Ophthalmology measurement system with optical path compensation deflection mechanism

Abstract

An ophthalmic measuring system with an optical path compensation deflection mechanism comprises an OCT light source, a reference arm, a sample arm module, an optical fiber coupler, a detector and the optical path compensation deflection mechanism. The sample arm module comprises a light path switching scanning device which can reflect detection light to a posterior segment or anterior segment light path. The optical path compensation deflection mechanism comprises a rotating mechanism and an optical path compensation deflection assembly. According to the mechanism, the optical path can be dynamically adjusted, the A-Scan optical path or phase change is kept constant, the Doppler frequency shift effect is simulated, and hardware cost does not need to be increased. The system can avoid using a carrier frequency adding technology in a preview stage, so that sampling requirements are reduced, and the cost is reduced. During measurement, shallow detection depth is adopted, the to-be-measured eye is quickly aligned, and the accuracy is improved. Fast switching of scanning modes allows for accurate measurement of ocular axial length, anterior chamber depth, and lens thickness. The invention provides an ophthalmology OCT imaging solution which is high in cost benefit, easy and convenient to operate and accurate in measurement, and the clinical diagnosis requirement is met.

Description

Technical Field

[0001] The invention relates to ophthalmic optical coherence tomography technology, in particular to an ophthalmic measurement system with an optical path compensation deflection mechanism. Background Art

[0002] Nowadays, more and more elderly people suffer from cataracts, and transplanting artificial lenses is an effective and widely used treatment for cataracts. However, the calculation of artificial lenses requires many parameters, such as the curvature of the anterior and posterior surfaces of the cornea, corneal thickness, anterior chamber depth, lens thickness, the curvature of the anterior and posterior surfaces of the lens, and axial length. There are many parameters to be measured, but it often requires multiple medical devices to detect them before the above complete data can be obtained. Therefore, if a medical device can be implemented that can obtain the above data, it can not only improve the convenience of measurement for patient testing, but also improve the accuracy of measurement.

[0003] With the in-depth research and development of ophthalmology, the medical community has found that the myopia problem of adolescents is closely related to the growth of their axial length. During the growth and development of adolescents, if the axial length grows too fast, it is often accompanied by the rapid deepening of myopia. Therefore, when preventing and controlling myopia in adolescents, studying and tracking the growth changes of the axial length of adolescents is also one of the important indicators of their ophthalmic parameters.

[0004] Optical coherence tomography (OCT) is an emerging optical imaging technology. Compared with traditional clinical imaging methods, it has the advantages of high resolution, fast imaging speed, no radiation damage, moderate price, and compact structure. It is an important potential tool for basic medical research and clinical diagnosis applications. Currently, among the various ophthalmic devices using optical instruments, OCT devices used for ophthalmic examination and treatment have become an indispensable ophthalmic device for the diagnosis of ophthalmic diseases.

[0005] 1) The existing technology for measuring shaft length often uses time domain tomography technology, which is slow and has low measurement accuracy.

[0006] Patent document 200710020707.9 discloses a method for measuring the axial length of the eye using OCT. Although this method can measure the axial length of the human eye and various living animals, it has the following two disadvantages: 1. The moving probe of the stepping motor is used to adjust the optical path, thereby realizing the imaging of the cornea and the fundus. However, it takes a certain amount of time for the motor to move back and forth, and it is impossible to achieve rapid switching between the front and back segments and real-time imaging. In addition, the eyes of the measured object will shake, making the measurement of the axial length inaccurate and the error large; 2. Due to the different structures of the cornea and the fundus, the same probe cannot be focused at both positions, resulting in poor imaging quality, which is an unavoidable defect of this method.

[0007] 2) The existing patent "An OCT system and method for measuring the optical path value of the eye axis, application number 201410214827.2" introduces corneal position alignment technology, which does not require switching between the anterior and posterior segments, but does not have the anterior segment measurement function and the corneal curvature measurement function (or does not mention it). Measuring the cornea requires an additional operation. It is impossible to achieve rapid diagnosis of patients.

[0008] 3) With the existing patents “Ophthalmic Measurement System and Method, Application No. 201810130278.9” and “Ophthalmic Measurement System, Application No. 201910116857.2”, it is difficult to deepen the detection depth of the OCT system.

[0009] 4) The existing patent "Ophthalmic measurement system based on shutter switching, application number 202020735955.2" measures the anterior chamber depth and lens thickness, and also uses OCT data after the optical path is switched twice to calculate the axial length. This switching speed will affect the measurement accuracy of the anterior chamber depth and lens thickness.

