TW202110389A - Multimodal eye imaging techniques and apparatus - Google Patents

Abstract

Aspects of the present disclosure provide improved techniques for imaging a subject’s retina fundus. Some aspects relate to an imaging apparatus that may be substantially binocular shaped and/or may house multiple imaging devices configured to provide multiple corresponding modes of imaging the subject’s retina fundus. Some aspects relate to techniques for imaging a subject’s eye using white light, fluorescence, infrared (IR), optical coherence tomography (OCT), and/or other imaging modalities that may be employed by a single imaging apparatus. Some aspects relate to improvements in white light, fluorescence, IR, OCT, and/or other imaging technologies that may be employed alone or in combination with other techniques. Some aspects relate to multi-modal imaging techniques that enable determination of a subject’s health status. Imaging apparatuses and techniques described herein provide medical grade retina fundus images and may be produced or conducted at low cost, thus increasing access to medical grade imaging.

Description

Multi-mode eye imaging technology and equipment

This application relates generally to imaging the eyes of a subject, and in particular to imaging the fundus of the retina of the subject.

The retinal fundus of an eye can usually be imaged using a conventional digital camera. The technology of the present invention for imaging the retinal fundus will benefit from improvements.

Certain aspects of the present invention relate to an imaging device for imaging and/or measuring the retinal fundus of a subject, the device including one selected from the following: At least two imaging and/or measurement devices of the group: a white light imaging device, a fluorescent imaging device, an infrared light imaging device and/or an optical coherent tomography device.

Certain aspects of the present invention relate to a method for imaging and/or measuring the retinal fundus of a subject, the method comprising using at least two of the following to make one The retinal fundus of one of the subjects is imaged and/or the retinal fundus of one of the subjects is measured: a white light imaging device, an infrared light imaging device, a fluorescent imaging device and/or an optical coherent tomography device.

Certain aspects of the present invention relate to an imaging device for measuring and/or imaging the retinal fundus of a subject. The imaging device includes: a binocular-shaped housing , Which includes: a first housing section, which includes a first opening configured to be placed adjacent to a first eye of a subject, and a second housing section, which includes a through set State to be placed adjacent to a second opening of a second eye of the subject; and at least one imaging and/or measurement device formed by the first housing section and/or the second housing area A segment support, the at least one imaging and/or measurement device is configured to image the retinal fundus of the subject and/or measure the retinal fundus of the subject.

Certain aspects of the present invention relate to a device for performing optical coherence tomography (OCT) on the fundus of the retina of a subject. The device includes: a plurality of light sources configured to emit light; an interference An instrument configured to receive the light from the plurality of light source components, divide the light between a reference component and a sampling component, illuminate one of the eyes of the subject through the sampling components, and recombine the light from the reference components And the light of the sampling components; and an image sensor configured to detect the recombined light from the interferometer.

Certain aspects of the present invention relate to a device for performing optical coherence tomography on the fundus of the retina of a subject. The device includes: a light source configured to emit light; and an interferometer Configured to receive the light from the light source, divide the light between the reference component and the sampling component, illuminate one of the subject's eyes through the sampling components, and recombine the light from the reference components and the sampling components ; And an image sensor configured to detect the recombined light from the interferometer.

Some aspects of the present invention relate to a device for performing time-domain optical coherence tomography on the fundus of the retina of a subject. The device includes: a light source configured to emit light; and a Michelson ( Michaelson) interferometer, which is configured to receive the light from the light source, divide the light between a reference component and a sampling component, illuminate one of the eyes of the subject through the sampling components, and recombine from the reference components And the light of the sampling components; and an image sensor configured to detect the recombined light from the Michelson interferometer in two image frames obtained at intervals of less than 100 milliseconds.

Some aspects of the present invention relate to a device for imaging and/or measuring the retinal fundus of a subject. The device includes: a housing and a white light imaging device A device supported by the casing and a fluorescent imaging device supported by the casing, wherein the white light imaging device and the fluorescent imaging device share at least a part of a common optical path in the casing.

Certain aspects of the present invention relate to a method that includes imaging the retinal fundus of a subject using a white light imaging device and a fluorescent imaging device that at least partially share an optical path.

Certain aspects of the present invention relate to a method comprising: imaging the retinal fundus of a subject using one of at least two imaging and/or measuring devices selected from the group consisting of And/or measure the retinal fundus of a subject: a white light imaging device, a fluorescent imaging device, and an optical coherence tomography device; and determine the subject based on an image captured during imaging and/or measurement. Medical status of one of the subjects.

Some aspects of the present invention relate to a method comprising: using at least one of a white light imaging device, a fluorescent imaging device, and an optical coherent tomography device to make the retina of a subject Fundus imaging and/or measurement of a subject's retinal fundus, and identification of the subject based on the image and/or measurement.

Certain aspects of the present invention relate to a method comprising: imaging the retinal fundus of a subject using one of at least two imaging and/or measuring devices selected from the group consisting of And/or measure the retinal fundus of a subject: a white light imaging device, a fluorescent imaging device, and an optical coherence tomography device; and based on the image and/or measurement to obtain a safe deposit of one of the subjects take.

Certain aspects of the present invention relate to a method comprising: imaging the retinal fundus of a subject using one of at least two imaging and/or measuring devices selected from the group consisting of And/or measure the fundus of the retina of a subject: a white light imaging device, a fluorescent imaging device, an optical coherence tomography device; and diagnose a medical condition of the subject based on the image and/or measurement .

Certain aspects of the present invention relate to a method comprising: imaging the retinal fundus of a person using fluorescence lifetime imaging and/or optical coherence tomography imaging and/or measuring the retinal fundus of a person, and identifying the person And/or obtain safe access for one of the people and/or determine a health state of the person based on the image and/or measurement and/or diagnose a medical condition of the person.

Some aspects of the present invention relate to a device for retinal imaging and/or measurement, which includes at least two imaging and/or measurement devices selected from the group consisting of: a white light imaging Device, a fluorescent imaging component and an optical coherent tomography component; and at least one modularized light transmission, reflection and/or refraction element, which is in at least one of the at least two imaging and/or measurement devices One light path.

Some aspects of the present invention relate to a device for retinal imaging and/or measurement, which includes: a white light imaging and/or measurement device, a fluorescent imaging and/or measurement device, and at least one A modularized light transmission, reflection and/or refraction element is in a light path of at least one of the white light imaging and/or measurement device and the fluorescent imaging and/or measurement device.

Aspects of the present invention provide improved techniques for imaging the retinal fundus of a subject. Certain aspects pertain to an imaging device that can be substantially binocular and/or can accommodate multiple imaging devices configured to provide multiple corresponding modes for imaging the subject's retinal fundus. Some aspects relate to the use of white light, fluorescent light, infrared light (IR), optical coherent tomography (OCT), and/or other imaging modes that can be used by a single imaging device to image the eyes of a subject. Certain aspects relate to improvements in white light, fluorescence, IR, OCT, and/or other imaging technologies that can be used alone or in combination with other technologies. Certain aspects are related to multi-modal imaging techniques that enable the determination of the health status of a subject. The imaging equipment and technologies described in this article provide medical-grade imaging quality and can be produced or performed at low cost, thus increasing the utilization of medical-grade imaging.

The inventor has recognized and should understand that a person's eyes provide a window into the body, which can be used not only to determine whether the person has an eye disease, but also to determine the person's general health status. However, conventional systems that make fundus imaging only provide rough information about the subject's eyes and cannot provide sufficient information to diagnose certain diseases. Therefore, in some embodiments, multiple imaging modes are used to more comprehensively image the fundus of a subject. For example, two or more techniques can be used to simultaneously image the fundus. In some embodiments, the techniques of optical imaging, fluorescent imaging, and optical coherent tomography can be used to provide multi-mode imaging of the fundus. The inventor has realized that compared with conventional two-dimensional imaging, by using multi-mode imaging, more information about the fundus can be obtained than can be used to determine the health of the subject. In some embodiments, two or more of two-dimensional optical imaging, optical coherence tomography (OCT), fluorescence spectral imaging, and fluorescence lifetime imaging (FLIM) can be used to provide a multi-dimensional image of the fundus. By way of example, one of two-dimensional optical imaging, optical co-modulation tomography (OCT), fluorescence spectral imaging, and fluorescence lifetime imaging (FLIM) is jointly used to provide five-dimensional imaging of the fundus.

The inventors have recognized and should understand that the limitations of conventional two-dimensional optical imaging of the fundus can be overcome by providing one or more of the aforementioned additional imaging modes. For example, OCT provides information about the characteristics of the fundus located below the surface of the fundus. This information cannot be obtained by conventional imaging techniques. Similarly, fluorescence imaging (using spectral and/or lifetime distinction) provides information about the molecular identity of the fundus and/or the presence or absence of biomarkers (if used) that cannot be distinguished using conventional optical imaging or OCT.

The inventor has recognized and should understand that the information of these additional dimensions contains additional information that can be used by an expert and/or machine learning technology to diagnose a wide range of diseases that are not limited to eye health but include the general health of the subject. News. Therefore, certain embodiments relate to a way to determine (for example) ophthalmic health, major organs, the presence of an infection, cardiovascular health, inflammation, and/or neurological health, and the health of an individual (including a person suffering from certain diseases). Health status tendency) real-time universal diagnostic equipment. By way of example, 34% of cardiovascular diseases can be effectively treated by identifying at-risk patients at an early stage. It is possible to diagnose and prevent blindness in children by screening premature babies for glaucoma and other eye diseases. The inventors have recognized that diagnostic tools such as the devices described in certain embodiments provide non-invasive techniques for determining whether a subject has a condition or is susceptible to such a condition.

The inventor has further recognized and should understand that making the device portable, hand-held and affordable will have the greatest impact on global health. Countries or regions that cannot afford specialized facilities for diagnosing certain diseases and/or do not have medical experts who analyze data from imaging tests are often left behind and harm the overall health of the population. A portable device that can be carried to any low-income community allows more access to important health care diagnoses. Therefore, certain embodiments relate to a device containing multiple modes for imaging the fundus in a housing, the device being portable, and in some instances hand-held. In some embodiments, the device has a binocular form factor so that a subject can lift the device to the eye for fundus imaging. In some embodiments, one or more of the imaging modes can share optical components to make the device more compact, efficient, and cost-effective. For example, an optical imaging device and a fluorescent imaging device can be housed in the first half of the binocular housing of the equipment and the OCT device can be housed in the second half of the binocular housing. Using this device, the subject's eyes can be imaged simultaneously using different devices. For example, the left eye of the subject can be imaged using an optical imaging device and/or a fluorescent imaging device, and the right eye of the subject can be imaged using an OCT device. After the initial imaging is completed, the subject can reverse the orientation of the binocular device so that each eye is then measured with a device placed in the other half of the binocular housing, for example, the left eye uses an OCT device to image and The right eye is imaged using an optical imaging device and/or a fluorescent imaging device. To ensure that the device can be operated in two orientations, the front surface of the device placed near the subject's eyes can be substantially symmetrical. Additionally or alternatively, the two halves of the housing of the device can be connected by a hinge that allows the two halves to be adjusted to any orientation.

The inventor has further recognized and should understand that providing an interface to a deep learning system for the device to enable the system to learn and become smarter allows easy use by non-professionals. In low-income communities, access to experts who can operate complex equipment and/or analyze the images obtained from this equipment is limited. In addition, the device can communicate with a smart device (for example, a cellular phone or tablet) and/or a cloud-based storage device in any direction, so that the device can be controlled by the smart device and/or the cloud and/or upload images to the device Smart device and/or cloud. By providing a device that interfaces with a deep learning system, the multi-modal images acquired by the device of certain embodiments can be automatically analyzed to determine one or more health indicators of the subject, without needing to be at the point of care One of the experts.

I. Multi-mode imaging equipment

The inventor has developed a new and improved imaging device with enhanced imaging functionality and a multifunctional form factor. In some embodiments, the imaging device described herein may include a plurality of imaging devices, such as at least two components selected from OCT, IR, white light and/or FLIM devices in a common housing. For example, a single imaging device may include a housing that is shaped to support various imaging devices (white light, IR, fluorescent, and/or OCT, etc.) in the housing. In some embodiments, different imaging devices can be divided between the two sides of the housing, where the imaging devices on each side of the housing are configured to image one of the subject's eyes. In some embodiments, all imaging devices can be configured to image the same eye in the subject's eyes. In some embodiments, a single multi-mode imaging device positioned in a portion of the housing can be configured to support multiple imaging modes (eg, IR and OCT, white light, and FLIM, etc.). In some embodiments, the housing may further include an electronic device for performing imaging, processing or preprocessing images, and/or accessing the cloud for image storage and/or transmission. In some embodiments, the on-board electronic device of the imaging device can be configured to determine the health or medical condition of one of the users.

In certain embodiments, the imaging device described herein may have a form factor that is beneficial for imaging (eg, simultaneously) both of a person's eyes. In some embodiments, the imaging devices described herein may be configured to use a different imaging device of one of the imaging devices to image each eye. For example, as described further below, the imaging device may include a pair of lenses held in a housing of the imaging device for aligning with a person's eyes, and the pair of lenses may also be separate imaging devices of the imaging device alignment. In some embodiments, the imaging device may include a substantially binocular form factor, with an imaging device positioned on each side of the imaging device. During the operation of the imaging device, one can simply flip the vertical orientation of the imaging device (for example, by rotating the device around an axis parallel to the direction in which imaging is performed). Therefore, the imaging device can switch from using a first imaging device to image the right eye of a person to using a second imaging device to image the right eye, and similarly, from using the second imaging device to image the left eye of a person to using The first imaging device images the left eye. In some embodiments, the imaging device described herein can be configured to be installed on a workbench or table, such as a stand. For example, the stand may allow the imaging device to rotate around one or more axes to facilitate rotation by a user during operation.

It should be understood that the aspect of the imaging device described in this article can be implemented using a form factor that is different from the substantially binocular shape. For example, an embodiment having a form factor that is different from a substantially binocular shape can be additionally configured in the manner described herein in connection with the exemplary imaging device described below. For example, these imaging devices may be configured to use one or more imaging devices of the imaging devices to simultaneously image one or both of a person's eyes.

An example of an imaging device according to one of the technologies described herein is illustrated in FIGS. 1A to 1B. As shown in FIG. 1A, the imaging device 100 includes a housing 101 having a first housing section 102 and a second housing section 103. In some embodiments, the first housing section 102 can accommodate a first imaging device 122 of the imaging device 100, and the second housing section 103 can accommodate a second imaging device 123 of the imaging device. As illustrated in FIGS. 1A to 1B, the housing 101 is substantially binocular-shaped.

In some embodiments, the first imaging device 122 and the second imaging device 123 may include an optical imaging device, a fluorescent imaging device, and/or an OCT imaging device. For example, in one embodiment, the first imaging device 122 may be an OCT imaging device, and the second imaging device 123 may be an optical and fluorescent imaging device. In some embodiments, the imaging apparatus 100 may include only a single imaging device 122 or 123, such as only one optical imaging device or only one fluorescent imaging device. In some embodiments, the first imaging device 122 and the second imaging device 123 may share one or more optical components, such as lenses (for example, converging, diverging, etc.), mirrors, and/or other imaging components. For example, in some embodiments, the first imaging device 122 and the second imaging device 123 may share a common optical path. It is envisaged that the devices can be operated independently or collectively. Each device can be an OCT imaging device, each device can be a fluorescent imaging device, or both devices can be an OCT imaging device or a fluorescent imaging device. Both eyes can be imaged and/or measured simultaneously, or each eye can be imaged and/or measured separately.

The housing sections 102 and 103 can be connected to a front end of the housing 101 by a front housing section 105. In an illustrative embodiment, the front housing section 105 is shaped to accommodate the facial contour of a person, such as having a shape that conforms to a human face. When accommodating a person's face, the front housing section 105 can further provide a line of sight from the person's eyes to the imaging device 122 and/or 123 of the imaging device 100. For example, the front housing section 105 may include a first opening 110 and a second opening 111, which correspond to the respective openings in the first housing section 102 and the second housing section 103 so as to be An optical device 122 and a second optical device 123 provide a minimally obstructed optical path between the human eye. In some embodiments, the openings 110 and 110 may be covered with one or more transparent windows that may include glass or plastic (for example, each has its own window, has a common window, etc.).

The first housing section 102 and the second housing section 103 may be connected by a rear housing section 104 at a rear end of the housing 101. The rear housing section 104 can be shaped to cover the ends of the first housing section 102 and the second housing section 103 so that light in an environment of the imaging device 100 does not enter the housing 101 and does not interfere with the imaging device 122 or 123.

