CN113876319A - Detection device and health detection equipment - Google Patents

Abstract

A detection device and a health detection device are used for realizing real non-invasive detection. The detection device comprises a display unit and a detection unit, wherein the display unit emits irradiation light and enables the irradiation light to irradiate an object to be detected on a first light path, the object to be detected under the irradiation of the irradiation light is shot, information obtained through shooting is sent to a display to be displayed, the information is used for indicating that the object to be detected is moved to a position to be detected, the detection unit emits detection light and enables the detection light to irradiate the object to be detected on the first light path, and the object to be detected is detected according to scattered light generated after the detection light is excited by the object to be detected. The detection unit and the display unit are combined, so that the same position of the object to be detected can be detected at every time, the detection of the same position has the characteristics of consistent detection conditions and high noise interference repeatability, the real change condition of the internal components of the object to be detected can be accurately reflected, and the reference value of the detection result can be improved.

Description

A detection device and health detection equipment

technical field

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

Background technique

Non-invasive detection technology has been researched and developed for more than 20 years, but there is no real non-invasive detection yet. Most of the non-invasive detection methods that can be done at present try to minimize the damage caused by the object to be measured, but cannot measure the internal components of the object to be measured without damaging the object to be measured. For example, in a currently commonly used non-invasive blood glucose detection method, a weak current needs to be used to stimulate the human skin, so that the glucose in the blood penetrates the human skin, and then the glucose solution on the skin surface is collected for detection. Although this method does not need to invade the inside of human skin, it still needs to apply certain stimulation to human skin, which will actually damage the normal function of human skin, so this method is not a non-invasive detection in the true sense.

Based on this, a detection device is urgently needed to realize non-invasive detection in the true sense.

SUMMARY OF THE INVENTION

The present application provides a detection device and health detection equipment, which are used to irradiate detection light into the interior of an object to be tested, and detect the components inside the object to be tested according to the scattered light scattered by the object to be tested, so as to avoid damage to the object to be tested. In the case of the object to be measured, the detection of the internal components of the object to be measured is realized. Further, the detection device further includes a display unit, which can display the information of the object to be measured under the illumination of the illumination light, and the information can show the internal texture of the object to be measured. When the composition of the detection unit is used, the detection light emitted by the detection unit can be aimed at 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 measured 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 measured. It helps to improve the reference value of test results.

In a first aspect, the present application provides a detection device, the detection device 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 illuminating light emitter can emit illuminating light, and after the illuminating light reaches the illuminating light transmission device, it is transmitted through the illuminating light transmission device to illuminate the object to be measured on the first optical path, and then the imaging device is used to irradiate the object to be measured by the illuminating light. The object to be measured is photographed, 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 to irradiate the object to be tested on the first optical path, and then detect the object to be tested according to scattered light generated by the detection light excited by the object to be tested.

In the above design, by irradiating the detection light into the object to be tested, the components inside the object to be tested can be detected according to the scattered light scattered back by the object to be tested, which is helpful to realize the treatment without damaging the object to be tested. Detection of internal components of objects. Moreover, each time the composition of the object to be measured is detected, the information of the object to be measured under the irradiation of the illumination light captured by the display unit can be referred to, and the detection light can be aimed at the same position of the object to be measured, and then the detection unit can be used for detection. This method helps to detect the same position of the object to be measured 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 measured. It helps to improve the reference value of test results.

In a possible design, the object to be measured is the blood sugar of the nail crease, and the information captured by the camera device can be used to indicate the position of the capillary in the nail crease and the position of the light spot formed after the detection light irradiates the nail crease. In this way, since most of different capillaries have different shapes, the user can accurately align the light spot formed after the detection light is irradiated on the nail fold to the position to be tested by checking the position of each capillary, which is helpful for realizing the position to be tested. blood sugar measurement.

In a possible design, the display device further includes a first prism, the optical axis of the first prism is set on the transmission light path for the illumination light emitter to emit the illumination light to the illumination light transmission device, and the first prism is used to transmit the illumination light The irradiating light which is not smaller than the first wavelength and not larger than the second wavelength emitted by the device is focused on the irradiating light transmission device, and the first wavelength is smaller than the second wavelength. Wherein, the irradiation light with the wavelength not less than the first wavelength and not greater than the second wavelength is the irradiation light capable of displaying the internal texture of the object to be measured. In this way, focusing the irradiation light in the wavelength range through the first prism helps to irradiate the object under test with the irradiation light suitable for the object under test, so as to display the internal texture of the object under test on the display.

In a possible design, when the object to be measured is the blood sugar of the nail fold, the first wavelength is 400 nm, and the second wavelength is 700 nm. Through this design, the irradiated light in the wavelength range of 400nm to 700nm belongs to visible light, and the visible light in this wavelength range can illuminate the inside of the skin dermis layer of the nail fold. Since the capillaries are arranged inside the dermis layer, the irradiated light in this wavelength range can The capillaries in the nail fold were successfully revealed.

In one possible design, the wavelength of the detection light is 785 nm. In this way, by setting the wavelength of the detection light to be closer to the wavelength of the irradiation light, and setting the detection light and the irradiation light to both irradiate the nail crease on the first optical path, the light spot formed by the detection light irradiated on the nail crease can also be displayed on the nail crease. information captured by the camera.

In a possible design, the illumination light transmission device includes a first reflecting mirror and a switching mirror, the first reflecting mirror is facing the light outlet of the illumination light emitter, and the first reflecting mirror is used for reflecting the illumination light emitted by the illumination light emitter After reflection, it is emitted to the switching mirror on 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, and the switching mirror is used to reflect the illumination light emitted to the switching mirror to the first optical path. In this way, by arranging the optical paths where the reflecting mirror and the switching mirror are located, the irradiation light can be accurately reflected on the first optical path.

In one possible design, the switching mirror can move along the second optical path, and when the switching mirror moves to a position other than the position of the intersection of the first optical path and the second optical path, the switching mirror can redirect the illumination emitted to the switching mirror The light is reflected to a third optical path, wherein 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. Through this design, the detection device can have two working modes: the display unit and the detection unit work at the same time, or the display unit does not work and the detection unit works, so that the user can set the working mode of the detection device according to actual needs.

In a possible design, the object to be measured is blood sugar of the nail crease, the imaging device includes an objective lens, the optical axis of the objective lens is set on the first optical path, and the objective lens has at least a first focal length and a second focal length, the first focal length. The multiple of the focal length is smaller than the multiple of the second focal length. Wherein, when the focal length of the objective lens is the first focal length, the imaging device may use the objective lens to photograph the local area of the nail crease to obtain the current local information corresponding to the nail crease. Wherein, the current local information is used to instruct to move the nail fold, so that the area irradiated by the irradiation light on the nail fold is the same as the local area corresponding to the position of the nail fold to be tested. In addition, when the focal length of the objective lens is the second focal length, the imaging device can also use the objective lens to photograph the local area of the nail fold, so as to obtain the current capillary information corresponding to the nail fold. Wherein, the current capillary information is used to instruct to move the nail fold, so that the position of the light spot illuminated by the detection light 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 first coarse adjustment and then fine adjustment, a small local nail wrinkle area can be locked first, and then the smaller local nail wrinkle area can be fine-tuned, instead of using a larger focal length to fine-tune the entire nail wrinkle all the time , thereby helping to reduce the workload of users to compare information.

In a possible design, the detection unit further 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 can emit detection light, and after the detection light reaches the detection light transmission device, it can be transmitted through the detection light transmission device so that it also illuminates the object to be measured on the first optical path, and then is collected by the edge filter. The Raman scattered light and Rayleigh scattered light generated after the object is excited by the detection light, the Rayleigh scattered light is filtered out and only the Raman scattered light is left, and the Raman scattered light is transmitted to the spectroscopic device, and then the spectroscopic device analyzes The Raman scattered light is subjected to spectroscopic processing to form a Raman spectrum, the Raman spectrum is transmitted to a spectrum detection device, and finally the object to be tested is detected by the spectrum detection device according to the Raman spectrum. In this way, by using the Raman spectrum detection method to detect the object to be measured, it is possible to detect components inside the object to be measured without damaging the object to be measured.

