Noninvasive blood glucose detection system

Abstract

The embodiment of the invention discloses a noninvasive blood glucose detection system. The system comprises an optical transceiver assembly; the filtering unit is electrically connected with the optical transceiver assembly; the micro-processing unit is electrically connected with the filtering unit; wherein the optical transceiver assembly comprises at least two light sources, a first detector and at least two second detectors, the at least two light sources are used for emitting laser detection signals, and the first detector and the at least two second detectors are used for detecting returned laser signals; the at least two light sources are arranged around the first detector; the at least two second detectors are arranged around the light source; the light detection surface of the first detector, the light detection surfaces of the at least two second detectors and the light emitting surfaces of the at least two light sources face the same direction. According to the application, the short-optical-path optical signal and the long-optical-path optical signal are used for data analysis and processing to obtain the optical concentration difference between the deep part and the superficial part of the skin, so that the influence of melanin and the skin is reduced, and the detection precision of noninvasive blood glucose is improved.

Description

Technical Field

[0001] The present application relates to the technical field of blood sugar detection, and in particular to a non-invasive blood sugar detection system. Background Art

[0002] Diabetes is a chronic disease caused by factors such as lack of insulin secretion or impaired insulin action, which leads to increased blood sugar concentration, resulting in acute or chronic complications. Diabetes is the third largest non-communicable disease after cardiovascular disease and cancer, and has become a global public health issue that seriously threatens human health. Under the current level of medical technology, there is no complete cure for diabetes, but studies have shown that continuous monitoring and control of patients' blood sugar levels can reduce or delay the occurrence of complications and improve patients' survival and quality of life.

[0003] At present, there are two ways of blood sugar testing: invasive and non-invasive. Invasive blood sugar testing generally requires blood sampling to obtain blood sugar concentration, but this type of blood sugar collection is point-like and cannot continuously and real-time track the changes in the patient's blood sugar concentration. In addition, invasive measurement requires biochemical reagents, high testing costs, and is prone to infection. At the same time, frequent blood sampling will also cause inconvenience and pain to patients. Therefore, non-invasive, non-invasive blood sugar testing is an ideal measurement method. However, existing non-invasive blood sugar detection devices all use light-emitting diodes (LEDs) to achieve optical non-invasive blood sugar detection, but the LED light source has a wide band and the light source is unstable, which makes it difficult to meet the high-precision requirements of blood sugar detection. Therefore, how to improve the detection accuracy of non-invasive blood sugar detection has become a problem that needs to be solved urgently. Summary of the invention

[0004] The embodiments of the present application provide a non-invasive blood glucose detection system to improve the detection accuracy of blood glucose detection.

[0005] In order to solve the above technical problems, the embodiments of the present application disclose the following technical solutions:

[0006] In one aspect, a non-invasive blood glucose detection system is provided, comprising:

[0007] Optical transceiver components;

[0008] a filtering unit, electrically connected to the optical transceiver assembly, the filtering unit being configured to filter the signal transmitted by the optical transceiver assembly; and

[0009] a microprocessing unit, electrically connected to the filtering unit, and configured to process a signal transmitted by the filtering unit;

[0010] The optical transceiver assembly includes: at least two light sources, a first detector and at least two second detectors, the at least two light sources are used to emit laser detection signals, and the first detector and at least two second detectors are used to detect the returned laser signals;

[0011] The at least two light sources are arranged around the first detector; the at least two second detectors are arranged around the light source;

[0012] The light detection surface of the first detector, the light detection surfaces of the at least two second detectors, and the light emitting surfaces of the at least two light sources face the same direction.

[0013] In addition to or as an alternative to one or more of the features disclosed above, the at least two light sources and the at least two second detectors are respectively arranged in an array on a circle with the first detector as the center.

[0014] In addition to or as an alternative to one or more features disclosed above, the first detector, the at least two second detectors and the at least two light sources are located on the same plane.