In some embodiments, the imaging device 100 may be configured to be communicatively coupled to another device, such as a mobile phone, desktop, laptop or tablet computer, and/or smart watch. For example, the imaging device 100 may be configured to establish a wired and/or wireless connection to one of these devices, such as via USB and/or a suitable wireless network. In some embodiments, the housing 101 may include one or more openings to accommodate one or more electrical (eg, USB) cables. In some embodiments, the housing 101 may have one or more antennas disposed thereon for transmitting wireless signals to and/or receiving wireless signals from these devices. In some embodiments, imaging devices 122 and/or 123 may be configured to interface with cables and/or antennas. In some embodiments, the imaging device 122 and/or 123 may receive power from a cable and/or antenna, such as to charge a rechargeable battery housed in the housing 101.

During the operation of the imaging device 100, a person using the imaging device 100 can place the front housing section 105 on the person's face so that the person's eyes are aligned with the openings 110 and 111. In some embodiments, the imaging device 100 may include a gripping member (not shown) coupled to the housing 101 and configured to be grasped by a person's hand. In some embodiments, the gripping member can be formed by using a soft plastic material, and can be ergonomically shaped to accommodate human fingers. For example, a person can use both hands to hold the gripping member, and place the front housing section 105 on the person's face so that the person's eyes are aligned with the openings 110 and 111. Alternatively or additionally, the imaging device 100 may include a mounting component coupled to the housing 101 and configured to mount the imaging device 100 to a mounting arm, such as mounting the imaging device 100 to a workbench or other equipment ( Not shown). For example, when using the mounting part to install, the imaging device 100 can be stabilized in one position for one person to use, and the person does not need to hold the imaging device 100 in place.

In some embodiments, the imaging device 100 may use a fixture such as a visible light projection from the imaging device 100 toward the eyes of the person along a direction in which the openings 110 and 111 are aligned with the eyes of the person, for example. According to various embodiments, the fixture may be a bright spot, such as a circular or elliptical spot, or an image, such as an image or a house or some other object. The inventor has realized that a person will usually move both eyes in the same direction to focus on an object even when only one eye perceives the object. Therefore, in certain embodiments, the imaging device 100 may be configured to provide a fixture to only one eye, such as using only one opening 110 or 111. In other embodiments, the fixture may be provided to both eyes, such as using both openings 110 and 111.

Figure 2 illustrates one of the other embodiments of the imaging device 200 according to certain embodiments. As shown, the imaging apparatus 200 includes a housing 201 in which one or more imaging devices (not shown) can be housed. The housing 201 includes a first housing section 202 and a second housing section 203 connected to a central housing part 204. The central housing portion 204 may include and/or operate to connect the first housing section 202 and the second housing section 203 and can rotate about a hinge of one of the first housing section 202 and the second housing section 203 . By rotating the first and/or second housing section 202 and/or 203 around the central housing portion 204, one of the separation of the first housing section 202 and the second housing section 203 can be increased or decreased accordingly distance. Before or during the operation of the imaging device 200, a person can rotate the first housing section 202 and the second housing section 203 to accommodate the separation of the human eye by a distance, such as to promote the human eye and the first housing section 203. The openings of the housing section 202 and the second housing section 203 are aligned.

The first housing section 202 and the second housing section 203 can be configured in combination with the manner described in FIGS. 1A to 1B for the first housing section 102 and the second housing section 103. For example, each section can accommodate one or more imaging devices, such as an optical imaging device, a fluorescent imaging device, and/or an OCT imaging device. In Figure 2, each section 202 and 203 is coupled to a single one of the front housing sections 205A and 205B. The front housing sections 205A and 205B may be shaped to conform to the facial contour of a person using the imaging device 200, such as to conform to the part of the face of a person who is adjacent to the eyes of the person. In one example, the front housing sections 205A and 205B can be formed using a flexible plastic that can conform to the contours of a person's face when placed on a person's face. The front housing sections 205A and 205B may have respective openings 211 and 210, which correspond to the openings of the first housing section 202 and the second housing section 203, such as those of the first housing section 202 and the second housing section 203. The opening of the housing section 203 is aligned to provide a minimally obstructed optical path from the human eye to the imaging device of the imaging device 200. In some embodiments, the openings 210 and 211 may be covered with a transparent window made of glass or plastic.

In certain embodiments, the center housing section 204 may contain one or more electronic circuits 220 (eg, integrated circuits, printed circuit boards, etc.) for operating the imaging device 200. In some embodiments, one or more processors may be disposed in the center housing section 204, such as to analyze data captured using imaging devices. The central housing section 204 may include wired and/or wireless components that electrically communicate with other devices and/or computers, such as those described for the imaging device 100. For example, the further processing may be performed by a device and/or a computer communicatively coupled to the imaging apparatus 200. In some embodiments, the on-board electronic circuit of the imaging device 200 can process the captured image data based on commands received from these communicatively coupled devices or computers. In some embodiments, the imaging device 200 may initiate an image capturing sequence based on a command received from a device and/or a computer communicatively coupled to the imaging device 200.

As described herein in conjunction with the imaging device 100, the imaging device 200 may include a gripping component and/or a mounting component and/or a fixture.

Figures 3A to 3D illustrate one of the other embodiments of the imaging device 300 according to certain embodiments. As shown in FIG. 3A, the imaging device 300 has a housing 301 that includes a plurality of housing parts 301a, 301b, and 301c. The housing part 301a has a control panel 325, which includes a plurality of buttons for turning on or off the imaging device 300 and for initiating a scanning sequence. FIG. 3B is an exploded view of the imaging device 300, which illustrates the components disposed in the housing 301, such as the imaging devices 322 and 323 and the electronic device 320. According to various embodiments, the imaging devices 322 and 323 may include one or more of the following: a white light imaging component, a fluorescent imaging component, an infrared light (IR) imaging component, and/or an OCT imaging component. In one example, the imaging device 322 may include an OCT imaging device and/or an IR imaging device, and the imaging device 323 may include a white light imaging device and/or a fluorescent imaging device. The imaging device further includes a housing portion 305 before being configured to receive a person's eyes for imaging, for example, as illustrated in FIG. 3C. FIG. 3D illustrates the imaging device 300 resting in the stand 350, as further explained herein.

As shown in FIGS. 3A to 3D, the housing portions 301a and 301b may substantially enclose the imaging device 300, such as by placing all or most of the components of the imaging device 300 between the housing portions 301a and 301b. The housing portion 301c may be mechanically coupled to the housing portions 301a and 301b, such as using one or more screws that fasten the housing 301 together. As illustrated in FIG. 3B, the housing part 301c may have multiple housing parts, such as housing parts 302 and 303 for accommodating the imaging devices 322 and 323. For example, in certain embodiments, the housing portions 302 and 303 may be configured to hold the imaging devices 322 and 323 in place. The housing part 301c further includes a pair of lens parts in which the lenses 310 and 311 are arranged. The housing portions 302 and 303 and the lens portion can be configured to hold the imaging devices 322 and 323 in alignment with the lenses 310 and 311. The housing parts 302 and 303 can accommodate the focusing parts 326 and 327 for adjusting the focus of the lenses 310 and 311. Certain embodiments may further include a fixed connection piece 328. By adjusting (for example, pressing, pulling, pushing, etc.) the fixing connecting piece 328, the housing parts 301a, 301b, and/or 301c can be decoupled from each other, such as for maintenance and/or repair purposes to the components of the imaging device 300 The access.

The electronic device 320 can be configured in combination with the manner described in FIG. 2 for the electronic circuit. The control panel 325 may be electrically coupled to the electronic device 320. For example, the scan button of the control panel 325 can be configured to transmit a scan command to the electronic device 320 to initiate a scan using the imaging devices 322 and/or 323. As another example, the power button of the control panel 325 can be configured to transmit a power-on or power-off command to the electronic device 320. As illustrated in FIG. 3B, the imaging device 300 may further include an electromagnetic shield 324 configured to isolate the electronic device 320 from electromagnetic interference (EMI) sources in the surrounding environment of the imaging device 300. Including the electromagnetic shielding 324 can improve the operation of the electronic device 320 (eg, noise performance). In some embodiments, the electromagnetic shield 324 may be coupled to one or more processors of the electronic device 320 to dissipate heat generated in the one or more processors.

In some embodiments, the imaging device described herein can be configured to be mounted to a stand, as illustrated in the example of FIG. 3D. In FIG. 3D, the imaging device 300 is supported by a bracket 350, and the support includes a base 352 and a holding portion 358. The base 352 is illustrated as including a substantially U-shaped support portion and has a plurality of feet 354 attached to a bottom side of the support portion. The base 352 may be configured to support the imaging device 300 on a workbench or table top, such as illustrated in the figure. The holding portion 358 may be shaped to accommodate the housing 301 of the imaging device 300. For example, the outside of one of the sides facing the holding portion 358 may be shaped to conform to the housing 301.

As illustrated in FIG. 3D, the base 352 can be coupled to the holding portion 358 by a hinge portion 356. The hinge portion 356 can permit rotation about an axis parallel to a surface of the support base 352. For example, during the operation of the imaging device 300 and the bracket 350, a person can rotate the holding portion 358 in which the imaging device 300 is placed to an angle that is comfortable for the person to image one or both eyes. For example, a person can sit on a workbench or table supporting bracket 350. In some embodiments, a person can rotate the imaging device 300 around an axis parallel to an optical axis, and the imaging device in the imaging device images the person's eyes along the optical axis. For example, in some embodiments, alternatively or additionally, the bracket 350 may include a hinge part parallel to the optical axis.

In some embodiments, the holding portion 358 (or some other portion of the bracket 350) may include charging hardware configured to transmit power to the imaging device 300 through a wired or wireless connection. In one example, the charging hardware in the cradle 350 may include a power supply coupled to one or a plurality of wireless charging coils, and the imaging device 300 may include a wireless power supply configured to receive power from the coil in the cradle 350 Charging coil. In another example, the charging hardware in the bracket 350 may be coupled to an electrical connector on one of the sides facing the holding portion 358, so that one of the imaging devices 300 is complementary when the imaging device 300 is placed in the holding portion 358 The connector is interfaced with the connector of the bracket 350. According to various embodiments, the wireless charging hardware may include one or more power converters (eg, AC to DC, DC to DC, etc.) configured to provide an appropriate voltage and current to the imaging device 300 for charging. In some embodiments, the stand 350 can house at least one rechargeable battery configured to provide wired or wireless power to the imaging device 300. In certain embodiments, the stand 350 may include one or more power connectors configured to receive power from a stand and a wall outlet, such as a single-phase wall outlet.

In some embodiments, the front housing portion 305 may include multiple portions 305a and 305b. The portion 305a can be formed using a mechanically elastic material, and the front portion 305b can be formed using a mechanically compliant material, so that the front housing portion 305 is comfortable for a user to wear. For example, in some embodiments, the portion 305a can be formed using plastic and the portion 305b can be formed using rubber or silicone. In other embodiments, the front housing portion 305 can be formed using a single mechanically elastic or mechanically compliant material. In some embodiments, the portion 305b may be disposed on the outer side of the front housing portion 305, and the portion 305a may be disposed within the portion 305b.

II. Optical coherent tomography and infrared light (IR) Imaging technology

The inventors have developed improved OCT and IR imaging techniques that can be implemented individually or in combination in a multi-mode imaging device. In certain embodiments, the combination of OCT and IR imaging components described further herein may be included together in one or both of the first and second housing sections of a multi-mode imaging device. In certain embodiments, the OCT imaging component may be disposed in one of the first or second housing section, and the IR imaging component may be disposed in the other housing section. The inventor has realized that combining OCT and IR components allows at least a part of the components to share an imaging path to reduce the form factor and produce the cost of a multi-mode imaging device.

In some embodiments, the OCT technology can focus the broadband light on a subject's retinal fundus and also focus on a reference surface, and then combine the light reflected from the subject's retinal fundus with the reference surface The reflected light obtains information about the structure in the fundus of the retina. The information can be determined based on the detected interference between the light received from the subject's retinal fundus and the light received from the reference surface. In some embodiments, OCT technology can provide depth imaging information about the structures beneath the surface of the retinal fundus. In some embodiments, a beam splitter can split the source light between a sampling component that provides light to the fundus of the subject's retina and a reference component that provides light to a reference surface. The beam splitter can then combine the light reflected from the sample and reference components and provide the combined light to the interferometer. In some embodiments, the interferometer can detect interference by determining a phase difference between the sampled light and the reference light.

In some embodiments, OCT can be performed in the time domain to scan the depth of the retinal fundus of a subject. For example, in some embodiments, the difference in path length between the reference component and the sampling component can be adjusted. In some embodiments, OCT can be performed in the frequency domain by using an interferometer to detect interference in a specific light spectrum. The embodiments described herein can be configured to perform time domain and/or frequency domain OCT.

In some embodiments, the IR imaging component can perform IR imaging on the retinal fundus of the subject, and the IR imaging can provide depth and/or temperature information of the retinal fundus of the subject. In some embodiments, at least some of the IR and OCT imaging components described herein can share an optical path. For example, in some embodiments, at least some of the same optical components may be used to perform IR imaging and OCT imaging at different times, as described herein.

It should be understood that the OCT and IR technologies described herein can be used alone or in combination in a single-mode or multi-mode imaging device. Moreover, certain embodiments may include only OCT components or only IR components, because the techniques described herein can be implemented individually or in combination.

4A to 4C illustrate a multi-mode imaging device 400 including a combined OCT/IR imaging device according to some embodiments, the combined OCT/IR imaging device having an OCT source component 410, a sampling component 420, a reference component 440, and a detection测Component 450. 4A is a top perspective view of the imaging device 400, FIG. 4B is a top view of the imaging device 400, and FIG. 4C is a side perspective view of the imaging device 400. In some embodiments, the source component 410 may include one or more light sources, such as a super luminous diode, and optical components configured to focus light from the source. The source assembly 410, the light source 412, the cylindrical lens 416, and the beam splitter 418 are shown in FIGS. 4A to 4C. In some embodiments, the sampling component 420 may be configured to provide light from the source component 410 to the eye of a subject via one or more optical components. The sampling assembly 420, the scanning mirror 422, and the fixed dichroic mirror 424 are shown in FIGS. 4A to 4C. In some embodiments, the reference component 440 may be configured to provide light from the source component 410 to one or more reference surfaces via one or more optical components. The reference component 440, the dispersion compensator 442, the cylindrical lens 444, the folding mirror 446, and the reference surface 448 are shown in FIGS. 4A to 4C. In some embodiments, the detection component 450 may be configured to receive reflected light from the sampling component 420 and the reference component 440 in response to providing light from the source component 410 to the sampling component 420 and the reference component 440. 4A to 4C show the detection component 450, aspheric lens 452, plano-concave lens 454, achromatic lens 456, transmission grating 458, achromatic lens 460 and OCT camera 468. The fixed display 476 is also shown in Figure 4C.

FIG. 4D is a top view of the imaging device 400 according to some embodiments, with the top part of the housing removed. Some of the reference components 440, such as the folding mirror 446 and the reference surface 448, are shown in FIG. 4D. 4E is a side perspective view of the components of the OCT and IR imaging device of the imaging device 400 according to some embodiments. In FIG. 4E, the IR camera 470, the light source 412, the scanning mirror 422, and the OCT motor scanning window 451 are shown.

This document includes other examples of the source component 410, the sampling component 420, the reference component 440, and the detection component 450 that can be included in the imaging device 400 with reference to FIGS. 5A to 5I.

FIG. 5A is a top view of an exemplary source assembly 510 according to some embodiments. In some embodiments, the source component 510 may be included in the OCT imaging device 400 as the source component 410. In some embodiments, the source component 510 may be configured to provide light to other OCT components, such as sampling and/or reference components. For example, the source element 510 can be configured to provide light to the sampling element for the eyes of a subject and the reference element for providing to a reference surface, so that the response to the light provided through the sampling element can be self-received. The light detected by the tester’s eyes is compared with the light provided to the reference surface.

In FIG. 5A, the source assembly 510 includes a light source 512, a beam expander 514, a cylindrical lens 516, and a beam splitter 518. In some embodiments, the light source 512 may include a super luminous diode. In some embodiments, the light source 512 may be configured to provide polarized light (eg, linear, circular, elliptical, etc.). In some embodiments, the light source 512 may be configured to provide broadband light, such as including white light and IR light. In some embodiments, the light source 512 may include a superluminescent diode having a spectral width greater than 40 nm and a center wavelength between 750 nm and 900 nm. In one example, the light source 512 may have a center wavelength at 850 nm, where the scattering of the subject's tissue is lower than at other wavelengths. In some embodiments, the light source 512 may include a superluminescent diode having a single lateral spatial pattern. In some embodiments, the light source 512 may include a vertical cavity surface emitting laser (VCSEL) with an adjustable mirror on one side. In some embodiments, the VCSEL can use a micromechanical movement (MEM) to have a tuning range greater than 100 nm. In some embodiments, the light source 512 may include a plurality of light sources, and the plurality of light sources together have a wide spectral width. In one example, the light source 512 may include a plurality of laser diodes in close proximity. The laser diode system is cost-effective because it is cheaper than super-luminescent diodes and has higher brightness and shorter pulse duration than super-luminescent diodes. In some embodiments, the spectrum of each laser diode can be superimposed on a single wavelength by a grating on the CMOS sensor.

