Fundus measurement methods, devices, computer equipment, storage media and software products

Abstract

This application discloses a fundus measurement method, apparatus, computer equipment, storage medium, and program product for achieving quantitative imaging of the optical properties and tissue composition of the fundus, which are hidden and cannot be directly observed. The method includes: acquiring a first reflected light field image formed by an optical phantom reflecting an illumination light field of a specified spatial frequency, and a second reflected light field image formed by the reflection of the illumination light field by the target fundus; generating a second optical property map of the target fundus in response to the illumination light field based on the first reflected light field image, the second reflected light field image, and a first optical property map of the optical phantom in response to the illumination light field; and generating a tissue composition map of the target fundus based on the second optical property map.

Description

Technical Field

[0001] This application relates to the field of quantitative imaging technology, and in particular to a fundus measurement method, device, computer equipment, storage medium, and program product. Background Technology

[0002] In the biomedical field, fundus imaging is often required to assist in disease diagnosis and health monitoring.

[0003] In related technologies, fundus images are obtained by directly capturing images with a color camera. However, these fundus images are non-quantitative images, providing only visual information. The images change with light intensity, camera exposure time, etc., and cannot reflect absolute physical quantities. They cannot quantitatively image the fundus tissues hidden inside and not directly observable, and therefore cannot make quantitative comparisons between different people and at different times. Summary of the Invention

[0004] The purpose of this application is to provide a fundus measurement method, apparatus, computer device, storage medium, and program product for realizing quantitative imaging of the optical characteristics and tissue components of the fundus that are hidden inside and cannot be directly observed.

[0005] To achieve the above objectives, the embodiments of this application adopt the following technical solutions:

[0006] In a first aspect, embodiments of this application provide a fundus measurement method, including:

[0007] Acquire a first reflected light field image formed by the reflection of an illumination light field of a specified spatial frequency by an optical phantom, and a second reflected light field image formed by the reflection of the illumination light field by the fundus of the target eye;

[0008] Based on the first reflected light field image, the second reflected light field image, and the first optical characteristic map of the optical phantom to the irradiated light field, a second optical characteristic map of the target fundus to the irradiated light field is generated.

[0009] Based on the second optical property map, a tissue composition map of the target fundus is generated.

[0010] Secondly, embodiments of this application provide a fundus measurement device, comprising:

[0011] The light field illumination module is used to illuminate the optical phantom and the target fundus with an illumination light field of a specified spatial frequency, respectively.

[0012] The detection module is used to acquire a first reflected light field image formed by the reflection of an illumination light field of a specified spatial frequency by an optical phantom, and a second reflected light field image formed by the reflection of the illumination light field by the fundus of the target eye.

[0013] The processing module is configured to generate a second optical characteristic map of the target fundus in relation to the irradiated light field based on the first reflected light field image, the second reflected light field image, and a first optical characteristic map of the optical phantom in relation to the irradiated light field, and to generate a tissue composition map of the target fundus based on the second optical characteristic map.

[0014] Thirdly, embodiments of this application provide a computer device, the computer device including a processor and a memory, the processor storing at least one computer program, the at least one computer program being loaded and executed by the processor to implement the fundus measurement method as provided in the first aspect.

[0015] Fourthly, embodiments of this application provide a computer-readable storage medium that, when instructions in the storage medium are executed by a processor of a computer device, enables the computer device to perform the fundus measurement method as provided in the first aspect.

[0016] Fifthly, embodiments of this application provide a computer program product, the computer program product including a non-transitory computer-readable storage medium storing a computer program operable to cause a computer to perform some or all of the steps in the fundus measurement method provided in the first aspect.

[0017] The above-described technical solutions adopted in the embodiments of this application can achieve the following beneficial effects:

[0018] Based on spatial frequency domain imaging technology, images of the reflected light fields formed by the target fundus and the optical phantom at a specified spatial frequency are acquired. Since objects with different optical properties respond differently to illumination fields at different spatial frequencies, the differences between the reflected light field images formed by the target fundus and the optical phantom can reflect the differences in optical properties between the target fundus and the optical phantom. Since the optical properties of the optical phantom to the illumination field are known, an optical property map of the target fundus to the illumination field can be obtained based on the optical property map of the optical phantom to the illumination field and the reflected light field images formed by the target fundus and the optical phantom, thereby achieving quantitative imaging of the optical properties of the target fundus. Furthermore, since there is a correlation between the optical properties of biological tissues and their tissue components, an analysis of the optical property map of the target fundus to the illumination field can yield a tissue composition map of the target fundus, thereby achieving quantitative imaging of the tissue components of the target fundus. Attached Figure Description

[0019] The accompanying drawings, which are included to provide a further understanding of this application and form part of this application, illustrate exemplary embodiments and are used to explain this application, but do not constitute an undue limitation of this application. In the drawings:

[0020] Figure 1 A schematic flowchart of a fundus measurement method provided for one embodiment of this application;

[0021] Figure 2 A schematic diagram of fundus imaging provided for one embodiment of this application;

