Detection device and health detection equipment

Abstract

A detection device and health detection equipment are used to achieve truly non-invasive detection. The detection device includes a display unit and a detection unit. The display unit emits an irradiation light and makes it irradiate the object to be tested on a first optical path, shoots the object to be tested under the irradiation light, and sends the information obtained by the shooting to the display for display. The information is used to instruct the object to be tested to move to the position to be tested. The detection unit emits a detection light and makes it irradiate the object to be tested on the first optical path, and detects the object to be tested based on the scattered light generated after the detection light is excited by the object to be tested. By combining the detection unit and the display unit, it is helpful to detect the same position of the object to be tested every time, and the detection of the same position has the characteristics of consistent detection conditions and high repeatability of noise interference, which can accurately reflect the real changes in the internal components of the object to be tested, and help to improve the reference value of the detection results.

Description

Technical Field

[0001] The present application relates to the field of optical technology, and in particular to a detection device and health detection equipment. Background Art

[0002] Non-invasive testing technology has been researched and developed for over 20 years, but true non-invasive testing has yet to emerge. Currently available non-invasive testing methods mostly minimize damage to the object being tested, but cannot measure the internal components of the object being tested without damaging it. For example, in a currently commonly used non-invasive blood glucose testing method, a weak electric current is first used to stimulate the human skin, causing the glucose in the blood to penetrate the skin, and then the glucose solution on the skin surface is collected for testing. Although this method does not require intrusion into the human skin, it still requires a certain amount of stimulation to the human skin, which will actually damage the normal function of the human skin. Therefore, this method is not considered a truly non-invasive test.

[0003] Based on this, there is an urgent need for a detection device to achieve truly non-invasive detection. Summary of the Invention

[0004] The present application provides a detection device and a health detection device, which are used to irradiate the detection light into the interior of the object to be tested, and detect the components inside the object to be tested based on the scattered light scattered back by the object to be tested, so that the internal components of the object to be tested can be detected without damaging the object to be tested. Furthermore, the detection device also includes a display unit, which can display information about the object to be tested under the irradiation light, and the information can show the internal texture of the object to be tested. In this way, each time the components of the object to be tested are detected, the detection light emitted by the detection unit can be aligned with the same position with reference to the internal texture of the object to be tested, and then the detection unit can be used to detect the position. This method helps to detect the same position of the object to be tested every time, and the detection of the same position has the characteristics of consistent detection conditions and high repeatability of noise interference, which can accurately reflect the real changes in the internal components of the object to be tested, and helps to improve the reference value of the detection results.

[0005] In a first aspect, the present application provides a detection device, which includes a display unit and a detection unit. The display unit includes an illumination light emitter, an illumination light transmission device, a camera device and a display, and the camera device is connected to the display. The illumination light emitter can emit illumination light, and after the illumination light reaches the illumination light transmission device, it is transmitted via the illumination light transmission device so that it illuminates the object to be measured on the first optical path, and then the object to be measured under the illumination light is photographed via the camera device, and the information obtained by the photographing is sent to the display for display, and the information is used to instruct the object to be measured to be moved to the position to be tested. Correspondingly, the detection unit can emit detection light, and transmit the detection light so that it also illuminates the object to be measured on the first optical path, and then detect the object to be measured based on the scattered light generated after the detection light is excited by the object to be measured.

[0006] In the above-mentioned design, by irradiating the detection light into the object to be tested, the internal components of the object to be tested can be detected based on the scattered light scattered back from the object to be tested, which helps to detect the internal components of the object to be tested without damaging the object to be tested. Moreover, each time the components of the object to be tested are detected, the detection light can be first aligned with the same position of the object to be tested, referring to the information of the object to be tested under the irradiation light captured by the display unit, and then the detection unit is used for detection. This method helps to detect the same position of the object to be tested each time. The detection of the same position has the characteristics of consistent detection conditions and high repeatability of noise interference. It can accurately reflect the actual changes in the internal components of the object to be tested, which helps to improve the reference value of the detection results.

[0007] In one possible design, the object to be measured is the blood glucose level of the nail fold. The information captured by the camera can be used to indicate the location of capillaries in the nail fold and the location of the light spot formed by the detection light hitting the nail fold. Because different capillaries generally have different shapes, the user can accurately align the light spot formed by the detection light hitting the nail fold with the target location by observing the location of each capillary, thus facilitating blood glucose measurement at the target location.

[0008] In one possible design, the display unit further includes a first prism, wherein the optical axis of the first prism is disposed on a transmission light path in which the illumination light emitter emits illumination light to the illumination light transmission device, and the first prism is configured to focus illumination light having a wavelength not less than a first wavelength and not greater than a second wavelength emitted by the illumination light emitter onto the illumination light transmission device, wherein the first wavelength is less than the second wavelength. The illumination light having a wavelength not less than the first wavelength and not greater than the second wavelength is illumination light capable of displaying the internal texture of the object to be measured. In this manner, focusing the illumination light within this wavelength range through the first prism facilitates illuminating the object to be measured with illumination light suitable for the object to be measured, so that the internal texture of the object to be measured can be displayed on the display.

[0009] In one possible design, when the object to be measured is blood sugar in the nail fold, the first wavelength is 400nm and the second wavelength is 700nm. With this design, the irradiation light in the wavelength range of 400nm to 700nm is visible light and can penetrate into the dermis of the skin in the nail fold. Since capillaries are located in the dermis, the irradiation light in this wavelength range can successfully visualize the capillaries in the nail fold.

[0010] In one possible design, the wavelength of the detection light is 785 nm. By setting the wavelength of the detection light close to the wavelength of the illumination light, and arranging both the detection light and the illumination light to illuminate the nail wrinkle along the first optical path, the light spot formed by the detection light irradiating the nail wrinkle can also be displayed in the information captured by the camera device.

[0011] In one possible design, the illumination light transmission device includes a first reflector and a switching mirror. The first reflector is directly opposite the light outlet of the illumination light emitter. The first reflector is used to reflect the illumination light emitted by the illumination light emitter and transmit it to the switching mirror along a second optical path perpendicular to the first optical path. Correspondingly, the switching mirror is located at the intersection of the first optical path and the second optical path. The switching mirror is used to reflect the illumination light emitted by the switching mirror back to the first optical path. In this way, by setting the optical path where the reflector and the switching mirror are located, the illumination light can be accurately reflected onto the first optical path.

[0012] In one possible design, the switching mirror can move along the second optical path. When the switching mirror moves to a position other than the intersection of the first and second optical paths, the switching mirror can reflect the incident light onto the switching mirror onto a third optical path. The third optical path is parallel to the first optical path and does not pass through the object to be measured. With this design, the detection device can have two operating modes: the display unit and the detection unit are operating simultaneously, or the display unit is not operating while the detection unit is operating. This allows users to configure the detection device's operating mode according to actual needs.

[0013] In one possible design, the object to be measured is the blood sugar of a nail fold, and the camera device includes an objective lens, wherein the optical axis of the objective lens is set on a first optical path, and the objective lens has at least a first focal length and a second focal length, and the multiple of the first focal length is smaller than the multiple of the second focal length. The camera device can use the objective lens to photograph a local area of ​​the nail fold when the focal length of the objective lens is the first focal length, thereby obtaining current local information corresponding to the nail fold. The current local information is used to instruct the movement of the nail fold so that the area of ​​the nail fold irradiated by the irradiation light is the same as the local area corresponding to the position of the nail fold to be tested. Furthermore, the camera device can also use the objective lens to photograph a local area of ​​the nail fold when the focal length of the objective lens is the second focal length, thereby obtaining current capillary information corresponding to the nail fold. The current capillary information is used to instruct the movement of the nail fold so that the position of the light spot of the detection light irradiated on the nail fold in the current capillary information is the same as the position of the light spot in the capillary information corresponding to the position of the nail fold to be tested. By using the method of coarse adjustment followed by fine adjustment, a smaller local nail fold area can be locked first, and then the smaller local nail fold area can be fine-tuned, without having to use a larger focal length to fine-tune the entire nail fold, which helps to reduce the user's workload in comparing information.

