CN118924235A - An OCT imaging system with integrated sample confocal imaging - Google Patents

Abstract

An OCT imaging system integrating sample confocal imaging comprises an OCT light source, a reference arm module, an OCT sample arm module, a coupler, an OCT signal acquisition module and a sample confocal scanning imaging module, wherein one part of illumination light emitted by the OCT light source is transmitted to the reference arm module after being split by the coupler, and the other part of illumination light is transmitted to the OCT sample arm module; the sample confocal scanning imaging module comprises an opening light splitting device and a receiving device, wherein the opening light splitting device is provided with a light through hole, the irradiation light transmitted to the OCT sample arm module irradiates the sample after passing through the light through hole, the returned signal light is split by the opening light splitting device, one part of the signal light returns to the coupler through the light through hole and is converged with the reference light returned by the reference arm module and then transmitted to the OCT signal acquisition module to generate an OCT image, and the other part of the signal light is guided to the receiving device by the opening light splitting device to generate a confocal scanning imaging image of the sample, so that the OCT light source is shared to realize OCT imaging and sample confocal scanning imaging, and the application of the light source is expanded and the cost is saved.

Description

OCT imaging system integrating confocal imaging of sample

Technical Field

The invention relates to the technical field of fundus imaging, in particular to an OCT imaging system integrating confocal imaging of a sample.

Background

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

Fundus imaging techniques in existing optical coherence tomography products generally employ several modes, such as LSO (LINE SCANNING Opthalmoscope, line scan laser inspection scope), fundus plane imaging, enface synthesis, CSLO (Confocal SCANNING LASER Ophthalmoscopy, confocal scan laser inspection scope), and the like.

The LSO or fundus plane imaging scheme needs to design an additional LSO imaging light path to acquire fundus images, and is complex in design scheme and high in cost.

The Enface synthesis scheme synthesizes fundus images by means of OCT signals reflected by fundus, and is limited by the acquisition speed of an OCT camera, so that real-time imaging cannot be realized. Secondly, a prerequisite for this solution is that OCT signals have to be present.

And fundus confocal scanning imaging techniques can improve the optical resolution and contrast of microscopic images by blocking defocused light using spatial pinholes. However, in order to realize the wide-range high-definition high-speed confocal imaging of the fundus, the scanning mechanism and the signal acquisition and processing system are often required to have high-speed scanning and acquisition performance, which complicates system hardware and increases the cost correspondingly.

Application number 202011120798.5 describes a complex ophthalmic OCT imaging system, but it does not have fundus preview and imaging functions for the eye under test.

Application number 202210493429.3 describes a fundus imaging optical system, but it does not have OCT system functionality.

In a general OCT system, as shown in fig. 1, after the irradiation light emitted by the OCT light source is split by the coupler, a part of the irradiation light is transmitted to the reference arm module and then returned to the coupler as reference light according to the original path; another portion is transmitted to OCT sample arm module 130 to illuminate the sample. The signal light returned from the sample is transmitted back to the coupler through the OCT sample arm module 130, interference occurs after the signal light is converged with the light returned by the reference arm module, the generated interference signal is transmitted to the OCT signal acquisition module to be converted into an electric signal, and the electric signal is processed by the computer to generate an OCT image. Illumination from the OCT light source is split by the coupler and is typically transmitted by the fiber end 101 of the coupler to illuminate the sample. The fiber collimator 1107 is used to collimate the illumination light, the optical path scanning device 1109 is used to form illumination beams of different forms, and the field lens 1301 and the objective lens 1305 deliver the illumination beams to the sample. After the signal light reflected from the sample passes through the objective lens 1305, the field lens 1301 and the optical path scanning device 1109, the signal light is collected by the fiber collimator 1107 at the fiber end 101 of the coupler.

The inventors of the present application have found in long-term research and development that conventional OCT systems can only obtain OCT images. The prior art lacks means to simply and reliably assist the OCT system in accurately aligning the sample.

Disclosure of Invention

The invention aims to provide an OCT imaging system integrating sample confocal imaging, which not only can simply and reliably realize confocal scanning imaging through a sample and assist the OCT system to accurately aim at the sample, but also can realize OCT imaging and confocal scanning imaging through sharing an OCT light source, thereby saving the cost.

In order to achieve the above purpose, the present invention adopts the following technical scheme:

An OCT imaging system integrating sample confocal imaging comprises an OCT light source, a reference arm module, an OCT sample arm module, a coupler, an OCT signal acquisition module and a sample confocal scanning imaging module, wherein irradiation light emitted by the OCT light source is split by the coupler, one part of irradiation light is transmitted to the reference arm module and then transmitted to the coupler to serve as reference light, and the other part of irradiation light is transmitted to the OCT sample arm module; the sample confocal scanning imaging module comprises an open-pore light splitting device and a receiving device, wherein the open-pore light splitting device is provided with a light through hole, irradiation light transmitted to the OCT sample arm module irradiates the sample after passing through the light through hole of the open-pore light splitting device, signal light returned from the sample is split by the open-pore light splitting device, part of the signal light returns to the coupler through the light through hole and is transmitted to the OCT signal acquisition module after being converged with reference light returned by the reference arm module so as to generate an OCT image, and the other part of the signal light is guided to the receiving device by the open-pore light splitting device so as to generate a confocal scanning imaging image of the sample.