[0010] It uses frequency-domain optical coherence tomography technology, which has faster scanning speed and higher imaging resolution than time-domain OCT systems, but a shallow detection depth. Compared with scanning frequency-domain optical coherence tomography technology, it has comparable scanning speed and resolution, and is much less expensive, but a shallow detection depth.

[0011] It should be noted that the information disclosed in the above background technology section is only used for understanding the background of the present application, and therefore may include information that does not constitute prior art known to ordinary technicians in the field. Summary of the invention

[0012] The main purpose of the present invention is to overcome the defects existing in the above-mentioned background technology and provide an ophthalmic measurement system with an optical path compensation deflection mechanism.

[0013] To achieve the above object, the present invention adopts the following technical solutions:

[0014] An ophthalmic measurement system with an optical path compensation deflection mechanism, comprising an OCT imaging module, the OCT imaging module comprising an OCT light source, a reference arm module, an OCT sample arm module, an optical fiber coupler and a detector, the OCT sample arm module comprising an optical path switching scanning device, a posterior segment OCT sample arm optical path and an anterior segment OCT sample arm optical path, the detection light output by the optical fiber coupler is reflected by the optical path switching scanning device at different angles and then enters the posterior segment OCT sample arm optical path or the anterior segment OCT sample arm optical path accordingly; and an optical path compensation deflection mechanism is also included, the detection light passes through the The optical path compensation deflection assembly then enters the optical path switching scanning device, and the optical path compensation deflection mechanism includes a rotating mechanism and an optical path compensation deflection assembly; wherein, when the rotating mechanism drives the optical path compensation deflection assembly to deflect to a set deflection angle, the detection light passes through the optical path compensation deflection assembly and deviates from the scanning center of the optical path switching scanning device, thereby introducing a Doppler frequency shift, and in conjunction with the scanning of the optical path switching scanning device, the optical path or phase change between adjacent A-Scans is kept constant, and when the optical path compensation deflection assembly is not deflected, the detection light passes through the optical path compensation deflection assembly and does not introduce a Doppler frequency shift.

[0015] Furthermore, the optical path compensation deflection assembly includes a deflection glass block and an optical path compensation glass block; wherein, when the rotating mechanism drives the optical path compensation deflection assembly to deflect to a set deflection angle, the detection light passes through the deflection glass block to generate a changed optical path, and the detection light does not pass through the optical path compensation glass block, and when the optical path compensation deflection assembly is not deflected, the detection light passes through the deflection glass block and the optical path compensation glass block.

[0016] Furthermore, the rotating mechanism is a rotating motor.

[0017] Furthermore, when the optical path compensation deflection assembly is not deflected, the optical path compensation deflection assembly is arranged parallel to the main optical axis of the detection light, and the detection light passes through the optical path compensation glass block and the deflection glass block at a vertical incident angle. When the optical path compensation deflection assembly is deflected to the set deflection angle, the main optical axis of the detection light forms an angle with the optical path compensation deflection assembly, and the detection light passes through the deflection glass block at an inclined angle.

[0018] Furthermore, the optical path compensation deflection component does not deflect when performing OCT scanning imaging of the posterior segment of the eye and the cornea, and the optical path compensation deflection component deflects to the set deflection angle when performing panoramic OCT scanning imaging of the anterior chamber of the eye and the entire lens.

[0019] Furthermore, the anterior chamber OCT sample arm optical path includes an anterior chamber measuring lens, which is configured to cut in or out of the optical path; the anterior chamber measuring lens is designed to guide the detection light beam to focus near the center of the anterior chamber of the eye when performing anterior chamber OCT scanning imaging; when performing panoramic OCT scanning imaging of the entire lens, the anterior chamber measuring lens is in a cut-out state.

[0020] Furthermore, the anterior segment OCT sample arm optical path includes a first reflector, a first lens, a third reflector, a fifth reflector, a third lens, a third beam splitter, a front beam splitter and an eyepiece objective lens. After the light beam is reflected by the optical path switching scanning device, it is successively reflected by the first reflector, transmitted by the first lens, and then reflected by the third reflector and the fifth reflector, and then transmitted by the third lens, transmitted by the third beam splitter, and then reflected by the front beam splitter to the eyepiece objective lens, and finally converged to the anterior segment of the human eye through the human eye; the anterior chamber insertion lens for measuring the anterior segment of the human eye can be inserted into the anterior segment OCT sample arm optical path.