[0014] In one possible design, the detection unit further includes a detection light emitter, a detection light transmission device, an edge filter, a spectrometer, and a spectrum detection device. The detection light emitter can emit detection light, which, after reaching the detection light transmission device, can be transmitted through the detection light transmission device so that it also illuminates the object to be detected along the first optical path. The edge filter then collects Raman scattered light and Rayleigh scattered light generated by the object to be detected after being excited by the detection light, filters out the Rayleigh scattered light, and leaves only the Raman scattered light. The Raman scattered light is then transmitted to the spectrometer, which then performs spectroscopic processing on the Raman scattered light to form a Raman spectrum, which is then transmitted to the spectrum detection device. Finally, the spectrum detection device detects the object to be detected based on the Raman spectrum. In this way, by utilizing the Raman spectrum detection method to detect the object to be detected, it is possible to detect the internal components of the object to be detected without damaging the object to be detected.

[0015] In one possible design, the detection unit further includes a light intensity adjustment device, disposed on the transmission path of the detection light emitted by the detection light emitter to the detection light transmission device. The light intensity adjustment device is configured to adjust the detection light emitted by the detection light emitter to the intensity required for detecting the object to be detected. In this way, the detection light adjusted by the light intensity adjustment device is more suitable for detecting the object to be detected. The adjusted detection light intensity is sufficient to detect the internal components of the object to be detected while protecting the object from damage.

[0016] In one possible design, when the object to be tested is the blood sugar of the nail wrinkle, the light intensity adjustment device is used to adjust the detection light emitted by the detection light emitter to a detection light with a power not exceeding 20mW to avoid excessive intensity of the detection light and burns to human skin.

[0017] In one possible design, the light intensity adjustment device includes a light shielding plate, which is arranged at the light outlet of the detection light emitter, and a light-transmitting hole is left between the light shielding plate and the light outlet of the detection light emitter. When the intensity of the detection light emitted by the detection light emitter is greater than the intensity required for detecting the object to be detected, the light shielding plate is moved to reduce the light-transmitting hole. By reducing the area of ​​the light-transmitting hole, less detection light can be irradiated onto the detection light transmission device, which helps to reduce the intensity of the detection light irradiated onto the object to be detected. When the intensity of the laser emitted by the detection light emitter is less than the intensity required for detecting the object to be detected, the light shielding plate is moved to increase the light-transmitting hole. By increasing the area of ​​the light-transmitting hole, more detection light can be irradiated onto the detection light transmission device, which helps to increase the intensity of the detection light irradiated onto the object to be detected.

[0018] In one possible design, the light intensity adjustment device includes a filter, which is arranged coaxially with the detection light emitter. When the intensity of the detection light emitted by the detection light emitter exceeds the intensity required to detect the object, the filter's attenuation ratio is increased, filtering out more light and reducing the intensity of the detection light incident on the object. When the intensity of the laser light emitted by the detection light emitter is less than the intensity required to detect the object, the filter's attenuation ratio is reduced, filtering out less light and increasing the intensity of the detection light incident on the object.

[0019] In one possible design, the detection light transmission device includes a second reflector and a third reflector arranged side by side, the optical axes of the second reflector and the third reflector are parallel, the central axis of the second reflector is arranged directly below the light outlet of the detection light emitter, and the central axis of the third reflector is arranged on the first optical path. The second reflector can reflect the detection light emitted by the detection light emitter to the third reflector, and the third reflector can reflect the detection light reflected by the second reflector to the switching mirror arranged on the first optical path, and the switching mirror can transmit the detection light transmitted to the switching mirror. In this way, by arranging the second reflector and the third reflector side by side, the detection light can be accurately reflected onto the first optical path by utilizing the principle of light reflection.

[0020] In one possible design, the detection unit further includes a spectroscope, the central axis of which is located on the first optical path, and the optical axis of light transmitted from the spectroscope to the edge filter is perpendicular to the first optical path. The spectroscope can transmit detection light transmitted from the detection light transmission device to the spectroscope, and separate the Raman scattered light and Rayleigh scattered light of each wavelength generated by the object to be detected after being excited by the detection light into different paths, and transmit the light to the edge filter. In this way, the edge filter can filter out the Rayleigh scattered light along the path corresponding to the wavelength of the Rayleigh scattered light, thereby retaining only the Raman scattered light.

[0021] In one possible design, the object to be measured is blood glucose, which is detected by nail wrinkles. In this case, the edge filter can be a 785nm edge filter with a cutoff point of 5nm. This design allows the edge filter to filter scattered light with wavelengths between 780nm and 790nm. As a result, the scattered light filtered by the edge filter essentially excludes scattered light with the same wavelength as the detection light (785nm), thereby facilitating the subsequent determination of the accuracy of the Raman spectrum.

[0022] In one possible design, the detection unit also includes a signal confocal device, which is arranged on the transmission light path of the edge filter and the spectrometer. The signal confocal device may include a first lens, a confocal hole, and a second lens, and the first lens, the confocal hole, and the second lens are arranged on the same optical axis. The weak Raman scattered light transmitted from the edge filter is first collected by the first lens and focused on the confocal hole, and then the focused Raman scattered light is projected onto the second lens through the confocal hole, and then the Raman scattered light projected by the confocal hole is scattered onto the spectrometer through the second lens. Through this design, the Raman scattered light before the confocal processing is relatively dispersed. By performing confocal processing on the Raman scattered light, the Raman scattered light can be converted into more concentrated Raman scattered light.

[0023] In one possible design, the spectrometer includes a grating and a second prism. The grating is coaxial with the signal confocal device, and the second prism is positioned in the transmission path between the grating and the spectrum detection device. With this design, the confocal Raman scattered light is transmitted to the grating via the second lens. The grating then directs the different wavelengths of the Raman scattered light to different locations, forming a Raman spectrum. The second prism then transmits the Raman spectrum to the spectrum detection device.

[0024] In the second aspect, the present application provides a health detection device, comprising a test bench, a base and the detection device described in any one of the first aspects, wherein the test bench is arranged on the base, and the light outlet of the detection device is aligned with the test bench. After the object to be tested is placed on the test bench, the detection device can emit irradiation light through the light outlet to illuminate the object to be tested, and photograph the object to be tested under the irradiation light, and then move the object to be tested to the test position of the test bench according to the information obtained from the photographing, and detect the object to be tested moved to the test position. By setting the detection device in the health detection device, the user can test blood sugar at any time even at home, which makes it convenient for diabetic patients or pre-diabetic patients to monitor and manage their blood sugar health at any time.

[0025] In one possible design, the object to be measured is the blood sugar level of the nail wrinkle of a finger to be measured. In this case, a finger clamp can also be provided on the test table to fix the finger to be measured on the test table to prevent the finger to be measured from shaking significantly during the test, which may lead to inaccurate test results.

[0026] In one possible design, a fingerprint recognition device can also be provided on the test bench, and the fingerprint recognition device is used to collect the user's fingerprint information. The user's fingerprint information is used to determine the local information or capillary information of the user's corresponding position to be tested, and the local information or capillary information of the user's corresponding position to be tested is used to determine to move the finger to be measured to the position to be tested. Through this design, the same detection device can also be used to measure blood sugar for different users. When detecting the blood sugar of a certain user, the fingerprint recognition device is used to distinguish the identity of the user, so that the detection device can display the information corresponding to the currently measured user on the display, thereby helping to ensure that the detected blood sugar is the blood sugar of the currently measured user.

[0027] The above aspects and other aspects of the present application will be described in detail in the following embodiments. BRIEF DESCRIPTION OF THE DRAWINGS

[0028] Figure 1 A schematic diagram showing the location of a nail fold is shown as an example;

[0029] Figure 2A An exemplary diagram of the skin layer structure of another part is shown;

[0030] Figure 2B A schematic diagram showing the hierarchical structure of the skin at the nail fold is shown as an example;

[0031] Figure 3 A schematic diagram of the structure of a health detection device is shown as an example;

[0032] Figure 4AA schematic structural diagram of a finger clamp is shown as an example;

[0033] Figure 4B A schematic structural diagram of another finger clamp is shown as an example;

[0034] Figure 5 A schematic structural diagram of a detection device provided in an embodiment of the present application is exemplified;

[0035] Figure 6 A schematic diagram showing an example of photographing a nail fold using objective lenses of different magnifications;

[0036] Figure 7 A Raman spectrum is shown as an example;

[0037] Figure 8 An optical path processing method for a detection device provided in an embodiment of the present application is exemplified;

[0038] Figure 9 The following illustrates an exemplary method of displaying an image by a fingerprint recognition device. DETAILED DESCRIPTION

[0039] The detection devices in the embodiments of the present application can be used to measure biological components, such as human blood lipids, cholesterol, and blood sugar, and can also be used to measure non-biological components, such as the content of metal elements and the hardness of non-metallic elements. For example, the detection devices proposed in the embodiments of the present application can be some blood sugar detection equipment or blood lipid detection equipment used in medicine.

