CN119073899A

CN119073899A - Ophthalmic testing device

Info

Publication number: CN119073899A
Application number: CN202411234740.1A
Authority: CN
Inventors: 王立峰; 蔡勇
Original assignee: Shanghai Aikangte Medical Technology Co ltd
Current assignee: Shanghai Aikangte Medical Technology Co ltd
Priority date: 2024-09-04
Filing date: 2024-09-04
Publication date: 2024-12-06

Abstract

The present disclosure relates to a sample arm module and an ophthalmic detection device, wherein the sample arm module includes an image sensor, an imaging lens unit, a first filter, a second filter, a focusing lens unit, a first collimator, and an illumination unit. The image sensor, the imaging lens unit, the first filter, and the second filter are sequentially arranged on a first optical path. The first collimator, the focusing lens unit, and the second filter are sequentially arranged on a second optical path. The thickness and arrangement direction of the first filter and/or the second filter are configured such that only when the first optical path coincides with the eye axis of the target eye, the image sensor can capture a ghost image, and the light does not shift or deflect after passing through the first filter and the second filter. With the help of this special ghost image, it is easy for people to align the ophthalmic detection device with the target eye.

Description

Ophthalmic testing device

Technical Field

The present disclosure relates to the field of optical devices, and more particularly, to an ophthalmic testing device and a sample arm module thereof.

Background

In the current information age, with the development of electronic products, people are more and more separated from the electronic products. People communicate with people, entertain, learn, etc. by means of electronic products. The proportion of people with overuse eyes is increasing. With the consequent occurrence of various ophthalmic diseases.

In order to detect problems in terms of myopia and the like in advance, so as to perform interventional treatment or slow down disease progression, various biological parameters of human eyes, such as the length of an eye axis, the thickness of a cornea and the like, need to be detected.

The principles of recent ocular axis biological parameter measuring instruments are roughly divided into two categories, one employing a partially coherent interference technique (Partial Coherence Interferometer, PCI) and the other employing a weak coherent reflectometry technique (Low Coherence Reflectometry, LCR). The eye axis length is measured by using an instrument of PCI technology, the Anterior Chamber Depth (ACD) is measured by using an optical interferometry technology, the corneal curvature is measured by using a traditional geometrical optical method integrated in the instrument, and the eye biological parameters can be measured by one scan by using an instrument of LCR technology, and the interference peak positions of the anterior and posterior surfaces of the cornea, the anterior and posterior surfaces of the crystal and the anterior and posterior surfaces of the retina are measured by using an optical weak coherence reflectometry technology principle, so that the thicknesses of the eye axis, the anterior chamber, the crystal and the vitreous body are obtained. Compared with the traditional ultrasonic A ultrasonic, the instrument adopting the optical interference technology has the advantages of non-contact measurement, high measurement precision (10 um, ultrasonic 100 um), automatic alignment and the like. However, the parameters measured at one time by the instrument adopting the PCI technology are few, even if the parameters of the eyeball are measured by other means, the thicknesses of the crystal and the vitreous body cannot be measured, and the biological parameters of the eyeball can be measured at one time by the instrument adopting the LCR technology. However, for instruments employing LCR techniques, there are often various uncertainties as to how the optical path of the sample arm module is aligned with the human eye's eye axis.

BRIEF SUMMARY OF THE PRESENT DISCLOSURE

In view of the above-described state of the art in various ophthalmic test devices, it is an object of the present disclosure to provide an ophthalmic test device and a sample arm module capable of simply aligning a sample arm optical path with an eye axis of an eye to be tested.