[0021] Furthermore, the optical path of the posterior segment OCT sample arm includes a light path adjustment module, a posterior segment and a gaze beam splitter, a refractive adjustment device, a third beam splitter, a front beam splitter and an eyepiece objective lens in sequence. After the light beam is reflected by the optical path switching scanning device, it passes through the light path adjustment module, and then is reflected by the posterior segment and the gaze beam splitter, passes through the refractive adjustment device, is reflected by the third beam splitter, and then is reflected by the front beam splitter to the eyepiece objective lens, and finally passes through the human eye to converge to the fundus of the human eye.

[0022] Furthermore, it also includes a computer connected to the detector, which processes the interference signal introduced with the Doppler frequency shift and uses a de-imaging algorithm to obtain an OCT image using positive and negative frequency image data.

[0023] The present invention has the following beneficial effects:

[0024] The ophthalmic measurement system of the present invention realizes efficient and accurate imaging of different parts of the eye by innovatively introducing an optical path compensation deflection mechanism. Through the optical path compensation deflection mechanism, the system can dynamically adjust the optical path in different imaging modes, keep the optical path or phase change between adjacent A-Scans constant, thereby introducing the frequency loading technology, effectively simulating the Doppler frequency shift effect, and enhancing the detection depth of the system without increasing the number of spectrometer pixels or sampling points of the system. Through the overall deflection of the optical path compensation deflection assembly, both frequency loading and optical path optical path are changed. Compared with the practice of using a motor to move the probe or relying on a servo mechanism that relies on high-speed rotation and precise deflection positioning to achieve frequency loading (another conceived solution of the inventor), the present invention can also avoid the use of frequency loading technology in the preview stage, reduce the demand for high sampling density, and effectively reduce the hardware cost of the OCT system. The system uses a shallow detection depth when measuring the cornea and retina, reducing the number of A-Scans required to be collected, which is not only conducive to quickly aligning the eye to be measured and finding the working position, but also improves the accuracy of the measurement. In addition, the present invention speeds up the scanning speed of switching between the front and rear segments, effectively avoiding the influence of eye movement on the measurement of axial length. After completing the corneal and retinal signal acquisition, the system can quickly switch to the panoramic OCT scanning mode of the anterior chamber and lens to achieve accurate measurement of depth and lens thickness. This design simplifies the hardware structure and reduces the requirements for the control accuracy of the rotating motor, while ensuring the detection accuracy and performance of the system and improving the cost performance of the system. By optimizing the optical path design and control mechanism, the present invention provides a cost-effective, easy-to-operate and accurate measurement ophthalmic OCT imaging solution, which effectively solves the limitations of traditional frequency domain systems in detection depth and meets the needs of clinical diagnosis.

[0025] Other beneficial effects of the embodiments of the present invention will be further described below. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] Figure 1 FIG. 4 is an optical path diagram of an OCT system according to an embodiment of the present invention.

[0027] Figure 2 This is a posterior segment OCT imaging system according to an embodiment of the present invention.

[0028] Figure 3 This is the corneal OCT scanning imaging of an embodiment of the present invention.

[0029] Figure 4 This is an anterior chamber OCT scanning imaging system according to an embodiment of the present invention.

[0030] Figure 5 This is a whole lens panoramic OCT scanning imaging system according to an embodiment of the present invention. DETAILED DESCRIPTION

[0031] The following is a detailed description of the embodiments of the present invention. It should be emphasized that the following description is only exemplary and is not intended to limit the scope and application of the present invention.

[0032] It should be noted that when an element is referred to as being "fixed to" or "disposed on" another element, it can be directly on the other element or indirectly on the other element. When an element is referred to as being "connected to" another element, it can be directly connected to the other element or indirectly connected to the other element. In addition, connection can be used for fixing as well as for coupling or communication.

[0033] It should be understood that the orientation or position relationship indicated by terms such as "length", "width", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside" and "outside" are based on the orientation or position relationship shown in the accompanying drawings, and are only for the convenience of describing the embodiments of the present invention and simplifying the description, and do not indicate or imply that the referred device or element must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as a limitation on the present invention.

[0034] In addition, the terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of the features. In the description of the embodiments of the present invention, the meaning of "plurality" is two or more, unless otherwise clearly and specifically defined.