In some embodiments of the present invention, the aperture spectroscopic device is an aperture prism having a light-passing aperture, the illumination light transmitted to the OCT sample arm module irradiates the sample after passing through the light-passing aperture of the aperture prism, a part of the signal light returned from the sample returns to the coupler through the light-passing aperture of the aperture prism, and another part is transmitted to the receiving device after being refracted through the peripheral region of the light-passing aperture of the aperture prism.

In some embodiments of the present invention, a compensation prism is disposed between the open-hole prism and the receiving device, and the signal light refracted by the open-hole prism is received by the receiving device after being refracted by the compensation prism.

In some embodiments of the present invention, a converging lens and a pinhole are sequentially disposed between the compensating prism and the receiving device, and the signal light refracted by the compensating prism is converged at the pinhole by the converging lens, passes through the pinhole, and is received by the receiving device.

In some embodiments of the present invention, the aperture spectroscopic device is an aperture mirror having a light-passing aperture, the illumination light transmitted to the OCT sample arm module irradiates the sample after passing through the light-passing aperture of the aperture mirror, a part of the signal light returned from the sample returns to the coupler through the light-passing aperture of the aperture mirror, and another part is transmitted to the receiving device after being reflected by the light-passing aperture peripheral region of the aperture mirror.

In some embodiments of the invention, the OCT sample arm module includes an optical path scanning device with a fiber collimating mirror disposed between the optical path scanning device and the fiber end of the coupler, and the aperture prism or the aperture mirror is disposed between the optical path scanning device and the fiber collimating mirror, or the aperture prism or the aperture mirror is disposed between the fiber collimating mirror and the fiber end of the coupler.

In some embodiments of the present invention, the iris image imaging module further comprises an iris image imaging module, the iris image imaging module comprises an iris illumination light source, an iris imaging lens and an iris imaging device, wherein the light emitted by the iris illumination light source irradiates the anterior chamber of the eye to be detected, is reflected by the tissue of the anterior chamber of the eye, and the reflected light passes through the iris imaging lens and is captured by the iris imaging device.

In some embodiments of the present invention, the OCT sample arm module includes an optical path scanning device, a field lens, a front dichroic mirror, and an objective lens, and the illumination light passing through the light-passing hole of the open-pore beam-splitting device is reflected by the optical path scanning device, passes through the field lens, is reflected by the front dichroic mirror to the objective lens, and is converged to the fundus by the eye to be tested; the iris split image imaging modules are distributed on the left side and the right side of the eye objective lens in pairs.

In some embodiments of the present invention, the system further comprises a fixation optical module including a fixation light source for providing a fixation mark for fixation of the eye of the person under examination; the front dichroic mirror transmits fixation light from the fixation light source.

In some embodiments of the invention, the coupler is a fiber optic coupler.

The invention has the following beneficial effects:

The invention provides an OCT imaging system integrating sample confocal imaging, wherein a sample confocal scanning imaging module is arranged, the sample confocal scanning imaging module comprises an open-pore light-splitting device and a receiving device, and the open-pore light-splitting device is provided with a light-passing hole; after being split by the coupler, part of the irradiation light emitted by the OCT light source is transmitted to the reference arm module and then transmitted to the coupler to be used as reference light, the other part of the irradiation light is transmitted to the OCT sample arm module, the irradiation light transmitted to the OCT sample arm module passes through a light-passing hole of the open-pore light-splitting device and irradiates a sample, signal light returned from the sample is split by the open-pore light-splitting device, part of the signal light returns to the coupler through the light-passing hole and is converged with the reference light returned by the reference arm module and then transmitted to the OCT signal acquisition module to generate an OCT image, and the other part of the signal light is guided to a receiving device by the open-pore light-splitting device to generate a confocal scanning imaging image of the sample; the generated sample image is a confocal image confocal with the OCT image, the confocal image and the OCT image can be displayed at the same time, and the confocal image can assist the OCT system to accurately align to the sample, so that the ophthalmic OCT imaging system combined with fundus confocal imaging has low cost, the light path of the original OCT system is not influenced, the optical system design and the mechanical structure design in the traditional fundus imaging technology are simplified, the system stability and reliability are improved, and the cost is reduced.

Furthermore, in some embodiments, the following benefits are also provided:

In some embodiments of the invention, ocular fundus confocal imaging is achieved by refracting ocular fundus return light through an apertured prism and achromatizing with a compensation prism; in addition, the eye OCT detection device which is convenient for doctors to use can be formed by combining the fixation light path and the split image iris alignment light path.

In some embodiments of the invention, the working distance can be automatically adjusted according to the iris split image imaging principle, and the main optical axis of the probe optical path is aligned to the pupil center of the eye to be detected; the ocular fundus diopter adjustment can be assisted by the OCT imaging quality of the ocular posterior segment; the imaging optical path adjusting lens is shared to realize synchronous adjustment and refraction of the fixation optical path, the fundus OCT imaging optical path and the fundus confocal scanning imaging optical path; and by combining the technologies of automatic recognition of the OCT images of the rear section and the like, the full-automatic detection of the system can be realized.

Other advantages of embodiments of the present invention are further described below.