[0015] In addition to or as an alternative to one or more of the features disclosed above, the light source is configured to emit a laser signal toward the analyte;

[0016] The first detector is configured to detect short-path optical signals returned by the at least two light sources after being emitted toward the analyte;

[0017] The second detector is configured to detect the long optical path optical signals returned by the at least two light sources after being emitted toward the analyte.

[0018] In addition to one or more features disclosed above, or as an alternative, the distance between the first detector and the light source in the radial direction of the circle formed with the first detector as the center is L1 mm, and the distance between the second detector and the light source in the radial direction of the circle formed with the first detector as the center is L2 mm, satisfying: 0.5≤L1 / L2<1.

[0019] In addition to one or more of the features disclosed above, or as an alternative, the distance L1 mm between the first detector and the light source in the radius direction of a circle formed with the first detector as the center also satisfies: 0.5 mm ≤ L1 ≤ 5 mm; and / or,

[0020] A distance L2 mm between the second detector and the light source in the radius direction of a circle formed with the first detector as the center also satisfies: 0.5 mm<L2≤10 mm.

[0021] In addition to or as an alternative to one or more features disclosed above, the light sources of the at least two light sources have multiple wavelengths, and the wavelengths of the at least two light sources are λnm, satisfying: 800nm≤λ≤2600nm.

[0022] In addition to one or more of the features disclosed above, or as an alternative, the optical transceiver assembly also includes: at least two third detectors, the at least two third detectors are arranged around the second detector, the at least two third detectors are located in the same plane as the at least two second detectors, and the light detection surfaces of the at least two third detectors and the light detection surfaces of the at least two second detectors face the same direction.

[0023] In addition to one or more of the features disclosed above, or as an alternative, the number of the light sources is n1, satisfying: n1 ≥ 3; and / or,

[0024] The number of the second detectors is n2, satisfying: n2 ≥ 3; and / or,

[0025] The number of the third detectors is n3, satisfying: n3≥3.

[0026] In addition to or as an alternative to one or more of the features disclosed above, the invention further comprises: a data processing terminal electrically or wirelessly connected to the microprocessing unit, wherein the data processing terminal is configured to process a signal transmitted by the microprocessing unit; and

[0027] A driving control element is electrically or wirelessly connected to the optical transceiver assembly and the microprocessor unit, respectively, and is configured to control the on / off and working mode of the optical transceiver assembly.

[0028] One of the above technical solutions has the following advantages or beneficial effects: In the present application, multiple light sources are arranged around the first detector, and multiple second detectors are arranged around the light source, so that the light source is used to emit a laser signal from the surface of the part to be measured to the subcutaneous tissue, and the first detector detects the short-path light signal of the subcutaneous tissue from the surface of the part to be measured, and the second detector detects the long-path light signal of the subcutaneous tissue from the surface of the part to be measured, so that the short-path light signal and the long-path light signal are used to perform data analysis and processing to obtain the optical concentration difference between the deep and shallow parts of the skin, so as to reduce the influence of melanin and skin, improve the detection accuracy of non-invasive blood glucose, and ensure the accuracy of non-invasive blood glucose detection results. BRIEF DESCRIPTION OF THE DRAWINGS

[0029] The technical solution and other beneficial effects of the present application will be made apparent by describing in detail the specific implementation methods of the present application in conjunction with the accompanying drawings.

[0030] Figure 1 is a structural diagram of a non-invasive blood glucose detection system provided according to an embodiment of the present application;

[0031] Figure 2 This is a structural view of an optical transceiver assembly provided according to another embodiment of the present application.

[0032] Description of reference numerals:

[0033] 100. Non-invasive blood glucose testing system;

[0034] 110, optical transceiver assembly; 111, light source; 112, first detector; 113, second detector; 114, third detector;

[0035] 120. Filter unit;

[0036] 130. Microprocessing unit;

[0037] 140. Data processing terminal;

[0038] 150. Drive control element;

[0039] 200. Part to be tested. DETAILED DESCRIPTION

[0040] In order to make the purpose, technical solution and beneficial effects of this application more clear, the following further describes this application in detail in conjunction with the accompanying drawings and specific implementation methods. It should be understood that the specific implementation methods described in this specification are only for explaining this application, not for limiting this application.

