WO2023193316A1 - 一种基于菲涅尔透镜的内窥式光学相干层析探头 - Google Patents

一种基于菲涅尔透镜的内窥式光学相干层析探头 Download PDF

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WO2023193316A1
WO2023193316A1 PCT/CN2022/088757 CN2022088757W WO2023193316A1 WO 2023193316 A1 WO2023193316 A1 WO 2023193316A1 CN 2022088757 W CN2022088757 W CN 2022088757W WO 2023193316 A1 WO2023193316 A1 WO 2023193316A1
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fresnel lens
coherence tomography
self
optical coherence
lens
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PCT/CN2022/088757
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French (fr)
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卞海溢
陈新建
曹苏群
季仁东
姚华
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苏州比格威医疗科技有限公司
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00163—Optical arrangements
    • A61B1/00188—Optical arrangements with focusing or zooming features
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/07—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements using light-conductive means, e.g. optical fibres
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging

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  • the invention belongs to the field of optical coherence tomography (OCT, Optical coherence tomography), and specifically relates to an endoscopic optical coherence tomography probe based on a Fresnel lens.
  • OCT optical coherence tomography
  • Optical Coherence Tomography is a new biomedical imaging method that uses the low coherence of a broadband light source to perform high-resolution imaging. It has the advantages of high resolution, fast imaging speed, and non-invasive measurement. .
  • the longitudinal resolution and lateral resolution of OCT can reach ⁇ 1 ⁇ m.
  • the longitudinal resolution mainly depends on the coherence length of the light source, and the lateral resolution mainly depends on the numerical aperture of the focusing lens.
  • the larger the numerical aperture of the focusing lens the higher the lateral resolution of the OCT system, but the smaller the focal depth, the effective imaging range of the OCT system will be limited. Therefore, solving the contradictory relationship between focal depth and lateral resolution is crucial to improving the performance of the OCT system.
  • the present invention proposes an endoscopic optical coherence tomography probe based on a Fresnel lens.
  • An endoscopic optical coherence tomography probe based on a Fresnel lens including a single-mode fiber for light guide, a self-focusing lens for collimating the light emitted from the single-mode fiber, and a self-focusing lens for focusing Fresnel lenses that focus the collimated light and microprisms that turn the light path;
  • the focal length of the Fresnel lens is determined by the lateral resolution required by the OCT system;
  • x represents the lateral resolution
  • ⁇ represents the wavelength
  • D represents the spot diameter
  • f represents the focal length of the Fresnel lens.
  • the distance between the exit end of the single-mode optical fiber and the end face of the self-focusing lens is 0 mm.
  • the pitch of the self-focusing lens is 0.25P, and the numerical aperture is greater than 0.13.
  • microprism is an isosceles right-angle prism with a refractive index between 1.52-1.54.
  • the aperture of the Fresnel lens is determined by the size of the diffraction spot.
  • exit end of the single-mode fiber and one end face of the self-focusing lens are bonded with optical glue
  • one end face of the microprism is bonded with the other end face of the self-focusing lens
  • the other end face of the Fresnel lens and the microprism is bonded with optical glue.
  • One end face is bonded with optical glue.
  • the present invention has the following advantages:
  • this invention does not require phase stability, does not require mechanical scanning and uses the same optical path to achieve illumination and detection, which is conducive to the miniaturization design of the probe;
  • Fresnel lenses are suitable for injection molding processes and have the advantages of simple processing, low cost, and simple optical path adjustment;
  • the present invention does not require the splicing of multiple optical fibers, can avoid the influence of dispersion, polarization and other factors of different optical fibers on the interference signal, and can obtain a large working distance and achieve uniform distribution of axial light intensity. .
  • Figure 1 is a schematic diagram of the present invention
  • Figure 2 shows the corresponding focal length relationship diagram of the Fresnel lens when light of different wavelengths is normally incident
  • Figure 3 is a schematic diagram of the imaging results of a traditional optical coherence tomography system
  • Figure 4 is a schematic diagram of the imaging results of the optical coherence tomography system based on Fresnel lenses.
  • an endoscopic optical coherence tomography probe based on a Fresnel lens is an endoscopic probe that solves the contradiction between high resolution and large focal depth.
  • Its main structure includes: Light-guiding single-mode fiber 1, self-focusing lens for collimating the light emitted from the single-mode fiber 2, Fresnel lens 3 for optimizing axial light intensity and controlling light field distribution, and microprism 4 for turning the light path .
