CN213525084U

CN213525084U - Ophthalmologic measuring system

Info

Publication number: CN213525084U
Application number: CN202020735168.8U
Authority: CN
Inventors: 王辉; 蔡守东; 吴蕾
Original assignee: Shenzhen Certainn Technology Co Ltd
Current assignee: Ganzhou Silton Medical Technology Co ltd; Shenzhen Moting Medical Technology Co ltd
Priority date: 2020-05-07
Filing date: 2020-05-07
Publication date: 2021-06-25
Anticipated expiration: 2030-05-07

Abstract

The embodiment of the application discloses ophthalmology measurement system includes: the device comprises a main body module, a light path switching and scanning device, a light path motion switching device, an anterior segment OCT light path component and a posterior segment OCT light path component; the main body module is used for providing measuring light for the optical path switching scanning device; the optical path switching scanning device is used for transmitting the measuring light to the anterior segment OCT optical path component or the posterior segment OCT optical path component; the optical path motion switching device is used for switching to a first state through motion so as to enable the measurement light from the anterior segment OCT optical path component to be transmitted to the anterior segment of the human eye and switching to a second state so as to enable the measurement light from the posterior segment OCT optical path component to be transmitted to the posterior segment of the human eye. The signal to noise ratio of the anterior segment and the posterior segment of the eye measured by the OCT can be improved.

Description

Ophthalmologic measuring system

Technical Field

The application relates to the technical field of ophthalmologic measurement, in particular to an ophthalmologic measurement system.

Background

Nowadays, the number of the elderly suffering from cataract is increasing, and the transplantation of the intraocular lens is an effective scheme for treating cataract which is widely used at present. However, the calculation of the intraocular lens requires many parameters, such as the anterior and posterior surface curvatures of the cornea, the thickness of the cornea, the anterior chamber depth, the thickness of the lens, the anterior and posterior surface curvatures of the lens, the axial length of the eye, the white-to-white distance, the diameter of the pupil, and the like. The measured parameters are more, but the complete data can be obtained after the detection of various medical devices is often needed. Therefore, if one device can be realized, the medical device which can obtain the data can improve the convenience of measurement and the accuracy of measurement for the detection of the patient.

Optical Coherence Tomography (OCT) is a new Optical imaging technique, and has the advantages of high resolution, fast imaging speed, no radiation damage, moderate price, compact structure and the like compared with the traditional clinical imaging means, and is an important potential tool for basic medical research and clinical diagnosis application. Currently, among a variety of ophthalmic apparatuses using an optical instrument, an OCT device for ophthalmic examination and treatment has become an indispensable ophthalmic apparatus for ophthalmic disease diagnosis.

Some previous technologies usually adopt time-domain tomography technology for measuring the axial length, but the speed is low and the measurement accuracy is not high.

Chinese patent application No. 200710020707.9 discloses a measurement method for measuring the axial length of an eye by using OCT. Although this method can realize the measurement of the length of the eye axis of human eyes and various living animals, the method has the following two problems:

1. the moving probe of the stepping motor is adopted to realize the adjustment of the optical path, thereby realizing the imaging of the cornea and the eyeground; the motor needs a certain time to move back and forth, the quick switching of the front section and the rear section and real-time imaging cannot be realized, and the eye of the measured object shakes, so that the measured eye axis length is inaccurate, and the error is large;

2. due to the different structures of the cornea and the fundus, the same probe cannot focus at the two positions, so that the imaging quality is poor, which cannot be avoided by the method.

The chinese patent application No. 201290000031.1 patent document "an ophthalmic optical coherence tomography system" employs a plurality of switching mechanisms, and the cost of the apparatus is high.

The chinese patent application No. 201410214827.2 discloses an OCT system and method for measuring an optical path length of an eye, which introduces a corneal position alignment technique, without switching between anterior and posterior segments, but without anterior segment measurement function and corneal curvature measurement function (or not mentioned). The cornea measurement is performed once more. Rapid diagnosis of the patient cannot be achieved.

The chinese patent application No. 201810130278.9, "ophthalmologic measurement system and method", uses a fixed beam splitter with partial beam splitting function, which results in a decrease in signal-to-noise ratio during OCT imaging of anterior and posterior segments.

The 'ophthalmologic measurement system' in chinese patent application No. 201920204215.3 adopts a fixed beam splitter with partial beam splitting function, which results in a decrease in signal-to-noise ratio during anterior-posterior segment OCT imaging.

The above background disclosure is only for the purpose of assisting in understanding the inventive concepts and technical solutions of the present application and does not necessarily pertain to the prior art of the present application, and should not be used to assess the novelty and inventive step of the present application in the absence of explicit evidence to suggest that such matter has been disclosed at the filing date of the present application.

SUMMERY OF THE UTILITY MODEL

The application provides an ophthalmology measurement system, can improve OCT and measure the SNR of anterior segment of eye and posterior segment of eye.

