A device for non-invasive blood glucose detection

Abstract

The embodiment of the application discloses a blood glucose detection device for non-invasive blood glucose detection by using mid-infrared light. The device comprises a laser, an optical element, a graphene detector and a computing device. The laser is used to send mid-infrared light to a to-be-detected object. The optical element is used to focus the mid-infrared light reflected by the to-be-detected object on the graphene detector. The graphene detector is used to obtain the absorbance of the to-be-detected object to the mid-infrared light by using the property that the conductivity of graphene in the graphene detector is related to the carrier concentration, and send the absorbance to the computing device. The computing device is used to obtain the blood glucose concentration of the to-be-detected object according to the absorbance and the spectrum of the mid-infrared light. By using the property of the graphene detector, the mid-infrared blood glucose concentration detection at room temperature is realized, and the difficulty of the mid-infrared non-invasive blood glucose detection to go to the clinic is reduced.

Description

Technical Field

[0001] This application relates to the field of blood glucose detection, and more particularly to a non-invasive blood glucose detection device. Background Technology

[0002] With the improvement of people's living standards and the acceleration of the pace of life, the number of people suffering from diabetes, which ranks first among "diseases of affluence," has risen rapidly, and China has become a major country with diabetes.

[0003] For diabetic patients, blood glucose monitoring has become an essential part of life. To reduce the impact of blood glucose testing wounds on patients' lives, mid-infrared blood glucose meters have been developed. To ensure the accuracy of the detector, the mid-infrared detector in this device uses either a mercury cadmium telluride (MCT) detector or an indium antimonide (InSb) detector to detect the absorption spectrum and accurately calculate the patient's blood glucose concentration based on the characteristic glucose peaks in the absorption spectrum.

[0004] Because the measurement accuracy of MCT and InSb detectors is highly sensitive to ambient temperature, MCT detectors require temperatures as low as -65°C to achieve their specified detectability, while InSb detectors require temperatures as low as -200°C. These excessively harsh operating conditions limit the application and widespread adoption of mid-infrared blood glucose meters. Therefore, enabling mid-infrared blood glucose meters to operate at room temperature has become a major challenge for non-invasive blood glucose monitoring devices to reach the forefront of medical applications. Summary of the Invention

[0005] This application provides a blood glucose detection device for non-invasive blood glucose detection at room temperature. It utilizes the property that the conductivity of graphene in a graphene detector is related to the carrier concentration to obtain the absorption spectrum of mid-infrared light. The blood glucose concentration of the subject is determined based on the absorption spectrum, which reduces the stringent requirements of mid-infrared non-invasive blood glucose detection on ambient temperature and realizes non-invasive blood glucose detection using mid-infrared light at room temperature.

[0006] The first aspect of this application provides a blood glucose detection device, including: a laser, an optical element, a graphene detector, and a computing device;

[0007] A laser is used to send mid-infrared light towards the object being tested.

[0008] Optical elements used to focus mid-infrared light reflected from the object under test onto the graphene detector;

[0009] A graphene detector is used to obtain the absorbance of the analyte to mid-infrared light by utilizing the property that the conductivity of graphene in the graphene detector is related to the carrier concentration, and then send the absorbance to a computing device.

[0010] A computing device used to determine the blood glucose concentration of the analyte based on absorbance and the spectrum of mid-infrared light.

[0011] In the embodiments of this application, the vibrational absorption band of glucose molecules is located in the 8-11 μm mid-infrared band. The mid-infrared wavelength emitted by the laser is measured, and after reflection from the analyte, it is focused onto the surface of a graphene detector by an optical element. The graphene detector utilizes the property that graphene's conductivity is related to carrier concentration to obtain the absorbance of the analyte to mid-infrared light and sends this information to a computing device. The computing device, after obtaining the absorbance of the mid-infrared light, determines the blood glucose concentration of the analyte based on the absorbance and the spectrum of the mid-infrared light. The graphene detector can meet the measurement accuracy requirements without requiring stringent environmental conditions, reducing the application difficulty of non-invasive mid-infrared blood glucose detection devices.