This object is achieved by disclosing a sample arm module and a corresponding ophthalmic testing device of the following form. The sample arm module comprises an image sensor, an imaging lens unit, a first optical filter, a second optical filter, a focusing lens unit, a first collimator and an illumination unit for illuminating a target eye, wherein the image sensor, the imaging lens unit, the first optical filter and the second optical filter are sequentially arranged on a first light path, the first collimator, the focusing lens unit and the second optical filter are sequentially arranged on a second light path, the image sensor is used for imaging reflected light from the target eye, the second optical filter is a dichroic optical filter for respectively splitting the reflected light from the target eye to the first optical filter and the focusing lens unit,

The thickness and the arrangement direction of the first optical filter and/or the second optical filter are configured so that the image sensor can collect ghost only when the first optical path is coincident with the eye axis of the target eye, and the light rays do not deviate or deflect after passing through the first optical filter and the second optical filter.

Preferably, the thickness and arrangement direction of the first filter and/or the second filter are configured such that, when the first optical path coincides with the axis of the target eye, there are at least 2 ghosts within the cornea of the target eye in the image acquired by the image sensor.

Preferably, the ghost is formed in a lower half region of the image or in upper and lower half regions of the image.

Preferably, the at least 2 ghosts are located in the same radial direction through the pupil center.

Preferably, the first filter and the second filter are parallel or perpendicular to each other.

Preferably, the thickness of the second filter is taken from any value in the range of 1mm-3 mm.

Preferably, the first filter is a dichroic filter.

Preferably, the thickness of the second filter is inversely related to the refractive index of the second filter and the magnification of the imaging lens unit.

In addition, the present disclosure relates to an ophthalmic testing device for testing biological parameters of a target eye, wherein the ophthalmic testing device comprises:

The detection module comprises a detection light source, a balance detector and an optical fiber module, wherein detection light provided by the detection light source is split into the downstream through the optical fiber module;

A reference arm module configured to adjust a reference optical path;

A sample arm module, the sample arm module being any of the above, and

A zero-point arm module configured to adjust a zero point of the ophthalmic testing device in a Z-axis direction,

Wherein the reference arm module, the sample arm module and the zero point arm module receive the detection light through the optical fiber module,

The reference light path signal passing through the reference arm module and the sample light path signal passing through the sample arm module enter the balance detector after being in interference coupling with the optical fiber module, and the balance detector generates biological parameters of the target eye.

Preferably, the detection light source is a weak coherent light source with a wavelength taken from 800nm to 1800 nm.

On the basis of the common general knowledge in the field, the above preferred embodiments can be arbitrarily combined to obtain each preferred example of the disclosure.

Unlike the previous approach intended to eliminate ghosts, in the sample arm module/ophthalmic testing device of the present disclosure, special ghosts are intentionally formed. The ghost image is formed only when the optical path of the sample arm module and the eye axis of the eye to be inspected are in the same direction. By means of this special ghost one can easily obtain centering of the ophthalmic testing device to the eye axis of the subject.

Drawings

For a better understanding of the above and other objects, features, advantages and functions of the present disclosure, reference should be made to the preferred embodiments illustrated in the accompanying drawings. Like reference numerals refer to like parts throughout the drawings. It will be appreciated by those skilled in the art that the drawings are intended to schematically illustrate preferred embodiments of the present disclosure, and that the scope of the present disclosure is not limited in any way, and that the various components in the drawings are not drawn to scale.

Fig. 1 is a schematic structural view of a sample arm module of an ophthalmic testing device according to a first preferred embodiment of the present disclosure.

Fig. 2 (a), 2 (b) are schematic diagrams showing the partial light path of the sample arm module of fig. 1 of the present disclosure.

Fig. 3 is a schematic diagram of the principle of the disappearance of the ghost in the eye image corresponding to the sample arm module of fig. 1.

Fig. 4 is a schematic diagram of the sample arm module corresponding to fig. 1, when ghosting occurs in an image of an eye to be inspected.

Fig. 5 is an image of an eye to be inspected acquired by the image sensor without the first filter.

Fig. 6 is an image acquired by the image sensor after the first optical path of the sample arm module of fig. 1 is centered with the eye axis of the eye being inspected.