In a possible design, the detection unit further includes a light intensity adjustment device, the light intensity adjustment device is arranged on the transmission light path of the detection light emitted by the detection light emitter to the detection light transmission device, and the light intensity adjustment device is used to adjust the detection light. The detection light emitted by the transmitter is adjusted to the detection light of the intensity required to detect the object to be detected. In this way, the detection light adjusted by the light intensity adjusting device can be more suitable for detecting the object to be measured, and the intensity of the adjusted detection light can not damage the object to be measured, but also can detect the components inside the object to be measured.

In a possible design, when the object to be tested is blood sugar of the nail crease, 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 of no more than 20mW, so as to avoid the intensity of the detection light Too high and burn human skin.

In a possible design, the light intensity adjustment device includes a light shielding plate, the light shielding plate is arranged at the light outlet of the detection light emitter, and a light transmission 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 to detect the object to be detected, the shading plate is moved to reduce the light transmission hole. There is less detection light, which helps to reduce the intensity of the detection light irradiated on the object to be tested. When the intensity of the laser light emitted by the detection light transmitter is less than the intensity required to detect the object to be tested, the light shielding plate is moved to increase the light transmission hole. More detection light helps to increase the intensity of detection light irradiated on the object to be tested.

In a possible design, the light intensity adjusting device includes an optical filter, and the optical filter is arranged on the same optical axis as the detection light emitter. When the intensity of the detection light emitted by the detection light emitter is greater than the intensity required to detect the object to be measured, the light reduction ratio of the filter is increased, and more light is filtered out by the filter, which can reduce the exposure to the object to be measured. the intensity of the detected light. When the intensity of the laser light emitted by the detection light emitter is less than the intensity required to detect the object to be measured, the light reduction ratio of the filter is reduced, and less light is filtered out by the filter, which can increase the amount of light irradiated on the object to be measured. The intensity of detection light.

In a possible design, the detection light transmission device includes a second reflection mirror and a third reflection mirror arranged side by side, the optical axes of the second reflection mirror and the third reflection mirror are parallel, and the central axis of the second reflection mirror is arranged in the detection Just below the light outlet of the light emitter, the central axis of the third reflector is arranged on the first light path. Wherein, the second reflecting mirror can reflect the detection light emitted by the detection light emitter to the third reflecting mirror, and the third reflecting mirror can reflect the detection light reflected by the second reflecting mirror to the switching mirror arranged on the first optical axis, 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.

In a possible design, the detection unit further includes a beam splitter, the central axis of the beam splitter is located on the first optical axis, and the optical axis of the beam splitter transmitting light to the edge filter is perpendicular to the first optical axis. The spectroscope can transmit the detection light transmitted from the detection light transmission device to the spectroscope, and separate the Raman scattered light and Rayleigh scattered light generated by the object to be detected after being excited by the detection light into different wavelengths. In this way, the edge filter can filter out the Rayleigh scattered light on the path corresponding to the wavelength according to the wavelength corresponding to the Rayleigh scattered light, so as to retain only the Raman scattered light.

In a possible design, the object to be tested is blood sugar for nail crease detection, in this case, the edge filter may be a 785nm edge filter, and the cutoff point of the edge filter is 5nm. Through this design, the edge filter can filter the scattered light whose wavelength is in the range of 780nm to 790nm. In this way, the scattered light filtered by the edge filter basically does not contain the scattering of the same wavelength (785nm) as the detection light. light, thereby contributing to the subsequent determination of the accuracy of Raman spectroscopy.

In a possible design, the detection unit further includes a signal confocal device, and the signal confocal device is arranged on the transmission optical path of the edge filter and the light splitting device. Wherein, the signal confocal device may include a first lens, a confocal aperture and a second lens, and the first lens, the confocal aperture and the second lens are arranged on the same optical axis. The weak Raman scattered light transmitted by 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 on the second lens through the confocal hole, and then passed through the second lens. The two lenses scatter the Raman scattered light projected by the confocal aperture onto the spectroscopic device. With this design, the Raman scattered light before the confocal treatment is relatively scattered, and by performing the confocal treatment on the Raman scattered light, the Raman scattered light can be converted into relatively concentrated Raman scattered light.

In a possible design, the spectroscopic device includes a grating and a second prism, the grating and the signal confocal device are arranged on the same optical axis, and the second prism is arranged on the transmission light path between the grating and the spectral detection device. Through this design, after the Raman scattered light after confocal processing is transmitted to the grating through the second lens, the light of different wavelengths in the Raman scattered light will appear at different positions through the grating to form a Raman spectrum, and then the light of different wavelengths in the Raman scattered light will appear at different positions through the grating. The quadratic prism transmits the Raman spectrum to the spectral detection device.

In a second aspect, the present application provides a health detection device, comprising a test table, a base and the detection device according to any one of the first aspect, wherein the test table is arranged on the base, and the light outlet of the detection device is aligned with the test table. After placing the object to be tested on the test table, the detection device can emit illumination light through the light outlet to illuminate the object to be tested, photograph the object to be tested under the illumination light, and then instruct the object to be tested to move according to the information obtained from the shooting to the position to be tested on the test bench, and to detect the object to be tested that moves to the position to be tested. By arranging the detection device in the health detection device, the user can detect blood sugar at any time even at home, so that it is convenient for diabetics or pre-diabetic patients to monitor and manage their blood sugar health at any time.

In a possible design, the object to be measured is the blood sugar of the nail crease of the finger to be measured. In this case, a finger clamp can also be provided on the test table, and the finger clamp is used to fix the finger to be measured on the test table, so as to avoid the inaccurate test result caused by the large shaking of the finger to be measured during the detection process .

In a possible design, a fingerprint identification device may also be provided on the test bench, and the fingerprint identification 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 moving 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 identification device is used to distinguish the identity of the user, so that the detection device can measure the current measurement of the user's blood sugar. Corresponding information is displayed on the display, thereby helping to ensure that the detected blood sugar is the currently measured blood sugar of the user.

The above-mentioned aspects or other aspects of the present application will be described in detail in the following examples.

Description of drawings

Fig. 1 exemplarily shows a positional schematic diagram of a nail fold part;

FIG. 2A exemplarily shows a skin hierarchy diagram of other parts;

FIG. 2B exemplarily shows a schematic diagram of the skin hierarchy of a nail fold site;

FIG. 3 exemplarily shows a schematic structural diagram of a health detection device;

FIG. 4A exemplarily shows a schematic structural diagram of a finger clamp;

FIG. 4B exemplarily shows a schematic structural diagram of another finger clamp;

FIG. 5 exemplarily shows a schematic structural diagram of a detection device provided by an embodiment of the present application;

Fig. 6 exemplarily shows a kind of schematic diagram of photographing nail folds with different magnifications of the objective lens;

FIG. 7 exemplarily shows a Raman spectrogram;

FIG. 8 exemplarily shows an optical path processing method of a detection device provided by an embodiment of the present application;

FIG. 9 exemplarily shows a manner in which the fingerprint identification device displays an image.

Detailed ways

The detection device in the embodiments of the present application can be used to measure biological components, such as human blood lipids, cholesterol, blood sugar, etc., and can also be used to measure non-biological components, such as the content of metal elements, the hardness of non-metal elements, and the like. For example, the detection device proposed in the embodiment of the present application may be some blood glucose detection equipment, blood lipid detection equipment, etc. applied in medicine.

Some terms involved in the embodiments of the present application are first introduced below.