[0012] In one possible implementation of the first aspect, the computing device is specifically used to: compare a first absorbance with reference concentration blood glucose data to obtain the blood glucose concentration of the analyte, wherein the first absorbance is the absorbance of a first beam in the absorbance.

[0013] In the embodiments of this application, after acquiring the absorbance of the analyte against mid-infrared light, the computing device compares the first absorbance with reference concentration blood glucose data. The reference concentration blood glucose data, as an empirical value, provides a correlation between the first absorbance and blood glucose concentration. The computing device can obtain the blood glucose concentration of the analyte by searching the first absorbance and reference concentration blood glucose data. By comparing the first absorbance with the reference concentration blood glucose data, a blood glucose concentration result with accuracy comparable to invasive blood glucose testing is obtained while reducing the risk of infection from the wound.

[0014] In one possible implementation of the first aspect, the first beam is the infrared characteristic fingerprint peak of glucose. In the embodiments of this application, by using the absorbance of the glucose characteristic fingerprint peak to determine blood glucose concentration, the influence of other substances on the blood glucose concentration detection results can be reduced, thereby improving the accuracy of blood glucose detection.

[0015] In one possible implementation of the first aspect, the first beam comprises at least two frequencies of 992 cm⁻¹. -1 1035cm -1 1080cm -1 1106cm -1 Or 1152cm -1 The beam;

[0016] The computing device is specifically used to: perform partial least squares regression analysis on the first absorbance to obtain the second absorbance, compare the second absorbance with the reference concentration blood glucose data of the first beam, and obtain the blood glucose concentration of the analyte.

[0017] In the embodiments of this application, the first beam, which serves as the sampling beam, includes at least two beams with a frequency of 992 cm⁻¹. -1 1035cm -1 1080cm -1 1106cm -1 Or 1152cm -1 The beamforming allows the computing device to use least squares regression analysis to calculate the first absorbance, obtaining a more accurate second absorbance. This second absorbance is then compared with reference blood glucose concentration data to obtain the blood glucose concentration of the analyte. Using least squares regression analysis to process the first absorbance reduces measurement errors, thus obtaining a blood glucose concentration of the analyte that is closer to its actual concentration.

[0018] In one possible implementation of the first aspect, a computing device is specifically used to subtract a third absorbance from a first absorbance to obtain a fourth absorbance, wherein the third absorbance is the absorbance of a second beam in the absorbance, and the second beam is a frequency band with no glucose absorption; and to compare the fourth absorbance with reference concentration blood glucose data of the first beam to obtain the blood glucose concentration of the analyte.

[0019] In the embodiments of this application, the computing device subtracts a third absorbance from the first absorbance to obtain a fourth absorbance. The third absorbance is the absorbance of the background beam, the second beam, which is a beam in which glucose is not absorbed. Subtracting the third absorbance from the first absorbance reduces the influence of impurities in the blood on the absorbance. The fourth absorbance is then compared with reference concentration blood glucose data to obtain the blood glucose concentration of the analyte. This further improves the accuracy of the blood glucose concentration of the analyte.

[0020] In one possible implementation of the first aspect, the frequency of the second beam is 1180 cm. -1 In the embodiments of this application, since the frequency is 1180cm... -1 The second beam does not absorb glucose at all, so by processing the second beam, the interference of other substances in the blood on blood glucose detection is reduced, thus improving the accuracy of blood glucose detection.

[0021] In one possible implementation of the first aspect, the mid-infrared light is a broadband mid-infrared wave. In the embodiments of this application, by using an infrared emitter to transmit broadband infrared waves, absorbance in different bands is obtained to plot the spectrum, reducing the time wastage and implementation complexity caused by multiple transmissions.

[0022] In one possible implementation of the first aspect, the wavelength of the mid-infrared light is 8-11 μm. In the embodiments of this application, by emitting a wavelength of 8-11 μm, both glucose-sensitive and glucose-insensitive bands are fully covered, which can reduce the sampling frequency and improve the efficiency of blood glucose detection.

