技术领域technical field
本实用新型涉及光学医疗领域，特别涉及一种具有近视眼扫描模块的光学相干断层扫描仪(OCT System，Optical Coherence TomographySystem)。The utility model relates to the field of optical medical treatment, in particular to an optical coherence tomography scanner (OCT System, Optical Coherence Tomography System) with a myopia scanning module.
背景技术Background technique
光学相干断层扫描是一种干涉测量方法，用于获取被扫描样品的散射特性。光学相干断层扫描仪可以分为时域光学相干断层扫描仪(TD-OCT)和频域光学相干断层扫描仪(FD-OCT)两种。与时域光学相干断层扫描技术相比，频域光学相干断层扫描技术在速度和信噪比方面具有明显的优势。频域光学相干断层扫描的光谱信息鉴别通常通过以下方式实现：在谱域光学相干断层扫描(SD-OCT)的情况下，可以利用探测臂中的分光计进行分光；在扫频(波长扫描)光学相干断层扫描(SS-OCT)的情况下，可以通过快速地变换激光光源的频率来获得光谱信息。Optical coherence tomography is an interferometry method used to obtain the scattering properties of a sample being scanned. Optical coherence tomography can be divided into time domain optical coherence tomography (TD-OCT) and frequency domain optical coherence tomography (FD-OCT). Compared with time-domain optical coherence tomography, frequency-domain optical coherence tomography has obvious advantages in terms of speed and signal-to-noise ratio. Discrimination of spectral information in frequency-domain optical coherence tomography is usually achieved by: in the case of spectral-domain optical coherence tomography (SD-OCT), the spectrometer in the detection arm can be used for spectroscopy; In the case of optical coherence tomography (SS-OCT), spectral information can be obtained by rapidly changing the frequency of the laser light source.
图1中示出了现有技术的用于收集3D图像数据的FD-OCT系统。FD-OCT系统包括光源101，传统的光源包括但不限于具有时间相干长度较短的宽带光源或扫描激光源。来自光源101的光通常被光纤105导向以照亮样品110，典型的样品为人眼的后部的组织。光通常借助于扫描器107在光纤和样品之间扫描，从而使得光束(虚线108)扫描过的区域或体积被成像。从样品散射的光被收集，典型被收集到与用于导向照亮样品的光的光纤相同的光纤105中。从相同的光源101获得的参考光在独立的路径上传输，在这种情况下，包括光纤103和后向反射器104。本领域技术人员能够想到还可以利用传导参考路径。收集到的样品光通常在光纤耦合器102中与参考光结合，从而在探测器120中形成光干涉。从探测器输出的数据被传送给处理器130。处理结果可以存储在处理器中或者展示在显示器140上。处理和存储功能可以在光学相干断层扫描仪内部实现，或者也可以在外部处理单元实现，被收集的数据可以被传输至该外部处理单元。该外部处理单元可以专门用于数据处理，或者还可以执行其它的不限于光学相干断层扫描功能的普通任务。A prior art FD-OCT system for collecting 3D image data is shown in FIG. 1 . The FD-OCT system includes a light source 101. Conventional light sources include but are not limited to broadband light sources or scanning laser sources with short temporal coherence lengths. Light from light source 101 is generally directed by optical fiber 105 to illuminate a sample 110, typically the tissue at the back of the human eye. The light is scanned between the fiber and the sample, typically by means of a scanner 107, such that the area or volume scanned by the beam (dashed line 108) is imaged. Light scattered from the sample is collected, typically into the same optical fiber 105 as used to guide the light illuminating the sample. Reference light obtained from the same light source 101 travels on a separate path, in this case comprising an optical fiber 103 and a retroreflector 104 . Those skilled in the art will appreciate that conductive reference paths can also be utilized. The collected sample light is typically combined with reference light in fiber coupler 102 , resulting in optical interference in detector 120 . Data output from the detectors is communicated to processor 130 . The processing results may be stored in the processor or displayed on the display 140 . The processing and storage functions can be implemented inside the optical coherence tomography scanner or also in an external processing unit to which the collected data can be transferred. The external processing unit may be dedicated to data processing, or may also perform other general tasks not limited to the optical coherence tomography function.
样品和干涉仪的参考臂可以组成bulk-optics、光导纤维或bulk-optic混合系统，并且可以具有不同的结构，例如Michelson、Mach-Zehnder或者本领域技术人员已知的基于共用路径的设计。这里使用的光束应当理解为任何仔细导向的光路。在时域系统中，参考臂需要具有可调的光延迟从而产生干涉。平衡的探测系统通常可以用在TD-OCT系统和SS-OCT系统中，而分光计通常用在SD-OCT系统的探测端口。本文中描述的实用新型可以用于任何类型的OCT系统。OCT系统通常可以封装在壳体中，其具有包括下颚架和头架的多种患者定位元件。The sample and the reference arm of the interferometer can be composed of bulk-optics, fiber optics or hybrid bulk-optic systems and can have different configurations such as Michelson, Mach-Zehnder or common path based designs known to those skilled in the art. A beam of light as used herein should be understood to mean any carefully directed path of light. In a time-domain system, the reference arm needs to have an adjustable optical delay to generate interference. Balanced detection systems can usually be used in TD-OCT systems and SS-OCT systems, while spectrometers are usually used in the detection ports of SD-OCT systems. The utility model described herein can be used with any type of OCT system. OCT systems may typically be housed in a housing with various patient positioning elements including a chin rest and a head frame.
现有技术中，光学相干断层扫描仪已经被用于对患者的视网膜进行扫描，从而进行辅助医疗诊断。图2示出了现有技术中用于对患者的视网膜进行扫描的光学相干断层扫描仪的光学相干断层扫描模块的一种具体实施方式，图2示出的光学相干断层扫描模块包括光纤1、准直镜2、色散补偿柱3、X/Y扫描单元4、视网膜扫描透镜5、接目镜6、以及位于视网膜扫描透镜5与接目镜6之间的用于光路折叠的光学反射镜，从而提供准直的入射扫描光束至示意性的眼睛8。In the prior art, an optical coherence tomography scanner has been used to scan a patient's retina, thereby assisting medical diagnosis. Fig. 2 shows a specific embodiment of an optical coherence tomography module of an optical coherence tomography scanner for scanning a patient's retina in the prior art. The optical coherence tomography module shown in Fig. 2 includes an optical fiber 1, A collimating mirror 2, a dispersion compensation column 3, an X/Y scanning unit 4, a retinal scanning lens 5, an eyepiece 6, and an optical mirror for optical path folding between the retinal scanning lens 5 and the eyepiece 6, thereby providing The collimated incident scanning beam is directed to an illustrative eye 8 .