(1) Raman spectrum

When the excitation light is irradiated on the substance, light scattering occurs, and the scattered light includes not only an elastic component with the same wavelength as the excitation light (called Rayleigh scattering light), but also a wavelength longer than that of the excitation light or Short inelastic components (called Raman scattered light) that arise from the interaction of molecular vibrations and excitation light in matter, or from elemental excitation and excitation light such as optical phonons in matter The spectrum formed by the interaction of Rayleigh scattered light and Raman scattered light is called Raman spectrum. In Raman spectroscopy, the difference between the frequencies of Raman scattered light and Rayleigh scattered light is called Raman shift, and the Raman shift and the vibrational frequency of molecules in a substance are related to the energy level, which can be used to characterize substances in a substance. molecular properties.

(2) Confocal

Confocal in the embodiments of the present application means that after the excitation light irradiates the object, it is displayed as a focal point (referred to as a light spot), rather than a scattered focal 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 region, which has large randomness and may not be able to characterize the molecular properties of the substance well. Among them, the Raman spectrum extracted by the confocal method can have higher resolution than the non-confocal method. Confocal extraction of Raman spectra can perform micron-level detection on object surfaces.

(3) Nail folds

The nail crease in the embodiments of the present application refers to the skin crease covering the root of the nail. Figure 1 exemplarily shows a schematic diagram of the location of a nail fold. As shown in Figure 1, the root of the nail also has an oval hollow area, called the claw meniscus, and the nail folds adjoin the claw meniscus through the paw epithelium.

In the examples of the present application, the skin hierarchy of the nail fold is slightly different from the skin hierarchy of other parts. Fig. 2A exemplarily shows a skin hierarchy diagram of other parts. As shown in Fig. 2A, the skin of other parts includes epidermis, stratum corneum, transparent layer, granular layer, spinous layer, and basal layer in order from top to bottom and the dermis, in which capillaries and veins are located. FIG. 2B exemplarily shows a schematic diagram of the skin hierarchy of a nail fold site. As shown in FIG. 2B , the skin at the nail fold includes the epidermis layer, the transparent layer, the granular layer, the spinous layer, the basal layer and the dermis layer in order from top to bottom. Compared with other parts of the skin, the skin in the nail fold does not contain the stratum corneum, so the capillaries in the nail fold are closer to the skin epidermis. The skin similar to the nail fold also includes the earlobe, nasal cavity, etc., and the skin of these parts does not contain the stratum corneum.

(4) Non-invasive detection

The non-invasive detection in the embodiments of the present application is a non-invasive detection method, and the physiological and biochemical parameters related to the component to be detected can be indirectly guided or sensed by contacting or non-contacting the measuring instrument with the skin. Because non-invasive detection does not cause trauma to the user's skin, it is very popular among users.

(5) wavelength of light

In the embodiment of the present application, if the wavelength of the light is longer, the depth of the light irradiated into the object is deeper, and if the wavelength of the light is shorter, the depth of the light irradiated into the object is shallower.

The solutions in the present application will be described in detail below with reference to the drawings in the embodiments of the present application. It should be noted that, in the embodiments of the present application, "at least one" refers to one or more, and "multiple" refers to two or more. "And/or", which describes the association relationship of the associated objects, indicates that there can be three kinds of relationships, for example, A and/or B, which can indicate: the existence of A alone, the existence of A and B at the same time, and the existence of B alone, where A, B can be singular or plural. The character "/" generally indicates that the associated objects are an "or" relationship. "At least one item(s) below" or similar expressions thereof refer to any combination of these items, including any combination of single item(s) or plural items(s). For example, at least one item (a) of a, b, or c can represent: a, b, c, a-b, a-c, b-c, or a-b-c, where a, b, c may be single or multiple .

And, in the description of the embodiments of the present application, the terms "first", "second" and "third" are only used for the purpose of description, and cannot be understood as indicating or implying relative importance or implying that The number of technical features, such as: "first mirror", "second mirror", "third mirror", etc. Thus, a feature defined as "first", "second", "third" may expressly or implicitly include one or more of that feature.

For ease of understanding, the following embodiments of the present application describe the structure of the detection device by taking the measurement of blood sugar at the nail folds of the human body as an example.

The detection apparatus in this embodiment of the present application may be set in a health detection device. FIG. 3 exemplarily shows a schematic structural diagram of a health detection device. As shown in FIG. 3 , the health detection device may include a base 310 , a test table 320 and a detection device 330 , wherein the light outlet of the detection device 330 is set at the test device 330 . Right above the table 320 , the lower bottom surface of the test table 320 is placed on the base 310 . When measuring the blood sugar at the nail fold, the user can place his finger on the test table 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 The nail fold is irradiated, the scattered light scattered by the nail fold is collected, and the blood sugar at the nail fold is measured based on the scattered light.

In an optional implementation manner, in order to avoid a large movement of the finger during the measurement process, resulting in inaccurate measurement results, a finger clamp may also be provided on the test table 320 . There are many possibilities for the structure of the finger clamp, two possible finger clamps are exemplified below:

FIG. 4A exemplarily shows a schematic structural diagram of a finger clamp 321. As shown in FIG. 4A, the finger clamp 321 may include a left side plate, a right side plate and a rear side plate, the left side plate and the right side plate are arranged in parallel, and the rear side plate The left side of the board is fixedly connected to the rear side of the left side board, the right side of the rear side board is fixedly connected to the rear side of the right side board, and the lower bottom surfaces of the left side board, the right side board and the rear side board are all fixed on the test bench 320 superior. Wherein, the distance between the left plate and the right plate may be slightly larger than the width of the middle knuckle of the finger. In this way, when the user places a finger between the left side plate and the right side plate and presses the fingertip against the rear side plate, the left side plate and the right side plate can just hold the finger. Moreover, in this case, the positions of the left side plate, the right side plate and the rear side plate also need to satisfy: when the finger is clamped between the left side plate and the right side plate, the light outlet of the detection device 330 can just irradiate the finger on the nail crease.

FIG. 4B exemplarily shows a schematic structural diagram of another finger clamp 321. As shown in FIG. 4B, the finger clamp 321 may include a left side panel, a right side panel, a rear side panel and an upper side panel. An accommodating space is formed between the test stands 320 , and the size of the accommodating space can be used to accommodate a user's finger. In addition, the upper side of the finger holder 321 may have a hole, and the position of the hole may be the position where the nail crease of the finger is aligned after the user inserts the finger into the accommodating space. The shape of the hole can be a square hole, a round hole, or an irregular hole. The size of the hole can be set by the user according to actual needs. For example, when the hole is a round hole, it can be set to no more than 0.05 mm. round hole. With the finger clamp of this structure, every time the user stretches his finger into the accommodating space formed by the finger clamp and the test table, the same nail crease area can be aligned with the through hole on the finger clamp, which is helpful for the detection device The blood sugar in the same nail fold area is tested each time.

It should be noted that, in FIGS. 4A and 4B, the structure of the finger clamp is introduced by taking the measurement of the nail fold of the index finger of the right hand as an example. In actual operation, the nail fold of the finger to be measured can be selected by the user, for example, it can also be measured. Ring finger.

In an optional embodiment, after the finger clamp 321 fixes the finger, if the position irradiated by the light outlet is different from the position to be measured in this measurement, the user can also move the test table 320 to indirectly Move your finger. 3 , the test table 320 can move along the X direction, the Y direction or the Z direction as shown in the figure. There are many ways to move the test table 320. For example, the user can manually push the test table 320 to move, or a micrometer driver can be set on the test table 320 in advance, and the driving accuracy of the micrometer driver can be no more than 1 micron, so , By realizing micron-level position fine-tuning, it can not only avoid the problem of repeated adjustment caused by excessive adjustment range, but also make the error between the final position and the position to be measured not greater than 1 micron, which improves the accuracy of the position to be measured. the accuracy of blood glucose testing. Wherein, the micrometer driver can be set as a micrometer three-dimensional driver, and the user operates the micrometer three-dimensional driver to control the movement of the test table 320 in the X direction, the Y direction or the Z direction. Alternatively, the micrometer driver can also be set as a micrometer two-dimensional driver, and the user operates the micrometer two-dimensional driver to control the test table 320 to move in the X direction or the Y direction, and the Z direction can be adjusted by the user controlling the manual circular adjuster of the test table .