[0023] In one possible implementation of the first aspect, the test object is a human body surface. Specifically, it can be a part of the body containing blood glucose information, such as the arm, fingers, or eyeball. In the embodiments of this application, the test object is a human body surface, which can be directly tested through contact without causing trauma to the human body, thus reducing the risk of infection from wounds.

[0024] In one possible implementation of the first aspect, the optical element is in contact with the analyte. In embodiments of this application, contact between the optical element and the analyte increases the collected light beam, thereby obtaining more absorbance information to aid in calculating the blood glucose concentration of the analyte.

[0025] In one possible implementation of the first aspect, the laser comes into contact with the analyte. In the embodiments of this application, by having the laser come into contact with the analyte, the attenuation of mid-infrared light in the environment is reduced, thereby obtaining absorbance information that is easier to collect and detect, thus improving the accuracy of calculating the blood glucose concentration of the analyte.

[0026] In one possible implementation of the first aspect, a mid-infrared optical fiber is provided between the laser and the object under test (DUT), which is used to conduct the mid-infrared light emitted by the laser to the surface of the DUT. In the embodiments of this application, by conducting the mid-infrared light emitted by the laser to the surface of the DUT via a mid-infrared optical fiber, it is not necessary to directly position the laser output port to the DUT when setting up the laser, thus adding more possibilities to the structural design of the device.

[0027] In one possible implementation of the first aspect, a mid-infrared optical fiber is provided between the optical element and the graphene detector. This mid-infrared optical fiber is used to transmit the mid-infrared light focused out of the optical element to the graphene detector. In the embodiments of this application, by transmitting the mid-infrared light focused by the optical element to the graphene detector through the mid-infrared optical fiber, the graphene detector can obtain the focused mid-infrared light without being directly facing the optical element during setup, adding more possibilities to the structural design of the device.

[0028] In one possible implementation of the first aspect, the laser includes an external cavity tunable quantum-level laser and a carbon dioxide laser.

[0029] In one possible implementation of the first aspect, the optical element is a prism, a mid-infrared fiber, or an integrating sphere.

[0030] In one possible implementation of the first aspect, the prism is a zinc sulfide prism, a zinc selenide prism, a chromium prism, or a silicon prism. Attached Figure Description

[0031] Figure 1 A schematic diagram of a blood glucose detection device provided in an embodiment of this application;

[0032] Figure 2 This is a schematic diagram of an absorption spectrum for blood glucose detection provided in an embodiment of this application;

[0033] Figure 3 A reference schematic diagram of reference blood glucose concentration data provided in the embodiments of this application;

[0034] Figure 4 Another schematic diagram of the blood glucose detection device provided in the embodiments of this application;

[0035] Figure 5 This is a schematic diagram of the structure of a wristband provided in an embodiment of this application;

[0036] Figure 6 This is a schematic diagram of a portable blood glucose testing device provided in an embodiment of this application. Detailed Implementation

[0037] This application provides a blood glucose detection device for non-invasive blood glucose detection at room temperature, realizing non-invasive blood glucose detection using mid-infrared light at room temperature.

[0038] The terms "first," "second," etc., used in the specification, claims, and accompanying drawings of this application are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such terms are interchangeable where appropriate; this is merely a way of distinguishing objects with the same attributes in the embodiments of this application. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover non-exclusive inclusion, so that a process, method, system, product, or apparatus that comprises a series of elements is not necessarily limited to those elements, but may include other elements not explicitly listed or inherent to those processes, methods, products, or apparatuses.

[0039] Before introducing the embodiments of this application, a brief introduction to mid-infrared non-invasive blood glucose detection technology will be given first, so as to better understand the solution proposed in this application.

[0040] Optical detection methods based on mid-infrared spectroscopy are among the most promising non-invasive blood glucose detection technologies. They utilize the vibrational absorption of glucose molecules in the 8-11 μm wavelength range. By measuring the changes in the absorption peaks of mid-infrared light after passing through glucose, and then determining the correlation between glucose concentration and absorption peaks, the blood glucose concentration of the analyte can be obtained. Furthermore, there are wavelengths in the 8-11 μm range that are insensitive to glucose, which can be used to remove background impurities in the blood, further improving the accuracy of blood glucose detection.

