。经准直的激光束被偏振分束器110反射，通过透镜112及116并入射到可变形反射镜118上。从可变形反射镜118反射的激光束由透镜120聚焦，通过透镜122与第二分束器124并在瞳孔上以大约1.5mm的直径到达眼球100。眼球100的晶状体在其视网膜101上聚焦该激光束。通过眼球100及透镜122相对于透镜120移动，可能使受测试眼的近视或远视得到矫正。
从视网膜101反射的光在瞳孔上形成畸变的波阵面，该畸变的波阵面由透镜122与120在可变形反射镜的平面内重建，还由透镜116与112在哈特曼-夏克波阵面传感器148的小透镜阵列平面内重建。瞳孔与小透镜的二维阵列148成共轭关系。阵列148中的每个小透镜在CCD摄象机146上形成视网膜上点光源的空间图象。CCD摄象机146将数字化图象传送至计算机150，在此处该数字化图象被存储在RAM中或存储在磁性或其它存储介质上。
象差以同每个小透镜上波阵面的局部倾斜成正比的量移动每个光斑。波阵面的倾斜可从与已知无象差基准相关的那些光斑的位移来确定。波阵面传感器154在同时跨越该扩张瞳孔的217个位置上沿X与Y两个方向测量局部倾斜。根据倾斜的阵列，如下文所述该波象差被重建。
构成波阵面传感器154一部分的分束器110最好具有如偏振分束器那样的构形，以便消除由眼球100角膜的第一表面和其它光学元件(如透镜112、116、120和122)反射的不需要的光。否则这类光会干扰波阵面传感器154的工作并会使测量波象差的自动化作业更困难。
本发明的波阵面传感器154比以往可能有的提供更加完全的眼球象差测量，部分是因为在眼瞳孔中有大量采样被采用。使用本发明的设备已经发现，眼球100含有不能用眼镜或接触透镜矫正的复杂象差，且这样的象差在瞳孔大时很显著。本波阵面传感器154首先测量的五级及更高级的平均象差对眼睛的光学质量具有重大的影响。并且，超出级数的更高级象差是稳定的。这种稳定性是重要的，因为它表明使用静态光学矫正器(如定做的接触透镜)可使象差得到矫正。
一旦波象差被测量，如上所述，即受到与眼球100的瞳孔相共轭的装置的补偿，它能控制瞳孔中不同点上光的相位。如结合图2将进一步详细描述的那样，在软件控制下，计算机150产生一反馈至可变形反射镜118的矫正信号。可变形反射镜118(由Xinetics公司生产的no.RX-170407-C型产品是合用的)与眼球100的瞳孔相共轭并产生变形以补偿眼睛波象差。可变形反射镜118含有一带有安装于背表面上矩形阵列中37个致动器的镀铝玻璃面板。另一方面，可使用液晶装置、微电机反射镜、双压电晶片反射镜或其它适宜的装置以代替可变形反射镜118。
图1的设备使用如下。计算机150通过打开发自激光器102的激光束的路径起动测量过程。从视网膜101返回的光被使用于测量波象差。哈特曼-夏克波阵面传感器148提供眼睛波象差的测量，可变形反射镜118据此而被驱动以对其进行矫正。这一过程由于计算机150而重复进行，以产生适宜的信号而引起可变形反射镜118持续变形直至被测试波象差的均方根误差达到一渐近值，尽管也可能使用其它的准则。在此处，可变形反射镜118取得了适合于对眼睛象差提供波阵面补偿的形状。
还在此处，由计算机150产生的最终的矫正信号可被提供给用于制做接触透镜的接触透镜制做系统152，该接触透镜将重复可变形反射镜118的波阵面补偿特性。本领域的普通技术人员会清楚，这样的接触透镜将成为用于每个要提供补偿的眼睛的定做依据。
现在转向图2，这里以流程图形式表示利用从CCD装置146获得的数据由驻留在计算机150中的软件所执行的步骤。在步骤1中，由计算机150从CCD摄象机中获取数字图象。每个图象由12比特位的512个象素乘512个象素组成。然后在步骤2中，计算机150对由波阵面传感器的每个小透镜形成的光斑的重心进行计算。每个光斑的重心规定它的位置。通过比较在参考图形中与从眼睛获得的图象中各相应光斑的位置，每个聚焦光斑在X与Y两个方向的偏移可被计算出。