[0041] In the description of the present application, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", "clockwise", "counterclockwise" and the like indicate positions or positional relationships based on the positions or positional relationships shown in the accompanying drawings, which are only for the convenience of describing the present application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as a limitation on the present application. In addition, the terms "first" and "second" are only used for descriptive purposes, and cannot be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Therefore, the features defined as "first" and "second" may explicitly or implicitly include one or more of the features. In the description of the present application, the meaning of "multiple" refers to two or more, unless otherwise clearly and specifically defined.

[0042] In the description of this application, it should be noted that, unless otherwise clearly specified and limited, the terms "installed", "connected", and "connected" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection, a direct connection, or an indirect connection through an intermediate medium, it can be the internal connection of two elements or the interaction relationship between two elements. For ordinary technicians in this field, the specific meanings of the above terms in this application can be understood according to specific circumstances.

[0043] In the present application, unless otherwise clearly specified and limited, a first feature being "above" or "below" a second feature may include that the first and second features are in direct contact, or may include that the first and second features are not in direct contact but are in contact through another feature between them. Moreover, a first feature being "above", "above" and "above" a second feature includes that the first feature is directly above and obliquely above the second feature, or simply indicates that the first feature is higher in level than the second feature. A first feature being "below", "below" and "below" a second feature includes that the first feature is directly above and obliquely above the second feature, or simply indicates that the first feature is lower in level than the second feature.

[0044] Reference Figure 1 to Figure 2 The present application provides a non-invasive blood glucose detection system 100. Specifically, the non-invasive blood glucose detection system 100 may include: an optical transceiver component 110, a filter unit 120, a microprocessor unit 130, a data processing terminal 140 and a drive control element 150. During detection, the optical transceiver component 110 is arranged on the surface of the part to be tested 200, the filter unit 120 is electrically or wirelessly connected to the optical transceiver component 110, and the filter unit 120 is configured to filter the signal transmitted by the optical transceiver component 110, the microprocessing unit 130 is electrically or wirelessly connected to the filter unit 120, and the microprocessing unit 130 is configured to process the signal transmitted by the filter unit 120, the data processing terminal 140 is electrically or wirelessly connected to the microprocessing unit 130, and the data processing terminal 140 is configured to process the signal transmitted by the microprocessing unit 130; the driving control element 150 is electrically or wirelessly connected to the optical transceiver component 110 and the microprocessing unit 130 respectively, and the driving control element 150 is configured to control the on / off and working mode of the optical transceiver component 110.

[0045] The aforementioned tested part 200 is a wrist or an arm, but is not limited thereto.

[0046] The optical transceiver assembly 110 includes an optical emitting element and an optical receiving element. The optical emitting element is used to emit an optical signal, and the optical receiving element is used to receive an optical signal.

[0047] Among them, the above-mentioned filtering unit 120 can be an amplifying filtering circuit. Since the human blood glucose signal detected during non-invasive detection by the non-invasive blood glucose detection system 100 is extremely small, the filtering unit 120 is needed to amplify the optical signal detected by the optical transceiver component 110. At the same time, the frequency band of the human PPG signal is approximately between 0.5-4Hz, and the filtering unit 120 is needed to filter out the signal outside this frequency band for subsequent further analysis and processing.

[0048] The microprocessing unit 130 may be a control chip, for example, an MCU chip, but is not limited thereto. The microprocessing unit 130 is used to control the overall operation of the non-invasive blood glucose detection system 100 and to process the signal transmitted by the filter unit 120.

[0049] The driving control element 150 may be a driving control circuit, but is not limited thereto. Specifically, the driving control element 150 is used to control the on / off and working mode of the optical transceiver assembly 110 .

[0050] The data processing terminal 140 may be a computer, a smart phone, or a tablet computer, but is not limited thereto. The data processing terminal 140 is connected to the microprocessing unit 130 via a wireless network or Bluetooth. The data processing terminal 140 is used for data analysis and processing.