Fig. 7 is a schematic structural view of a sample arm module of an ophthalmic testing device according to a second preferred embodiment of the present disclosure.

Fig. 8 is an image acquired by the image sensor after the first optical path corresponding to the sample arm module of fig. 7 is centered with the eye axis of the eye being inspected.

Fig. 9 is a schematic structural view of an ophthalmic testing device equipped with the sample arm module shown in fig. 1.

Detailed Description

The disclosed concept of the present disclosure will be described in detail with reference to the accompanying drawings. What has been described herein is merely a preferred embodiment according to the present disclosure, and other ways of enabling the present disclosure based on the preferred embodiment will occur to those skilled in the art, which also fall within the scope of the present disclosure. In the following detailed description, directional terms, such as "upper", "lower", "inner", "outer", "longitudinal", "transverse", etc., are used with reference to the directions described in the drawings. The components of the embodiments of the present disclosure can be positioned in a number of different orientations and the directional terminology is used for purposes of illustration and is in no way limiting.

Herein, both the "target eye" and the "subject eye" denote the same object, i.e., the eye of the subject (subject). The target eye and the eye to be inspected may be represented as eyeballs of real world animals and humans, and may be represented as simulated eyes and eye models.

Herein, "shifting" of the optical paths means that the optical paths are shifted, and the shifted optical paths are parallel to each other as compared to the previous optical paths. "deflection" of the optical path means that the optical path is deflected and rotated.

Referring to fig. 1, a sample arm module 10 according to a first embodiment of the present disclosure includes an image sensor 11, an imaging lens unit 12, a first filter 13, a second filter 14, a focusing lens unit 15, a first collimator 16, an illumination unit 17 for illuminating a target eye E, and the like. Wherein the image sensor 11, the imaging lens unit 12, the first filter 13, and the second filter 14 are sequentially arranged on the first optical path. The first collimator 16, the focusing lens unit 15, and the second filter 14 are sequentially disposed on the second optical path. The image sensor 11 is used to image reflected light from the target eye, which is in fact a monitoring camera. The combination of the image sensor 11 and the imaging lens unit 12 is used to ensure that an image is acquired on the image sensor 11.

The first filter 13 of the sample arm module 10 may optionally be a dichroic filter or other optical element for adjusting the optical path of the light beam incident from the second filter 14.

The second filter 14 of the sample arm module 10 is a dichroic filter that splits reflected light from a target eye (i.e., an "eye to be inspected") to the first filter 13 and the focusing lens unit 15, respectively.

The first optical path of the sample arm module 10 serves as an observation branch that serves to confirm whether the ophthalmic testing device 100 is aligned with the eye axis of the target eye. The second optical path of the sample arm module 10 acts as an interference branch for providing a sample optical path signal that feeds back the biological parameters of the target eye. The function of the second optical path is not obviously related to the purpose of "how to center the ophthalmic testing device to the eye axis of the target eye" in the present invention, and will not be described herein.

The illumination unit 17 of the sample arm module 10 is typically an illumination unit consisting of a multi-ring point light source. The illumination unit 17 illuminates the target eye and feeds back a plurality of annular shadows S3 in the image acquired by the image sensor 11 (see fig. 5, 6, 8). These annular shadows S3 provide a preliminary reference for an operator to adjust the centering operation of the ophthalmic testing device 100.

In operating the ophthalmic detection apparatus 100, the operator judges whether or not the positional relationship between the eyes of the subject and the ophthalmic detection apparatus 100 is accurate by observing the real-time image provided by the image sensor 11 (monitoring camera). In the case where the relationship between the two is inaccurate, the operator adjusts by remotely or manually operating the upper, lower, left, right, front, and rear spatial positions of the ophthalmic detection apparatus 100.

