CN209733949U - An optical coherence tomography system for measuring eye pulsations - Google Patents

Abstract

The utility model provides an optical coherence tomography system for measuring eyeball pulsation, which at least includes the following modules: a light source module; an optical fiber coupler; a reference arm module, which reflects the incoming light beam and returns it to the optical fiber coupler; a sample arm module, It is used to focus part of the incoming light to the fundus to generate backscattered light, and focus the remaining incoming light beam to the center of the cornea, and interfere to output the first interference light; the backscattered light enters the fiber coupler and reflects light from the reference arm When interference occurs, the second interference light is output; the spectrometer module is used to receive the interference light and output it. The optical coherence tomography imaging system of the utility model can present the fundus choroid and cornea at the same time, so as to intuitively calculate the pulsation of the fundus choroid, and provide a new observation method for judging fundus diseases.

Description

An optical coherence tomography system for measuring eye pulsations

technical field

The utility model belongs to the technical field of optical detection, in particular to an optical coherence tomography system for measuring eyeball pulsation.

Background technique

Optical coherence tomography (OCT) is a non-destructive optical inspection technology developed in the 1990s. It is based on the optical signal delay and phase change measurement system of the optical low-coherence interferometer, and indirectly measures the backscattering and reflection signals at different depths inside the sample. Signals with different contrasts are generated according to the different refractive indices inside the sample, so as to realize the imaging of the cross-section of the sample. According to the indirect delay and phase measurement of the scattered light of the sample, it can be divided into time-domain OCT, Doppler OCT, spectral OCT, etc. Among them, since the spectral OCT is not suitable for mechanical scanning components for axial depth scanning, the layered information of the axial direction of the sample can be obtained directly through the Fourier transform of the spectrum, so the imaging speed of the system can be greatly improved, and the mechanical movement of the scanning structure can be avoided. introduced noise. At the same time, the wavelength used by spectral OCT has extremely little absorption by water molecules, and thus has achieved great success in the fields of ophthalmic medical treatment and diagnosis.

However, although the spectral OCT system provided by the prior art can already be used for the measurement and imaging of tissues such as the retina and cornea, due to the influence of eyeball movement, this system cannot be directly applied to the measurement field of eyeball pulse movement, making a series of fundus Disease diagnosis and measurement methods have been greatly restricted and limited.

Contents of the invention

The purpose of the utility model is to provide an optical coherence tomography system for measuring eyeball pulsation, intuitively calculate the pulsation of the fundus choroid, and provide an observation method for judging fundus diseases.

In order to achieve the above-mentioned technical purpose, the technical scheme of the utility model is as follows:

An optical coherence tomography system for measuring eye pulsation, at least including the following modules:

a light source module, configured to provide initial light;

A fiber optic coupler is used to split the initial light into two and enter the reference arm module and the sample arm module respectively;

The reference arm module is used to reflect the incoming beam into the fiber coupler;

The sample arm module is used to focus part of the incoming light beam to the fundus choroid layer to generate backscattered light, and focus the remaining part of the incoming light beam to the center of the cornea, and interfere at the center of the cornea to output the first interference light; The scattered light entering the fiber coupler interferes with the reflected light of the reference arm module, and outputs the second interference light;

and a spectrometer module, configured to receive the first interference light and the second interference light, and split the first interference light and the second interference light according to wavelengths to output.

The optical coherence tomography system provided by the utility model has the following beneficial effects:

1. The optical coherence tomography system of the present invention can present the fundus choroid and cornea at the same time, thereby intuitively calculating the pulsation of the fundus choroid, and providing a new observation method for judging fundus diseases;

2. Since the utility model utilizes the principle of self-coherent interference to realize the measurement of the anterior segment, the observation method of the disease is more convenient and intuitive;

3. Simultaneously image the cornea and the fundus choroid layer, distinguish the eye movement from the fundus choroid layer pulsation, and better solve the interference problem of eye movement on the fundus choroid pulsation measurement.

Preferably, the light source module selects a broadband light source, the central wavelength of the primary light is 840nm, and the bandwidth is 49nm.

Specifically, the reference arm module further includes a first collimating lens and a reflector, and the first collimating lens collimates the incoming light beam into parallel light and then enters the reflector to output reflected light.

Specifically, in the optical coherence tomography system, the sample arm module includes a second collimating lens, a first focusing lens, an X scanning galvanometer, a second focusing lens, and a third focusing lens, and the first The focusing lens is a focusing lens with a hole in the middle; the incoming light beam is collimated by the second collimator lens into parallel light and then enters the first focusing lens with a hole in the middle, and part of the light beam passes through the hole and then enters the X-scan in parallel In the vibrating mirror, the X scanning vibrating mirror reflects the part of the light beam to the second focusing lens, and after passing through the third focusing lens, it is focused to the fundus choroid layer to generate backscattered light; the remaining part of the light beam is scanned by the X The vibrating mirror is focused to the center of the vibrating mirror, and after being reflected by the X scanning vibrating mirror, it is focused to the center of the cornea through the second focusing lens and the third focusing lens in sequence.