In the embodiment of the present application, since the position of the finger may be adjusted during the blood glucose test, a certain distance can also be reserved between the upper surface of the finger and the light outlet when setting the health detection device. In this way, when measuring blood sugar, the user's finger does not actually touch the light outlet. Therefore, even if the finger is moved during the measurement, the user's finger will not rub against the light outlet. In this way, not only the degree of wear of the light outlet can be reduced, but also the user will not feel discomfort during the process of moving the finger, which helps to improve the user experience.

In the above-mentioned embodiment, although the provision of the finger clamp helps to detect the blood sugar in the same nail fold area, the same nail fold area includes a larger range (for example, a circular surface with a radius of 0.5 cm) on the microscopic level. , and the detection device only measures one micron-level point at a time. In this case, the slight shaking of the finger may make the position measured by the detection device this time different from the previous measurement position, and the blood sugar in different positions has different detection conditions and different noise interference, so according to different positions The blood sugar change information determined by blood sugar contains relatively large noise and cannot reflect the real blood sugar change of the user.

In view of this, an embodiment of the present application provides a detection device, the detection device includes a detection unit and a display unit, wherein the display unit can display the capillary information of the nail fold. First refer to the capillary information of the nail fold to align the light spot irradiated by the irradiated light in the detection unit to the same position (for example, a certain position on a capillary with a special shape or length or a certain position around it), and then use the detection unit Have a blood sugar test. This method helps to detect the blood sugar at the same location every time, and because the blood sugar at the same location has the characteristics of consistent detection conditions and high repeatability of noise interference, it can accurately reflect the real changes in blood sugar and help improve detection. The reference value of the result.

FIG. 5 exemplarily shows a schematic structural diagram of a detection device provided by an embodiment of the present application. As shown in FIG. 5 , the detection device may include a display unit and a detection unit, and the display unit may include an illumination light emitter and an illumination light transmission device. , a camera and a display, and the camera is connected to the display. Wherein, the irradiating light emitter can emit irradiating light, and the irradiating light can be irradiated to the nail fold on the first optical path (L1) after being transmitted by the irradiating light transmission device, and the imaging device can take pictures of the nail fold part irradiated by the irradiating light , and send the information obtained by shooting to the monitor for display. Correspondingly, the detection unit can emit detection light, and transmit the detection light so that the detection light is also irradiated to the nail fold on the first optical path (L1), and the detection unit can also be excited by the skin of the nail fold according to the detection light. The scattered light was used to detect the blood sugar in the nail fold.

In the embodiment of the present application, the information obtained by the camera device photographing the nail crease may be an image of the nail crease. Since the skin at the nail crease is thin (without a stratum corneum), after the nail crease is irradiated with irradiated light, the image of the nail crease is captured by the camera. The obtained image shows capillaries in the nail folds. In addition, after the nail fold is irradiated with the detection light, the image captured by the imaging device can also display the light spot formed by the detection light irradiated to the nail fold. In this case, if the user wants to detect the blood sugar at a certain position, the user can check the current image displayed on the display. If not, the test table 320 can be moved to drive the fingers to move until the position of the spot where the detection light irradiates the nail fold in the current image displayed on the display is consistent with the position to be measured, and then the detection unit is used to measure the blood sugar at this position. Illustratively, since different capillaries are mostly of different shapes, the location to be measured may be identified by capillaries having a particular shape.

In an optional implementation manner, a standard image and a current image can also be displayed on the display at the same time, wherein the standard image can be the image of the measured position displayed on the display when the user measured blood glucose last time, or it can be an image of the measured position displayed on the display when the user measures blood sugar last time, or it can be an image of the measured position displayed by the user for each blood glucose measurement set by the user. An image of the location where the blood glucose needs to be measured each time. In this case, the user does not need to memorize the image of the position to be measured, but can directly compare the position of the spot where the detection light irradiates the nail fold in the current image displayed on the monitor with the spot in the standard image If the two positions are inconsistent, move the test table 320 until the two positions are consistent, and then use the detection unit to measure blood sugar.

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

In an optional implementation manner, continuing to refer to FIG. 5 , the display unit may further include a first prism in addition to the illuminating light emitter, the illuminating light transmitting device, the camera device and the display shown in FIG. 5 , The optical axis of the first prism may be disposed on a transmission light path through which the illumination light emitter emits illumination light to the illumination light transmission device. In this way, after the irradiation light of various wavelengths emitted by the irradiation light emitter is irradiated to the first prism, the irradiation light in the wavelength range of 400nm˜700nm can be focused to the irradiation light transmission device through the first prism. In this implementation, the irradiated light in the wavelength range of 400 nm to 700 nm belongs to visible light, and the visible light in this wavelength range can illuminate the inside of the skin dermis at the nail fold. The irradiated light can reveal the capillaries in the nail folds.

In an optional implementation manner, continuing to refer to FIG. 5 , the illumination light transmission device may include a first reflection mirror and a switching mirror, and the first reflection mirror may be disposed directly above the light outlet of the illumination light emitter, and the illumination light The illumination light emitted by the light emitter can be emitted to the switching mirror on a second light path ( L2 ) perpendicular to the first light path L1 after being reflected by the first reflecting mirror. Among them, the switching mirror can move along the direction of the second optical path L2, in this case:

When the switching mirror moves to the intersection of the first optical path L1 and the second optical path L2 (position A as shown in FIG. 5 ), the switching mirror can reflect the irradiation light irradiated on the switching mirror to the first optical path L1, thus, The irradiation light can be irradiated on the nail crease; or, when the switching mirror moves to a position other than the intersection of the first optical path L1 and the second optical path L2 (for example, the position B shown in FIG. 5 ), the switching mirror can irradiate the nail fold. The irradiation light on the switching mirror is reflected to the third optical path (L3), the third optical path L3 is parallel to the first optical path L1, and the third optical path L3 does not pass through the test bench, so the irradiation light cannot irradiate the nail crease.

In the embodiment of the present application, the switching mirror can reflect the illumination light irradiated on the switching mirror, and can transmit the detection light irradiated on the switching mirror. In this way, the detection device can have two working modes: when the switching mirror is moved to the 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. With this implementation, the user can set the working mode of the detection device according to actual needs, for example:

In one scenario, if the user wants to measure the blood sugar change before and after a meal, the blood sugar at the same location needs to be measured before and after a meal, so that the blood sugar change value obtained is the most accurate. In this case, the switching mirror can be moved to the position A, so that the display unit and the detection unit work at the same time. When measuring blood sugar before meals, the display can be controlled to store the capillary images at the measured position (including the detection light irradiated to the nail folds). spots and capillaries). When measuring blood sugar after a meal, observe the capillary image of the measured position before meals and the capillary image of the current position through the display, and move the test table 320 when the two are not at the same time until the capillary image of the moved position and the capillary image of the current position are not the same. After the position of the light spot on the capillary image of the measurement position is consistent, the blood glucose after a meal is measured.

In another scenario, if the user wants to conduct a comparative experiment on the blood sugar at different positions of the nail fold, the blood sugar at a certain position of the nail fold can be randomly measured each time without aligning with the same position. In this case, the switching mirror can be moved to position B, and the detection unit can be activated and the display unit deactivated. In this way, only the detection light emitted by the detection unit on the first optical path irradiates the nail fold, and no irradiation light from the display unit irradiates the nail fold. Therefore, the scattered light excited by the skin at the nail fold can receive less interference, which helps improve the accuracy of blood glucose testing.

