CN110996792A - 用于表征渗出物的红外耳镜 - Google Patents
用于表征渗出物的红外耳镜 Download PDFInfo
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Abstract
耳镜使用吸收范围和邻近波长范围内的光能的差分反射响应来确定水的存在(其中所述波长是水吸收波长和邻近的非吸收激发波长)。在本发明的另一示例中,耳镜利用OCT结合细菌和水的吸收和非吸收范围。
Description
技术领域
本发明涉及用于表征耳中流体的耳镜。具体地,本发明涉及使用流体和细菌光学性质的测定来检测与膜相对的流体中的细菌,所述测定使用一个或多个双波长光源和在特定时间间隔期间仅响应于特定源的检测器。
技术背景
急性中耳炎(AOM)是一种常见的内耳疾病,涉及组织炎症和撞击鼓膜的流体压力。急性中耳炎可能由病毒感染引起,由病毒感染引起的中耳炎通常无需治疗即可消退,或者其可能由细菌感染引起,由细菌感染引起的中耳炎可能发展并导致听力损失或其他有害和不可逆的影响。遗憾的是,难以使用目前可用的诊断装置来区分病毒感染或细菌感染,并且针对两种潜在感染的治疗方法有很大的不同。对于细菌感染,抗生素是首选的治疗方法,而对于病毒感染,感染往往会自行消退,并且抗生素不仅无效,而且还可能导致抗生素耐药性,这会降低其治疗后续细菌感染的有效性。准确诊断急性中耳炎很重要,因为AOM可能是慢性渗出性中耳炎(COME)的前兆,为此,指示手术引流渗出物并在鼓膜中插入导管。
用于内耳感染的确定性诊断工具是鼓膜切开术,这是一种侵入性手术,涉及切入鼓膜,抽出流体,以及在显微镜下检查渗出液以鉴别渗出物中的感染因子。由于该手术造成的并发症,因此其仅用于严重的情况。这对于医疗从业者来说是一个两难的问题,因为针对病毒感染的抗生素处方被认为会导致细菌中抗生素耐药性的进化,而这可能在以后的余生中导致更严重的后果,并且由于用抗生素治疗病毒感染因子是无效的而并无有效的治疗结果。需要用于诊断急性中耳炎的改进的诊断工具。
发明目的
本发明的第一目的是用于测定疑似患有急性中耳炎的个体中存在的感染因子的装置,所述装置具有多个光源,每个光源在独特的波长或波长范围内操作,每个光源在特定波长范围内操作一段时间间隔,该时间间隔不包括当其他波长的光源操作时的时间间隔,所述装置具有用于测定反射光能的检测器,所述检测器测定在第一波长检测到的光能与在第二波长或第三波长检测到的光能的比率,此后形成比率度量值作为估计细菌负载的指标。
本发明的第二目的是用于确定细菌浓度的方法,通过以独占的时间间隔使用第一波长和第二波长相继照射膜的第一表面,在每个相关的间隔期间测定从所述膜的相对表面反射的光能,形成来自相关联的照射事件的第一波长与第二波长检测器响应的比率,每个照射事件处于独特的波长或波长范围内,其中照射波长中的至少一个对应于细菌吸收带,并且照射波长中的另一个是对于细菌菌落或一组分散细菌具有非吸收或非散射特性的波长。
本发明的第三目的是提供用于插入耳道的窥器尖端(speculumtip),一对或多对光源,每个光源通过所述窥器尖端耦合到光输出,每个光源在独特的波长或波长范围内操作,每对光源生成选定用于水样流体或细菌的反射衰减的第一波长的第一光输出,并且还生成选定用于水样流体或细菌的比较性非衰减反射的第二波长,所述第二波长在所述第一波长附近操作,其中从所述鼓膜反射的光能被引导到检测器,所述检测器响应于反射到窥器尖端中的光能的每个光源波长,所述检测器耦合到控制器,所述控制器测定来自所述第一波长和所述第二波长的检测器响应的比率,从而根据与每对发射器相关联的检测器响应比率形成指示存在细菌和/或水样流体的度量(metric)。
发明内容