Drawings

FIG. 1 is a schematic diagram of a prior art OCT system;

FIG. 2 is a schematic diagram of an OCT sample arm module and sample confocal scanning imaging module of example 1;

FIG. 3 is a schematic view of an open cell prism of example 1;

FIG. 4 is a schematic view of the reflected signal beam in embodiment 1;

FIG. 5 is a schematic diagram of an OCT sample arm module and sample confocal scanning imaging module of example 2;

FIGS. 6a and 6b are schematic diagrams of the compensation prism in example 2, respectively;

FIG. 7 is a schematic diagram of an OCT sample arm module and sample confocal scanning imaging module of example 3;

FIGS. 8a and 8b are different schematic diagrams of OCT imaging systems for integrated confocal imaging of samples according to example 4;

FIG. 9 is a schematic diagram showing the composition and installation of an iris image imaging module in example 4;

FIG. 10 is a schematic diagram of an OCT imaging system integrating confocal imaging of a sample in example 5;

FIG. 11 is a schematic view of an aperture mirror in example 5.

The reference numerals are as follows:

1 is an OCT light source, 2 is a reference arm module, 3 is a coupler, 4 is an OCT signal acquisition module, 5 is a sample, 10 is a probe module, and 130 is an OCT sample arm module;

101 is an optical fiber end;

1103 is an optical fiber coupler, 1105 is a polarization controller, 1107 is an optical fiber collimator, 1109 is an optical path scanning device;

11091 is an X-direction scanning device, 11093 is a Y-direction scanning device;

1121 is a reference arm optical path lens, 1123 is a reference arm mirror, 1143 is a computer;

1301 is a field lens, 1303 is a front dichroic mirror, 1305 is an objective lens;

1501 is an open-cell prism, 1503 is a compensation prism, 1505 is a converging lens, 1507 is a pinhole, 1509 is a receiving device;

15011 is a light-passing hole, 15012 is a light-passing hole peripheral region;

1701 is a fixation light source, 1703 is a fixation light path lens, 1705 is a fixation light path diaphragm, and 1707 is a fixation relay lens;

180 is an iris split image imaging module, 1811L is a left iris illumination light source, 1811R is a right iris illumination light source, 1801L is a left iris imaging device, 1801R is a right iris imaging device, 1803L is a left iris imaging lens, 1803R is a right iris imaging lens, L18L is a left iris split image light path, and L18R is a right iris split image light path;

2501 is an aperture mirror;

25011 is a light passing hole of the open-pore reflector, 25012 is a peripheral portion of the open-pore reflector; a reflected signal beam central portion 301, a reflected signal beam peripheral portion 302;

l1 is the main optical axis.

Detailed Description

The application will be further described with reference to the following drawings in conjunction with the preferred embodiments. It should be noted that, without conflict, the embodiments of the present application and features of the embodiments may be combined with each other.

It should be noted that, in this embodiment, the terms of left, right, upper, lower, top, bottom, etc. are merely relative terms, or refer to the normal use state of the product, and should not be considered as limiting.

The following embodiments of the present invention enable the generation of OCT images and sample images simultaneously after spatial separation of the reflected signal beam with a device.

The following embodiments of the present invention provide an OCT imaging system with integrated sample confocal imaging, including an OCT light source 1, a reference arm module 2, an OCT sample arm module 130, a coupler 3, an OCT signal acquisition module 4, and a sample confocal scanning imaging module, where the OCT sample arm module 130 and the sample confocal scanning imaging module together form a probe module 10, and after being split by the coupler 3, a part of illumination light emitted by the OCT light source 1 is transmitted to the reference arm module 2 and then transmitted to the coupler 3 as reference light, and another part is transmitted to the OCT sample arm module 130; the sample confocal scanning imaging module comprises an open-hole light splitting device (such as 1501 or 2501) and a receiving device 1509, the open-hole light splitting device is provided with a light through hole 15011, the irradiation light transmitted to the OCT sample arm module 130 irradiates the sample 5 after passing through the light through hole 15011 of the open-hole light splitting device, the signal light returned from the sample 5 is split by the open-hole light splitting device, one part of the signal light is returned to the coupler 3 through the light through hole 15011, and is transmitted to the OCT signal acquisition module 4 after being combined with the reference light returned by the reference arm module 2 so as to generate an OCT image, and the other part of the signal light is guided to the receiving device 1509 by the open-hole light splitting device so as to generate a confocal scanning imaging image of the sample 5.

Referring to fig. 2, 5, and 7 to 8b, in a preferred embodiment, the aperture beam splitter is an aperture prism 1501 having a light-passing aperture, the illumination light transmitted to the OCT sample arm module 130 irradiates the sample 5 after passing through the light-passing aperture 15011 of the aperture prism 1501, a portion of the signal light returned from the sample 5 returns to the coupler 3 through the light-passing aperture 15011 of the aperture prism 1501, and another portion is transmitted to the receiving device 1509 after being refracted through the light-passing aperture peripheral region 15012 of the aperture prism 1501.

Referring to fig. 10, in another preferred embodiment, the aperture spectroscopic device is an aperture mirror 2501 having a light-passing aperture, the irradiation light transmitted to the OCT sample arm module 130 irradiates the sample 5 through the light-passing aperture of the aperture mirror 2501, a part of the signal light returned from the sample 5 returns to the coupler 3 through the light-passing aperture of the aperture mirror 2501, and the other part is refracted through the peripheral region of the light-passing aperture of the aperture mirror 2501 and transmitted to the receiving device 1509.