In this embodiment of the present application, the camera device may include an image sensor (not shown in FIG. 5 ), and the capillary blood vessel image captured by the camera device may be sent to the image sensor first, and the image sensor filters out the capillary blood vessel images irrelevant to the capillary blood vessel. After pixels, the filtered capillary image is sent to the display for display. This method can not only reduce the complexity of displaying the capillary blood vessel image on the display, reduce the memory occupied by the capillary blood vessel image, but also enable the user to watch the capillary blood vessel image without being disturbed by other pixels.

In an optional embodiment, continuing to refer to FIG. 5 , the imaging device may further include an objective lens, and the optical axis of the objective lens is set on the first optical path L1 and has a certain distance from the nail fold. . The objective lens can focus the detection light emitted to the objective lens, and the distance between the objective lens and the nail fold can be set according to the depth of the skin where the detection light irradiates the nail fold, for example, when the detection light does not reach the nail fold. In the case of the dermis layer of the skin, the distance can be reduced, and when the detection light is irradiated to the dermis layer of the nail fold but is too deep, the distance can be increased in order to prevent the detection light from damaging the human skin. In addition, the objective lens can also magnify the nail fold according to the set focal length, so that the imaging device can capture an enlarged capillary image.

In this embodiment of the present application, the objective lens may 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, the corresponding aperture is 0.24 nm, and the second focal length is 20 times, the corresponding pore size is 0.2nm. FIG. 6 exemplarily shows a schematic diagram of photographing the nail fold with different magnifications of the objective lens. When measuring blood sugar, the focal length of the objective lens can be adjusted to the first focal length, so that the camera device first uses a small magnification to take pictures of the nail fold (image a in Figure 6), and obtain the current partial image of the nail fold. , as shown in image b in Figure 6. In this case, the current partial image and the standard partial image can also be displayed on the display at the same time. If the two images are inconsistent, the nail fold can be moved by moving the test table 320 to roughly adjust the position where the irradiation light hits the nail fold. . When the current partial image displayed on the display is consistent with the standard partial image, the focal length of the objective lens can be adjusted to the second focal length, so that the camera device can use a large magnification to take pictures of the partial nail fold to obtain the partial nail fold. The current capillary image of the site, as shown in image c in Figure 6. In this case, the current capillary image and the standard capillary image can also be displayed on the display at the same time. If the position of the spot where the detection light irradiates the nail fold is not the same on the two images, you can continue to move the test table 110 to drive the nail. The wrinkle moves to finely adjust the position of the spot where the detection light irradiates the nail fold until the position of the spot where the detection light strikes the nail fold is consistent with the position of the spot on the current capillary image and the standard capillary image.

Exemplarily, in the above-mentioned implementation manner, only the display unit can be started without starting the detection unit during rough adjustment, and the display unit and the detection unit can be started at the same time during fine adjustment, so as to reduce the power consumption of the detection device as much as possible and improve the performance of the detection device. Check the battery life of the device. Of course, the display unit and the detection unit can also be activated at the same time during the rough adjustment and the fine adjustment. If this is the implementation method, the user is also required to compare the position of the spot on the current local image where the detection light irradiates the nail crease during the rough adjustment. and the location of the spot in the standard partial image. The specific method to be used can be set by the user according to actual needs, which is not limited in this application.

In the embodiment of the present application, by adopting the method of first coarse adjustment and then fine adjustment, a small local nail wrinkle area can be locked first, and then the small local nail wrinkle area can be fine-tuned without using a larger focal length all the time. Fine-tune the entire nail crease to help ease the user's workload in comparing images.

In an optional implementation manner, continuing to refer to FIG. 5 , the detection unit may include a detection light emitter, a detection light transmission device, an edge filter, a spectroscopic device, and a spectrum detection device. The detection light emitter can emit detection light, and the detection light can also be irradiated to the nail fold on the first optical path L1 after being transmitted by the detection light transmission device. After the nail fold is excited by the detection light, Raman scattered light and After Rayleigh scattered light, Raman scattered light and Rayleigh scattered light are transmitted to the edge filter, the Rayleigh scattered light is filtered out by the edge filter and only the Raman scattered light is left, and the Raman scattered light is split. After the device performs spectroscopic processing, a Raman spectrum is formed and transmitted to a spectrum detection device, and the spectrum detection device determines the blood sugar at the nail fold according to the Raman spectrum.

In this embodiment of the present application, the detection light emitter may emit detection light with a single wavelength and a fixed power, and the wavelength and power of the detection light may be determined according to the substance to be tested. In the case where the substance to be tested is blood sugar at the nail fold, the wavelength of the detection light can be selected as near-infrared light that is closer to the wavelength of the irradiation light on the nail fold. The nail fold is irradiated on the first optical path L1, so the light spot formed by the detection light irradiated on the nail fold can also be displayed in the image captured by the imaging device. Exemplarily, if the wavelength of the irradiation light used to irradiate the nail fold is 400 nm to 700 nm, the wavelength of the detection light emitted by the detection light emitter can be set to 785 nm, and the power of the detection light emitted by the detection light emitter can be set to 500 mW ( Power units, milliwatts).

In an optional implementation manner, continuing to refer to FIG. 5 , the detection unit may further include a light intensity adjustment device, and the light intensity adjustment device may be arranged on the optical path of the detection light emitted by the detection light emitter to the detection light transmission device , and the light intensity adjusting device is used for dimming the detection light emitted by the detection light emitter. For example, assuming that the detection light transmitter emits detection light with a power of 500mW, the detection light can be adjusted to a detection light with a power of no more than 20mW through the light intensity adjustment device, and then irradiated to the nail crease to avoid burning human skin.

In one example, as shown in FIG. 5 , the light intensity adjustment device may include a shading 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 left between the light-outlets, and the shading plate can move along the light-outlet to change the size of the light-transmitting hole. When the size of the light-transmitting hole is smaller, the larger area of the detection light emitted by the detection light emitter is blocked by the light shielding plate, so that the power of the detection light emitted to the detection light transmission device is also smaller. When the size of the light-transmitting hole is larger, the area where the detection light emitted by the detection light emitter is blocked by the light shield is smaller, so that the power of the detection light emitted to the detection light transmission device is also larger.

In another example, continuing to refer to FIG. 5 , the light intensity adjustment device may include an optical filter, and the optical filter may be disposed on the same optical axis as the detection light emitter. After the detection light emitted by the detection light emitter reaches the filter, the filter can be used for dimming treatment according to the corresponding dimming ratio, and then the dimming detection light can be irradiated to the nail crease. Among them, multiple light reduction ratios can be preset in the filter, and the corresponding light reduction ratio can be determined according to the detection optical power required to measure the blood sugar in the nail fold and the detection optical power emitted by the detection optical transmitter. When the dimming effect corresponding to the current dimming ratio is too small, and the detection light may burn human skin, you can adjust the dimming ratio to the next level. The dimming effect corresponding to the current dimming ratio is too large. When the detection light cannot irradiate the blood in the blood vessels, the light reduction ratio can be reduced to the previous level. In order to improve the sensitivity of filter dimming, you can set the filter to 8-segment Neutral Density (ND) dimming filter. The 8-segment dimming filter has 8 dimming ratios, and the dimming ratio of each stage can be reduced. 400mW of power.

In yet another example, continuing to refer to as shown in FIG. 5 , the light intensity adjusting device may include both a light shield and an optical filter. In this way, when the light intensity adjustment effect of one of the components is not good, the light intensity can be adjusted together through the cooperative operation of the other component. Due to the synergistic dimming of the shading plate, in this implementation manner, the optical filter can be set as an optical filter with a smaller dimming ratio, so as to reduce the cost of the optical filter.