光学相干断层扫描仪的光源可以是相干长度较短的宽波段光源或者是频率扫描激光。这些光源发出的光经由光纤1的引导进入光学相干断层扫描系统。从样品反射/散射的光又被收集进入光纤1，被收集的样品光与参考光在干涉模块中(未示出)中形成光干涉，光干涉信号被探测器(未示出)接收。从探测器输出的数据被传输至处理器(未示出)。处理结果可以存储在处理器中或者展示在显示器上。处理和存储功能可以在光学相干断层扫描仪内部实现，或者也可以在外部处理单元实现，被收集的数据可以被传输至该外部处理单元。该外部处理单元可以专门用于数据处理，或者还可以执行其它的不限于光学相干断层扫描功能的普通任务。The light source of an optical coherence tomography scanner can be a broadband light source with a short coherence length or a frequency-swept laser. The light emitted by these light sources enters the optical coherence tomography system through the guidance of the optical fiber 1 . The light reflected/scattered from the sample is collected into the optical fiber 1, and the collected sample light and reference light form optical interference in the interference module (not shown), and the optical interference signal is received by the detector (not shown). Data output from the detectors is transmitted to a processor (not shown). The processing results can be stored in the processor or displayed on the display. The processing and storage functions can be implemented inside the optical coherence tomography scanner or also in an external processing unit to which the collected data can be transferred. The external processing unit may be dedicated to data processing, or may also perform other general tasks not limited to the optical coherence tomography function.
光学相干断层扫描仪可以被置于眼睛8前面一定距离处，光学相干断层扫描仪的出瞳(出射光瞳，exit pupil，也就是来自光学相干断层扫描仪的单个扫描光束的枢转点)处于眼睛的瞳孔的位置。如图2所示，来自光学相干断层扫描仪的单个扫描光束都会聚焦至眼睛8的视网膜，单个扫描光束聚焦角度为α1，对应的数值孔径N.A.＝n_eyeball(眼球的折射率)*sin(α1)，该数值孔径N.A.决定了所获得的扫描信号的强度(信噪比)。对于一个屈光正常眼(emmetropic eye)来说，随着光束的扫描，很多个不同入射角度的单个扫描光束聚焦在眼睛8的视网膜的不同位置上(本专利中所提及的“扫描光束”指单个扫描光束或由多个这样的单个扫描光束构成的集合)，这些单个扫描光束的主光线在视网膜上形成一个视场(角)β(FOV，即扫描角度β)，在横向方向上覆盖一定角度的视网膜区域，由此形成的在深度上由视网膜的成像区域跨越的最大光程差(MaximumOPD，即，Maximum Optical Path Difference)H1。The optical coherence tomography scanner can be placed at a certain distance in front of the eye 8, the exit pupil of the optical coherence tomography scanner (exit pupil, i.e. the pivot point of a single scanning beam from the optical coherence tomography scanner) at The position of the pupil of the eye. As shown in Figure 2, a single scanning beam from an optical coherence tomography scanner will be focused to the retina of the eye 8, the single scanning beam focusing angle is α1 , and the corresponding numerical aperture NA=n_eyeball (refractive index of the eyeball)*sin(α1 ), the numerical aperture NA determines the strength of the acquired scanning signal (signal-to-noise ratio). For an emmetropic eye, as the light beam scans, many individual scanning light beams with different incident angles focus on different positions of the retina of the eye 8 (the "scanning light beam" mentioned in this patent Refers to a single scanning beam or a collection of multiple such single scanning beams), the chief rays of these single scanning beams form a field of view (angle) β (FOV, that is, scanning angle β) on the retina, covering in the lateral direction The retinal area at a certain angle, and thus the maximum optical path difference (Maximum OPD, ie, Maximum Optical Path Difference) H1 spanned by the imaging area of the retina in depth.
近视眼是一种常见的屈光不正现象，在光学相干断层扫描仪临床诊断中常会遇到近视眼患者。并且，现有研究显示病理性近视眼会增加某些眼底疾病的概率，这些眼底疾病可以由光学相干断层扫描仪辅助诊断，由此也增加了在临床诊断中近视眼患者需使用光学相干断层扫描仪的概率。Myopia is a common refractive error, and patients with myopia are often encountered in the clinical diagnosis of optical coherence tomography. Moreover, existing studies have shown that pathological myopia will increase the probability of certain fundus diseases, which can be assisted by optical coherence tomography, which also increases the need for optical coherence tomography in clinical diagnosis of myopia patients. Probability of instrument.
图3中的(a)和(b)分别示出利用现有的光学相干断层扫描仪来扫描屈光正常眼和近视眼的一阶光学原理图。与扫描屈光正常眼的情况相比较，在现有技术中，在扫描近视眼时，其补偿原理为根据被检查的眼睛的屈光误差大小，使相干断层扫描仪的出射扫描光束成为相应的发散光束，以使扫描光束重新聚焦在近视眼视网膜上。可以例如通过改变视网膜扫描透镜5和接目镜6之间的距离或者改变光源和准直镜之间的距离来对被检查的眼睛的屈光误差进行补偿，如蔡司公司在2007年推出的OCT系统。例如，如图3中的(b)所示，视网膜扫描透镜和接目镜之间的距离可以被缩短，出射的扫描光束成为发散光束，被检查的眼睛的瞳孔位于接目镜的焦点从而使得眼睛的瞳孔位于来自光学相干断层扫描仪的多束扫描光束的枢转点。在这种调节机制下，根据高斯光学性质，可证明入射屈光正常眼的单个扫描光束截面直径(H_eye)等于调整视网膜扫描透镜和接目镜之间的距离后的入射近视眼的单个扫描光束截面直径(H’_eye)，即，其中，Δ是视网膜扫描透镜和接目镜之间被调节的距离，f2是接目镜的焦距，d是接目镜和眼睛的瞳孔之间的距离并且等于f2。并且如图3中所示，视网膜扫描透镜和接目镜之间的空间为各扫描光束主光线的平行空间，视网膜扫描透镜和接目镜之间的距离变化不会影响在接目镜后各扫描光束主光线的视场β。(a) and (b) in FIG. 3 respectively show the first-order optical principle diagrams of using an existing optical coherence tomography scanner to scan a refractive eye and a myopic eye. Compared with the case of scanning normal eyes, in the prior art, when scanning myopia, the compensation principle is to make the outgoing scanning beam of the coherence tomography scanner become corresponding The beam is diverged so that the scanning beam is refocused on the retina of myopic eyes. For example, by changing the distance between the retinal scanning lens 5 and the eyepiece 6 or changing the distance between the light source and the collimating mirror, the refractive error of the eye being examined can be compensated, such as the OCT system launched by Zeiss in 2007 . For example, as shown in (b) in Figure 3, the distance between the retinal scanning lens and the eyepiece can be shortened, the outgoing scanning beam becomes a diverging beam, and the pupil of the eye being examined is located at the focal point of the eyepiece so that the eye's The pupil is located at the pivot point of the multiple scanning beams from the optical coherence tomography scanner. Under this adjustment mechanism, according to Gaussian optical properties, it can be proved that the single scanning beam section diameter (H_eye) of the incident normal eye is equal to the single scanning beam section of the incident myopic eye after adjusting the distance between the retinal scanning lens and the eyepiece diameter (H'_eye), i.e., where Δ is the adjusted distance between the retinal scanning lens and the eyepiece,f2 is the focal length of the eyepiece, and d is the distance between the eyepiece and the pupil of the eye and is equal tof2 . And as shown in Figure 3, the space between the retinal scanning lens and the eyepiece is the parallel space of the principal light rays of each scanning light beam, and the distance change between the retinal scanning lens and the eyepiece will not affect the main rays of each scanning light beam behind the eyepiece. The field of view β of the ray.