[0022] Figure 3 A schematic diagram of diffuse reflectance images of an optical phantom and a target fundus at a spatial frequency, provided for an embodiment of this application;

[0023] Figure 4 A schematic diagram illustrating the mapping relationship between diffuse reflectance, scattering coefficient, and absorption coefficient, provided for one embodiment of this application;

[0024] Figure 5 A schematic diagram of a target fundus tissue component concentration image provided for one embodiment of this application;

[0025] Figure 6 A schematic diagram of the structure of a fundus measurement device provided in one embodiment of this application;

[0026] Figure 7 This is a schematic diagram of the structure of a computer device provided in one embodiment of this application. Detailed Implementation

[0027] To make the purpose, technical solutions, and advantages of this application more clear, the technical solutions of this application will be clearly and completely described below in conjunction with the specific embodiments of this application and the corresponding drawings. Obviously, the embodiments described are only part of the embodiments of this application, not all of them. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of this application.

[0028] The terms "first," "second," etc., used in this specification and claims are used to distinguish similar objects and not to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that embodiments of this application can be implemented in orders other than those illustrated or described herein. Furthermore, in this specification and claims, "and / or" indicates at least one of the connected objects, and the character " / " generally indicates that the preceding and following objects are in an "or" relationship.

[0029] Explanation of some terms:

[0030] Spatial frequency domain: Corresponds to time frequency.

[0031] Spatial Frequency Domain Imaging (SFDI): An optical method that uses structured light to measure objects with optical absorption and scattering properties (such as biological tissues and fruits). The structured light used has a specific spatial frequency (e.g., 0~0.5mm). -1 Objects with different absorption and scattering properties respond differently to structured light of different spatial frequencies. Therefore, structured light of several spatial frequencies can be used to measure objects and calculate their absorption and scattering coefficients. From the absorption and scattering coefficients of an object, information such as the size and distribution of its main components and internal parts can be deduced. For example, measuring the absorption coefficients at multiple wavelengths can help calculate information such as the concentration of oxyhemoglobin, deoxyhemoglobin, and oxygen saturation in biological tissues.

[0032] As mentioned earlier, related technologies involve directly capturing fundus images using a color camera. However, these fundus images are non-quantitative images, providing only visual information. The images change with light intensity, camera exposure time, etc., and cannot reflect absolute physical quantities. They cannot quantitatively image the fundus tissues hidden inside and not directly observable, and therefore cannot make quantitative comparisons between different people and at different times.

[0033] In view of this, the fundus measurement method proposed in this application, based on spatial frequency domain imaging technology, acquires the reflected light field images formed by the target fundus and the optical phantom at a specified spatial frequency of illumination light field. Since objects with different optical properties respond differently to illumination light fields of different spatial frequencies, the difference between the reflected light field images formed by the target fundus and the optical phantom can reflect the difference in optical properties between the target fundus and the optical phantom. Since the optical properties of the optical phantom to the illumination light field are known, the optical property map of the target fundus to the illumination light field can be obtained based on the optical property map of the optical phantom to the illumination light field and the reflected light field images formed by the target fundus and the optical phantom, thereby achieving quantitative imaging of the optical properties of the target fundus. Furthermore, since there is a correlation between the optical properties of biological tissues and their tissue components, by analyzing the optical property map of the target fundus to the illumination light field, the tissue composition map of the target fundus can be obtained, thereby achieving quantitative imaging of the tissue components of the target fundus.

[0034] The technical solutions provided by the various embodiments of this application are described in detail below with reference to the accompanying drawings.

[0035] Please refer to Figure 1 The following is a flowchart illustrating a fundus measurement method according to an embodiment of this application. The method includes the following steps:

[0036] S102, acquire a first reflected light field image formed by the reflection of the irradiation light field of the optical phantom at a specified spatial frequency, and a second reflected light field image formed by the reflection of the irradiation light field by the fundus of the target eye.

[0037] An optical phantom is an artificially manufactured material or structure whose optical properties (such as absorption, scattering coefficient, refractive index, etc.) are designed to resemble those of a real eye.

[0038] Specifically, the optical phantom is irradiated with an irradiation light field (such as structured light) of a specified spatial frequency through the light field irradiation module, generating a corresponding diffuse reflection light field in the fundus. The image of this diffuse reflection light field (i.e., the first reflection light field image) is detected by the detection module.

[0039] The target fundus refers to the fundus of the eye being measured. Similarly, such as Figure 2 As shown, a light field of a specified spatial frequency is irradiated onto the human eye through the light field irradiation module. The irradiated light field passes through the lens in front of the eye and is irradiated onto the fundus without distortion, forming a light field of the specified spatial frequency on the fundus. The irradiated light field generates a corresponding diffuse reflection light field on the fundus, and the image of the diffuse reflection light field (i.e., the second reflection light field image) is detected by the detection module.