In some embodiments, the beam expander 514 may include a cylindrical beam expander. In some embodiments, the beam expander 514 may include an aspheric lens. In certain embodiments, the beam expander 514 and/or the cylindrical lens 516 may be configured to form the light from the light source 512 into an elongated line for scanning the fundus of the retina of a subject. For example, when the light reaches the fundus of the retina of the subject, the light can be focused in a first direction and elongated in a second direction perpendicular to the first direction. In some embodiments, a folding mirror can be positioned between the beam expander 514 and the cylindrical lens 516. In some embodiments, the cylindrical lens 516 may be configured to spatially focus the source light on a scanning mirror 522, which may include other sampling components coupled to the source component 510. In some embodiments, the scanning mirror 522 may be actuated using one or more stepping motors, galvanometers, polygon scanners, microelectromechanical switch (MEMS) mirrors, and/or other moving mirror devices. As shown in FIG. 5A, the cylindrical lenses 516 face opposite directions, with the rounded surfaces facing each other.

In certain embodiments, the beam splitter 518 may be configured to couple light from the light source 512 to other OCT components, such as sampling components and/or reference components. In certain embodiments, the beam splitter 518 can be configured to couple light to a sampling component such as a scanning mirror 522, which in turn can be configured to provide light to other sampling components. In some embodiments, the beam splitter 518 can be configured as a long pass filter. In some embodiments, the beam splitter 518 may be configured to reflect the white source light and transmit the IR source light incident from the light source 512. In certain embodiments, the beam splitter 518 may be configured to transmit IR light to the sampling component and reflect white light to the reference component. In some embodiments, the beam splitter 518 may be configured to provide half of the source light to the sampling component and half of the source light to the reference component. In certain embodiments, the beam splitter 518 may be configured to provide more source light to the sampling component than to the reference component. In certain embodiments, the beam splitter 518 may be further configured to provide the interfering light self-sampling and reference component to the detecting component. In some embodiments, the beam splitter 518 may be a plate beam splitter.

FIG. 5B is a side view of the exemplary sampling assembly 520 according to some embodiments, and FIG. 5C is a top view of the sampling assembly 520. In some embodiments, the sampling component 520 may be included in the OCT imaging device 400 as the sampling component 420. As shown in FIGS. 5B to 5C, the sampling component includes a scanning mirror 522, a fixed dichroic mirror 524, an IR fundus dichroic mirror 526, a plano-convex lens 528, a bi-concave lens 530, a plano-concave lens 532, and a plano-convex lens 534. In some embodiments, the fixed dichroic mirror 524 may be configured to reflect some of the source light toward a fixed component such as a fixed display. In some embodiments, the fixed dichroic mirror 524 can be configured as a long pass filter, so that short wavelength (eg, visible) light is reflected by the fixed dichroic mirror 524. In some embodiments, the IR fundus dichroic mirror 526 can be configured as a short-pass filter so that long-wavelength (for example, IR) light is reflected by the IR fundus dichroic mirror 526. In some embodiments, the IR dichroic mirror 526 can be configured to reflect IR light and transmit white light. In certain embodiments, lenses 528, 530, 532, and/or 534 can be adjusted to provide diopter compensation. In certain embodiments, these lenses can be adjusted to compensate subjects with different corrections, hyperopia, or hyperopia. 5B and 5C further illustrate how the sampling component 520 can focus the source light on the retina of a subject. As shown in FIG. 5B, when viewed from the side, the light provided by the sampling component 510 can be focused on a point on the back of the eye. As shown in FIG. 5C, the light provided by the sampling component 510 can be focused on a point (for example, the pupil) at the front of the eye, so that when viewed from the top, the light expands in a dotted line at the back of the eye.

FIG. 5D is a perspective view of the source component 510 and the sampling component 520 in an optical coupling configuration according to some embodiments. In FIG. 5D, the scanning mirror 522 is shown configured to couple light from the source component 510 to the sampling component 520. In some embodiments, the scanning mirror 522 can be configured to couple IR light from the source component 510 to the sampling component 520. In some embodiments, the sampling component 520 can focus the light reflected back from the eye of a subject on the scanning mirror 522 to provide the reflected light to the beam splitter 518. In certain embodiments, the beam splitter 518 may be further configured to provide reflected light to the detection component.

Figure 5E is a perspective view of an exemplary reference assembly 540 according to certain embodiments. In some embodiments, the reference component 540 may be included in the OCT imaging device 400 as the reference component 440. As shown in FIG. 5E, the reference component 540 includes a dispersion compensator 542, a collimating lens 544, a folding mirror 546, and a reference surface 548. As shown in FIG. 5E, the beam splitter 518 of the source component 510 may be configured to reflect white light to the reference component 540. In some embodiments, the dispersion compensator 542 may include a mirror. In some embodiments, the dispersion compensator 542 may be configured to provide the same amount of dispersion to the light passing through the reference element 540 as the amount of dispersion provided by the eye of a subject to the light passing through the sampling element 520. In some embodiments, the collimating lens 544 may include a cylindrical plano-convex lens. In certain embodiments, the reference surface 548 may include wedge glass. In some embodiments, the reference surface 548 may include a scattering reflector configured to reflect reflections similar to the human eye, since each reflection point acts as a point source. In some embodiments, the reference surface 548 may include a mirror. In some embodiments, the reference component 540 may have an adjustable path length of +/- 5 mm.

FIG. 5F is a perspective view of the source component 510 and the reference component 540 in an optical coupling configuration according to some embodiments. In FIG. 5F, the beam splitter 518 is shown configured to couple the light source 512 of the light source component 510 to the reference component 540. In certain embodiments, the reference component 540 can be configured to return light from the reference surface 548 to the beam splitter 518, which can provide the returned reference light to the detection component.

FIG. 5G is a top view of an exemplary detection component 550 according to some embodiments. In some embodiments, the detection component 550 can be included in the OCT imaging device 400 as the detection component 450. As shown in FIG. 5G, the detection component 550 includes an aspheric lens 552, a plano-concave lens 554, an achromatic lens 556, a transmission grating 558, an achromatic lens 560, a polarizer 562, a field lens (including a plano-convex lens 564 and a plano-concave lens) 566) and OCT camera 568. In certain embodiments, the aspheric lens 552, the plano-concave lens 554, and the achromatic lens 556 can be configured to expand the detected light received from the beam splitter 518. For example, the received light may include the reflected light from the eyes of a subject from the sampling element, and the light reflected by the reference surface 548 of the reference element 540. In some embodiments, the OCT camera 568 may include an interferometer, such as a Mach-Zehnder interferometer and/or a Michelson interferometer.

In some embodiments, the transmission grating 558 can improve the spectral signal-to-noise ratio of the light received by the OCT camera 568. In some embodiments, the transmission grating 558 may be configured to provide light to the OCT camera 568 at normal incidence. In some embodiments, the transmission grating 558 can enhance the noise performance of the transfer function of the OCT camera 568.

In certain embodiments, the transmission grating 558 can be configured to increase symmetry and reduce aberrations in the received light. In some embodiments, the transmission grating 558 may be configured to transmit received light at a Littrow angle. In certain embodiments, the transmission grating 558 can be configured to split the received light by wavelength. In some embodiments, the transmission grating 558 may have a dispersion grating between 1200 lines/mm and 1800 lines/mm. In some embodiments, the transmission grating 558 may have a dispersion grating between 1500 lines/mm and 1800 lines/mm. In some embodiments, the transmission grating 558 may have a dispersion grating of 1800 lines/mm.

In certain embodiments, the achromatic lens 560 and the field lens can be configured to focus light from the transmission grating 558 toward the OCT camera 568, which can be configured to detect the focused light. The polarizer 562 is shown as being positioned between the achromatic lens 560 and the field lens. In some embodiments, the polarizer 562 may have the same polarization as the light source 512 of the source assembly 510, so that light having a different polarization from the light source 512 can be filtered out. In some embodiments, the polarizer 562 may have a different polarization from the light source 512, such as for transmitting light received by the eye of a subject with a different (eg, opposite) polarization and having been reflected by the eye. In some embodiments, the field lens can be configured to flatten the field of received light. In some embodiments, the field lens can be configured to adjust the chief ray angle of the received light. In some embodiments, the field lens can be configured to affect the divergent rays in the received light.

FIG. 5H is a perspective view of the source component 510, the reference component 540, and the detection component 550 in an optical coupling configuration according to some embodiments. In FIG. 5H, the beam splitter 518 is shown configured to couple light from the source component 510 to the reference component 540 and provide light received from the reference component 540 to the detection component 550.

FIG. 51 is a perspective view of the sampling component 520 coupled to the detection component 550, the IR camera 570, and the fixed component (including the focus lens 574 and the fixed display 576) according to some embodiments. As shown in FIG. 5I, lenses 528, 530, and 534 may be configured as pupil relay components 590. In some embodiments, the biconcave lens 530 can be configured to provide a negative focal length. In some embodiments, the pupil relay component can provide comparable spectral and spatial expansion and/or reduce spatial expansion. In one example, the pupil relay component can reduce spatial expansion by a factor of 5.

As shown in FIG. 5I, at least some of the IR light received from the eyes of a subject via lenses 534, 530, and 528 can be reflected off the IR fundus dichroic mirror 526 and provided to the IR camera 570 by the focusing lens 527. In some embodiments, the focusing lens 572 can be configured to illuminate in a ring shape. For example, the focusing lens 572 may include an IR light emitting diode (LED) ring. In some embodiments, the IR LED may have a wavelength of 910 nm. In some embodiments, the IR LED may have a wavelength of 940 nm. As also shown in FIG. 5I, at least some of the visible light received from the subject's eyes can be reflected off the fixed dichroic mirror 524 and provided to the fixed display 576 by the focusing lens 574. As shown in FIG. 5I, some visible and IR light is also provided to the detection component 550 through the scanning mirror 522 for OCT imaging. In FIG. 5I, lenses 528, 530, and 534 provide a common optical path for OCT and IR imaging.

6A is a top perspective view of an alternative embodiment of a multi-mode imaging apparatus 600 including a combined optical coherent tomography (OCT) and infrared (IR) imaging device according to some embodiments. In some embodiments, the components of the imaging device 600 can be configured in combination with the methods described in FIGS. 4A to 4C and 5A to 5I. As shown in FIG. 6A, the imaging device 600 includes an OCT and IR component 602, which includes a source component, a sampling component, a reference component, and a detection component. The sampling component, beam splitter 618, scanning mirror 622, and IR fundus dichroic mirror 626 are shown in FIG. 6A. In some embodiments, the beam splitter 618 may be a plate beam splitter. The detection component, achromatic lenses 654 and 656, transmission grating 658, and OCT camera 668 are shown in FIG. 6A. FIG. 6A also shows a fixed display 674 and a diopter component, which includes a diopter motor 682 and a diopter mechanism 684. In some embodiments, the OCT camera 668 may include an interferometer, such as a Mach-Zehnder interferometer and/or a Michelson interferometer. In some embodiments, the scanning mirror 622 may be actuated using one or more stepper motors, galvanometers, polygon scanners, microelectromechanical switch (MEMS) mirrors, and/or other moving mirror devices. As shown in FIG. 5A, the cylindrical lenses 516 face opposite directions, with the rounded surfaces facing each other.

FIG. 6B is a side perspective view of a component 602 of the imaging device 600 according to some embodiments. FIG. 6B shows the OCT and IR components 602, the IR camera 664, and the fixed components. The fixed components include a fixed lens 672 and a fixed display 674. The OCT and IR components 602 include a source component, a sampling component, a reference component, and a detection component. The source assembly, light source 612, and beam splitter 618 are shown in FIG. 6B, where the light source 612 can be a super luminous diode. 6B shows the sampling component, scanning mirror 622, plano-convex lens 630, double-concave lens 632, and plano-convex lens 634. The lenses 630, 632, and 634 are diopter adjustable components 690. In certain embodiments, these lenses can be adjusted to compensate subjects with different corrections, hyperopia, or hyperopia. The detection component, transmission grating 658 and OCT camera 668 are shown in FIG. 6B. Figure 6B also shows the motor and scanning window 651.

FIG. 6C is an exploded view of an alternative component 602' that may be included in the imaging device 600 according to some embodiments. 6C shows the light source 612 and the collimating lens 616 of the source component 610, the dispersion compensator 642, the collimating lens 644 and the reference surface 648 of the reference component 640, and the pickup mirror 652, the reflection grating 658' and the field lens of the detecting component 650 666 and OCT camera 668. In some embodiments, alone or in combination with a cylindrical or aspherical beam expander, the cylindrical lens 616 can be configured to form the light from the light source 612 into an elongated line for scanning a subject. Fundus of the retina. For example, when the light reaches the fundus of the retina of the subject, the light can be focused in a first direction and elongated in a second direction perpendicular to the first direction.

6C also shows the pupil relay lens 690a of the sampling component 620 and the pupil relay lens 690c of the detection component 690c. In some embodiments, the pupil relay lens 690c may include a first lens disposed adjacent to the beam splitter 618, and a second lens disposed adjacent to the reflection grating 658', wherein the first lens has a smaller size than the second lens. A focal length makes the second lens magnify the interference light from the beam splitter 618, thereby reducing the angular range of the interference light. In some embodiments, the reflective grating 658' can be configured to reflect and diffract the interfering light, thereby causing light of different wavelengths to propagate toward the second lens in different directions. In some embodiments, the direction of expansion of different wavelengths may be perpendicular to the direction of the elongated axis of the light. As shown in FIG. 6C, the second lens can focus the diffracted light onto the pickup mirror 652, which reflects the diffracted light toward the OCT camera 668. In some embodiments, the light reflected by the pickup mirror 652 may be transmitted toward the OCT camera 668 through the cylindrical lens pair 666. In some embodiments, the cylindrical lens pair 666 can be configured to flatten the light field and make the light spread in the spectral direction due to the reflective grating 658' between the light spread in the spatial direction of the line. The focal lengths are equal.

In some embodiments, the OCT camera 668 can be configured to use the received light to capture a two-dimensional image. In some embodiments, the OCT camera 668 can be configured to expand the light in two directions, where a first direction corresponds to the spectral expansion of the light attributed to the reflective grating 658', and a second direction corresponds to The spatial expansion of light attributed to the cylindrical lens 616 used to form the light. In some embodiments, the OCT camera 668 can be configured to perform a Fourier transform along the spectral direction to obtain depth information. In some embodiments, a two-dimensional image of the part of the retinal fundus of the subject irradiated by the line corresponding to the elongated direction and depth of the line can be obtained. In some embodiments, the OCT camera 668 can be configured to capture a three-dimensional image. In some embodiments, the OCT camera 668 can be configured to capture multiple images when the component 602' crosses the scan line of the subject's retinal fundus. In some embodiments, each acquired image may correspond to a slice of the fundus of the retina in one of the direction perpendicular to the elongation direction of the line and the direction perpendicular to the depth direction. In one example, 15 to 30 images can be captured, where each image corresponds to a different section of the retinal fundus.

In some embodiments, the component 602' can be configured to cross the scan line of the subject's retinal fundus to acquire multiple images. In some embodiments, a scanning mirror (eg, scanning mirror 622) may be positioned between the beam splitter 618 and the pupil relay lens 690c. In some embodiments, the scanning mirror can be attached to one of the stepping motors (eg, motor and scanning window 651) that is configured to rotate the scanning mirror so that the line illuminates the subject's retinal fundus in different orientations of the scanning mirror. ). In other embodiments, the non-moving part may be used to span the eye scan line. In one example, a fixed display may include a moving fixture object so that scanning can be performed when the subject's eyes follow the fixture object.

FIG. 7A illustrates a block diagram of the OCT component 602 of the imaging device 600 according to some embodiments. As shown in FIG. 7A, the OCT component 602 includes a source component 610, a sampling component 620 (shown in more detail in FIGS. 8 and 11A), a reference component 640, and a detection component 650 (shown in more detail in FIG. 10). The source assembly 610 includes a light source 612 (which is shown as a super luminous diode), a collimator lens 616, and a beam splitter 618. In some embodiments, the collimating lens 616 may include a cylindrical collimating lens and/or an aspheric lens. In FIG. 6, the beam splitter 618 is configured to split the light from the light source 612 between the sampling component 620 and the reference component 640 and direct the reflected light from the sampling component 620 and the reference component 640 to the detection component 650. The scanning mirror 622 of the sampling assembly 620 is also shown in FIG. 6B. The reference component 640 includes a dispersion compensator 642, a collimating lens 644 (in some embodiments, the collimating lens may be a cylindrical collimating lens), and a reference surface 648a (which is shown as a single mirror). In some embodiments, the reference surface 648a may include a scattering reflector configured to reflect reflections similar to the human eye, since each reflection point acts as a point source.

