CN103338692B - 眼睛内部的结构的扫描控制照明的系统和方法 - Google Patents
眼睛内部的结构的扫描控制照明的系统和方法 Download PDFInfo
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Abstract
提供一种利用预先确定的照明光束的扫描模式来加强眼睛结构的照明的系统、装置和方法。进一步提供该系统、装置和方法以获得眼睛的多个结构的加强的单个图像。
Description
相关申请交叉引用
本申请按照35U.S.C.§1.19(e)(1)要求2010年10月15日提交的美国临时申请序列号61/455,178的优先权，该申请的全部内容通过引用结合于此。
技术领域
本发明涉及用于照明、获得眼睛内部的结构的图像，以及确定眼睛内部的结构的形状和位置，具体而言，涉及眼睛的角膜、天然人体晶状体及相邻结构。更具体地，本发明涉及这种结构的激光照明的可变控制扫描、采用精确校准的数码相机对被照明结构的图像的受控和预先确定的数字化捕获，以及被照明结构的加强的数字合成图像的创建。
背景技术
老花眼最经常表现为近视力缺陷，不能读取小号印刷字，尤其在约40-45岁的年纪之后在昏暗的光线下。老花眼，或随着年纪的调节幅度的下降，与眼睛不能改变允许人改变远和近之间的焦距的天然晶状体的形状有关，并且基本上发生在100％的人口中。调节幅度已显示出在人生的第五个十年中随着年龄稳定地下降。
每年有百万人发生白内障，或天然晶状体变得不透明和视觉暗淡的情况，并且采用外科技术进行有效地治疗，例如30年前由Kelman开创的超声乳化白内障吸出术。虽然多年来该技术已经得到改善，但眼外伤所涉及的安全性，尤其是受到粉碎硬性白内障所需的超声波能量的角膜内皮细胞的安全性是不理想的；尤其是对那些具有受损角膜内皮细胞的人，例如那些患有角膜内皮营养不良症的人。此外，激光在白内障治疗中的使用有进一步的问题。白内障散射光（包括激光），因此可防止激光治疗光束具有所需的组织效果。此外，白内障的光散射效应和其他浑浊化可使得在光学上难以确定晶状体的位置和形状。
为白内障制定的治疗是去除乳白的人体晶状体并且采用人工晶状体（“IOL”）进行替代。一般而言，IOL包括具有被称为触觉介面的塑料侧支柱的小塑料晶状体，以将晶状体保持在眼睛内部的囊袋内的位置上。IOL的示例性类型包括单焦晶状体、为患者提供在远处和阅读距离的多焦点视域的多焦IOL，以及为患者提供视觉调节的可调节IOL。许多IOL的灵活特性使得它们能够被转动和/或折叠以插入晶状体囊。
目前采用撕囊术和/囊切开手术来去除乳白的天然晶状体并且采用诸如IOL之类的晶状体替代材料进行替代。撕囊术一般包括去除晶状体前囊膜的一部分并在晶状体囊中创建孔或开口，该孔和开口至少部分地由撕裂动作造成。囊切开术一般包括切割晶状体囊，而不撕裂或最小化撕裂晶状体囊。因此，为了去除乳白的天然晶状体材料，晶状体囊被打开。存在若干已知的用于执行撕囊术和囊切开术的技术，包括Fugo等离子刀的使用。
近来，已经开发和引进了用于治疗白内障、老花眼、执行囊切开术，以及用于分割和去除天然晶状体材料的激光系统和方法。在共同转让的公开的专利申请US2007/0173794、US2007/0173795、US2007/0185475、US2010/0004641、US2010/0004643、US2010/0022994、US2010/002995、US2010/0042079、WO2007/084627，以及WO2007/084694中给出了此类创新的和新颖的系统和方法的示例，每个申请的全部公开内容通过引用结合于此。在共同转让的美国专利申请12/840,818、12/831,859、12/831,845、12/831,783以及12/842,870中给出了此类创新的和新颖的系统和方法的进一步的示例，每个申请的全部公开内容通过引用结合于此。
在白内障、老花眼的治疗中，眼睛的条件和眼睛的痛苦，尤其是在使用激光器用于此类治疗时，确定眼睛结构的位置（相对于眼睛的其它结构和/或相对于诸如激光器之类的任何治疗设备），和眼睛结构的形状是必要的，以允许激光能量的精确应用来影响治疗。一般而言，在做出此类确定时更准确和精确是有益的。此外，用于治疗医生观察的这些结构的视觉图像可以是有益的并且可以改善任何手术的结果。因此，如在本说明书中所详细提供的，本文提供对眼睛结构的照明的改进，该改进产生了改进的眼睛内部的结构的位置和形状的确定以及那些结构的加强图像。