近视眼具体包括两种类型，其中一种类型的近视眼为轴性近视眼，轴性近视眼与眼轴长度伸长有关。眼轴长度伸长的轴性近视眼导致角膜曲率的增加。另一种类型的近视眼是屈光性近视眼，屈光性近视眼与眼睛内部组织的折射状态有关。Myopia specifically includes two types, one of which is axial myopia, which is associated with elongation of the axial length of the eye. Axial myopia in which the axial length of the eye is elongated results in increased corneal curvature. Another type of nearsightedness is refractive myopia, which is related to the refractive state of the tissues inside the eye.
图4中的(a)和(b)分别示出具有正常的眼轴的屈光性近视眼和具有伸长的眼轴的轴性近视眼。对于眼轴长度仍保持正常的屈光性近视眼，视网膜与眼睛的瞳孔之间的距离L’eye基本等于屈光正常眼的视网膜与瞳孔之间的距离Leye，该距离大约为20mm。在现有的调节机制作用下，此时OCT在屈光正常眼情况下的数值孔径N.A.等于OCT在屈光性近视眼情况下的数值孔径N.A.’,即:(a) and (b) in FIG. 4 show a refractive myopia with a normal eye axis and an axial myopia with an elongated eye axis, respectively. For a refractive myopic eye whose axial length remains normal, the distance L'eye between the retina and the pupil of the eye is basically equal to the distance Leye between the retina and the pupil of the normal eye, which is about 20 mm. Under the action of the existing adjustment mechanism, the numerical aperture N.A. of OCT in the case of normal refractive eye is equal to the numerical aperture N.A.' of OCT in the case of refractive myopia, that is:
N.A.’＝n_eyeball*sin(α1)≈n_eyeball*tg(α1)＝n_eyeball*(H’_eye/L’eye)＝n_eyeball*(H_eye/Leye)＝N.A.(H’_eye和H_eye已证相同，分别为入射屈光正常眼和进行补偿调整后入射近视眼的单个扫描光束的截面直径)。并且，由于扫描光束主光线的视场和眼轴长度均未发生变化，眼轴长度正常的屈光性近视眼的在深度上由视网膜的成像区域跨越的最大光程差也保持与正常眼相同。NA'=n_eyeball*sin(α1 )≈n_eyeball*tg(α1 )=n_eyeball*(H'_eye/L'eye)=n_eyeball*(H_eye/Leye)=NA(H'_eye and H_eye have been proved to be the same, are the cross-sectional diameters of a single scanning beam incident on a normal eye and a myopic eye after compensation adjustment, respectively). Moreover, since neither the field of view nor the axial length of the chief ray of the scanning beam has changed, the maximum optical path difference spanned by the imaging area of the retina in depth in a refractive myopic eye with a normal axial length also remains the same as that of a normal eye .
但是，根据医学研究，大多数高度近视眼通常由眼轴的轴向长度伸长所导致，即具有轴性近视。对于轴性近视眼，现有的屈光补偿机制则会产生一些问题。However, according to medical research, most highly myopic eyes are usually caused by the elongation of the axial length of the eye axis, that is, axial myopia. For axial myopia, the existing refractive compensation mechanism will cause some problems.
图5基于和图3同样的原理示出利用现有的光学相干断层扫描仪来扫描屈光正常眼和具有伸长的眼轴的近视眼的示意图。如图5所示，对于具有伸长的眼轴的近视眼。视网膜扫描透镜5和接目镜6之间的距离被缩短从而使得扫描光束重新聚焦至视网膜以补偿被扫描的近视眼的屈光误差。补偿后单个扫描光束聚焦角度α2小于正常眼的扫描光束聚焦角度α1。所以，虽然如前面所分析扫描光束截面直径H_eye保持不变，但与屈光正常眼的情况相比，由于眼轴以系数(L_eye+δL)/L_eye伸长，其中L_eye是标准正常眼的眼轴长，sin(α2)和tg(α2)相比sin(α1)和tg(α1)减小。因此，在具有伸长的眼轴的近视眼的情况下，OCT的数值孔径N.A.＝n_eyeball*sin(α2)≈n_eyeball*tg(α2)会变小。由于光学相干断层扫描仪在减小的数值孔径的情况下从视网膜收集信号，所以，获得的扫描信号的强度相对于没有眼轴伸长的情况减小，这导致扫描信号的信噪比小于没有眼轴伸长的情况。FIG. 5 shows a schematic diagram of using an existing optical coherence tomography scanner to scan a normal eye and a myopic eye with an elongated eye axis based on the same principle as FIG. 3 . As shown in Figure 5, for myopic eyes with elongated axial length. The distance between the retinal scanning lens 5 and the eyepiece 6 is shortened so that the scanning beam is refocused to the retina to compensate for the refractive error of the myopic eye being scanned. After compensation, the focusing angle α2 of a single scanning beam is smaller than the focusing angle α1 of a normal eye. Therefore, although the cross-sectional diameter H_eye of the scanning beam remains unchanged as analyzed above, compared with the case of a normal eye, since the eye axis is elongated by the coefficient (L_eye+δL)/L_eye, where L_eye is the standard normal eye The axial length, sin(α2 ) and tg(α2 ) is reduced compared to sin(α1 ) and tg(α1 ). Therefore, in the case of a myopic eye having an elongated eye axis, the numerical aperture NA=n_eyeball*sin(α2 )≈n_eyeball*tg(α2 ) of the OCT becomes small. Since optical coherence tomography collects signals from the retina at reduced numerical aperture, the intensity of the obtained scan signal is reduced relative to the case without axial elongation, which results in a lower signal-to-noise ratio of the scan signal than without A condition in which the axial length of the eye is elongated.