In the present application, the core of the operator's judgment as to whether the positional relationship between the subject's eye and the ophthalmic detection apparatus 100 is accurate is to ensure that the ophthalmic detection apparatus 100 satisfies that at least one of the first filter 13 and the second filter 14 on the sample arm module 10 is configured so that the image sensor 11 can acquire the ghost only when the first optical path coincides with the axis of the target eye. This can be achieved by setting the thickness, arrangement direction, and the like of at least one of the first filter 13 and the second filter 14.

The following description of the sample arm module 10 in conjunction with fig. 2-4 provides an eye axis alignment mechanism for the ophthalmic test device 100 and the subject. Referring first to fig. 2 (a), the dashed portion of the figure is shown as the first optical path. In the state shown in fig. 2 (a), the first optical path of the sample arm module 10 is aligned with the eye axis direction of the target eye E/the eye E to be inspected. As is clear from fig. 2 (a), when only the second filter 14 for light splitting is provided and the first filter 13 is not provided, the first optical path is significantly deflected after passing through the second filter 14, and the entire first optical path is deflected (the deflection τ is shown in fig. 2 (a)). As can be seen from the schematic view of the optical path in fig. 2 (a), in the state shown in fig. 2 (a), the operator acquires fraudulent information, that is, information of "the ophthalmic detection device and the eye axis are centered at this time", from the image acquired by the image sensor 11. When the optical path of the eye to be inspected through the second filter 14 in fig. 2 (a) is in the same direction as the eye axis of the eye to be inspected, the information obtained from the image sensor 14 by the operator is "the ophthalmic detection device is not aligned with the eye axis at this time". Obviously, in this case, the operator cannot distinguish the true and accurate condition of whether the ophthalmic test device is centered on the eye axis.

Next, referring to fig. 2 (b), in the case where the first filter 13 is provided near the image sensor 11 side of the second filter 14, the ophthalmic detecting apparatus 100 can correct the judgment error caused by the above-described optical path shift. Specifically, referring to fig. 2 (b), after the light passes through the adjusting unit of the first filter 13 and the second filter 14, deflection and offset alignment have been achieved. That is, the light is not deflected or deviated before and after passing through the adjusting unit composed of the first filter 13 and the second filter 14.

Referring to fig. 3 and 4, in conjunction with fig. 2 (b), the process of forming the ghost image is illustrated. Referring to fig. 3, when the light of the first optical path deflects in the direction of the eye axis of the target eye (deflects in the direction of the X-axis or the Y-axis), the light of the first optical path cannot return in the original path after being reflected by the target eye. Instead, the reflected light is deflected at an angle with respect to the first optical path (see the reflected light indicated by the arrow obliquely upward and leftward in fig. 3). The image sensor 11 will not be able to obtain a ghost image.

Referring to fig. 4, when the light of the first optical path is aligned with the eye axis direction (i.e., Z direction) of the target eye, the light is reflected by the target eye and returns to the second optical filter 14. The light rays are refracted when entering the second optical filter 14, and different light rays are reflected in the second optical filter 14 for different times and then are emitted out of the light emitting surface of the second optical filter 14. Because the reflection times of the light rays of different groups on the second optical filter 14 are different, the light rays of different groups form mutually parallel light beams which are mutually spaced after exiting from the second optical filter 14. Three different light beams are schematically indicated in fig. 4 in three colors green, red and dark green. As will be understood from fig. 4 and fig. 2 (b), the light beams after exiting from the second filter 14 are aligned by the optical path of the first filter 13, and finally imaged as different ghosts S1 on the image sensor 11. It will be appreciated that the sample arm spot real image S2 (see schematic illustrations in fig. 5-6, 8) is ultimately formed corresponding to the light beam identified as blue in fig. 4 (i.e., the light beam that is not reflected within the second filter 14 but is directed out of the light exit face).

Besides the purpose of correcting the optical path offset of the second optical filter 14, the first optical filter 13 can better inhibit the brightness of the light source returned to the image sensor 11 by the target eye, and the measurement efficiency and the repeatability, consistency and stability of the test data are improved.