The aperture spectroscopic device (aperture prism 1501 or aperture mirror 2501) may be used to split light, and the aperture spectroscopic device may be used to allow all light output from the OCT light source 1 to pass through the aperture (light-passing hole 15011 or aperture mirror light-passing hole 25011), and light returned from the fundus oculi is split by the aperture spectroscopic device. The utilization rate of the light source is improved, and it is easy to understand that if the common or non-perforated spectroscope is used for replacing, the spectroscope is used for splitting light according to different wave bands or partially transmitting and partially reflecting, so that the utilization rate of the light source is reduced, and the same effect of the perforated spectroscope cannot be realized.

Referring to fig. 5, in a preferred embodiment, a compensating prism 1503, a converging lens 1505 and a pinhole 1507 are sequentially disposed between the perforated prism 1501 and the receiving device 1509, and the signal light refracted by the perforated prism 1501 is refracted by the compensating prism 1503, converged by the converging lens 1505 into the pinhole 1507, passes through the pinhole 1507 and is received by the receiving device 1509.

Referring to fig. 7, in a preferred embodiment, the OCT sample arm module 130 includes an optical path scanning device 1109, a fiber collimating mirror 1107 is disposed between the optical path scanning device 1109 and the fiber end 101 of the coupler, and the aperture prism 1503 is disposed between the fiber collimating mirror 1107 and the fiber end 101 of the coupler.

In a preferred embodiment, the iris split image imaging module 180 further comprises an iris illumination light source, an iris imaging lens and an iris imaging device, wherein the light emitted by the iris illumination light source irradiates the anterior chamber of the eye to be detected, is reflected by the tissue of the anterior chamber of the eye, and the reflected light passes through the iris imaging lens and is captured by the iris imaging device.

In a preferred embodiment, the OCT sample arm module 130 includes an optical path scanning device 1109, a field mirror 1301, a front dichroic mirror 1303, and an objective lens 1305, and the illumination light passing through the light-passing hole of the open-pore beam splitter device is reflected by the optical path scanning device 1109, passes through the field mirror 1301, is reflected by the front dichroic mirror 1303, and then reaches the objective lens 1305, and is converged to the fundus through the eye to be tested; preferably, the iris imaging modules 180 are arranged in pairs on the left and right sides of the objective 1305.

In a preferred embodiment, the device further comprises a fixation optical module, wherein the fixation optical module comprises a fixation light source 1701 for providing a fixation mark for fixation of the eye of the person to be examined; the front dichroic mirror 1303 transmits fixation light from the fixation light source 1701.

In a preferred embodiment, the coupler 3 employs a fiber optic coupler 1103.

Example 1

In this embodiment, the aperture spectroscopic device is an aperture prism 1501 having a light-passing aperture, that is, a prism having a light-passing aperture, and the reflected signal beam central portion 301 passes through the light-passing aperture of the prism to generate an OCT image, and the reflected signal beam peripheral portion 302 is refracted at the peripheral region of the light-passing aperture of the prism to generate a sample image. Prisms include, but are not limited to, right angle prisms, wedge prisms, and other forms of prisms that can change the direction of beam transmission.

Preferably, the coupler 3 in this embodiment is an optical fiber coupler 1103.

As shown in fig. 2, the probe module 10 in this embodiment includes an OCT sample arm module 130 and a sample confocal scanning imaging module, and specifically includes an optical fiber end 101, an optical fiber collimator 1107, an optical path scanning device 1109, a field lens 1301, an objective lens 1305, an aperture prism 1501, a converging lens 1505, a pinhole 1507, and a receiving device 1509; between the fiber collimator 1107 and the optical path scanning device 1109, an open-pore prism 1501 is designed to perform spatial decoupling to generate a sample image. The OCT illumination beam is collimated by the optical fiber end 101 and then passes through the optical fiber collimator 1107, passes through the light-passing hole 15011 (the light-passing hole is parallel to the transmission direction of the illumination beam) in the open prism 1501, and then is transmitted to the optical path scanning device 1109, and finally is transmitted to the sample 5 through the field lens 1301 and the objective lens 1305. When the illumination beam reaches the sample 5 for reflection, the reflected signal beam size is typically larger than the original illumination beam size due to scattering of the sample 5, etc. When the reflected signal beam passes through the objective lens 1305, the field lens 1301, and the optical path scanning device 1109 and reaches the aperture prism 1501, the reflected signal beam center portion 301 passes through the light passing hole 15011 of the aperture prism 1501, and is focused back through the fiber collimator 1107 to the fiber end 101 of the coupler, and finally used to form an OCT image. The reflected signal beam peripheral portion 302 is refracted and transmitted through the light-transmitting aperture peripheral region 15012 of the aperture prism 1501, and is received by the receiving device 1509 through the converging lens 1505, focusing on the pinhole 1507, and forms a sample image.

As shown in fig. 3, the perforated prism 1501 includes a light-passing hole 15011 and a light-passing hole peripheral region 15012.

The reflected signal beam includes a reflected signal beam central portion 301 and a reflected signal beam peripheral portion 302, as shown in fig. 4.

The OCT signal acquisition module 4 is preferably a time domain OCT module, a fourier domain OCT module, a swept domain OCT module, or other OCT modules.

Example 2

In this embodiment, as shown in fig. 5, a compensating prism 1503 is added between an open prism 1501 and a converging lens 1505. When the reflected signal beam is refracted by the perforated prism 1501 and reaches the compensating prism 1503 for secondary refraction, the imaging signal beam direction is turned to the direction parallel to the system, so as to reduce the overall size of the system, realize dispersion compensation for the perforated prism 1501, reduce the focusing light spot of the reflected signal beam, and improve the image definition and signal to noise ratio of fundus confocal scanning imaging.