另外，由于在补偿过程中扫描光束主光线的视场β1并未发生变化，所以扫描光束主光线由眼轴伸长的近视眼视网膜形成的最大光程差H2大于在屈光正常眼的视网膜上形成的最大光程差H1。由于目前的频域光学相干断层扫描仪仅支持有限的扫描深度范围，由视网膜的成像区域跨越的最大光程差超过光学相干断层扫描仪的最大扫描深度会导致光学相干断层扫描仪产生错误的“镜像”扫描图像。例如，图6中示出了这种错误的“镜像”扫描图像。在频域OCT中，分光仪获得的能量谱密度信号，经傅里叶变换后获得样品深度方向信号。对于任意实数信号a(ν),In addition, since the field of view β1of the principal ray of the scanning beam does not change during the compensation process, the maximum optical path differenceH2 formed by the principal ray of the scanning beam by the retina of the myopic eye with elongated eye axis is greater than that of the normal eye The maximum optical path difference H1 formed on the retina. Since current frequency-domain optical coherence tomography scanners only support a limited range of scan depths, the maximum optical path difference spanned by the imaging region of the retina exceeding the maximum scan depth of the optical coherence tomography scanner will cause the optical coherence tomography scanner to generate an erroneous ""Mirror" scanned image. Such an erroneous "mirror" scan image is shown, for example, in FIG. 6 . In frequency-domain OCT, the energy spectral density signal obtained by the spectrometer is transformed by Fourier to obtain the signal in the depth direction of the sample. For any real signal a(ν),
若FT[c(v)]＝C(t),则该信号关于零位呈对称分布。由于能量的谱密度为实数信号，由傅里叶变换特性可知，能够获得两个关于零深度位置对称的深度方向信号，因此，当物体被跨越零深度位置测量时，由于深度差大于光学相干断层扫描仪的扫描深度，从而产生了零深度位置之前(之上)的物体的一部分的镜像并且折叠成如图6所示的横向扫描图像。If FT[c(v)]=C(t), then The signal is distributed symmetrically about the null. Since the spectral density of energy is a real number signal, it can be known from the characteristics of Fourier transform that two depth direction signals that are symmetrical about the zero depth position can be obtained. Therefore, when the object is measured across the zero depth position, since the depth difference is greater than the The scan depth of the scanner, thus creating a mirror image of the part of the object before (above) the zero depth position and folded into a transverse scan image as shown in FIG. 6 .
综上所述，现有技术中，在利用光学相干断层扫描仪对近视眼进行扫描具有一定的缺陷。如果利用视网膜扫描透镜和接目镜之间的距离调整，可以进行屈光误差校正，但是，对于眼轴伸长的近视眼，单个扫描光束的聚焦角度小于屈光正常眼的扫描光束的聚焦角度，从而使整个系统的数值孔径变小，导致获得的扫描信号的强度相对于屈光正常眼的情况减小，扫描信号的信噪比与屈光正常的眼睛的情况相比较小。另外，由于眼轴伸长和视网膜曲率的增加，在深度上由视网膜的成像区域跨越的最大光程差会增加。由于目前频域光学相干断层扫描仪仅支持有限的扫描深度范围，视网膜的成像区域的最大光程差的增加会导致光学相干断层扫描仪产生错误的“镜像”扫描图像。To sum up, in the prior art, the use of an optical coherence tomography scanner to scan myopia has certain defects. If the distance adjustment between the retinal scanning lens and the eyepiece is used, refractive error correction can be performed, however, for a myopic eye with an elongated eye axis, the focusing angle of a single scanning beam is smaller than that of a refractive normal eye, As a result, the numerical aperture of the entire system becomes smaller, resulting in a reduction in the intensity of the obtained scanning signal relative to the case of amemetropic eyes, and a smaller signal-to-noise ratio of the scanning signal than in the case of amemetropic eyes. Additionally, due to axial elongation and increased retinal curvature, the maximum optical path difference spanned in depth by the imaged area of the retina increases. Since the current frequency-domain optical coherence tomography scanner only supports a limited scanning depth range, the increase of the maximum optical path difference of the imaging area of the retina will cause the optical coherence tomography scanner to generate false "mirror" scanning images.
实用新型内容Utility model content
为了解决上述问题，本实用新型提供的光学相干断层扫描仪包括：用于对屈光正常眼进行视网膜扫描的光学相干断层扫描模块，所述光学相干断层扫描仪还包括近视眼扫描模块，所述近视眼扫描模块能够附接至所述光学相干断层扫描模块的外部，以便实现所述光学相干断层扫描仪对屈光正常眼的扫描功能和对眼轴伸长的近视眼的扫描功能的转换；所述近视眼扫描模块具有负光焦度。In order to solve the above problems, the optical coherence tomography scanner provided by the utility model includes: an optical coherence tomography scanning module for performing retinal scanning on ametropic eyes, and the optical coherence tomography scanner also includes a myopic eye scanning module, the The myopic eye scanning module can be attached to the outside of the optical coherence tomography module, so as to realize the conversion of the scanning function of the optical coherence tomography scanner on the normal ametropic eye and the myopic eye with elongated eye axis; The myopia scanning module has negative optical power.
在一个优选的实施方式中，近视眼扫描模块可使得来自光学相干断层扫描仪的扫描光束在进入眼轴伸长的近视眼之前产生发散，从而增加聚焦在眼轴伸长的近视眼的视网膜上的扫描光束的聚焦角度。同时该具有负光焦度的外置近视扫描模块使得来自光学相干断层扫描仪的扫描光束的主光线的视场减小，从而减少由视网膜的成像区域跨越的最大光程差。In a preferred embodiment, the myopia scanning module can make the scanning beam from the optical coherence tomography scanner diverge before entering the myopic eye with elongated eye axis, so as to increase the focus on the retina of the myopic eye with elongated eye axis The focusing angle of the scanning beam. At the same time, the external myopia scanning module with negative focal power reduces the field of view of the chief ray of the scanning beam from the optical coherence tomography scanner, thereby reducing the maximum optical path difference spanned by the imaging area of the retina.
在一个优选的实施方式中，所述近视眼扫描模块为独立的可分离模块，并且能够附接至所述光学相干断层扫描模块的外部。In a preferred embodiment, the myopia scanning module is an independent detachable module, and can be attached to the outside of the optical coherence tomography module.
在一个优选的实施方式中，所述近视眼扫描模块包括一个或多个单透镜、双胶合透镜、多胶合透镜、反射境或者可变光焦度的单透镜。In a preferred embodiment, the myopia scanning module includes one or more single lenses, doublet lenses, doublet lenses, reflective lenses or single lenses with variable optical power.