Figure 7B illustrates a block diagram of an alternative component 602'' that may be included in the OCT and IR imaging devices of Figures 6A-6B according to certain embodiments. In some embodiments, the component 602' may be configured to perform off-axis scanning of the fundus of the retina of a subject. For example, in certain embodiments, the folding mirror of the reference surface 648b may be oriented off-axis so that multiple reflections can be provided to the detection component 650 along multiple paths. As shown in FIG. 7B, the component 602'' can be configured in the same manner as the component 602, except that the reference surface 648b of the reference component 640'' includes a pair of folding mirrors. The reference surface 648b is shown as reflecting light to the detection component 650 along multiple paths, where at least one of the paths is spatially offset from the light received through the sampling component 620. FIG. 7B further illustrates the achromatic lens 556 and the OCT camera 668 of the detection component 650.

In some embodiments, off-axis illumination may provide a means to remove DC and/or autocorrelation components that would otherwise interfere with OCT imaging. In some embodiments, off-axis illumination can allow recovery of complex spectra, thereby achieving recovery of complex analysis signals for full-range imaging. In some embodiments, increasing the imaging range can reduce the imaging speed (including sampling fewer spectral signals), and vice versa.

在某些實施例中，可將⍺設定為提供奈奎斯特(Nyquist)速率之50%至90%之間的一空間頻率之一角度(例如，1度至6度之間)。在某些實施例中，在兩個方向上以1.2或更大之因子進行過取樣可提供一更好信雜比及經改良解調。在某些實施例中，預處理一OCT影像可包含裁剪、減去平均光譜(例如，DC分量)及/或採用一或多個窗口函數。在某些實施例中，處理一OCT影像可包含一或多個快速傅立葉變換(FFT，例如，x空間FFT)，解調(例如，將所關注空間頻率移位至基頻)及/或裁剪經接收信號之DC及AC分量。在某些實施例中，處理可進一步包含應用一逆FF及/或k空間重新取樣及快速傅立葉變換。In some embodiments, a camera receives a spatial direction of adjustable light with a relative orientation angle of the irradiated line. In some embodiments, the inter-correlation modulation can be expressed as: I _⍺ (k,x) = I _cc (k,x)e ^{-j ⍺ xq} + I _DC (k,x) + I _AC (k,x) )

In some embodiments, ⍺ can be set to provide an angle of a spatial frequency between 50% and 90% of the Nyquist rate (for example, between 1 degree and 6 degrees). In some embodiments, oversampling by a factor of 1.2 or greater in both directions can provide a better signal-to-noise ratio and improved demodulation. In some embodiments, preprocessing an OCT image may include cropping, subtracting the average spectrum (eg, DC component), and/or using one or more window functions. In some embodiments, processing an OCT image may include one or more fast Fourier transforms (FFT, for example, x-space FFT), demodulation (for example, shifting the spatial frequency of interest to the fundamental frequency) and/or cropping The DC and AC components of the received signal. In some embodiments, processing may further include applying an inverse FF and/or k-space resampling and fast Fourier transform.

FIG. 8 is a top view of the sampling assembly 620 and the fixing assembly 670 according to some embodiments. As shown in FIG. 8, the sampling component 620 includes a scanning mirror 622, an IR fundus dichroic mirror 624, a fixed dichroic dichroic mirror 626, and an objective lens 628, which may be an achromatic lens. Also shown in FIG. 8 is the diopter adjustable component 680a, which includes the plano-convex lenses 630 and 634 that receive light through the scanning mirror 622 and the biconcave lens 632 shown in FIG. 6B. In some embodiments, the diopter adjustable component 680a can be configured to accommodate a diopter adjustment of up to +/- 10 diopters. In some embodiments, the diopter adjustable component 680a can be configured to avoid inducing excessive pupil de-space that can interfere with image quality. For the IR ophthalmoscopy system, imagine an imaging system that will view the image sensor and the fixed target through a scanning window. In some embodiments, the diopter adjustable component 680a can be configured to substantially reduce the back reflection from the IR component and the influence of the subject's cornea. In certain embodiments, the diopter adjustable component 680a can be configured to eliminate or substantially reduce the visibility of fluorescence from the lens of the subject's eye. In some embodiments, the diopter adjustable component 680a may use Schweitzer technology.

As shown in FIG. 8, the fixing assembly 670 includes a fixed dichroic beam splitter 626 and a fixed display 674. In some embodiments, the fixed dichroic beam splitter can be configured to reflect short-wavelength (for example, visible) light and transmit long-wavelength (for example, IR) light toward the fixed display 674 via the fixed lens 672. A long pass filter . In some embodiments, the fixed display 674 can be configured to display a visible fixed image. In some embodiments, the fixed display 674 can be configured to display a color display of a visible fixed image. In some embodiments, the fixed display 674 can be a New Haven Display International model NHD 0.6-6464G display. In some embodiments, the fixed display 674 can be a monochrome Sony IMX273 sensor with a resolution of 1440×1080 at 3.45 square microns. In some embodiments, the fixed component 670 may include a Sony IMX273 sensor with a resolution of 1440×1080 at 3.45 square microns. In some embodiments, a short dimension of the fixed display 674 (for example, vertical for an aspect ratio of 4:3, 16:9, or 16:10) is mapped to a 30-degree field of view of the viewing eye. In some embodiments, the fixed display 674 may have a full-circle 30-degree diameter field of view, or other fields of view as appropriate, with substantially no vignetting. In some embodiments, the fixed display 674 (e.g., a square array) is mapped to a 20-degree by 20-degree field of view as seen by the eye.

In some embodiments, some IR light can also be transmitted all the way to the detection component 650. In some embodiments, the fixed lens 672 may be adjustable to provide diopter compensation. The IR dichroic beam splitter 624 is shown as a short-pass filter that reflects long-wavelength (for example, IR) light toward the IR detection component (shown in FIGS. 9A and 9D to 9E) and reduces the short-wavelength The (for example, visible) light is transmitted to the detection component 650.

FIG. 9A is a side view of the IR detection component 660a that can be coupled to the sampling component 660a according to some embodiments. As shown in FIG. 9A, the IR detection component 660a includes an IR fundus dichroic mirror 624, an IR pupil repeater 690b, an astigmatism corrector 662, a diopter adjustable lens 680c, and an IR camera 664. Figure 9B is a side view of pupil repeater 690b and fiber 692 according to some embodiments. Figure 9C is a top view of a pupil repeater 690b and fibers 692 according to some embodiments.

FIG. 9D is a side view of an alternative IR detection component 660b that can be coupled to the sampling component 620 according to some embodiments. Like the IR detecting component 660a, the IR detecting component 660b includes an astigmatism corrector 662, an adjustable diopter lens 680b, and an IR camera 664. The IR detection component 660b further includes a pupil repeater 690b including a plurality of off-axis LEDs 694. In some embodiments, the pupil relay 690b may further include a holographic plate to place a low-intensity light spot on the reflective part of the front objective lens, thereby reducing the coupling between the reflective part and the imaging plane.

FIG. 9E is a side view of other alternative IR detection components 660c that can be coupled to the sampling component 620 according to certain embodiments. Like the IR detection components 660a and 660b, the IR detection component 660c includes an astigmatism corrector 662, a diopter adjustable lens 680b, and an IR camera 664. The IR detection component 660c further includes a pupil repeater 690c including a plurality of off-axis LEDs 694 and a diffraction plate 696. In some embodiments, the diffractive plate 696 can be configured to place a low-intensity light spot on the reflective part of the front objective lens, thereby reducing the coupling between the reflective part and the imaging plane.

FIG. 10 is a top view of a detection component 650 coupled to the beam splitter 618 according to some embodiments. As shown in FIG. 10, the detection component 650 includes an aspheric lens 653, achromatic lenses 654 and 656, a transmission grating 658, a field lens 666, and an OCT camera 668. In certain embodiments, the transmission grating 658 may be configured as described for the transmission grating 558. In some embodiments, the transmission grating 558 can improve the spectral signal-to-noise ratio of the light received by the OCT camera 568. In some embodiments, the transmission grating 558 may be configured to provide light to the OCT camera 568 at normal incidence. In some embodiments, the transmission grating 558 can enhance the noise performance of the transfer function of the OCT camera 568. In certain embodiments, the aspheric lens 653 may be configured to provide a pupil repeater 690c in front of the achromatic lens 654. In some embodiments, the aspheric lens 653 can be configured to reduce the spatial expansion by a factor of 5. In certain embodiments, the achromatic lens 654 may be configured to collimate the received light toward the transmission grating 658. In certain embodiments, the achromatic lens 656 may be configured to focus light on the OCT camera 668. In some embodiments, the field lens 666 can be configured to flatten the field, adjust the angle of the chief ray, and achieve a divergent chief ray.

FIG. 11A is a side view of the sampling assembly 620 illustrating the scan path of the OCT and IR imaging device according to some embodiments. The horizontal scanning path 798a and the vertical scanning path 798b are shown as passing from the scanning mirror 622 through the lenses 630, 632, and 634.

FIG. 11B is a side view of the sampling assembly 620, which includes a scanning mirror 622, a fixed dichroic mirror 624, an IR fundus dichroic mirror 626, and diopter adjustable lenses 630, 632, 634, and 636. In some embodiments, the lenses 630, 632, 634, and/or 636 can be moved along the optical axis from the scanning mirror 622 to the subject's eye to provide diopter compensation. In some embodiments, the IR camera 664 and/or the lens 666 may include an IR LED, such as a 910nm LED or a 940nm LED.

It should be understood that, in some embodiments, the imaging device described herein (for example, in conjunction with FIGS. 4A to 11B) may be configured to perform time-domain OCT. In some embodiments, a scanning mirror of the imaging device can be configured to scan the depth of the retinal fundus of a subject. In some embodiments, the scanning mirror can be used as the reference surface 548 or 648 in the reference assembly 540 or 640, respectively. In some embodiments, a piezoelectric actuator of the imaging device can be configured to control the scanning of the scanning mirror.

In some embodiments, the imaging device described herein (for example, in conjunction with FIGS. 4A to 11B) can be configured to continuously capture two images to form a single depth image. In some embodiments, the two images taken continuously are close enough in time to ensure that no eye movement occurs between the two images. The inventor realized that the frame rate of a conventional camera can be too slow to guarantee this. For example, in order to keep the price of imaging equipment low, a camera with a frame rate of less than 276 frames per second can be used. In some embodiments, such a camera can be configured to operate at a much higher frame rate by limiting the imaging field of view. To overcome the shortcomings associated with the use of a slow frame rate, the light source of the imaging device can be pulsed towards the end of one frame and at the beginning of the next frame, as described herein including with reference to FIG. 7.

FIG. 12 is a graph of the light intensity of a light source of an imaging device (eg, of FIGS. 4A to 11B) over time when the light source pulse is synchronized with one or more cameras of the imaging device according to some embodiments. In FIG. 12, the dashed line 1202 represents the duration of an imaging frame, and the solid line 1204 represents the duration of the light pulse. By synchronizing the light pulse with the frame rate of the image sensor, an image sensor can be used to obtain two images of the fundus taken with an interval of less than 1 ms with a much longer frame period (for example, 10 ms) .

FIG. 13 is a diagram illustrating a diagram of a retinal spot diagram of a pupil relay component that may be included in an imaging device (for example, FIGS. 4A to 11B) according to some embodiments. In Figure 13, the scale is 1 mm per grid, and a 30 mm diameter field of view corresponds to an 8.5 mm diameter disk. In some embodiments, the pupil relay components described herein can be configured to provide a 50% peak reduction. In some embodiments, the pupil relay component may include two Ereli discs separated by a distance of one wavelength of 1.41 as a baseline interpretation of the resolution, instead of the Rayleigh criterion of twice the wavelength of 2.44. In one example, the nominal IR imaging wavelength is 910 nm, the pupil diameter is 2.5 mm, and the aerial eye focal length is 22.2 mm, which provides a resolution of one diffraction limit of 11 um. In another example, the central white light has a wavelength of 550 nm, which results in a reduced resolution to one of 7 um. The desired imaging from an 8.5 mm disk on the retinal fundus to a 1080-column camera results in one Nyquist limit per 16 um 1 cycle, resulting in an imaging quality target of 50% MTF. Exemplary optical patterns for various iResearch disc separations are illustrated in Figs. 20A to 20C. FIG. 20A is a graph of an optical pattern generated using two iResearch disks separated by a distance of 1.22 wavelengths according to some embodiments. FIG. 20B is a graph of an optical pattern generated using two iResearch disks separated by a distance of 1.41 wavelengths according to some embodiments. FIG. 20C is a graph of an optical pattern generated by using two iResearch disks separated by a distance of a distance of 2.44 wavelengths according to some embodiments.

In some embodiments, a scanning mirror may be placed conjugate to a pupil of the subject's eye and configured to relay a collimated light beam generated by the imaging device to one of the pupils of the subject. One position of the straight beam. In one example, the scanning mirror can be configured to produce a first surface reflection at an incident angle of 45+/-6 degrees and a scanning thickness of 3 mm. In some embodiments, the scanning mirror can be configured as a variable angle window.

Figure 14A illustrates the combined interference amplitude for three different light sources that may be included in an OCT imaging device (eg, of Figures 4A-11B). Figure 14B illustrates the individual interference amplitudes for three different diode lasers that can be included in an OCT imaging device (eg, of Figures 4A-11B). As shown in Figure 14B, the depth resolution for the three combined laser diodes is greater than the depth resolution of any of the individual laser diodes.

Figure 15A illustrates one possible technique for combining multiple diode lasers to form a broadband transmitter 1500. The broadband transmitter 1500 includes a first diode laser 1501, a second diode laser 1502, and a third diode laser 1503. The first diode laser 1501 emits a first wavelength of light, the first wavelength is greater than the wavelength of the light emitted by the second diode laser 1502, the light emitted by the second diode laser 1502 is The wavelength itself is greater than the wavelength of the light emitted by the third diode laser 1503. The light from the first diode laser 1501 and the light from the second diode laser 1502 are combined at a first dichroic beam splitter 1504. The light from the first diode laser 1501 and the light from the second diode laser 1502 are combined with the light from the third diode laser 1503 at a second dichroic beam splitter 1505. Therefore, the resulting output from the second dichroic mirror 1505 can be used for a broadband light in an imaging device. Figure 15B illustrates each of the laser diodes fed to an imaging system.

In some embodiments, the laser wavelength separation is not greater than 1.5 times the spectral width of adjacent lasers. In one example, a 40 nm bandwidth optical transmitter can be formed by making each of the three lasers have a 10 nm bandwidth, with a 5 nm gap between the spectral peaks of adjacent lasers It is 5 nm.

III. Fluorescent and/ Or white light imaging technology

The inventors have developed improved white light and fluorescent imaging technologies that can be implemented alone or in combination with a multi-mode imaging device, as described herein. In certain embodiments, one or more white light and/or fluorescent imaging devices may be included in one or both of the first and second housing sections of the device. In some embodiments, a fluorescent imaging device and a white light imaging device are contained in the same housing section so that one eye is imaged by two imaging devices in a short period of time (eg, several seconds). In some embodiments, the devices described herein can be configured to capture white light and fluorescent images without the subject having to move or reorient the subject's eyes. According to various examples, the white light and fluorescent imaging device may be configured to capture respective white light and fluorescent images in a period of less than 5 seconds, less than 3 seconds, and/or less than 1 second. Moreover, in an embodiment in which the imaging device is contained in two housing sections of the imaging device, the imaging components in each section can be configured to simultaneously and/or in a short period of time as explained above Capture an image inside.

In some embodiments, white light imaging can be achieved by using light from a white light source (or a plurality of color LEDs) to illuminate the subject's retinal fundus and using a white light camera to sense the reflected light from the retinal fundus carried out. In one example, a plurality of color LEDs can illuminate the fundus of the subject’s retina at different time points, and the camera can capture multiple images corresponding to different color LEDs, and the images can be combined to form the subject’s A color image of the fundus of the retina. In some embodiments, fluorescent imaging can be achieved by using an excitation light source (eg, one or more narrowband LEDs) to illuminate the subject’s retinal fundus and using a fluorescent sensor and/or camera to sense Performed by fluorescent light on the fundus of the retina of the subject. For example, a wavelength of the excitation light source can be selected to cause fluorescence in one or more molecules of interest in the fundus of the subject's retina, so that the detection of fluorescence light can indicate the position of the molecule in an image. According to various embodiments, the fluorescence of a specific molecule can be determined based on a lifetime, intensity, spectrum, and/or other properties of the detected light.

