CN112168131B - Wearable optical coherence in-vivo cornea elasticity measurement system - Google Patents
Wearable optical coherence in-vivo cornea elasticity measurement system Download PDFInfo
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- CN112168131B CN112168131B CN202011101491.0A CN202011101491A CN112168131B CN 112168131 B CN112168131 B CN 112168131B CN 202011101491 A CN202011101491 A CN 202011101491A CN 112168131 B CN112168131 B CN 112168131B
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- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/102—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for optical coherence tomography [OCT]
Abstract
The invention discloses a wearable optical coherence in vivo corneal elasticity measuring system, which comprises an OCT system, measuring glasses, an excitation air source, a processing module and a control module, wherein the OCT system consists of a low coherence light source, an optical fiber coupler, a sampling module, a reference arm and a sample arm in the measuring glasses; the optical fiber of the sample arm is externally connected to the mirror frame; the optical fiber coupler is respectively connected with the low-coherence light source, the sampling module, the reference arm and the measuring glasses; the measuring glasses are provided with a left glass frame, a right glass frame and a sliding module, the sliding module can move back and forth from the left glass frame and the right glass frame, and a pupil camera, a micro stepping motor, a conducting optical fiber, an exciting tube and a gas valve are arranged inside the sliding module. The sampling module obtains feedback information of the corneal vibration, and the processing module obtains the feedback information of the corneal vibration through the sampling module and calculates elastic parameters capable of representing the biomechanical property of the cornea. The system is mainly used in the technical field of optical measuring instruments.
Description
Technical Field
The invention relates to the technical field of optical measurement instruments, in particular to a wearable optical coherence in-vivo corneal elasticity measurement system.
Background
Optical coherence elastography is a novel optical technology for quantifying biomechanical characteristics of soft tissues, and can realize non-contact in-vivo corneal elastography measurement. The conventional OCE system adopts a method of multiple excitation and multiple detection to splice the elastic response of each measuring point of a sample, thereby estimating the propagation speed of mechanical waves and obtaining the elastic modulus of each measuring point. With the development of a multi-probe beam OCT system, elastic responses of a plurality of measurement positions of a corneal excitation point under single excitation can be rapidly and simultaneously measured without galvanometer scanning, and in-vivo measurement of a plurality of elastic parameters of the corneal measurement position is realized.
The Common-path OCE system adopts a structure that a detection light path and a reference light path are Common, and further improves the displacement sensitivity and the optical phase stability of dynamic elastography (from Common-path-sensitive optical coherence enhanced phase stability and detection sensitivity for dynamic elastography). Due to the research, the complexity, the volume and the weight of an OCE system are greatly reduced, and the wearable optical coherence in-vivo corneal elasticity measurement is possible.
The wearable system existing in the industry at that time is generally an ultrasonic wearable system, obtains related information in eyeball tissues by utilizing the reflection characteristic of ultrasonic waves, and has the advantages of high portability, simple and convenient operation and small occupied space. However, the ultrasonic imaging technology has the problems of overlong scanning time, low resolution and the like, and the accuracy and stability of the system are not high, so that a system with high accuracy and stability is urgently needed in the industry.
Disclosure of Invention
It is an object of the present invention to provide a wearable optical coherence in vivo corneal elasticity measurement system, which solves one or more of the technical problems of the prior art, and at least provides a useful choice or creation.
The solution of the invention for solving the technical problem is as follows: a wearable optical coherence in vivo corneal elasticity measuring system comprises an OCT system, measuring glasses, an excitation air source, a processing module and a control module, wherein the OCT system consists of a low coherence light source, a fiber coupler, a sampling module, a reference arm and a sample arm in the measuring glasses; the optical fiber of the sample arm is externally connected to the mirror frame; the optical fiber coupler is respectively connected with the low-coherence light source, the sampling module, the reference arm and the measuring glasses; the sampling module obtains feedback information of the corneal vibration, and the processing module obtains the feedback information of the corneal vibration through the sampling module and calculates elastic parameters capable of representing the biomechanical property of the cornea.