Preferably, the first filter 13 and/or the second filter 14 are configured such that, when the first optical path coincides with the axis of the target eye, there are at least 2 ghosts S1 (2 ghosts S1 are shown in fig. 6) within the cornea of the target eye in the image acquired by the image sensor 11. In general, the number of the above-described ghosts S1 can be adjusted by setting the thickness, refractive index, and the like of the second filter 14.

In the embodiment of fig. 1, the ghosts S1 are imaged on the upper half and the lower half of the image acquired by the image sensor 11, more specifically, on the upper and lower sides of the pupil center S2 (i.e., the sample arm flare real image S2) of the target eye, respectively. The two ghosts S1 lie in the same radial direction through the pupil center. In this example, the image formed when the ophthalmic detection device 100 is centered on the target eye axis can be seen in fig. 6.

In this example, the arrangement direction of the second filter 14 is set to form an angle of 45 ° with the incident optical axis (first optical path). In the example of fig. 1, the first filter 13 and the second filter 14 form an angle of 90 °. The first optical filter 13 and the second optical filter 14 are made of the same film material, and the thicknesses of the first optical filter and the second optical filter are the same. For example, in one example, the first filter 13 and the second filter 14 are made of an N-BK7 glass material having a thickness of 2mm and a refractive index of 1.51680 at 587.5618nm (yellow helium line).

The first filter 13 does not necessarily use the same physical parameters as the second filter 14 under the condition that the above correction of the light deflection caused by the second filter 14 is satisfied.

The thickness of the second filter 14 may be set according to the refractive index of itself, the magnification of the imaging lens unit 12. The thickness of the second filter 14 may be taken from any value in the range of 1mm-3mm, such as 1.5mm, 2mm, 2.5mm, etc. According to the present application, the thickness t of the second filter 14 is determined based on the following formula:

In the formula, t represents the thickness of the second optical filter 14, r represents the minimum distance between the ghost image of the image sensor 11 and the flare real image of the sample arm module, i.e., the distance between the flare real image of the sample arm module and the nearest ghost image, n represents the refractive index of the second optical filter 14, and β represents the magnification of the imaging lens unit 12.

In the above formula of t, the minimum distance r between the ghost image of the image sensor 11 and the real image of the spot of the sample arm can be set manually to ensure that the ghost image does not interfere with the real image of the spot of the sample arm (the image formed by the annular bright spots in fig. 5, 6, 8). In addition, the value of t should not be too large to avoid the second optical filter 14 from causing larger optical aberration in the first optical path of the sample arm module 10, deteriorating the imaging quality of the image sensor 11, and simultaneously reducing the alignment accuracy of the human eye in the Z direction, greatly reducing the device performance. According to the t value obtained by calculation, the value of the t value is ensured to be within the range of 1mm-3mm as much as possible.

Looking at fig. 5 and 6, when the first optical path of the ophthalmic detection apparatus 100 is not aligned with the eye axis, the image acquired by the image sensor 11 is shown in fig. 5, and the image includes only the sample arm flare real image S2 located at the center of the pupil and the illumination flare located at the same radial distance from the sample arm flare real image S3. Referring to fig. 6, in the case that the first optical path of the ophthalmic detecting apparatus 100 is aligned with the eye axis, in the image collected by the image sensor 11, in addition to the various light spots S3 and the real image S2 shown in fig. 5, there are 2 ghosts on the upper and lower sides of the central sample arm light spot real image S2. The line connecting the two ghosts passes through the real image S2 of the spot of the sample arm, namely the two ghosts S1 are located in the same radial direction.

Referring to fig. 7, another sample arm module 10 according to the present disclosure is shown. Unlike the corresponding sample arm module 10 of fig. 1-6, in this example the first filter 13 is arranged parallel to the second filter 14. Parameters such as the thickness of the first filter 13 of this embodiment can be designed as described above with reference to the examples of fig. 1 to 6.