[0041] In the currently common mid-infrared non-invasive blood glucose detection methods, a tunable laser emits mid-infrared light to the human body surface. After being absorbed and reflected by the vibration of glucose molecules in the subcutaneous tissue, a portion of the reflected light is focused by optical elements and received by a detector and sent to a computing device. The computing device processes the infrared spectrum obtained from the detection and, based on the correlation between absorbance and glucose concentration obtained from the experiment, determines the blood glucose concentration of the human body.

[0042] To ensure accuracy, existing technologies use MCT or InSb detectors to collect mid-infrared light reflected from the human body. However, MCT detectors can only achieve 10 kHz accuracy at a detection temperature of -65°C. 9 cmHz 1 / 2 W -1 The detection rate of InSb detectors is only achieved at a detection temperature of -200℃. This environmental requirement has become the most difficult hurdle for mid-infrared non-invasive blood glucose monitoring devices to overcome in clinical applications.

[0043] Based on the above principles and solutions, in order to solve the problem of the difficulty in clinical application of mid-infrared non-invasive blood glucose detection devices, this application proposes to use a graphene detector as an infrared light detector to collect mid-infrared light reflected or scattered by the human body, and to transmit the absorbance of the analyte to a computing device, so that the computing device can use the absorbance of the analyte to refer to the experimentally obtained correspondence between absorbance and glucose concentration to obtain the blood glucose concentration of the analyte.

[0044] Specifically, due to the sensitive conductivity of graphene itself changing with carrier density, the temperature change caused by glucose vibration absorbing energy can excite changes in carriers, thereby inducing changes in the conductivity of graphene, ultimately revealing the absorbance of the analyte. This enables the detection of mid-infrared light at room temperature, achieving the goal of non-invasive blood glucose detection using mid-infrared light at room temperature.

[0045] Based on the above ideas, the blood glucose detection device provided in this application will be described in detail below. Please refer to... Figure 1 , Figure 1This is a schematic diagram of a blood glucose detection device provided in an embodiment of this application.

[0046] The blood glucose detection device 10 includes: a laser 101, an optical element 102, a graphene detector 103, and a computing device 104.

[0047] Laser 101 sends a broadband mid-infrared wave to the object under test 105. Using an external grating, laser 101 emits wavelengths within a range of 8-11 μm. The output power of the laser is adjusted between 0-350 mW, resulting in a pulsed light modulation frequency between 0.1-100 kHz. In practical applications, the modulation frequency is typically increased to reduce measurement errors caused by instantaneous changes in displacement and temperature.

[0048] Optionally, the laser 101 can be an external cavity tunable quantum-level laser or a carbon dioxide laser. It should be noted that the specific type of laser is not limited in this application embodiment, as long as it can emit infrared light with a wavelength of 8-11 μm.

[0049] Optical element 102 is disposed near the object to be tested 105 and is used to focus the mid-infrared light reflected by the object to be tested onto graphene detector 103.

[0050] It should be noted that the optical element 102 can be a prism, an integrating sphere, or a mid-infrared fiber, and the prism can be made of materials capable of total internal reflection, such as zinc sulfide, zinc selenide, chromium, or silicon. The types of optical elements described in this embodiment are merely examples, and in practical applications, they are not limited to the optical elements mentioned above.

[0051] After receiving the mid-infrared light focused by the optical element 102, the graphene detector 103 uses the characteristic that the conductivity of graphene is highly sensitive to the carrier concentration to obtain the absorbance of glucose molecules in the analyte 105 to the mid-infrared light, and sends the absorbance to the computing device 104.