As described herein, an imaging device may include fluorescent and white light imaging components configured to share at least some components such that the imaging components share at least a portion of an optical path. Therefore, while providing high-quality medical images, imaging equipment including these components can be more compact and have lower production costs. It should be understood that certain embodiments may include only fluorescent imaging components or only white light imaging components, because the techniques described herein can be implemented individually or in combination.

16A to 16B are top views of the white light and fluorescent imaging component 1604 of the multi-mode imaging device 1600 according to some embodiments. 16A is a top view of the multi-mode imaging device 1600, which has a partial view of the white light and fluorescent imaging component 1604, and FIG. 16B is a top view of the white light and fluorescent imaging component 1604, in which part of the imaging device 1600 is moved except. As shown in FIGS. 16A to 16B, the white light and fluorescent imaging component 1604 includes a white light source component 1610, an excitation source component 1620, a sampling component 1630, a fixed display 1640, and a detection component 1650. In some embodiments, the white light source component 1610 and the excitation source component 1620 can be configured to illuminate the subject's retinal fundus through the sampling component 1630 so that the reflected and/or fluorescent light from the subject's retinal fundus can be The detection component 1650 is used for imaging. In certain embodiments, the fixed display 1640 may be configured to provide a fixed object for focusing the subject during imaging.

In some embodiments, the white light source component 1610 can be configured to illuminate the retinal fundus of the subject so that light reflected and/or scattered by the retinal fundus can be captured and imaged by the detecting component 1650, as described herein. As shown in FIGS. 16A to 16B, the white light source assembly 1610 includes a white light source 1612, a collimator lens 1614, and a laser dichroic mirror 1616. In some embodiments, the white light source 1612 may include a white LED. In some embodiments, the white light source 1612 may include a plurality of color LEDs combined to substantially cover the visible spectrum, thereby being similar to a white light source. In certain embodiments, the white light source 1612 may include one or more blue or ultraviolet (UV) lasers.

In some embodiments, the excitation source component 1620 can be configured to excite fluorescence in one or more molecules of interest in the fundus of the retina of the subject, so that the fluorescence light can be captured by the detection component 1650. As shown in FIGS. 16A to 16B, the fluorescent light source assembly includes a laser 1622, a collimating lens 1624, and a mirror 1626. In some embodiments, the laser 1622 can be configured to generate light at one or more wavelengths corresponding to the fluorescent properties of one or more individual molecules of interest in the retinal fundus of the subject. In certain embodiments, these molecules can occur naturally in the fundus of the retina. In certain embodiments, these molecules can be biomarkers configured for fluorescence imaging. For example, the laser 1622 can be configured to generate excitation light having a wavelength between 405 nm and 450 nm. In some embodiments, the laser 1622 can be configured to generate light with a frequency bandwidth of 5 nm to 6 nm. It should be appreciated that certain embodiments may include a plurality of lasers configured to generate light with different wavelengths.

As shown in FIGS. 16A-16B, the white light source 1612 is configured to generate white light and transmit the white light to the laser dichroic mirror 1616 through the collimator lens 1614. The laser 1622 is configured to generate excitation light and transmit the excitation light to the mirror 1626 through the collimating lens 1624, which reflects the excitation light to the laser dichroic mirror 1616. The laser dichroic beam splitter 1616 can be configured to transmit white light and reflect excitation light so that the white and excitation light share an optical path to the fundus of the subject's retina. In some embodiments, the laser dichroic beam splitter 1616 can be configured as a long pass filter.

In some embodiments, the fixed display 1640 may be configured to display a fixed object used to focus the subject during imaging. The fixed display 1640 can be configured to provide fixed light to the fixed dichroic mirror 1642. In some embodiments, the fixed dichroic beam splitter 1642 can be configured to transmit fixed light and reflect white light and excitation light so that the fixed light, white light and excitation light are all shared from the fixed dichroic beam splitter 1642 to the subject One of the optical paths of the retinal fundus.

In some embodiments, the sampling component 1630 can be configured to provide white light and excitation light to the retinal fundus of the subject, and to provide reflected and/or fluorescent light from the retinal fundus of the subject to the Detecting component 1650. As shown in FIGS. 16A-16B, the sampling component 1630 includes an achromatic lens 1632, an iris 1634, an illumination lens 1636, and an achromatic lens 1638. In certain embodiments, achromatic lenses 1632 and 1638 can be configured to focus white light, excitation light, and fixed light on the fundus of the subject's retina. In some embodiments, the iris 1634 can be configured to scatter some of white light, excitation light, and/or fixed light, so that light from different sources is focused on various parts of the subject’s retinal fundus . In some embodiments, the illumination mirror 1636 can be adjusted, such as by moving the positioning component 1637 in a direction parallel to the imaging axis. In certain embodiments, the achromatic lens 1638 may be further configured to provide the reflected and/or fluorescent light from the retinal fundus of the subject to the detection component 1650.

The detection component 1650 can be configured to focus and capture light from the retinal fundus of the subject to use the received light to form an image. As shown in FIGS. 16A-16B, the detection component 1650 includes an achromatic lens 1652, a dichroic mirror 1654, a focusing lens 1656, and a camera 1658. In certain embodiments, the achromatic lens 1652 and the focusing lens 1656 can be configured to focus the received light on the camera 1658 so that the camera 1658 can use the received light to capture an image. In some embodiments, the dichroic mirror 1654 can be configured to transmit white light and fluorescent light and reflect the excitation light so that the excitation light does not reach the camera 1658.

Figure 17 is a perspective view of an alternative fluorescent and white light imaging component 1704 that may be included in an imaging device according to certain embodiments. For example, in certain embodiments, the fluorescent and white light imaging component 1704 may be disposed in the first and/or second housing section of the imaging device, as discussed above. As shown in FIG. 17, the fluorescent and white light imaging component 1704 includes a white light imaging component, which includes a white light source component 1710 and a white light camera 1760; and a fluorescent imaging component, which includes an excitation source component 1720 and a fluorescent detector Test component 1770. The fluorescent and white light imaging component 1704 further includes a sampling component 1730 and a detecting component 1750, which include a common imaging path for fluorescent and white light imaging. In some embodiments, the white light source component 1710 and the excitation source component 1720 can be configured to provide light to the sampling component 1730 that can focus the light on the fundus of the retina of a subject. In some embodiments, the detection component 1750 can be configured to receive the light reflected and/or emitted from the subject's retina and/or the fundus, and provide the received white light to the white light camera 1760 and provide fluorescent light To the fluorescence detection component 1770.

In some embodiments, the white light source component 1710 can be configured to illuminate the retinal fundus of the subject so that light reflected and/or scattered by the retinal fundus can be captured and imaged by the white light camera 1760, as described herein. In FIG. 17, the white light source assembly 1710 includes a white light source 1712 and a collimating lens 1714. In some embodiments, the white light source 1712 may include a white LED. In some embodiments, the white light source 1712 may include a plurality of color LEDs combined to substantially cover the visible spectrum, thereby being similar to a white light source.

In some embodiments, the excitation light source component 1720 can be configured to generate light to excite the fluorescent molecules in the retinal fundus of the subject, so that the fluorescent light can be captured and imaged by the fluorescence detection component 1770. In FIG. 17, the excitation light source assembly 1720 includes a first laser 1722a and a second laser 1722b, a first collimating lens 1724a and a second collimating lens 1724b, and a first laser dichroic mirror 1726a and a second laser Shoot a two-way beam splitter 1726b. In some embodiments, the first laser 1722a and the second laser 1722b can be configured to generate wavelengths corresponding to the fluorescent characteristics of one or more of the individual molecules of interest in the fundus of the subject’s retina. Light. In certain embodiments, these molecules can occur naturally in the fundus of the retina. In certain embodiments, these molecules can be biomarkers configured for fluorescence imaging. In some embodiments, the first laser 1722a and the second laser 1722b can be configured to generate light at a wavelength that can be combined in a single optical path to image the subject's retinal fundus. In some embodiments, the first laser 1722a can be configured to generate excitation light having a wavelength of 405 nm. In some embodiments, the second laser 1722b can be configured to generate excitation light having a wavelength of 450 nm. In some embodiments, the first laser 1722a and/or the second laser 1722b can be configured to generate light with a frequency bandwidth of 5 nm to 6 nm. It should be understood that certain embodiments may include more or fewer lasers than shown in FIG. 17. According to various embodiments, the excitation light source assembly 1720 may include 3-6 lasers configured to generate light at wavelengths of 405 nm, 450 nm, 473 nm, 488 nm, 520 nm, and 633 nm, respectively. In some embodiments, the excitation light source assembly 1720 can be configured to provide excitation light suitable for fluorescence intensity measurement. In one example, the excitation light source assembly 1720 may include a range of LEDs that span the visible light spectrum.

As shown in FIG. 17, the first laser 1722a is configured to emit excitation light toward the first laser dichroic mirror 1726a through the collimator lens 1724a. In some embodiments, the first laser dichroic mirror 1726a can be configured to transmit the light from the white light source 1712 and reflect the light from the first laser 1722a, so that the light from the first laser 1722a is different from the light from the first laser 1722a. The light of the white light source 1712 shares an optical path from the first laser dichroic mirror 1726a to the second laser dichroic mirror 1726b. In some embodiments, the first laser dichroic beam splitter 1726a can be configured as a long pass filter. As also shown in FIG. 17, the second laser 1722b is configured to emit excitation light toward the second laser dichroic mirror 1726b through the collimator lens 1724b. In some embodiments, the second laser dichroic mirror 1726b can be configured to transmit the light from the white light source 1712 and the first laser 1722a and reflect the light from the second laser 1722b, so that the light from the second laser The light emitted 1722b shares an optical path with the light from the white light source 1712 and the first laser 1722a. In some embodiments, the second laser dichroic beam splitter 1726b can be configured as a long pass filter. In FIG. 17, the light from the white light source 1712, the first laser 1722a, and the second laser 1722b share an optical path from the second laser dichroic mirror 1726b to the beam splitter 1754. At this time, after receiving the fluorescent light The light and the white light are split between the fluorescence detection component 1770 and the white light camera 1760 respectively.

As shown in FIG. 17, the mirror 1728 is configured to reflect the combined light toward the sampling component 1730. In some embodiments, the mirror 1728 can be a flat mirror. In some embodiments, the mirror 1728 may be a spherical mirror configured to adjust the size and/or divergence of the reflected light.

In some embodiments, the sampling component 1730 can be configured to focus the white and excitation light from the white light source component 1710 and the excitation source component 1720 on the fundus of the subject's retina. As shown in FIG. 17, the sampling component 1730 includes a first achromatic lens 1732 and a scattering component 1734. The scattering element 1734 can be configured to reflect light from the mirror 1728 toward the first achromatic lens 1732. In some embodiments, the scattering element 1734 can be a flat mirror. In some embodiments, the scattering element 1734 may have a mirror configured to provide a scattering surface that provides more uniform illumination of the subject's retinal fundus than a flat mirror. In some embodiments, the scattering component 1734 may have a 1200 grit scattering surface. According to various embodiments, the scattering component 1734 may have a scattering surface of one of 800 grit, 1000 grit, 1400 grit, or 1600 grit.

As shown in FIG. 17, the scattering element 1734 includes a hole 1736 that is configured to allow certain light to pass through the scattering element 1734. In some embodiments, the light received through the hole 1736 through the second laser dichroic mirror 1726b may not be used for imaging. In some embodiments, the hole 1736 may be configured to allow scattered light received from the retinal fundus of the subject to pass through the scattering element 1734 toward the white light camera 1760 and the fluorescence detection element 1770. In some embodiments, the hole 1736 may be cylindrical. In some embodiments, the hole 1736 can be configured to prevent noise light from reaching the white light camera 1760 and the fluorescence detection component 1770. For example, the hole 1736 may be configured to block the light incident on the scattering element 1734 from reaching the white light camera 1760 and the fluorescence detecting element 1770 from directions other than the direction in which light is received from the subject's retina fundus. . In some embodiments, at least a portion of an inner wall of the hole 1736 may include a black material configured to reduce reflection. In some embodiments, the black material may be tied with a black tape. In some embodiments, the holes 1736 can be shaped to reduce reflections. For example, in some embodiments, the hole 1736 may have a tapered shape.

The first achromatic lens 1732 may be configured to focus the light received via the scattering element 1734 on the fundus of the subject's retina. In some embodiments, the first achromatic lens 1732 may be configured to collimate the light received from the retinal fundus of the subject. In some embodiments, the first achromatic lens 1732 may be positioned at a distance from the fundus of the retina that causes the received light to be almost collimated. In an example, the focal length of the first achromatic lens 1732 may be 20 mm, and the distance from the first achromatic lens 1732 to the front of the subject's eye may be 37 mm.

In certain embodiments, when light is focused on the fundus of the retina by the sampling element 1730, the excitation source element 1720 can be configured to cause fluorescence in the fundus of the retina of the subject. In some embodiments, fluorescence may cause the fundus of the retina of the subject to emit light at a wavelength different from that of the excitation light. For example, depending on the molecule of interest that can be excited by the excitation light and respond by emitting fluorescent light, the fluorescent light can have a ratio of 30 nm to 50 nm, 50 nm to 70 nm, or 70 nm to 80 nm. One of the wavelengths. In some embodiments, the sampling component 1730 can be configured to receive both excitation light and fluorescent light from the retinal fundus of the subject and provide the received light to the detection component 1750.

In some embodiments, the detection component 1750 can be configured to receive light from the sampling component 1730 and provide the received white light to the white light camera 1760 and fluorescent light to the fluorescence detection component 1770. As shown in FIG. 17, the detection component 1750 includes a second achromatic lens 1752 and a beam splitter 1754. In some embodiments, the second achromatic lens 1752 can be configured to further collimate the light received from the retinal fundus of the subject via the sampling component 1730. In some embodiments, the received light may have a larger spread at the second achromatic lens 1752 than at the first achromatic lens 1732. Therefore, in some embodiments, the second achromatic lens 1752 may have a larger diameter than the first achromatic lens 1732. In one example, the first achromatic lens 1732 may have a half-inch diameter, and the second achromatic lens 1752 may have a one-inch diameter.

In some embodiments, the beam splitter 1754 may be configured to reflect some of the received light to the white light camera 1760 and transmit some of the received light to the fluorescence detection component 1770. In some embodiments, the beam splitter 1754 may be configured to reflect one half of the received light to the white light camera 1760 and transmit one half of the received light to the fluorescence detection component 1770. In some embodiments, the light level may be lower in the fluorescent detection component 1770 than in the white light camera 1760. Therefore, in some embodiments, the beam splitter 1754 can be configured to transmit more received light to the fluorescence detection component 1770 than is reflected in the white light camera 1760. In some embodiments, the beam splitter 1754 can be configured to transmit 90%, 95%, 99%, or 99.9% of the light to the fluorescent detection component 1770 and 10%, 5%, 1% of the light Or 0.1% reflected to white light camera 1760. As shown in FIG. 17, the beam splitter 1754 separates the optical paths for fluorescent and white light imaging.

In some embodiments, the white light camera 1760 can be configured to detect the light reflected from the beam splitter 1754 and store image data for analysis. In some embodiments, the white light camera 1760 can be a high-resolution color digital camera. In some embodiments, the white light camera 1760 may have a resolution ranging from 3 megapixels to 10 megapixels. In some embodiments, the white light camera 1760 may be a high-resolution black and white digital camera. In some embodiments, the white light source 1712 may include a plurality of color LEDs, and the white light camera 1760 may be configured to capture a color image of the retinal fundus of the subject. In one example, the light source 1712 includes a red LED, a blue LED, and a green LED, each LED is configured to emit light in a sequence over time, and the white light camera 1860 can be configured to target the sequence Each shot captures a separate image. The white light camera 1760 and/or the processing circuit coupled to the white light camera 1760 can be configured to combine the images captured for each emission of the sequence to form a color image of the retinal fundus.

In some embodiments, the fluorescence detection component 1770 can be configured to detect the fluorescence light transmitted through the beam splitter 1754 and extract fluorescence information from the light. As shown in FIG. 17, the fluorescence detection component 1770 includes a spectral filter 1772, a field lens 1774, and a fluorescence sensor 1776. In certain embodiments, the spectral filter 1772 can be configured to block excitation light and transmit fluorescent light. In one example, the spectral filter 1772 can be configured to block light having wavelengths of 405 nm and 450 nm. In certain embodiments, the field lens 1774 can be configured to focus the received light on the fluorescent sensor 1776.