[0040] In practical applications, there can be at least two specified spatial frequencies, each with a different phase. There can also be at least two illumination light fields at each specified spatial frequency, each with a different phase. This means that illumination light fields of the same spatial frequency but with multiple phases can be projected onto the target fundus and the optical phantom, respectively. In this case, illumination light fields of the same spatial frequency but different phases have corresponding first and second reflected light field images.

[0041] Specifically, the spatial frequency of the illumination light field can be adjusted by changing the modulation mode of the light field illumination module, thereby enabling the detection module to acquire the first reflected light field image of the optical phantom at at least two specified spatial frequencies and the second reflected light field image of the target fundus at at least two specified spatial frequencies.

[0042] Furthermore, the wavelengths of the illumination light fields at different specified spatial frequencies are different. In this case, the first optical characteristic map of the optical phantom differs for illumination light fields at different specified spatial frequencies, and consequently, the second optical characteristic map of the target fundus differs for illumination light fields at different specified spatial frequencies.

[0043] S104, based on the first reflected light field image, the second reflected light field image, and the first optical characteristic map of the optical phantom in relation to the illumination light field, generate the second optical characteristic map of the target fundus in relation to the illumination light field.

[0044] The first optical characteristic map of an optical phantom with respect to an irradiated light field is used to represent the distribution of optical characteristic parameters (such as absorption coefficient, scattering coefficient, etc.) of the optical phantom, that is, the optical characteristic parameters of the optical phantom at various positions with respect to the irradiated light field. When there are multiple specified spatial frequencies, and the wavelength of the irradiated light field is different for each specified spatial frequency, the optical phantom has a corresponding first optical characteristic map for each wavelength of irradiated light field. Specifically, the first optical characteristic map includes: a first absorption coefficient map and a first scattering coefficient map of the optical phantom at each wavelength. The first absorption coefficient map for each wavelength represents the distribution of the absorption coefficient of the optical phantom at that wavelength, and the first scattering coefficient map for each wavelength represents the distribution of the scattering coefficient of the optical phantom at that wavelength.

[0045] The above-mentioned S104 can be implemented in various appropriate ways, and the embodiments of this application do not limit it.

[0046] In one embodiment, since the illumination light fields of different specified spatial frequencies carry the absorption and scattering information of the target fundus, and with the corresponding system optical path calibration, the optical characteristics of the target fundus at different wavelengths can be calculated using diffusion optics theory.

[0047] In another embodiment, since objects with different optical properties respond differently to illumination light fields of different spatial frequencies, the difference between the reflected light field images formed by the target fundus and the optical phantom can reflect the difference in optical properties between the target fundus and the optical phantom. Since the optical properties of the optical phantom to the illumination light field are known, the optical property map of the target fundus to the illumination light field can be obtained based on the optical property map of the optical phantom to the illumination light field and the reflected light field images formed by the target fundus and the optical phantom, thereby realizing quantitative imaging of the optical properties of the target fundus.

[0048] Specifically, S104 above includes the following steps:

[0049] S141, Analyze the first reflected light field image to obtain the first diffuse reflectance map of the optical phantom at a specified spatial frequency.

[0050] The first diffuse reflectance map is used to represent the distribution of diffuse reflectance of an optical phantom at a specified spatial frequency, that is, the diffuse reflectance of each position of the optical phantom at a specified spatial frequency.

[0051] For each specified spatial frequency, by analyzing the first reflected light field image formed by the reflection of the illumination light field of the optical phantom at that specified spatial frequency, the first diffuse reflectance map of the optical phantom at that specified spatial frequency can be obtained.

[0052] As an example, such as Figure 3As shown, for each specified spatial frequency, the number of illumination light fields at that specified spatial frequency can be three, that is, three illumination light fields with the same specified spatial frequency but different phases are respectively irradiated onto the optical phantom to obtain the first reflected light field image formed by the optical phantom for each illumination light field; further, by demodulating and calibrating the first reflected light field images corresponding to the three illumination light fields with the same specified spatial frequency but different phases, the diffuse reflectance of each position of the optical phantom at the specified spatial frequency can be obtained, thereby generating the first diffuse reflectance map of the optical phantom at the specified spatial frequency.

[0053] S142, Analyze the second reflected light field image to obtain the second diffuse reflectance image of the target fundus at a specified spatial frequency.

[0054] As an example, such as Figure 3 As shown, for each specified spatial frequency, the number of illumination light fields at that specified spatial frequency can be three, that is, three illumination light fields with the same specified spatial frequency but different phases are respectively irradiated onto the target fundus, and a second reflected light field image formed by the reflection of the target fundus for each illumination light field is obtained; further, by demodulating and calibrating the second reflected light field images corresponding to the three illumination light fields with the same specified spatial frequency but different phases, the diffuse reflectance of each position of the target fundus at the specified spatial frequency can be obtained, thereby generating a second diffuse reflectance map of the target fundus at the specified spatial frequency.

[0055] S143, based on the first diffuse reflectance image and the first optical characteristic map, determine the first mapping relationship between the diffuse reflectance at a specified spatial frequency and the optical characteristic parameters.