在本发明的第一示例中,控制器启动第一多个光源中的一个,或者替代地,具有用于细菌吸收的波长的单个第一光源,以及第二多个光源中的一个,或者替代地,在对细菌非吸收的邻近波长下操作的第二光源,在吸收水样流体的波长下操作的可选的第三源,以及在邻近对水样流体非吸收的波长下操作的可选的第四源,每个光源或源可选地以交替的或独占的时间间隔操作。每个波长源通过插入到待检查的受试者的耳道中的锥形窥器光学耦合。来自每个光源的光束可以作为定向光束承载,或者光束可以在围绕窥器的环形光导或光管中承载,来自照射配置的光能撞击到鼓膜的前(远侧)表面上,鼓膜在待表征的鼓膜的相对(近侧)表面上具有细菌薄膜或细菌液。反射的光能进入到窥器尖端中耦合到具有从第一源反射的能量的第一波长响应和从第二波长源反射的能量的第二波长响应的单个检测器,或耦合到在相应光源的每个光波长范围内操作的单独的检测器。在相关的间隔上使第一波长响应和第二波长响应平均,使相应光源能够形成每个第一波长响应和每个第二波长响应的平均测量,并且由这两个测量形成比率。第一波长在待表征的细菌的波长的吸收或散射范围内,并且第二波长邻近于第一波长且在细菌的散射或吸收波长之外。将第一波长与第二波长的响应比率应用于多项式或查找表,该多项式或查找表根据第一波长的功率与第二波长的功率的比率提供细菌负载的估计,当不存在吸收性或散射性流体时,例如通过使用单独补偿散射的存储的波长尺度系数来可选地补偿波长特定衰减。也可以形成针对水的与分别在邻近的吸收和非吸收波长中的第三波长源和第四波长源相关的检测器响应的类似比率。
在在测量区域上提供轴向范围特异性的本发明的第二示例中,第一波长和第二波长源被选择为细菌的吸收响应和非吸收响应的邻近波长,并且还具有较短的相干长度,其中在将光能分成测量路径和参考路径之后,每个源的光输出被引导至待表征的鼓膜的近侧表面和中耳。测量路径将光能引导至长度与参考路径相等的待表征流体,将来自测量路径和反射路径的反射光能组合,从而在较窄深度范围上形成相干响应,该较窄深度范围被设置为包括待表征的鼓膜的近侧表面和中耳区域。在独占的时间间隔期间启用第一波长源和第二波长源,并且将组合的测量路径和参考路径光能引导至相关波长的检测器响应。第一波长检测器响应和第二波长检测器响应形成用作细菌负载度量的比率,该比率度量充当用于检测细菌存在的指标。如第一示例同样将第三波长和第四波长选择为邻近的但对水样流体是相对散射和非散射的,并且用于形成充当用于在所选择的轴向范围中检测水样流体的指标的第二比率。
对于第一示例或第二示例,通过将第二度量(存在水样流体)与第一度量(存在细菌)组合,可以确定急性中耳炎的范围的更完整的调查。
附图说明
图1示出了用于进行鼓膜测定的红外光谱系统的框图。
图2示出了相对于鼓膜的窥器尖端和光学部件的详细视图。
图3示出了来自鼓膜的散射IR光谱响应对波长的图。
图4示出了用于测定来自第一光源和第二光源的反射光能的波形图。
图5示出了用于双波长测量的OCT测量系统的框图。
图6A和图6B示出了多波长检测器的框图。
图7A、图7B、图7C、图7D、图7E和图7F示出了正常鼓膜的波形图。
图8A、图8B、图8C、图8D、图8E和图8F示出了鼓膜中病毒渗出物的波形图。
图9A、图9B、图9C、图9D、图9E和图9F示出了鼓膜中细菌渗出物的波形图。
图10示出了用于双波长纤维内双光谱的基于光纤的OCT系统的框图。
具体实施方式
图1示出了带有图2中的窥器尖端的展开视图的红外(IR)光谱系统的框图。控制器134耦合到检测器响应处理器130和双源控制器132。在交替间隔期间,双源控制器132启用并向第一波长λ1的第一光源(未示出)和第二波长λ2的第二光源(未示出)提供功率。来自源的光能被引导通过窥器尖端102并到达待表征的鼓膜120的前(远侧)表面上,其中窥器尖端120使通过除首先从鼓膜120反射的路径之外的路径从窥器尖端120内部到检测器106的反射光能最小化。反射的光能由光学检测器106感测并被提供给图像处理器130,图像处理器130将第一波长的反射光能与第二波长的反射光能进行比较,并形成度量,如在检测器处测量的每个波长的反射光功率的比率波长度量可以用于估计在鼓膜120的相对(近侧)表面上的内耳流体中存在细菌或细菌负载的可能性。