[0040] The following is an introduction to some of the terms involved in the embodiments of this application.

[0041] (1) Raman spectroscopy

[0042] When excitation light strikes a substance, light scattering occurs. The scattered light includes not only an elastic component with the same wavelength as the excitation light (called Rayleigh scattered light), but also an inelastic component with a longer or shorter wavelength than the excitation light (called Raman scattered light). These inelastic components are generated by the interaction between molecular vibrations in the substance and the excitation light, or by the interaction between the excitation of elements such as optical phonons in the substance and the excitation light. The spectrum formed by the combination of Rayleigh scattered light and Raman scattered light is called a Raman spectrum. In Raman spectroscopy, the difference between the frequencies of Raman scattered light and Rayleigh scattered light is called the Raman shift. The Raman shift is related to the vibrational frequency and energy level of the molecules in the substance and can be used to characterize the molecular properties of the substance.

[0043] (2) Confocal

[0044] Confocal in the embodiment of the present application means that after the excitation light is irradiated on the object, it appears as a focused point (called a light spot), rather than a scattered focused area. In the case of confocal, the extracted Raman spectrum is the Raman spectrum of the light spot, and the Raman spectrum can better characterize the molecular properties of the substance. In the case of non-confocal, the extracted Raman spectrum may be the Raman spectrum of any point in the focal area. The Raman spectrum has a large randomness and may not be able to better characterize the molecular properties of the substance. Among them, the confocal method of extracting Raman spectra can have a higher resolution than the non-confocal method of extracting Raman spectra. For example, the non-confocal method of extracting Raman spectra can only detect the surface of the object at the millimeter or micrometer level, while the confocal method of extracting Raman spectra can detect the surface of the object at the micron level.

[0045] (3) Nail fold area

[0046] The nail fold in the embodiment of the present application refers to the skin fold covering the root of the nail. Figure 1 A schematic diagram of the position of the nail fold is shown as an example. Figure 1 As shown, the base of the nail also has an oval hollow area, called the lunula, and the nail fold is adjacent to the lunula through the nail epithelium.

[0047] In the embodiment of the present application, the skin layer structure of the nail fold is slightly different from that of other parts of the skin. Figure 2A An exemplary skin layer structure diagram of another part is shown, such as Figure 2A As shown, the skin of other parts of the body includes the epidermis, stratum corneum, transparent layer, granular layer, spinous layer, basal layer and dermis from top to bottom, among which capillaries and veins are located in the dermis. Figure 2B The following is a schematic diagram showing the skin layer structure of a nail fold. Figure 2B As shown, the skin of the nail fold consists of the epidermis, stratum lucidum, stratum granulosum, stratum spinosum, stratum basale, and dermis, from top to bottom. Compared to skin in other areas, the nail fold lacks a stratum corneum, so the capillaries there are closer to the epidermis. Other areas of skin similar to the nail fold include the earlobe and nasal cavity, which also lack a stratum corneum.

[0048] (4) Non-invasive testing

[0049] The non-invasive testing described in the embodiments of this application is a non-invasive testing method that can indirectly guide or sense physiological and biochemical parameters related to the component to be tested, typically by placing a measuring instrument in contact with or without contact with the skin. Because non-invasive testing does not cause trauma to the user's skin, it is highly popular among users.

[0050] (5) Wavelength of light

[0051] In the embodiment of the present application, if the wavelength of light is longer, the depth to which the light penetrates into the object is deeper, and if the wavelength of light is shorter, the depth to which the light penetrates into the object is shallower.

[0052] The scheme in this application is described in detail below with reference to the drawings in the embodiments of this application. It should be noted that, in the embodiments of this application, "at least one" refers to one or more, and "more" refers to two or more. "And / or" describes the association relationship of associated objects, indicating that three relationships may exist. For example, A and / or B can represent: the existence of A alone, the existence of A and B at the same time, and the existence of B alone, where A and B can be singular or plural. The character " / " generally indicates that the previous and next associated objects are in an "or" relationship. "At least one of the following items" or similar expressions refers to any combination of these items, including any combination of single items or plural items. For example, at least one of a, b, or c can represent: a, b, c, ab, ac, bc, or abc, where a, b, c can be single or multiple.

[0053] Furthermore, in the description of the embodiments of this application, the terms "first," "second," and "third" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly specifying the number of the technical features indicated, for example: "first reflector," "second reflector," "third reflector," etc. Therefore, features specified as "first," "second," and "third" may explicitly or implicitly include one or more of such features.

[0054] For ease of understanding, the following embodiments of the present application describe the structural composition of the detection device by taking the measurement of blood sugar in the nail fold of a human body as an example.

[0055] The detection device in the embodiment of the present application can be set in a health detection device. Figure 3 A schematic diagram of the structure of a health detection device is shown as an example. Figure 3 As shown, the health monitoring device may include a base 310, a test platform 320, and a detection device 330. The light outlet of the detection device 330 is located directly above the test platform 320, and the lower surface of the test platform 320 is placed on the base 310. When measuring blood sugar in the nail fold, the user can place their finger flat on the test platform 320 and align the nail fold with the light outlet of the detection device 330. In this way, the detection device 330 can emit detection light from the light outlet to illuminate the nail fold, collect scattered light from the nail fold, and measure the blood sugar in the nail fold based on the scattered light.

[0056] In an optional embodiment, in order to avoid significant movement of the finger during the measurement process, which may lead to inaccurate measurement results, a finger fixture may be provided on the test bench 320. There are many possible structures for the finger fixture, and two possible finger fixtures are described below as examples:

[0057] Figure 4A A schematic structural diagram of a finger clamp 321 is shown as an example. Figure 4A As shown, the finger clamp 321 may include a left side panel, a right side panel and a rear side panel, wherein the left side panel and the right side panel are arranged in parallel, the left side edge of the rear side panel is fixedly connected to the rear side surface of the left side panel, and the right side edge of the rear side panel is fixedly connected to the rear side surface of the right side panel, and the lower bottom surfaces of the left side panel, the right side panel and the rear side panel are all fixed on the test bench 320. Among them, the spacing between the left side panel and the right side panel may be slightly larger than the width of the middle phalanx of the finger. In this way, when the user places the finger between the left side panel and the right side panel and presses the fingertip against the rear side panel, the left side panel and the right side panel can just clamp the finger. Moreover, in this case, the positions of the left side panel, the right side panel and the rear side panel also need to meet the following requirements: when the left side panel and the right side panel clamp the finger, the light outlet of the detection device 330 can just illuminate the nail wrinkle of the finger.

[0058] Figure 4B A schematic structural diagram of another finger clamp 321 is shown as an example. Figure 4B As shown, the finger fixture 321 may include a left panel, a right panel, a rear panel, and an upper panel. These four panels and the test bench 320 form a storage space that is precisely sized to accommodate the user's finger. Furthermore, a hole may be formed on the upper side of the finger fixture 321. The hole may be positioned so that the user's nail fold aligns with the user's finger after inserting the finger into the storage space. The hole may be square, round, or irregular in shape, and the size of the hole may be customized by the user based on actual needs. For example, if the hole is round, it may be no larger than 0.05 mm. With this structure, each time the user inserts their finger into the storage space formed by the finger fixture and the test bench, the same nail fold area can be aligned with the through hole in the finger fixture, thereby facilitating the detection device to consistently test blood glucose levels in the same nail fold area.

[0059] It should be noted that Figure 4A and Figure 4B The structure of the finger fixture is introduced by taking the nail fold measurement of the right index finger as an example. In actual operation, the user can select which finger's nail fold to measure, for example, the ring finger can also be measured.