In certain embodiments, the fluorescence sensor 1776 can be configured to distinguish between fluorescence emission from at least two different molecules. In some embodiments, the fluorescence sensor 1776 can be configured to distinguish between molecules whose fluorescence emission has different lifetimes. For example, in some embodiments, the fluorescent sensor 1776 can be configured to determine the location of different molecules in the fundus of the retina of the subject by determining the lifetime of the received light. In some embodiments, the fluorescent sensor 1776 can be configured to distinguish between molecules whose fluorescent emission has different wavelengths. For example, in some embodiments, the fluorescent sensor 1776 can be configured to determine the location of different molecules in the fundus of the retina by determining the lifetime of the received light. In some embodiments, the fluorescence sensor 1776 can be configured to distinguish between molecules whose fluorescence emission has different intensities. For example, in some embodiments, the fluorescence sensor 1776 can be configured to determine the position of different molecules in the fundus of the retina by determining the intensity of the received light. It should be understood that according to various embodiments, the fluorescent sensor 1776 may be configured for lifetime, spectrum, intensity, and/or other measurements, alone or in combination.

Figure 18 is a perspective view of other alternative fluorescent and white light imaging components 1804 that may be included in an imaging device according to certain embodiments. As shown in FIG. 18, the fluorescent and white light imaging component 1804 includes a white light source component 1810, an excitation source component 1820, a sampling component 1830, and a detection component 1850. In certain embodiments, the white light source component 1810 and the excitation source component 1820 can be configured to provide light to the sampling component 1830 to image the retinal fundus of a subject. In some embodiments, the sampling component 1830 may be configured to focus light on the fundus of the retina of the subject, and receive light reflected and/or emitted by the fundus of the retina of the subject in response. In some embodiments, the detection component 1850 can be configured to use the light received through the sampling component 1830 to capture an image. Compared with the fluorescent and white light component 1704 including the white light camera 1760 and the fluorescent detecting component 1770, the detecting component 1850 includes a combined white light and fluorescent sensor 1858. Moreover, compared with the excitation source assembly 1720 including the first laser 1722a and the second laser 1722b, the excitation source assembly 1820 is shown in FIG. 18 as including a single laser 1822. In the embodiment illustrated in FIG. 18, the white light and fluorescent sensor 1858 is configured to distinguish between molecules with different fluorescent emission wavelengths. The fluorescent and white light imaging component 1804 further includes a fixed display 1840 configured to provide a fixed object to allow the subject to focus visually during imaging.

In some embodiments, the white light source assembly 1810 may be configured to provide white light for transmission to the fundus of the retina of the subject. As shown in FIG. 18, the white light source assembly 1820 includes a white light source 1812 and a collimating lens 1814, which can be configured in combination with the manner described in FIG. 17 for the white light source 1712 and the collimating lens 1714.

In certain embodiments, the excitation light source assembly 1820 may be configured to provide excitation light to stimulate the fluorescence emission from one or more molecules of interest in the fundus of the subject's retina. As shown in FIG. 18, the excitation light source assembly 1820 includes a laser 1822, a collimating lens 1824, a mirror 1826, and a laser dichroic mirror 1816. In some embodiments, the laser 1822 can be configured for the first and/or second laser 1722a and/or 1722b, and the collimating lens 1824 can be configured for the first and/or second collimating lens The laser dichroic beam splitter 1816 can be configured in the manner described in 1724a and/or 1724b, and the laser dichroic beam splitter 1816 can be configured in the manner described in the first and/or second laser dichroic beam splitter 1726a and/or 1726b. The mirror 1826 can be configured to reflect light from the laser 1822 to the laser dichroic mirror 1816. As shown in FIG. 18, the excitation and white light share an optical path from the laser dichroic beam splitter 1816 to the white light and fluorescent sensor 1858.

In certain embodiments, the fixed display 1840 may be configured to provide a fixed object that allows the subject to focus during imaging so that the subject's eyes are oriented in a desired direction for imaging. For example, in some embodiments, the fixed display 1840 may be configured to display a point and a house as a fixed object. As shown in FIG. 18, the fixed display is configured to provide fixed light to the fixed dichroic mirror 1842. In some embodiments, the fixed dichroic mirror 1842 can be configured to reflect white and excitation light and transmit fixed light, so that the white, excitation, and fixed light are combined to be transmitted to the fundus of the subject's retina through the sampling element 1830 .

In certain embodiments, the sampling component 1830 can be configured to provide white, excitation, and fixed light to the fundus of the subject's retina. As shown in FIG. 18, the sampling component 1830 includes a first achromatic lens 1832, an iris 1834, an injection lens 1836, and a second achromatic lens 1838. In some embodiments, the second achromatic lens 1838 is configured to receive the reflected and/or emitted light from the retinal fundus of the subject and collimate the received light to be transmitted to the detection component 1850.

In some embodiments, the detection component 1850 can be configured to use light received from the retinal fundus of the subject to capture images. As shown in FIG. 18, the detection component 1850 includes an iris 1852, a focusing lens 1854, a dichroic mirror 1856, and a white light and fluorescent sensor 1858. In certain embodiments, the iris 1852 can be configured to block light received from directions other than the direction in which light is received from the subject's retinal fundus from reaching the white light and fluorescent sensor 1858. In some embodiments, the focusing lens 1854 may be configured to focus the light received from the subject's retinal fundus on the white light and fluorescent light sensor 1858. In some embodiments, the dichroic mirror 1856 can be configured to block the reflected excitation light from reaching the white light and fluorescent sensor 1858. In some embodiments, the dichroic beam splitter 1856 can be configured as a long pass filter.

FIG. 19 is a side view of an alternative sampling component 1930 and a detection component 1950 included in other white light and/or fluorescent imaging components that can be combined with a multi-mode imaging device according to certain embodiments. As shown in FIG. 19, the sampling component 1930 includes a pupil relay lens 1990 including plano-convex lenses 1932 and 1936 and a biconcave lens 1934. In certain embodiments, the biconcave lens 1934 can be configured to provide negative dispersion and/or field flattening. In some embodiments, the biconcave lens 1934 can be configured to provide a negative focal length. In some embodiments, the sampling component 1930 may further include other sampling components, such as those described herein in conjunction with FIGS. 17 to 18. According to various embodiments, the sampling component 1930 can be configured to irradiate the subject's retinal fundus from an on-axis or off-axis illumination ring.

As also shown in FIG. 19, the detection component 1950 includes achromatic lenses 1952 and 1956 and a camera 1958. In some embodiments, the achromatic lenses 1952 and 1956 can be configured to flatten the illuminated field, adjust the chief ray angle, and achieve a divergent chief ray. In some embodiments, the camera 1958 can be a white light and/or fluorescent imaging sensor. In some embodiments, the pupil relay lens 1990 can be adjusted to correct the field curvature of the camera 1958. For example, as shown in FIG. 19, the pupil relay lens 1990 is configured to spatially distribute light of different wavelengths at different angles. As shown, the achromatic lenses 1952 and 1956 are configured to focus light of different wavelengths on different parts of the camera 1958.

IV. application

The inventors have developed improved imaging techniques that can be implemented using the imaging equipment described herein. According to various embodiments, these imaging technologies can be used for biometric identification, health status determination, disease diagnosis, and others.

The inventor has realized that various health conditions can be indicated by the appearance of the fundus of the retina of a person in one or more images captured according to the techniques described herein. For example, diabetic retinopathy can be indicated by tiny bumps or microaneurysms that bulge from smaller blood vessels, sometimes causing fluid and blood to leak into the retina. In addition, larger retinal blood vessels can begin to expand and become irregular in diameter. The nerve fibers in the retina may begin to swell. Sometimes, the central part of the retina (macular) begins to swell, such as macular edema. Damaged blood vessels can be closed, leading to the growth of new and abnormal blood vessels in the retina. Glaucoma optic neuropathy or glaucoma can be indicated by thinning of the parapapillary retinal nerve fiber layer (RNFL) as a result of axon and secondary retinal ganglion cell loss and optic disc depression. The inventors have realized that, for example, the RNFL defect indicated by OCT is one of the earliest signs of glaucoma. In addition, age-related macular degeneration (AMD) can be caused by macular peeling and/or bulging, macular pigmentation disorders (such as the yellow substance under the pigmented skin layer in the central retinal area), and/or crypts (such as macular crypts, peripheral Hidden knots and/or granular pattern hidden knots). AMD can also be indicated by map-like atrophy, such as a clearly demarcated circular area of hyperpigmentation, coin-shaped atrophy, and/or subretinal fluid. Stargard's disease can be indicated by the death of photoreceptor cells in the central part of the retina. Macular edema can be indicated by a groove in a zone surrounding the fovea. A macular hole can be indicated by a hole in the macula. Eye floaters can be indicated by blurring of the non-focused optical path. Retinal detachment can be indicated by severe optic disc rupture and/or separation from the underlying pigment epithelium. Retinal degeneration can be indicated by the deterioration of the retina. Central serous retinopathy (CSR) can be indicated by elevation of one of the photosensitive retinas in the macula and/or localized detachment from the pigment epithelium. Choroidal melanoma can be indicated by a malignant tumor derived from pigment cells that originate in the choroid. Cataracts can be indicated by an opaque lens and can also cause blurred fluorescence lifetime and/or 2D retinal fundus images. Macular microvascular expansion can be indicated by a significant increase in the fluorescent life cycle of the macula and the degeneration of smaller blood vessels in and around the fovea. Alzheimer's disease and Parkinson's disease can be indicated by the thinning of RNFL. It should be understood that if not properly screened and treated, diabetic retinopathy, glaucoma and other such conditions can lead to blindness or severe visual impairment.

Therefore, in some embodiments, one or more images of the fundus of the retina of a person acquired according to the techniques described herein can be used to determine the physique of the person susceptible to various medical conditions. For example, if one or more of the above-explained signs of a specific medical condition (for example, macular peeling and/or uplift for age-related macular degeneration) is detected in the captured image, the People can be susceptible to other medical conditions.

The inventor has also recognized that certain health conditions can be detected using the fluorescent imaging technology described herein. For example, a macular puncture can use an excitation light wavelength between 340 nm and 500 nm to excite the retinal pigment epithelium with a fluorescent emission wavelength of 540 nm and/or a fluorescence emission wavelength between 430 nm and 460 nm in the subject's eye ( RPE) and/or macular pigment. The fluorescence from RPE can be mainly attributed to lipofuscin from RPE lysosomes. Retinal artery occlusion can use an excitation light wavelength of 445 nm to excite flavin adenine dinucleotide (FAD), RPE and/or a fluorescent emission wavelength between 520 nm and 570 nm in the subject's eye Nicotinamide adenine dinucleotide (NADH) for detection. AMD in the cryptojunction can be detected by using an excitation wavelength between 340 nm and 500 nm to excite the subject's eyes with an RPE with a fluorescence emission wavelength between 540 nm and/or 430 nm and 460 nm . AMD including geographic atrophy can be detected by using an excitation wavelength of 445 nm to excite RPE and elastin with a fluorescent emission wavelength between 520 nm and 570 nm in the subject's eyes. AMD with diversified neovascularization can be detected by exciting the choroid and/or inner retinal layer of the subject. Diabetic retinopathy can be detected by using an excitation wavelength of 448 nm to excite FAD with a fluorescent emission wavelength between 590 nm and 560 nm in the subject's eyes. Central serous chorioretinopathy (CSCR) can be detected by using an excitation wavelength of 445 nm to excite RPE and elastin with a fluorescent emission wavelength of 520 nm to 570 nm in the subject's eyes. Stargard’s disease can be detected by using an excitation light wavelength between 340 nm and 500 nm to excite the subject’s eyes with an RPE with a fluorescence emission wavelength between 540 nm and/or 430 nm and 460 nm. . Choroidal disease can be detected by using an excitation light wavelength between 340 nm and 500 nm to excite RPE with a fluorescence emission wavelength between 540 nm and/or a fluorescence emission wavelength between 430 nm and 460 nm in the subject's eyes.

The inventor has also developed a technique for diagnosing various health problems of a person using the captured images of one of the fundus of the retina of the person. For example, in certain embodiments, any of the health conditions set forth above can be diagnosed.

In some embodiments, the imaging techniques described herein can be used to determine health status, which can include heart health, cardiovascular disease, anemia, retinal toxicity, body mass index, water weight, hydration status, muscle mass, age , Smoking habits, blood oxygen level, heart rate, white blood cell count, red blood cell count and/or other judgments related to these health attributes. For example, in some embodiments, a light source with a frequency bandwidth of at least 40 nm can be configured to be sufficient to capture red blood cells with a diameter of 6 µm and white blood cells with a diameter of at least 15 µm Imaging resolution. Therefore, the imaging techniques described herein can be configured to facilitate the classification and counting of red blood cells and white blood cells, thereby estimating the density of each in the blood and/or other such determinations.

In some embodiments, the imaging techniques described herein can facilitate the tracking of the movement of blood cells to measure the blood flow rate. In some embodiments, the imaging techniques described herein can facilitate tracking the width of blood vessels, which can provide an estimate of blood pressure changes and richness. For example, an imaging device configured to analyze red and white blood cells using a 3-dimensional (3D) spatial scan completed in 1 µs as described in this article can be configured to capture at 1 meter per second The movement of blood cells. In certain embodiments, light sources that can be included in the devices described herein, such as superluminescent diodes, LEDs, and/or lasers, can be configured to emit sub-microsecond light pulses that can be less than Capture an image in one microsecond. Using the spectral line scanning technique described in this article, the entire profile of a scanned line pair depth can be captured in a sub-microsecond. In some embodiments, a 2-dimensional (2D) sensor described herein can be configured to capture these images at a slow rate for internal or external reading and subsequent analysis. In some embodiments, a 3D sensor can be used. The embodiments described below overcome the challenge of obtaining multiple high-quality scans in a single microsecond.

In some embodiments, the imaging device described herein can be configured to scan a line aligned along a blood vessel direction. For example, after identifying a blood vessel configuration of the retinal fundus of the subject and selecting a larger blood vessel for observation, the scan line can be rotated and positioned. In some embodiments, a vessel that is small and allows only one cell to sequentially pass through a blood vessel can be selected so that the selected blood vessel fits a single scan line. In some embodiments, restricting the target imaging area to a smaller section of the subject's eyes can reduce the collection area for the imaging sensor. In some embodiments, the use of part of the imaging sensor facilitates increasing the imaging frame rate to 10s of KHz. In some embodiments, the imaging device described herein can be configured to perform a fast scan in a cell of the subject's eye while reducing spectral spread interference. For example, each scan line can use a different 2D section of the imaging sensor array. Therefore, multiple line scans can be captured at the same time, where each line scan is captured by a separate part of the imaging sensor array. In some embodiments, each line scan can be enlarged to result in a wider spacing on the imaging sensor array, such as a wider dispersion spectrum, so that each 2D line scan can be measured independently.

Therefore, having described several aspects and embodiments of the technology described in the present invention, it should be understood that various changes, modifications, and improvements will easily occur for those who are familiar with the technology. These changes, modifications and improvements are intended to be within the spirit and scope of the technology described in this article. For example, those familiar with the technology will easily conceive various other components and/or structures for performing functions and/or obtaining one or more of the results and/or advantages described herein, and these variations Each of and/or modification is considered to be within the scope of the embodiments set forth herein. Those who are familiar with the technology will recognize or be able to ascertain many equivalents of the specific embodiments described herein only by using routine experiments. Therefore, it should be understood that the foregoing embodiments are presented only by way of examples and are within the scope of the appended patent application and their equivalents, and the inventive embodiments may be practiced differently from those specifically illustrated. In addition, if two or more features, systems, articles, materials, kits and/or methods described herein are not inconsistent with each other, any of these features, systems, articles, materials, kits and/or methods A combination is included in the scope of the present invention.

The embodiments set forth above can be implemented in any of numerous ways. One or more aspects and embodiments of the present invention related to the performance of a program or method may utilize program instructions that can be executed by a device (for example, a computer, a processor, or other device) to execute the program or method or control its performance. In this regard, various inventive concepts can be embodied as a computer-readable storage medium (or multiple computer-readable storage media) (for example, a computer memory, one or more floppy disks, compact discs, optical discs, tapes) , Flash memory, field programmable gate arrays or other semiconductor devices in the circuit configuration or other tangible computer storage media), the computer-readable storage media is encoded when executed on one or more computers or other processors One or more programs are executed to implement one or more of the various embodiments described above. The computer-readable medium or several computer-readable mediums can be transportable so that the program or several programs stored thereon can be loaded onto one or more different computers or other processors to implement the state described above Various aspects in the sample. In some embodiments, computer-readable media is non-transitory media.

The term "program" or "software" is used in this article in a general sense to refer to any type of computer code or computer code that can be used to program a computer or other processor to implement the various aspects described above. Computer executable instruction set. In addition, it should be understood that according to one aspect, one or more computer programs that execute the method of the present invention do not need to reside on a single computer or processor, but can be distributed on several different computers in a modular manner. Or the processor can implement various aspects of the present invention.