  • the single-mode optical fiber 1 in this embodiment mainly implements light guidance to avoid the influence of multi-mode optical fiber inter-mode dispersion and other factors on the interference signal.
  • the self-focusing lens 2 of this embodiment generates collimated light, and the divergence angle of the collimated light is affected by the pitch of the self-focusing lens 1 and the distance from the exit end of the optical fiber to the end face of the self-focusing lens.
  • the pitch of the self-focusing lens 2 used in this embodiment is 0.25P, and the numerical aperture is greater than 0.13.
  • the Fresnel lens 3 of this embodiment is mainly used to focus the light collimated by the self-focusing lens and regulate the axial light intensity to achieve uniform distribution of light intensity in the axial direction and simultaneously achieve high resolution and large focal depth. , to achieve the resolution required by the OCT system.
  • the focal length of the Fresnel lens 3 is determined by the lateral resolution required by the OCT system;
  • x represents the lateral resolution
  • ⁇ represents the wavelength
  • D represents the spot diameter
  • f represents the focal length of the Fresnel lens.
  • the aperture of the Fresnel lens 3 is determined by the size of the diffraction spot.
  • the focal length of the first-order diffracted light of the Fresnel lens is:
  • ⁇ d and f d are the design wavelength and focal length of the Fresnel lens
  • m is the band number of the Fresnel lens.
  • the focal length of the Fresnel lens is inversely proportional to the wavelength of the incident light, which means that when the incident light is polychromatic light, the focal depth of the focused beam is greatly expanded.
  • the design wavelength and focal length of the Fresnel lens are 1310nm and 30mm
  • the wavelength range of the incident light is 1310 ⁇ 50nm
  • the collimated light spot size is 4mm.
  • the focusing lens is a Fresnel lens
  • the focal length corresponding to each wavelength satisfies formula (2). After MATLAB simulation, the focal length distribution is shown in Figure 2.
  • the abscissa in Figure 2 represents the wavelength, and the ordinate represents the focal length; the incident light
  • the focal length range is 2.29mm.
  • the microprism 4 in this embodiment is an isosceles right-angle prism with a refractive index between 1.52 and 1.54, which enables full emission of light, avoids loss of light energy, and turns the optical path.
  • the optical coherence tomography probe based on the Fresnel lens proposed in this embodiment not only solves the contradiction between focal depth and resolution, but also optimizes the axial intensity uniformity of the outgoing beam.
  • the probe is produced by the following steps:
  • Step 1 Bond the single-mode fiber exit port and one end face of the self-focusing lens with optical glue; the distance from the single-mode fiber exit port to the end face of the self-focusing lens is 0 mm to achieve collimation of the fiber exit beam.
  • Step 2 Bond one end surface of the microprism and the other end surface of the self-focusing lens together with optical glue to achieve the turning of the optical path;
  • Step 3 Bond the other end surface of the microprism and the Fresnel lens together with optical glue to achieve spatial control of light.
  • the invention expands the focal depth of the optical coherence tomography system, optimizes the axial light intensity uniformity, and extends the working distance while maintaining the lateral resolution.
  • the present invention uses a Fresnel lens instead of a self-focusing lens to focus the light beam, solving the contradiction between high resolution and large focal depth. Compared with other methods, the present invention does not require mechanical scanning, allows for greater manufacturing errors, and reduces manufacturing costs. cost.
  • the third element of the sixth group of the 1951USAF resolution plate at different depths was imaged using a conventional optical coherence tomography system and a Fresnel lens-based optical coherence tomography system.
  • the central wavelength of the light source of the two systems is 830nm and the bandwidth is 50nm.
  • Only the focusing objective lens of the sample arm of the two systems is different.
  • the focusing lens of the sample arm of the traditional optical coherence tomography system is an ordinary objective lens with a focal length of 30mm.
  • the focusing objective lens of the sample arm of the optical coherence tomography system based on Fresnel lens is Fresnel.
  • the lens has a focal length of 30mm and a design wavelength of 830nm.
  • the imaging results of the traditional optical coherence tomography system are shown in Figure 3. Since the third element of the sixth group of the 1951USAF resolution plate cannot be seen at -500 and 500 in Figure 3, but can be seen at 400 and -400, so The effective imaging range is 800 ⁇ m.
  • the imaging results of the optical coherence tomography system based on the Fresnel lens are shown in Figure 4. Since the third element of the sixth group of the 1951USAF resolution plate can also be seen at -1000 and 1000 in Figure 4, the imaging is effective.
  • the range is 2000 ⁇ m, which is 2.5 times that of traditional optical coherence tomography systems.
  • the abscissas in Figures 3 and 4 both represent relative intensity, and the ordinates represent lateral positions.