An ophthalmic measurement system comprising: the device comprises a main body module, a light path switching and scanning device, a light path motion switching device, an anterior segment OCT light path component and a posterior segment OCT light path component;

the main body module is used for providing measuring light for the optical path switching scanning device;

the optical path switching scanning device is used for transmitting the measuring light to the anterior segment OCT optical path component or the posterior segment OCT optical path component;

the optical path movement switching device is used for switching to a first state through movement so as to enable the measurement light from the anterior segment OCT optical path component to be transmitted to the anterior segment of the human eye and switching to a second state so as to enable the measurement light from the posterior segment OCT optical path component to be transmitted to the posterior segment of the human eye

In some preferred embodiments, the optical path moving and switching device is configured to switch the first state and the second state by moving at least a part of the optical path to switch the optical path.

In some preferred embodiments, the optical path movement switching device includes a driving part and an optical part; the drive member is used to move the optical member.

In some preferred embodiments, the optical component is a spectroscopic component.

In some preferred embodiments, the optical component includes a transmissive region and a reflective region.

In some preferred embodiments, the driving member is configured to rotate the optical member so that the optical member is rotated to a position where the transmissive region transmits light in the first direction and to a position where the reflective region reflects light in the second direction.

In some preferred embodiments, the optical component is a mirror; the driving component is used for moving the reflecting mirror to a first position to irradiate the light in the first direction to the human eye anterior segment, and is used for moving the reflecting mirror to a second position inserted into the optical path of the posterior segment OCT optical path component to reflect the light in the second direction to the human eye posterior segment.

In some preferred embodiments, further comprising a fixation optical assembly; the optical path movement switching device is used for switching to a first state or a second state through movement so as to enable the light from the fixation optical component to be transmitted to human eyes.

In some preferred embodiments, the device further comprises an anterior ocular segment camera assembly; the anterior segment imaging assembly shares at least a portion of the optical components with the anterior segment OCT optical path assembly, the posterior segment OCT optical path assembly, and the fixation optical assembly.

In some preferred embodiments, the anterior segment camera assembly includes a fifth spectroscope and an ocular objective lens; the fifth spectroscope and the eye objective lens are used for transmitting light to the human eye; the anterior segment image pickup assembly shares the fifth spectroscope and the ocular objective lens with the anterior segment OCT optical path assembly, the posterior segment OCT optical path assembly and the fixation optical assembly.

In some preferred embodiments, the anterior segment OCT optical path component shares at least a portion of the optical components with the posterior segment OCT optical path component.

In some preferred embodiments, the anterior segment OCT optical path component includes a plurality of mirrors.

Compared with the prior art, the beneficial effects of the embodiment of the application are as follows:

the optical path switching scanning device is matched with the optical path movement switching device, so that the rapid switching of the front and rear sections of the optical path can be realized, and the scanning of the front and rear sections of the human eyes can be realized. The optical path movement switching device realizes the switching between the first state and the second state through movement, so that the measuring light from the anterior segment OCT optical path component is transmitted to the anterior segment of the human eye and the measuring light from the posterior segment OCT optical path component is transmitted to the posterior segment of the human eye; compared with a fixed spectroscope structure which transmits part of light and reflects part of light, the light-transmitting efficiency is higher, so that the signal-to-noise ratio during front-section and rear-section OCT measurement can be improved. The cost control and the signal-to-noise ratio of the front-section OCT signal acquisition and the back-section OCT signal acquisition are more reasonably distributed, and the quality of the acquired image can be improved under the condition of limited cost; the detection of a plurality of optical parameters of human eyes can be solved, so that the requirements of measurement of different parts are met; accurate data of a plurality of important parameters of human eyes can be obtained, thereby meeting the requirement of clinical diagnosis of doctors.

Drawings

In order to more clearly illustrate the technical solutions in the embodiments or the background art of the present application, the drawings required to be used in the embodiments or the background art of the present application will be described below.

Fig. 1 shows the overall structure of an ophthalmic measurement system applying the first embodiment;

fig. 2 shows a specific structure of an ophthalmic measurement system of a first embodiment of the present application;

FIG. 3 shows a structure of a posterior segment OCT optical path component of the first embodiment of the present application;

FIG. 4 shows a structure of an optical member of the first embodiment of the present application;

fig. 5 shows another structure of the optical member of the first embodiment of the present application;

FIG. 6 shows the structure of an anterior segment OCT optical path component of the first embodiment of the present application;

fig. 7 shows the structure of a fixation optical assembly of the first embodiment of the present application;

fig. 8 shows the structure of an anterior ocular segment camera assembly according to the first embodiment of the present application;

fig. 9 shows a specific structure of an ophthalmic measurement system of the first embodiment of the present application.

Detailed Description

In order to make the technical problems, technical solutions and advantageous effects to be solved by the embodiments of the present application more clearly apparent, the present application is further described in detail below with reference to fig. 1 to 9 and the embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the present application and are not intended to limit the present application.

It will be understood that when an element is referred to as being "secured to" or "disposed on" another element, it can be directly on the other element or be 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 be indirectly connected to the other element. The connection may be for fixation or for circuit connection.