[0052] In a possible implementation, the graphene detector includes an infrared absorption layer, an insulating layer, an electrode layer, a graphene layer, a pyroelectric thin film layer, and a support layer. Mid-infrared light is absorbed by glucose molecules in the analyte. The reflected light is focused by optical element 102 and enters the infrared absorption layer of the graphene detector 103. The reflected light is absorbed by the infrared absorption layer and reaches the surface of the pyroelectric thin film layer, generating polarized charges. These polarized charges then reach the graphene layer. Utilizing the high sensitivity of graphene's conductivity to changes in carrier concentration, room-temperature detection of mid-infrared light is achieved. This detection mode can operate at room temperature, and the corresponding wavelength can cover the entire 900-1250 cm⁻¹ wavelength range. -1 The detection rate can reach 10 in the 8-11 μm band. 9 cmHz1 / 2 W -1 .

[0053] After receiving the absorbance from the graphene detector 103, the computing device 104 combines the absorbance with the spectrum of mid-infrared light to obtain the blood glucose concentration of the analyte.

[0054] There are several ways to obtain the blood glucose concentration of the analyte by combining the absorbance and mid-infrared light spectrum. The specific methods for obtaining the blood glucose concentration of the analyte will be introduced below, based on the absorbance and mid-infrared light spectrum collected by the computing device 104 and the reference diagram of absorbance and blood glucose concentration of the analyte.

[0055] Please see Figure 2 and Figure 3 , Figure 2 This is a schematic diagram of an absorption spectrum for blood glucose detection provided in an embodiment of this application; Figure 3 This is a reference schematic diagram illustrating reference blood glucose concentration data provided in the embodiments of this application. The specific method for obtaining blood glucose concentration is described below with reference to these two diagrams:

[0056] Figure 2 The spectrum contains multiple spectral peaks, including one at a wavelength of 1152 cm⁻¹. -1 The characteristic peak of the pyran ring has a wavelength of 1106 cm⁻¹. -1 The carbonyl characteristic peak has a wavelength of 1080 cm⁻¹. -1 The characteristic peaks of hydrocarbons are at a wavelength of 10355 cm⁻¹. -1 The characteristic peak of C4-OH and the wavelength are 992 cm⁻¹ -1 The characteristic peaks of hydroxymethyl groups. These peaks are characteristic fingerprint peaks of glucose molecules and can be used to detect the glucose content in the blood.

[0057] Figure 3 In the reference diagram of the reference blood glucose concentration data, it can be seen that when the wavelength of the first beam is 1080cm... -1 If the absorbance of the analyte is 0.033, the blood glucose concentration is 143 mg / dL; if the absorbance is 0.024, the blood glucose concentration is 112 mg / dL; if the absorbance is 0.016, the blood glucose concentration is 90 mg / dL; and if the absorbance is 0.013, the blood glucose concentration is 78 mg / dL.

[0058] It is important to note that Figure 3 The data shown is only from reference blood glucose concentration data, with a wavelength of 1080 cm⁻¹. -1The relationship between absorbance and blood glucose concentration is shown as an example. This data is empirical data obtained from experiments and can be continuously revised according to needs and the amount of experimental data in practical applications. The relationship between absorbance and blood glucose concentration of other glucose fingerprint peaks is similar and is not specifically limited here.

[0059] Based on the above data and conclusions, this application proposes the following methods for obtaining the blood glucose concentration of the analyte by measuring its absorbance and the spectrum of mid-infrared light:

[0060] 1. Obtain the blood glucose concentration of the analyte using the comparison method.

[0061] Because different functional groups in glucose are sensitive to different wavelengths of mid-infrared light, a segment of the first beam can be extracted from the absorption spectrum of mid-infrared light to determine the absorbance of the first beam. The first beam can be a wavelength of 992 cm⁻¹. -1 1035cm -1 1080cm -1 1106cm -1 Or 1152cm -1 The arbitrary beam, i.e., the first beam, can be the infrared characteristic fingerprint peak of glucose. After determining the wavelength and corresponding absorbance of the first beam, the computing device 104 can obtain a relatively accurate glucose concentration of the analyte based on the correspondence between the reference data provided by the reference glucose concentration data.

[0062] In this embodiment, a graphene detector is used instead of a conventional MCT detector. Utilizing the different characteristics of graphene and MCT detectors, high-precision blood glucose detection is achieved at room temperature. This allows non-invasive mid-infrared blood glucose detection technology to be applied in a room-temperature environment.