Further, the measuring glasses are provided with a left glass frame, a right glass frame and a sliding module, the sliding module can move back and forth from the left glass frame and the right glass frame, a pupil camera, a micro stepping motor, a conduction optical fiber, an exciting tube and a gas valve are arranged inside the sliding module, the pupil camera is used for achieving positioning of human eyes based on pupils, the micro stepping motor is connected with the conduction optical fiber, one end of the conduction optical fiber faces towards the cornea, the other end of the conduction optical fiber is connected with an optical fiber coupler, one end of the exciting tube is connected with an exciting gas source through the gas valve, and the control module is connected with the gas valve and the micro stepping motor respectively and used for controlling the gas valve to enable the exciting tube to generate micro gas pulses to enable the cornea to deform.
Further, the control module gives an electric signal to control the micro stepping motor to drive the conducting optical fiber and/or the exciting tube to generate gas pulse on a preset measuring point and scan the gas pulse, and the scanning mode comprises the following steps: any one of a linear scan, a cross scan, a circular scan, a spiral scan, or a square scan.
Furthermore, elastic parameters of the biomechanical property of the cornea comprise the hardness degree, the Young modulus, the natural frequency and the elastic hysteresis, wherein the elastic hysteresis can be quantified by calculating the area of a curve according to a stress and strain closed curve in the loading and unloading processes; fitting a cornea recovery curve into an exponential decay curve to indirectly measure the natural frequency, and obtaining the natural frequency by adopting Fast Fourier Transform (FFT) according to damping vibration; the young's modulus can be obtained from a stress/strain curve, a propagation model of mechanical waves.
Further, the excitation tube is perpendicular to the corneal surface, and generates stimulation with local diameter of 50 μm-1mm and low pressure of 0-100Pa, the duration of each gas pulse is 0.5ms-20ms, and the pressure of the gas pulse is 0-100 Pa.
Further, the gas pulse excitation acts on the cornea, so that the cornea is subjected to sub-nanometer to micron-scale micro deformation.
Furthermore, the measuring glasses further comprise a sliding track, the sliding track penetrates through the left glass frame and the right glass frame and is connected with a buckle, and the buckle can fix the sliding module.
The invention has the beneficial effects that: the wearable optical coherence in-vivo corneal elasticity measuring system comprises an OCT system, measuring glasses, an excitation air source, a processing module and a control module, wherein the OCT system consists of a low coherence light source, a fiber coupler, a sampling module, a reference arm and a sample arm in the measuring glasses; the optical fiber of the sample arm is externally connected to the mirror frame; the optical fiber coupler is respectively connected with the low-coherence light source, the sampling module, the reference arm and the measuring glasses; the sampling module obtains feedback information of the corneal vibration, and the processing module obtains the feedback information of the corneal vibration through the sampling module and calculates elastic parameters capable of representing the biomechanical property of the cornea.
Wearable measurement is realized on the elastic parameters of the cornea. Meanwhile, the wearable measurement enables the axial distance of the eye to be unchanged, so that the local vibration influence caused by the surrounding environment or slight movement and the like between the eye and the measurement system is reduced, and the physical stability and the optical phase sensitivity of the system are improved.
Drawings
In order to more clearly illustrate the technical solution in the embodiments of the present invention, the drawings used in the description of the embodiments will be briefly described below. It is clear that the described figures are only some embodiments of the invention, not all embodiments, and that a person skilled in the art can also derive other designs and figures from them without inventive effort.
FIG. 1 is a system block diagram of the present measurement system;
FIG. 2 is a schematic view of the structure of the measurement glasses;
fig. 3 is a schematic view of the internal structure of the slide module;
fig. 4 is a schematic diagram of the trace of the micro-motion stepper motor driving the conducting optical fiber and/or the exciting tube to scan at the preset measuring point.