图2示出了IR窥器尖端102相对于示例实施方式的其他元件的示例详细视图。对于细菌测定,第一波长λ1和邻近的第二波长λ2光能212可以以任何已知的方式耦合到窥器尖端102,窥器尖端102随后耦合到环形光管,诸如用围绕窥器尖端102的圆周定位的多个光纤,从而将光能200耦合到鼓膜120和可能在鼓膜120的近侧的流体204,但是直到从鼓膜120和可能与面向窥器尖端102的鼓膜120远侧表面相对的任何流体204反射之后,才直接耦合到检测器106。增加从鼓膜反射以外的源排除光能的结构可能是额外有利的。包括来自鼓膜120和可能存在的任何流体204的响应的反射光能被透镜206聚焦到双程波长检测器106中。在一个示例实施方式中,窥器尖端212的内表面是反射性的,且不存在透镜或聚焦机构206以将未聚焦的反射光引导到检测器106。在不存在透镜206的情况下,检测器106响应于直接从鼓膜行进的光能以及从窥器尖端212的内部的反射表面反射的光能。在该实施方式中,可以使用激光指示器(未示出)或其他光学观察系统来完成选择区域的鉴别。在测定间隔期间,可以可选地禁用激光指示器发射器,以避免由激光指示器的散射反射造成不必要的检测器响应。类似的第三波长和第四波长组可以用于测定吸收和非吸收波长中邻近波长的水含量。在另一示例性实施方式中,透镜系统206与检测器106一起存在,检测器106具有较小范围和相对较小数目的像素并且定位在焦点207处,或者替代地,其可以放置在如图2所示的具有较大数目的像素如50×50或100×100的图像平面处,或者具有由像素间距和在图像或焦平面处的窥器102的可用内径所控制的分辨率。
图3示出了在有和没有细菌/水样流体的情况下从鼓膜反射的能量的光谱响应。反射特性具有与瑞利散射相关的特征吸收衰减,由此较长波长比较短波长具有更少的散射相互作用和更低的吸收。吸收图302通常与波长增长成反比,然而,细菌具有与相关波长如范围309下的光能相互作用的物理长度,与响应图302中的非细菌流体相比,范围309在针对细菌流体的图的区域309中对各种细菌具有更大吸收312、314。在范围309内具有吸收性的特定细菌包括流感嗜血菌(Haemophilus Influenzae)、粘膜炎莫拉菌(MoraxellaCatarrhalis)和肺炎链球菌(Streptococcus Pneumoniae)。类似地,发现在不同波长范围内与水吸收相关的升高的吸收峰306。在本发明中,检测器响应于在诸如1050nm至1150nm的第一波长范围309中的反射光能,这提供了由于细菌散射而在检测器处的减小的响应,并且检测器使用在诸如1000nm的邻近波长322下或在400至800nm的可见光范围308内的吸收,范围308也可以用作第五波长λ5,用于指向和照射用于形成λ1和λ2或λ3和λ4度量比率的检查区域。在该情况下,λ5可以在可见光范围或2D检测器106的检测波长范围内,其中λ5源具有较窄色散激光器(未示出),用于照射检查区域并且指示界标区域,如用于定位测量区域的鼓膜的“光锥”。
在一说明性示例中,图3 326示出了当存在细菌时(区域309)与未受细菌存在影响的第二波长322相比具有增大吸收的第一波长,并且当存在水样流体时与邻近水样流体的吸收波长的第四波长324相比第三波长326具有更大的吸收。这些示例是为了说明的目的而给出的,用于细菌或水吸收的波长可能与图3的示例中所示的波长不同。在本说明书的上下文中,波长特定吸收也可以称为散射或反射衰减。在本发明的一个示例中,在细菌存在下可操作用于增大吸收或散射的第一波长在1050nm至1150nm的范围内,并且邻近波长是在1050nm以下或在1150nm以上的波长。在本发明的另一示例中,在水样流体存在下可操作用于增大吸收或散射的第三波长在1450nm至1600nm的范围310内,并且邻近于第三波长的第四波长在1450nm以下或在1600nm以上。
图4示出了用于图1和图2的装置的操作的波形图,该装置使用诸如λ1和λ2的两个光源,尽管可以以任何顺序完成四个波长的变换(commutation)(也称为时间复用)。在间隔408、416和424期间,第一波长λ1光源402被变换为接通,并且当第二波长λ2光源被启用时,在排他的间隔412、420期间第一波长λ1光源402被变换为断开。中间间隙410、414、418、422可以用于检测器处的环境光校正,其可以用于估计环境光和检测器偏移值,并且此后在λ1的间隔408、416、424和λ2的间隔412和420期间将该偏移值从检测器响应中减去。检测器响应406包括检测器噪声,可以使其在第一波长λ1的测量间隔408、416、424上或第二波长λ2的测量间隔412、420上平均。