[0063] 2. Establish a mathematical model to obtain the blood glucose concentration of the analyte.

[0064] Based on the method for obtaining the blood glucose concentration of the analyte provided in Method 1, this method proposes that the first beam may include at least two beams with a frequency of 992 cm⁻¹. -1 1035cm -1 1080cm -1 1106cm -1 Or 1152cm -1 The beam is adjusted so that the computing device 104 can perform partial least squares regression analysis on the two values ​​of the first absorbance to obtain the second absorbance after removing interference factors. The obtained second absorbance is compared with the reference data provided by the reference blood glucose concentration data to obtain the blood glucose concentration of the analyte.

[0065] In this embodiment, a second absorbance is obtained by performing least-squares regression analysis on multiple glucose-sensitive infrared fingerprint peaks obtained from measurements. This second absorbance, after deducting the influence of some measurement-related interference factors on the test results, is then compared with reference data provided by reference blood glucose concentration data to obtain the blood glucose concentration of the analyte. Through mathematical model calculations, the influence of measurement-related interference factors on blood glucose detection results is reduced, thereby improving the accuracy of blood glucose detection.

[0066] 3. Remove impurities from the analyte to obtain the blood glucose concentration of the analyte.

[0067] Based on method 1 or method 2, this method proposes that the computing device 104 can also collect the absorbance of a beam in the glucose-insensitive band from the absorption spectrum of mid-infrared light, namely the absorbance of the second beam, the wavelength of which can be 1180 cm⁻¹. -1 Subtracting the third absorbance from the first absorbance yields a fourth absorbance, which reflects impurities in the blood, including albumin, acetate, lactic acid, urea, and cholesterol. This fourth absorbance is then compared to reference data provided by a reference blood glucose concentration database to determine the blood glucose concentration of the analyte.

[0068] In this embodiment, a fourth absorbance is obtained by subtracting the third absorbance caused by other impurities in the blood from the first absorbance that is sensitive to glucose. The fourth absorbance is then compared with reference data provided by reference blood glucose concentration data to obtain the blood glucose concentration of the analyte. By subtracting the third absorbance of the second beam that is not sensitive to glucose, the impact of other impurities in the blood on the accuracy of blood glucose detection is reduced, further improving the accuracy of blood glucose detection.

[0069] It should be noted that the above method for obtaining the blood glucose concentration of the analyte by means of absorbance and mid-infrared light spectrum is only an example and does not limit the specific calculation method. In practical applications, it can be adjusted according to specific needs.

[0070] Optionally, the computing device 104 may also include a lock-in amplifier for removing noise signals and amplifying the electrical signals received from the graphene detector. (900-1250cm) -1 The band, every 2cm -1 Collect a data point and collect data at least 50 times. Take the average value of the collected data and use this average value as the basis for obtaining the blood glucose concentration of the analyte.

[0071] Optionally, the object to be tested can be any area of ​​the human body with blood vessels, such as the skin or eyeball. Since mid-infrared light has poor penetrability, and the stratum corneum of the inner lip mucosa or earlobe is relatively thin, the preferred human body surface is the inner lip mucosa or earlobe surface. The specific location of the object to be tested is not limited in this application embodiment.

[0072] This application provides an implementation of the solution under relatively ideal conditions. Typically, the placement of components in a device may be limited by the device's space or unavoidable space-avoidance issues in other structural designs. Therefore, the blood glucose detection device provided in this application is difficult to implement according to... Figure 1 The positional relationships shown are set accordingly. The following will combine... Figure 4 Another possible implementation of the embodiments of this application will be described. Figure 4 Another schematic diagram of the blood glucose detection device provided in the embodiments of this application;

[0073] Different from Figure 1 The blood glucose detection device shown has a mid-infrared light emitted by laser 10, which is guided to the test object 105 by a mid-infrared optical fiber. After being reflected by the test object 105, the light is focused by optical element 20 and transmitted to the graphene detector 103 through the mid-infrared optical fiber. The graphene detector 103 collects the data and sends it to the computing device 104 for processing to obtain the blood glucose concentration of the test object.