Compensation prism 1503 as shown in fig. 6a, 6b, the number of compensation prisms 1503 may be one or a combination of prisms.

Example 3

In this embodiment, as shown in fig. 7, the probe module 10 is configured to spatially decouple an open prism 1501 or the like between the fiber end 101 of the coupler and the fiber collimator 1107 to generate a sample image. At this time, after the reflected signal beam passes through the fiber collimator 1107, the central portion 301 of the reflected signal beam will pass through the light-passing hole 15011 of the open prism 1501 and be focused back into the fiber end 101 of the coupler, ultimately for OCT imaging. The reflected signal beam peripheral portion 302 is refracted and transmitted through the light-transmitting aperture peripheral region 15012 of the aperture prism 1501, and is received by the receiving device 1509 through the converging lens 1505, focusing on the pinhole 1507, and forms a sample image.

Example 4

The OCT imaging system combined with confocal imaging of the fundus integrated sample according to this embodiment is shown in fig. 8a, where the lens is shown as a schematic, and may be formed as a glue or a lens group.

The OCT imaging system comprises: an OCT imaging module and a probe module 10, wherein the probe module 10 comprises an OCT sample arm module 130 and a sample confocal scanning imaging module; preferably, the probe module 10 further comprises a fixation optical module and an iris split image imaging module 180; the sample confocal scanning imaging module is the fundus confocal scanning imaging module.

The probe module 10 as a whole is capable of X/Y/Z three-dimensional translation (transmission not shown). The present embodiment defines the X-axis as the axis perpendicular to the paper surface. The Y-axis is defined as the axis parallel to the page in the up-down direction. The Z-axis is defined as the axis parallel to the paper surface in the left-right direction. The above definitions are only used for convenience of description of the present embodiment.

The OCT imaging system further includes a combination module that is composed of the objective 1305 and the iris split imaging module 180. The module is capable of moving in the Z direction (the actuator is not shown) to effect refractive adjustment.

(1) OCT imaging module

The OCT imaging module comprises an OCT light source 1, a reference arm module 2, a coupler 3, an OCT signal acquisition module 4, a computer 1143 and an OCT sample arm module 130; preferably, the coupler is a fiber optic coupler 1103.

The computer 1143 is not a PC computer in the conventional sense in this embodiment, but is a circuit control and processing system capable of performing operations, control, storage, display, and other functions.

Wherein the reference arm module 2 illustratively includes a reference arm optical path lens 1121, a reference arm mirror 1123.

Wherein the OCT sample arm module 130 includes a polarization controller 1105, a fiber collimator 1107, and an optical path scanning device 1109.

The optical path scanning device 1109 adopts a two-dimensional scanning mechanism, and is composed of an X-direction scanning device 110911 and a Y-direction scanning device 11093.

The OCT imaging module optical path includes an OCT light source 1, the light of which output provides light to the OCT sample arm module 130 and the reference arm module 2 via a fiber coupler 1103. The reference arm module 2 has a known length and reflects light back into the fiber optic coupler 1103 through the reference arm mirror 1123. The OCT sample arm module 130 provides light to the human Eye E (Eye) to be measured, the light scattered from the sample is interfered in the optical fiber coupler 1103 by the OCT sample arm module 130, the polarization controller 1105 and the reference arm module 2, the interference light is detected by the OCT signal collecting module 4, and then processed by the computer 1143, and finally the OCT image of the sample to be measured is displayed. The sample is scanned by the optical path scanning device 1109, and tomographic imaging of OCT is realized.

The OCT light source 1 outputs near infrared light.

(2) OCT sample arm module 130

The OCT sample arm module 130 includes a fiber collimator 1107, an aperture prism 1501, an optical path scanning device 1109, a field lens 1301, a pre-dichroic mirror 1303, and an objective lens 1305.

The optical path scanning device 1109 may be a one-dimensional optical path switching scanning device, or may be two-dimensional or even three-dimensional. The optical path scanning device 1109 realizes one-dimensional to multi-dimensional scanning of a sample to be measured.

The fiber collimator 1107 is connected to the fiber of the sample arm, and the whole fiber collimator is driven by a motor and can translate along the optical axis of the fiber collimator, so that the optical path of the sample arm is changed.

When OCT imaging is performed, light emitted from the fiber collimator 1107 passes through the light-passing hole 15011 of the open-cell prism 1501, and is reflected by the optical path scanning device 1109. At this time, the optical path scanning device 1109 is controlled by the computer 1143, and the light beam is reflected by the optical path scanning device 1109, passes through the field lens 1301, is reflected by the front dichroic mirror 1303 to the objective lens 1305, and is incident on the sample 5. In this example, the eye E to be measured is listed as incident, and finally, the eye E to be measured is converged to the fundus Er of the eye. The detection light beam of the OCT imaging light path system of the posterior segment of the eye meets the requirement that the central line of the scanning light beam is converged near the pupil of the human eye, and the OCT light beam is focused on the fundus Er of the human eye at any moment. The light returned through the fundus Er of the human eye returns along the original path, still passes through the light-passing hole 15011 of the open-pore prism 1501, and is converged to the sample end optical fiber head of the optical fiber coupler 1103 through the optical fiber collimating mirror 1107. The return light interferes with the light reflected by the reference arm module 2 in the optical fiber coupler 1103, thereby obtaining a coherent signal of the fundus Er of the human eye to be measured.