[0056] Specifically, based on the first diffuse reflectance map, the diffuse reflectance at each location of the optical phantom is determined; based on the first optical characteristic map, the optical characteristic parameters at each location of the optical phantom are determined; based on the diffuse reflectance and optical characteristic parameters at each location of the optical phantom, a first mapping relationship between the diffuse reflectance and optical characteristic parameters at a specified spatial frequency is determined.

[0057] More specifically, by fitting the diffuse reflectance and optical characteristic parameters at various locations of the optical phantom, the first mapping relationship between the diffuse reflectance and optical characteristic parameters at a specified spatial frequency can be obtained.

[0058] Alternatively, by incorporating the diffuse reflectance and optical characteristic parameters of various locations on the optical phantom into a diffusion model or a Monte Carlo model, a first mapping relationship between the diffuse reflectance and optical characteristic parameters at a specified spatial frequency can be obtained. Both the diffusion model and the Monte Carlo model are mathematical models that describe the correspondence between diffuse reflectance and optical characteristic parameters at different spatial frequencies.

[0059] For example, such as Figure 4As shown, the optical characteristic parameters of this application embodiment may include, but are not limited to: optical coefficient absorption (absorption coefficient for short) and reduced scattering absorption (scattering absorption for short). In this case, the first mapping relationship may include, but is not limited to: the mapping relationship between diffuse reflectance and absorption coefficient at a specified spatial frequency (e.g., Figure 4 As shown on the left), the mapping relationship between diffuse reflectance and scattering coefficient at a specified spatial frequency (e.g.) Figure 4 (As shown on the right side of the middle section).

[0060] S144, based on the first mapping relationship and the second diffuse reflectance map, generate the second optical characteristic map of the target fundus in response to the illumination light field.

[0061] Specifically, the diffuse reflectance of each location of the target fundus is determined from the first diffuse reflectance map. Then, based on the diffuse reflectance of each location of the target fundus and the first mapping relationship, the optical characteristic parameters of each location of the target fundus to the illumination light field are determined, and then integrated to generate the second optical characteristic map of the target fundus to the illumination light field.

[0062] More specifically, based on the first mapping relationship and the second diffuse reflectance map at at least two specified spatial frequencies, a linear equation (which may be called the second linear equation) is established. This linear equation describes the mapping relationship between the diffuse reflectance and optical characteristic parameters at each specified spatial frequency of the target fundus. Furthermore, solving this linear equation yields the optical characteristic parameters such as the absorption coefficient and scattering coefficient at each location of the target fundus. Finally, based on these optical characteristic parameters, a second optical characteristic map is generated, for example... Figure 3 The image shows the second absorption coefficient and the second scattering coefficient of the target fundus.

[0063] S106, Based on the second optical property map, generate a tissue composition map of the target fundus.

[0064] Absorption and scattering are two physical effects of light on biological tissues. The scattering coefficient is related to the size of the components that make up the biological tissue, while the absorption coefficient is related to the concentration of those components. Based on this, by using the second optical characteristic map of the target fundus, the size and concentration of the tissue components in the target fundus can be determined, and a corresponding tissue composition map can be generated, thereby achieving quantitative imaging of the tissue components in the target fundus.

[0065] Specifically, in one embodiment, the number of specified spatial frequencies is at least two, and the wavelength of the irradiated light field is different for each specified spatial frequency. The second optical characteristic map includes a second absorption coefficient map and a second scattering coefficient map of the target fundus at each wavelength. Accordingly, the above-described S106 may include the following steps:

[0066] S161, Based on the second scattering coefficient map of the target fundus at at least two wavelengths, generate a size distribution map of the tissue components of the target fundus.

[0067] The size distribution map of tissue components is used to represent the size of tissue components at various locations in the target fundus.

[0068] Specifically, when light propagates through tissue, it is scattered when it encounters various components within the tissue. From a microscopic perspective, strong scattering occurs when the wavelength of light is similar to the size of the tissue components. For example, when the size of the tissue components is much smaller than the wavelength of light, Rayleigh scattering primarily occurs; when the size of the tissue components is similar to or larger than the wavelength of light, Mie scattering occurs. Based on this, a mathematical model can be established to determine the size of the tissue components using the aforementioned Mie and Rayleigh scattering theories, combined with the measured second scattering coefficient diagram and other known parameters (such as the wavelength of the irradiating light field, the refractive index at various locations in the target fundus, etc.).

[0069] S162, based on the second absorption coefficient map of the target fundus at at least two wavelengths, generate a concentration distribution map of the tissue components of the target fundus.

[0070] Tissue component concentration distribution maps are used to identify the concentration of tissue components at various locations in the target fundus. For example, Figure 5 It shows the concentration distribution maps of tissue components such as oxyhemoglobin and deoxyhemoglobin, as well as the concentration distribution maps of total hemoglobin and oxygen saturation.