在一个优选的实施方式中，所述近视眼扫描模块可为一个系列，系列中包括多个具有不同固定光焦度的模块。优选地，具有较大负光焦度的模块用于眼轴长度伸长较长的近视眼，具有较小负光焦度的模块用于眼轴长度伸长较短的近视眼。In a preferred embodiment, the myopia scanning module can be a series, and the series includes a plurality of modules with different fixed optical powers. Preferably, the module with larger negative optical power is used for myopic eyes with longer axial length extension, and the module with smaller negative optical power is used for myopic eyes with shorter axial length extension.
在一个优选的实施方式中，所述近视眼扫描模块包括具有例如单透镜、双胶合透镜、多胶合透镜、反射境或者可变光焦度的单透镜的多个透镜的变焦透镜组，所述变焦透镜组的光焦度可以被调节。优选地，通过调节所述变焦透镜组的多个透镜之间的距离或者通过调节可变光焦度的单透镜的光焦度来调节所述变焦透镜组的光焦度。优选地，所述变焦透镜组的多个透镜之间的距离能够通过电动或手动方式被调节。In a preferred embodiment, the myopia scanning module includes a zoom lens group having a plurality of lenses such as a single lens, a doublet lens, a doublet lens, a reflective lens or a single lens with variable focal power, the The power of the zoom lens group can be adjusted. Preferably, the optical power of the zoom lens group is adjusted by adjusting the distance between a plurality of lenses of the zoom lens group or by adjusting the optical power of a single lens with variable optical power. Preferably, the distance between the multiple lenses of the zoom lens group can be adjusted electrically or manually.
在一个优选的实施方式中，所述光学相干断层扫描模块的视网膜扫描透镜和接目镜之间的距离可调节。In a preferred embodiment, the distance between the retinal scanning lens and the eyepiece of the optical coherence tomography module is adjustable.
在一个优选的实施方式中，所述光学相干断层扫描模块的光源和准直镜之间的距离可调节。In a preferred embodiment, the distance between the light source and the collimating mirror of the optical coherence tomography module can be adjusted.
本实用新型还提供了用于光学相干断层扫描仪的近视眼扫描模块，所述光学相干断层扫描仪包括用于进行视网膜扫描的光学相干断层扫描模块，其中，所述近视眼扫描模块能够附接至所述光学相干断层扫描模块的外部，以便实现所述光学相干断层扫描仪对屈光正常眼的扫描功能和对眼轴伸长的近视眼的扫描功能的转换；所述近视眼扫描模块具有负光焦度。The utility model also provides a myopia scanning module for an optical coherence tomography scanner, the optical coherence tomography scanner includes an optical coherence tomography module for retinal scanning, wherein the myopia scanning module can be attached to To the outside of the optical coherence tomography module, in order to realize the conversion of the scanning function of the optical coherence tomography scanner to the normal eye and the scanning function of the myopic eye with elongated eye axis; the myopic eye scanning module has Negative optical power.
在一个优选的实施方式中，近视眼扫描模块可使得来自光学相干断层扫描仪的扫描光束在进入眼轴伸长的近视眼之前产生发散，从而增加聚焦在眼轴伸长的近视眼的视网膜上的扫描光束的聚焦角度，并且减少来自光学相干断层扫描仪的扫描光束的主光线的视场。In a preferred embodiment, the myopia scanning module can make the scanning beam from the optical coherence tomography scanner diverge before entering the myopic eye with elongated eye axis, so as to increase the focus on the retina of the myopic eye with elongated eye axis Focusing angle of the scanning beam of the optical coherence tomography scanner and reducing the field of view of the chief ray of the scanning beam of the optical coherence tomography scanner.
在一个优选的实施方式中，所述近视眼扫描模块为独立的可分离模块，并且能够附接至所述光学相干断层扫描模块的外部。In a preferred embodiment, the myopia scanning module is an independent detachable module, and can be attached to the outside of the optical coherence tomography module.
在一个优选的实施方式中，所述近视眼扫描模块包括一个或者多个单透镜、双胶合透镜、多胶合透镜、反射境或者可变光焦度的单透镜。In a preferred embodiment, the myopia scanning module includes one or more single lenses, doublet lenses, doublet lenses, reflective lenses or single lenses with variable optical power.
在一个优选的实施方式中，所述近视眼扫描模块可以为一个模块系列，系列中每个模块具有不同光焦度。In a preferred embodiment, the myopia scanning module may be a series of modules, and each module in the series has a different optical power.
在一个优选的实施方式中，具有较大负光焦度的近视眼扫描模块用于眼轴长度伸长较长的近视眼，具有较小负光焦度的近视眼扫描模块用于眼轴长度伸长较短的近视眼。In a preferred embodiment, the myopia scanning module with larger negative optical power is used for myopic eyes with longer eye axial length, and the myopic eye scanning module with smaller negative optical power is used for eye axial length Elongated short-sighted eyes.
在一个优选的实施方式中，所述近视眼扫描模块包括具有例如单透镜、双胶合透镜、多胶合透镜、反射境或者可变光焦度的单透镜的多个透镜的变焦透镜组，所述变焦透镜组的光焦度可以被调节。优选地，通过调节所述变焦透镜组的多个透镜之间的距离或者通过调节可变光焦度的单透镜的光焦度来调节所述变焦透镜组的光焦度。优选地，所述变焦透镜组的多个透镜之间的距离能够通过电动或手动方式被调节。In a preferred embodiment, the myopia scanning module includes a zoom lens group having a plurality of lenses such as a single lens, a doublet lens, a doublet lens, a reflective lens or a single lens with variable focal power, the The power of the zoom lens group can be adjusted. Preferably, the optical power of the zoom lens group is adjusted by adjusting the distance between a plurality of lenses of the zoom lens group or by adjusting the optical power of a single lens with variable optical power. Preferably, the distance between the multiple lenses of the zoom lens group can be adjusted electrically or manually.
与现有技术相比，本实用新型的光学相干断层扫描仪至少具有以下优点：由于本实用新型的光学相干断层扫描仪中的近视眼扫描模块具有负光焦度，使得来自光学相干断层扫描仪的扫描光束在进入眼轴伸长的近视眼之前产生发散，而扫描光束的主光线的视场减小，从而增加聚焦在眼轴伸长的近视眼的视网膜上的扫描光束的聚焦角度并且减少由视网膜的成像区域跨越的最大光程差，以获得较强的扫描信号(较大的信噪比)且避免错误的“镜像”扫描图像。Compared with the prior art, the optical coherence tomography scanner of the present utility model has at least the following advantages: since the myopia scanning module in the optical coherence tomography scanner of the present utility model has negative optical power, the optical coherence tomography scanner from the optical coherence tomography scanner The scanning beam diverges before entering the myopic eye with elongated eye axis, and the field of view of the chief ray of the scanning beam decreases, thereby increasing the focusing angle of the scanning beam focused on the retina of the myopic eye with elongated eye axis and reducing The maximum optical path difference spanned by the imaging area of the retina to obtain a stronger scan signal (greater signal-to-noise ratio) and to avoid false "mirror" scan images.