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Abstract

一种基于菲涅尔透镜的内窥式光学相干层析探头，由用于导光的单模光纤(1)、用于准直单模光纤(1)出射光的自聚焦透镜(2)、用于优化轴向光强及调控光场分布的菲涅尔透镜（3）和用于转折光路的微棱镜（4）组成；在保持横向分辨率不变的情况下扩展了光学相干层析系统的焦深，优化了轴向光强均匀性，提高了系统的有效成像深度，并利用菲涅尔透镜代替自聚焦透镜实现光束的聚焦，解决高分辨率和大焦深的矛盾；不需要机械扫描，容许更大的制造误差，降低了制造成本。

Description

一种基于菲涅尔透镜的内窥式光学相干层析探头 技术领域
本发明属于光学相干层析成像(OCT，Optical coherence tomography)领域，具体涉及一种基于菲涅尔透镜的内窥式光学相干层析探头。
背景技术
光学相干层析术(Optical Coherence Tomography,OCT)是一种利用宽带光源的低相干性进行高分辨率成像的新型生物医学成像手段，它具有分辨率高、成像速度快、非侵入式测量的优点。目前OCT的纵向分辨率和横向分辨率能达到～1μm，纵向分辨率主要取决于光源的相干长度，横向分辨率主要取决于聚焦透镜的数值孔径。聚焦透镜的数值孔径越大，OCT系统的横向分辨率越高，但是焦深越小，OCT系统的有效成像范围将会受到限制。所以解决焦深与横向分辨率的矛盾关系对于改善OCT系统的性能至关重要。
为了实现大焦深高分辨率的改善型OCT系统，各OCT研究小组提出了多种方案，比如数字聚焦，动态聚焦和准光针(Optical needle)聚焦。但是上述方法有的需要相位稳定性，有的需要机械扫描，有的需要使用两条光路分别实现照明和探测。这些方法难以应用于小型化的探头中。微型轴锥镜、微型二元相位板和微透镜阵列也已用于探头焦深的扩展，但是这些元器件或者加工工艺复杂，或者光路调节比较困难。另一方面，基于多光纤组合或者阶跃折射率光纤技术的内窥探头也是解决大焦深和高分辨矛盾的一种方法，但是这些方法存在下列不足：1)对光纤的切割及熔接的精度存在很高的要求；2)焦深区域内的干涉相消现象导致出射光束的光强在轴向上分布不均匀，对整体成像效果产生了不利影响；3)多模光纤的使用使得模间色散及偏振对整体成像效果产生不利的影响。
发明内容
发明目的：为了解决焦深与横向分辨率的矛盾关系，以及为了改善OCT系统的性能，本发明提出了一种基于菲涅尔透镜的内窥式光学相干层析探头。
技术方案：一种基于菲涅尔透镜的内窥式光学相干层析探头，包括用于导光的单模光纤、用于准直单模光纤出射光的自聚焦透镜、用于对经自聚焦透镜准直的光进行聚焦的菲涅尔透镜和用于转折光路的微棱镜；
所述菲涅尔透镜的焦距由OCT系统所要求的横向分辨率所确定；
Figure PCTCN2022088757-appb-000001
式中，x表示横向分辨率，λ表示波长，D表示光斑直径，f表示菲涅尔透镜的焦距。
进一步的，单模光纤的出射端与自聚焦透镜的端面之间的距离为0mm。
进一步的，所述的自聚焦透镜的节距为0.25P，数值孔径大于0.13。
进一步的，所述的微棱镜为等腰直角棱镜，折射率在1.52-1.54之间。
进一步的，所述的菲涅尔透镜的孔径由衍射光斑的大小确定。
进一步的，单模光纤的出射端与自聚焦透镜的一端面通过光学胶水粘合，微棱镜的一端面与自聚焦透镜的另一端面通过光学胶水粘合，菲涅尔透镜与微棱镜的另一端面通过光学胶水粘合。
有益效果：本发明具有以下优点：
1、与数字聚焦、动态聚焦和准光针聚焦相比，本发明不要求相位稳定性、不需要机械扫描并且使用同一条光路实现照明和探测，利于探头的小型化设计；
2、与基于微型轴锥镜、微型二元相位板的方法相比，菲涅尔透镜适用于注塑工艺，具有加工简单、成本较低、光路调节简单等优点；
3、与多光纤方法相比，本发明无需多根光纤的熔接，可以避免不同光纤的色散、偏振等因素对干涉信号的影响，并且可以获得大的工作距，实现轴向光强的均匀分布。
附图说明：
图1为本发明示意图；
图2为不同波长光正入射时，菲涅尔透镜相应的焦距关系图；
图3为传统光学相干层析系统成像结果示意图；
图4为基于菲涅尔透镜的光学相干层析系统的成像结果示意图。