[0051] Specifically, the optical transceiver assembly 110 includes: at least two light sources 111, a first detector 112 and at least two second detectors 113, the at least two light sources 111 are used to emit laser detection signals, the first detector 112 and the at least two second detectors 113 are used to detect returned laser signals, the at least two light sources 111 are arranged around the first detector 112, the at least two second detectors 113 are arranged around the light source 111, and the light detection surface of the first detector 112, the light detection surface of the at least two second detectors 113 and the light emitting surface of the at least two light sources 111 are facing the same direction.

[0052] The light source 111 , the first detector 112 and the second detector 113 are all electrically connected to the driving control element 150 and the filtering unit 120 .

[0053] Furthermore, the light source 111 is configured to emit a laser detection signal from the surface of the test site 200 to the analyte of the subcutaneous tissue, so as to constitute the light emitting part of the optical transceiver component 110; the first detector 112 is configured to detect short-path light signals returned from the surface of the test site 200 after at least two light sources 111 are emitted to the analyte of the subcutaneous tissue; the second detector 113 is configured to detect long-path light signals returned from the surface of the test site 200 after at least two light sources 111 are emitted to the analyte of the subcutaneous tissue. The first detector 112 and the second detector 113 constitute the light receiving part of the optical transceiver component 110.

[0054] The short optical path optical signal refers to the optical signal reflected by the analyte which is closer to the light source 111 , and the long optical path optical signal refers to the optical signal reflected by the analyte which is farther from the light source 111 .

[0055] It can be understood that when the non-invasive blood glucose detection system 100 in the present application needs to perform non-invasive blood glucose detection on the part to be detected 200, the light source 111, the first detector 112 and the second detector 113 are arranged on the surface of the part to be detected 200, and multiple light sources 111 are arranged around the first detector 112, and multiple second detectors 113 are arranged around the light source 111. The microprocessor unit 130 sends a control instruction to the drive control element 150, and after receiving the control instruction, the drive control element 150 sends a control instruction to the light source 111, the first detector 112 and the second detector 113 to control the light source 111 to emit an excitation light signal from the surface of the part to be detected 200 to the analyte of the subcutaneous tissue, the first detector 112 detects the short optical path light signal reflected from the analyte of the subcutaneous tissue from the surface of the part to be detected 200, and the second detector 113 detects the long optical path light signal reflected from the analyte of the subcutaneous tissue from the surface of the part to be detected 200.

[0056] The first detector 112 transmits the detected short optical path optical signal to the filter unit 120, and the second detector 113 transmits the detected long optical path optical signal to the filter unit 120. The filter unit 120 amplifies the short optical path optical signal and the long optical path optical signal. At the same time, the filter unit 120 filters out the signals in the frequency band outside 0.5-4Hz in the short optical path optical signal and the long optical path optical signal. After the filter unit 120 completes the amplification and filtering operations, it transmits the amplified and filtered short optical path optical signal and the long optical path optical signal to the microprocessing unit 130. After receiving the signal, the microprocessing unit 130 transmits the amplified and filtered short optical path optical signal and the long optical path optical signal to the data processing terminal 140. The data processing terminal 140 analyzes and processes the signal, calculates the optical concentration difference between the deep and shallow parts of the subcutaneous tissue, and obtains the blood sugar test result.

[0057] In the present application, multiple light sources 111 are arranged around the first detector 112, and multiple second detectors 113 are arranged around the light source 111, so that the light source 111 emits a laser signal from the surface of the test site 200 to the analyte of the subcutaneous tissue, the first detector 112 detects the short-path light signal of the analyte of the subcutaneous tissue from the surface of the test site 200, and the second detector 113 detects the long-path light signal of the analyte of the subcutaneous tissue from the surface of the test site 200, so that the short-path light signal and the long-path light signal are used to perform data analysis and processing to obtain the optical concentration difference between the deep and shallow parts of the skin, so as to reduce the influence of melanin and skin, improve the detection accuracy of non-invasive blood glucose, and ensure the accuracy of the non-invasive blood glucose detection results.