It will be understood that the terms "length," "width," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," and the like, refer to an orientation or positional relationship indicated in the drawings that is solely for the purpose of facilitating the description of the embodiments and simplifying the description, and do not indicate or imply that the referenced device or element must have a particular orientation, be constructed and operated in a particular orientation, and thus should not be considered as limiting the application.

Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed 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 that feature. In the description of the embodiments of the present application, "a plurality" means two or more unless specifically defined otherwise.

First embodiment

Referring to fig. 1, the present embodiment provides an ophthalmic measurement system including a main body module 100 and a detection module 10.

Referring to fig. 1 and 2, the body module 100 includes a light source 1101, a coupler 1103, a reference arm, a detector 1141, and a computer 1143.

The light source 1101 is a weak coherent light source, and outputs light having a wavelength of about near infrared light.

The coupler 1103 is a fiber optic coupler.

The reference arm includes a reference arm optical path lens 1121 and a reference arm mirror 1123.

The detection module 10, which may also be referred to as a sample arm, may form a detection light path. In this embodiment, the detection module 10 includes a polarization controller 1105, a collimating mirror 1107, an optical path switching scanning device 1109, an optical path motion switching device 1307, an anterior segment OCT optical path component 150, and a posterior segment OCT optical path component 130.

The body module 100 provides reference light to the reference arm through a light source 1101 and measurement light to the detection module 10. Specifically, light output from the light source 1101 provides measurement light to the detection module 10, i.e., the sample arm, and reference light to the reference arm via the coupler 1103. The reference arm has a known length and reflects light back into the coupler 1103 through the reference arm mirror 1123. The detection module 10 supplies measurement light to the eye E to be examined. Light from the sample, i.e. light scattered back by the human eye, passes through the detection module 10, the polarization controller 1105 and light reflected back from the reference arm, and interferes in the coupler 1103. The interference light is detected by the detector 1141, processed by the computer 1143, and finally displayed as an OCT image of the sample to be detected, i.e., human eyes. In this process, the main body module 100 supplies measurement light to the optical path switching scanning device 1109 through the polarization controller 1105 and the collimator mirror 1107. The sample is scanned by the optical path switching scanning device 1109, and tomographic imaging of OCT is realized.

The posterior segment OCT optical path component 130 is used to measure the posterior segment of the human eye E.

The anterior segment OCT optical path component 150 is used to measure the anterior segment of the human eye E.

The optical path switching scanning device 1109 is used for optical path switching of the measurement light from the main body module 100 and for scanning the human eye E. The optical path switching scanning device 1109 may be a one-dimensional optical path switching scanning device, and may be two-dimensional or even three-dimensional. The measuring light is divided into two paths after the light path switching scanning device 1109, one path of measuring light is transmitted to the posterior segment OCT light path component 130, and the other path of measuring light is transmitted to the anterior segment OCT light path component 150. The two measuring lights can enter the human eye E to be measured after passing through the light path movement switching device 1307.

The optical path switching scanning device 1109 performs not only a scanning function but also an optical path switching function. The light path switching scanning device 1109 may adopt vibrating mirror or other high precision positioning structure to meet the requirement of fast switching and scanning of system light path.

In this embodiment, the optical path switching scanning device 1109 switches the optical path of the measuring light by reflecting the measuring light, that is, the optical path switching scanning device 1109 includes a mirror. The optical path switching scanner 1109 is controlled by the computer 1143 and can be located at a position for realizing the imaging of the anterior segment OCT or a position for realizing the imaging of the posterior segment OCT, so as to transmit the measuring light to the anterior segment OCT optical path component 150 or the posterior segment OCT optical path component 130.

The optical path movement switching device 1307 is switched to two different states, a first state and a second state, by movement. That is, at least a part of the optical path movement switching device 1307 is movable; the optical path movement switching device 1307 can switch between the first state and the second state by moving at least a part of itself out of the optical path in which it was originally located.

Referring to fig. 2, the optical path movement switching device 1307 includes a driving member 13073 and an optical member 13071. The drive component 13073 is used to move the optical component 13071. In particular, the drive component 13073 can move the optical component 13071 to different positions, such as a first position and a second position; when the optical member 13071 is in the first position, the optical path movement switching device 1307 is in the first state; when the optical member 13071 is in the second position, the optical path movement switching device 1307 is in the second state; there may be a plurality of first positions, but all correspond to the first state; there may be more than one second position, but all correspond to the second state. Wherein the specific form of motion includes rotation or rotation and movement.

Illustratively, the driving component 13073 is a switching motor, and the optical component 13071 is a light splitting component such as a switching beam splitter. Optical component 13071 is provided with transmissive region 130711 and reflective region 130713.