[0071] As an example, for each wavelength, based on the second absorption coefficient map of the target fundus at that wavelength, a second mapping relationship between the absorption coefficient of each location of the target fundus at that wavelength and the concentration of tissue components is determined; based on the second mapping relationship between the absorption coefficient of each location at at least two wavelengths and the concentration of tissue components, a first linear equation is established; the first linear equation is solved to obtain the concentration of tissue components at each location; based on the concentration of tissue components at each location, a concentration distribution map of tissue components in the target fundus is generated.

[0072] According to Beer-Lambert's law, for each location in the target fundus, the second mapping relationship between the absorption coefficient of that location at each wavelength and the concentration of the tissue component is: the absorption coefficient of that location at each wavelength is the sum of the products of the concentration of the tissue component at that location and the extinction coefficient of the tissue component.

[0073] For example, the main tissue components of the target fundus include oxyhemoglobin, deoxyhemoglobin, lipids, and water. In this case, any location in the target fundus at a wavelength... The second mapping relationship between the absorption coefficient and the concentration of tissue components is shown in the following formula (1), where the target fundus is located at a wavelength of [wavelength value missing]. The second mapping relationship between the absorption coefficient and the concentration of tissue components is shown in the following formula (2).

[0074] (1)

[0075] (2)

[0076] in, This indicates that any location in the fundus of the target eye is at a wavelength of absorption coefficient, This indicates that oxyhemoglobin at a wavelength The extinction coefficient, This indicates the concentration of oxyhemoglobin at that location. This indicates that deoxyhemoglobin is at a wavelength The extinction coefficient, This indicates the concentration of deoxyhemoglobin at that location. Indicates water content at wavelength The extinction coefficient, This indicates the water concentration at that location. Indicates lipids at wavelength The extinction coefficient, This indicates the concentration of lipids at that location.

[0077] This indicates that any location in the fundus of the target eye is at a wavelength of absorption coefficient, This indicates that oxyhemoglobin at a wavelength The extinction coefficient, This indicates that deoxyhemoglobin is at a wavelength The extinction coefficient, Indicates water content at wavelength The extinction coefficient, Indicates lipids at wavelength The extinction coefficient.

[0078] Furthermore, based on the above second mapping relationship, the first linear equation shown in the following formula (3) can be established.

[0079] (3)

[0080] Furthermore, by solving the first linear equation mentioned above, the concentrations of tissue components such as oxyhemoglobin, deoxyhemoglobin, water, and lipids at any location in the target fundus can be obtained.

[0081] The tissue composition maps obtained through the above methods, without skin obstruction, can more accurately reflect the concentration and size distribution of tissue components, such as the hemoglobin concentration in the retinal blood vessels, and can provide new methods and techniques for disease diagnosis and treatment.

[0082] One or more embodiments of this application provide a fundus measurement method that, based on spatial frequency domain imaging technology, acquires reflected light field images formed by the target fundus and the optical phantom at a specified spatial frequency of illumination. Since objects with different optical properties respond differently to illumination fields of different spatial frequencies, the differences between the reflected light field images formed by the target fundus and the optical phantom reflect the differences in optical properties between them. Since the optical properties of the optical phantom in response to the illumination field are known, an optical property map of the target fundus in response to the illumination field can be obtained based on the optical property map of the optical phantom and the reflected light field images formed by the target fundus and the optical phantom, thereby achieving quantitative imaging of the optical properties of the target fundus. Furthermore, since there is a correlation between the optical properties of biological tissues and their tissue components, an analysis of the optical property map of the target fundus in response to the illumination field can yield a tissue composition map of the target fundus, thereby achieving quantitative imaging of the tissue components of the target fundus.

[0083] The foregoing has described specific embodiments of this specification. Other embodiments are within the scope of the appended claims. In some cases, the actions or steps recited in the claims may be performed in a different order than that shown in the embodiments and may still achieve the desired result. Furthermore, the processes depicted in the drawings do not necessarily require the specific or sequential order shown to achieve the desired result. In some embodiments, multitasking and parallel processing are possible or may be advantageous.

[0084] Based on the same inventive concept, this application also provides a fundus measurement device. Please refer to... Figure 6 The following is a schematic diagram of the structure of a fundus measurement device 600 provided in an embodiment of this application. The device 600 includes: a light field illumination module 610, a detection module 620, and a processing module 630.

[0085] The light field illumination module 610 is used to illuminate the optical phantom and the target fundus with an illumination light field of a specified spatial frequency, respectively.

[0086] The detection module 620 is used to acquire a first reflected light field image formed by the reflection of an illumination light field of a specified spatial frequency by an optical phantom, and a second reflected light field image formed by the reflection of the illumination light field by the fundus of the target eye.

[0087] The processing module 630 is configured to generate a second optical characteristic map of the target fundus in relation to the irradiated light field based on the first reflected light field image, the second reflected light field image, and a first optical characteristic map of the optical phantom in relation to the irradiated light field, and to generate a tissue composition map of the target fundus based on the second optical characteristic map.