[0058] In one embodiment, at least two light sources 111 and at least two second detectors 113 are respectively arranged in an array on a circle with the first detector 112 as the center, that is, at least two light sources 111 and at least two second detectors 113 are respectively arranged in concentric circles with the first detector 112 as the center, so that the light source 111, the first detector 112 and the second detector 113 are regularly arranged, so that the first detector 112 and the second detector 113 can detect the optical signal of the analyte, thereby improving the detection accuracy of non-invasive blood glucose and ensuring the accuracy of the non-invasive blood glucose detection results; at the same time, it is convenient to assemble the light source 111, the first detector 112 and the second detector 113, thereby improving the assembly efficiency of the non-invasive blood glucose detection system 100.

[0059] In one embodiment, the first detector 112, at least two second detectors 113 and at least two light sources 111 are located on the same plane, that is, the distance between the first detector 112 and the measured part 200, the distance between the at least two second detectors 113 and the measured part 200, and the distance between the at least two light sources 111 and the measured part 200 are all the same, thereby further improving the detection accuracy of non-invasive blood glucose and ensuring the accuracy of the non-invasive blood glucose detection results.

[0060] Furthermore, the detection depth of the detector is related to the distance between the light sources. In the embodiments of the present application, refer to Figure 1, the distance between the first detector 112 and the light source 111 in the radial direction of the circle formed by the first detector 112 as the center is L1 mm, and the distance between the second detector 113 and the light source 111 in the radial direction of the circle formed by the first detector 112 as the center is L2 mm, which satisfies: 0.5≤L1 / L2<1. That is, the ratio of the distance L1 mm between the first detector 112 and the light source 111 in the radial direction of the circle formed by the first detector 112 as the center and the distance L2 mm between the second detector 113 and the light source 111 in the radial direction of the circle formed by the first detector 112 as the center can be controlled in the range of 0.5 to 1. For example, the ratio of L1 to L2 can be 0.5, 0.55, 0.6, 0.65, 0.7, 0.75, 0.8, 0.85, 0.9, 0.95 or 0.99 or a range consisting of any two of them. It is worth noting that the above specific numerical values ​​of the ratio of L1 to L2 are given for example only, and any value within the range of 0.5 to 1 is within the protection scope of the present application.

[0061] In the present application, the ratio of the distance L1 mm between the first detector 112 and the light source 111 in the radial direction of the circle formed with the first detector 112 as the center and the distance L2 mm between the second detector 113 and the light source 111 in the radial direction of the circle formed with the first detector 112 as the center is controlled within the range of 0.5 to 1, so that the first detector 112 detects the short-path light signal of the analyte of the subcutaneous tissue from the surface of the tested part 200, and the second detector 113 detects the long-path light signal of the analyte of the subcutaneous tissue from the surface of the tested part 200, thereby using the short-path light signal and the long-path light signal to perform data analysis and processing to obtain the optical concentration difference between the deep and shallow parts of the skin, so as to reduce the influence of melanin and skin, improve the detection accuracy of non-invasive blood glucose, and ensure the accuracy of the non-invasive blood glucose detection results.

[0062] It should be understood that the distance L1 mm between the first detector 112 and the light source 111 in the radial direction of the circle formed by the first detector 112 as the center and the distance L2 mm between the second detector 113 and the light source 111 in the radial direction of the circle formed by the first detector 112 as the center in the present application are not limited to the above ratio relationship, and other parameter relationships between the two, for example, L1 is greater than L2, or 1<L1 / L2≤2. Even if the first detector 112 is configured to detect the long optical path light signal returned after the at least two light sources 111 are emitted to the analyte; the second detector 113 is configured to detect the short optical path light signal returned after the at least two light sources 111 are emitted to the analyte, the technical solution in the present application can also be implemented and should also be regarded as an embodiment of the present application.