发明内容
需要一种能够提供眼睛结构的加强图像并且能够提供那些结构的位置和形状的系统和方法。除了其他方面，本发明通过提供对此类结构的控制光束照明来解决这些需要。因此，此处提供一种用于眼睛结构的加强照明和用于捕获具有每个结构的最佳照明的那些结构的单个合成图像的系统和方法。
进一步需要图像捕获设备被良好地校准以能够产生眼睛结构的尺寸精确的图像。需要此类校准来消除图像失真的源，诸如照明光束的角度和用于形成眼睛结构的合成图像的图像捕获设备的图像平面之间的倾斜或图像捕获设备中的像差。此类的图像失真源在需要较大景深的成像应用中是常见的，诸如对眼睛结构成像的本申请。
因此，提供了一种用于加强多组件结构的组件的照明的方法，该方法包括：选择第一预先确定的照明光扫描模式，所述第一预先确定的照明光扫描模式具有预先确定的速率和扫描区域；选择第二预先确定的照明光扫描模式，所述第二预先确定的照明光扫描模式具有预先确定的速率和扫描区域；其中，第二扫描速率或区域中的至少一个不同于第一扫描速率或扫描区域；将第一扫描模式中的照明光束指向多组件结构的第一组件，由此创建第一照明图像；将第二扫描模式中的照明光束指向多组件结构的第二组件，由此创建第二照明图像；数字化捕获图像捕获设备的第一预先确定的部分上的第一照明图像；数字化捕获图像捕获设备的第二预先确定的部分上的第二照明图像，其中第二部分与第一部分不同；因此，通过图像捕获设备创建被照明组件的单个合成图像，而不需要将第一照明图像配准到第二照明图像。
进一步提供上述方法，在该方法中对于待扫描的组件优化至少一个预先确定的照明光扫描模式中；第一组件为眼睛的角膜；第一组件为任何眼睛的天然晶状体；和/或所述第二组件为眼睛的天然晶状体。
进一步提供一种用于校准图像捕获设备的方法，使得包括眼睛中感兴趣的组件的空间的三维容积中的每个点和图像捕获设备的二维图像平面之间存在已知的关系或映射。该方法包括在使用图像捕获设备来产生眼睛中的结构的图像之前（或之后）向图像捕获设备呈现一个或多个校准目标的手段，此类校准目标一并包括多个具有在空间的容积中的已知位置的唯一可识别对象的三维阵列或序列，在该空间的容积中眼睛将被成像。该方法进一步包括采用图像捕获设备捕获一个或多个校准目标的图像并识别捕获图像中的某些或所有的唯一可识别对象，以及记录某些或所有的唯一可识别对象在捕获图像中的位置的手段。此外，该方法包括确定在校准目标中的唯一可识别对象的已知位置和在捕获图像中的唯一可识别对象的记录位置之间的线性或非线性数学关系或映射的手段。再进一步，该方法包括使用前述映射来减少或消除在图像捕获设备中或在相对于空间的容积的图像捕获设备的几何布局中固有的图像失真的源的手段，在所述空间的容积中对象将被成像，例如，眼睛内部的结构或校准目标，并因此产生基本上尺寸精确的图像。通过尺寸精确来表示除单个整体比例因子之外，在通过图像捕获设备所捕获的图像中的实体（例如眼睛结构或部分的眼睛结构）之间的距离基本上与在被成像的实际对象中的相同实体之间的对应距离相同。
仍进一步，提供一种用于提供多组件结构的组件的加强照明的系统，该系统具有：用于提供照明光束的照明源；与用于扫描照明光束的照明光源光学相关联的扫描器；与光源和扫描器相关联的控制系统；该控制系统包括：第一预先确定的照明光束扫描模式，该第一预先确定的照明光束扫描模式具有预先确定的速率和扫描区域；第二预先确定的照明扫描模式，该第二预先确定的照明扫描模式具有预先确定的速率和扫描区域；其中，第二扫描速率或区域中的至少一个不同于第一扫描速率或区域；用于数字化捕获通过第一照明光束扫描模式产生的第一图像的装置；用于数字化捕获通过第二照明激光束扫描模式产生的第二图像的装置；并且，用于数字化捕获第一图像的装置和用于捕获第二图像的装置为相同装置的不同部分。