The OCT beam can be converged on the eye fundus Er of the human eye by moving the objective lens 1305 along the optical axis L1 for different eyes (which are different in diopter). That is, the light beam is focused on the retina, so that the signal-to-noise ratio and the transverse resolution of OCT images can be effectively improved during retina measurement.

The front dichroic mirror 1303 can reflect the signal light emitted from the OCT light source 1, and transmit the fixation light emitted from the fixation light source 1701 in the fixation optical module.

When fundus is measured, scanning is performed by the X-direction scanning device 11091 and the Y-direction scanning device 11093; the optical path matching for the eyeground of different eyes is realized by combining the integral translation of the sample arm optical fiber head (not shown) through the optical fiber collimating lens 1107; the eye objective 1305 translates along the main optical axis L1 to adjust and bend for different eyes; finally, the acquisition of OCT images of the posterior segment of the eye is realized, so that important parameters of human eye structures such as retina thickness and the like are obtained.

(3) Fundus confocal scanning imaging module

The fundus confocal scanning imaging module emits light by the OCT light source 1 to enter the eye to be detected, realizes two-dimensional scanning by the optical path scanning device 1109, adjusts and bends by the eye-receiving objective lens 1305, and synthesizes fundus images by receiving fundus return light. The fundus confocal scanning imaging chart can be used for previewing and imaging functions during eye operation to be detected.

The OCT light source 1 of the OCT imaging module emits light, and the light passes through the optical fiber coupler 1103 and the optical fiber collimator 1107, then is collimated and emitted, passes through the light-passing hole 15011 of the open-pore prism 1501, and is reflected by the optical path scanning device 1109, and two-dimensional scanning is achieved. The light then passes through the field lens 1301, is reflected by the front dichroic mirror 1303 to the objective lens 1305, and finally is converged to the fundus Er by the human eye E to be measured. The light returned by the fundus Er returns to the optical path scanning device 1109 along the original path, the return light passes through the light passing hole peripheral area 15012 of the open pore prism 1501 after being reflected by the optical path scanning device 1109, the light beam is deflected after being refracted by the light passing hole peripheral area 15012 of the open pore prism 1501, and is received by the receiving device 1509 after being refracted by the compensating prism 1503, thereby obtaining single-point image information of the fundus Er of the human eye E to be detected. By the two-dimensional scanning of the optical path scanning device 1109, an image of the fundus Er can be obtained.

It is also preferable that the return light is converged to the pinhole 1507, and then the return light passes through the pinhole 1507 and is received by the receiving device 1509.

The light source, the scanning device, part of the light path and the bending adjustment device of the fundus confocal scanning imaging module are shared with the OCT imaging system, so that the hardware cost of the system can be greatly reduced. Because the OCT scanning line is shared by the bending adjustment devices, when the OCT scanning line is clearly projected on the fundus Er to be measured, the fundus confocal scanning imaging module is also positioned at the optimal bending adjustment position for clear imaging.

The OCT light source 1 of the OCT imaging module is utilized by the fundus confocal scanning imaging module. The OCT light source 1 has a certain wavelength bandwidth. After the return light is refracted by the peripheral area 15012 of the light passing hole of the perforated prism 1501, dispersion occurs, so that the focusing state of the converging lens 1505 is dispersed, that is, the light beam is dispersed at the pinhole 1507. This reduces the image sharpness and signal-to-noise ratio of the fundus confocal scanning imaging. The present embodiment incorporates a compensation prism 1503 so that the return light is not dispersed. The focusing state of the return light through the converging lens 1505 can be improved, thereby improving the image definition and the signal-to-noise ratio of the fundus confocal scanning imaging.

As is clear from the above, when the bandwidth of the OCT light source 1 is narrow, the dispersion effect due to refraction through the peripheral region 15012 of the aperture prism 1501 becomes insignificant, and the compensation prism 1503 can be eliminated. That is, the return light is refracted by the peripheral area 15012 of the light passing hole of the perforated prism 1501, and then focused on the pinhole 1507 by the converging lens 1505, as shown in fig. 8 b.

(4) Fixation optical module

The fixation light source 1701 in the fixation optical module is used for fixation marks (internal fixation marks) for fixation of the eye E to be measured. The light from the fixation light source 1701 passes through the fixation light path lens 1703 and fixation light path stop 1705, and then, after fixation of the relay lens 1707 and the front dichroic mirror 1303, the light passes through the objective lens 1305 and then enters the human eye E to be measured. Finally, the internal fixation index is projected onto the fundus Er of the human eye E to be measured.

Preferably, the fixation light source 1701 may employ a single point LED, or an LCD screen, an OLED screen, or an LED array screen, or the like.

When fundus OCT imaging is carried out, when different eyes observe the fixation point, the definition degree of the fixation point is different, which causes discomfort to a tested person in fixation, and is inconvenient for fixation and fixation of the eyes to be tested. After the fundus OCT light is adjusted and bent by the eye objective 1305, the OCT light can be focused on the retina of the fundus, namely, the OCT scanning line can be clearly projected on the fundus Er to be measured. The eye objective 1305 is shared by the OCT optical path and the fixation optical path for bending, so that clear OCT imaging can be carried out on the fundus of different eyes while the fixation target can be seen clearly.