[0060] In an optional embodiment, after the finger fixture 321 fixes the finger, if the position illuminated by the light outlet in this measurement is different from the position to be measured, the user can also move the test table 320 to indirectly move the finger. Figure 3 As shown, the test bench 320 can move along the X direction, Y direction, or Z direction shown in the figure. There are many ways to move the test bench 320. For example, the user can use another hand to manually push the test bench 320 to move, or a micrometer driver can be pre-installed on the test bench 320. The driving accuracy of the micrometer driver can be no more than 1 micron. In this way, by achieving micron-level position fine-tuning, not only can the problem of repeated adjustments caused by excessive adjustment amplitude be avoided, but the error between the final position and the desired measurement position can also be no more than 1 micron, thereby improving the accuracy of blood glucose testing at the desired measurement position. Among them, the micrometer driver can be configured as a three-dimensional micrometer driver, and the user operates the three-dimensional micrometer driver to control the movement of the test bench 320 in the X direction, Y direction, or Z direction. Alternatively, the micrometer driver can also be configured as a two-dimensional micrometer driver, and the user operates the two-dimensional micrometer driver to control the movement of the test bench 320 in the X direction or Y direction, and the Z direction can be adjusted by the user controlling the manual circular adjuster of the test bench.

[0061] In the embodiment of the present application, since the finger's position may be adjusted during the blood sugar test, a certain distance can be reserved between the upper surface of the finger and the light outlet when setting up the health monitoring device. This way, the user's finger does not actually touch the light outlet during the blood sugar measurement. Therefore, even if the user moves the finger during the measurement, the finger will not rub against the light outlet. This not only reduces the wear and tear on the light outlet, but also prevents the user from feeling discomfort when moving the finger, thus improving the user experience.

[0062] In the above embodiment, while the finger gripper facilitates blood glucose monitoring within the same nail wrinkle area, the same nail wrinkle area microscopically encompasses a relatively large area (e.g., a circular surface with a radius of 0.5 cm), and the detection device only measures a single micrometer-scale point at a time. In this case, even the slightest movement of the finger could cause the detection device to measure a different location from previous measurements. Because blood glucose levels at different locations experience varying testing conditions and noise interference, the resulting blood glucose variation information derived from these measurements will contain significant noise and may not reflect the user's true blood glucose levels.

[0063] In view of this, an embodiment of the present application provides a detection device comprising a detection unit and a display unit, wherein the display unit is capable of displaying capillary information in the nail fold. Thus, each time blood glucose is measured, the light spot illuminated by the detection unit can be aligned with the same location (e.g., a location on or around a capillary of a particular shape or length) with reference to the capillary information in the nail fold, and then the detection unit is used to perform a blood glucose test. This method facilitates the detection of blood glucose at the same location each time. Because the detection conditions are consistent and the noise interference repeatability is high, the blood glucose at the same location can accurately reflect the actual changes in blood glucose, thereby improving the reference value of the test results.

[0064] Figure 5 A schematic diagram of the structure of a detection device provided in an embodiment of the present application is shown as an example. Figure 5 As shown, the detection device may include a display unit and a detection unit. The display unit may include an illumination light emitter, an illumination light transmission device, a camera device, and a display, wherein the camera device is connected to the display. The illumination light emitter may emit illumination light, which, after being transmitted by the illumination light transmission device, may illuminate the nail fold area along a first optical path (L1). The camera device may capture the nail fold area illuminated by the illumination light and transmit the captured information to the display for display. Correspondingly, the detection unit may emit detection light and transmit the detection light so that the detection light also illuminates the nail fold area along the first optical path (L1). The detection unit may also detect blood glucose in the nail fold area based on scattered light generated by the detection light after being excited by the skin in the nail fold area.

[0065] In this embodiment of the present application, the information obtained by the camera device from capturing the nail fold can be an image of the nail fold. Because the skin in the nail fold is relatively thin (lacking a stratum corneum), the image captured by the camera device after irradiating the nail fold with the illumination light can show the capillaries in the nail fold. Furthermore, after irradiating the nail fold with the detection light, the image captured by the camera device can also show the light spot formed by the detection light irradiating the nail fold. In this case, if a user wishes to test blood glucose at a certain location, they can view the current image displayed on the display. If the location of the light spot where the detection light irradiates the nail fold in the current image does not match the desired measurement location, they can move the test platform 320 to move their finger until the location of the light spot where the detection light irradiates the nail fold in the current image displayed on the display matches the desired measurement location. The detection unit can then measure blood glucose at that location. For example, since different capillaries generally have different shapes, the desired measurement location can be identified by a capillary with a unique shape.

[0066] In an optional embodiment, the display may also simultaneously display a standard image and a current image, wherein the standard image may be the image of the measured position displayed on the display during the user's last blood glucose measurement, or it may be the image of the desired measurement position set by the user for each blood glucose measurement. In this case, the user does not need to remember the image of the desired measurement position, but can directly compare the position of the light spot where the detection light illuminates the nail fold in the current image displayed on the display with the position of the light spot in the standard image. If the two positions are inconsistent, the test table 320 is moved until the two positions are consistent, and then the detection unit is used to measure blood glucose again.

[0067] The structures of the display unit and the detection unit are respectively introduced in detail below.

[0068] In an optional embodiment, continue to refer to Figure 5 As shown, the display unit includes Figure 5 In addition to the illustrated illumination light emitter, illumination light transmission device, camera device, and display, a first prism may also be included. The optical axis of the first prism may be disposed on the transmission light path of the illumination light emitted by the illumination light emitter to the illumination light transmission device. Thus, after the illumination light of various wavelengths emitted by the illumination light emitter strikes the first prism, the illumination light within the wavelength range of 400nm to 700nm may be focused by the first prism onto the illumination light transmission device. In this implementation, the illumination light within the wavelength range of 400nm to 700nm is visible light, and visible light within this wavelength range can penetrate into the dermis layer of the skin in the nail fold area. Since capillaries are located within the dermis, the illumination light within this wavelength range can visualize the capillaries in the nail fold area.

[0069] In an optional embodiment, continue to refer to Figure 5 As shown, the illumination light transmission device may include a first reflector and a switching mirror. The first reflector may be disposed directly above the light outlet of the illumination light emitter. The illumination light emitted by the illumination light emitter, after being reflected by the first reflector, may be emitted to the switching mirror along a second optical path (L2) perpendicular to the first optical path L1. The switching mirror may be movable along the direction of the second optical path L2. In this case:

[0070] When the switching mirror moves to the intersection of the first light path L1 and the second light path L2 (such as Figure 5 The switching mirror can reflect the irradiation light irradiated on the switching mirror to the first light path L1, so that the irradiation light can be irradiated on the nail fold; or, when the switching mirror is moved to a position other than the intersection of the first light path L1 and the second light path L2 (for example, Figure 5In the position B shown in the figure, the switching mirror can reflect the illumination light that hits the switching mirror to the third optical path (L3). The third optical path L3 is parallel to the first optical path L1 and does not pass through the test bench. Therefore, the illumination light cannot be irradiated on the nail fold.

[0071] In the embodiment of the present application, the switching mirror can reflect the illumination light that impinges on the switching mirror and can transmit the detection light that impinges on the switching mirror. In this way, the detection device can have two operating modes: when the switching mirror moves to position A, the display unit and the detection unit work simultaneously. When the switching mirror moves to position B, the display unit does not work, and the detection unit works. Using this embodiment, the user can set the operating mode of the detection device according to actual needs, for example:

[0072] In one scenario, a user wants to measure their blood sugar levels before and after a meal. This requires measuring blood sugar at the same location both before and after a meal to ensure the most accurate blood sugar change. In this case, the switching mirror can be moved to position A, enabling the display unit and detection unit to operate simultaneously. When measuring blood sugar before a meal, the display is controlled to store the capillary image at the measured location (including the light spot where the detection light illuminates the nail fold and the capillaries). When measuring blood sugar after a meal, the capillary image at the measured location before the meal and the capillary image at the current location are observed on the display. If the two images differ, the test platform 320 is moved until the capillary image at the moved location matches the location of the light spot in the capillary image at the measured location before the meal. The blood sugar level after the meal is then measured.