[0074] It should be noted that in practical applications, the mid-infrared optical fiber between the laser 101 and the object under test 105 can be in contact with the object under test 105 or not in direct contact with the object under test. Figure 4 The positions shown are for illustrative purposes only. In actual applications, they should be implemented according to specific scenarios.

[0075] On the other hand, the object under test 105 and the optical element 102 may or may not be in contact in practical applications. Figure 4 The positional relationships shown are for illustrative purposes only. In practical applications, they should be implemented according to the specific scenario.

[0076] In this embodiment, mid-infrared optical fiber is used to guide mid-infrared light to any desired location, which improves the flexibility of the placement of various components of the blood glucose detection device and makes it possible to apply this solution to more scenarios.

[0077] Considering the practicality of the solution provided in this application, the following is a brief introduction to the solution proposed in this application based on the aforementioned blood glucose detection device and in combination with different application scenarios:

[0078] Please see Figure 5 , Figure 5This is a schematic diagram of a wristband provided in an embodiment of this application. The wristband 60 includes a blood glucose detection device 10, a wristband 501, and a display screen 502. The wristband 501 is used to fix the wristband 50 to the object being tested 105, i.e., the wrist. The display screen 502 is in contact with the wristband 501 and is fixed by the wristband. The blood glucose detection device 10 is disposed below the display screen 502, in contact with the wrist or at a certain distance from the wrist.

[0079] The inner surface of the wristband 50 contacts the wrist. The blood glucose detection device 10 sends mid-infrared light to the wrist and receives the mid-infrared light reflected back from the wrist surface. The computing device in the blood glucose detection device 10 analyzes the absorbance of the wrist to the mid-infrared light and the spectrum of the mid-infrared light to calculate the user's blood glucose concentration. The blood glucose concentration result is then displayed to the user on the display screen 502. When using the wristband, after the user wears the wristband, blood glucose is sampled at preset time intervals to achieve blood glucose testing at fixed times every day. Alternatively, the blood glucose testing function can be activated at any time the user needs to perform blood glucose testing.

[0080] Optionally, the wristband 50 can also establish a wireless connection with devices such as mobile phones and computers equipped with wireless modules, allowing the mobile phone or computer to control the wristband for non-invasive blood glucose testing via wireless connection. This application embodiment only provides a brief introduction to the possible blood glucose test result output methods that the wristband may use; in practical applications, the specific method of displaying blood glucose test results to the user is not limited.

[0081] In this embodiment of the application, it is proposed that the blood glucose detection device can be set inside the wristband, so that users can perform non-invasive blood glucose detection at any time as needed after wearing the wristband provided in this embodiment of the application, which provides greater convenience for the daily blood glucose monitoring of the majority of diabetic patients.

[0082] Please see Figure 6 , Figure 6 This is a schematic diagram of a portable blood glucose testing device provided in an embodiment of this application. The portable blood glucose testing device includes: a blood glucose testing device 10 and a gripper structure 601.

[0083] The blood glucose detection device 10 is positioned above the gripper structure 601. The device 10 sends mid-infrared light to the test object 105 and receives mid-infrared light reflected from the surface of the test object 20. The computing device within the blood glucose detection device 10 analyzes and calculates the absorbance and spectrum of the mid-infrared light from the test object 105 to obtain the user's blood glucose concentration. The gripper structure 601 is fixed to the blood glucose detection device 10 via a hardware connection. This gripper structure is used to fix the blood glucose detection device 10 to the test object 105 during blood glucose testing. The test object 105 can be a finger, ear, or other location on the human body that is convenient for the gripper to fix.

[0084] Optionally, the portable blood glucose testing device may be equipped with a wireless communication module, which can establish a wireless connection with devices such as mobile phones and computers that also have wireless modules. The mobile phone or computer can then control the wristband for non-invasive blood glucose testing via this wireless connection. Alternatively, the device can output the blood glucose concentration of the analyte to the user at any time via various electrical interfaces. This application only briefly introduces the possible methods of outputting blood glucose test results using the portable blood glucose testing device; in practical applications, the specific method of displaying blood glucose test results to the user is not limited.