Computer-executable instructions can take many forms, such as program modules, that are executed by one or more computers or other devices. Generally speaking, program modules include routines, programs, objects, components, data structures, etc. that perform specific tasks or implement specific abstract data types. Generally, in various embodiments, the functionality of the program modules can be combined or distributed as desired.

In addition, the data structure can be stored in a computer-readable medium in any suitable form. For the purpose of simplifying the illustration, the data structure can be displayed to have fields related to the position in the data structure. These relationships can also be achieved by assigning storage areas to fields using positions in a computer-readable medium, and these positions convey the relationship between the fields. However, any suitable mechanism can be used to establish a relationship between information in the fields of a data structure, including through the use of indicators, tags, or other mechanisms that establish relationships between data elements.

When implemented in software, the software code can be executed on any suitable processor or collection of processors, whether provided in a single computer or distributed among multiple computers.

Further, it should be understood that, as a non-limiting example, a computer can be embodied in any of several forms, such as a rack-mounted computer, a desktop computer, a laptop computer, or a tablet computer. In addition, a computer can be embedded in a device that is not generally regarded as a computer but has suitable processing capabilities, including a personal assistant (PDA), a smart phone or any other suitable portable or fixed electronic device.

In addition, a computer may have one or more input and output devices. Among other things, these devices can be used to present a user interface. Examples of output devices that can be used to provide a user interface include printers or display screens for visual presentation of output, and speakers or other sound generating devices for audio presentation of output. Examples of input devices that can be used in a user interface include keyboards and pointing devices, such as mice, touch pads, and digital input pads. As another example, a computer can receive input information through voice recognition or other audio formats.

These computers can be interconnected in any suitable manner via one or more networks, including a local area network or a wide area network, such as an enterprise network, and an intelligent network (IN) or the Internet. These networks can be based on any suitable technology and can operate according to any suitable protocol and can include wireless networks, wired networks, or fiber optic networks.

The actions performed as part of the method can be sequenced in any suitable way. Thus, embodiments may be constructed in which actions are performed in a different order than that illustrated, which may include performing certain actions at the same time, even if shown as sequential actions in the illustrative embodiment.

The definitions and all definitions used in this text should be understood to be controlled within the dictionary definitions, the definitions in the documents incorporated by reference, and/or the conventional meanings of the defined terms.

Unless expressly indicated to the contrary, the indefinite articles "一 (a)" and "一 (an)" used in the specification and in the scope of patent application should be understood to mean "at least one."

As used herein in the specification and in the scope of the patent application, the phrase "and/or" should be understood to mean "either or both" of the elements so combined, that is, in some cases Elements that exist in a combined manner and in other cases exist in a separate manner. Multiple elements listed in "and/or" shall be regarded as being in the same manner, that is, "one or more" of the elements so combined. There may be other elements other than those specifically identified by the "and/or" clause, regardless of whether they are related or not related to the specifically identified elements. Therefore, as a non-limiting example, when used in conjunction with an open language such as "including", in one embodiment, a reference to one of "A and/or B" may refer to only A (including Elements other than B); in another embodiment, it refers to only B (including elements other than A as appropriate); in another embodiment, it refers to both A and B (including other elements as appropriate) ;and many more.

As used herein in the specification and in the scope of patent applications, the phrase "at least one" referring to a list of one or more elements should be understood to mean one or more elements selected from the list of elements At least one element, but does not necessarily include at least one of each and every element specifically listed in the element list, and any combination of elements in the element list is not excluded. This definition also allows the existence of elements other than the specifically identified elements in the list of elements referred to by the phrase "at least one", regardless of whether they are related or not related to the specifically identified elements. Therefore, as a non-limiting example, in one embodiment, "at least one of A and B" (or equivalently, "at least one of A or B", or equivalently, "A And/or at least one of B") may refer to at least one (including more than one as the case may be) A without the presence of B (and optionally including elements other than B); in another embodiment, it means At least one (including more than one as the case may be) B, but no A (and optionally including elements other than A); in another embodiment, it refers to at least one (including more than one as the case may be) A and at least one ( Including more than one) B (and other elements as appropriate); etc.

In addition, the wording and terminology used in this article are for explanatory purposes and should not be regarded as restrictive. The use of "including", "comprising" or "having", "containing", "involving" and their variations in this article means to include the items listed thereafter And its equivalents and additional items.

In the scope of patent application and in the above description, all transitional phrases (such as "include", "include", "carrying", "have", "contain", "involved", "holding (holding) )", "composed of" and the like) should be understood as open-ended, that is, it means including but not limited to. Only transitional phrases "consisting of" and "consisting essentially of" should be closed or semi-closed transitional phrases, respectively .

100: imaging equipment 101: Shell 102: First shell section/shell section 103: second shell section/shell section 104: Rear shell section 105: front housing section 110: first opening/opening 111: second opening/opening 122: first imaging device/imaging device/first optical device 123: second imaging device/imaging device/second optical device 200: imaging equipment 201: Shell 202: first housing section/first housing section/section 203: second housing section/second housing section/section 204: Center shell section/center shell section 205A: Front housing section 205B: Front housing section 210: opening 211: open 200: electronic circuit 300: imaging equipment 301: Shell 301a: shell part 301b: shell part 301c: shell part 302: shell part 303: shell part 305: Front housing part 305a: Partial 305b: part/front part 310: lens 311: lens 320: electronic device 322: imaging device 323: imaging device 324: Electromagnetic shielding 325: Control Panel 326: focus part 327: focus part 328: Fixed connecting piece 350: bracket 352: Pedestal 354: foot 356: Hinge 358: holding part 400: Multi-mode imaging equipment/imaging equipment/optical coherent tomography imaging device 410: Optical coherent tomography source assembly/source assembly 412: light source 416: Cylindrical lens 418: beam splitter 420: Sampling component 422: Scanning Mirror 424: Fixed dichroic beam splitter 440: Reference component 442: Dispersion Compensator 444: Cylindrical lens 446: Folding Mirror 448: Reference Surface 450: Detection component 451: Optical Coherent Tomography Motor Scan Window 452: Aspheric lens 454: Plano-concave lens 456: Achromatic lens 458: Transmission grating 460: Achromatic lens 468: OCT Camera 470: Infrared camera 476: fixed display 510: Illustrative source component/source component/sampling component 512: light source 514: beam expander 516: Cylindrical lens 518: beam splitter 520: Exemplary sampling assembly/sampling assembly 522: Scanning Mirror 524: fixed dichroic beam splitter 526: Infrared light fundus dichroic mirror 528: Plano-convex lens/lens 530: biconcave lens/lens 532: Plano-concave lens/lens 534: Plano-convex lens/lens 540: Illustrative reference component/reference component 542: Dispersion Compensator 544: collimating lens 546: Folding Mirror 548: Reference Surface 550: Exemplary detection component/detection component 552: Aspheric lens 554: Plano-Concave Lens 556: Achromatic lens 558: Transmission grating 560: Achromatic lens 562: Polarizer 564: Plano-convex lens 566: Plano-Concave Lens 568: Optical Coherent Tomography (OCT) Camera 570: Infrared camera 572: Focusing lens 574: focus lens 576: fixed display 590: Pupil Relay Assembly 600: Multi-mode imaging equipment/imaging equipment 602: Optical Coherent Tomography and Infrared Optical Components/Components/Optical Coherent Tomography Components 602’: Alternative components/components 602’’: Alternative component/component 610: source component 612: Light Source 616: collimator lens/cylindrical lens 618: beam splitter 620: Sampling component 622: Scanning Mirror 624: Infrared light fundus dichroic spectroscope/fixed dichroic spectroscope 626: Infrared light fundus dichroic spectroscope/fixed dichroic spectroscope 630: Plano-convex lens/lens 632: biconcave lens/lens 634: Plano-convex lens/lens 636: lens 640: Reference component 640’’: Reference component 642: Dispersion Compensator 644: collimating lens 648: Reference Surface 648a: Reference surface 648b: Reference surface 650: Detection component 651: Motor and scan window 652: Pickup Mirror 653: Aspheric lens 654: Achromatic lens 656: Achromatic lens 658: Transmission grating 658’: Reflection grating 660a: Sampling component / infrared light detection component 660b: Replace infrared light detection component/infrared light detection component 660c: infrared light detection component 662: Astigmatism Corrector 664: Infrared camera 666: field lens/cylindrical lens pair/lens 668: Optical Coherent Tomography Camera 670: fixed components 672: fixed lens 674: fixed display 680a: Diopter adjustable components 680b: Adjustable diopter lens 682: Diopter motor 684: Diopter mechanism 690a: pupil relay lens 690b: Infrared pupil repeater/pupil repeater 690c: Detection component/pupil relay lens 692: Fiber 694: Off-axis LED 696: Diffraction Plate 798a: horizontal scan path 798b: vertical scan path 1202: dotted line 1204: solid line 1500: Broadband transmitter 1501: The first diode laser 1502: The second diode laser 1503: The third diode laser 1504: The first two-way beam splitter 1505: The second two-way beam splitter 1600: Multi-mode imaging equipment/imaging equipment 1604: White light and fluorescent imaging components 1610: White light source assembly 1612: white light source 1614: collimating lens 1616: Laser dichroic beam splitter 1620: Excitation source component 1622: Laser 1624: collimating lens 1626: mirror 1630: Sampling component 1632: Achromatic lens 1634: iris 1636: Illuminating Mirror 1637: positioning components 1638: Achromatic lens 1640: fixed display 1642: Fixed dichroic beam splitter 1650: Detection component 1652: Achromatic lens 1654: Two-way beam splitter 1656: Focusing lens 1658: camera 1704: Replacement of fluorescent and white light imaging components/fluorescent and white light imaging components/fluorescent and white light components 1710: White light source assembly 1712: white light source/light source 1714: collimating lens 1722a: the first laser 1722b: second laser 1724a: The first collimating lens/collimating lens 1724b: second collimating lens/collimating lens 1726a: The first laser dichroic beam splitter 1726b: Second laser dichroic beam splitter 1728: mirror 1730: Sampling components 1732: The first achromatic lens 1734: Scattering component 1736: hole 1750: Detection component 1752: second achromatic lens 1754: beam splitter 1760: White light camera 1770: Fluorescence detection component 1772: Spectral filter 1774: field lens 1776: Fluorescence sensor 1804: Fluorescent and white light imaging components 1810: White light source assembly 1812: white light source 1814: collimating lens 1816: Laser dichroic beam splitter 1820: Excitation source component/white light source component 1822: Laser 1824: collimating lens 1826: mirror 1830: Sampling components 1832: the first achromatic lens 1834: iris 1836: injection mirror 1838: second achromatic lens 1840: fixed display 1842: Fixed dichroic beamsplitter 1850: Detection component 1852: Iris 1854: Focusing lens 1856: Two-way beam splitter 1858: White light and fluorescent sensor 1930: Replacement sampling kit/sampling kit 1932: Plano-convex lens 1934: biconcave lens 1936: Plano-convex lens 1950: Detection component 1952: Achromatic lens 1956: Achromatic lens 1958: camera 1990: Pupil relay lens

The drawings are not intended to be drawn to scale. In the drawings, each identical or nearly identical component illustrated in the various figures is represented by a similar number. For clarity, not every component can be marked in every drawing. In the schema:

Figure 1A is a front perspective view of a multi-mode imaging device according to some embodiments.

FIG. 1B is a rear perspective view of one of the multi-mode imaging apparatus of FIG. 1B according to some embodiments.

Figure 2 is a bottom perspective view of an alternative embodiment of a multi-mode imaging device according to certain embodiments.

Figure 3A is a rear perspective view of an alternative embodiment of a multi-mode imaging device according to certain embodiments.

FIG. 3B is an exploded view of the multi-mode imaging device of FIG. 3A according to some embodiments.

Fig. 3C is a side view of a subject operating one of the multi-mode imaging devices of Figs. 3A to 3B according to certain embodiments.

3D is a side perspective view of the multi-mode imaging device of FIGS. 3A to 3C supported by a stand according to some embodiments.

4A is a top perspective view of a multi-mode imaging device including a combined optical coherent tomography (OCT) and infrared (IR) imaging device according to some embodiments.

FIG. 4B is a top view of the multi-mode imaging apparatus of FIG. 4A according to some embodiments, in which a part of the housing and some of the imaging device are removed.

Figure 4C is a side perspective view of the multi-mode imaging device as shown in Figure 4B according to some embodiments.

Fig. 4D is a top view of the multi-mode imaging device of Fig. 4A according to some embodiments, with the top part of the housing removed.

4E is a side perspective view of the components of the OCT and IR imaging device of the multi-mode imaging device of FIGS. 4A to 4D according to some embodiments.

FIG. 5A is a top view of a source component of the OCT imaging device of FIGS. 4A to 4C according to some embodiments.

FIG. 5B is a side view of the sampling assembly of the OCT imaging device of FIG. 5A according to some embodiments.

Fig. 5C is a top view of the sampling assembly shown in Fig. 5B according to some embodiments.

5D is a perspective view of the source assembly and sampling assembly shown in FIGS. 5A to 5C according to some embodiments.

FIG. 5E is a perspective view of the reference components of the OCT imaging device of FIGS. 4A to 4C according to some embodiments.

Figure 5F is a perspective view of the source component and the reference component shown in Figures 5A and 5E according to some embodiments.

FIG. 5G is a top view of the detection component of the OCT imaging device of FIGS. 4A to 4C according to some embodiments.

FIG. 5H is a perspective view of a source component, a reference component, and a detection component shown in FIGS. 5A and 5E to 5G according to some embodiments.

FIG. 5I is a perspective view of the sampling assembly of FIGS. 5B to 5D coupled to an infrared light (IR) camera and fixed assembly according to some embodiments.

6A is a top perspective view of an alternative embodiment of a multi-mode imaging device including a combined optical coherent tomography (OCT) and infrared light (IR) imaging device according to some embodiments.

FIG. 6B is a side perspective view of the components of the OCT and IR imaging device of FIG. 6A according to some embodiments.

6C is an exploded view of an alternative component that may be included in the OCT and IR imaging devices of FIGS. 6A to 6B according to some embodiments.

FIG. 7A is a block diagram illustrating the components of the OCT and IR imaging device of FIGS. 6A to 6B according to some embodiments.

FIG. 7B illustrates a block diagram of alternative components that may be included in the OCT and IR imaging devices of FIGS. 6A to 6B according to certain embodiments.

FIG. 8 is a top view of a sampling component and a fixing component of the OCT and IR imaging device of FIG. 6A to FIG. 7A according to some embodiments.

FIG. 9A is a side view of an IR detection component that can be coupled to the sampling component of FIG. 8 according to some embodiments.

Figure 9B is a side view of the pupil repeater shown in Figure 9A according to some embodiments.

Fig. 9C is a top view of the pupil repeater of Figs. 9A to 9B according to some embodiments.

FIG. 9D is a side view of an alternative IR detection component that can be coupled to the sampling component of FIG. 8 according to some embodiments.

FIG. 9E is a side view of other alternative IR detection components that can be coupled to the sampling component of FIG. 8 according to certain embodiments.

FIG. 10 is a top view of the detection component of the OCT imaging device of FIGS. 6A to 6B according to some embodiments.

FIG. 11A is a side view of the sampling assembly of FIG. 8 illustrating the scanning path of the OCT and IR imaging device according to some embodiments.

FIG. 11B is a side view of the sampling assembly including the diopter compensation assembly shown in FIG. 11A according to some embodiments.

FIG. 12 is a graph of the light intensity of a light source of an imaging device over time when the light source pulse is synchronized with one or more cameras of the imaging device according to some embodiments.

FIG. 13 is a diagram illustrating a retinal spot pattern for a pupil relay component that may be included in an imaging device according to certain embodiments.

Figure 14A illustrates the individual interference amplitudes of three different light sources used in an optical coherent tomography (OCT) device according to certain embodiments.

Figure 14B illustrates the combined interference amplitude of three different light sources used in an optical coherent tomography device according to certain embodiments.

Figure 15A illustrates a light emitter having multiple light sources for use in an optical coherent tomography apparatus according to certain embodiments.

Figure 15B illustrates a light emitter having a line of multiple light sources that emit light for use in an optical coherent tomography apparatus according to certain embodiments.

Figure 16A is a top view of a white light imaging component and a fluorescent imaging component of a multi-mode imaging device according to some embodiments.

FIG. 16B is a top view of the white light imaging component and the fluorescent imaging component of FIG. 16A according to some embodiments, with parts of the imaging device removed.

FIG. 17 is a perspective view of an alternative white light imaging component and a fluorescent imaging component that may be included in the imaging device of FIG. 16A according to some embodiments.