(5) Iris split image imaging module 180

Referring to fig. 8a and 9, iris imaging modules 180 are mounted on the left and right sides of the objective 1305. It is composed of a left iris illumination light source 1811L, a right iris illumination light source 1811R, a left iris imaging lens 1803L, a right iris imaging lens 1803R, a left iris imaging device 1801L, a right iris imaging device 1801R, and the like.

Wherein light emitted from left/right iris illumination light source 1811L/1811R (infrared light) is irradiated to anterior chamber of eye E to be measured, and the light is reflected by anterior chamber tissue. The reflected light passes through the left/right iris imaging lens 1803L/1803R and is finally captured by the left/right iris imaging device 1801L/1801R.

The iris imaging module 180 is preferably distributed on both the left and right sides of the objective 1305. If distributed in the up-down direction of the probe module 10, the iris image is easily blocked by eyelid, and the iris image is not used. While left/right iris illumination light sources 1811L/1811R may be composed of 1 or more light sources, the distribution may be distributed as shown above in the left-right with respect to the objective 1305, or may be distributed up-down, in an array, etc. If a single iris illumination light source 1811 is used, it is preferable to arrange it under the objective 1305.

Because the left and right sides of the two paths of iris split image light paths are symmetrically distributed, a left iris split image light path L18L and a right iris split image light path L18R of a light path main optical axis of the two paths of iris split image light paths intersect with a system light path main optical axis L1. Similar to the principle that binocular can range, the working position of the eye to be detected can be judged by two paths of iris split image light paths. Or two paths of iris split image light paths, respectively obtaining upper and lower part anterior chamber images of the eye E to be detected through imaging, and judging the working distance through image stitching of the upper and lower part anterior chamber images. When the images of the upper and lower eye anterior chamber images can just spell out a complete iris image or pupil image, the eye to be detected can be judged to be in a required working position.

When the eye E to be measured deviates from the working position up and down, pupil or iris images deviate from one of the images of the upper and lower eye anterior chamber images, so that the pupil or iris is not distributed symmetrically up and down along the images of the upper and lower eye anterior chamber images.

When the eye E to be measured deviates from the working position left and right, pupils or iris images in the images of the upper eye anterior chamber image and the lower eye anterior chamber image deviate from the center position of the image in the same direction.

When the front and back of the eye E to be detected deviate from the working position, the pupil or the iris image in the images of the upper and lower eye anterior chamber images deviate in opposite directions, so that the splicing of the pupil or the iris image cannot be completed.

In the upper judging method, the probe module 10 can be assisted to perform three-dimensional adjustment up and down, left and right, front and back through two paths of iris split image light paths, and finally the eye E to be tested is positioned at a working position required by fundus imaging.

Example 5

As shown in fig. 10 and 11, the aperture prism 1501 and the compensation prism 1503 are replaced with an aperture mirror 2501.

Therefore, with the OCT sample arm module, when OCT imaging is performed, light emitted from the fiber collimator 1107 passes through the light-passing hole 25011 of the aperture mirror 2501, and is reflected by the optical path scanning device 1109.

For a fundus confocal scanning imaging module, the OCT light source 1 of the OCT imaging module 110 emits light, and the light is collimated and emitted through the optical fiber coupler 1103 and the optical fiber collimator 1107, passes through the light passing hole 25011 of the open hole reflector 2501, is reflected by the optical path scanning device 1109, and realizes two-dimensional scanning. The light then passes through the field lens 1301, is reflected by the front dichroic mirror 1303 to the objective lens 1305, and finally is converged to the fundus Er by the human eye E to be measured. The light returned from the fundus Er returns to the optical path scanning device 1109 along the original path, and after being reflected by the optical path scanning device 1109, the return light is reflected by the outer peripheral portion 25012 of the aperture mirror 2501, and after passing through the converging lens 1505, the return light is converged at the pinhole 1507. Since the aperture mirror 2501 is employed, it reflects the return light without dispersion.

The embodiment of the invention has the following advantages:

the OCT imaging system for integrated sample confocal imaging provided by the embodiment of the invention can provide a low-cost solution for OCT detection for a person to be detected, is not only beneficial to popularization of OCT equipment, but also can enable more patients to enjoy the fundus nondestructive detection technology, and can provide an intuitive and graphical detection means for doctor diagnosis.

The embodiment of the invention adopts the traditional ophthalmic OCT imaging technology, but by arranging the confocal scanning imaging module and utilizing the scanning mechanism and the light source of the OCT system, the confocal scanning imaging with fundus OCT imaging is realized, thereby greatly saving the system cost, and the confocal image can assist the OCT system to accurately align with a sample (fundus). In addition, the eye OCT detection device which is convenient for doctors to use can be formed by combining the fixation light path and the split image iris alignment light path.

The OCT imaging system for integrated sample confocal imaging designed by the embodiment of the invention can automatically adjust the working distance according to the iris split image imaging principle, and leads the main optical axis of the probe optical path to be aligned with the pupil center of the eye to be detected; the ocular fundus diopter adjustment can be assisted by the OCT imaging quality of the ocular posterior segment; the imaging optical path adjusting lens is shared to realize synchronous adjustment and refraction of the fixation optical path, the fundus OCT imaging optical path and the fundus confocal scanning imaging optical path; and by combining the technologies of automatic recognition of the OCT images of the rear section and the like, the full-automatic detection of the system can be realized.