Detailed Description
The conception, the specific structure and the technical effects produced by the present invention will be clearly and completely described in conjunction with the embodiments and the attached drawings, so as to fully understand the objects, the features and the effects of the present invention. It is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all embodiments, and other embodiments obtained by those skilled in the art without inventive efforts are within the protection scope of the present invention based on the embodiments of the present invention. In addition, all the coupling/connection relationships mentioned herein do not mean that the components are directly connected, but mean that a better coupling structure can be formed by adding or reducing coupling accessories according to specific implementation conditions. All technical characteristics in the invention can be interactively combined on the premise of not conflicting with each other.
Embodiment 1, referring to fig. 1, 2 and 3, a wearable optical coherence in vivo corneal elasticity measurement system comprises an OCT system, a measurement glasses 100, an excitation gas source, a processing module and a control module, wherein the OCT system is composed of a low coherence light source, a fiber coupler, a sampling module, a reference arm and a sample arm in the measurement glasses, the measurement glasses are provided with a left frame 110, a right frame 120 and a sliding module 200, the sliding module 200 can move back and forth from the left frame and the right frame, the sliding module 200 is internally provided with a pupil camera 240, a micro-motion stepper motor 210, a conducting fiber 220, a gas valve 250 and an excitation tube 230, the pupil camera 240 is used for realizing pupil-based human eye positioning, and the control module is respectively connected with the gas valve 250 and the micro-motion stepper motor 210.
The micro-motion stepping motor 210 is connected with a conducting optical fiber 220, one end of the exciting tube 230 is connected with an exciting gas source through a gas valve 250, one end of the conducting optical fiber 220 faces the cornea, the other end of the conducting optical fiber is connected with a fiber coupler, and the control module respectively controls the gas valve 250 and the micro-motion stepping motor 210. Wherein, the gas valve 250 can make the exciting tube 230 generate micro gas pulse to stimulate the cornea to generate vibration; the micro-stepping motor 210 drives the conducting fiber 220 and/or the exciting tube 230 to scan at a predetermined measuring point, wherein the scanning comprises: linear scan, cross scan, circular scan, helical scan, or square scan. Referring to fig. 4, a track of linear scanning, a track of cross scanning, a track of circular scanning, a track of spiral scanning, and a track of square scanning are sequentially provided from left to right. Then the reflected light of the reference arm and the measuring glasses generates interference in the optical fiber coupler, the reflected light is received by the sampling module and converted into an electric signal to be transmitted to the processing module, a mechanical wave propagation model of the corneal vibration is obtained, and the elastic parameters of the cornea are calculated.
The elastic parameters comprise soft and hard degrees, elastic hysteresis, natural frequency, Young modulus and the like. In some preferred embodiments, the specific method for obtaining the softness and hardness degree includes: and calculating the phase to obtain the displacement of each measuring point of the cornea under the excitation. Surface deformation information Δ z (t)J-t0) (in air):
phase change delta phiz(tJ-t0)，tJAnd t0Is a time node, t0Is a reference time point, λ0Is the center wavelength. Similarly, the phase change and surface deformation information of each measuring point can be obtained, and the amplitude of the main deformation is directly influenced by the excitation load. Relatively hard corneas deform less under the same driving force; while the primary deformations of equal magnitude decay more rapidly in a relatively hard cornea. The degree of softness or hardness of the cornea can therefore be determined by the magnitude of the main deformation.
In some preferred embodiments, the present system can also measure the elastic hysteresis of the cornea: specifically, a pressure sensor is adopted to quantify the pressure change in the loading and unloading processes of the gas pulse, and an OCE is used to measure a time-deformation curve of a sample in the loading process and a time-recovery curve in the unloading process under the same pressure. The deformation amplitude decreases with increasing distance and there is a delay in the phase signal. A second order fourier curve fit is performed on the "time-deformation" curve and the "time-recovery" curve. The 'time-pressure' curve of the pulse is combined with the 'time-deformation' curve of the sample, the 'time' parameter is removed, a 'force-displacement' closed curve of the sample in the loading and unloading processes is drawn, and the area of the curve is calculated to quantify the elastic hysteresis.