附图说明Description of drawings
图1示出了现有技术中的光学相干断层扫描仪的示意图；FIG. 1 shows a schematic diagram of an optical coherence tomography scanner in the prior art;
图2示出了现有技术中的光学相干断层扫描仪的另一示意图；Fig. 2 shows another schematic diagram of an optical coherence tomography scanner in the prior art;
图3示出了利用现有的光学相干断层扫描仪来扫描屈光正常眼和近视眼的示意图；Fig. 3 shows the schematic diagram of using existing optical coherence tomography scanner to scan normal refractive eye and myopic eye;
图4示出了具有正常的眼轴和具有伸长的眼轴的近视眼的示意图；Figure 4 shows a schematic diagram of a myopic eye with a normal eye axis and with an elongated eye axis;
图5示出了另一个利用现有的光学相干断层扫描仪来扫描屈光正常眼和具有伸长的眼轴的近视眼的示意图；Fig. 5 shows another schematic diagram of using an existing optical coherence tomography scanner to scan a refractive eye and a myopic eye with an elongated eye axis;
图6示出了利用现有的光学相干断层扫描仪扫描具有伸长的眼轴的近视眼所获得的“镜像”扫描图像；Figure 6 shows the "mirror" scan image obtained by scanning a myopic eye with an elongated eye axis using an existing optical coherence tomography scanner;
图7示出了本实用新型的具有附加的近视眼扫描模块的光学相干断层扫描仪的示意图；Fig. 7 shows a schematic diagram of an optical coherence tomography scanner with an additional myopia scanning module of the present invention;
图8示出了本实用新型的具有附加的近视眼扫描模块的光学相干断层扫描仪的一个具体实施方式；Fig. 8 shows a specific embodiment of an optical coherence tomography scanner with an additional myopia scanning module of the present invention;
图9示出了本实用新型的具有附加的近视眼扫描模块的光学相干断层扫描仪的另一个具体实施方式。Fig. 9 shows another embodiment of the optical coherence tomography scanner with an additional myopia scanning module of the present invention.
具体实施方式Detailed ways
下面参照附图描述根据本实用新型的实施例的光学相干断层扫描仪。在下面的描述中，阐述了许多具体细节以便使所属技术领域的技术人员更全面地了解本实用新型。但是，对于所属技术领域内的技术人员明显的是，本实用新型的实现可不具有这些具体细节中的一些。此外，应当理解的是，本实用新型并不限于所介绍的特定实施例。相反，可以考虑用下面的特征和要素的任意组合来实施本实用新型，而无论它们是否涉及不同的实施例。因此，下面的方面、特征、实施例和优点仅作说明之用而不应被看作是权利要求的要素或限定，除非在权利要求中明确提出。An optical coherence tomography scanner according to an embodiment of the present invention will be described below with reference to the accompanying drawings. In the following description, many specific details are set forth so that those skilled in the art can more fully understand the utility model. It will be apparent, however, to one skilled in the art that the present invention may be practiced without some of these specific details. Furthermore, it should be understood that the invention is not limited to the particular embodiments described. On the contrary, any combination of the following features and elements can be considered to implement the present invention, regardless of whether they relate to different embodiments. Accordingly, the following aspects, features, embodiments and advantages are by way of illustration only and should not be considered elements or limitations of the claims unless explicitly stated in the claims.
图7示出了本实用新型的具有附加的近视眼扫描模块的光学相干断层扫描仪，在图7所示的光学相干断层扫描仪中，除了用于对屈光正常眼的视网膜进行扫描的光学相干断层扫描仪的常规光学元件之外，还包括附加的近视眼扫描模块，具有负光焦度的近视眼扫描模块7被附接至现有的光学相干断层扫描仪的机械接口的外部，以便实现光学相干断层扫描仪对屈光正常眼的扫描功能和对眼轴伸长的近视眼的扫描功能的转换。附加的近视眼扫描模块7被置于接目镜6的外部，近视眼扫描模块7具有负光焦度，离开光学相干断层扫描仪的接目镜6的各束单个扫描光束在通过附加的近视眼扫描模块7之后会变得更加发散，从而使得扫描光束在眼睛的瞳孔位置的光束截面直径增大。由于扫描光束在瞳孔位置的光束截面直径增大，从而增加聚焦在眼轴伸长的近视眼的视网膜上的扫描光束的聚焦角度。同时，扫描光束的主光线在经由具有负光焦度的附加近视扫描模块7后视场变小，从而使得由视网膜的成像区域跨越的最大光程差减少。如图7所示，由于附接了具有负光焦度的近视眼扫描模块7，增加了扫描光束聚焦角度并且减少了由视网膜的成像区域跨越的最大光程差，即，由于扫描光束的发散，具有附加近视眼扫描模块的扫描光束聚焦角度α3大于没有附加近视眼扫描模块的扫描光束聚焦角度α2。根据数值孔径公式N.A.＝n_eyeball(眼球的折射率)*sin(α3)，附接了具有负光焦度的近视眼扫描模块7的光学相干断层扫描仪的数值孔径N.A.相应增加，甚至可以增加到比没有附加近视眼扫描模块时扫描屈光正常眼的数值孔径N.A.还要大。另外，各扫描光束主光线在具有负光焦度的近视扫描模块7的作用下，其视场会减小，即具有附加近视眼扫描模块的扫描光束主光线的视场β3小于没有附加近视眼扫描模块的扫描光束主光线的视场β2(等于背景技术中的β1)，从而使具有附加近视眼扫描模块时的最大光程差H3小于没有附加近视眼扫描模块时的最大光程差H2。因此，在附接了具有负光焦度的近视扫描模块7之后，聚焦在具有伸长的眼轴的近视眼的视网膜上的扫描光束的聚焦角度回复并保持与扫描屈光正常眼时近似相等，从而与没有附加近视眼扫描模块而采用现有技术中补偿屈光误差的方法扫描具有伸长的眼轴的近视眼的情况相比获得了较强的扫描信号(信噪比)，并且，由于利用了附加的近视眼扫描模块，扫描光束的视场减小，由视网膜的成像区域跨越的最大光程差也相应减小，由此在大部分情况下避免了错误的“镜像”扫描图像。Fig. 7 shows an optical coherence tomography scanner with an additional myopic eye scanning module of the present invention, in the optical coherence tomography scanner shown in Fig. In addition to the conventional optical components of the coherence tomography scanner, an additional myopia scanning module is also included, and the myopia scanning module 7 with negative optical power is attached to the outside of the mechanical interface of the existing optical coherence tomography scanner, so that Realize the transformation of the scanning function of the optical coherence tomography scanner on the normal refractive eye and the myopic eye with elongated eye axis. The additional myopia scanning module 7 is placed outside the eyepiece 6, the myopia scanning module 7 has a negative refractive power, and each single scanning light beam leaving the eyepiece 6 of the optical coherence tomography scanner passes through the additional myopia scanning The module 7 then becomes more divergent, so that the diameter of the beam section of the scanning beam at the pupil of the eye increases. Since the cross-sectional diameter of the scanning beam at the pupil position increases, the focusing angle of the scanning beam focused on the retina of the myopic eye with elongated eye axis increases. At the same time, the field of view becomes smaller after the chief ray of the scanning beam passes through the additional myopic scanning module 7 with negative optical power, so that the maximum optical path difference spanned by the imaging area