[0085] In this embodiment of the application, it is proposed that the blood glucose testing device can be placed on top of the gripper structure, so that users can clamp the portable blood glucose testing device on their fingers or other parts of their body anytime and anywhere to perform blood glucose testing, which greatly facilitates the daily blood glucose testing of users.

[0086] In the several embodiments provided in this application, it should be understood that the disclosed systems, apparatuses, and methods can be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative; for instance, the division of units is only a logical functional division, and in actual implementation, there may be other division methods. For example, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Furthermore, the coupling or direct coupling or communication connection shown or discussed may be an indirect coupling or communication connection between apparatuses or units through some interfaces, and may be electrical, mechanical, or other forms.

[0087] The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the units can be selected to achieve the purpose of this embodiment according to actual needs.

[0088] Furthermore, the functional units in the various embodiments of this application can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit.

[0089] If the integrated unit is implemented as a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause a computer device (which may be a personal computer, server, or network device, etc.) to execute all or part of the steps of the methods described in the various embodiments of this application. The aforementioned storage medium includes various media capable of storing program code, such as USB flash drives, portable hard drives, read-only memory (ROM), random access memory (RAM), magnetic disks, or optical disks.

Claims

1. A blood glucose detection device, characterized in that, include: Lasers, optical components, graphene detectors, and computing devices; The laser is used to send mid-infrared light to the object under test; The optical element is used to focus the mid-infrared light reflected by the object under test onto the graphene detector; The graphene detector is used to obtain the absorbance of glucose molecules in the analyte to the mid-infrared light by utilizing the property that the conductivity of graphene in the graphene detector is related to the carrier concentration, and to send the absorbance to the computing device. The computing device is used to obtain the blood glucose concentration of the analyte based on the absorbance and the spectrum of the mid-infrared light. The graphene detector includes an infrared absorption layer, a pyroelectric thin film layer, and a graphene layer. Specifically, the graphene detector is used to generate polarized charges on the surface of the pyroelectric thin film layer after the mid-infrared light is absorbed by the infrared absorption layer. After the polarized charges reach the graphene layer, the absorbance of glucose molecules in the analyte to the mid-infrared light is obtained by utilizing the property that the conductivity of the graphene is related to the carrier concentration.

2. The apparatus according to claim 1, characterized in that, The computing device is specifically used for: By comparing the first absorbance with the reference concentration blood glucose data, the blood glucose concentration of the analyte is obtained, where the first absorbance is the absorbance of the first beam in the absorbance.

3. The apparatus according to claim 2, characterized in that, The first beam is the infrared characteristic fingerprint peak of glucose.

4. The apparatus according to claim 3, characterized in that, The first beam includes at least two frequencies of 992 cm⁻¹. -1 1035cm -1 1080cm -1 1106cm -1 Or 1152cm -1 The beam; The computing device is specifically used for: Partial least squares regression analysis is performed on the first absorbance to obtain the second absorbance. The second absorbance is then compared with the reference concentration blood glucose data to obtain the blood glucose concentration of the analyte.

5. The apparatus according to any one of claims 2 to 4, characterized in that, The computing device is specifically used to subtract the third absorbance from the first absorbance to obtain the fourth absorbance, wherein the third absorbance is the absorbance of the second beam in the absorbance, and the second beam is a frequency band in which there is no glucose absorption. By comparing the fourth absorbance with the reference concentration blood glucose data, the blood glucose concentration of the analyte is obtained.

6. The apparatus according to claim 5, characterized in that, The frequency of the second beam is 1180cm. -1 .

7. The apparatus according to any one of claims 1 to 4, characterized in that, The mid-infrared light is a broadband mid-infrared wave.

8. The apparatus according to any one of claims 1 to 4, characterized in that, The wavelength of the mid-infrared light is 8-11 μm.

9. The apparatus according to any one of claims 1 to 4, characterized in that, The object to be tested is the surface of the human body.

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