[0063] In one embodiment, the distance L1 mm between the first detector 112 and the light source 111 in the radial direction of the circle formed with the first detector 112 as the center also satisfies: 0.5mm≤L1≤5mm. That is, the distance L1 mm between the first detector 112 and the light source 111 in the radial direction of the circle formed with the first detector 112 as the center can be controlled within the range of 0.5mm to 5mm. For example, the distance L1 mm between the first detector 112 and the light source 111 in the radial direction of the circle formed with the first detector 112 as the center can be 0.5mm, 1mm, 1.5mm, 2mm, 2.5mm, 3mm, 3.5mm, 4mm, 4.5mm or 5mm, or a range consisting of any two of them. It is worth noting that the above-mentioned specific numerical value of the distance L1 mm is only given as an example, and any value within the range of 0.5 to 5mm is within the protection scope of this application. The present application controls the distance L1 mm between the first detector 112 and the light source 111 in the radius direction of the circle formed with the first detector 112 as the center within the range of 0.5 mm to 5 mm, so that the first detector 112 can more accurately detect the short-path light signals returned after at least two light sources 111 are irradiated toward the analyte, thereby ensuring the detection accuracy of the first detector 112, thereby improving the detection accuracy of non-invasive blood glucose and ensuring the accuracy of the non-invasive blood glucose detection results.

[0064] The distance L2 mm between the second detector 113 and the light source 111 in the radial direction of the circle formed by the first detector 112 as the center also satisfies: 0.5mm<L2≤10mm. That is, the distance L2 mm between the second detector 113 and the light source 111 in the radial direction of the circle formed by the first detector 112 as the center can be controlled within the range of 0.5mm~10mm. For example, the distance L2 mm between the second detector 113 and the light source 111 in the radial direction of the circle formed by the first detector 112 as the center can be 0.51mm, 1mm, 1.5mm, 2mm, 2.5mm, 3mm, 3.5mm, 4mm, 4.5mm, 5mm, 5.5mm, 6mm, 6.5mm, 7mm, 7.5mm, 8mm, 8.5mm, 9mm, 9.5mm or 10mm, or any two of them. It is worth noting that the above-mentioned specific numerical value of the distance L2mm is given for example only, and any value within the range of 0.5mm to 10mm is within the protection scope of this application. This application controls the distance L2mm between the second detector 113 and the light source 111 in the radius direction of the circle formed with the first detector 112 as the center within the range of 0.5mm to 10mm, so that the second detector 113 can more accurately detect the long optical path light signal returned after at least two light sources 111 are emitted to the analyte, thereby ensuring the detection accuracy of the second detector 113, thereby improving the detection accuracy of non-invasive blood glucose and ensuring the accuracy of the non-invasive blood glucose detection results.

[0065] In one embodiment, the first detector 112 and the second detector 113 are both photodetectors with low dark current and large target area.

[0066] Further, in one embodiment, the number of the second detectors 113 is n2, satisfying: n2 ≥ 3. Specifically, for example, the number n2 of the second detectors 113 can be 3, 4, 6, 8, 10, 12, etc. This is not specifically limited in the present application and can be specifically set according to actual circumstances.

[0067] In this embodiment, refer to Figure 1 , the number n2 of the second detectors 113 is 4.

[0068] The fluctuation of the light signal caused by the change of blood sugar concentration is extremely weak. The detection system must have a high signal-to-noise ratio so that the test results can meet the accuracy required in daily blood sugar testing or clinical diagnosis. Therefore, the intensity and stability of the incident light are extremely high. Therefore, in the embodiment of the present application, the light source 111 is a laser diode. The laser emitted by the laser diode has good monochromaticity and high stability. In this application, the light source 111 uses a laser diode to further improve the accuracy of non-invasive blood sugar detection.

[0069] Specifically, the light source 111 may be an edge emitting laser, or a vertical cavity surface emitting laser, but the invention is not limited thereto.

[0070] In an embodiment of the present application, the light sources in the at least two light sources 111 mentioned above have multiple wavelengths.