此外，提供一种用于眼睛结构的加强照明的系统，该系统具有：用于提供照明光束的照明源；与用于扫描照明光束的照明源光学关联的扫描器；控制系统，该控制系统与照明源和扫描器相关联；该控制系统包括：第一预先确定的照明扫描模式，该第一预先确定的照明扫描模式具有预先确定的速率和扫描区域；第二预先确定的照明扫描模式，该第二预先确定的照明扫描模式具有预先确定的速率和扫描区域；其中，第二扫描速率或区域中的至少一个不同于第一扫描速率或区域；用于数字化捕获通过第一照明光束扫描模式产生的第一图像的装置；用于数字化捕获通过第二照明光束扫描模式产生的第二图像的装置；并且，用于数字化捕获第一图像的装置和用于捕获第二图像的装置为相同装置的不同部分。
仍进一步，提供一种用于加强眼睛结构的照明的方法，该方法包括：以预先确定的速率和扫描区域在眼睛的角膜区域上扫描照明光束；以及，以预先确定的速率和区域在眼睛的晶状体区域上扫描照明光束；其中角膜的照明不同于晶状体的照明。该方法可进一步使得角膜和晶状体的照明分别是最优的。
本领域的普通技术人员将认识到，基于在这些说明书和附图中所陈述的教示，存在各种实施方案和这些教示的实施以实现本发明。因此，在该发明内容中的实施方案并没有意图以任何方式限制这些教示。
附图说明
图1A至1D为本发明的眼睛结构的相同激光扫描照明的四个不同的透视图。
图2为眼睛的瞳孔的示意图。
图3至图5为通过本发明获得的眼睛的单个合成图像。
图6为基于通过本发明获得的加强图像的可指向眼睛的治疗激光照射模式的图示。
图7A示意性地示出了根据本发明的用于校准对象（例如眼睛）的图像的系统的一部分。
图7B示意性地示出了根据本发明的图7A的系统的第二部分。
具体实施方式
一般而言，本发明涉及一种用于提供眼睛的加强激光扫描照明的方法和系统，以提供眼睛结构的改进图像，具体而言，为角膜和天然晶状体的改进图像。本发明进一步涉及一种利用加强激光扫描照明来确定角膜和晶状体的形状和位置并且提供那些结构的加强图像的系统和方法。
一般而言，本发明使用光束和扫描器来照明眼睛结构。光束可通过非相干光源或激光源来产生。在US2007/0173794、US2007/0173795、US2007/0185475、US2010/0004641、US2010/0004643、US2010/0022994、US2010/002995、US2010/0042079、WO2007/084627以及WO2007/084694中公开了可用于照明的激光束和扫描器系统的示例。在共同转让的美国专利申请12/840,818、12/831,859、12/831,845、12/831,783以及12/842,870中给出了此类激光束和扫描器系统的进一步示例。在使用激光源的情况下，照明激光应当是人眼安全激光。因此，照明激光可以是不同于治疗激光的激光，或者照明激光可以是治疗激光，但是功率水平低于激光可影响被照明结构的阈值。在使用非相干光源的情况下，在之前提及的US2007/0173794、US2007/0173795、US2007/0185475、US2010/0004641、US2010/0004643、US2010/0022994、US2010/002995、US2010/0042079、WO2007/084627、WO2007/084694、美国专利申请12/840,818、12/831,859、12/831,845、12/831,783以及12/842,870中所公开的激光束和扫描器系统可适合于包括这样的用于代替激光源进行照明的非相干光源。
在传统的照明技术中，一次性照明所有的结构并且捕获这些被照明结构的图像（例如采用数码相机）；眼睛的图像在不同的区域中和不同结构上过度曝光或曝光不足。因此，采用这些传统技术，人们相信，在单个图像中通常眼睛的多个结构的均匀照明地清晰且锐利的图像如果不是无法获得，就是难以获得的。替代地，此类传统图像具有过度曝光或曝光不足的区域，其导致了有害地影响整体图像的清晰度和锐度的亮点和暗点。这些有害的影响部分取决于眼睛的不同结构对照明光的不同反应。因此，最适合捕获例如晶状体的前表面的图像的照明光可能不是最适合捕获角膜的外围边缘的。然而，在这种“一个照明源适合”所有类型的技术中，在单个图像中使照明适合眼睛的所有结构是毫无办法的，或至少这是极其困难的。