In an optional implementation manner, continuing to refer to FIG. 5 , the detection light transmission device may include a second reflection mirror and a third reflection mirror arranged side by side, and the optical axes of the second reflection mirror and the third reflection mirror are parallel, The central axis of the second reflecting mirror is set directly below the light exit port of the detection light emitter, and the central axis of the third reflecting mirror is set on the first optical path L1. Wherein, the detection light emitted by the detection light transmitter can be first reflected to the fourth optical axis (L4) perpendicular to the first optical axis L1 through the second reflection mirror, and then transmitted to the third reflection mirror along the fourth optical axis L4, Further, it is reflected to the first optical axis L1 by the third reflecting mirror, and then transmitted to the nail fold through the switching mirror arranged on the first optical axis L1. In the embodiment of the present application, when the wavelength of the detection light is 785 nm, the detection light can pass through the skin dermis at the nail fold and enter the blood at the nail fold. Raman scattered light and Rayleigh scattered light will be generated after the blood sugar in the blood is excited by the detection light. After the Raman scattered light and Rayleigh scattered light are focused by the objective lens, they are transmitted along the opposite direction of the first optical path L1.

In an optional embodiment, continuing to refer to FIG. 5 , the detection unit may further include a beam splitter, the central axis of the beam splitter is located on the first optical axis L1, the central axis of the beam splitter and the center of the edge filter The straight line on which the axis is located is perpendicular to the first optical axis L1. In the embodiment of the present application, if the wavelength of the detection light used to irradiate the nail fold is 785 nm, after the detection light of this wavelength is scattered by blood sugar, the wavelength of the corresponding Rayleigh scattered light is also 785 nm. In this case, in order to For better filtering of Rayleigh scattered light, the edge filter can be set to a 785nm edge filter, and the cut-off point of the edge filter can be set to 5nm. In this way, the Raman scattered light and Rayleigh scattered light focused on the objective lens are first transmitted to the beam splitter, and the beam splitter divides the light of each wavelength into different paths and then transmits it to the edge filter, and then the edge filter The Rayleigh scattered light whose wavelength is in the range of 780 nm to 790 nm is filtered out, and only the Raman scattered light of other wavelengths is retained.

In an optional implementation manner, continuing to refer to FIG. 5 , the detection unit may further include a signal confocal device, the signal confocal device is arranged on the optical path of the edge filter and the spectroscopic device, and the signal confocal device may include A first lens, a confocal aperture and a second lens. Wherein, the confocal hole may be a plate-like structure with a central opening. The first lens, the confocal aperture 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 can be collected and focused on the confocal hole through the first lens, and then passed through the central opening of the confocal hole. It is transmitted to the second lens, and finally scattered by the second lens to the beam splitting device. The Raman scattered light before the confocal treatment is relatively scattered. By using a signal confocal device to perform the confocal treatment on the Raman scattered light, the Raman scattered light can be converted into a relatively concentrated Raman scattered light.

In an optional implementation manner, continuing to refer to as shown in FIG. 5 , the light splitting device may include a grating and a second prism. Wherein, the grating can be a plate-like structure, and the width of the plate-like structure needs to be larger than the width of the second prism, and the grating can also be called a beam splitter. Exemplarily, in order to improve the spectral accuracy of the grating, the wave number range of the grating may be set to 0˜1/3200 cm, and the scribe line density may be set to 1200 scribes per millimeter. In this way, after the second lens transmits the confocal Raman scattered light to the grating, the light of different wavelengths in the Raman scattered light appears at different positions through the grating to form a Raman spectrum, and finally the Raman spectrum is regenerated. It is transmitted from the second prism to the spectral detection device.

FIG. 7 exemplarily shows a Raman spectrogram. As shown in FIG. 7 , the abscissa of the Raman spectrogram is the Raman shift, and the unit is the wavenumber, and the ordinate of the Raman spectrogram is the intensity of the Raman scattered light, The unit is mW. Among them, the Raman spectrum can include multiple spectral lines, each spectral line corresponding to a wavelength, the spectral line is caused by the interaction between the vibration of a certain substance in the blood and the Rayleigh scattered light, such as cholesterol, glucose ( or blood sugar), fat (or blood lipid), hemoglobin, etc. The spectral lines corresponding to each wavelength shown in FIG. 7 have signal characteristic peaks of the same wavenumber. In other possible examples, spectral lines corresponding to different wavelengths may also have signal characteristic peaks of different wavenumbers.

In the embodiment of the present application, after acquiring the Raman spectrum corresponding to the current blood, the spectral detection device can obtain the characteristic peak intensity of glucose and the characteristic peak intensity of hemoglobin according to the Raman spectrum, then divide and calculate to obtain the relative intensity of the glucose peak, and finally The current blood glucose concentration is obtained by comparing with the preset corresponding relationship between the relative intensity and concentration of the glucose peak. Wherein, the preset corresponding relationship between the relative intensity of the glucose peak and the concentration is obtained by measuring blood glucose in the blood of a normal person. Raman spectrum, according to the Raman spectrum to obtain the characteristic peak intensity of the normal person's glucose and the characteristic peak intensity of the normal person's hemoglobin, then divide and calculate the relative intensity of the normal person's glucose peak, and calculate the difference between the different glucose concentrations and the normal person's peak intensity. The ratio of the relative intensities of the glucose peaks obtains the preset corresponding relationship between the relative intensity of the glucose peak and the concentration, and the preset corresponding relationship between the relative intensity and the concentration of the glucose peak is subsequently used as the basis for quantitative measurement of the blood glucose concentration.

Based on the above content, FIG. 8 exemplarily shows an optical path processing method of a detection device provided by an embodiment of the present application. As shown in FIG. 8 , the method includes:

In step 801, the finger to be measured is placed on the test table, and the nail fold of the finger to be measured is aligned with the light outlet of the camera device.

In this embodiment of the present application, the user can select the finger to be measured by himself. Exemplarily, taking the finger to be measured as the ring finger of the right hand as an example, if a finger clamp as shown in FIG. 4A or FIG. 4B is set on the test bench, the user can directly insert the ring finger of the right hand into the finger clamp. In this case, , Since the position of the finger clamp and the position of the detection device are preset, the nail crease on the ring finger of the right hand can just be aligned with the light outlet of the camera device. If it is the finger clamp shown in FIG. 4B, and the opening of the finger clamp is small, the image captured by the camera directly corresponds to the local area of the nail crease, so the process of coarse adjustment of the position in the following steps 804 to 806 may not be necessary. Instead, the process of fine-tuning the position in steps 807 to 809 can be directly performed.

Step 802, start the detection device, and execute:

If the blood sugar at the location to be tested is measured, perform steps 803 to 810; or,

If the blood glucose at a random location is measured, step 811 and step 812 are performed.

Step 803, move the switching mirror to position A, the irradiating light emitted by the illuminating light emitter is irradiated to the nail fold of the finger to be measured through the illuminating light transmission optical path, and the detection light emitted by the detection light emitter is irradiated to the to-be-measured finger through the detection light transmission optical path. Measure the nail crease of the finger.

In an optional embodiment, when the switching mirror is located at the position A, the irradiating light transmission optical path includes: illuminating the irradiating light emitted by the illuminating light emitter and focusing the irradiating light in the wavelength range of 400 nm˜700 nm to a The first reflecting mirror is reflected to the switching mirror through the first reflecting mirror, and then reflected to the first optical path L1 by the switching mirror, and irradiates the nail fold along the first optical path L1. Correspondingly, when the switching mirror is located at position A, the detection light transmission optical path includes: after the detection light emitted by the detection light emitter is subjected to light reduction processing through the shading plate and the filter, it is converted into the required blood glucose test at the nail fold. The detection light with a wavelength of 785nm and a power of 20mW is transmitted to the second reflector, reflected by the second reflector to the third reflector, reflected by the third reflector to the switching mirror, and transmitted by the switching lens to the first reflector. An optical path L1 irradiates the nail fold along the first optical path L1.