Specifically, the spectrometer module includes a third collimating lens, a grating, a fourth focusing lens, and a camera. The first interference light and the second interference light are collimated by the third collimating lens and split by the grating according to wavelengths, and finally received by the camera.

As a preferred manner, the space diameter of the middle hole of the first focusing lens is 1.5 mm, the focal length of the second focusing lens is 80 mm, the focal length of the third focusing lens is 46 mm, and the focal length of the fourth focusing lens is 60mm.

As a preferred manner, the grating is a 1800-line grating.

As a preferred mode, the camera is a high-speed scanning line scan camera e2v with a maximum line rate of 150KHZ.

In order to analyze the first interference light and the second interference light, the optical coherence tomography system further includes a processing module, the processing module is configured to receive the data of the first interference light and the second interference light, and perform Images of the first interference light and the second interference light are acquired after analysis and processing. For example, the processing module may be an electronic device such as a computer.

Since the fundus blood flow originates from the beating of the heart, in order to simultaneously measure the heart pulse motion and eyeball pulsation, the optical coherence tomography system also includes a finger blood oxygen detector, and the finger blood sample detector is connected with the optical coherence tomography The system measures the measured object at the same time, and is used to record the pulse rate and eyeball pulse rate at the same time, so that the fundus pulsation law can be combined with the pulse rate measurement of the human body, which is beneficial to the judgment and diagnosis of fundus diseases.

Description of drawings

FIG. 1 is a schematic structural diagram of an optical coherence tomography system for measuring ocular pulsations provided by Embodiment 1 of the present invention.

Detailed ways

The technical scheme of the utility model will be described in detail below in conjunction with the accompanying drawings and specific embodiments.

Example 1

Referring to Figure 1, an optical coherence tomography system for measuring ocular pulsations includes the following modules:

The light source module SLD is used to provide initial light; the light source module selects a broadband light source, the central wavelength of the initial light is 840nm, and the bandwidth is 49nm.

The fiber optic coupler FOC is used to split the initial light into two and enter the reference arm module and the sample arm module respectively; the coupler is a coupler with a splitting ratio of 50/50.

The reference arm module is used to reflect the incoming light beam into the fiber coupler to form reflected light; the reference arm module includes a first collimating lens CL1 and a mirror F, and the first collimating lens CL1 collimates the incoming light beam After being straightened into parallel light, it enters the mirror F, outputs the reflected light, and returns to the fiber coupler FOC.

The sample arm module is used to focus part of the incoming light beam to the fundus choroid layer to generate backscattered light, and focus the remaining part of the incoming light beam to the center of the cornea, and interfere at the center of the cornea to output the first interference light; The scattered light enters the fiber coupler FOC and interferes with the reflected light of the reference arm module to output the second interference light; the sample arm module includes the second collimating lens CL2, the first focusing lens FL1, the X scanning galvanometer S, the second The second focusing lens FL2, and the third focusing lens FL3, the first focusing lens FL1 is a focusing lens with a hole in the middle; the incoming light beam is collimated by the second collimating lens CL2 into parallel light and then enters the first focusing lens with a hole in the middle In the lens FL1, part of the light beam passes through the hole and then enters the X scanning galvanometer S in parallel, and the X scanning galvanometer S reflects the part of the light beam to the second focusing lens FL2, and then focuses it to The choroid layer of the fundus produces backscattered light; the remaining part of the beam is focused by the X scanning galvanometer S to the center of the galvanometer, reflected by the X scanning galvanometer S, and then focused to the center of the cornea through the second focusing lens FL2 and the third focusing lens FL4 . The cornea is similar to a layer of thin film. When light is incident on the center of the cornea vertically, the light reflected by the upper and lower layers of the cornea can produce interference, thus outputting the first interference light.

and a spectrometer module, configured to receive the first interference light and the second interference light, and split the first interference light and the second interference light according to wavelengths to output. The spectrometer module includes a third collimating lens CL3, a grating G, a fourth focusing lens FL4, and a camera. The first interference light and the second interference light formed are collimated by the third collimating lens CL3 and split by the grating G according to the wavelength. After the fourth focusing lens FL4, it is received by the camera C.

Wherein, the space diameter of the middle hole of the first focusing lens FL1 is 1.5mm, the focal length of the second focusing lens FL2 is 80mm, the focal length of the third focusing lens FL3 is 46mm, and the focal length of the fourth focusing lens FL4 is 60mm; The grating G is 1800 line raster; camera C is a high-speed scanning line scan camera e2v, the highest line rate is 150KHZ.