Referring to fig. 4, for light output by the light source 1101, the left half of the optical member 13071 is a transmissive region and the right half is a reflective region; alternatively, referring to fig. 5, the first and third quadrants are transmissive regions, and the second and fourth quadrants are reflective regions; alternatively, n transmissive regions and n reflective regions (not shown) are designed. The design of the optical member 13071 is determined by the rotational speed and switching speed of the switching motor as the driving member 13073 and the optical path switching scanning device 1109. The transmissive regions and the reflective regions may be arranged alternately or in some combination.

When the driving component 13073 rotates the optical component 13071 to the second position, the optical path motion switching device 1307 is in the second state, and the measurement light from the posterior segment OCT optical path component 130 is irradiated to the front of the reflection region 130713 of the optical component 13071; taking the measurement light from the posterior segment OCT optical path component 130 as light in a second direction; a reflective region 130713 of optic 13071 reflects measurement light from posterior segment OCT optical path component 130 to the human posterior segment; if there is measuring light from anterior segment OCT optical path assembly 150, the measuring light will irradiate the opposite side of reflection region 130713 of optical component 13071, and then be reflected by reflection region 130713 of optical component 13071 to other directions, and will not irradiate human eyes.

When the driving component 13073 rotates the optical component 13071 to the first position, the optical path motion switching device 1307 is in the first state, and the measurement light from the anterior segment OCT optical path component 150 is irradiated to the front surface of the transmission region 130711 of the optical component 13071; taking the measurement light from the anterior segment OCT optical path component 150 as light in a first direction; at this time, the reflection region 130713 has left the original optical path, specifically, the optical path of the posterior segment OCT optical path component 130; the measurement light from the anterior segment OCT optical path component 150 is irradiated to the human anterior segment through the transmission region 130711 of the optical member 13071; if there is measurement light from posterior segment OCT optical path component 130, the measurement light will irradiate the opposite side of transmission area 30711 of optical component 13071, and then transmit transmission area 130711 of optical component 13071 to other places, and cannot irradiate human eyes.

In this embodiment, the light of the first direction and the light of the second direction are light from different directions.

The driving component 13073 rotates the optical component 13071 to the second position, and the transmission region 130711 of the optical component 13071 switches out of the optical path originally located, specifically, the optical path away from the anterior segment OCT optical path component 150. By doing so, the switching between the first state and the second state of the optical path movement switching device 1307 can be realized.

Of course, since the optical paths of the anterior segment OCT optical path component 150 and the posterior segment OCT optical path component 130 overlap or intersect, the transmission region 130711 or the reflection region 130713 can also be said to switch out the optical paths of the anterior segment OCT optical path component 150 and the posterior segment OCT optical path component 130.

The detection module 10 of the present embodiment further includes a fifth spectroscope 1309 and an objective lens 1311. The first spectroscope 1303 is a posterior segment of the eye and a fixation spectroscope. The fifth dichroic 1309 is a front dichroic mirror.

Referring to fig. 3, the posterior segment OCT optical path component 130 includes an optical path adjusting unit 1301, a first spectroscope 1303, and a diopter adjusting unit 1305. The light adjustment range unit 1301 may be formed by a cube-corner prism, a right-angle prism, or two total reflection mirrors disposed perpendicular to each other.

When the posterior segment OCT imaging is carried out, the optical path motion switching device 1307 is in a second state; the optical path switching scanner 1109 is controlled by the computer 1143, and the optical path switching scanner 1109 rotates to the position where the posterior segment OCT imaging is realized to transmit the measuring light to the posterior segment OCT optical path component 130. Specifically, the measuring beam emitted from the collimator 1107 is reflected by the optical path switching scanning device 1109, passes through the light path adjusting unit 1301, is reflected by the first beam splitter 1303, passes through the refraction adjusting unit 1305, is reflected by the optical path movement switching device 1307, is reflected by the fifth beam splitter 1309 to the eye objective 1311, and finally is converged to the fundus of the eye by the eye E. The detection beam of the posterior segment OCT imaging optical path system meets the condition that the central line of the scanning beam is converged near the pupil of the human eye, and the OCT beam is focused on the fundus of the human eye at any time. At this time, the optical path switching scanning device 1109 is located at a position that just makes the included angle between the main optical axis of the incident light from the collimating mirror 1107 and the main optical axis of the reflected light be α, that is, the main optical axis of the light beam changes the angle α. The OCT light beam can be converged on the fundus of the human eye by adjusting the diopter adjusting unit 1305 for different human eyes (the diopters of the human eyes are different), namely, the light beam is focused on the retina. Therefore, the signal-to-noise ratio and the transverse resolution of the OCT image during retina measurement can be effectively improved.

Referring to fig. 6, anterior segment OCT optical path component 150 includes a plurality of mirrors to effect the turning of the optical path. Specifically, anterior segment OCT optical path component 150 includes first mirror 1501, first lens 1503, third mirror 1505, fifth mirror 1507, and third lens 1509.