[0035] See also Figures 1 to 5The embodiment of the present invention provides an ophthalmic measurement system with an optical path compensation deflection mechanism, including an OCT imaging module, the OCT imaging module including an OCT light source 1101, a reference arm module, an OCT sample arm module, a fiber coupler 1103 and a detector 1141, the OCT sample arm module including an optical path switching scanning device 1109, a posterior segment OCT sample arm optical path and an anterior segment OCT sample arm optical path, the detection light output by the fiber coupler 1103 is reflected by the optical path switching scanning device 1109 at different angles and enters the posterior segment OCT sample arm optical path or the anterior segment OCT sample arm optical path accordingly. arm optical path; it also includes an optical path compensation deflection mechanism 44, after the detection light passes through the optical path compensation deflection assembly 440, it enters the optical path switching scanning device 1109, the optical path compensation deflection mechanism 44 includes a rotating mechanism (such as a rotating motor 4405) and an optical path compensation deflection assembly 440, the optical path compensation deflection assembly 440 includes a deflection glass block 4401 and an optical path compensation glass block 4403; wherein, when the rotating mechanism drives the optical path compensation deflection assembly 440 to deflect to a set deflection angle, the detection light is deflected by the deflection glass block 4401, and a Doppler frequency shift is introduced when the incident light path switching scanning device 1109. In conjunction with the scanning of the optical path switching scanning device 1109, the optical path or phase change between adjacent A-Scans is kept constant, and the detection light does not pass through the optical path compensation glass block 4403. When the optical path compensation deflection assembly 440 is not deflected, the detection light passes through the deflection glass block 4401 and the optical path compensation glass block 4403, and no Doppler frequency shift is introduced.

[0036] like Figures 1 to 5 As shown, in a preferred embodiment, when the optical path compensation deflection assembly 440 is not deflected, the optical path compensation deflection assembly 440 is arranged parallel to the main optical axis of the detection light, and the detection light passes through the optical path compensation glass block 4403 and the deflection glass block 4401 at a vertical incident angle. When the optical path compensation deflection assembly 440 is deflected to the set deflection angle, the main optical axis of the detection light forms an angle with the optical path compensation deflection assembly 440, and the detection light passes through the deflection glass block 4401 at an inclined angle.

[0037] In a preferred embodiment, the optical path compensation deflection assembly 440 does not deflect when performing posterior segment and corneal OCT scanning imaging (see Figure 2 and Figure 3 ), the optical path compensation deflection assembly 440 is deflected to the set deflection angle (see Figure 4 and Figure 5 ).

[0038] The ophthalmic measurement system of the present invention realizes efficient and accurate imaging of different parts of the eye by introducing an optical path compensation deflection mechanism. The system can quickly switch between anterior and posterior segment OCT imaging, improve the detection range of the OCT system, while maintaining the stability and accurate positioning capability of the system, and does not affect the signal-to-noise ratio of the system. The optical path compensation deflection mechanism allows the light beam to be focused separately at different positions, providing high-quality imaging for human eyes with different vision, with high lateral resolution. The system can obtain a large number of human eye parameter data including corneal curvature, corneal thickness, anterior chamber depth, lens thickness, etc., and can focus separately on tissues at different depths such as the anterior chamber, lens and retina, thereby improving the signal-to-noise ratio and resolution of OCT detection. In addition, the system deepens the detection depth of the system while maintaining the detection resolution unchanged through innovative optical path design and control mechanism, combined with Doppler frequency shift technology, effectively solving the limitations of traditional frequency domain systems in terms of detection depth. This design not only improves the speed and accuracy of imaging, but also enhances the versatility of the system, enabling it to meet the diverse needs of clinical diagnosis. In summary, the present invention provides a cost-effective, easy-to-operate and precise ophthalmic OCT imaging solution by optimizing the optical path design and control mechanism, meeting the high standard requirements for ophthalmic disease diagnosis.

[0039] The ophthalmic measurement system of the present invention realizes both frequency loading and optical path change through the overall deflection of the optical path compensation deflection assembly. Compared with the practice of using a motor to move the probe or relying on a servo mechanism that relies on high-speed rotation and precise deflection positioning to achieve frequency loading, the present invention avoids the use of frequency loading technology in the preview stage, reduces the need for high sampling density, and effectively reduces the hardware cost of the OCT system. The system uses a shallow detection depth when measuring the cornea and retina, reducing the number of A-Scans required for collection, which is not only conducive to quickly aligning the eye to be measured and finding the working position, but also improves the accuracy of the measurement. In addition, the present invention speeds up the scanning speed of switching between the anterior and posterior segments, effectively avoiding the influence of eye movement on the measurement of axial length. After completing the corneal and retinal signal acquisition, the system can quickly switch to the panoramic OCT scanning mode of the anterior chamber and lens to achieve accurate measurement of the anterior chamber depth and lens thickness. This design simplifies the hardware structure and reduces the requirements for the control accuracy of the rotating motor, while ensuring the detection accuracy and performance of the system and improving the cost performance of the system.