The ophthalmic OCT imaging system combining fundus confocal imaging has low cost, does not influence the light path of the original OCT system, refracts fundus return light by using an open-pore prism, and realizes fundus confocal imaging by using a compensation prism to achromatize.

The confocal image formed by the embodiment of the invention can be displayed simultaneously with the OCT image, and the confocal image can assist the OCT system to accurately align with the sample.

The embodiment of the invention simplifies the design of the optical system and the mechanical structure in the traditional fundus imaging technology, improves the stability and the reliability of the system and reduces the cost.

The foregoing is a further detailed description of the invention in connection with the preferred embodiments, and it is not intended that the invention be limited to the specific embodiments described. It will be apparent to those skilled in the art that several equivalent substitutions and obvious modifications can be made without departing from the spirit of the invention, and the same should be considered to be within the scope of the invention.

Claims (10)

1. An OCT imaging system with integrated sample confocal imaging, characterized in that it includes an OCT light source, a reference arm module, an OCT sample arm module, a coupler, an OCT signal acquisition module and a sample confocal scanning imaging module, wherein the irradiation light emitted by the OCT light source is split by the coupler, a part of which is transmitted to the reference arm module and then transmitted to the coupler as reference light, and the other part is transmitted to the OCT sample arm module; wherein the sample confocal scanning imaging module includes an aperture spectrometer and a receiving device, the aperture spectrometer has a light-through hole, the irradiation light transmitted to the OCT sample arm module passes through the light-through hole of the aperture spectrometer and then irradiates the sample, and the signal light returned from the sample is split by the aperture spectrometer, a part of the signal light is returned to the coupler through the light-through hole, and is transmitted to the OCT signal acquisition module after merging with the reference light returned by the reference arm module to generate an OCT image, and the other part of the signal light is guided by the aperture spectrometer to the receiving device to generate a confocal scanning imaging diagram of the sample. 2. The OCT imaging system for integrated sample confocal imaging as described in claim 1 is characterized in that the open-aperture spectroscopic device is an open-aperture prism with a light-through hole, and the illumination light transmitted to the OCT sample arm module passes through the light-through hole of the open-aperture prism and then illuminates the sample, and a part of the signal light returned from the sample returns to the coupler through the light-through hole of the open-aperture prism, while the other part is refracted through the peripheral area of the light-through hole of the open-aperture prism and then transmitted to the receiving device. 3. The OCT imaging system for integrated sample confocal imaging as described in claim 2 is characterized in that a compensation prism is arranged between the perforated prism and the receiving device, and the signal light refracted by the perforated prism is further refracted by the compensation prism and then received by the receiving device. 4. The OCT imaging system for integrated sample confocal imaging as described in claim 3 is characterized in that a converging lens and a pinhole are sequentially arranged between the compensation prism and the receiving device, and the signal light refracted by the compensation prism is converged at the pinhole through the converging lens, and is received by the receiving device after passing through the pinhole. 5. The OCT imaging system with integrated sample confocal imaging as described in claim 1 is characterized in that the open-aperture spectroscopic device is an open-aperture reflector with a light-through hole, and the irradiation light transmitted to the OCT sample arm module passes through the light-through hole of the open-aperture reflector and then irradiates the sample, and a part of the signal light returned from the sample returns to the coupler through the light-through hole of the open-aperture reflector, while the other part is reflected by the peripheral area of the light-through hole of the open-aperture reflector and then transmitted to the receiving device. 6. The OCT imaging system for integrated sample confocal imaging as described in any one of claims 2 to 5, characterized in that the OCT sample arm module includes an optical path scanning device, a fiber optic collimator is arranged between the optical path scanning device and the optical fiber end of the coupler, the open-hole prism or the open-hole reflector is arranged between the optical path scanning device and the optical fiber collimator, or the open-hole prism or the open-hole reflector is arranged between the optical fiber collimator and the optical fiber end of the coupler. 7. The OCT imaging system for integrated sample confocal imaging as described in any one of claims 1 to 5 is characterized in that it also includes an iris split-image imaging module, which includes an iris illumination light source, an iris imaging lens and an iris camera device, wherein the light emitted by the iris illumination light source is irradiated to the anterior chamber of the eye to be tested, and is reflected by the anterior chamber tissue of the eye to be tested. The reflected light passes through the iris imaging lens and is captured by the iris camera device. 8. The OCT imaging system for integrated sample confocal imaging as described in claim 7 is characterized in that the OCT sample arm module includes an optical path scanning device, a field lens, a front dichroic mirror and an eyepiece objective lens, and the irradiation light passing through the light hole of the open-aperture spectrometer is reflected by the optical path scanning device, passes through the field lens, is reflected to the eyepiece objective lens by the front dichroic mirror, and converges to the fundus through the eye to be tested; the iris split-image imaging modules are distributed in pairs on the left and right sides of the eyepiece objective lens. 9. The OCT imaging system for integrated sample confocal imaging as described in claim 7 is characterized in that it also includes a fixation optical module, the fixation optical module includes a fixation light source, which is used to provide a fixation mark for the subject's eye to fixate; the front dichroic mirror transmits the fixation light from the fixation light source. 10. The OCT imaging system with integrated sample confocal imaging according to any one of claims 1 to 5, characterized in that the coupler is a fiber optic coupler.