[0088] In another embodiment, when the processing module generates a second optical characteristic map of the target fundus relative to the irradiated light field based on the first reflected light field image, the second reflected light field image, and the first optical characteristic map of the optical phantom with respect to the irradiated light field, the following steps are performed:

[0089] Analyze the first reflected light field image to obtain the first diffuse reflectance map of the optical phantom under the illumination light field;

[0090] By analyzing the second reflected light field image, a second diffuse reflectance map of the target fundus under the illumination light field is obtained;

[0091] Based on the first diffuse reflectance map and the first optical characteristic map, a first mapping relationship between the diffuse reflectance and optical characteristic parameters at the specified spatial frequency is determined;

[0092] Based on the first mapping relationship and the second diffuse reflectance map, a second optical characteristic map of the target fundus in response to the irradiated light field is generated.

[0093] In another embodiment, when the processing module determines the first mapping relationship between the diffuse reflectance and optical characteristic parameters at the specified spatial frequency based on the first diffuse reflectance map and the first optical characteristic map, it performs the following steps:

[0094] Based on the first diffuse reflectance map, the diffuse reflectance at each location of the optical phantom is determined;

[0095] Based on the first optical characteristic map, the optical characteristic parameters of each position of the optical phantom are determined;

[0096] Based on the diffuse reflectance and optical characteristic parameters at various locations of the optical phantom, a first mapping relationship between the diffuse reflectance and optical characteristic parameters at the specified spatial frequency is determined.

[0097] In another embodiment, the number of specified spatial frequencies is at least two, and the wavelength of the irradiated light field at each specified spatial frequency is different. The second optical characteristic map includes: a second absorption coefficient map and a second scattering coefficient map of the target fundus at each wavelength.

[0098] When generating the tissue composition map of the target fundus based on the second optical property map, the processing module performs the following steps:

[0099] Based on the second scattering coefficient map of the target fundus at at least two wavelengths, a size distribution map of the tissue components of the target fundus is generated;

[0100] Based on the second absorption coefficient map of the target fundus at at least two wavelengths, a concentration distribution map of the tissue components of the target fundus is generated.

[0101] In another embodiment, when the processing module generates a concentration distribution map of the tissue components of the target fundus based on a second absorption coefficient map at at least two wavelengths, it performs the following steps:

[0102] For each wavelength, based on the second absorption coefficient map of the target fundus at that wavelength, a second mapping relationship between the absorption coefficient of each location of the target fundus at that wavelength and the concentration of the tissue component is determined;

[0103] A first linear equation is established based on the second mapping relationship between the absorption coefficients of each location at at least two wavelengths and the concentration of tissue components.

[0104] Solve the first linear equation to obtain the concentration of tissue components at each location;

[0105] Based on the concentration of tissue components at each location, a concentration distribution map of the tissue components in the target fundus is generated.

[0106] In another embodiment, for each location of the target fundus, a second mapping relationship between the absorption coefficient of the location at each wavelength and the concentration of the tissue component is: the absorption coefficient of the location at each wavelength is the sum of the products of the concentration of the tissue component at the location and the extinction coefficient of the tissue component.

[0107] Obviously, the fundus measurement device 600 provided in this application embodiment can be used as the above-mentioned... Figure 1 The entity performing the fundus measurement method shown above is therefore able to realize the fundus measurement method described above. Figure 1 The functions implemented are the same, so they will not be explained again here.

[0108] Figure 7 This is a schematic diagram of the structure of a computer device provided in one embodiment of this application. Please refer to it. Figure 7At the hardware level, the computer device includes a processor, and optionally also an internal bus, network interface, and memory. The memory may include main memory, such as high-speed random-access memory (RAM), or non-volatile memory, such as at least one disk drive. Of course, the computer device may also include other hardware required for its business operations.

[0109] The processor, network interface, and memory can be interconnected via an internal bus, which can be an ISA (Industry Standard Architecture) bus, a PCI (Peripheral Component Interconnect) bus, or an EISA (Extended Industry Standard Architecture) bus, etc. This bus can be divided into address bus, data bus, control bus, etc. For ease of representation, Figure 7 The symbol is represented by a single double-headed arrow, but this does not mean that there is only one bus or one type of bus.

[0110] The memory is used to store programs. Specifically, the program may include program code, which includes computer operating instructions. The memory may include internal memory and non-volatile memory, and provides instructions and data to the processor.

[0111] The processor reads the corresponding computer program from non-volatile memory into main memory and then executes it, forming a fundus measurement device at the logical level. The processor executes the program stored in memory and specifically performs the following operations:

[0112] Acquire a first reflected light field image formed by the reflection of an illumination light field of a specified spatial frequency by an optical phantom, and a second reflected light field image formed by the reflection of the illumination light field by the fundus of the target eye;

[0113] Based on the first reflected light field image, the second reflected light field image, and the first optical characteristic map of the optical phantom to the irradiated light field, a second optical characteristic map of the target fundus to the irradiated light field is generated.

[0114] Based on the second optical property map, a tissue composition map of the target fundus is generated.