[0073] In another scenario, if a user wants to conduct a comparative experiment on blood sugar levels at different locations on the nail fold, they can randomly measure blood sugar at a specific location on the nail fold each time, without having to focus on the same location. In this case, the switching mirror can be moved to position B, enabling the detection unit to operate while the display unit to disable it. This way, only the detection light emitted by the detection unit on the first optical path illuminates the nail fold, while no illumination light from the display unit illuminates the nail fold. This reduces the amount of interference with scattered light emitted by the skin in the nail fold, helping to improve the accuracy of blood sugar testing.

[0074] In the embodiment of the present application, the camera device may include an image sensor ( Figure 5 (Not shown in the figure), the capillary image captured by the camera can be first sent to the image sensor, which then filters out pixels not related to the capillaries. The filtered capillary image is then sent to the display for display. This approach not only reduces the complexity of displaying the capillary image on the display and reduces the memory occupied by the capillary image, but also allows the user to view the capillary image without being distracted by other pixels.

[0075] In an optional embodiment, continue to refer to Figure 5 As shown, the imaging device may further include an objective lens, the optical axis of which is disposed on the first optical path L1 and at a predetermined distance from the nail fold. The objective lens can focus the detection light emitted by the objective lens. The distance between the objective lens and the nail fold can be set based on the depth of the skin at which the detection light penetrates the nail fold. For example, if the detection light does not penetrate the dermis of the skin at the nail fold, the distance can be reduced. If the detection light penetrates the dermis of the skin at the nail fold but too deeply, the distance can be increased to prevent the detection light from damaging the human skin. Furthermore, the objective lens can magnify the nail fold according to the set focal length, so that the imaging device captures a magnified image of the capillaries.

[0076] In an embodiment of the present application, the objective lens can have at least a first focal length and a second focal length, and the multiple of the first focal length is smaller than the multiple of the second focal length. For example, the first focal length is 10 times, and the corresponding aperture is 0.24nm, and the second focal length is 20 times, and the corresponding aperture is 0.2nm. Figure 6 A schematic diagram of using a pair of objective lenses with different magnifications to photograph the nail fold is shown as an example. When measuring blood sugar, the focal length of the objective lens can be adjusted to a first focal length so that the camera device can first use a small magnification to photograph the nail fold (e.g. Figure 6 Image a in the figure), get the current local image of the nail wrinkle, such as Figure 6 As shown in image b in FIG. In this case, the display can also display the current local image and the standard local image simultaneously. If the two images are inconsistent, the nail fold area can be moved by moving the test platform 320 to roughly adjust the position of the irradiation light on the nail fold area. When the current local image displayed on the display is consistent with the standard local image, the focal length of the objective lens can be adjusted to a second focal length so that the camera device can use a large magnification to capture the local nail fold area, thereby obtaining the current capillary image of the local nail fold area, as shown in FIG. Figure 6 In this case, the display can also simultaneously display the current capillary image and the standard capillary image. If the positions of the light spots where the detection light illuminates the nail fold are inconsistent in the two images, the test platform 110 can be continuously moved to cause the nail fold to move, thereby fine-tuning the position of the light spots where the detection light illuminates the nail fold until the position of the light spots on the current capillary image and the standard capillary image are consistent.

[0077] For example, in the above implementation, during coarse adjustment, only the display unit can be activated without the detection unit. During fine adjustment, both the display unit and the detection unit can be activated simultaneously to minimize the power consumption of the detection device and increase the endurance of the detection device. Of course, it is also possible to activate both the display unit and the detection unit simultaneously during coarse and fine adjustment. If this implementation is used, during coarse adjustment, the user will need to compare the position of the light spot of the detection light irradiating the nail fold area on the current local image with the position of the light spot in the standard local image. The specific method to be used can be set by the user according to actual needs and is not limited by this application.

[0078] In the embodiment of the present application, by adopting the implementation method of coarse adjustment first and then fine adjustment, a smaller local nail fold area can be locked first, and then the smaller local nail fold area can be fine-tuned, without having to use a larger focal length to fine-tune the entire nail fold area, thereby helping to reduce the user's workload in comparing images.

[0079] In an optional embodiment, continue to refer to Figure 5 As shown, the detection unit may include a detection light emitter, a detection light transmission device, an edge filter, a spectrometer, and a spectrum detection device. The detection light emitter can emit detection light, which, after being transmitted by the detection light transmission device, can also illuminate the nail wrinkle along the first optical path L1. The nail wrinkle, when excited by the detection light, generates Raman scattered light and Rayleigh scattered light. After the Raman scattered light and Rayleigh scattered light are transmitted to the edge filter, the edge filter removes the Rayleigh scattered light, leaving only the Raman scattered light. The Raman scattered light is then spectroscopically processed by the spectrometer to form a Raman spectrum, which is then transmitted to the spectrum detection device. The spectrum detection device then determines the blood glucose level in the nail wrinkle based on the Raman spectrum.

[0080] In an embodiment of the present application, the detection light emitter can emit detection light of a single wavelength and fixed power. The wavelength and power of the detection light can be determined based on the substance to be measured. If the substance to be measured is blood glucose in the nail fold, the wavelength of the detection light can be selected as near-infrared light that is relatively close to the wavelength of the irradiation light irradiating the nail fold. In this way, since both the detection light and the irradiation light irradiate the nail fold along the first optical path L1, the light spot formed by the detection light irradiating the nail fold can also be displayed in the image captured by the camera device. For example, if the wavelength of the irradiation light used to irradiate the nail fold is 400nm to 700nm, the wavelength of the detection light emitted by the detection light emitter can be set to 785nm, and the power of the detection light emitted by the detection light emitter can be set to 500mW (power unit, milliwatts).

[0081] In an optional embodiment, continue to refer to Figure 5As shown, the detection unit may further include a light intensity adjustment device. The light intensity adjustment device may be disposed on the optical path between the detection light emitted by the detection light emitter and the detection light transmission device. The light intensity adjustment device is configured to reduce the intensity of the detection light emitted by the detection light emitter. For example, if the detection light emitter emits a detection light with a power of 500mW, the detection light may be adjusted to a power of no more than 20mW by the light intensity adjustment device before being irradiated to the nail fold to avoid burning the human skin.

[0082] In one example, continue with Figure 5 As shown, the light intensity adjustment device may include a light shielding plate, which is disposed at the light outlet of the detection light emitter and may be a dense plate-like structure. A light-transmitting hole is provided between the light shielding plate and the light outlet of the detection light emitter. The light shielding plate can be moved along the light outlet to change the size of the light-transmitting hole. When the size of the light-transmitting hole is smaller, the area of ​​the detection light emitted by the detection light emitter blocked by the light shielding plate is larger, and thus, the power of the detection light emitted to the detection light transmission device is also lower. When the size of the light-transmitting hole is larger, the area of ​​the detection light emitted by the detection light emitter blocked by the light shielding plate is smaller, and thus, the power of the detection light emitted to the detection light transmission device is also higher.

[0083] In another example, continue with Figure 5 As shown, the light intensity adjustment device may include an optical filter, which may be arranged coaxially with the detection light emitter. After the detection light emitted by the detection light emitter reaches the optical filter, it may first be dimmed by the filter according to a corresponding dimming ratio. The dimmed detection light is then irradiated onto the nail fold. The optical filter may be pre-set with multiple dimming ratios, which can be determined based on the detection light power required for measuring blood glucose at the nail fold and the detection light power emitted by the detection light emitter. If the dimming effect corresponding to the current dimming ratio is too low, potentially causing burns to the skin, the dimming ratio may be increased to the next level. If the dimming effect corresponding to the current dimming ratio is too high, preventing the detection light from irradiating blood vessels, the dimming ratio may be decreased to the previous level. To improve the filter's dimming sensitivity, the filter may be configured as an 8-level neutral density (ND) filter. The 8-level ND filter has 8 levels of dimming, with each level reducing the power by 400mW.

[0084] In another example, continue to refer to Figure 5 As shown, the light intensity adjustment device can include both a light shield and a filter. This allows for coordinated operation of the other component to adjust light intensity even when one component is not providing adequate light intensity adjustment. Because the light shield provides coordinated light reduction, this implementation allows the filter to have a lower light reduction ratio, reducing filter costs.