[0040] The specific embodiments of the present invention are further described below.

[0041] Figure 1 Shown is an optical path diagram of an OCT system according to a specific embodiment.

[0042] Posterior Segment OCT Sample Arm Module

[0043] The posterior segment OCT imaging system of the embodiment is as follows Figure 2 shown.

[0044] The posterior segment of the eye sample arm module includes an optical path switching scanning device 1109, an optical path adjustment module 1301, a posterior segment of the eye and a gaze spectroscope 1303 (a first spectroscope 1303), a refraction adjustment device 1305, a third spectroscope 1307, a front spectroscope 1309 (a fifth spectroscope 1309), and an eye contact objective lens 1311. In this embodiment, the posterior segment of the eye sample arm module also includes an optical path compensation deflection mechanism 44. The optical path compensation deflection mechanism 44 is composed of a rotating motor 4405 and an optical path compensation deflection assembly 440. The optical path compensation deflection assembly 440 is composed of a deflection glass block 4401 and an optical path compensation glass block 4403.

[0045] When performing posterior segment OCT imaging, the light emitted from the collimator 1107 passes through the optical path compensation deflection assembly 440 and is reflected by the optical path switching scanning device 1109. At this time, the optical path switching scanning device 1109 is controlled by the computer 1143. After the light beam is reflected by the optical path switching scanning device 1109, it passes through the optical path adjustment module 1301, and then reflects by the posterior segment and the gaze beam splitter 1303 (the first beam splitter 1303), passes through the refractive adjustment device 1305, is reflected by the third beam splitter 1307, and then is reflected by the front beam splitter 1309 (the fifth beam splitter 1309) to the eye lens 1311, and finally passes through the human eye E to converge to the human eye fundus Er. The detection light beam of the posterior segment OCT imaging optical path system meets the requirement that the center line of the scanning light beam converges near the pupil of the human eye, and the OCT light beam is focused on the human eye fundus Er at any time.

[0046] The optical path compensation deflection assembly 440 is controlled by a rotating motor 4405 to be arranged parallel to the main optical axis L44. At this time, the posterior segment OCT scanning detection light passes through the deflection glass block 4401 and the optical path compensation glass block 4403.

[0047] Anterior Segment OCT Sample Arm Module

[0048] The anterior segment sample arm module includes an optical path switching scanning device 1109, a first reflector 1501, a first lens 1503, a third reflector 1505, a fifth reflector 1507, a third lens 1509, a third beam splitter 1307, a front beam splitter 1309 (fifth beam splitter 1309) and an eyepiece objective lens 1311. The anterior segment sample arm module also includes an anterior chamber insertion lens 3601 for measuring the anterior chamber of the eye and an optical path compensation deflection mechanism 44.

[0049] In this embodiment, the anterior segment OCT sample arm module can be used for corneal OCT scanning imaging, entire lens panoramic OCT scanning imaging and anterior segment OCT scanning imaging.

[0050] Corneal OCT scanning imaging

[0051] Corneal OCT scanning imaging of the embodiment Figure 3 shown.

[0052] When performing corneal OCT scanning imaging, the light emitted from the collimator 1107 passes through the optical path compensation deflection assembly 440 and is reflected by the optical path switching scanning device 1109. At this time, the optical path switching scanning device 1109 is controlled by the computer 1143. After being reflected by the optical path switching scanning device 1109, the light beam is successively reflected by the first reflector 1501, transmitted through the first lens 1503, and then reflected by the third reflector 1505, passed through the anterior chamber insertion lens 3601, and then reflected by the fifth reflector 1507, and then transmitted through the third lens 1509, transmitted through the third beam splitter 1307, and then reflected by the pre-beam splitter 1309 (fifth beam splitter 1309) to the eyepiece objective 1311, and finally converged to the human cornea through the human eye E. The detection light beam of the anterior segment OCT imaging optical path system satisfies the OCT light beam focusing on the human cornea.

[0053] The optical path switching scanning device 1109 is controlled by the computer 1143 and is in a position to realize anterior segment OCT imaging. At this time, the optical path switching scanning device 1109 is in a position that makes the angle between the main optical axis of the incident light from the collimator 1107 and the main optical axis of the reflected light be β.

[0054] In this embodiment, the anterior segment OCT sample arm module is preferentially used for corneal OCT scanning imaging. At this time, the insertion mirror of the shutter device for OCT imaging of different depth tissues of the anterior segment, the anterior chamber insertion mirror 3601, is inserted into the anterior segment OCT optical path. That is, when measuring corneal OCT scanning imaging, the detection light passes through the insertion mirror of the shutter device.