When the anterior segment OCT imaging is performed, the optical path movement switching device 1307 is in the first state; the optical path switching scanner 1109 is controlled by the computer 1143, and the optical path switching scanner 1109 rotates to the position where the anterior segment OCT imaging is realized to transmit the measuring light to the anterior segment OCT optical path component 150. Specifically, the measurement light emitted from the collimator 1107 is reflected by the optical path switching scanning device 1109, then sequentially reflected by the first reflecting mirror 1501, transmitted through the first lens 1503, reflected by the third reflecting mirror 1505 and the fifth reflecting mirror 1507, transmitted through the third lens 1509, transmitted through the optical path movement switching device 1307, reflected by the fifth beam splitter 1309 to the eye objective 1311, and finally converged by the eye E to the anterior segment of the eye. The detection beam of the anterior segment OCT imaging optical path system meets the condition that the central line of the scanning beam is parallel to the main optical axis L1 of the optical path system and enters the human eye, and the OCT beam is focused on the anterior segment of the human eye at any moment. At this time, the optical path switching scanning device 1109 is located at a position that just makes the included angle between the main optical axis of the incident light from the collimating mirror 1107 and the main optical axis of the reflected light be β, that is, the main optical axis of the light beam changes the β angle.

The light path switching scanning device 1109 can realize the switching of the front and rear light paths by matching with the light path movement switching device 1307.

The anterior segment OCT optical path component 150 shares the fifth beam splitter 1309 and the ocular objective 1311 with the posterior segment OCT optical path component 130.

In other embodiments, anterior segment OCT optical path assembly 150 and posterior segment OCT optical path assembly 130 each include fifth beamsplitter 1309 and objective 1311, as previously described. That is, the aforementioned fifth spectroscope 1309 and the aforementioned ocular objective 1311 are divided into the anterior segment OCT optical path component 150 and the posterior segment OCT optical path component 130.

According to the above, the optical path switching scanning device 1109 is matched with the optical path motion switching device 1307, which can realize the rapid switching of the front and rear section optical paths and the scanning of the front and rear sections of the human eyes. Compared with a fixed spectroscope structure which transmits part of light and reflects part of light, the light path motion switching device 1307 has higher light transmission efficiency, so that the signal-to-noise ratio during anterior-posterior segment OCT measurement can be improved.

Referring to fig. 1, the detection module 10 of the present embodiment further includes a fixation optical assembly 170. The optical path movement switching device 1307 is switched to the first state or the second state by movement to propagate light from the fixation optical assembly 170 to the human eye. Taking the second state as an example, the optical path of the fixation optical assembly 170 and the optical path of the posterior segment OCT optical path assembly 130 are partially overlapped, so that the light from the fixation optical assembly 170 is reflected to the human eye by the optical path movement switching device 1307.

In other embodiments, the optical path movement switching device 1307 switches to the first state by moving so that the light from the fixation optical component 170 propagates to the human eye. Specifically, the optical path of the fixation optical assembly 170 and the optical path of the anterior segment OCT optical path assembly 150 are partially overlapped, so that the light from the fixation optical assembly 170 is reflected to the human eye by the optical path movement switching device 1307.

Referring to fig. 7, the fixation optical assembly 170 includes a fixation light source 1701, a fifth lens 1703, a first spectroscope 1303, and a dioptric adjustment unit 1305. It can be seen that the fixation optical assembly 170 shares a part of the optical components with the posterior segment OCT optical path assembly 130, i.e., shares the first beam splitter 1303 and the diopter adjustment unit 1305.

The first spectroscope 1303 can transmit fixation light (wavelength 550nm) emitted from the fixation light source 1701 in the fixation optical assembly 170 and can reflect light output from the light source 1101.

The fifth beam splitter 1309 can reflect not only the signal light emitted from the light source 1101 but also the fixation light emitted from the fixation light source 1701 in the fixation optical assembly 170.

The fixation light source 1701 is a fixation target (internal fixation target) for fixing the eye E of the subject. The fixation light source 1701 may employ a single point LED, or an LCD screen, an OLED screen, or an LED array screen, etc.

The reflective region 130713 of the optical member 13071 may reflect fixation light emitted from the fixation light source 1701 in the fixation optical assembly 170.

Light from the fixation light source 1701 passes through the fifth lens 1703, passes through the first spectroscope 1303, is diopter-adjusted by the diopter adjustment unit 1305, and after reflection by the optical path movement switching device 1307 and reflection by the fifth spectroscope 1309, the light is re-entered to the eye E through the objective lens 1311. Finally, the internal fixation index is projected to the fundus of the eye E of the subject. When fundus OCT imaging, namely posterior segment OCT imaging, is carried out, when different human eyes observe fixation points, the definition degrees of the fixation points are different, discomfort is caused to a tested person when the tested person fixes the vision, and the fixation and fixation of the tested person eyes are inconvenient. After the optical path of the fundus OCT is adjusted and bent by the refraction adjusting unit 1305, the fundus OCT can be focused on the retina of the fundus, namely, the human eyes can see the scanning line clearly. Because the posterior segment OCT optical path and the fixation optical path share the refraction adjusting unit 1305, the fixation sighting mark can be seen clearly for different human eyes.