接下来在步骤3中，倾斜数据与65个Zernike多项式的一次微分之和相符合，使用最小平方法以确定每个多项式的权重，这与上文提到的由Liang等人在其报告中所讨论的内容类似，虽然他们的方法不包括超过四级的多项式。
然后在步骤4中，用步骤3中计算出来的系数对Zernike多项式加权。波阵面符合中的65个多项式多包括径向倍率小于或等于10的全部Zernike模型，但柱塞项除外。一级Zernike模型为线性项。二级模型为平方项，其对应于常见的象差、散焦及散光。三级模型为立方项，其对应于彗形象差和类似彗差的象差。四级模型包括球面象差以及其它类型的象差。五至十级模型为更高级的、不规则的象差。瞳孔中波阵面中的局部不规则性用这些更高级的Zernike模型来表示。
加权的Zernike多项式在步骤5中相加在一起，以取得重建的波象差。该波象差在可变形反射镜118的致动器的位置上被评定以便在步骤6中产生矫正信号，该矫正信号然后由计算机150传送至波阵面补偿装置，如图1中所示，该波阵面补偿装置最好是可变形反射镜118。该反馈环持续接收重建的波象差结果，反馈适宜的矫正信号直至重建波象差信号中的均方根误差达到一渐近值。在此处，可变形反射镜118如此产生变形，当眼睛通过它看时，它将补偿眼睛100的全部被检测象差。
正如本领域的普通技术人员所了解的那样，眼镜和接触透镜适用于矫正视力，但它们只能矫正眼睛的散焦和有时矫正散光。甚至正常的眼睛也具有用传统的眼镜或接触透镜不能矫正的其它象差。本发明的波阵面传感器154能自动地测量这些象差。因而，使用图1的适合的光学系统容许在散焦与散光之外矫正人眼的单色象差。因此，图1的适合的光学系统在改善视力与提供更清晰的视网膜图象两方面对人眼提供空前的视觉质量。
图3a-3d为波阵面传感器数据的图形，表示本发明适合的光学系统成功地矫正眼睛的象差。图3a与3b分别表示，对于一个被测对象，使用本发明无适宜补偿与有适宜补偿时相对于瞳孔位置的波阵面误差。在有四个受测对象的测试中，适当的补偿使跨过6mm瞳孔的峰至谷波阵面误差平均减少至原来的四分之一。
图3c与3d分别表示无适宜补偿与有适宜补偿时由波象差计算出的点散布函数(PSF)。适当的补偿会增加Strehl比，它正比于PSF的峰值强度，从0.09至0.47。对于全部四个受测眼来说平均增加至近于原来的四倍，从0.06至0.23。补偿之后，所表示的用于该对象的PSF具有2.0微米的半宽度(FWHH)，接近于因单独衍射而期望的1.9微米的数值。本发明提供被认为是人眼从未达到的最好的视觉质量。
图4为与波象差的每个Zernike级相关的，面对四个眼睛平均的均方根波阵面误差曲线图。该均方根波阵面误差由适于高达五级的Zernike级补偿得以降低。眼镜、接触透镜和以往使用可变形反射镜矫正眼睛象差的一种尝试只矫正二级象差(散焦与散光)。
矫正一旦实现，本发明的设备可用于向对象提供超常的视网膜成象质量，在此情况下，该对象通过可变形反射镜118观察可视映象。如使用对于细光栅的对比灵敏度所进行的测量，对于通过本设备的单独观察已获得视力的六倍的改善。通过适合的光学系统，单个人可看见非常高频率的光栅，胜过没有适合光学系统的常态观察的分辨力限度。
另一方面，矫正一旦实现，示于图1中的本发明的设备还可被用于提供视网膜101的高分辨力图象。氪闪光灯138由透镜134、132、130和120在通过分束器124之后成象在眼瞳孔上。氪闪光灯138释放4毫秒的闪光，借此对1度直径的视网膜101上的视网膜盘进行照明。窄带干涉滤光片136对闪光灯138的光谱输出整形。