[0055] The optical path compensation deflection assembly 440 is controlled by a rotating motor 4405 to be arranged parallel to the main optical axis L44. At this time, the anterior segment OCT scanning detection light passes through the deflection glass block 4401 and the optical path compensation glass block 4403.

[0056] OCT scan of the anterior chamber

[0057] The anterior chamber OCT scanning imaging system of the embodiment is as follows Figure 4 shown.

[0058] When performing anterior chamber OCT scanning imaging, the anterior chamber OCT sample arm optical path also includes an optical path switching scanning device 1109, a first reflector 1501, a first lens 1503, a third reflector 1505, anterior chamber insertion mirror 3601 of a shutter device, a fifth reflector 1507, a third lens 1509, a third beam splitter 1307, a front beam splitter 1309 (fifth beam splitter 1309), an eyepiece objective lens 1311 and an optical path compensation deflection mechanism 44.

[0059] When performing an OCT scan of the anterior chamber of the eye, the light emitted from the collimator 1107 passes through the optical path compensation deflection assembly 440. At this time, the optical path compensation deflection assembly 440 is controlled by the rotating motor 4405 so that it is set to deflect at a specific angle relative to the main optical axis L44. The deflection angle causes the optical path compensation glass block 4403 to deflect out of the anterior chamber of the eye OCT detection light path, and allows the deflection glass block 4401 to rotate to the deflection angle. The deflection angle satisfies the requirement that the optical path or phase change between adjacent A-Scans remain constant during the OCT scan of the anterior chamber of the eye, so as to meet the requirements of the subsequent computer 1143 using the Doppler de-imaging algorithm. The deflection angle is related to the optical path parameters, the number and speed of A-Scans, etc. Then, the anterior chamber of the eye OCT detection light is reflected by the optical path switching scanning device 1109, and at this time, the optical path switching scanning device 1109 is controlled by the computer 1143. After being reflected by the optical path switching scanning device 1109, the light beam is successively reflected by the first reflector 1501, transmitted by the first lens 1503, and then reflected by the third reflector 1505, and passed through the anterior chamber insertion lens 3601 for measuring the anterior chamber, and then reflected by the fifth reflector 1507, and then transmitted through the third lens 1509, the third beam splitter 1307, and then reflected by the pre-beam splitter 1309 (fifth beam splitter 1309) to the eyepiece objective lens 1311, and finally converged to the vicinity of the center of the anterior chamber of the human eye through the human eye E. The detection light beam of the anterior chamber OCT scanning imaging optical path system satisfies the OCT light beam focusing near the center of the anterior chamber of the human eye.

[0060] At this time, the anterior chamber insertion mirror 3601 of the shutter device is inserted into the anterior chamber OCT optical path. That is, when the anterior chamber OCT scans the anterior chamber, the detection light passes through the anterior chamber insertion mirror 3601, but the optical path compensation deflection component 440 needs to be deflected at a specific angle. The optical path compensation glass block 4403 deflects the light path to meet the need for optical path matching when measuring the anterior chamber OCT.

[0061] Panoramic OCT scanning of the entire lens

[0062] The whole lens panoramic OCT scanning imaging system of the embodiment is as follows Figure 5 shown.

[0063] When performing panoramic OCT scanning imaging of the entire lens, the light emitted from the collimator 1107 passes through the optical path compensation deflection assembly 440. At this time, the optical path compensation deflection assembly 440 is controlled by the rotating motor 4405 so that it is set at a specific angle of deflection relative to the main optical axis L44. The deflection angle causes the optical path compensation glass block 4403 to deflect out of the anterior chamber OCT detection light path, and allows the deflection glass block 4401 to rotate to the deflection angle. The deflection angle satisfies the requirement that the optical path or phase change between adjacent A-Scans remains constant during the OCT scanning imaging of the anterior chamber, so as to meet the needs of the subsequent computer 1143 using the Doppler de-imaging algorithm. The deflection angle is related to the optical path parameters, the number and speed of A-Scans, etc. Then, the anterior chamber OCT detection light is reflected by the optical path switching scanning device 1109. At this time, the optical path switching scanning device 1109 is controlled by the computer 1143. After the light beam is reflected by the optical path switching scanning device 1109, it is successively reflected by the first reflector 1501, transmitted by the first lens 1503, and then reflected by the third reflector 1505 and the fifth reflector 1507, and then transmitted by the third lens 1509, the third beam splitter 1307, and then reflected by the front beam splitter 1309 (fifth beam splitter 1309) to the eyepiece objective lens 1311, and finally converged to the human eye lens through the human eye E. The detection light beam of the anterior chamber OCT imaging optical path system satisfies the OCT beam focusing on the human eye lens.