[0085] In an optional embodiment, continue to refer to Figure 5 As shown, the detection light transmission device may include a second reflector and a third reflector arranged side by side. The optical axes of the second and third reflectors are parallel. The central axis of the second reflector is located directly below the light outlet of the detection light emitter, and the central axis of the third reflector is located on the first optical path L1. The detection light emitted by the detection light emitter can first be reflected by the second reflector to a fourth optical path (L4) perpendicular to the first optical path L1. It is then transmitted along the fourth optical path L4 to the third reflector. It is then reflected by the third reflector back to the first optical path L1. It is then transmitted through a switching mirror provided on the first optical path L1 to the nail fold. In this embodiment of the present application, when the wavelength of the detection light is 785 nm, the detection light can penetrate the dermis layer of the skin at the nail fold and enter the blood at the nail fold. When excited by the detection light, the blood glucose in the blood generates Raman scattered light and Rayleigh scattered light. The Raman scattered light and Rayleigh scattered light are focused by the objective lens and then transmitted in the opposite direction of the first optical path L1.

[0086] In an optional embodiment, continue to refer to Figure 5 As shown, the detection unit may further include a spectroscope, the central axis of the spectroscope being located on the first optical path L1, and the line on which the central axis of the spectroscope and the central axis of the edge filter lie being perpendicular to the first optical path L1. In an embodiment of the present application, if the wavelength of the detection light used to illuminate the nail wrinkle is 785 nm, then after the detection light of this wavelength is scattered by blood glucose, the corresponding Rayleigh scattered light also has a wavelength of 785 nm. In this case, to better filter the Rayleigh scattered light, the edge filter may be set to a 785 nm edge filter, and the cutoff point of the edge filter may be set to 5 nm. In this manner, the Raman scattered light and Rayleigh scattered light focused by the objective lens are first transmitted to the spectroscope, which then separates the light of each wavelength into different paths and transmits the light to the edge filter. The edge filter then filters out the Rayleigh scattered light with a wavelength in the range of 780 nm to 790 nm, retaining only the Raman scattered light of other wavelengths.

[0087] In an optional embodiment, continue to refer to Figure 5As shown, the detection unit may further include a signal confocal device, which is arranged in the optical path of the edge filter and the spectrometer. The signal confocal device may include a first lens, a confocal hole, and a second lens. The confocal hole may be a plate-like structure with a central opening. The first lens, the confocal hole, and the second lens may be arranged on the same optical axis. In this way, after the edge filter transmits the Raman scattered light to the first lens, the weak Raman scattered light may be first collected by the first lens and focused on the confocal hole, and then transmitted to the second lens through the central opening of the confocal hole, and finally scattered by the second lens to the spectrometer. The Raman scattered light before the confocal treatment is relatively dispersed. By using the signal confocal device to perform confocal treatment on the Raman scattered light, the Raman scattered light can be converted into more concentrated Raman scattered light.

[0088] In an optional embodiment, continue to refer to Figure 5 As shown, the spectroscopic device may include a grating and a second prism. The grating may be a plate-like structure, the width of which needs to be greater than the width of the second prism. The grating may also be referred to as a spectrometer. For example, to improve the accuracy of grating spectrometry, the wavenumber range of the grating may be set to 0 to 1 / 3200 cm, and the line density may be set to 1200 grooves per millimeter. In this way, after the second lens transmits the confocal processed Raman scattered light to the grating, the grating causes the different wavelengths of light in the Raman scattered light to appear at different positions, thereby forming a Raman spectrum. Finally, the Raman spectrum is transmitted to the spectrum detection device by the second prism.

[0089] Figure 7 An example of a Raman spectrum is shown, such as Figure 7 As shown in the figure, the horizontal axis of the Raman spectrum is the Raman shift, measured in wavenumbers, and the vertical axis is the intensity of the Raman scattered light, measured in mW. A Raman spectrum can include multiple spectral lines, each corresponding to a wavelength. These spectral lines are caused by the interaction between the vibration of a substance in the blood and Rayleigh scattered light, such as cholesterol, glucose (or blood sugar), fat (or blood lipids), hemoglobin, etc. Figure 7 The spectral lines corresponding to the illustrated wavelengths have signal characteristic peaks with the same wave number. In other possible examples, the spectral lines corresponding to different wavelengths may also have signal characteristic peaks with different wave numbers.

[0090] In an embodiment of the present application, after the spectral detection device obtains the Raman spectrum corresponding to the current blood, it can obtain the characteristic peak intensity of glucose and the characteristic peak intensity of hemoglobin based on the Raman spectrum, then divide them to calculate the relative intensity of the glucose peak, and finally compare them with the preset corresponding relationship between the relative intensity of the glucose peak and the concentration to obtain the glucose concentration in the current blood. The preset corresponding relationship between the relative intensity of the glucose peak and the concentration is obtained by measuring blood glucose in normal human blood. The measurement process can be as follows: for different glucose concentrations, using the detection device to measure the Raman spectrum corresponding to the normal human blood, obtain the characteristic peak intensity of glucose and the characteristic peak intensity of hemoglobin of the normal human based on the Raman spectrum, then divide them to calculate the relative intensity of the glucose peak of the normal human, calculate the ratio of the relative intensity of the glucose peak at different glucose concentrations to the relative intensity of the glucose peak of the normal human to obtain the preset corresponding relationship between the relative intensity of the glucose peak and the concentration, and the preset corresponding relationship between the relative intensity of the glucose peak and the concentration is subsequently used as the basis for quantitative measurement of blood glucose concentration.

[0091] Based on the above, Figure 8 An optical path processing method for a detection device provided in an embodiment of the present application is exemplified as follows: Figure 8 As shown, the method includes:

[0092] Step 801 : Place the finger to be measured flat on a test bench, with the nail wrinkle of the finger to be measured aligned with the light outlet of the camera device.

[0093] In the embodiment of the present application, the user can select the finger to be measured. For example, if the finger to be measured is the ring finger of the right hand, Figure 4A or Figure 4B The user can directly insert the ring finger of the right hand into the finger fixture. In this case, since the position of the finger fixture and the position of the detection device are pre-set, the nail wrinkle on the ring finger of the right hand can be aligned with the light outlet of the camera device. Figure 4B For the finger clamp shown in the figure, and the opening of the finger clamp is small, the image captured by the camera device directly corresponds to the local area of ​​the nail fold. Therefore, the process of coarse adjustment of the position in the following steps 804 to 806 can no longer be performed, and the process of fine adjustment of the position in steps 807 to 809 can be directly performed.

[0094] Step 802: Start the detection device and execute:

[0095] If the blood sugar at the location to be tested is measured, then steps 803 to 810 are executed; or,

[0096] If the blood glucose level at a random position is to be measured, steps 811 and 812 are executed.

[0097] In step 803, the switching mirror is moved to position A, and the illumination light emitted by the illumination light emitter is irradiated to the nail fold of the finger to be measured via the illumination light transmission path, and the detection light emitted by the detection light emitter is irradiated to the nail fold of the finger to be measured via the detection light transmission path.

[0098] In an optional embodiment, when the switching mirror is in position A, the illumination light transmission path includes: illumination light emitted by the illumination light emitter is focused by the first prism to the first reflector in the wavelength range of 400nm to 700nm, which is then reflected by the first reflector to the switching mirror, and then reflected by the switching mirror to the first optical path L1, and then irradiated to the nail fold area along the first optical path L1. Correspondingly, when the switching mirror is in position A, the detection light transmission path includes: detection light emitted by the detection light emitter is subjected to light reduction processing by the light shielding plate and the filter, and then converted into detection light with a wavelength of 785nm and a power of 20mW required for testing blood glucose in the nail fold area, and then transmitted to the second reflector, reflected by the second reflector to the third reflector, and then reflected by the third reflector to the switching mirror, and then transmitted by the switching lens to the first optical path L1, and then irradiated to the nail fold area along the first optical path L1.