在从图4所示的一个示例扩展的本发明的一个示例中,λ1是增大的细菌吸收的波长,λ2是在细菌吸收波长λ1之外的附近参考波长,λ3是水吸收的波长,λ4是接近λ3但不受水吸收影响的波长,并且λ5是用于可视化的光波长,在如图4的波形402和404所示的独占的间隔期间,将每个波长λ1和λ2变换为接通以形成细菌度量可选地,在此之后,在独占的间隔402和404期间将每个波长λ3和λ4变换以形成流体度量然后,可以将每个相应的度量标准与每个度量标准的阈值进行比较,以得出液体或细菌存在的估计可能性。在本发明的一个示例中,可以针对波长特定衰减或散射(在不存在水样流体或细菌的情况下)校正相应的细菌或水流体检测器波长响应,使得当分别不存在细菌或水样流体时,每对波长(病菌特定的和邻近的)提供统一度量比率
图5示出了光学相干断层扫描(OCT)表征系统的框图,其具有较窄的轴向特异性深度的优点,这允许被测量的响应被限制到特定的轴向深度和深度范围,如鼓膜的近侧表面和中耳区域。具有多个波长范围输出的低相干源514包括沿路径518被引导至第一分路器516并此后被引导至第二分路器526的第一波长λl和第二波长λ2。此后,一半的光能被引导至测量光路528,并且一半被引导至反射镜512和可移动反射器508,其将参考路径的长度调整为与包括鼓膜的近侧表面和中耳区域的测量路径的长度相等。将从反射器508返回和从鼓膜532返回的光能在第二分路器526处组合,并且相加的光能继续到达第一分路器516,并且此后到达反射镜524和检测器520。在参考光路(从分路器526到反射器508的光学距离)与测量光路(从第二分路器526到鼓膜532)的长度完全相同的情况下,相干相加的参考光能和反射光能被依次引导至第二分路器526、第一分路器516、反射镜524和检测器520。源514的较短相干长度提供了深度特异性,这允许测定细菌响应,该测定通常具有小于鼓膜532的近侧深度中的光波长的特异性。示意性图5仅用于说明而示出,可以使用光学反射镜和分路器的其他配置。
图6A示出了多波长检测器520A的第一示例,其中第一波长λl检测器602响应于λl,并且对于与第二检测器604相关联的第二波长λ2是透明的。通过使用光学透明粘合剂将第一检测器602和第二检测器604粘结在一起,面向前的检测器602对于其后面的检测器604的光能λ2是透明的。检测器602/604的该构造可能需要对各种光源的进行变换,如图4中所述,特别是在检测器之一对用于诸如水与细菌吸收的不同测量的邻近波长光能具有带外响应的情况下。
图6B示出了多波长检测器520A的另一实施方式,其利用衍射光栅608将各个波长λl、λ2、λ3、λ4等分离到检测器606,以便对每个波长进行空间隔离。因为各个波长是空间分离的,所以检测器的该配置可以允许四个光源连续地和同时地操作,因为它们由于在图6A的检测器配置中不存在的波长的空间分离而本质上无干扰。可以在启用光源之前或之后进行暗电流检测器响应(在没有光能的情况下用于建立基线响应水平的检测器响应,当存在光能时从读数中减去该检测器响应)。
图7A、图7B、图7C、图7D、图7E和图7F示出了位置驱动器701和703的相关波形,它们调制了图5的反射器508的轴向位置,其中位置“0”对应于图5的位置536b,位置“-0.5”指示位置536a,“+0.5”指示位置536c,并且“+1.0”指示位置536d。
对于图3的衰减图,并在最大示例性病毒衰减波长1100nm处使用λ1,并在示例性邻近波长1000nm处使用λ2,并在示例水吸收波长1500nm处使用λ3,并在水吸收波长之外的示例性附近波长1400nm处使用λ4,可以将λ1与λ2的相对响应以及λ3与λ4的相对响应进行比较,以确定临床感兴趣的三个条件:不存在水样流体、存在不含细菌的渗出液以及存在含有细菌的渗出液,如患有耳部不适的受试者所需要的。设备和方法从而提供了用于病毒感染与细菌感染的诊断工具,以及确定在鼓膜近侧没有流体存在。