Referring to fig. 1, the detection module 10 of the present embodiment further includes an anterior ocular segment camera assembly 190 (which may also be referred to as an iris camera module); the assembly can be used for photographing and previewing the anterior segment of the eye so as to guide a doctor to operate an instrument and enable the optical path of the probe to be aligned with the eye of a person to be detected.

Referring to fig. 8, the anterior ocular segment camera module 190 includes an illumination light source 1901, a seventh lens 1905, a seventh reflector 1907, a ninth lens 1909, and an image capturing unit 1911. The light emitted from the illumination light source 1901 is near-infrared light.

The fifth beamsplitter 1309 is also capable of transmitting illumination light from an illumination light source 1901 in the anterior segment camera assembly 190.

The light emitted by the illumination light source 1901 is irradiated to the anterior chamber of the eye E to be detected, and the light is reflected or scattered by the anterior chamber tissue; the return light passes through the objective lens 1311 and the fifth beam splitter 1309, then passes through the seventh lens 1905, is reflected by the seventh mirror 1907, passes through the ninth lens 1909, and is finally captured by the imaging unit 1911.

The examiner fixes the head of the examinee using the lower jaw support unit (not shown), and fixes the eye of the examinee to the fixation mark of the fixation system, that is, the fixation mark of the fixation optical assembly 170. Then, the examiner controls the movement of the chin rest, the probe, and the like by the operation lever while observing the display screen of the computer 1143, so that the anterior segment of the eye E of the examinee enters the imaging unit 1911 and an image of the anterior segment is displayed on the display screen of the computer 1143.

In other embodiments, the anterior segment camera assembly 190 further comprises a fifth beamsplitter 1309 and an eye objective 1311. As can be seen, the anterior segment imaging assembly 190 shares at least a part of optical components with the anterior segment OCT optical path assembly 150, the posterior segment OCT optical path assembly 130, and the fixation optical assembly 170, that is, shares the fifth spectroscope 1309 and the objective lens 1311, so that the optical path can be simplified.

Second embodiment

Referring to fig. 9, the present embodiment is different from the first embodiment in that: the optical component 13071 is a mirror.

The optical path movement switching device 1307 of the present embodiment also has a first state and a second state.

The first state of the present embodiment is realized by: the driving member 13073 may move the reflecting mirror 13071 to the first position, specifically, may rotate the reflecting mirror 13071 to the first position; at this time, the reflecting mirror 13071 is withdrawn or separated from the optical path of the anterior segment OCT optical path component 50 to give way to the measurement light from the anterior segment OCT optical path component 50, so that the measurement light can be irradiated to the anterior segment of the human eye through the optical path movement switching device 1307. The light in the first direction is the measurement light from the anterior segment OCT optical path component 50.

The second state of the present embodiment is realized by: the driving component 13073 moves the reflecting mirror 13071 to the second position inserted into the optical path of the posterior segment OCT optical path component 130, specifically, the reflecting mirror 13071 may be rotated to the second position; in the second state, the mirror 13071 is in the optical path of the posterior segment OCT optical path component 130, and if there is measurement light from the posterior segment OCT optical path component 130, the mirror 13071 will reflect the measurement light; mirror 13071 is moved to a second position so that the measurement light from posterior segment OCT optical path component 130, i.e. the light in a second direction, can impinge on the posterior segment of the human eye.

It can be seen that the driving part 13073 can switch the mirror 13071 into the optical path or out of the optical path. In the first position, the mirror 13071 is switched out of the optical path of the anterior segment OCT optics 50 so that the measurement light from the anterior segment OCT optics 50 can be directed to the anterior segment of the human eye; mirror 13071 is still in the optical path of posterior segment OCT optical path component 130, but if there is measurement light from posterior segment OCT optical path component 130, mirror 13071 will reflect the measurement light to another location than the posterior segment of the human eye. In the second position, mirror 13071 is switched into the optical path of posterior segment OCT optical path component 130 so that the measurement light from posterior segment OCT optical path component 130 can be directed to the posterior segment of the human eye; although the mirror 13071 is still in the optical path of the anterior segment OCT optical path component 50, if there is measurement light from the anterior segment OCT optical path component 50, the mirror 13071 will reflect the measurement light to another location than the anterior segment of the human eye.

When imaging of posterior segment OCT is performed, the optical path switching scanning device 1109 rotates to a position where imaging of posterior segment OCT is realized, so that an included angle between a main optical axis of incident light from the collimating mirror 1107 and a main optical axis of reflected light is α; the optical path movement switching device 1307 is in the second state, that is, the driving component 13073 moves the reflecting mirror 13071 to the second position inserted into the optical path where the posterior segment OCT optical path component 130 is located; thus, the OCT imaging of the posterior segment of the eye can be realized.

When the anterior segment OCT is imaged, the optical path switching scanning device 1109 rotates to a position where the anterior segment OCT is imaged, so that an included angle between a main optical axis of incident light from the collimating mirror 1107 and a main optical axis of reflected light is β; the optical path movement switching device 1307 is in a first state, that is, the driving component 13073 moves the reflecting mirror 13071 to a first position which is away from the optical path where the anterior segment OCT optical path component 50 is located; thus, anterior segment OCT imaging can be realized.