FIG. 18 is a perspective view of other alternative white light imaging components and fluorescent imaging components that may be included in the imaging device of FIG. 16A according to certain embodiments.

FIG. 19 is a side view of alternative sampling components and detection components that may be included in the white light imaging components and fluorescent imaging components of FIG. 17 or FIG. 18 according to some embodiments.

FIG. 20A is a graph of an optical pattern generated using two iResearch disks separated by a distance of 1.22 wavelengths according to some embodiments.

FIG. 20B is a graph of an optical pattern generated using two iResearch disks separated by a distance of 1.41 wavelengths according to some embodiments.

FIG. 20C is a graph of an optical pattern generated by using two iResearch disks separated by a distance of a distance of 2.44 wavelengths according to some embodiments.

101: Shell

102: First shell section/shell section

103: second shell section/shell section

104: Rear shell section

105: front housing section

110: first opening/opening

111: second opening/opening

122: first imaging device/imaging device/first optical device

123: second imaging device/imaging device/second optical device

Claims (105)

An imaging device for imaging the retinal fundus of a subject and/or measuring the retinal fundus of a subject, the device including at least two imaging devices selected from one of the following groups and/or Or measuring device: A white light imaging device; A fluorescent imaging device; An infrared light imaging device; and/or An optical coherent tomography device. The imaging device of claim 1, wherein the imaging device includes the white light imaging device and the fluorescent imaging device. Such as the imaging device of claim 1, wherein the imaging device includes the white light imaging device and the optical coherence tomography device. The imaging device of claim 1, wherein the imaging device includes the white light imaging device, the fluorescent imaging device, and the optical coherent tomography device. Such as the imaging device of claim 1, wherein the imaging device includes the fluorescent imaging device, and wherein the fluorescent imaging device is configured to determine the spectral information and lifetime information of the received fluorescent emission. The imaging device of any one of claims 1 to 5, further comprising a housing having at least two housing sections configured to support the at least two imaging devices. The imaging device of claim 6, wherein the at least two housing sections include two housing sections with optical components configured to align with the subject's eyes. Such as the imaging device of claim 7, wherein the shell system is binocular-shaped. Such as the imaging device of claim 7, wherein each of the two housing sections is configured to support at least one of the at least two imaging devices. The imaging device of claim 9, wherein the at least two imaging sections include at least four imaging devices, and wherein each of the two housing sections is configured to support two of the at least four imaging devices. A method for imaging and/or measuring the retinal fundus of a subject, the method comprising: Use at least two of the following to image and/or measure the retinal fundus of one of the subjects: A white light imaging device; An infrared light imaging device; A fluorescent imaging device; and/or An optical coherent tomography device. The method of claim 11, wherein the imaging and/or measurement includes using the white light imaging device and the fluorescent imaging device. The method of claim 11, wherein the imaging and/or measurement includes using the white light imaging device and the optical coherent tomography device. The method of claim 11, wherein the imaging and/or measurement includes using the white light imaging device, the fluorescent imaging device, and the optical coherent tomography device. Such as the method of claim 11, wherein imaging and/or measurement includes using the fluorescent imaging device, and wherein the fluorescent imaging device is configured to determine the spectral information and lifetime information of the received fluorescent emission. The method of any one of claims 11 to 15, further comprising supporting the at least two imaging devices by a housing having at least two housing sections. The method of claim 16, further comprising aligning two of the at least two imaging devices with the subject's eyes. Such as the method of claim 17, wherein the shell system is binocular. The method of claim 17, wherein the two housing sections each support at least one of the at least two imaging devices. The imaging device of claim 19, wherein the at least two housing sections include at least four imaging devices, and wherein the two housing sections each support at least two of the at least four imaging devices. An imaging device for measuring the retinal fundus of a subject and/or imaging the retinal fundus of a subject, the imaging device comprising: A binocular-shaped shell, which includes: A first housing section including a first opening configured to be placed adjacent to a first eye of a subject; and A second housing section including a second opening configured to be placed adjacent to a second eye of the subject; and At least one imaging and/or measurement device supported by the first housing section and/or the second housing section, and the at least one imaging and/or measurement device is configured to enable the subject Imaging the retinal fundus and/or measuring the retinal fundus of the subject. Such as the imaging device of claim 21, wherein the at least one imaging and/or measuring device includes a white light imaging device. Such as the imaging device of claim 21 or 22, wherein the at least one imaging and/or measurement device includes a fluorescent imaging device. Such as the imaging device of claim 23, wherein the fluorescent imaging device is configured for fluorescent spectral imaging. Such as the imaging device of claim 23, wherein the fluorescent imaging device is configured for fluorescent lifetime imaging. Such as the imaging device of claim 23, wherein the fluorescent imaging device is configured for fluorescent intensity imaging. Such as the imaging device of claim 21 or 22, wherein the at least one imaging and/or measurement device includes a white light imaging device in the first housing section and an optical coherence tomography in the second housing section Scanning device. The imaging device of claim 27, wherein the at least one imaging and/or measuring device further includes a fluorescent imaging device in the first housing section. Such as the imaging device of claim 28, wherein the at least one imaging and/or measuring device is further configured to pass through the first opening of the first housing section and through the second housing section at different times The second opening displays a fixed object to the subject. Such as the imaging device of claim 29, wherein the fixed object is an image of an object. Such as the imaging device of claim 30, wherein the fixed object is a bright spot. Such as the imaging device of claim 28, wherein the at least one imaging and/or measurement device is further configured to simultaneously display a first fixed object and a first fixed object to the subject through the first opening of the first housing section A second fixed object is displayed to the subject through the second opening of the second housing section. The imaging device of claim 21 or 22, which further includes a grasping member coupled to the housing and configured to be grasped by at least one hand of the subject. Such as the imaging device of claim 21 or 22, which further includes a mounting component attached to the housing and configured to mount the device to a mounting arm and/or bracket. Such as the imaging device of claim 21 or 22, which further includes a hinge part coupled between the first housing section and the second housing section. A device for performing optical coherence tomography (OCT) on the fundus of the retina of a subject, the device comprising: A plurality of light sources, which are configured to emit light; An interferometer configured to: Receiving the light from the plurality of light source components; Divide the light between the reference component and the sampling component; Irradiating one of the eyes of the subject through the sampling components; Recombine the light from the reference components and the sampling components; and An image sensor configured to detect the recombined light from the interferometer. Such as the device of claim 36, wherein the plurality of light sources are configured to emit light of a wavelength different from the others of the plurality of light sources. Such as the equipment of claim 36, wherein the interferometer is a Michelson interferometer. Such as the device of claim 36, wherein the plurality of light sources includes a plurality of light-emitting diodes. The device of claim 36, which further includes at least one dichroic mirror configured to combine light from a plurality of light sources into a single optical path. The device of any one of claims 36 to 40, wherein the plurality of light sources includes three light sources. Such as the device of claim 41, wherein the three light sources include: A first light source configured to emit light having a center wavelength between 620 nm and 630 nm; A second light source configured to emit light having a center wavelength between 635 nm and 645 nm; and A third light source configured to emit light having a center wavelength between 650 nm and 660 nm. Such as the equipment of claim 42, where: The first light source is configured to emit light having a central wavelength of 625 nm; The second light source is configured to emit light having a central wavelength of 640 nm; and The third light source is configured to emit light having a center wavelength of 655 nm. Such as the device of any one of claims 36 to 40, wherein the plurality of light sources are configured to emit light sequentially. Such as the device of claim 44, wherein the image sensor is configured to sequentially detect the recombined light associated with each of the plurality of light sources. Such as the device of claim 45, which further includes at least one processor configured to: Receiving image data associated with the recombined light from the image sensor, wherein the image data includes individual image data associated with each of the plurality of light source components; and Combine the image data associated with each of the plurality of light sources into a single OCT image. A device for performing optical coherence tomography on the fundus of the retina of a subject, the device comprising: A light source, which is configured to emit light; An interferometer configured to: Receiving the light from the light source; Divide the light between the reference component and the sampling component; Irradiating one of the eyes of the subject through the sampling components; Recombine the light from the reference components and the sampling components; and An image sensor configured to detect the recombined light from the interferometer. The device of claim 47, wherein the sampling components are configured to focus a scan line at the retinal fundus of the subject and the reference components are configured to focus a scan line at a reference surface . Such as the equipment of claim 47, wherein the interferometer is a Michelson interferometer. The device of claim 47, which further includes a first cylindrical lens pair located between the light source and the interferometer. Such as the device of claim 50, which further includes a second cylindrical lens pair located between the interferometer and the image sensor. The device of any one of claims 47 to 51, which further includes a transmission grating located between the interferometer and the image sensor. The device of claim 47, wherein the interferometer is configured to scan the scan line at the retinal fundus of the subject in a direction across the fundus. The device of claim 47, wherein the image sensor is configured to detect the recombined light from the interferometer so that different parts of the image sensor correspond to different scans of a part of the fundus of the retina. A device for performing time-domain optical coherence tomography on the fundus of the retina of a subject, the device comprising: A light source, which is configured to emit light; A Michelson interferometer configured to: Receiving the light from the light source; Divide the light between the reference component and the sampling component; Irradiating one of the eyes of the subject through the sampling components; Recombine the light from the reference components and the sampling components; and An image sensor configured to detect the recombined light from the Michelson interferometer in two image frames obtained at an interval of less than 100 milliseconds. Such as the device of claim 55, wherein the light source is configured to emit a plurality of light pulses synchronized with a frame rate of the image sensor. Such as the equipment of claim 56 in which the light source is configured to: Emitting a first light pulse of the plurality of light pulses at a first time corresponding to the end of a first frame of the image sensor; and A second light pulse of the plurality of light pulses is emitted at a second time corresponding to the beginning of a second frame of the image sensor, wherein the second frame is the next frame after the first frame A picture frame. The device of claim 56, wherein each light pulse emitted by the light source has a duration that is less than the duration of a frame of the image sensor. Such as the equipment of claim 58, where: The light source is configured to emit each light pulse having a duration between 0.1 millisecond and 5 milliseconds; and The image sensor is configured to have a frame duration between 5 ms and 20 ms. Such as the device of claim 55, where: The light source is configured to emit each light pulse having a duration between 0.1 millisecond and 1 millisecond; and The image sensor is configured to have a frame duration between 9 milliseconds and 11 milliseconds. A device for imaging and/or measuring the retinal fundus of a subject, the device comprising: A shell A white light imaging device supported by the housing; and A fluorescent imaging device supported by the housing, The white light imaging device and the fluorescent imaging device share at least a part of a common optical path in the housing. Such as the equipment of claim 61, wherein the white light imaging device and the fluorescent imaging device share an imaging sensor. Such as the equipment of claim 62, in which: The white light imaging device includes a white light source; The fluorescent imaging device includes at least one laser; and The device further includes an optical element configured to combine an optical path of the light emitted from the white light source and an optical path of the light emitted from the at least one laser, so that the light emitted from the white light source and The light emitted from the at least one laser shares the common optical path. Such as the equipment of claim 63, in which: The fluorescent imaging device includes a first laser configured to emit light at a first wavelength, and a second laser configured to emit light at a second wavelength; and The equipment includes: A first optical element configured to combine the optical path of light emitted from the white light source and an optical path of light emitted from the first laser; and A second optical element configured to combine the optical path of the light emitted from the white light source and the optical path of the light emitted from the first laser and the light emitted from the second laser An optical path such that the light emitted from the white light source, the light emitted from the first laser, and the light emitted from the second laser share the common optical path. The device of claim 63, wherein the common optical path includes a path from the first optical element to an eye of the subject and a path from the eye of the subject to the imaging sensor. The device of any one of claims 61 to 65, further comprising a reflector in the common optical path, the reflector including an opening configured to allow light reflected from the fundus of the retina to pass through an opening of the reflector. Such as the equipment of claim 61 to 65, which further includes a device configured to transmit light for a fluorescent imaging device to the fluorescent imaging sensor and reflect light for a white light imaging device to the white Optical image sensor and one beam splitter. The device of claim 67, wherein a transmittance of the beam splitter is greater than a reflectance of the beam splitter. The device of claim 68, wherein the fluorescent imaging sensor is configured to detect a fluorescent lifetime of at least one molecule in the subject's eye. The device of claim 68, wherein the fluorescent imaging sensor is configured to detect a fluorescent wavelength of at least one molecule in the subject's eye. A method including: A white light imaging device and a fluorescent imaging device that at least partially share an optical path are used to image the retinal fundus of a subject. A method including: Use a device including at least two imaging and/or measurement devices selected from one of the following groups to image the retinal fundus of a subject and/or measure the retinal fundus of a subject: A white light imaging device; A fluorescent imaging device; and An optical coherent tomography device; and A medical condition of the subject is determined based on an image captured during imaging and/or measurement. The method of claim 72, wherein determining the medical condition includes determining whether the subject has an eye disease. The method of claim 73, wherein the eye disease includes age-related macular degeneration (AMD). The method of claim 73, wherein the eye disease includes Stargard's disease. The method of claim 73, wherein the eye disease includes diabetic retinopathy. The method of claim 73, wherein the eye disease includes macular edema. The method of claim 73, wherein the eye disease includes a macular hole. Such as the method of claim 73, wherein the eye disease includes eye floaters. The method of claim 73, wherein the eye disease includes glaucoma. The method of claim 73, wherein the eye disease includes retinal detachment. The method of claim 73, wherein the eye disease includes cataract. The method of claim 73, wherein the eye disease includes macular microvascular dilation. The method of claim 72, wherein determining the medical condition includes determining whether the subject has a non-ocular disease. The method of claim 84, wherein the non-ocular disease includes Alzheimer's disease. The method of claim 85, wherein determining whether the subject has Alzheimer's disease comprises using the image to determine a thickness of a retinal nerve fiber layer of the subject. The method of claim 84, wherein the non-ocular disease includes Parkinson's disease. The method of claim 87, wherein determining whether the subject has Parkinson's disease comprises using the image to determine a thickness of a retinal nerve fiber layer of the subject. The method of claim 87, wherein determining whether the subject has Parkinson's disease includes using the image to determine a measure of eye tracking ability. The method of claim 84, wherein the non-ocular disease includes a concussion. A method including: Use equipment including at least two of the following to image and/or measure the retinal fundus of a subject: A white light imaging device; A fluorescent imaging device; and An optical coherent tomography device; and Identify the subject based on the image and/or measurement. A method including: Use a device including at least two imaging and/or measurement devices selected from one of the following groups to image the retinal fundus of a subject and/or measure the retinal fundus of a subject: A white light imaging device; A fluorescent imaging device; and An optical coherent tomography device; and A safe access to one of the subjects is obtained based on the image and/or measurement. A method including: Use a device including at least two imaging and/or measurement devices selected from one of the following groups to image the retinal fundus of a subject and/or measure the retinal fundus of a subject: A white light imaging device; A fluorescent imaging device; and An optical coherent tomography device; and Based on the image and/or measurement, a medical condition of the subject is diagnosed. A method including: Use fluorescence lifetime imaging and/or optical coherent tomography imaging to image and/or measure a person's retinal fundus; and Identify the person and/or obtain safe access to one of the persons and/or determine a health state of the person based on the image and/or measurement and/or diagnose a medical condition of the person. A device for retinal imaging and/or measurement, which includes: At least two imaging and/or measurement devices selected from one of the following groups: A white light imaging device; A fluorescent imaging component; and An optical coherent tomography unit; and At least one modularized light transmission, reflection and/or refraction element, which is in one of the light paths of at least one of the at least two imaging and/or measurement devices. Such as the device of claim 95, wherein the at least one modular element includes a mirror. Such as the device of claim 95, wherein the at least one modular component includes a scallop. The device of claim 95, wherein the at least one modular element includes a lens. The device of claim 95, wherein the at least one modular element includes a beam splitter. A device for retinal imaging and/or measurement, which includes: A white light imaging and/or measuring device; A fluorescent imaging and/or measurement device; and At least one modularized light transmission, reflection and/or refraction element, which is in one of the light paths of at least one of the white light imaging and/or measurement device and the fluorescent imaging and/or measurement device. Such as the device of claim 100, wherein the white light imaging device further includes an optical coherent tomography imaging and/or measurement device. Such as the device of claim 100, wherein the device is in the form of a pair of eyepieces. Such as the device of claim 100, wherein the at least one modular element includes at least one component selected from the group consisting of: A pupil repeater; A scanning mirror A light source; A cylindrical lens; and/or One board beam splitter. For example, the device of claim 100, which further includes at least one component in one of the following groups: A complementary metal oxide semiconductor (CMOS) image sensor; An infrared light retinal fundus image sensor; A fluorescent image sensor; and/or A white light retinal fundus image sensor. For example, the device of claim 100 is further configured to display a fixed target including a two-dimensional (2D) screen and/or a light emitting diode (LED) embedded in the device.

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