图7A和图7D是图5的反射器508的轴向位置图,图7B和图7C分别示出了对于细菌是差分的λ1和λ2响应,并且图7E和图7F分别示出了对于水样流体的存在是差分的λ3和λ4响应。波形702、740、703和741示出了相等振幅检测器响应714和750,其中在鼓膜近侧不存在流体。响应706、744、718和754是由于耳垢、耳囊或鼓膜远侧的其他微小结构的斑点引起的最小的相干反射,并且响应712、713、722和758是分别在鼓膜处的λ1至λ4的相应检测器响应。在靠近鼓膜的位置+0.5处响应708、748、721和757的较短持续时间也指示只有鼓膜正在提供返回信号,并且仅在鼓膜的相干反射的较短持续时间内。由于存在特定于波长的最小差分衰减,因此响应振幅714、750、724和756均为等效振幅。
图8A和图8D类似地分别示出了如图7A和图7D所述对应于鼓膜相干区域的反射器位置801和803的图。图8B和图8C的示出出了来自鼓膜近侧的病毒(水样)流体的OCT响应。如前所述,鼓膜远侧的响应806、844、818和854最小。鼓膜响应和近侧响应812、841、822和858具有与鼓膜近侧流体边界相关联的延长的响应持续时间,并且与狭窄的鼓膜检测器响应诸如图7的712相比,包括更长的响应时间范围808和848,这与来自邻近鼓膜的流体的空间扩展响应有关。峰值振幅检测器响应814(λ1)和850(λ2)在振幅上相似,而峰值响应824(λ3)与856(λ4)相比有所减小,这是因为λ3与λ4相比的水差分吸收。
图9A和图9D示出了反射器位置图,图9B、图9C、图9E和图9F是对鼓膜近侧细菌渗出物的响应。与在λ2处对细菌没有吸收的检测器振幅响应947相比,OCT检测器响应912对λ1的振幅914减小。如前所述,由于可能邻近于鼓膜的细菌浓度,因此OCT响应908和948的范围延长。图903和941中示出了λ3与λ4相比的水衰减,与在更大的振幅956下的图958相比,响应922在振幅924处衰减。
如先前的响应图中所述,反射信号λ1/λ2的比率可用于估计细菌浓度,并且反射信号λ3/λ4的比率可用于估计邻近于鼓膜的液体的存在,并且该比率可以补偿来自每对波长的较短波长(具有更多的瑞利散射)的较低振幅响应,使得在每个相应比率中不存在细菌或水样流体的情况下将比率归一化为1。
图10示出了用于执行OCT以形成前述差分测量的光纤架构。低相干源1002以变换序列(用于图6A的检测器1022,或同时用于图6B的检测器)生成被施加到第一分路器1006的λl、λ2、λ3、λ4,低相干源耦合到光纤1008并耦合到第二分路器1010,光源功率的一半此后被引导到光纤1012和透镜1013,其引导光束通过窥器尖端(未示出)到达鼓膜1051,来自鼓膜和邻近结构的反射沿着L测量路径被引导返回透镜1013、光纤1012,并返回第二分路器1010。从源1002通过分路器1004行进到第二分路器1010的功率的另一半被引导到具有终止于抛光纤尾端1019的长度为L参考的参考路径1017,其在反向传播方向上反射光能并返回第二分路器1010。参考路径长度L参考等于从第二分路器1010到鼓膜1050的总测量长度。通过使用PZT调制器1014调节L参考,该PZT调制器1014通过纵向拉伸光纤来改变光纤的长度,可以围绕鼓膜轴向地调制光学相干的区域。
以上是本发明优选实施方式的描述。应理解,可以进行各种替换而不限制本发明的范围。例如,对于细菌吸收或水吸收,除指定的那些波长之外,其他波长可能是优选的。
Claims (19)
1.一种用于表征邻近于鼓膜的液体的装置,所述液体为水样流体或细菌,所述装置包括:
窥器尖端,所述窥器尖端用于插入耳道;
一对或多对光源,其中一对光源中的每个光源通过所述窥器尖端耦合到一光输出,一对光源中的每个光源在独特的波长或波长范围操作,每对光源生成第一波长的第一光输出,该第一波长选定用于水样流体或细菌的反射衰减,并且每对光源生成还生成第二波长,该第二波长选定用于水样流体或细菌的比较性非衰减反射,所述第二波长在所述第一波长附近操作;
检测器,所述检测器响应于反射到所述窥器尖端中的光能的每个光源波长;
控制器,所述控制器测定来自每个所述光源对的所述第一波长和所述第二波长的检测器响应的比率;
所述控制器根据与每个光源波长对的所述检测器响应相关联的检测器比率来形成指示存在细菌或水样流体的度量。