After the first filter 13 of the type shown in fig. 7 is provided, the image acquired by the image sensor 11 is as shown in fig. 8 when the first optical path has been aligned with the eye axis of the target eye and in alignment with each other. In fig. 8, 4 ghosts S1 can be observed. The ghosts S1 at these 4 are in the same radial direction and are all below the sample arm spot real image S2.

Referring to fig. 9, a schematic diagram of the overall structure of an ophthalmic testing device 100 employing the sample arm module 10 of fig. 1 is shown. The ophthalmic testing device 100 is used for biological parameters of a target eye, such as corneal curvature, ocular axis length, and the like. As shown in fig. 9, the ophthalmic testing device 100 includes a detection module 40, a reference arm module 20, a sample arm module 10, and a zero-point arm module 30. The detection module 40 includes a detection light source 41, a balance detector 42, and a fiber optic module 50. The detection light provided by the detection light source 41 is split downstream via the fiber optic module 50. The fiber optic module 50 is the fiber optic module 50 of 3*3 in the example of fig. 9. The probe light source 41 enters the fiber optic module 50 via one port and enters the reference arm module 20, the sample arm module 10 and the zero-point arm module 30 via three ports of the outlet end, respectively.

The reference arm module 20 is used to adjust the reference optical path. In the example of fig. 9, the reference arm module 20 includes a polarization controller 21, a second collimator 22, a first corner cube 23, a second corner cube 24, and a first mirror 25 (plane mirror) disposed in this order on the optical path thereof. The first corner cube prism 23 is disposed opposite the second corner cube prism 24. The reference arm module 20 further includes a drive mechanism 26 for adjusting the first axicon 23. In the example of fig. 9, the drive mechanism 26 includes a voice coil motor 26A and a grating scale 26B. The voice coil motor 26A drives the first pyramid prism 23 to move in a direction toward or away from the second pyramid prism 24, and the grating scale 26B provides a reference for the movement amount of the voice coil motor 26A. In addition, the voice coil motor 26A in the driving mechanism 26 may alternatively be designed to drive the second corner cube 24, or to drive the first corner cube 23 and the second corner cube 24 to move, so that the reference optical path length of the reference arm module 20 is adjusted as needed.

The signal from the optical fiber module 50 enters the second collimator 22 through an optical fiber connector after passing through the polarization controller 21, the collimated optical path signal enters the first pyramid prism 23, is reflected to the second pyramid prism 24 by the first pyramid prism 23, is reflected to the first pyramid prism 23, and is finally reflected to the first reflecting mirror 25. The first mirror 25 reflects the optical path signal, which is then routed back to the fiber optic module 50.

The zero-point arm module 30 includes a third collimator 31 and a second mirror 32 (planar mirror). The zero-point arm module 30 adjusts the distance between the second reflecting mirror 32 and the third collimator 31, so that the interference signal generated by the zero-point arm module 30 and the reference arm module 20 is located at the front end of the interference signal generated by the cornea of the eye to be inspected on the sample arm module 10 and the reference arm module, thereby serving as a zero point (zero plane) of the ophthalmic detection device 100 in the Z-axis direction.

The optical path signal is collimated by the third collimator 31 on the zero-point arm module 30 and then projected to the second reflector 32, and then reflected by the second reflector 32, and the optical path signal is returned to the optical path module.

In the sample arm module 10, the optical path signal sequentially passes through the first collimator 16, the focusing lens unit 15 and the second optical filter 14 to enter the human eye, and then is reflected by the human eye to return to the optical fiber module 50.

The reference optical path signal via the reference arm module 20 and the sample optical path signal via the sample arm module 10 are interference coupled by the optical fiber module 50 and then enter the balance detector 42, and the biological parameters of the target eye are generated by the balance detector 42.

For the ophthalmic testing device 100 shown in fig. 9, the detection light source 41 is preferably a weak coherent light source, the wavelength of which can be set in the range of 800nm to 1800 nm.