为了解决传统照明和图像捕获系统的这些缺点，本发明扫描待被照明的眼睛结构上的照明光束。基于待被照明的眼睛结构、待被照明的那个结构的截面，以及瞳孔的相对位置和大小，预先确定扫描速率和扫描区域。由于照明光束沿着待被照明的眼睛的特定结构的截面扫描，因此通过预先确定的像素或图像捕获设备（例如数码相机）上的线来捕获来自那个扫描的照明图像。当眼睛中的额外结构被扫描时，其他的预先确定的像素，或数码相机上的线捕获它们的照明图像。以这种方式，基于每个单独结构的每个单独扫描，建立被照明的眼睛结构的合成图像，并且每个结构具有最佳的照明。因此，本系统提供了具有预先确定和预先选择的多个且不同的组成部分、子结构，或多组件结构的结构（例如人眼）的照明，以及产生在多组件结构中所有那些组件的单个、清晰和锐利的图像的能力。图像可在单个程序（多个照明扫描的串行集合）中实时产生，而不需要后续或以后对图像进行数字修改或数字加强（例如通过使用以商标PHOTOSHOP出售的软件）。因此，例如在本系统和方法中确定瞳孔的大小。在角膜的特定区域上执行光的扫描。该扫描优选以大约12-13mm的长度并且以基于相机的设置适合且优选最佳地照明角膜的速率进行。例如，将通过在例如相机的行X至X+250处的像素捕获来自该第一扫描的照明图像。然后，将执行眼睛的晶状体的前表面的特定区域的扫描（优选该区域直接在角膜区域的前面，并因此获得结构的截面）。为了避免来自瞳孔的干扰，该扫描以约7至7.5mm并且以基于相机的设置适合且优选最佳地照明晶状体的前囊的速率进行。例如，将通过在例如行X+252至X+300处的像素捕获该第二扫描的照明图像。以这种方式，可在单个图像中捕获角膜和晶状体的前囊的扫描图像两者，并且每个都具有不同的且最佳的照明。将在相机的更多行上继续扫描和捕获图像的步骤直到眼睛的所有所需结构已被捕获在单个图像中。此外，应当理解，对于不同的应用可改变在相机的行上的扫描的顺序和捕获的位置。另外，可通过激光器或通过超辐射发光二极管（SLD）产生用于扫描的光束。使用SLD的有益之处在于，SLD是非相干源，避免了降低图像质量的激光散斑。
翻到图1A至1D，存在从照明光的扫描图像的不同角度的四个视图以创建眼睛120结构的区域的单个合成图像100。因此，在这些附图中示出了角膜121和天然晶状体122，天然晶状体122具有前囊123和后囊124。图中还示出了图像窗口125，图像窗口125可以是照明系统（例如患者界面的一部分）。在这些附图中示出了代表用于照明眼睛结构的扫描照明光束的射线130。如从图像位置100可看出的，这些图显示了相同扫描、图像和眼睛结构但从不同视角（例如，如果一个使用时钟的面作为参考，则为12、3、6和9点）的不同透视图。
图2示出了眼睛的截面200，具有与瞳孔的边缘同心定位的计算机产生的线201。该线201可用于确定放大的瞳孔的直径，之后，该放大的瞳孔的直径可用于确定并优化定位在瞳孔后方的结构的特定照明扫描的长度。
图3提供了利用扫描光照明获得的眼睛结构的单个图像310，每个扫描具有不同的扫描速率和扫描区域，该速率和区域是预先确定的用以优化所获得的图像。因此，这里示出了角膜300、晶状体301，以及晶状体前囊302和后囊303。翻到图4，示出了与图3相同的图像310，位置和形状测定线已经经由计算机添加至其中。因此，线401沿着角膜的前表面并且具有多个点，为了说明和简化附图的目的，将多个点中的点401a、401b和401c编号。线402沿着角膜的后表面并且具有多个点，为了说明和简化附图的目的，将多个点中的点402a、402b和402c编号。线403沿着晶状体前囊并且具有多个点，为了说明和简化附图的目的，将多个点中的点403a、403b和403c编号。线404沿着晶状体后囊并且具有多个点，为了说明和简化附图的目的，将多个点中的点404a、404b和404c编号。这些基于从光扫描照明获得的加强图像产生的各个计算机产生的点和线被用于确定晶状体和角膜的位置和形状。之后，该位置和形状信息可用于确定激光治疗的照射模式，例如图6所示的照射模式。
扫描照明技术具有获得角膜的外围边缘（即仍清晰但毗邻巩膜的角膜的外截面）的清晰且锐利的图像的能力。例如在白内障手术期间，获得角膜的该部分的清晰图像，以及获得角膜的该部分的精确位置和形状是有利的。这是制造切口以提供到晶状体的入口的眼睛的该截面。因为角膜的该区域是清晰的，获得精确确定该区域的位置和形状所必需的图像的清晰度和锐度对传统技术（例如OCT）来说是困难的。此外，扫描照明技术加强了前囊和后囊的细节并且能够通过深度白内障对后囊成像。