视网膜101的图象通过分束器124和透镜122与120为已被成形来补偿眼睛象差的可变形反射镜118反射，并且通过透镜116。而后该光被反射镜114反射到透镜140上并且通过孔阑141，被反射的图象在此被透镜142聚焦在CCD装置145上。与被CCD摄象机145收集的光相应的电信号，可以从CCD摄象机146获得数据的光获取系统相类似的方式来获得，然后存储在计算机150中用于后面的使用。该图象然后可在与计算机150相连接的监视器(未示出)上显示和/或传送至与计算机150相连接的适合的打印装置(未示出)。
使用本发明的设备，人的活体视网膜中的单个细胞第一次常规地被分辨。本发明适宜的光学系统提供一种用来以显微立体规模研究正常与病态活体视网膜的非侵入技术。眼底成象的横向分辨力的理论极限正比于扩展瞳孔的直径。如果适宜的补偿是相对例如8mm瞳孔完成的，则横向分辨力将会比相对2.5mm瞳孔增加至3.2倍，典型的瞳孔直径被目前适合的眼底摄影机所使用。
轴向分辨力随着瞳孔直径的平方增长，该轴向分辨力在视网膜的深度方向视力分段中是很关键的。因此，跨越8mm瞳孔完成适宜补偿在理论上可使共焦检眼镜的轴向分辨力比具有2.5mm出瞳的仪器增加至10倍。在深度方面PSF的半宽度(FWHH)为27微米，它接近于光学相干性层析X线照相术的数值，但提供了对于单独光学相干性层析X线照相术不可能有的高横向分辨力方面的附加优点。
本发明设备的成功证明，它还可被用于通过对眼睛光学系统整形来改进视力，如在激光屈光手术中或通过生产定做的光学元件，如接触透镜或眼内透镜。如图1与图2所示，最终的矫正信号可提供给接触透镜或眼内透镜制做系统或激光屈光外科处置152，以代替可变形反射镜118。本领域的熟练技术人员清楚，这样的接触透镜、眼内透镜或外科矫正对每个要提供补偿的眼睛将是定做的。除散焦与散光外的附加象差可用无论是开环还是闭环系统进行矫正。
此处描述的本发明考虑到与所示范的矫正这些象差的方法相结合对人眼的象差进行最完整的描述。本发明的应用有四方面。首先，本发明可被利用来提供对肉眼象差的更精确的测量。第二，本发明可被利用于评估各种矫正眼睛象差的技术，如定做眼镜，定做接触透镜及外科处置的益处。第三，本发明可被使用在光学仪器(如望远镜和双筒镜)、定做的眼镜、定做的接触透镜中改进视力以及使用外科处置，如光反射照相角膜切除术(PRK)来改进视力。第四，本发明可被利用于改进活体视网膜成象的轴向与横向分辨力。现行的眼底照相机存在的问题是，在现有技术中，眼睛象差限制它的分辨力，一种自发明检眼镜以来保留的限制。
虽然在此只对优选的实施方案进行了专门的图解与说明，但应理解，根据上述的技术以及在所附权利要求的权限之内，不脱离本发明的精神与预定范围可对本发明作许多改进和变化。

Claims (28)

1.一种用于确定活眼波象差的波阵面传感器，所述波阵面传感器接收所述眼体视网膜反射的点光源图象，包括：
构成用于接收所述视网膜反射的所述点光源图象及用于产生视网膜上点光源空间图象的小透镜阵列的多个小透镜；所述小透镜阵列如此配置，以使其能对至少五级象差提供分辨力；
一与所述小透镜阵列相邻设置的摄象机，用于观察在所述小透镜阵列的所述多个小透镜的每个小透镜上形成的视网膜上点光源的所述空间图象；以及
一相连的数字数据处理器，以从所述摄象机接收视频输出信号并将其转换成表征所述视网膜上点光源空间图象的数字信号，所述数字数据处理器利用所述表征数字信号进一步对所述眼体的波象差进行计算，以便包括至少五级模型。
2.如权利要求1的波阵面传感器，进一步包括一偏光镜，所述视网膜反射的所述点光源图象在被所述多个小透镜接收之前通过该偏光镜。
3.如权利要求1的波阵面传感器，进一步包括一与所述数字数据处理器相连的光学补偿装置，以致于在所述数字数据处理器的控制之下，所述光学补偿装置被进行调整，以对所述眼体的所述波象差提供波阵面补偿。