of the retina is reduced. As shown in Figure 7, due to the attachment of the myopia scanning module 7 with negative optical power, the scanning beam focusing angle is increased and the maximum optical path difference spanned by the imaging area of the retina is reduced, i.e., due to the divergence of the scanning beam , the scanning beam focus angle α3 with the additional myopia scanning module is greater than the scanning beam focus angle α2 without the additional myopia scanning module. According to numerical aperture formula NA=n_eyeball (refractive index of eyeball)*sin (α 3), the numerical aperture NA of the optical coherence tomography scanner that has attached the myopic eye scanning module 7 with negative optical power increases correspondingly, even can increase to It is larger than the numerical aperture NA of scanning the normal ametropic eye when there is no additional myopic eye scanning module. In addition, under the effect of the myopia scanning module 7 with negative optical power, the main rays of each scanning beam will reduce the field of view, that is, the field of view β3 of the chief ray of the scanning beam with the additional myopia scanning module is smaller than that without the additional myopia. The field of view β2 (equal to β1 in the background technology) of the scanning light beam chief ray of the scanning module, thereby make the maximum optical path difference H when there is an additional myopia scanning module smallerthan the maximum optical path difference H when there is no additional myopic scanning module2 . Thus, after attaching the myopic scanning module 7 with negative optical power, the focus angle of the scanning beam focused on the retina of the myopic eye with elongated eye axis returns and remains approximately equal to when scanning the ammetropic eye , thereby obtaining a stronger scanning signal (signal-to-noise ratio) compared with the case of scanning a myopic eye with an elongated eye axis by using the prior art method of compensating for refractive errors without an additional myopic eye scanning module, and, Due to the use of the additional myopia scanning module, the field of view of the scanning beam is reduced and the maximum optical path difference spanned by the imaging area of the retina is correspondingly reduced, thus avoiding false "mirror" scanned images in most cases .
本实用新型中，无需现有的光学相干断层扫描仪的屈光误差校正机制，即无需对光学相干断层扫描仪中的视网膜扫描透镜和接目镜之间的距离进行调节，借助于附加的具有负光焦度的近视眼扫描模块，可以对具有伸长的眼轴的高度近视眼进行扫描，获得较强的扫描信号(信噪比)且可避免错误的“镜像”扫描图像。本实用新型的技术方案如果与现有的光学相干断层扫描仪的屈光误差校正机制相结合，则可以进一步扩展屈光误差校正范围。In the utility model, there is no need for the existing optical coherence tomography scanner's refractive error correction mechanism, that is, there is no need to adjust the distance between the retinal scanning lens and the eyepiece in the optical coherence tomography scanner. The optical myopia scanning module can scan high myopia with elongated eye axis, obtain stronger scanning signal (signal-to-noise ratio) and avoid wrong "mirror image" scanning images. If the technical solution of the utility model is combined with the existing refractive error correction mechanism of the optical coherence tomography scanner, the correction range of the refractive error can be further expanded.
本实用新型中，附加的近视眼扫描模块中的透镜数量、类型和焦距是可变的。例如，附加的近视眼扫描模块可以包括一个或者多个单透镜、双胶合透镜、多胶合透镜或者由若干个透镜组成的透镜组，只要单透镜、双胶合透镜、多胶合透镜或透镜组所构成的近视眼扫描模块的等效负光焦度可以满足对于一定屈光范围的近视眼的扫描需求即可。优选地，所述近视眼扫描模块可以采用多个具有不同固定光焦度的透镜或变焦系统来覆盖较大的近视眼屈光度范围，所述变焦透镜系统的光焦度可以被调节。变焦透镜系统可以包括单透镜、双胶合透镜、多胶合透镜、反射境、可变光焦度的单透镜(即液体透镜)。在实际产品中，所述近视眼扫描模块可以为一个模块系列，系列中每个模块具有不同负光焦度。In the utility model, the quantity, type and focal length of lenses in the additional myopia scanning module are variable. For example, the additional myopia scanning module can include one or more single lenses, doublet lenses, doublet lenses or lens groups composed of several lenses, as long as the single lens, doublet lenses, doublet lenses or lens groups constitute The equivalent negative optical power of the myopia scanning module can meet the scanning requirements for myopia with a certain range of refraction. Preferably, the myopia scanning module can use a plurality of lenses with different fixed powers or a zoom system to cover a larger range of myopia diopters, and the power of the zoom lens system can be adjusted. The zoom lens system may include singlets, doublets, doublets, reflectors, variable power singlets (ie liquid lenses). In an actual product, the myopia scanning module may be a module series, and each module in the series has a different negative optical power.
图8示出本实用新型的具有附加的近视眼扫描模块的光学相干断层扫描仪的一个具体实施方式，该方式中包含两个具有固定光焦度的双胶合透镜的近视眼扫描模块。图8(a)中，对于眼轴长度伸长较大的近视眼，可以使用具有较强的负光焦度的双胶合透镜的近视眼扫描模块。而图8(b)中，对于眼轴长度伸长较小的近视眼，可以使用具有较弱的负光焦度的双胶合透镜的近视眼扫描模块。Fig. 8 shows a specific embodiment of the optical coherence tomography scanner with an additional myopia scanning module of the present invention, which includes two myopia scanning modules with doublet lenses with fixed refractive power. In FIG. 8( a ), for the myopic eye with a large elongation of the axial length of the eye, a myopic eye scanning module with a doublet lens with strong negative power can be used. In FIG. 8( b ), for a myopic eye with a small elongation of the axial length of the eye, a myopic eye scanning module with a doublet lens with a weaker negative power can be used.