In some preferred embodiments, the system can derive the natural frequency of the cornea from the interference signal. Specifically, (1) the recovery curve of the cornea is measured and the recovery curve is fitted to an exponential decay curve, and the method for indirectly measuring the natural frequency is as follows: the recovery curve is related to the viscoelasticity (viscoelasticity) of the cornea, and can be fitted into an exponential attenuation curve according to a dynamic model (the dynamic model is described in Wu C.etc. IOVS.2015,56(2): 1292-1300), so as to realize indirect measurement of the natural frequency, wherein a differential equation of stimulated damping vibration of the cornea is obtained according to the exponential attenuation curve, and the natural frequency of the cornea is obtained by solving the differential equation, wherein the differential equation is as follows:
where ξ is the damping ratio, f is the natural frequency, and y (t) is the exponential decay curve. The solution to the differential equation of the stimulated damping vibration of the cornea can be solved according to three conditions, which are respectively: critical damping (ξ ═ 1), under-damping (0 ≦ ξ <1), and over-damping (ξ > 1).
Where the amplitude constants a and B are derived from an exponential fit of the recovery curve.
(2) The method for obtaining the natural frequency of the cornea by performing high-resolution detection and Fast Fourier Transform (FFT) on the stimulated damping vibration of the cornea comprises the following steps: the vertical air pulse stimulation induces submicron to sub-nanometer oscillations in the cornea, which are observed with the present system. The natural frequency and damping ratio are obtained in the time domain and the frequency domain using a single degree of freedom (SDOF) model to quantify tissue vibration dynamics.
Wherein the damping characteristics and the oscillation frequency can be calculated from the damped oscillation and the damping envelope can be expressed as
Where A is the attenuation amplitude, t1For the time of maximum occurrence of A, B is the attenuation coefficient (B ═ 2 π fnζ). Zero padding (Zeropadding) the data before the FFT can improve the frequency resolution: within the sampling time of OCT (e.g., 30ms), the damped vibration amplitude of the cornea will gradually go to zero (the sampling time is too short, and substantially no response is seen), expanding the sampling time. Then, the oscillation frequency was analyzed by the FFT method with a frequency resolution of 2 hz. According to the main damping frequency fdFitted a and B values, estimate the damping ratio ζ. When ζ is very small, the formula
Obtaining the natural frequency fnApproximately equal to the damping natural frequency fd。
In some preferred embodiments, the specific method for obtaining the young's modulus includes: (1) the linear relationship between stress (sigma, force per unit area) and strain (epsilon, proportional deformation) is used to calculate
Wherein σ ═ F/a, a is the cross-sectional area of the sample, F is the force applied to the sample; and epsilon is delta L/L, wherein delta L is the length change, and L is the initial length of the sample in the corresponding direction.
(2) The analysis of the information obtained from the sampling module allows to obtain a model of the propagation of mechanical waves, where shear waves are the elastic waves most commonly used in soft tissue elastic performance measurements, preferably by estimating the young's modulus (E) of a homogeneous isotropic sample from shear:
where ρ is the sample density, V is the poisson's ratio (generally assuming V is 0.5), VSIs the shear wave velocity.
With respect to how the sliding module 200 can move back and forth between the left frame 110 and the right frame 120, in some preferred embodiments, the wearable optical coherence in vivo corneal elasticity measurement system further includes a sliding rail 300, the sliding rail 300 is connected with a buckle 400, the sliding rail 300 passes through the left frame 110 and the right frame 120, and the sliding module 200 can be fixed by the buckle 400. The sliding module 200 is moved left and right along the sliding track 300 and then fixed by the ring buckle 400, so that the measurement switching from the left eye cornea to the right eye cornea can be realized, and the measurement is very convenient.
In some preferred embodiments, the excitation tube is perpendicular to the corneal surface and generates a stimulus with a local diameter of 50 μm to 1mm and a low pressure of 0 to 100Pa, each gas pulse has a duration of 0.5ms to 20ms and a gas pressure of 0 to 100Pa, and the cornea is slightly deformed in a sub-nanometer to micron scale.