In the embodiment of the present application, when the display unit is working, the illuminating light emitter can emit the illuminating light according to the first set frequency, and when the detection unit is working, the detection light emitter can emit the detection light according to the second set frequency Light. 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.

In step 804, the focal length of the objective lens is adjusted to a low magnification focal length, and the camera device periodically captures the current partial image of the nail fold under the irradiation of the irradiation light, and sends it to the display for display.

In this embodiment of the present application, the display may only display the current partial image of the nail fold. In this case, the user is also required to memorize the partial image of the location to be tested, so as to facilitate subsequent comparison. Alternatively, the display can also display the partial image of the location to be tested and the current partial image at the same time. In this way, the user does not need to memorize the partial image of the location to be tested, so even people with poor memory can accurately locate the location to be tested. The local area where the location is located, and it can also avoid the large randomness and error-prone problems that rely on the user's memory to find the local area where the location to be tested is located.

Fig. 9 exemplarily shows a manner of displaying an image based on a fingerprint identification device. As shown in Fig. 9, in an optional implementation manner, fingerprint identification can also be set at a position on the test bench used for pressing the belly of a finger device, the fingerprint identification device is connected to the display. In this case, when the user puts his finger on the test bench, the fingerprint identification device can collect the fingerprint information on the belly of the user's finger and send it to the display. Compare at least one pre-stored standard fingerprint information, find the standard fingerprint information that matches the user's fingerprint information from at least one standard fingerprint information, and after collecting the current image (partial image or capillary image), compare the current image with the The image of the position to be tested corresponding to the standard fingerprint information is simultaneously displayed on the display. If there is no standard fingerprint information matching the user's fingerprint information in the at least one standard fingerprint information, the display can perform an alarm processing, for example, displaying the information "the user's fingerprint is not recorded" on the display. With this embodiment, the same detection device can also be used to measure blood sugar for different users. In the case where images of the locations to be tested of multiple users are stored in the detection device, the fingerprint identification device is used to verify the user's identity. Differentiation enables the detection device to display the image corresponding to the currently measured user on the display, thereby helping to ensure that the measured blood glucose is the blood glucose of the currently measured user's location to be tested.

It should be noted that the above is only an optional implementation manner, and in another optional implementation manner, the fingerprint identification device can also be set at other positions of the test bench, for example, the fingerprint identification device can also be set in an untested The position where the belly of the finger is pressed, or it can also be set at the edge of the test bench to collect the fingerprint of the user's other hand. It can be understood that the fingerprint identification device can also be replaced with other biological information collection devices, such as palmprint collectors, iris collectors, etc., which are not limited.

Step 805, determine whether the position of the light spot where the detection light irradiates the nail fold in the current partial image is the same as the position of the light spot in the partial image of the position to be tested, if it is different, then go to step 806, if it is the same, go to step 807 .

In the embodiment of the present application, the light spot refers to the focus point after the detection light is irradiated on the human skin, and the position of the light spot corresponds to the position where the detection light is irradiated on the nail fold.

Step 806 , move the finger to change the position where the detection light is irradiated on the nail fold, and perform step 805 .

In the embodiment of the present application, during the movement of the finger, the position where the detection light is irradiated on the nail fold also changes, and therefore, the position of the light spot formed after the detection light is irradiated on the human skin also changes. In addition, the user can continue to view the current partial image displayed on the display while moving the finger, and stop moving the finger after the position of the light spot in the current partial image is the same as the position of the light spot in the partial image of the location to be tested.

In step 807, the focal length of the objective lens is adjusted to a high magnification focal length, and the imaging device periodically captures the current capillary image of the nail fold under the irradiation of illumination light, and sends the image to the display for display.

In an optional implementation manner, the display may only display the current capillary image of the nail fold. In this case, the user is also required to memorize the capillary image of the position to be tested for subsequent comparison. In another optional embodiment, the display can also display the capillary image of the position to be tested and the current capillary image at the same time. In this way, the user does not need to memorize the capillary image of the position to be tested. A good person can also accurately locate the location to be tested, and can avoid the random and error-prone problems of relying on the user's memory to find the location to be tested.

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 they are different, execute step 809. If they are the same, execute Step 810.

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

In the embodiment of the present application, the user can continue to view the current capillary blood vessel image displayed on the display while moving the finger. After the position of the light spot in the current capillary blood vessel image is the same as the position of the light spot in the capillary blood vessel image of the position to be tested , stop moving your finger.

Step 810: Raman scattered light and Rayleigh scattered light are generated after the blood at the position to be tested is excited by the detection light. The light is divided into different paths, and then the Rayleigh scattered light is filtered out by the edge filter, and only the Raman scattered light is retained, and the Raman scattered light is transmitted to the first lens. The first lens focuses the Raman scattered light on the confocal hole, and then transmits it to the second lens through the confocal hole, and is scattered by the second lens to the grating, and then the light of different wavelengths in the Raman scattered light is divided into different wavelengths through the grating. The second prism transmits the Raman spectrum to the spectral detection device, and the spectral detection device determines the current blood sugar at the location to be tested according to the Raman spectrum.

In an optional embodiment, the detection device may also be provided with a start measurement button. After adjusting the spot where the detection light is irradiated to the nail crease to the position to be tested, the user may press the start measurement button. In this case, the spectral detection device starts to acquire the Raman signal transmitted from the second prism, and determines the current blood sugar at the location to be tested according to the Raman signal. However, the current blood sugar determined each time by the spectral detection device is actually a real-time blood sugar. In order to improve the stability of blood sugar detection, each blood sugar detection process can last for 1 minute (that is, after the user presses the start measurement button, the spectral detection device It will continue to measure for 1 minute and then end), the spectral detection device can detect multiple current blood sugars in real time within this 1 minute, and then integrate the multiple current blood sugars detected within 1 minute, and use the integrated value as the blood sugar measured this time. . During this 1-minute period, the user can see the position of the spot where the detection light irradiates the nail fold in real time through the display. Therefore, once the spot is found to be different from the position to be tested, the user can move his finger to It is ensured as much as possible that the multiple current blood sugars measured in the one minute are the current blood sugars of the location to be tested, and the noise interference among the multiple current blood sugars is consistent. In this way, the signal-to-noise ratio of the integration based on the multiple current blood sugars measured in the one minute can be increased, and the blood sugar measured this time obtained by the integration can better indicate the blood sugar situation at the current location.

In the embodiment of the present application, the spectral detection device can also be connected to a display, and after the measurement is completed, the spectral detection device can send the blood glucose measured this time to the display, so that the display can display it to the user. Exemplarily, the display can also store the user's historical blood sugar. When displaying the blood sugar measured this time, the display can also display the user's historical blood sugar and the blood sugar measured this time to the user at the same time, so that the user can know his own blood sugar in time. Changes in blood sugar.

In step 811, the switching mirror is moved to position B, and the detection light emitted by the detection light emitter is irradiated to the nail fold through the detection light transmission optical path.

In an optional implementation manner, when the switching mirror is located at position B, the detection light transmission optical path includes: after the detection light emitted by the detection light emitter is subjected to light reduction processing through a light shield and a filter, the detection light is converted into a test light The detection light with a wavelength of 785nm and a power of 20mW required for blood sugar in the nail fold is transmitted to the second mirror, reflected by the second mirror to the third mirror, and then reflected by the third mirror to the first optical path L1 , and irradiate the nail fold along the first optical path L1.