The drive member 13073 can rapidly switch the mirror 13071 back and forth between the first and second positions. When the posterior segment of the eye is subjected to OCT imaging, the reflecting mirror 13071 is switched into a light path to reflect the output light of the light source 1101 and the fixation light emitted by the fixation light source 1701; when the anterior segment OCT is performed, the mirror 13071 is switched out of the optical path, and at this time, the mirror 13071 does not affect the light source 1101 and the optical path movement switching device 1307. For the light from the fixation optical assembly 170, since the optical path is rapidly switched between the anterior segment and the posterior segment, the fixation point can be perceived by human eyes when the posterior segment of the eye is subjected to OCT imaging. When the switching is carried out quickly, the tested person cannot feel that the fixed viewpoint is suddenly bright and suddenly dark due to the persistence effect of human eyes; as long as the switching speed is fast, the subject considers that the fixation point is normally bright.

In the embodiment of the application, the optical path switching scanning device 1109 and the optical path motion switching device 1307 are controlled by a computer to realize the switching of the optical path, so that the OCT imaging of different parts of human eyes can be realized. The posterior segment OCT optical path component 130 can obtain important parameters of human eye structures such as retina thickness and the like; the anterior segment OCT optical path component 150 can obtain OCT images of the anterior and posterior surfaces of the cornea and the crystalline lens, so that important parameters of human eye structures such as the anterior and posterior surface curvature of the cornea, the corneal thickness, the anterior chamber depth, the crystalline lens thickness and the anterior and posterior surface curvature of the crystalline lens can be obtained; the anterior segment OCT optical path component 150 is matched with the posterior segment OCT optical path component 130, so that important parameters of human eye structures such as the length of an eye axis can be obtained; the anterior segment camera assembly 190 can obtain important parameters of the human eye structure such as white-to-white distance, pupil diameter and the like.

The fast switching front-back section OCT imaging system combining the switching light splitting device of the embodiment of the application comprises: on one hand, the OCT system has a quick switching function, can realize measurement of different depths of an object, can improve the detection range (front and back imaging) of the OCT system, is stable in switching system and accurate in positioning, and does not influence the signal-to-noise ratio of the system; on the other hand, the OCT imaging system can realize the respective focusing of light beams at different positions, can realize high-quality OCT imaging of different parts aiming at human eyes with different eyesight, and has higher transverse resolution. The OCT system can obtain a plurality of parameter data of the human eye, such as corneal curvature, corneal thickness, anterior chamber depth, lens thickness, lens surface curvature, eye axial length, white-to-white distance, pupil diameter and the like.

The embodiment of the application also has the following characteristics.

When the front and back surfaces of the cornea and the crystalline lens are measured, the OCT light beam is focused on the middle area of the anterior segment of the eye, and the signal-to-noise ratio and the transverse resolution of the OCT image can be effectively improved when the front and back surfaces of the cornea and the crystalline lens are measured. In addition, the scanning beam central line is parallel to the main optical axis L1 of the optical path system and is incident to human eyes, which is beneficial to the refraction correction of the front and back surfaces of the cornea and the crystalline lens, thereby obtaining the accurate curvature of the front and back surfaces of the cornea and the crystalline lens.

The probe light path requires OCT imaging of different parts of human eye, but the scanning mode and focusing position adopted by the probe light path are different, so the light path adopted by measurement is different. When fundus OCT imaging is carried out, the central line of a scanning beam is required to be converged at the pupil of a human eye, and OCT beams at any moment are required to be incident into the human eye in parallel; when the anterior segment of the eye is imaged, the central line of the scanning beam is required to be incident to the human eye in parallel, and the OCT beam at any moment needs to be focused on the anterior segment of the human eye. This is beneficial for the correction of OCT images of the cornea and the front and back surfaces of the crystalline lens.

The refraction compensation can be carried out aiming at human eyes with different eyesight, and human eye imaging at different parts is realized.

The optical path for fixing the vision of the human eyes is provided, and the fixation of the vision of the left eye and the right eye can be met.

Because the probe optical path design abandons the traditional fundus imaging optical path (such as a color fundus camera, an LSLO and the like), the anterior segment camera assembly 190 guides a doctor to operate the instrument and can be used for measuring the diameter of the pupil and the white-to-white distance.

And the fast and accurate switching device is adopted, so that fast OCT imaging of different parts of human eyes can be realized.

On the basis of OCT imaging of different parts of human eyes, the rapid and accurate measurement of the axial length of the eye, the anterior chamber depth, the lens thickness and the like can be realized without moving a reference arm.

The front section and the rear section are switched rapidly, and the cost is low due to fewer moving mechanisms.