4.如权利要求3的波阵面传感器，进一步包括一偏振滤光器，所述视网膜反射的所述点光源图象在被所述多个小透镜接收之前通过该偏振滤光器。
5.如权利要求1的波阵面传感器，其中所述小透镜阵列能够提供高达至少十级波象差的分辨力。
6.如权利要求1的波阵面传感器，其中所述小透镜阵列为具有高达217个小透镜的哈特曼-夏克波阵面传感器。
7.如权利要求1的波阵面传感器，进一步包括至少一个与其相连的接触透镜及眼内透镜制做系统，以便为制做至少一个用于对所述活眼的所述波象差提供波阵面补偿的接触透镜或眼内透镜从所述数字数据处理器接收计算出的波象差。
8.如权利要求1的波阵面传感器，进一步包括与其相连接的外科设备，以从所述数字数据处理器接收计算出的波象差，供在所述活眼上执行手术以对所述活眼的所述波象差提供波阵面补偿。
9.如权利要求3的设备，其中所述光学补偿装置为可变形反射镜、液晶器件、微电机反射镜和双压电晶片反射镜中的一个。
10.用于制做接触透镜或眼内透镜以矫正活眼至少三级波象差的设备，包括：
用于产生所述活眼视网膜反射的点光源图象的装置；
用于接收所述被反射的点光源图象并将其转换成相应数字信号的装置；
利用所述数字信号用于计算眼体波象差以致包括至少三级模型的数字数据处理器，以及
至少一个与之相连的接触透镜与眼内透镜制做系统，以便为制做至少一个可对所述活眼的所述至少三级波象差提供波阵面补偿的接触透镜或眼内透镜，从所述数字数据处理器接收计算出的波象差。
11.如权利要求10的设备，其中所述产生装置包括形成用于接收所述视网膜反射的所述点光源图象的小透镜阵列的多个小透镜，所述小透镜阵列如此配置，以使其能对至少三级象差提供分辨力。
12.如权利要求10的设备，进一步包括一偏振滤光器，所述视网膜反射的所述点光源图象在被接收所述被反射点光源用的所述装置接收之前通过该偏振滤光器。
13.一种制做接触透镜以矫正活眼的至少三级波象差的方法，包括如下步骤：
产生所述活眼视网膜反射的点光源图象；
接收所述被反射的点光源图象并将其转换成相应的数字信号；
利用所述数字信号计算所述眼体的波象差，致使包括至少三级模型；以及
接收计算出的波象差用于制做至少一个接触透镜，以便对所述活眼的所述至少三级波象差提供波阵面补偿。
14.如权利要求13的方法，进一步包括使所述被反射点光源图象产生偏振的步骤，以便在接收所述被反射点光源图象之前消除从所述活眼角膜反射的杂散光。
15.一种利用波阵面传感器确定活眼波象差的方法，该波阵面传感器接收所述眼体视网膜反射的点光源图象，包括如下步骤：
提供构成用于接收所述视网膜反射的所述点光源图象的小透镜阵列的多个小透镜，所述小透镜阵列如此配置，以使其能对至少五级象差提供分辨力；
接收在所述小透镜阵列的所述多个小透镜的每个小透镜上形成的视网膜上点光源的空间图象，并产生其表征信号；以及
将所述信号转换成表征所述视网膜上点光源空间图象的数字信号，并且利用所述表征数字信号计算所述眼体的波象差，以致包括至少五级模型。
16.如权利要求15的方法，进一步包括使所述被反射点光源图象产生偏振的步骤，以便在所述多个小透镜接收所述被反射点光源图象之前消除从所述活眼角膜反射的杂散光。
17.一种利用波阵面传感器确定活眼波象差的方法，该波阵面传感器接收所述眼体视网膜反射的点光源图象，包括如下步骤：
提供构成用于接收所述视网膜反射的所述点光源图象的小透镜阵列的多个小透镜，所述小透镜阵列如此配置，以使其能对至少三级象差提供分辨力；
接收在所述小透镜阵列的所述多个小透镜的每个小透镜上形成的视网膜上点光源的空间图象，并产生其表征信号；
将所述信号转换成表征所述视网膜上点光源空间图象的数字信号，并且利用所述表征数字信号计算所述眼体的波象差，以便包括至少三级模型，以及
利用所述计算出的所述活眼的至少三级波象差对光学补偿进行调整，以为所述活眼的所述波象差提供波阵面补偿。