具体实施方式
为使本发明的目的、技术方案和优点更加清楚，下面结合具体实施方式，进一步阐明本发明。
如图1所示出的一种基于菲涅尔透镜的内窥式光学相干层析探头，该探头为一种解决高分辨率与大焦深矛盾的内窥探头，其主要结构包括：用于导光的单模光纤1、用于准直单模光纤出射光的自聚焦透镜2、用于优化轴向光强及调控光场分布的菲涅尔透镜3和用于转折光路的微棱镜4。
本实施例的单模光纤1主要实现导光，避免多模光纤模间色散等因素对干涉信号的影响。
本实施例的自聚焦透镜2产生准直光，该准直光的发散角受自聚焦透镜1的节距和光纤出射端到自聚焦透镜端面距离的影响。本实施例中采用的自聚焦透镜2的节距为 0.25P，数值孔径大于0.13。
本实施例的菲涅尔透镜3主要用于对经自聚焦透镜准直的光进行聚焦，并对轴向光强进行调控，实现光强在轴向上均匀分布和同时实现高分辨大焦深，实现OCT系统所要求的分辨率。其中，菲涅尔透镜3的焦距由OCT系统所要求的横向分辨率所确定；
Figure PCTCN2022088757-appb-000002
式中，x表示横向分辨率，λ表示波长，D表示光斑直径，f表示菲涅尔透镜的焦距。
菲涅尔透镜3的孔径由衍射光斑的大小确定。
当波长为λ的准直光沿光轴垂直入射菲涅尔透镜时，菲涅尔透镜的一级衍射光的焦距为：
Figure PCTCN2022088757-appb-000003
其中，λ d和f d为菲涅尔透镜的设计波长及焦距，m为菲涅尔透镜的波带数。
当菲涅尔透镜入射光的波长与设计波长相差不大时，上式可以改写为：
Figure PCTCN2022088757-appb-000004
由此可以看到，菲涅尔透镜的焦距与入射光的波长成反比，这就意味着，当入射光为复色光时，聚焦光束的焦深得到极大的扩展。譬如，菲涅尔透镜的设计波长和焦距为1310nm和30mm，入射光的波长范围为1310±50nm，准直光光斑大小为4mm。当聚焦透镜为普通透镜时，聚焦光束的焦深为b＝8λf 2/(πD 2)＝187μm。当聚焦透镜为菲涅尔透镜时，各波长所对应的焦距满足公式(2)，经MATLAB仿真，焦距分布如图2所示，图2中的横坐标表示波长，纵坐标表示焦距；入射光的焦距范围为2.29mm，此时菲涅尔透镜的焦深为2.29+0.187＝2.477mm，约为普通透镜焦深的13倍。
本实施例的微棱镜4为等腰直角棱镜，折射率在1.52-1.54之间，实现光的全发射，避免光能量损失，从而转折光路。
本实施例提出的基于菲涅尔透镜的光学相干层析探头在解决焦深与分辨率矛盾的同时，优化了出射光束的轴向光强均匀性，该探头由以下步骤制作得到：
步骤1：将单模光纤出射端口与自聚焦透镜的一端面通过光学胶水粘合；其中，单模光纤出射端口到自聚焦透镜的端面的距离为0mm，实现光纤出射光束的准直。
步骤2：将微棱镜的一端面与自聚焦透镜的另一端面通过光学胶水粘合在一起，实现光路的转折；
步骤3：将微棱镜的另一端面与菲涅尔透镜通过光学胶水粘合在一起，实现对光的空间调控。
本发明在保持横向分辨率不变的情况下扩展了光学相干层析系统的焦深，优化了轴向光强均匀性，并且延长了工作距。本发明利用菲涅尔透镜代替自聚焦透镜实现光束的聚焦，解决高分辨率和大焦深的矛盾；相比于其它方法，本发明不需要机械扫描，容许更大的制造误差，降低了制造成本。
实施案例：
利用传统的光学相干层析系统和基于菲涅尔透镜的光学相干层析系统，对不同深度处的1951USAF分辨率板的第六组第三个元素进行了成像。两系统的光源中心波长为830nm，带宽为50nm。两系统仅样品臂的聚焦物镜不一样，传统光学相干层析系统样品臂的聚焦透镜为普通物镜，焦距为30mm，基于菲涅尔透镜的光学相干层析系统样品臂的聚焦物镜为菲涅尔透镜，焦距为30mm，设计波长为830nm。传统光学相干层析系统成像结果如图3所示，由于图3中-500和500处不能看到1951USAF分辨率板的第六组第三个元素，而400和-400处能看到，所以有效成像范围为800μm。基于菲涅尔透镜的光学相干层析系统的成像结果如图4所示，由于图4中-1000和1000处都还能看到1951USAF分辨率板的第六组第三个元素，所以有效成像范围为2000μm，是传统光学相干层析系统的2.5倍。图3和图4中的横坐标均表示相对强度，纵坐标表示横向位置。