In step 812, the blood at random positions is excited by the detection light to generate Raman scattered light and Rayleigh scattered light. The Raman scattered light and Rayleigh scattered light are collected by the objective lens and then transmitted to the spectroscope. The light is divided into different paths and then transmitted to the edge filter, where the Rayleigh scattered light is filtered out by the edge filter and only the Raman scattered light is retained, and the Raman scattered light is transmitted to the first lens. The first lens focuses the Raman scattered light on the confocal hole, and then transmits it to the second lens through the confocal hole, and the second lens scatters the light on the grating, and then the light of different wavelengths in the Raman scattered light is divided into different wavelengths through the grating. The Raman spectrum is formed by the second prism, and finally the second prism transmits the Raman spectrum to the spectrum detection device, and the spectrum detection device determines the current blood sugar at the random position according to the Raman spectrum.

It should be noted that the above embodiments only take the measurement of human blood sugar as an example to introduce the structure of the detection device. The light wavelength is set to 785nm, and the detection light of 785nm can penetrate the skin to 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 body components. For example, if the component to be measured is moisture or Natural Moisturizing Factors (NMF), since both moisture and NMF are located in the depth of the skin epidermis below 100 microns In the stratum corneum, the wavelength of the detection light emitted by the detection light emitter in the above example can be set to not greater than 500 nm, and the detection light of 500 nm can penetrate the skin until the stratum corneum, and extract the Raman scattering corresponding to moisture or NMF. Light. It can be seen that the detection device in this application can detect the content of components in human skin without invading human skin, which belongs to a non-invasive detection method in the true sense. Further, the detection device in this application also The component content at the same position can be detected multiple times, so that the change determined based on the component content detected multiple times can better reflect the real physical condition of the user.

The above are only specific embodiments of the present application, but the protection scope of the present application is not limited to this. Any person skilled in the art can easily think of changes or replacements within the technical scope disclosed in the present application, and should cover within the scope of protection of this application. Therefore, the protection scope of the present application shall be subject to the protection scope of the claims.

Claims (15)

1. A detection device, comprising a display unit and a detection unit, the display unit comprising an illuminating light emitter, an illuminating light transmission device, a camera and a display, and the camera is connected to the display; the illuminating light emitter for emitting illuminating light; The illumination light transmission device is used to transmit the illumination light so that the illumination light is irradiated to the object to be measured on the first optical path; The imaging device is used for photographing the object to be measured under the irradiation of the illuminating light, and sending the information obtained by photographing to the display for display; the display, for displaying the information, the information being used for instructing to move the object to be tested to the position to be tested; The detection unit is used to emit detection light, and transmit the detection light so that the detection light irradiates the object to be measured on the first optical path, and the detection light is generated after being excited by the object to be measured. The scattered light detects the object to be detected. 2 . The detection device according to claim 1 , wherein the object to be detected is blood sugar in the nail fold, and the information is used to indicate the position of the capillary in the nail fold and the detection light irradiated to the position of the capillary in the nail fold. 3 . The position of the light spot formed after the nail crease. 3 . The detection device according to claim 2 , wherein the display device further comprises a first prism, and the optical axis of the first prism is set at the point where the illumination light emitter emits to the illumination light transmission device. 4 . on the transmission light path of the irradiated light; The first prism is used for focusing the irradiating light not smaller than the first wavelength and not larger than the second wavelength emitted by the illuminating light emitter onto the illuminating light transmission device. 4 . The detection device according to claim 3 , wherein when the object to be detected is blood sugar in the nail fold, the first wavelength is 400 nm, and the second wavelength is 700 nm. 5 . 5 . The detection device according to claim 4 , wherein the wavelength of the detection light is 785 nm. 6 . 6. The detection device according to any one of claims 1 to 5, wherein the illumination light transmission device comprises a first reflection mirror and a switching mirror; The first reflecting mirror is facing the light outlet of the illuminating light emitter; the first reflecting mirror is used for reflecting the illuminating light emitted by the illuminating light emitter, and is perpendicular to the first reflecting light The second optical path of the optical path is emitted to the switching mirror; The switching mirror is located at the intersection of the first optical path and the second optical path, and the switching mirror is used for reflecting the illumination light emitted to the switching mirror to the first optical path. 7. The detection device according to claim 6, wherein the switching mirror is further used for: When the switching mirror is moved along the second optical path to a position other than the position of the intersection of the first optical path and the second optical path, the irradiation light emitted to the switching mirror is reflected to the second optical path. three light way; Wherein, 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. 8. The detection device according to any one of claims 2 to 7, wherein the object to be measured is blood sugar in nail folds; The imaging device includes a pair of objective lenses, and 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 first focal length. multiples of the bifocal length; The imaging device is configured 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 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 where the irradiation light is irradiated on the nail fold is the same as the local area corresponding to the position of the nail fold to be tested; When the focal length is the second focal length, use the pair of objective lenses to photograph the local area of the nail fold to obtain current capillary blood vessel information corresponding to the nail fold; the current capillary blood vessel information is used to instruct to move the nail fold so that the position of the light spot irradiated on the nail crease by the detection light 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 crease to be tested. 9. The detection device according to any one of claims 1 to 8, wherein the detection unit comprises a detection light emitter, a detection light transmission device, an edge filter, a spectroscopic device and a spectrum detection device; The detection light emitter is used to emit detection light; the detection light transmission device, configured to transmit the detection light so that the detection light irradiates the object to be measured on the first optical path; The edge filter is used to collect Raman scattered light and Rayleigh scattered light generated after the object to be tested is excited by the detection light, filter out the Rayleigh scattered light and leave only the Raman scattered light, transmitting the Raman scattered light to the spectroscopic device; the spectroscopic device, configured to perform spectral processing on the Raman scattered light to form a Raman spectrum, and transmit the Raman spectrum to the spectrum detection device; The spectral detection device is used for detecting the object to be detected according to the Raman spectrum. 10 . The detection device according to claim 9 , wherein the detection unit further comprises a beam splitter, the central axis of the beam splitter is located on the first optical axis, and the beam splitter filters toward the edge. 11 . The optical axis of the light transmitted by the optical device is perpendicular to the first optical axis; The spectroscope is used to transmit the detection light transmitted from the detection light transmission device to the spectroscope, and to transmit Raman scattering light and Rayleigh scattering generated after the object to be detected is excited by the detection light The light of each wavelength in the light is divided into different paths and transmitted to the edge filter; The edge filter is used for filtering out the Rayleigh scattered light on the path corresponding to the wavelength according to the wavelength corresponding to the Rayleigh scattered light. 11. The detection device according to claim 10, wherein the object to be measured is blood sugar of nail folds; The edge filter is a 785nm edge filter, and the cutoff point of the edge filter is 5nm. 12. The detection device according to any one of claims 9 to 11, wherein the detection unit further comprises a signal confocal device, and the signal confocal device is arranged on the edge filter and the On the transmission light path of the splitting device; The signal confocal device includes 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 for collecting the weak Raman scattered light transmitted by the edge filter and focusing on the confocal aperture; the confocal aperture for projecting the focused Raman scattered light onto the second lens; The second lens is used for scattering the Raman scattered light projected by the confocal aperture to the spectroscopic device. 13. A health detection device, characterized in that it comprises a test table, a base and the detection device according to any one of claims 1 to 12; the test table is arranged on the base; The light outlet is aligned with the test bench; The test bench is used to place the object to be tested; The detection device is used for irradiating the object to be measured by emitting illuminating light through the light outlet, and photographing the object to be measured under the irradiation of the illuminating light, and moving the object to be measured according to the information obtained by shooting to the to-be-tested position of the test table, and to detect the to-be-tested object moved to the to-be-tested position. 14. The health detection device according to claim 13, wherein the object to be measured is the blood sugar of the nail fold of the finger to be measured; a finger clamp is provided on the test table; The finger clamp is used to fix the finger to be measured on the test table. 15. The health detection device according to claim 14, wherein a fingerprint identification device is further provided on the test bench; The fingerprint identification device is used to collect the fingerprint information of the user; Wherein, 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 identify the finger to be measured Move to the position to be tested.

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