[0099] In an embodiment of the present application, when the display unit is operating, the illumination light emitter may emit illumination light at a first set frequency, and when the detection unit is operating, the detection light emitter may emit detection light at a second set frequency. The first set frequency and the second set frequency may be the same or different. For example, in one example, both the first set frequency and the second set frequency may be set to 50 times / second.

[0100] Step 804: Adjust the focal length of the objective lens to a low-magnification focal length, and the camera device periodically captures the current local image of the nail fold under the illumination light, and sends it to the display for display.

[0101] In an embodiment of the present application, the display may only display the current partial image of the nail fold. In this case, the user is required to memorize the partial image of the location to be tested for subsequent comparison. Alternatively, the display may simultaneously display the partial image of the location to be tested and the current partial image. This approach eliminates the need for the user to memorize the partial image of the location to be tested. Therefore, even those with poor memory can accurately locate the local area where the location to be tested is located. This also avoids the randomness and error-prone nature of relying on the user's memory to locate the local area where the location to be tested is located.

[0102] Figure 9 An example of a method for displaying an image based on a fingerprint recognition device is shown. Figure 9As shown, in an optional embodiment, a fingerprint recognition device can be installed at the fingertip pressure position on the test bench, and the fingerprint recognition device is connected to a display. In this case, when the user places their finger flat on the test bench, the fingerprint recognition device can capture fingerprint information from the user's fingertip and send it to the display. The display compares the user's fingerprint information with at least one pre-stored standard fingerprint information, finds a standard fingerprint information that matches the user's fingerprint information from the at least one standard fingerprint information, and after capturing the current image (a local image or a capillary image), simultaneously displays the current image and the image of the test location corresponding to the standard fingerprint information on the display. If no standard fingerprint information matches the user's fingerprint information in the at least one standard fingerprint information, the display can issue an alarm, such as displaying a message saying "The user's fingerprint has not been recorded." Using this embodiment, the same test device can be used to measure blood sugar for different users. If the test device stores images of the test locations of multiple users, the fingerprint recognition device can distinguish the users' identities, allowing the test device to display the image corresponding to the user currently being measured on the display, thereby helping to ensure that the measured blood sugar is the blood sugar of the user's test location.

[0103] It should be noted that the above is only one optional embodiment. In another optional embodiment, the fingerprint recognition device can also be placed in other locations on the test bench. For example, the fingerprint recognition device can be placed at the position where the pad of the finger not being tested is pressed, or it can be placed at the edge of the test bench to collect fingerprints from the user's other hand. It is understood that the fingerprint recognition device can also be replaced with other biometric information collection devices, such as palm print collectors, iris collectors, etc., without limitation.

[0104] Step 805 , determining whether the position of the light spot where the detection light irradiates the nail wrinkle in the current local image is the same as the position of the light spot in the local image of the position to be tested. If they are different, executing step 806 ; if they are the same, executing step 807 .

[0105] In the embodiment of the present application, the light spot refers to the focal point after the detection light is irradiated onto the human skin, and the position of the light spot corresponds to the position where the detection light is irradiated onto the nail fold.

[0106] Step 806 , move the finger to change the position where the detection light is irradiated on the nail wrinkle, and execute step 805 .

[0107] In the embodiment of the present application, as the finger moves, the position of the detection light irradiated on the nail fold also changes. Therefore, the position of the light spot formed by the detection light irradiating the human skin also changes. Furthermore, the user can continue to view the current partial image displayed on the display while moving the finger. When the position of the light spot in the current partial image matches the position of the light spot in the partial image of the location to be tested, the user stops moving the finger.

[0108] Step 807: Adjust the focal length of the objective lens to a high-power focal length, and the camera device periodically captures the current capillary image of the nail fold under the irradiation light, and sends it to the display for display.

[0109] In one alternative embodiment, the display may only show the current capillary image of the nail fold. In this case, the user is required to memorize the capillary image of the location to be tested for subsequent comparison. In another alternative embodiment, the display may simultaneously display the capillary image of the location to be tested and the current capillary image. This approach eliminates the need for the user to memorize the capillary image of the location to be tested. Therefore, even those with poor memory can accurately locate the location to be tested, while also avoiding the randomness and error-prone nature of relying on the user's memory to locate the location to be tested.

[0110] Step 808, determine whether the position of the light spot where the detection light irradiates the nail fold in the current capillary image is the same as the position of the light spot in the capillary image of the position to be tested. If different, execute step 809; if the same, execute step 810.

[0111] Step 809 , move the finger to change the position where the detection light is irradiated on the nail fold, and execute step 808 .

[0112] In an embodiment of the present application, the user can continue to view the current capillary image displayed on the display while moving the finger, and stop moving the finger after the position of the light spot in the current capillary image is the same as the position of the light spot in the capillary image of the position to be tested.

[0113] In step 810, the blood at the test site is excited by the test light and generates Raman scattered light and Rayleigh scattered light. The Raman scattered light and Rayleigh scattered light are collected by the objective lens and transmitted to a spectroscope. The spectroscope separates the light of different wavelengths into different paths. An edge filter removes the Rayleigh scattered light, retaining only the Raman scattered light. The Raman scattered light is then transmitted to a first lens. The first lens focuses the Raman scattered light onto a confocal aperture, which then transmits it to a second lens. The second lens scatters the Raman scattered light onto a grating, which then directs the different wavelengths of the Raman scattered light to different locations, forming a Raman spectrum. Finally, a second prism transmits the Raman spectrum to a spectral detection device, which determines the current blood glucose level at the test site based on the Raman spectrum.

[0114] In an optional embodiment, the detection device may also be provided with a start measurement button. After adjusting the spot of detection light irradiating the nail fold to the location to be tested, the user can press the start measurement button. In this case, the spectral detection device begins acquiring the Raman signal transmitted by the second prism and determines the current blood glucose level at the location to be tested based on the Raman signal. However, each current blood glucose level determined by the spectral detection device is actually a real-time blood glucose level. To improve the stability of blood glucose detection, each blood glucose detection process can last for one minute (i.e., after the user presses the start measurement button, the spectral detection device will continue measuring for one minute before terminating). During this one-minute period, the spectral detection device can detect multiple current blood glucose levels in real time and then integrate the multiple current blood glucose levels detected within the one-minute period, with the integrated value serving as the current blood glucose level. Since the user can see the location of the detection light spot irradiating the nail fold in real time on the display during this one-minute period, if the user finds that the location of the detection light spot is different from the location to be tested, the user can move their finger to ensure that the multiple current blood glucose levels measured within the one-minute period are the current blood glucose levels at the location to be tested and that the noise interference between the multiple current blood glucose levels is consistent. In this way, the signal-to-noise ratio of the integration of multiple current blood sugars measured within 1 minute can be increased, and the blood sugar measured this time obtained by integration can better indicate the blood sugar situation at the current location.

[0115] In an embodiment of the present application, the spectral detection device may also be connected to a display. After the measurement is completed, the spectral detection device may send the currently measured blood glucose value to the display for display to the user. For example, the display may also store the user's historical blood glucose value. When displaying the currently measured blood glucose value, the display may also display the user's historical blood glucose value and the currently measured blood glucose value simultaneously, so that the user can promptly understand changes in their blood glucose value.

[0116] Step 811 , moving the switching mirror to position B, and irradiating the detection light emitted by the detection light emitter to the nail wrinkle via the detection light transmission path.

[0117] In an optional embodiment, when the switching mirror is in position B, the detection light transmission optical path includes: the detection light emitted by the detection light emitter is dimmed by a shading plate and an optical filter, and then converted into detection light with a wavelength of 785nm and a power of 20mW required for testing blood sugar in the nail fold and transmitted to the second reflector, reflected by the second reflector to the third reflector, and then reflected by the third reflector to the first optical path L1, and irradiated to the nail fold along the first optical path L1.

[0118] In step 812, blood at a random location is excited by the detection light and generates Raman scattered light and Rayleigh scattered light. The Raman scattered light and Rayleigh scattered light are collected by the objective lens and transmitted to a spectroscope. The spectroscope separates the light of each wavelength into different paths and transmits the light to an edge filter. The edge filter then filters out the Rayleigh scattered light, retaining only the Raman scattered light. The Raman scattered light is then transmitted to the first lens. The first lens focuses the Raman scattered light onto a confocal aperture, which then transmits it to the second lens. The second lens scatters the Raman scattered light onto a grating, which then directs the different wavelengths of the Raman scattered light to different locations, forming a Raman spectrum. Finally, the second prism transmits the Raman spectrum to a spectral detection device, which determines the current blood glucose level at the random location based on the Raman spectrum.