[0115] The above is as stated in this application. Figure 1The method performed by the fundus measurement device disclosed in the illustrated embodiment can be applied to a processor or implemented by a processor. The processor may be an integrated circuit chip with signal processing capabilities. During implementation, each step of the above method can be completed by integrated logic circuits in the processor's hardware or by instructions in software form. The processor can be a general-purpose processor, including a Central Processing Unit (CPU), a Network Processor (NP), etc.; it can also be a Digital Signal Processor (DSP), an Application Specific Integrated Circuit (ASIC), a Field-Programmable Gate Array (FPGA), or other programmable logic devices, discrete gate or transistor logic devices, or discrete hardware components. It can implement or execute the methods, steps, and logic block diagrams disclosed in the embodiments of this application. The general-purpose processor can be a microprocessor or any conventional processor. The steps of the method disclosed in the embodiments of this application can be directly embodied in the execution of a hardware decoding processor, or executed by a combination of hardware and software modules in the decoding processor. The software module can reside in a mature storage medium in the field, such as random access memory, flash memory, read-only memory, programmable read-only memory, electrically erasable programmable memory, or registers. This storage medium is located in memory, and the processor reads information from the memory and, in conjunction with its hardware, completes the steps of the above method.

[0116] This computer device can also perform Figure 1 The method, and to realize the fundus device in Figure 1 The functions of the embodiments shown are not described in detail here.

[0117] Of course, in addition to software implementation, the computer device of this application does not exclude other implementation methods, such as logic devices or a combination of hardware and software, etc. In other words, the execution subject of the following processing flow is not limited to each logic unit, but can also be hardware or logic devices.

[0118] This application also proposes a computer-readable storage medium that stores one or more programs, the programs including instructions that, when executed by a computer device including multiple applications, enable the computer device to perform... Figure 1 The method of the embodiment shown is specifically used to perform the following operations:

[0119] Acquire a first reflected light field image formed by the reflection of an illumination light field of a specified spatial frequency by an optical phantom, and a second reflected light field image formed by the reflection of the illumination light field by the fundus of the target eye;

[0120] Based on the first reflected light field image, the second reflected light field image, and the first optical characteristic map of the optical phantom to the irradiated light field, a second optical characteristic map of the target fundus to the irradiated light field is generated.

[0121] Based on the second optical property map, a tissue composition map of the target fundus is generated.

[0122] This application also provides a computer program product, which includes a non-transitory computer-readable storage medium storing a computer program operable to cause a computer to perform some or all of the steps in the fundus measurement method provided in this application.

[0123] In summary, the above description is merely a preferred embodiment of this application and is not intended to limit the scope of protection of this application. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this application should be included within the scope of protection of this application.

[0124] The systems, devices, modules, or units described in the above embodiments can be implemented by computer chips or entities, or by products with certain functions. A typical implementation device is a computer. Specifically, a computer can be, for example, a personal computer, laptop computer, cellular phone, camera phone, smartphone, personal digital assistant, media player, navigation device, email device, game console, tablet computer, wearable device, or any combination of these devices.

[0125] Computer-readable media includes both permanent and non-permanent, removable and non-removable media that can store information using any method or technology. Information can be computer-readable instructions, data structures, modules of programs, or other data. Examples of computer storage media include, but are not limited to, phase-change memory (PRAM), static random access memory (SRAM), dynamic random access memory (DRAM), other types of random access memory (RAM), read-only memory (ROM), electrically erasable programmable read-only memory (EEPROM), flash memory or other memory technologies, CD-ROM, digital versatile optical disc (DVD) or other optical storage, magnetic tape, magnetic disk storage or other magnetic storage devices, or any other non-transferable medium that can be used to store information accessible by a computing device. As defined herein, computer-readable media does not include transient computer-readable media, such as modulated data signals and carrier waves.

[0126] It should also be noted that the terms "comprises," "includes," or any other variations thereof are intended to encompass non-exclusive inclusion, such that a process, method, commodity, or apparatus that includes a series of elements includes not only those elements but also other elements not explicitly listed, or includes elements inherent to such process, method, commodity, or apparatus. In the absence of further limitations, an element defined by the phrase "comprises a ..." does not exclude the presence of other identical elements in the process, method, commodity, or apparatus that includes the element.

[0127] The various embodiments in this specification are described in a progressive manner. Similar or identical parts between embodiments can be referred to interchangeably. Each embodiment focuses on describing the differences from other embodiments. In particular, the system embodiments are basically similar to the method embodiments, so the description is relatively simple; relevant parts can be referred to the descriptions in the method embodiments.