[0071] The wavelength of the light source 111 may include the near-infrared region of the harmonic vibration and the combined frequency vibration of the glucose molecule, and may also include an absorption band that does not conform to the glucose molecule, which can be used for comparison to improve the detection accuracy.

[0072] Further, the wavelength of the at least two light sources 111 is λnm, which satisfies: 800nm≤λ≤2600nm. That is, the wavelength λnm of the light source 111 can be controlled within the range of 800nm ​​to 2600nm. For example, the wavelength λnm of the light source 111 can be one of 800nm, 900nm, 940nm, 980nm, 1000nm, 1100nm, 1310nm, 1450nm, 1536nm, 1688nm, 1800nm, 2000nm, 2200nm, 2400nm, and 2600nm. It is worth noting that the above-mentioned specific values ​​of the wavelength λ are only given by way of example, and any value within the range of 800nm ​​to 2600nm is within the protection scope of the present application.

[0073] Further, the number of light sources 111 is n1, and satisfies: n1 ≥ 3. Specifically, for example, the number n2 of the second detectors 113 can be 3, 6, 9, 12, 15, etc. This application does not make a specific limitation and can be specifically set according to actual circumstances.

[0074] Reference Figure 1 There are 12 light sources 111, and the light sources 111 have 3 different wavelengths. There are 4 light sources 111 of each wavelength, and a total of 12 light sources 111 are arranged in an array on a circle with the first detector 112 as the center.

[0075] Among them, in the present application, the laser signals emitted by the light sources 111 of multiple different wavelengths can be detected by the first detector 112 and the second detector 113 of different models. Specifically, for example, when the wavelength λnm of the light source 111 is in the range of 400-1100nm, the first detector 112 and the second detector 113 can use silicon detectors, and when the wavelength λnm of the light source 111 is in the range of 900-1700nm, the first detector 112 and the second detector 113 can use three-five group detectors, etc. In the present application, different models of first detectors 112 and second detectors 113 are set to detect the laser signals of the light sources 111 of multiple different wavelengths, so as to ensure that the laser signals of the light sources 111 of different wavelengths are accurately detected, so as to improve the detection accuracy of the detector, thereby improving the detection accuracy of non-invasive blood glucose.

[0076] In the present application, multiple light sources 111 adopt multiple different wavelengths, and the wavelength λnm of the light source 111 is controlled within the range of 800 to 2600nm, so as to use multiple light sources 111 with different wavelengths for detection, which greatly improves the detection accuracy and stability, thereby improving the detection accuracy of non-invasive blood glucose.

[0077] In order to further improve the non-invasive blood glucose detection accuracy of the non-invasive blood glucose detection system 100, in the embodiment of the present application, refer to Figure 2 The above-mentioned optical transceiver assembly 110 also includes: at least two third detectors 114, the above-mentioned at least two third detectors 114 are arranged around the second detector 113, the above-mentioned at least two third detectors 114 and the at least two second detectors 113 are located in the same plane, and the light detection surfaces of the above-mentioned at least two third detectors 114 and the light detection surfaces of the at least two second detectors 113 face the same direction.

[0078] In the present application, the third detector 114 is provided to detect the optical signal with a longer optical path of the subcutaneous tissue using the third detector 114, thereby further improving the detection accuracy and further improving the detection accuracy of non-invasive blood glucose.

[0079] The third detector 114 is a photoelectric detector with low dark current and large target area, so as to ensure that the third detector 114 can accurately detect the light signal emitted by the light source, thereby improving the detection accuracy of non-invasive blood glucose.

[0080] In the embodiment of the present application, the number of the third detectors 114 is n3, satisfying: n3 ≥ 3. Specifically, for example, the number n2 of the third detectors 114 can be 3, 4, 6, 8, 10, 12, etc. This is not specifically limited in the present application and can be specifically set according to actual circumstances.

[0081] In a preferred embodiment, reference Figure 2, the number n3 of the third detectors 114 is 4.