图9示出本实用新型的具有附加的近视眼扫描模块的光学相干断层扫描仪的另一个具体实施方式。如图9所示，近视眼扫描模块7是包括两个透镜7-1、7-2的变焦系统，其中一个透镜7-1可以具有负光焦度，而另一个透镜7-2则具有正光焦度，它们所组成的变焦系统具有负光焦度。图9(a)至9(c)示出了两个透镜7-1、7-2的间距从小至大的不同状态，通过调节变焦系统的两个透镜7-1、7-2之间的距离，近视眼扫描模块7可以覆盖一定范围的近视眼屈光度(对应于具有不同眼轴伸长度的近视眼)。具体地，当用于眼轴伸长度较大的近视眼时，可以将变焦系统的两个透镜7-1、7-2调节为具有较小的间距，当用于眼轴伸长度较小的近视眼时，可以将变焦系统的两个透镜7-1、7-2调节为具有较大的间距。具体地，可以通过电动或者手动方式来调节变焦系统中的透镜之间的距离，该变焦系统也可包括两个以上的透镜或者透镜组。FIG. 9 shows another embodiment of the optical coherence tomography scanner with an additional myopia scanning module of the present invention. As shown in Figure 9, the myopia scanning module 7 is a zoom system comprising two lenses 7-1, 7-2, wherein one lens 7-1 can have a negative power, while the other lens 7-2 has a positive light focal power, the zoom system composed of them has negative focal power. Fig. 9 (a) to 9 (c) have shown the different states of the spacing of two lenses 7-1, 7-2 from small to large, by adjusting the distance between the two lenses 7-1, 7-2 of the zoom system distance, the myopia scanning module 7 can cover a certain range of myopia diopters (corresponding to myopia with different axial elongation). Specifically, when used for myopia with relatively large axial elongation, the two lenses 7-1 and 7-2 of the zoom system can be adjusted to have a smaller distance; For myopia, the two lenses 7-1 and 7-2 of the zoom system can be adjusted to have a larger distance. Specifically, the distance between lenses in the zoom system can be adjusted electrically or manually, and the zoom system can also include more than two lenses or lens groups.
在本实用新型的具有近视眼扫描模块的光学相干断层扫描仪可以在不改变现有光学相干断层扫描仪内部结构、不增加光学相干断层扫描仪本身的成本的基础上克服现有技术中的缺陷。由于近视眼扫描模块具有负光焦度，使得来自光学相干断层扫描仪的扫描光束在进入眼轴伸长的近视眼的瞳孔之前产生发散，从而增加聚焦在眼轴伸长的近视眼的视网膜上的扫描光束的聚焦角度。并且使得来自光学相干断层扫描仪的扫描光束主光线的视场变小以减少由视网膜的成像区域跨越的最大光程差。从而获得了较强的扫描信号(信噪比)，并且避免了错误的“镜像”扫描图像。The optical coherence tomography scanner with the myopia scanning module of the utility model can overcome the defects in the prior art without changing the internal structure of the existing optical coherence tomography scanner and without increasing the cost of the optical coherence tomography scanner itself . Due to the negative power of the myopia scanning module, the scanning beam from the optical coherence tomography scanner diverges before entering the pupil of the myopic eye with elongated eye axis, thereby increasing the focus on the retina of the myopic eye with elongated eye axis The focusing angle of the scanning beam. And the field of view of the chief ray of the scanning beam from the optical coherence tomography scanner is made smaller to reduce the maximum optical path difference spanned by the imaging area of the retina. This results in a stronger scan signal (signal-to-noise ratio) and avoids erroneous "mirror" scan images.
另外，将本实用新型描述的近视眼扫描模块用于正常人眼扫描时，由于视场变小，实际在正常视网膜上的扫描范围也相应变小。此时OCT仪器将较小的扫描范围依然显示在相同的显示区域，起到了一个对正常人眼扫描进行局部放大的作用。In addition, when the myopic eye scanning module described in the present invention is used for scanning normal human eyes, since the field of view becomes smaller, the actual scanning range on the normal retina is also correspondingly smaller. At this time, the OCT instrument still displays a smaller scanning range in the same display area, which plays a role of partially zooming in on normal human eye scanning.
虽然本实用新型已以较佳实施例披露如上，但本实用新型并非限定于此。任何本领域技术人员，在不脱离本实用新型的精神和范围内所作的各种更动与修改，均应纳入本实用新型的保护范围内，因此本实用新型的保护范围应当以权利要求所限定的范围为准。Although the utility model has been disclosed above with preferred embodiments, the utility model is not limited thereto. Any changes and modifications made by those skilled in the art without departing from the spirit and scope of the present utility model should be included in the protection scope of the present utility model, so the protection scope of the present utility model should be defined by the claims range prevails.
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| CN201520135596.6UCN204636295U (en) | 2015-03-10 | 2015-03-10 | For the myopia scan module of OCT |
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| CN201520135596.6UCN204636295U (en) | 2015-03-10 | 2015-03-10 | For the myopia scan module of OCT |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106031629A (en)* | 2015-03-10 | 2016-10-19 | 卡尔蔡司医疗技术公司 | A myopic eye scanning module used for an optical coherence tomography instrument |
| CN108366713A (en)* | 2016-03-18 | 2018-08-03 | 株式会社吉田制作所 | Optical coherence tomographic imaging apparatus and its application method |
| CN112351757A (en)* | 2018-04-06 | 2021-02-09 | 克拉诺瓦公司 | Device for treating tissue comprising an original optical system for laser deflection and focusing |
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106031629A (en)* | 2015-03-10 | 2016-10-19 | 卡尔蔡司医疗技术公司 | A myopic eye scanning module used for an optical coherence tomography instrument |
| CN108366713A (en)* | 2016-03-18 | 2018-08-03 | 株式会社吉田制作所 | Optical coherence tomographic imaging apparatus and its application method |
| US10799099B2 (en) | 2016-03-18 | 2020-10-13 | The Yoshida Dental Mfg. Co., Ltd. | Optical interference tomographic image generating apparatus and method for using same |
| CN112351757A (en)* | 2018-04-06 | 2021-02-09 | 克拉诺瓦公司 | Device for treating tissue comprising an original optical system for laser deflection and focusing |
| CN112351757B (en)* | 2018-04-06 | 2023-09-29 | 克拉诺瓦公司 | Apparatus for treating tissue comprising an original optical system for laser deflection and focusing |
| Publication | Publication Date | Title |
|---|---|---|
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