[0064] The optical path switching scanning device 1109 is controlled by the computer 1143 and is in a position to realize anterior segment OCT imaging. At this time, the optical path switching scanning device 1109 is in a position that makes the angle between the main optical axis of the incident light from the collimator 1107 and the main optical axis of the reflected light be β.

[0065] At this time, the insertion mirror of the shutter device for OCT imaging of different depth tissues in the anterior segment of the eye - the anterior chamber insertion mirror 3601 for measuring the eye, is in a state of leaving the anterior segment of the eye OCT optical path. That is, when measuring the panoramic OCT scanning imaging of the entire lens, the detection light does not pass through the insertion mirror of the shutter device, but the optical path compensation deflection assembly 440 still maintains a specific deflection angle. In addition, the anterior chamber insertion mirror 3601 for measuring the eye not only plays a role in adjusting the optical path, but also plays a role in changing the focusing position of the anterior segment of the eye OCT sample arm optical path. The position of its insertion is only schematically shown in the figure. In principle, it can be inserted into other positions of the anterior segment of the eye OCT sample arm optical path.

[0066] In summary, the present invention provides an ophthalmic measurement system, which achieves efficient and accurate imaging of different parts of the eye by introducing an optical path compensation deflection mechanism. Compared with the inventor's other scheme of increasing the detection depth of the OCT system through Doppler frequency shift technology, these schemes use a motor to drive the flat glass to rotate or deflect, and a servo mechanism to drive the fiber collimator and the sample arm fiber head to move horizontally, to dynamically adjust the optical path and keep the optical path change between adjacent OCT scans A-Scan constant. Although these methods can achieve deeper detection from the cornea to the back surface of the lens, they need to increase the number of spectrometer pixels or sampling points of the system, thereby increasing the hardware cost. In addition, in order to synthesize a single-frame OCT image, these schemes need to collect more A-Scans, which not only increases the acquisition speed requirements of the system, but may also cause freezes and eye movements during real-time preview and fast switching scans.

[0067] In contrast, the present invention does not introduce frequency loading technology in the preview stage, but uses an optical path compensation deflection mechanism to adopt a shallow detection depth when measuring the cornea (tissue thickness is about 0.5mm) and retina, reducing the number of A-Scans required for collection, thereby reducing the requirements for sampling density and hardware costs. The present invention also speeds up the scanning speed of switching between the anterior and posterior segments, effectively avoiding the influence of eye movement on the measurement, and can quickly switch to other scanning modes after completing the corneal and retinal signal collection, so as to achieve accurate measurement of depth and crystal thickness. This design simplifies the hardware structure and reduces the requirements for the control accuracy of the rotating motor, which can be achieved with only mechanical limiters. The required OCT system detection depth is shallow and the acquisition rate is relatively low. At the same time, the detection accuracy and performance of the system are guaranteed, and the cost performance of the system is improved. In general, the present invention provides an ophthalmic OCT imaging solution that is cost-effective, easy to operate and accurate in measurement by optimizing the optical path design and control mechanism.

[0068] The above content is a further detailed description of the present invention in combination with specific / preferred embodiments, and it cannot be determined that the specific implementation of the present invention is limited to these descriptions. For ordinary technicians in the technical field to which the present invention belongs, without departing from the concept of the present invention, it can also make several substitutions or modifications to these described embodiments, and these substitutions or modifications should be regarded as belonging to the protection scope of the present invention. In the description of this specification, the description of reference terms "an embodiment", "some embodiments", "preferred embodiments", "examples", "specific examples", or "some examples" means that the specific features, structures, materials or characteristics described in combination with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic representation of the above terms does not necessarily target the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described can be combined in any one or more embodiments or examples in a suitable manner. In the absence of mutual contradiction, those skilled in the art can combine and combine the different embodiments or examples described in this specification and the features of different embodiments or examples. Although the embodiments of the present invention and their advantages have been described in detail, it should be understood that various changes, substitutions and modifications can be made herein without departing from the scope of protection of the patent application.