In order to analyze the first interference light and the second interference light, the optical coherence tomography system further includes a processing module, the processing module is configured to receive the data of the first interference light and the second interference light, and perform Images of the first interference light and the second interference light are acquired after analysis and processing. For example, the processing module may be an electronic device such as a computer.

Since the fundus blood flow originates from the beating of the heart, in order to simultaneously measure the heart pulse motion and eyeball pulsation, the optical coherence tomography system also includes a finger blood oxygen detector, and the finger blood sample detector is connected with the optical coherence tomography The system measures the measured object at the same time, and is used to record the pulse rate and eyeball pulse rate at the same time, so that the fundus pulsation law can be combined with the pulse rate measurement of the human body, which is beneficial to the judgment and diagnosis of fundus diseases.

The optical coherence tomography system provided in Embodiment 1 has the following beneficial effects:

1. The optical coherence tomography system of the present invention can present the fundus choroid and cornea at the same time, thereby intuitively calculating the pulsation of the fundus choroid, and providing a new observation method for judging fundus diseases;

2. Since the utility model utilizes the principle of self-coherent interference to realize the measurement of the anterior segment, the observation method of the disease is more convenient and intuitive;

3. Simultaneously image the cornea and the fundus choroid layer, distinguish the eye movement from the fundus choroid layer pulsation, and better solve the interference problem of eye movement on the fundus choroid pulsation measurement.

According to the disclosure and teaching of the above specification, those skilled in the art to which the present utility model belongs can also change and modify the above embodiment. Therefore, the utility model is not limited to the specific implementation manners disclosed and described above, and some modifications and changes to the utility model should also fall within the scope of protection of the claims of the utility model. In addition, although some specific terms are used in this specification, these terms are only for convenience of description and do not constitute any limitation to the present utility model.

Claims (10)

1. an optical coherence tomography system for measuring the pulsation of an eye, characterized in that it comprises at least the following modules:

A light source module for providing primary light;

The optical fiber coupler is used for dividing the initial light into two parts which respectively enter the reference arm module and the sample arm module;

the reference arm module is used for reflecting the entering light beam and then entering the optical fiber coupler;

The sample arm module is used for focusing part of the entered light beams to the fundus choroid layer to generate back scattered light, focusing the rest of the entered light beams to the center of the cornea, interfering the light beams at the center of the cornea and outputting first interference light; the backward scattering light enters the optical fiber coupler to interfere with the reflected light of the reference arm module, and second interference light is output;

And the spectrometer module is used for receiving the first interference light and the second interference light, splitting the first interference light and the second interference light according to wavelength and outputting the split light.

2. The optical coherence tomography system of claim 1, wherein the light source module selects a broadband light source, the initial light has a central wavelength of 840nm and a bandwidth of 49 nm.

3. The optical coherence tomography system of claim 1, wherein the reference arm module further comprises a first collimating lens and a mirror, wherein the first collimating lens collimates the incoming beam into parallel light and then injects the parallel light into the mirror, and outputs the reflected light.

4. the optical coherence tomography system of claim 3, wherein the sample arm module comprises a second collimating lens, a first focusing lens, an X-scan galvanometer, a second focusing lens, and a third focusing lens, the first focusing lens is a middle aperture focusing lens;

the light beam enters the first focusing lens with a hole in the middle after being collimated into parallel light by a second collimating lens, part of the light beam passes through the hole and then enters an X-ray scanning galvanometer in parallel, the X-ray scanning galvanometer reflects the part of the light beam to the second focusing lens, and the light beam is focused to the fundus choroid layer through the third focusing lens to generate backward scattered light; and the rest part of light beams are focused to the center of the galvanometer by the X scanning galvanometer, and are focused to the center of the cornea after being reflected by the X scanning galvanometer through a second focusing lens and a third focusing lens in sequence.

5. the optical coherence tomography system of claim 4, wherein the spectrometer module comprises a third collimating lens, a grating, a fourth focusing lens and a camera, and the first interference light and the second interference light are collimated by the third collimating lens, split by the grating according to wavelength, and finally received by the camera.

6. The optical coherence tomography system of claim 5, wherein the spatial diameter of the central aperture of the first focusing lens is 1.5mm, the focal length of the second focusing lens is 80mm, the focal length of the third focusing lens is 46mm, and the focal length of the fourth focusing lens is 60 mm.

7. The optical coherence tomography system of claim 6, wherein the grating is an 1800 line grating.

8. The optical coherence tomography system of claim 6, wherein the camera is a high speed scanning line camera e2v with a maximum line speed of 150 KHZ.

9. The optical coherence tomography system of claim 1, further comprising a processing module, wherein the processing module is configured to receive data of the first interference light and the second interference light, and to obtain images of the first interference light and the second interference light after analyzing and processing the data.

10. The optical coherence tomography system of any one of claims 1-9, further comprising a finger blood oxygen detector, wherein the finger blood detector measures the subject simultaneously with the optical coherence tomography system.