[0082] It should be understood that the present application is not limited to setting the third detector 114 around the second detector 113, and the detector array can continue to be increased, for example: further increasing the fourth detector array to surround the periphery of the third detector 114, further increasing the fifth detector array to surround the periphery of the fourth detector array, etc., to further improve the detection accuracy of non-invasive blood glucose, which should also be regarded as an embodiment of the present application. The introduction provided in the above steps is only used to help understand the method, structure and core idea of ​​the present application. For ordinary technicians in this technical field, without departing from the principles of the present application, several improvements and modifications can be made to the present application, and these improvements and modifications also fall within the scope of protection of the claims of the present application.

Claims

1. A non-invasive blood glucose detection system, characterized in that: include: Optical transceiver components; A filtering unit, electrically connected to the optical transceiver assembly, for filtering the signal transmitted by the optical transceiver assembly; as well as A microprocessing unit, electrically connected to the filter unit, and processing the signal transmitted by the filter unit; The optical transceiver assembly includes: at least two light sources, a first detector and at least two second detectors, the at least two light sources are used to emit laser detection signals, and the first detector and at least two second detectors are used to detect the returned laser signals; The at least two light sources are arranged around the first detector; the at least two second detectors are arranged around the light source; The light detection surface of the first detector, the light detection surfaces of the at least two second detectors, and the light emitting surfaces of the at least two light sources face the same direction.

2. The non-invasive blood glucose detection system according to claim 1, characterized in that: The at least two light sources and the at least two second detectors are respectively arranged in an array on a circle with the first detector as the center.

3. The non-invasive blood glucose detection system according to claim 1, characterized in that: The first detector, the at least two second detectors and the at least two light sources are located on the same plane.

4. The non-invasive blood glucose detection system according to claim 1, characterized in that: The light source is configured to emit a laser signal toward the analyte; The first detector is configured to detect short-path optical signals returned by the at least two light sources after being emitted toward the analyte; The second detector is configured to detect the long optical path optical signals returned by the at least two light sources after being emitted toward the analyte.

5. The non-invasive blood glucose detection system according to claim 4, characterized in that: The distance between the first detector and the light source in the radial direction of the circle formed by the first detector as the center is L1 mm, and the distance between the second detector and the light source in the radial direction of the circle formed by the first detector as the center is L2 mm, satisfying: 0.5≤L1 / L2<1.

6. The non-invasive blood glucose detection system according to claim 5, characterized in that: The distance L1 mm between the first detector and the light source in the radius direction of a circle formed with the first detector as the center also satisfies: 0.5 mm ≤ L1 ≤ 5 mm; and / or, A distance L2 mm between the second detector and the light source in the radius direction of a circle formed with the first detector as the center also satisfies: 0.5 mm<L2≤10 mm.

7. The non-invasive blood glucose detection system according to any one of claims 1 to 6, characterized in that: The light sources of the at least two light sources have multiple wavelengths, and the wavelengths of the at least two light sources are λnm, satisfying: 800nm≤λ≤2600nm.

8. The non-invasive blood glucose detection system according to claim 1, characterized in that: The optical transceiver assembly also includes: at least two third detectors, the at least two third detectors are arranged around the second detector, the at least two third detectors and the at least two second detectors are located in the same plane, and the light detection surfaces of the at least two third detectors and the light detection surfaces of the at least two second detectors face the same direction.

9. The non-invasive blood glucose detection system according to claim 8, characterized in that: The number of the light sources is n1, satisfying: n1 ≥ 3; and / or, The number of the second detectors is n2, satisfying: n2 ≥ 3; and / or, The number of the third detectors is n3, satisfying: n3≥3.

10. The non-invasive blood glucose detection system according to claim 1, characterized in that: Also includes: a data processing terminal, electrically or wirelessly connected to the microprocessing unit, the data processing terminal being configured to process a signal transmitted by the microprocessing unit; as well as A driving control element is electrically or wirelessly connected to the optical transceiver assembly and the microprocessor unit, respectively, and is configured to control the on / off and working mode of the optical transceiver assembly.

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