18.产生活眼视网膜高分辨力图象用的设备，包括：
用于产生所述活眼视网膜反射点光源图象的装置；
用于接收所述被反射的点光源图象并将其转换为相应数字信号的装置；
用于利用所述数字信号计算至少三级波象差的数字数据处理器；
用于对所述活眼上的视网膜盘照明以产生视网膜盘图象的装置；
用于反射所述视网膜盘图象的光学补偿装置，所述光学补偿装置利用所述计算出的波象差进行调整，以为所述活眼提供对于所述波象差的波阵面补偿；以及
在被所述光学补偿装置反射之后，用于提供所述被反射视网膜盘图象的装置。
19.如权利要求18的设备，其中所述光学补偿装置为可变形反射镜、液晶器件、微电机反射镜及双压电晶片反射镜中的一个。
20.如权利要求18的设备，进一步包括一偏光镜，在被所述多个小透镜接收之前所述视网膜反射的所述点光源图象通过该偏光镜。
21.如权利要求18的设备，其中所述的产生装置包括构成用于接收所述视网膜反射的所述点光源图象的小透镜阵列的多个小透镜，所述小透镜阵列如此配置，以使其能对至少三级象差提供分辨力。
22.一种结合有用于确定活眼波象差的波阵面传感器的光学仪器，所述波阵面传感器接收所述眼体视网膜反射的点光源图象，包括：
构成用于接收所述视网膜反射的所述点光源图象及用于产生视网膜上点光源空间图象的小透镜阵列的多个小透镜；所述小透镜阵列如此配置，以使其能对至少五级象差提供分辨力；
一与所述小透镜阵列相邻设置的摄象机，用于观察在所述小透镜阵列的所述多个小透镜的每个小透镜上形成的视网膜上点光源的所述空间图象，以及
一相连的数字数据处理器，以从所述摄象机接收视频输出信号并将其转换成表征所述视网膜上点光源空间图象的数字信号，所述数字数据处理器利用所述表征数字信号进一步对所述眼体的波象差进行计算，以致包括至少三级模型，因而当所述活眼利用所述光学仪器时视力得到改善。
23.一种产生活眼视网膜上高分辨力图象的方法，包括如下步骤：
产生所述活眼视网膜反射的点光源图象；
接收所述被反射的点光源图象并将其转换为相应的数字信号；
利用所述数字信号计算所述至少三级波象差；
照明所述活眼上的视网膜盘，以产生视网膜盘图象；以及
在光学补偿装置上反射所述视网膜盘图象，所述光学补偿装置如此被调整，以为所述活眼的所述波象差提供波阵面补偿。
24.如权利要求23的方法，进一步包括使所述被反射的点光源图象产生偏振的步骤，以在接收所述被反射的点光源图象之前消除从所述活眼的角膜反射的杂散光。
25.产生活眼视网膜高分辨力图象用的设备，包括：
用于确定所述活眼至少三级波象差及用于产生其表征矫正信号的装置；
用于反射所述视网膜图象并接收所述矫正信号的光学补偿装置，所述光学补偿装置利用所述矫正信号如此进行调整，以为所述活眼提供对于至少三级波象差的波阵面补偿；以及
用于在其被所述光学补偿装置反射之后提供所述视网膜的所述高分辨力图象的装置。
26.用于在活眼的视网膜上完成手术以便矫正波象差的设备，包括：
用于产生所述活眼的所述视网膜的被反射点光源图象的装置；
用于接收所述被反射的点光源图象并将其转换为相应数字信号的装置；
用于利用所述数字信号计算该眼体波象差的数字数据处理器，以及
用于控制激光光源的装置，所述装置被进行连接以接收由所述数字数据处理器计算出的波象差，以便控制所述激光光源的激光对所述视网膜的轰击，以为所述活眼的所述波象差提供波阵面补偿。
27.如权利要求26的设备，其中所述用于产生的装置包括构成用于接收所述视网膜反射的所述点光源图象的小透镜阵列的多个小透镜。
28.如权利要求26的设备，进一步包括一偏振滤光器，所述被反射的视网膜上点光源图象在被用于接收所述被反射点光源的所述装置接收之前通过它。
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