为了校正之前参照图1-6描述的系统和方法所产生的图像，可采用校准程序。如图7A-B所示，校准系统100包括图像捕获设备102（例如照相机），图像捕获设备102包括成像透镜104和具有相对于透镜104的光轴A成角度的平面的平面检测器106。图像接收孔径108以对象容积110为目标，其包含图像捕获设备102形成图像的对象。这样的具有在透镜104的光轴A和检测器106的平面之间的适当选择的角度的布置允许图像捕获设备102形成具有在z方向的较大深度的焦点的图像，该z方向与图7B所示的眼睛120的晶状体的光轴对齐。
参照图7A，为了校准系统，将包含唯一可识别对象（例如方块1、2、…）的一个或多个目标呈现给（通常按顺序地）图像捕获设备102。目标为仔细制造并且被精确地放置在已知位置上。这种唯一可识别对象的一个示例为“增强现实标签（Augmented Reality Tags）”中所描述的AR标签，增强现实：实用指南，Stephen Cawood和Mark Fiala。
针对每个目标产生一个或多个图像。将在平面检测器106处形成的图像发送至处理器112，其中处理器112分析每个图像并识别图像中的一些或所有的唯一可识别对象，并将唯一可识别对象的位置记录在存储器114中。之后，将所记录的位置发送至处理器116，处理器116生成在目标的图像中的唯一可识别对象的位置和对象容积内的唯一可识别对象的精确已知位置之间的线性或非线性数学关系或映射。这样的映射的示例为TSAI算法。R.Y.Tsai的用于3D机器视觉的有效且精确的相机校准技术（“An Efficient and AccurateCamera Calibration Technique for3D Machine Vision”），计算机视觉和模式识别的IEEE会议论文集，迈阿密海滩，佛罗里达，第364-374页，1986。
映射存储在存储器118中并且用于校正由图像捕获设备产生的原始图像，以在对象容积内产生对象的尺寸精确的图像。唯一可识别对象的使用大大地简化了产生创建尺寸精确的图像所需的数学映射的过程。
以上确定的映射用于处理眼睛内部的结构的原始图像，例如图7B的角膜和晶状体的表面和其他特征。如图7B所示的，图像捕获设备102形成眼睛120内的结构的原始图像，该原始图像位于对象容积122中并且通过照明眼睛120的纵向截面的光B的平面来照明。在图7B中，纵向截面垂直于页面的平面。被照明的纵向截面的原始图像受制于各种失真源，包括：图像捕获设备透镜的光轴和z轴之间的视角、检测器平面到透镜的光轴的角度，以及图像捕获设备透镜中的光学像差。因此，对象容积122的原始图像被存储在存储器124中并被发送至处理器126。利用来自存储器118的校正的数学映射，处理器126处理从存储器124接收的原始图像，以形成存储在存储器128中的眼睛的基本上尺寸精确的图像。
换句话说，除总体比例因子之外，在处理的图像上测量的结构或部分的结构之间的距离对应于在被照明的眼睛的纵向截面中的对应距离。
尺寸精确的图像允许将用于白内障治疗的激光能量的应用精确地使用于眼睛内部的特定区域，例如执行囊切开术或使晶状体碎成在白内障手术中更容易移除的碎片。
通过以上提及的对改进的照明和校准的讨论，可以预期，这种技术可应用于各种成像和光束布置系统。同时描述了这种系统的一个示例。例如，预期将改进的照明和校准应用于使用共焦系统的系统，在共焦系统中成像和光束传输系统是共轴的并且共享共同的焦点和光路。这种系统在眼睛的成像和激光照射传输之间将没有系统错误，例如飞秒脉冲。成像系统可基于Scheimpflug原理，以便捕获导致景深加强的从前角膜到后囊的单个图像。扫描激光是这样的：其提高了在重要界面处的对比度，并且因此允许前囊碎片和后囊碎片因本发明的更精确的光束布置而更接近后方。扫描光束相机和光学器件将用于提供较高的对比度噪声比。这种成像系统将使用根据射线追踪的三维重建，并因此避免了多个扫描的二维拼接。
根据以上描述，本领域的技术人员可容易地确定本发明的本质特征，并且不背离本发明的精神和范围，可做出对本发明的各种改变和/或修改以适应于各种用途和条件。
Claims (5)
1.一种用于加强眼睛结构的照明的方法，所述方法包括：
a.选择第一预先确定的照明激光扫描模式，其中所述模式是部分基于观察到的数据和数值模型，所述第一预先确定的照明激光扫描模式具有预先确定的速率和区域；