Claims (6)

  1. 一种基于菲涅尔透镜的内窥式光学相干层析探头，其特征在于：包括用于导光的单模光纤、用于准直单模光纤出射光的自聚焦透镜、用于对经自聚焦透镜准直的光进行聚焦的菲涅尔透镜和用于转折光路的微棱镜；
    所述菲涅尔透镜的焦距由OCT系统所要求的横向分辨率所确定；
    Figure PCTCN2022088757-appb-100001
    式中，x表示横向分辨率，λ表示波长，D表示光斑直径，f表示菲涅尔透镜的焦距。
  2. 根据权利要求1所述的一种基于菲涅尔透镜的内窥式光学相干层析探头，其特征在于：单模光纤的出射端与自聚焦透镜的端面之间的距离为0mm。
  3. 根据权利要求1所述的一种基于菲涅尔透镜的内窥式光学相干层析探头，其特征在于：所述的自聚焦透镜的节距为0.25P，数值孔径大于0.13。
  4. 根据权利要求1所述的一种基于菲涅尔透镜的内窥式光学相干层析探头，其特征在于：所述的微棱镜为等腰直角棱镜，折射率在1.52-1.54之间。
  5. 根据权利要求1所述的一种基于菲涅尔透镜的内窥式光学相干层析探头，其特征在于：所述的菲涅尔透镜的孔径由衍射光斑的大小确定。
  6. 根据权利要求1所述的一种基于菲涅尔透镜的内窥式光学相干层析探头，其特征在于：单模光纤的出射端与自聚焦透镜的一端面通过光学胶水粘合，微棱镜的一端面与自聚焦透镜的另一端面通过光学胶水粘合，菲涅尔透镜与微棱镜的另一端面通过光学胶水粘合。
PCT/CN2022/088757 2022-04-07 2022-04-24 一种基于菲涅尔透镜的内窥式光学相干层析探头 WO2023193316A1 (zh)

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