While the preferred embodiments of the present invention have been illustrated and described, it will be understood by those skilled in the art that the present invention is not limited to the details of the embodiments shown and described, but is capable of numerous modifications and substitutions without departing from the spirit of the present invention and within the scope of the appended claims.
Claims (6)
1. A wearable optical coherence in vivo cornea elasticity measurement system is characterized in that: the device comprises an OCT system, measuring glasses, an excitation gas source, a processing module and a control module, wherein the OCT system consists of a low-coherence light source, an optical fiber coupler, a sampling module, a reference arm and a sample arm in the measuring glasses; the optical fiber of the sample arm is externally connected to the mirror frame; the optical fiber coupler is respectively connected with the low-coherence light source, the sampling module, the reference arm and the measuring glasses; the sampling module obtains feedback information of corneal vibration, and the processing module obtains the feedback information of corneal vibration through the sampling module and calculates elastic parameters capable of representing corneal biomechanical properties; the measuring glasses are provided with a left glass frame, a right glass frame and a sliding module, the sliding module can move back and forth from the left glass frame and the right glass frame, a pupil camera, a micro stepping motor, a conduction optical fiber, an excitation tube and a gas valve are arranged inside the sliding module, the pupil camera is used for achieving eye positioning based on the pupil, the micro stepping motor is connected with the conduction optical fiber, one end of the conduction optical fiber faces towards the cornea, the other end of the conduction optical fiber is connected with an optical fiber coupler, one end of the excitation tube is connected with an excitation gas source through the gas valve, and the control module is connected with the gas valve and the micro stepping motor respectively and used for controlling the gas valve to enable the excitation tube to generate micro gas pulses to enable the cornea to deform.
2. The wearable optical coherence in-vivo corneal elasticity measurement system according to claim 1, wherein: the control module gives an electric signal to control the micro-motion stepper motor to drive the conducting optical fiber and/or the exciting tube to generate gas pulse on a preset measuring point and carry out scanning, and the scanning mode comprises the following steps: any one of a linear scan, a cross scan, a circular scan, a spiral scan, or a square scan.
3. The wearable optical coherence in-vivo corneal elasticity measurement system according to claim 1, wherein: elastic parameters of the corneal biomechanical property comprise the hardness degree, the Young modulus, the natural frequency and the elastic hysteresis, wherein the elastic hysteresis can be quantified by calculating the area of a curve according to a stress and strain closed curve in the loading and unloading processes; fitting a cornea recovery curve into an exponential decay curve to indirectly measure the natural frequency, and obtaining the natural frequency by adopting Fast Fourier Transform (FFT) according to damping vibration; young's modulus can be obtained from stress/strain curves, propagation models of mechanical waves.
4. The wearable optical coherence in-vivo corneal elasticity measurement system according to claim 1, wherein: the exciting tube is perpendicular to the surface of the cornea and generates stimulation with the local diameter of 50 mu m-1mm and the low pressure of 0-100Pa, the duration of each gas pulse is 0.5ms-20ms, and the gas pressure of the gas pulse is 0-100 Pa.
5. The wearable optical coherence in-vivo corneal elasticity measurement system according to claim 2, wherein: the gas pulse excitation acts on the cornea, so that it produces micro-deformations on the sub-nanometer to micrometer scale.
6. The wearable optical coherence in-vivo corneal elasticity measurement system according to claim 1, wherein: the measuring glasses further comprise a sliding track, the sliding track penetrates through the left glass frame and the right glass frame and is connected with a buckle, and the buckle can fix the sliding module.
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| CN204909384U (en) * | 2015-07-06 | 2015-12-30 | 殷昭云 | Eyesight verifying attachment |
| JP2020515368A (en) * | 2017-04-03 | 2020-05-28 | ホーガン，ジョシュア，ノエル | Home Monitoring Optical Coherence Tomography System |
| CN109620130A (en) * | 2018-12-14 | 2019-04-16 | 佛山科学技术学院 | A kind of the multiple beam optical coherence elasticity measurement system and measurement method of optical path altogether |
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