Claims

1. An ophthalmic measurement system with an optical path compensation deflection mechanism, comprising an OCT imaging module, the OCT imaging module comprising an OCT light source, a reference arm module, an OCT sample arm module, a fiber coupler and a detector, the OCT sample arm module comprising an optical path switching scanning device, a posterior segment OCT sample arm optical path and an anterior segment OCT sample arm optical path, the detection light output by the fiber coupler is reflected at different angles by the optical path switching scanning device and then enters the posterior segment OCT sample arm optical path or the anterior segment OCT sample arm optical path respectively; characterized in that: It also includes an optical path compensation deflection mechanism, and the detection light enters the optical path switching scanning device after passing through the optical path compensation deflection assembly. The optical path compensation deflection mechanism includes a rotation mechanism and an optical path compensation deflection assembly; wherein, when the rotation mechanism drives the optical path compensation deflection assembly to deflect to a set deflection angle, the detection light passes through the optical path compensation deflection assembly and deviates from the scanning center of the optical path switching scanning device, thereby introducing a Doppler frequency shift, and in conjunction with the scanning of the optical path switching scanning device, the optical path or phase change between adjacent A-Scans remains constant, and when the optical path compensation deflection assembly is not deflected, the detection light passes through the optical path compensation deflection assembly and does not introduce a Doppler frequency shift.

2. The ophthalmic measurement system according to claim 1, wherein: The optical path compensation deflection assembly includes a deflection glass block and an optical path compensation glass block; wherein, when the rotating mechanism drives the optical path compensation deflection assembly to deflect to a set deflection angle, the detection light passes through the deflection glass block to generate a changed optical path, and the detection light does not pass through the optical path compensation glass block, and when the optical path compensation deflection assembly is not deflected, the detection light passes through the deflection glass block and the optical path compensation glass block.

3. The ophthalmic measurement system according to claim 1, wherein: The rotating mechanism is a rotating motor.

4. The ophthalmic measurement system according to claim 2, wherein: When the optical path compensation deflection assembly is not deflected, the optical path compensation deflection assembly is arranged parallel to the main optical axis of the detection light, and the detection light passes through the optical path compensation glass block and the deflection glass block at a vertical incident angle. When the optical path compensation deflection assembly is deflected to the set deflection angle, the main optical axis of the detection light forms an angle with the optical path compensation deflection assembly, and the detection light passes through the deflection glass block at an inclined angle.

5. The ophthalmic measurement system according to any one of claims 1 to 4, characterized in that: The optical path compensation deflection component does not deflect when performing OCT scanning imaging of the posterior segment of the eye and the cornea, and the optical path compensation deflection component deflects to the set deflection angle when performing panoramic OCT scanning imaging of the anterior chamber of the eye and the entire lens.

6. The ophthalmic measurement system according to any one of claims 1 to 5, characterized in that: The anterior chamber OCT sample arm optical path includes an anterior chamber insertion mirror, which is configured to cut in or out of the optical path; the anterior chamber insertion mirror is designed to guide the detection light beam to focus near the center of the anterior chamber of the eye when performing anterior chamber OCT scanning imaging; when performing panoramic OCT scanning imaging of the entire lens, the anterior chamber insertion mirror is in a cut-out state.

7. The ophthalmic measurement system according to claim 6, wherein: The optical path of the anterior segment OCT sample arm includes a first reflector, a first lens, a third reflector, a fifth reflector, a third lens, a third beam splitter, a front beam splitter and an eyepiece objective lens. After the light beam is reflected by the optical path switching scanning device, it is successively reflected by the first reflector, transmitted by the first lens, and then reflected by the third reflector and the fifth reflector, and then transmitted by the third lens, the third beam splitter, and then reflected by the front beam splitter to the eyepiece objective lens, and finally converged to the anterior segment of the human eye through the human eye; The anterior chamber insertion lens can be inserted into the optical path of the anterior segment OCT sample arm.

8. The ophthalmic measurement system according to any one of claims 1 to 7, characterized in that: The optical path of the posterior segment OCT sample arm includes a light path module, a posterior segment and a gaze beam splitter, a refractive adjustment device, a third beam splitter, a front beam splitter and an eyepiece objective lens in sequence. After the light beam is reflected by the optical path switching scanning device, it passes through the light path module, and then is reflected by the posterior segment and the gaze beam splitter, passes through the refractive adjustment device, is reflected by the third beam splitter, and then is reflected by the front beam splitter to the eyepiece objective lens, and finally passes through the human eye to converge to the fundus of the human eye.

9. The ophthalmic measurement system according to any one of claims 1 to 8, characterized in that: Also included is a computer connected to the detector, which processes the interference signal introduced with the Doppler frequency shift and uses a de-imaging algorithm to obtain an OCT image using positive and negative frequency image data.

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