The fixation optical path and the posterior segment OCT share the refraction adjusting unit, so that moving parts of the fixation optical path can be reduced, the fixation optical path and the posterior segment OCT optical path are confocal, and the fixation of the tested human eye and the acquisition of the fundus OCT image are facilitated.

By combining with a switching light splitting scheme, the fast detection of the front-back section OCT is realized under the condition of not weakening the detection light transmission rate, and the higher detection signal-to-noise ratio is realized.

Compared with a time domain system, the method has the advantages that a frequency domain optical coherence tomography technology is adopted, the scanning imaging speed is high, the imaging resolution is high, and the detection depth is shallow; compared with the scanning frequency domain optical coherence tomography, the scanning speed, the resolution ratio and the like are equivalent, the cost is much lower, and the detection depth is shallow.

The embodiment of the application adopts the method for rapidly switching scanning to realize rapid switching scanning of the front section and the rear section, almost realizes quasi-real time, can realize scanning of dozens of pictures per second, is high in speed, and can avoid the influence of irregular movement of human eyes, thereby accurately measuring the axial length of the human eyes.

According to the embodiment of the application, the front and back images are acquired by one-time measurement, so that the operation of a doctor is facilitated, the diagnosis speed can be increased, and the doctor-patient interaction experience can be improved; the other measurement realizes the detection of a plurality of human eye key parameters such as cornea, anterior chamber depth, eye axial length, corneal curvature, white to white and the like; its advantages are high cost, speed, precision and multiple functions.

The ophthalmologic measuring system in the embodiment of the application is a multifunctional ophthalmologic measuring system, is mainly used for measuring relevant optical parameters of the eyes of patients, is used for guiding the selection of parameters of intraocular lenses and the examination of the eyes of the patients, and can measure a plurality of ophthalmologic relevant parameters such as axial length, corneal curvature, anterior chamber depth, white-to-white distance and the like of the eyes. The ophthalmic measurement system of the embodiments of the present application is primarily based on optical coherence tomography. The optical coherence tomography technology is combined with the quick switching scanning of the front section and the rear section to realize the measurement of the axial length of the human eye, the measurement of the anterior chamber depth, the measurement of the crystal thickness and the measurement of the cornea thickness, and finally realize the measurement of a plurality of optical parameters of the human eye.

The foregoing is a further detailed description of the present application in connection with specific/preferred embodiments and is not intended to limit the present application to that particular description. For a person skilled in the art to which the present application pertains, several alternatives or modifications to the described embodiments may be made without departing from the concept of the present application, and these alternatives or modifications should be considered as falling within the scope of the present application.

Claims

1. An ophthalmic measurement system, comprising: the device comprises a main body module, a light path switching and scanning device, a light path motion switching device, an anterior segment OCT light path component and a posterior segment OCT light path component;

the optical path motion switching device is used for switching to a first state through motion so as to enable the measurement light from the anterior segment OCT optical path component to be transmitted to the anterior segment of the human eye and switching to a second state so as to enable the measurement light from the posterior segment OCT optical path component to be transmitted to the posterior segment of the human eye.

2. The ophthalmic measurement system of claim 1, wherein: the optical path movement switching device comprises a driving component and an optical component; the drive member is used to move the optical member.

3. The ophthalmic measurement system of claim 2, wherein: the optical component is a light splitting component.

4. The ophthalmic measurement system of claim 2, wherein: the optical member includes a transmissive region and a reflective region.

5. The ophthalmic measurement system of claim 4, wherein: the driving component is used for rotating the optical component, so that the optical component rotates to a position where the transmission area transmits the light in the first direction and rotates to a position where the reflection area reflects the light in the second direction.

6. The ophthalmic measurement system of claim 2, wherein: the optical component is a reflector; the driving component is used for moving the reflecting mirror to a first position to irradiate the light in the first direction to the human eye anterior segment, and is used for moving the reflecting mirror to a second position inserted into the optical path of the posterior segment OCT optical path component to reflect the light in the second direction to the human eye posterior segment.

7. The ophthalmic measurement system of claim 1, wherein: the optical path movement switching device is used for switching at least one part of the optical path movement switching device out of the original optical path to realize the switching between the first state and the second state.

8. The ophthalmic measurement system of claim 1, wherein: the vision fixation optical assembly is also included; the optical path movement switching device is used for switching to a first state or a second state through movement so as to enable the light from the fixation optical component to be transmitted to human eyes.

9. The ophthalmic measurement system of claim 8, wherein: the device also comprises an anterior ocular segment camera shooting component; the anterior segment imaging assembly shares at least a portion of the optical components with the anterior segment OCT optical path assembly, the posterior segment OCT optical path assembly, and the fixation optical assembly.

10. The ophthalmic measurement system of claim 9, wherein: the anterior segment camera shooting assembly comprises a fifth spectroscope and an eye objective lens; the fifth spectroscope and the eye objective lens are used for transmitting light to the human eye; the anterior segment image pickup assembly shares the fifth spectroscope and the ocular objective lens with the anterior segment OCT optical path assembly, the posterior segment OCT optical path assembly and the fixation optical assembly.