Claims

1. A method for fundus measurement, characterized in that, include: Acquire a first reflected light field image formed by the reflection of an illumination light field of a specified spatial frequency by an optical phantom, and a second reflected light field image formed by the reflection of the illumination light field by the fundus of the target eye; the number of specified spatial frequencies is at least two, and the wavelength of the illumination light field of each specified spatial frequency is different; Based on the first reflected light field image, the second reflected light field image, and the first optical characteristic map of the optical phantom to the irradiated light field, a second optical characteristic map of the target fundus to the irradiated light field is generated. The second optical characteristic map includes: a second absorption coefficient map and a second scattering coefficient map of the target fundus at each wavelength; Based on the second scattering coefficient map of the target fundus at at least two wavelengths, a size distribution map of the tissue components of the target fundus is generated; For each wavelength, based on the second absorption coefficient map of the target fundus at that wavelength, a second mapping relationship between the absorption coefficient of each location of the target fundus at that wavelength and the concentration of the tissue component is determined; Based on the second mapping relationship between the absorption coefficients of each location at at least two wavelengths and the concentration of the tissue component, a first linear equation is established; for each location of the target fundus, the second mapping relationship between the absorption coefficient of the location at each wavelength and the concentration of the tissue component is: the absorption coefficient of the location at each wavelength is the sum of the products of the concentration of the tissue component at the location and the extinction coefficient of the tissue component; Solve the first linear equation to obtain the concentration of tissue components at each location; Based on the concentration of tissue components at each location, a concentration distribution map of the tissue components in the target fundus is generated.

2. The method according to claim 1, characterized in that, The step of generating a second optical characteristic map of the target fundus in response to the irradiated light field based on the first reflected light field image, the second reflected light field image, and the first optical characteristic map of the optical phantom in response to the irradiated light field includes: Analyze the first reflected light field image to obtain the first diffuse reflectance map of the optical phantom under the illumination light field; By analyzing the second reflected light field image, a second diffuse reflectance map of the target fundus under the illumination light field is obtained; Based on the first diffuse reflectance map and the first optical characteristic map, a first mapping relationship between the diffuse reflectance and optical characteristic parameters at the specified spatial frequency is determined; Based on the first mapping relationship and the second diffuse reflectance map, a second optical characteristic map of the target fundus in response to the irradiated light field is generated.

3. The method according to claim 2, characterized in that, The step of determining the first mapping relationship between the diffuse reflectance at the specified spatial frequency and the optical characteristic parameters based on the first diffuse reflectance map and the first optical characteristic map includes: Based on the first diffuse reflectance map, the diffuse reflectance at each location of the optical phantom is determined; Based on the first optical characteristic map, the optical characteristic parameters of each position of the optical phantom are determined; Based on the diffuse reflectance and optical characteristic parameters at various locations of the optical phantom, a first mapping relationship between the diffuse reflectance and optical characteristic parameters at the specified spatial frequency is determined.

4. A fundus measurement device, characterized in that, include: The light field illumination module is used to illuminate the optical phantom and the target fundus with illumination light fields of a specified spatial frequency, respectively; the number of specified spatial frequencies is at least two, and the wavelength of the illumination light field of each specified spatial frequency is different; The detection module is used to acquire a first reflected light field image formed by the reflection of an illumination light field of a specified spatial frequency by an optical phantom, and a second reflected light field image formed by the reflection of the illumination light field by the fundus of the target eye. The processing module is configured to generate a second optical characteristic map of the target fundus in relation to the irradiated light field based on the first reflected light field image, the second reflected light field image, and a first optical characteristic map of the optical phantom in relation to the irradiated light field, and to generate a tissue composition map of the target fundus based on the second optical characteristic map; The second optical characteristic map includes: a second absorption coefficient map and a second scattering coefficient map of the target fundus at each wavelength; The processing module generates the tissue composition map of the target fundus in the following manner: Based on the second scattering coefficient map of the target fundus at at least two wavelengths, a size distribution map of the tissue components of the target fundus is generated; For each wavelength, based on the second absorption coefficient map of the target fundus at that wavelength, a second mapping relationship between the absorption coefficient of each location of the target fundus at that wavelength and the concentration of the tissue component is determined; Based on the second mapping relationship between the absorption coefficients of each location at at least two wavelengths and the concentration of the tissue component, a first linear equation is established; for each location of the target fundus, the second mapping relationship between the absorption coefficient of the location at each wavelength and the concentration of the tissue component is: the absorption coefficient of the location at each wavelength is the sum of the products of the concentration of the tissue component at the location and the extinction coefficient of the tissue component; Solve the first linear equation to obtain the concentration of tissue components at each location; Based on the concentration of tissue components at each location, a concentration distribution map of the tissue components in the target fundus is generated.

5. A computer device, characterized in that, The computer device includes a processor and a memory, the processor storing at least one computer program, the at least one computer program being loaded and executed by the processor to implement the fundus measurement method as described in any one of claims 1 to 3.

6. A computer-readable storage medium, characterized in that, When the instructions in the storage medium are executed by the processor of a computer device, the computer device is able to perform the fundus measurement method as described in any one of claims 1 to 3.

7. A computer program product, characterized in that, The computer program product includes a non-transitory computer-readable storage medium storing a computer program operable to cause a computer to perform some or all of the steps in the fundus measurement method as described in any one of claims 1 to 3.

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