2.如权利要求1所述的装置,其中所述光学检测器包括响应于第一波长且对第二波长透明的第一检测器,所述第一检测器位于响应于第二波长的第二检测器的前部。
3.如权利要求1所述的装置,其中所述光学检测器包括用于分离波长的衍射光栅,所述波长被施加到第一检测器,该第一检测器被设置为边缘邻近于第二检测器。
4.如权利要求1所述的装置,其中所述第一波长在范围1050nm至1150nm内,并且所述第二波长在1050nm以下。
5.如权利要求2所述的装置,其中对于每对光源,所述光源第一波长和所述光源第二波长以独占的时间间隔操作。
6.如权利要求3所述的装置,其中对于每对光源,所述光源第一波长和所述光源第二波长同时地操作。
7.如权利要求1所述的装置,其中对于每对光源,所述光源第一波长和所述光源第二波长通过由所述窥器尖端形成的环形光导耦合。
8.如权利要求1所述的装置,其中使用一个或多个透镜将反射到所述窥器尖端中的光能聚焦到所述检测器上。
9.如权利要求1所述的装置,其中使用所述窥器尖端内部的反射性涂层将反射到所述窥器尖端中的光能引导到所述检测器。
10.如权利要求1所述的装置,其中对于每对光波长,对于每个所述光源对,根据反射到所述检测器的所述第一波长的光能与反射到所述检测器的所述第二波长的光能的比率来形成渗出物度量。
11.一种用于测定邻近于膜的细菌或水样流体的装置,所述装置包括:
窥器尖端,用于插入受试者耳道;
多个低相干光源,每个所述光源在一独特的波长下操作,所述多个光源包括对感兴趣的细菌有吸收性的第一波长、对感兴趣的细菌有相对较小吸收性的第二波长、对水样流体有吸收性的第三波长和对水样流体无吸收性的第四波长;
所述多个低相干光源通过第一分路器耦合,所述第一分路器具有被引导至第二分光器的输出,所述第二分光器将入射的光能分成参考光路和测量光路;
所述参考光路耦合到一反射器,所述反射器具有与感兴趣的测量路径长度相等的路径长度;
所述测量光路被引导至鼓膜以供表征;
来自所述测量光路和所述参考光路的反射光能在所述第二分路器处组合,所述光能随后被引导至所述第一分路器和检测器;
所述检测器基于所述第一波长的反射光能与所述第二波长的反射光能的比率来形成第一度量;
所述检测器基于所述第三波长的反射光能与所述第四波长的反射光能的比率来形成第二度量。
12.如权利要求11所述的装置,其中所述光学检测器包括响应于第一波长且对第二波长透明的第一检测器,所述第一检测器位于响应于第二波长的第二检测器的前部。
13.如权利要求11所述的装置,其中所述光学检测器包括用于分离波长的衍射光栅,所述波长被施加到第一检测器,该第一检测器被设置为边缘邻近于第二检测器。
14.如权利要求11所述的装置,其中所述第一波长在范围1050nm至1150nm内,并且所述第二波长在1050nm以下。
15.如权利要求12所述的装置,其中所述光源第一波长和所述光源第二波长以独占的时间间隔操作。
16.如权利要求13所述的装置,其中所述光源第一波长和所述光源第二波长同时地操作。
17.如权利要求1所述的装置,其中所述光源第一波长与所述光源第二波长通过由所述窥器尖端的壳厚度形成的环形光导耦合。
18.如权利要求11所述的装置,其中由光纤形成所述第一分路器、所述第二分路器、所述参考光路和部分所述测量光路。
19.如权利要求11所述的装置,其中使用反射镜和透镜形成所述第一分路器、所述第二分路器、所述参考光路和所述光路。
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CA3065926A1 (en) | 2018-12-06 |
US20190200873A1 (en) | 2019-07-04 |
US11317811B2 (en) | 2022-05-03 |
US10357161B1 (en) | 2019-07-23 |
KR20200017436A (ko) | 2020-02-18 |
EP3629926A4 (en) | 2020-10-28 |
JP2020522320A (ja) | 2020-07-30 |
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