[0119] It should be noted that the above embodiment only introduces the structure of the detection device using the measurement of human blood sugar as an example. Since blood sugar is located in the dermis layer at a depth of more than 200 microns from the epidermis of the skin, the detection light wavelength emitted by the detection light emitter in the above example is set to 785nm. The 785nm detection light can penetrate the skin into the blood in the dermis layer and extract the Raman scattered light corresponding to the blood sugar. The detection device in this application can also be used to measure other human body components. For example, if the component to be measured is water or natural moisturizing factors (NMF), since water and NMF are both located in the stratum corneum at a depth of less than 100 microns from the epidermis of the skin, the detection light wavelength emitted by the detection light emitter in the above example can be set to no more than 500nm. The 500nm detection light can penetrate the skin into the stratum corneum and extract the Raman scattered light corresponding to the water or NMF. It can be seen from this that the detection device in the present application can detect the content of components in human skin without invading human skin, which is a truly non-invasive detection method. Furthermore, the detection device in the present application can also perform multiple detections on the component content at the same position. In this way, the changes in the component content determined based on multiple detections can better reflect the user's actual physical condition.

[0120] The above are only specific embodiments of the present application, but the scope of protection of this application is not limited thereto. Any changes or substitutions that can be easily conceived by a person skilled in the art within the technical scope disclosed in this application should be included in the scope of protection of this application. Therefore, the scope of protection of this application should be based on the scope of protection of the claims.

Claims

1. A detection device, characterized in that: It includes a display unit and a detection unit, wherein the display unit includes an illumination light emitter, an illumination light transmission device, a camera device and a display, and the camera device is connected to the display; The illumination light emitter is used to emit illumination light; The illumination light transmission device is used to transmit the illumination light so that the illumination light is irradiated onto the object to be measured on the first optical path; The camera device is used to photograph the object to be measured under the illumination of the illumination light, and send the photographed information to the display for display; The display is used to display the information, wherein the information is used to instruct the object to be tested to be moved to a position to be tested; The detection unit is configured to emit detection light, transmit the detection light so that the detection light is irradiated onto the object to be detected along the first optical path, and detect the object to be detected based on scattered light generated after the detection light is excited by the object to be detected; Wherein, the object to be measured is the blood sugar of nail wrinkle; The imaging device includes a pair of objective lenses, wherein the optical axis of the pair of objective lenses is arranged on the first optical path; the pair of objective lenses has at least a first focal length and a second focal length, and the multiple of the first focal length is smaller than the multiple of the second focal length; The camera device is used to use the pair of objective lenses to photograph a local area of ​​the nail fold when the focal length of the pair of objective lenses is the first focal length, so as to obtain current local information corresponding to the nail fold; the current local information is used to instruct to move the nail fold so that the area of ​​the nail fold irradiated by the illumination light is the same as the local area corresponding to the position of the nail fold to be tested; and, when the focal length of the pair of objective lenses is the second focal length, use the pair of objective lenses to photograph a local area of ​​the nail fold to obtain current capillary information corresponding to the nail fold; the current capillary information is used to instruct to move the nail fold so that the position of the light spot of the detection light irradiated on the nail fold in the current capillary information is the same as the position of the light spot in the capillary information corresponding to the position of the nail fold to be tested.

2. The detection device according to claim 1, wherein The display unit further includes a first prism, wherein the optical axis of the first prism is arranged on a transmission light path of the illumination light emitted by the illumination light emitter to the illumination light transmission device; The first prism is used to focus the illumination light emitted by the illumination light emitter and having a wavelength not less than the first wavelength and not greater than the second wavelength onto the illumination light transmission device.

3. The detection device according to claim 2, wherein: When the object to be measured is blood sugar in nail wrinkles, the first wavelength is 400 nm and the second wavelength is 700 nm.

4. The detection device according to claim 3, wherein The wavelength of the detection light is 785 nm.

5. The detection device according to any one of claims 1 to 4, characterized in that The illumination light transmission device includes a first reflecting mirror and a switching mirror; The first reflector is directly opposite to the light outlet of the illumination light emitter; the first reflector is used to reflect the illumination light emitted by the illumination light emitter and emit it onto the switching mirror along a second optical path perpendicular to the first optical path; The switching mirror is located at the intersection of the first optical path and the second optical path, and is used to reflect the irradiation light emitted to the switching mirror to the first optical path.

6. The detection device according to claim 5, characterized in that The switching mirror is further used for: When the switching mirror moves along the second optical path to a position other than the intersection of the first optical path and the second optical path, the irradiation light emitted to the switching mirror is reflected to a third optical path; The third optical path is parallel to the first optical path, and the third optical path does not pass through the object to be measured.

7. The detection device according to any one of claims 1 to 4, characterized in that The detection unit includes a detection light emitter, a detection light transmission device, an edge filter, a light splitting device and a spectrum detection device; The detection light emitter is used to emit detection light; The detection light transmission device is used to transmit the detection light so that the detection light is irradiated onto the object to be detected along the first optical path; The edge filter is used to collect Raman scattered light and Rayleigh scattered light generated by the object to be measured after being excited by the detection light, filter out the Rayleigh scattered light and leave only the Raman scattered light, and transmit the Raman scattered light to the spectroscopic device; The spectroscopic device is used to perform spectroscopic processing on the Raman scattered light to form a Raman spectrum, and transmit the Raman spectrum to the spectrum detection device; The spectrum detection device is used to detect the object to be detected based on the Raman spectrum.

8. The detection device according to claim 7, characterized in that The detection unit further includes a spectroscope, wherein a central axis of the spectroscope is located on the first optical path, and an optical axis of the spectroscope transmitting light to the edge filter is perpendicular to the first optical path; The spectroscope is used to transmit the detection light transmitted to the spectroscope by the detection light transmission device, and to separate the Raman scattered light and Rayleigh scattered light of each wavelength generated by the object to be detected after being excited by the detection light into different paths, and transmit the light to the edge filter; The edge filter is used to filter out the Rayleigh scattered light on a path corresponding to the wavelength according to the wavelength corresponding to the Rayleigh scattered light.

9. The detection device according to claim 8, characterized in that The object to be measured is the blood sugar of nail wrinkles; The edge filter is a 785nm edge filter, and the cutoff point of the edge filter is 5nm.

10. The detection device according to claim 7, wherein: The detection unit further comprises a signal confocal device, which is arranged on a transmission light path between the edge filter and the spectrometer; The signal confocal device comprises a first lens, a confocal hole and a second lens; the first lens, the confocal hole and the second lens are arranged on the same optical axis; The first lens is used to collect the weak Raman scattered light transmitted from the edge filter and focus it on the confocal hole; The confocal aperture is used to project the focused Raman scattered light onto the second lens; The second lens is used to scatter the Raman scattered light projected by the confocal hole onto the spectroscopic device.

11. A health detection device, characterized in that: The device comprises a test bench, a base, and a detection device according to any one of claims 1 to 10; the test bench is arranged on the base; and the light outlet of the detection device is aligned with the test bench; The test bench is used to place the object to be tested; The detection device is used to emit illumination light through the light outlet to illuminate the object to be tested, and to photograph the object to be tested under the illumination light, to move the object to be tested to the test position of the test bench according to the information obtained from the photographing, and to detect the object to be tested moved to the test position.

12. The health detection device according to claim 11, wherein: The object to be tested is the blood sugar of the nail wrinkle of the finger to be measured; the test table is provided with a finger clamp; The finger fixture is used to fix the finger to be measured on the test bench.

13. The health detection device according to claim 12, wherein: The test bench is also provided with a fingerprint recognition device; The fingerprint recognition device is used to collect the user's fingerprint information; The fingerprint information of the user is used to determine the local information or capillary information of the position to be tested corresponding to the user, and the local information or capillary information of the position to be tested corresponding to the user is used to move the finger to be measured to the position to be tested.

Images