The scope of protection of the present disclosure is limited only by the claims. Those skilled in the art, having the benefit of the teachings of this disclosure, will readily recognize alternative constructions to the disclosed structures as viable alternative embodiments, and may combine the disclosed embodiments to create new embodiments that fall within the scope of the appended claims. Description of the drawings:

An ophthalmic testing device 100. Sample arm module 10. Image sensor 11. Imaging lens unit 12.

A first filter 13.

And a second filter 14. And a focusing lens unit 15. First collimator 16. And a lighting unit 17.

Reference arm module 20. A first filter 13. And a second filter 14. And a focusing lens unit 15.

First collimator 16. And a lighting unit 17.

Reference arm module 20. Polarization controller 21.

A second collimator 22.

A first angular cone prism 23.

And a second corner cube 24.

A first mirror 25. And a driving mechanism 26.

Voice coil motor 26A. And 26B of grating ruler.

Zero point arm module 30.

And a third collimator 31.

Second mirror 32. And a detection module 40. The detection light source 41. Balance detector 42. Fiber optic module 50.

Claims

1. A sample arm module of an ophthalmic detection device, the sample arm module comprising an image sensor, an imaging lens unit, a first filter, a second filter, a focusing lens unit, a first collimator, and an illumination unit for illuminating a target eye, wherein the image sensor, the imaging lens unit, the first filter, and the second filter are sequentially arranged on a first optical path, the first collimator, the focusing lens unit, and the second filter are sequentially arranged on a second optical path, the image sensor is used to image reflected light from the target eye, the second filter is a dichroic filter to split the reflected light from the target eye to the first filter and the focusing lens unit, respectively.

The thickness and arrangement direction of the first filter and/or the second filter are configured so that the image sensor can capture ghost images only when the first optical path coincides with the eye axis of the target eye, and the light does not shift or deflect after passing through the first filter and the second filter.

2. The sample arm module according to claim 1, wherein the thickness and arrangement direction of the first filter and/or the second filter are configured so that when the first optical path coincides with the eye axis of the target eye, there are at least two ghost images within the cornea of the target eye in the image captured by the image sensor.

3 . The sample arm module according to claim 2 , wherein the ghost is formed in a lower half of the image, or in an upper half and a lower half of the image.

4 . The sample arm module according to claim 3 , wherein the at least two ghost images are located on the same radial direction passing through the center of the pupil.

5. The sample arm module according to any one of claims 1 to 4, wherein the first filter and the second filter are parallel to each other or form an angle of 90°.

6 . The sample arm module according to claim 5 , wherein the thickness of the second filter is any value within the range of 1 mm to 3 mm.

The sample arm module according to claim 5 , wherein the first filter is a dichroic filter.

8 . The sample arm module according to claim 6 , wherein a thickness of the second filter is negatively correlated with its own refractive index and a magnification of the imaging lens unit.

9. An ophthalmic detection device for detecting biological parameters of a target eye, characterized in that the ophthalmic detection device comprises:

A detection module, the detection module comprising a detection light source, a balanced detector and an optical fiber module, the detection light provided by the detection light source is split to the downstream via the optical fiber module;

A reference arm module, wherein the reference arm module is configured to adjust a reference optical path;

A sample arm module, wherein the sample arm module is the sample arm module according to any one of claims 1 to 8; and

a zero point arm module, wherein the zero point arm module is configured to adjust the zero point of the ophthalmic detection device in the Z-axis direction,

The reference arm module, the sample arm module, and the zero arm module receive the detection light through the optical fiber module.

The reference optical path signal via the reference arm module and the sample optical path signal via the sample arm module enter the balanced detector after interference coupling in the optical fiber module, and the biological parameters of the target eye are generated by the balanced detector.

10 . The ophthalmological detection device according to claim 9 , wherein the detection light source is a weak coherent light source with a wavelength of 800 nm-1800 nm.