b.选择第二预先确定的照明激光扫描模式，其中所述模式是部分基于观察到的数据和数值模型，所述第二预先确定的照明激光扫描模式具有预先确定的速率和区域；其中，第二扫描速率或区域中的至少一个不同于第一扫描速率或区域；
c.将所述第一预先确定的照明激光扫描模式中的第一照明光束指向眼睛的角膜，由此创建第一照明图像；
d.将所述第二预先确定的照明激光扫描模式中的第二照明光束指向眼睛的天然晶状体，由此创建第二照明图像；
e.数字化捕获图像捕获设备的第一预先确定的部分上的所述第一照明图像；
f.数字化捕获所述图像捕获设备的第二预先确定的部分上的所述第二照明图像，其中第二预先确定的部分与第一预先确定的部分不同；
g.由此通过所述图像捕获设备创建被照明的眼睛结构的单个合成图像。
2.根据权利要求1所述的方法，其中对于角膜优化所述第一预先确定的照明激光扫描模式和/或对于天然晶状体优化所述第二预先确定的照明激光扫描模式。
3.一种用于提供眼睛结构的加强照明的系统，所述系统包括：
a.用于提供照明光束的照明光源；
b.与用于扫描所述照明光束的所述照明光源光学相关联的扫描器；
c.控制系统，所述控制系统与所述照明光源和扫描器相关联；所述控制系统包括：
d.第一预先确定的照明光扫描模式，其中所述模式是部分基于观察到的数据和数值模型，所述第一预先确定的照明光扫描模式具有预先确定的速率和区域；
e.第二预先确定的照明光扫描模式，其中所述模式是部分基于观察到的数据和数值模型，所述第二预先确定的照明光扫描模式具有预先确定的速率和区域；其中，第二扫描速率或区域中的至少一个不同于第一扫描速率或区域；
f.用于数字化捕获通过第一照明光束扫描模式产生的第一图像的装置；
g.用于数字化捕获通过第二照明光束扫描模式产生的第二图像的装置；以及
h.用于数字化捕获所述第一图像的所述装置和用于捕获所述第二图像的所述装置为相同装置的不同部分。
4.一种用于加强眼睛结构的照明的方法，所述方法包括：以第一预先确定的照明光束扫描模式在眼睛的角膜区域上扫描照明光束，其中所述第一预先确定的照明光束扫描模式是部分基于观察到的数据和数值模型，所述第一预先确定的照明光束扫描模式具有预先确定的第一扫描速率；以第二预先确定的照明光束扫描模式在眼睛的晶状体区域上扫描照明光束，其中所述第二预先确定的照明光束扫描模式是部分基于观察到的数据和数值模型，所述第二预先确定的照明光束扫描模式具有预先确定的第二扫描速率；其中所述第二扫描速率不同于所述第一扫描速率。
5.根据权利要求4所述的方法，其中所述角膜和所述晶状体的照明分别是最优的。
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| US10052020B2 (en) | 2018-08-21 |
| WO2012051490A1 (en) | 2012-04-19 |
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| US20220087526A1 (en) | 2022-03-24 |
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| US20160220113A1 (en) | 2016-08-04 |
| EP2627240A1 (en) | 2013-08-21 |
| US9271645B2 (en) | 2016-03-01 |
| CN106974614A (zh) | 2017-07-25 |
| US20120182522A1 (en) | 2012-07-19 |
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| US11019999B2 (en) | 2021-06-01 |
| CN103338692A (zh) | 2013-10-02 |
| US8801186B2 (en) | 2014-08-12 |
| US20180353068A1 (en) | 2018-12-13 |
| US20150022779A1 (en) | 2015-01-22 |
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